US20020161394A1 - Aortic filter catheter - Google Patents

Aortic filter catheter Download PDF

Info

Publication number
US20020161394A1
US20020161394A1 US10/108,245 US10824502A US2002161394A1 US 20020161394 A1 US20020161394 A1 US 20020161394A1 US 10824502 A US10824502 A US 10824502A US 2002161394 A1 US2002161394 A1 US 2002161394A1
Authority
US
United States
Prior art keywords
catheter
filter
aortic
filter assembly
embolic
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/108,245
Inventor
John Macoviak
James Leary
Wilfred Samson
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cardeon Corp
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Priority to US10/108,245 priority Critical patent/US20020161394A1/en
Assigned to CARDEON CORPORATION reassignment CARDEON CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: LEARY, JAMES L., MACOVIAK, JOHN A., SAMSON, WILFRED J.
Publication of US20020161394A1 publication Critical patent/US20020161394A1/en
Assigned to SILICON VALLEY BANK, GATX VENTURES, INC. reassignment SILICON VALLEY BANK SECURITY INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CARDEON CORPORATION
Abandoned legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/01Filters implantable into blood vessels
    • A61F2/013Distal protection devices, i.e. devices placed distally in combination with another endovascular procedure, e.g. angioplasty or stenting
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12099Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder
    • A61B17/12109Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/12136Balloons
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/12168Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure
    • A61B17/12172Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure having a pre-set deployed three-dimensional shape
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B17/221Gripping devices in the form of loops or baskets for gripping calculi or similar types of obstructions
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/01Filters implantable into blood vessels
    • A61F2/013Distal protection devices, i.e. devices placed distally in combination with another endovascular procedure, e.g. angioplasty or stenting
    • A61F2/014Retrograde blood flow filters, i.e. device inserted against the blood flow direction
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22051Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
    • A61B2017/22065Functions of balloons
    • A61B2017/22067Blocking; Occlusion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/01Filters implantable into blood vessels
    • A61F2/011Instruments for their placement or removal
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/01Filters implantable into blood vessels
    • A61F2002/018Filters implantable into blood vessels made from tubes or sheets of material, e.g. by etching or laser-cutting
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/30Joints
    • A61F2002/30001Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30003Material related properties of the prosthesis or of a coating on the prosthesis
    • A61F2002/3006Properties of materials and coating materials
    • A61F2002/3008Properties of materials and coating materials radio-opaque, e.g. radio-opaque markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/30Joints
    • A61F2002/30001Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30003Material related properties of the prosthesis or of a coating on the prosthesis
    • A61F2002/3006Properties of materials and coating materials
    • A61F2002/30092Properties of materials and coating materials using shape memory or superelastic materials, e.g. nitinol
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A61F2210/0019Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at only one temperature whilst inside or touching the human body, e.g. constrained in a non-operative shape during surgery, another temperature only occurring before the operation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A61F2210/0023Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at different temperatures whilst inside or touching the human body, heated or cooled by external energy source or cold supply
    • A61F2210/0033Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at different temperatures whilst inside or touching the human body, heated or cooled by external energy source or cold supply electrically, e.g. heated by resistor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0004Rounded shapes, e.g. with rounded corners
    • A61F2230/0006Rounded shapes, e.g. with rounded corners circular
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063Three-dimensional shapes
    • A61F2230/0067Three-dimensional shapes conical
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063Three-dimensional shapes
    • A61F2230/0069Three-dimensional shapes cylindrical
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063Three-dimensional shapes
    • A61F2230/0073Quadric-shaped
    • A61F2230/008Quadric-shaped paraboloidal
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0003Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having an inflatable pocket filled with fluid, e.g. liquid or gas
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0023Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in porosity
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0096Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers
    • A61F2250/0098Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers radio-opaque, e.g. radio-opaque markers

Definitions

  • the present invention relates generally to a catheter or cannula for infusion of oxygenated blood or other fluids into a patient for cardiopulmonary support and cerebral protection. More particularly, it relates to an arterial perfusion catheter with a deployable embolic filter for protecting a patient from adverse effects due to emboli that are dislodged during cardiopulmonary bypass.
  • Cardiopulmonary bypass is an important enabling technology that has helped to make these advances possible.
  • CABG coronary artery bypass grafting
  • CPB cardiopulmonary bypass
  • Chief among these concerns is the potential for stroke or neurologic deficit associated with heart surgery and with cardiopulmonary bypass.
  • One of the likely causes of stroke and of neurologic deficit is the release of emboli into the blood stream during heart surgery.
  • Potential embolic materials include atherosclerotic plaques or calcific plaques from within the ascending aorta or cardiac valves and thrombus or clots from within the chambers of the heart. These potential emboli may be dislodged during surgical manipulation of the heart and the ascending aorta or due to high velocity jetting (sometimes called the “sandblasting effect”) from the aortic perfusion cannula. Air that enters the heart chambers or the blood stream during surgery through open incisions or through the aortic perfusion cannula is another source of potential emboli. Emboli that lodge in the brain may cause a stroke or other neurologic deficit.
  • Vena cava filters are devices that are implanted into a patient's inferior vena cava for capturing thromboemboli and preventing them from entering the right heart and migrating into the pulmonary arteries. These are generally designed for permanent implantation and are only intended to capture relatively large thrombi, typically those over a centimeter in diameter, that could cause a major pulmonary embolism.
  • Vena cava filters are also not adapted for simultaneously providing arterial blood perfusion in connection with cardiopulmonary bypass.
  • the present invention takes the form of a perfusion filter catheter or cannula having an embolic filter assembly mounted on an elongated tubular catheter shaft.
  • the elongated tubular catheter shaft is adapted for introduction into a patient's ascending aorta either by a peripheral arterial approach or by a direct aortic puncture.
  • a fine filter mesh for capturing macroemboli and/or microemboli is mounted on the embolic filter assembly.
  • the embolic filter assembly has an undeployed state in which the filter is compressed or wrapped tightly around the catheter shaft and a deployed state in which the embolic filter assembly expands to the size of the aortic lumen and seals against the inner wall of the aorta.
  • the embolic filter assembly can be passively or actively deployable. Various mechanisms are disclosed for both passive and active deployment of the embolic filter assembly.
  • an outer tube may cover the embolic filter assembly when it is in the undeployed state.
  • Radiopaque markers and/or sonoreflective markers may be located on the catheter and/or the embolic filter assembly.
  • a perfusion lumen extends through the elongated tubular catheter shaft to one or more perfusion ports upstream of the embolic filter assembly. Oxygenated blood is perfused through the perfusion lumen and any embolic materials that might be dislodged are captured in the deployed embolic filter assembly.
  • the surface area of the filter mesh be greater than twice the cross-sectional area of the aortic lumen, more preferably three, four, five or six times greater than luminal cross section of the aorta.
  • the embolic filter assembly is also configured to hold at least a majority of the filter mesh away from the aortic wall when deployed to maximize the effective filter surface area.
  • the embolic filter assembly configurations described include an elongated cone, a frustum of a cone, a trumpet-shape, a modified trumpet-shape, and helically, circumferentially and longitudinally convoluted shapes. Further configurations are described having standoff members for centering the embolic filter assembly within the aorta and for holding at least a majority of the filter mesh away from the aortic walls when deployed.
  • Embodiments are also described that combine the perfusion filter catheter with an aortic occlusion device, which may be a toroidal balloon, an expandable balloon or a selectively deployable external catheter flow control valve.
  • the combined device allows percutaneous transluminal administration of cardiopulmonary bypass and cardioplegic arrest with protection from undesirable embolic events.
  • An embodiment of the perfusion filter catheter is described having an aortic transillumination system for locating and monitoring the position and the deployment state of the catheter and the embolic filter assembly without fluoroscopy.
  • the perfusion filter catheter is introduced into the patient's aorta with the embolic filter assembly in a collapsed state either by a peripheral arterial approach or by a direct aortic puncture.
  • the embolic filter assembly is advanced across the aortic arch and into the ascending aorta.
  • the embolic filter assembly is either actively or passively deployed.
  • the position of the catheter and the deployment state of the embolic filter assembly may be monitored using fluoroscopy, ultrasound, transesophageal echography (TEE) or aortic transillumination.
  • embolic filter assembly Once the embolic filter assembly is deployed, oxygenated blood may be infused into the aorta through the perfusion lumen. Any potential emboli are captured by the embolic filter assembly and prevented from entering the neurovasculature or other branches downstream. After use, the embolic filter assembly is returned to the collapsed position and the catheter is withdrawn from the patient.
  • FIGS. 1 - 3 show a perfusion filter catheter configured for retrograde deployment via a peripheral arterial access point.
  • FIG. 1 is a cutaway perspective view of the perfusion filter catheter deployed within the aorta via femoral artery access.
  • FIG. 2 shows the distal end of the catheter with the embolic filter assembly in a deployed state.
  • FIG. 3 shows the distal end of the catheter with the embolic filter assembly in a collapsed state for insertion or withdrawal of the device from the patient.
  • FIGS. 4 - 6 show a method of passively deploying an embolic filter assembly on a perfusion filter catheter.
  • FIGS. 7, 7A, 8 and 8 A show a flow-assisted method of passively deploying an embolic filter assembly on a perfusion filter catheter.
  • FIGS. 9 - 11 show a method of passively deploying a self-expanding and self-supporting embolic filter assembly on a perfusion filter catheter.
  • FIGS. 12 - 14 show a method of actively deploying an embolic filter assembly with a collapsible outer hoop and a plurality of actuation wires.
  • FIGS. 15 - 17 show a method of actively deploying an embolic filter assembly with an inflatable filter support structure.
  • FIGS. 18 - 20 show a method of actively deploying a spiral fluted embolic filter assembly by twisting or furling the embolic filter assembly around an inner catheter shaft.
  • FIGS. 21 - 23 show a method of actively deploying a circumferentially pleated embolic filter assembly on a perfusion filter catheter.
  • FIG. 24 shows a perfusion filter catheter adapted for retrograde deployment via subclavian artery access.
  • FIGS. 25 - 27 show a perfusion filter catheter adapted for antegrade deployment via direct aortic puncture.
  • FIGS. 28 and 29 show a perfusion filter catheter having an embolic filter assembly with a graded porosity filter screen.
  • FIGS. 30 and 30A show a perfusion filter catheter having a longitudinally fluted embolic filter assembly.
  • FIGS. 31 and 31A show a perfusion filter catheter having a longitudinally ribbed embolic filter assembly.
  • FIG. 32 shows a perfusion filter catheter having an embolic filter assembly that is surrounded by a cage of longitudinally oriented standoff members.
  • FIG. 33 shows a perfusion filter catheter having an embolic filter assembly that is surrounded by a cage of coiled wire standoff members.
  • FIG. 34 shows a perfusion filter catheter having an embolic filter assembly that is surrounded by a cage of coarse netting.
  • FIG. 35 shows a cutaway view of a perfusion filter catheter having an embolic filter assembly that is surrounded by a fender made from a porous foam or a fibrous network.
  • FIGS. 36 and 37 show an alternate embodiment of a perfusion filter catheter with a passively deployed embolic filter assembly.
  • FIGS. 38 - 41 show an alternate embodiment of a perfusion filter catheter with an actively deployed embolic filter assembly having a filter support structure with a preshaped, superelastic actuation wire.
  • FIGS. 42 and 43 show another alternate embodiment of a perfusion filter catheter with an actively deployed embolic filter assembly having a filter support structure with a preshaped, superelastic wire purse string loop.
  • FIGS. 44 and 45 show another alternate embodiment of a perfusion filter catheter with an actively deployed inflatable embolic filter assembly.
  • FIGS. 46 - 50 show the operation of an embodiment of a perfusion filter catheter that combines an embolic filter assembly with a toroidal balloon aortic occlusion device.
  • FIG. 51 shows an embodiment of a perfusion filter catheter that combines an embolic filter assembly with an inflatable balloon aortic occlusion device.
  • FIG. 52 shows an embodiment of a perfusion filter catheter that combines an embolic filter assembly with a selectively deployable external catheter flow control valve.
  • FIG. 53 shows an embodiment of a perfusion filter catheter with an embolic filter assembly having areas of different filter porosity.
  • FIG. 54 shows an embodiment of a perfusion filter catheter with a fiberoptic system for aortic transillumination.
  • FIGS. 1 - 3 show a perfusion filter catheter 100 according to the present invention configured for retrograde deployment via a peripheral arterial access point.
  • FIG. 1 is a cutaway perspective view of the perfusion filter catheter 100 deployed within the aorta of a patient via femoral artery access.
  • FIG. 2 shows the distal end of the catheter 100 with the embolic filter assembly 102 in a deployed state.
  • FIG. 3 shows the distal end of the catheter with the embolic filter assembly 102 ′ in a collapsed state for insertion or withdrawal of the device from the patient.
  • the perfusion filter catheter 100 includes an elongated tubular catheter shaft 104 with a proximal end 108 and distal end 110 .
  • the catheter shaft 104 is preferably extruded of a flexible thermoplastic material or a thermoplastic elastomer. Suitable materials for the catheter shaft 104 include, but are not limited to, polyvinylchloride, polyurethane, polyethylene, polypropylene, polyamides (nylons), and alloys or copolymers thereof, as well as braided, coiled or counterwound wire or filament reinforced composites.
  • the tubular catheter shaft 104 may have a single lumen or multilumen construction.
  • the catheter 100 has a single perfusion lumen 106 extending from the proximal end 108 to the distal end 110 of the catheter shaft 104 .
  • the perfusion lumen 106 is open at the distal end 110 of the catheter shaft 104 .
  • the distal end 110 of the catheter shaft 104 may have a simple beveled or rounded distal edge, as shown, or it may include additional side ports or a flow diffuser to reduce jetting when oxygenated blood is infused through the perfusion lumen 106 .
  • the proximal end 108 of the elongated tubular catheter shaft 104 is adapted for connecting the perfusion lumen 106 to a cardiopulmonary bypass pump or other source of oxygenated blood using standard barb connectors or other connectors, such as a standard luer fitting (not shown).
  • the catheter shaft 104 is made with thin walled construction to maximize the internal diameter and therefore the flow rate of the perfusion lumen 106 for a given outside diameter and length of the catheter shaft 104 .
  • Thin walled construction also allows the outside diameter of the catheter shaft 104 to be minimized in order to reduce the invasiveness of the procedure and to reduce trauma at the insertion site.
  • the perfusion lumen 106 should be configured to allow sufficient blood flow to preserve organ function without hemolysis or other damage to the blood.
  • a catheter shaft 104 of 18-24 French size (6-8 mm outside diameter) is sufficient to deliver the requisite 3-4 liters of oxygenated blood to preserve organ function.
  • the size of the catheter shaft 104 can be reduced to 9-18 French size (3-6 mm outside diameter) for delivering 0.5-3 liters of oxygenated blood to preserve organ function.
  • the catheter shaft 104 should have a length sufficient to reach from the arterial access point where it is inserted to the ascending aorta of the patient.
  • the catheter shaft 104 preferably has a length from approximately 80-120 cm.
  • a deployable embolic filter assembly 102 is located just proximal to the distal end 110 of the catheter shaft 104 .
  • the embolic filter assembly 102 includes a filter screen 112 made of a fine mesh material.
  • the fine mesh material of the filter screen 112 may be a woven or knitted fabric, such as Dacron polyester or nylon mesh, or other textile fabrics, or it may be a nonwoven fabric, such as a spun bonded polyolefin or expanded polytetrafluoroethylene or other nonwoven materials.
  • the fine mesh material of the filter screen 112 may be woven, knitted or otherwise formed from monofilament or multifilament fibers.
  • the fine mesh material of the filter screen 112 may also be a fine wire mesh or a combination of wire and textile fibers.
  • the fine mesh material of the filter screen 112 may be an open cell foam material.
  • the fine mesh material of the filter screen 112 must be nontoxic and hemocompatible, that is, non-thrombogenic and non-hemolytic.
  • the fine mesh material of the filter screen 112 has a high percentage of open space, with a uniform pore size.
  • the pore size of the filter screen 112 can be chosen to capture macroemboli only or to capture macroemboli and microemboli. In most cases the pore size of the filter screen 112 will preferably be in the range of 1-200 micrometers.
  • the pore size of the filter screen 112 will preferably be in the range of 50-200 micrometers, more preferably in the range of 80-100 micrometers.
  • the pore size of the filter screen 112 will preferably be in the range of 1-100 micrometers, more preferably in the range of 5-20 micrometers.
  • a larger pore size e.g. up to 1000 micrometers (1 mm) or larger, would also be useful.
  • a combination of filter materials having different pore sizes may be used.
  • the material of the filter screen in each embodiment of the filter catheter may be made of or coated with an adherent material or substance to capture or hold embolic debris which comes into contact with the filter screen within the embolic filter assembly.
  • adherent materials include, but are not limited to, known biocompatible adhesives and bioadhesive materials or substances, which are hemocompatible and non-thrombogenic. Such materials are known to those having ordinary skill in the art and are described in, among other references, U.S. Pat. Nos. 4,768,523, 5,055,046, 5,066,709, 5,197,973, 5,225,196, 5,374,431, 5,578,310, 5,645,062, 5,648,167, 5,651,982, and 5,665,477.
  • only the upstream side of the elements of the filter screen are coated with the adherent material to positively capture the embolic debris which comes in contact with the upstream side of the filter screen after entering the filter assembly.
  • Other bioactive substances for example, heparin or thrombolytic agents, may be impregnated into or coated on the surface of the filter screen material or incorporated into an adhesive coating.
  • the embolic filter assembly 102 is movable between a collapsed state, as shown in FIG. 3, and an expanded or deployed state, as shown in FIGS. 1 and 2.
  • the filter screen 112 may be attached directly to the catheter shaft 104 and it may constitute the entire embolic filter assembly 102 , particularly if the filter screen 112 is made of a resilient or semirigid fabric that has enough body to be self-supporting in the deployed state.
  • the embolic filter assembly 102 will also include a filter support structure 114 , particularly if a highly flexible or flaccid material is used for the filter screen 112 .
  • the filter support structure 114 attaches and supports the filter screen 112 on the catheter shaft 104 .
  • the filter support structure 114 is constructed with an outer hoop 116 and a plurality of struts 118 which extend approximately radially from a ring-shaped hub 126 that is mounted on the catheter shaft 104 .
  • four struts 118 are shown, however, two, three or more struts 118 may be used.
  • the open distal end 122 of the filter screen 112 is attached to the outer hoop 116 and the proximal end 120 of the filter screen 112 is sealingly attached to the catheter shaft 104 .
  • the outer hoop 116 of the filter support structure 114 holds the open distal end 122 of the filter screen 112 against the inner wall of the aorta, as shown in FIG. 1.
  • the outer hoop 116 of the filter support structure 114 and the distal end 122 of the filter screen 112 have a diameter of approximately 2.5 to 4 cm, plus or minus 0.5 cm. Larger and smaller diameter filter support structures 114 may be made to accommodate patients with distended or Marfan syndrome aortas or for pediatric patients.
  • the embolic filter assembly 102 may be deployed by a passive means or by an active means.
  • Passive means for deploying the embolic filter assembly 102 could include using the elastic memory of the filter screen 112 and/or the filter support structure 114 to deploy the embolic filter assembly 102 , and/or using pressure from the blood flow in the aorta to deploy the embolic filter assembly 102 .
  • active means for deploying the embolic filter assembly 102 could include one or more actuation members within the catheter shaft 104 for mechanically actuating the filter support structure 114 to deploy the embolic filter assembly 102 from the proximal end 108 of the catheter 100 .
  • Shape memory materials may also be used as actuation members for deploying the embolic filter assembly 102 .
  • active means for deploying the embolic filter assembly 102 could include one or more lumens within the catheter shaft 104 for hydraulically actuating the filter support structure 114 to deploy the embolic filter assembly 102 .
  • Passive means may be used to augment the action of the active deployment means.
  • an outer tube 124 may be provided to cover the embolic filter assembly 102 when it is in the collapsed state in order to create a smooth outer surface for insertion and withdrawal of the catheter 100 and to prevent premature deployment of the embolic filter assembly 102 , particularly if passive deployment means are used.
  • the perfusion filter catheter 100 is prepared for use by folding or compressing the embolic filter assembly 102 into a collapsed state within the outer tube 124 , as shown in FIG. 3.
  • the distal end 110 of the catheter 100 is inserted into the aorta in a retrograde fashion. Preferably, this is done through a peripheral arterial access, such as the femoral artery or subclavian artery, using the Seldinger technique or an arterial cutdown.
  • the catheter 100 may be introduced directly through an incision into the descending aorta after the aorta has been surgically exposed.
  • the embolic filter assembly 102 is advanced up the descending aorta and across the aortic arch while in the collapsed state.
  • the position of the catheter 100 may be monitored using fluoroscopy or ultrasound, such as transesophageal echography (TEE).
  • Appropriate markers which may include radiopaque markers and/or sonoreflective markers, may be located on the distal end 110 of the catheter 100 and/or the embolic filter assembly 102 to enhance imaging and to show the position of the catheter 100 and the deployment state of the embolic filter assembly 102 .
  • a distal portion of the catheter shaft 104 may be precurved to match the curvature of the aortic arch to aid in placement and stabilization of the catheter 100 and the embolic filter assembly 102 within the aorta.
  • oxygenated blood may be infused through the perfusion lumen 106 to augment cardiac output of the beating heart or to establish cardiopulmonary bypass so that the heart can be arrested. Any potential emboli are captured by the filter screen 112 and prevented from entering the neurovasculature or other branches downstream.
  • the embolic filter assembly 102 is returned to the collapsed position and the catheter 100 is withdrawn from the patient.
  • the embolic filter assembly 102 is configured so that, when it is in the deployed state, at least a majority of the filter screen 112 is held away from the aortic walls so that flow through the pores of the filter screen 112 is not occluded by contact with the aortic wall. In addition, this also assures that blood flow into the side branches of the aorta will not be obstructed by the filter screen 112 . In this way, each side branch of the aorta will receive the benefit of flow through the full surface area of the filter screen 112 so that blood flow is not restricted by the area of the ostium of each side branch. In the illustrative embodiment of FIGS.
  • the filter screen 112 has a roughly conical shape with an open distal end 122 .
  • the conical shape holds the fine mesh material of the filter screen 112 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 112 .
  • FIGS. 4 - 11 show various methods of passively deploying the embolic filter assembly 102
  • FIGS. 12 - 23 show various methods of actively deploying the embolic filter assembly 102
  • FIGS. 4 - 6 show one method of passively deploying the embolic filter assembly 102 .
  • the outer hoop 116 and the struts 118 of the filter support structure 114 are made of an elastic or superelastic metal or polymer, for example a superelastic nickel/titanium alloy, which is easily deformed into the collapsed state and which expands passively from the collapsed state to the deployed state.
  • the struts 118 are folded back in the proximal direction and the outer hoop 116 is folded against the catheter shaft 104 along with the material of the filter screen 112 .
  • the outer tube 124 is placed over the folded embolic filter assembly 102 to hold it in the collapsed position.
  • the outer tube 124 is pulled back, as shown in FIG. 5, to release the folded embolic filter assembly 102 .
  • the outer hoop 116 and struts 118 expand the filter screen 112 to its deployed position, shown in FIG.
  • the embolic filter assembly 102 is returned to the collapsed position by advancing the outer tube 124 distally over the filter screen 112 and the filter support structure 114 , then the catheter 100 is withdrawn from the patient.
  • FIGS. 7, 7A, 8 and 8 A show another method of passively deploying an embolic filter assembly 132 on a perfusion filter catheter 130 .
  • the filter support structure includes a plurality of struts 136 which are hinged or flexibly attached at their inner, proximal ends to the catheter shaft 134 .
  • the struts 136 may be made of either a metal or a polymer.
  • the distal end 138 of the filter screen 140 is attached to the struts 136 along an outer, distal portion of the struts 136 .
  • the proximal end 146 of the filter screen 140 is sealingly attached to the catheter shaft 134 .
  • the portion of the filter screen 140 attached to the struts 136 forms a skirt 142 along the distal edge of the filter assembly 132 .
  • the remaining portion of the filter screen 140 forms a filter pocket 144 along the proximal end of the filter assembly 132 .
  • the skirt 142 and the filter pocket 144 may be made of the same filter material or they may be made of different filter materials having different porosities.
  • the skirt 142 of the filter screen 140 may even be made of a nonporous material.
  • FIG. 7A is a cutaway view of the catheter 130 with the embolic filter assembly 132 in the collapsed position.
  • the material of the filter screen 140 is folded around or in between the struts 136 .
  • the outer tube 148 is placed over the folded embolic filter assembly 132 to hold it in the collapsed position. Once the perfusion filter catheter 130 is in position within the patient's aorta, the outer tube 148 is pulled back, as shown in FIG. 8, to release the folded embolic filter assembly 132 .
  • FIG. 8A is a cutaway view of the catheter 130 with the embolic filter assembly 132 in the deployed position.
  • the struts 136 may be resiliently biased toward the deployed position to assist in passive deployment of the embolic filter assembly 132 .
  • the skirt 142 of the filter screen 140 naturally and atraumatically seals against the aortic wall.
  • the passive deployment of the skirt 142 also naturally compensates for patient-to-patient variations in aortic luminal diameter.
  • the filter pocket 144 of the embolic filter assembly 132 is held away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 140 .
  • FIGS. 9 - 11 show another method of passively deploying an embolic filter assembly 152 on a perfusion filter catheter 150 .
  • the filter screen 154 is self-expanding and self-supporting, so no separate filter support structure is needed.
  • the embolic filter assembly 152 includes resilient wires or filaments 156 that are interwoven with the fibers of the filter screen 154 .
  • the resilient wires or filaments 156 may be attached to the interior or exterior surface of the filter screen 154 fabric.
  • the resilient wires or filaments 156 may be made of either a polymer or a metal, such as an elastic or superelastic alloy.
  • the resilient wires or filaments 156 are woven at an angle to the longitudinal axis of the embolic filter assembly 152 , so that the embolic filter assembly 152 can expand and contract in diameter by changing the angle of the wires or filaments 156 .
  • the angle between the wires or filaments 156 and the longitudinal axis of the embolic filter assembly 152 increases and the embolic filter assembly 152 may also foreshorten.
  • the resilient wires or filaments 156 urge the embolic filter assembly 152 to expand to the deployed position.
  • the proximal end 158 of the filter screen 154 is sealingly attached to the catheter shaft 162 .
  • the perfusion filter catheter 150 is shown in FIG. 9 with the embolic filter assembly 152 compressed into the collapsed position.
  • the embolic filter assembly 152 compresses in diameter smoothly without folding as the resilient wires or filaments 156 and the fibers of the filter screen 154 decrease their angle with respect to the longitudinal axis of the embolic filter assembly 152 .
  • An outer tube 164 holds the embolic filter assembly 152 in the collapsed position. Once the perfusion filter catheter 150 is in position within the patient's aorta, the outer tube 164 is pulled back, which allows the embolic filter assembly 152 to expand, as shown in FIG. 10.
  • FIG. 11 shows the embolic filter assembly 152 fully expanded in the deployed position.
  • the resilient wires or filaments 156 are preformed so that, when deployed, the filter screen 154 has a roughly conical shape with an open distal end 160 .
  • the conical shape holds the filter screen 154 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 154 .
  • the distal end 160 of the embolic filter assembly 152 seals against the aortic wall.
  • the self-expanding aspect of the embolic filter assembly 152 naturally compensates for patient-to-patient variations in aortic luminal diameter.
  • the resilient wires or filaments 156 may be preformed to other geometries so that the filter screen 154 of the embolic filter assembly 152 assumes a different configuration when deployed, including each of the other configurations discussed within this patent specification.
  • FIGS. 12 - 14 show one method of actively deploying an embolic filter assembly 168 on a perfusion filter catheter 166 .
  • the filter support structure 170 includes a collapsible outer hoop 172 and a plurality of actuation wires 174 .
  • the distal end 176 of the filter screen 180 is attached to the outer hoop 172 and the proximal end 182 of the filter screen 180 is sealingly attached to the catheter shaft 184 .
  • the actuation wires 174 are slidably received within actuation wire lumens 186 located in the outer wall of the catheter shaft 184 .
  • the actuation wires 174 exit the actuation wire lumens 186 through side ports 188 located near the distal end of the catheter shaft 184 .
  • the actuation wires 174 and the outer hoop 172 are each made of a resilient polymer or a metal, such as stainless steel, nickel/titanium alloy or the like.
  • the perfusion filter catheter 166 is shown in FIG. 12 with the embolic filter assembly 168 compressed into the collapsed position.
  • the actuation wires 174 are withdrawn into the actuation wire lumens 186 through the side ports 188 and the outer hoop 172 is folded or collapsed against the catheter shaft 184 .
  • the material of the filter screen 180 is folded or collapsed around the catheter shaft 184 .
  • An outer tube 190 covers the embolic filter assembly 168 in the collapsed position to facilitate insertion of the catheter 166 .
  • FIG. 14 shows the embolic filter assembly 168 fully expanded in the deployed position.
  • the filter screen 180 is configured as a frustum of a cone with an open distal end 176 .
  • the outer hoop 172 at the distal end 176 of the filter screen 180 seals against the aortic wall.
  • FIGS. 15 - 17 show another method of actively deploying an embolic filter assembly 202 on a perfusion filter catheter 200 .
  • the filter support structure 204 includes an outer hoop 206 and a plurality of struts 208 , which are all interconnected hollow tubular members.
  • the outer hoop 206 and the struts 208 are made of a flexible polymeric material.
  • the filter support structure 204 is connected to an inflation lumen 210 , which parallels the perfusion lumen 218 within the catheter shaft 212 .
  • the inflation lumen 210 branches off from the catheter shaft 212 to a side arm 214 with a luer fitting 216 for connecting to a syringe or other inflation device.
  • this embodiment of the embolic filter assembly 202 is shown with a trumpet-shaped filter screen 220 .
  • the filter screen 220 includes a skirt portion 222 extending distally from a proximal, filter pocket 224 .
  • the skirt portion 222 is in the shape of a frustum of a cone with an open distal end, which is attached to the outer hoop 206 .
  • the filter pocket 224 is roughly cylindrical in shape with a closed proximal end, which is sealingly attached to the catheter shaft 212 .
  • the skirt 222 and the filter pocket 224 may be made of the same filter material or they may be made of different filter materials having different porosities.
  • the skirt 222 of the filter screen 220 may even be made of a nonporous material.
  • the perfusion filter catheter 200 is shown in FIG. 17 with the embolic filter assembly 202 folded into a collapsed position.
  • the outer hoop 206 and the struts 208 of the filter support structure 204 are deflated and the material of the filter screen 220 is folded or collapsed around the catheter shaft 212 .
  • An outer tube 226 covers the embolic filter assembly 202 in the collapsed position to facilitate insertion of the catheter 200 .
  • the outer tube 226 may have a slit or a weakened longitudinal tear line along its length to facilitate removal of the outer tube 226 over the side arm 214 at the proximal end of the catheter 200 .
  • the outer tube 226 is pulled back to expose the embolic filter assembly 202 .
  • the embolic filter assembly 202 is deployed by inflating the outer hoop 206 and the struts 208 with fluid injected through the inflation lumen 210 to actively expand the filter support structure 204 , as shown in FIG. 16.
  • the outer hoop 206 of the filter support structure 204 seals against the inner wall of the aorta, as shown in FIG. 15.
  • at least the outer wall of the outer hoop 206 is somewhat compliant when inflated in order to compensate for patient-to-patient variations in aortic luminal diameter.
  • FIGS. 18 - 20 show another method of actively deploying an embolic filter assembly 232 on a perfusion filter catheter 230 .
  • the filter support structure 234 includes an outer hoop 236 and a plurality of struts 238 , which are connected to an inner catheter shaft 240 .
  • the outer hoop 236 and the struts 238 may be made of a resilient polymer or metal, for example a superelastic nickel/titanium alloy.
  • the distal end 242 of the filter screen 244 is attached to the outer hoop 236 .
  • the proximal end 246 of the filter screen 244 is sealingly attached to an outer catheter shaft 250 .
  • the inner catheter shaft 240 is slidably and rotatably received within the outer catheter shaft 250 .
  • the filter screen 244 has one or more spiral grooves or flutes 248 that wind helically around the filter screen 244 .
  • the embolic filter assembly 232 is folded into the collapsed position shown in FIG. 20 by extending and rotating the inner catheter shaft 240 in a first direction with respect to the outer catheter shaft 250 . This collapses the filter support structure 234 back against the inner catheter shaft 240 and furls the filter screen 244 around the inner catheter shaft 240 . The spiral flutes 248 in the filter screen 244 help it to collapse smoothly around the inner catheter shaft 240 .
  • An outer tube 252 covers the embolic filter assembly 232 in the collapsed position to facilitate insertion of the catheter 230 . Once the perfusion filter catheter 230 is in position within the patient's aorta, the outer tube 252 is pulled back to expose the embolic filter assembly 232 .
  • the embolic filter assembly 232 is deployed by rotating the inner catheter shaft 240 in the opposite direction with respect to the outer catheter shaft 250 and allowing it to retract slightly, as shown in FIG. 19.
  • the filter support structure 234 and the filter screen 244 will expand within the aorta and the distal end 242 of the filter screen 244 will seal against the aortic wall, as shown in FIG. 18.
  • the spiral flutes 248 of the embolic filter assembly 232 hold most of the filter screen 244 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 244 .
  • the embolic filter assembly 232 is returned to the collapsed position as described above and the catheter 230 is withdrawn from the patient.
  • the coaxial arrangement of the inner catheter shaft 240 and the outer catheter shaft 250 in this embodiment of the perfusion filter catheter 230 creates an annular space that can optionally be used as a lumen 258 to aspirate potential emboli that are captured by the filter screen 244 .
  • a side arm 254 with a luer fitting and a sliding hemostasis valve 256 may be added to the proximal end of the outer catheter shaft 250 , as shown in FIG. 18.
  • FIGS. 21 - 23 show another method of actively deploying an embolic filter assembly 262 on a perfusion filter catheter 260 .
  • the filter support structure 234 includes an outer hoop 266 and a plurality of struts 268 , which are connected to an inner catheter shaft 270 .
  • the outer hoop 266 and the struts 268 may be made of a resilient polymer or metal, for example a superelastic nickel/titanium alloy.
  • the distal end 272 of the filter screen 274 is attached to the outer hoop 266 .
  • the proximal end 276 of the filter screen 274 is sealingly attached to an outer catheter shaft 280 .
  • the inner catheter shaft 270 is slidably received within the outer catheter shaft 280 .
  • the filter screen 274 has a series of circumferential pleats 278 that give the filter screen 274 an accordion appearance.
  • the embolic filter assembly 262 is folded into the collapsed position shown in FIG. 23 by extending the inner catheter shaft 270 distally with respect to the outer catheter shaft 280 . This collapses the filter support structure 264 back against the inner catheter shaft 270 and collapses the circumferential pleats 248 of the filter screen 274 against the inner catheter shaft 270 .
  • An outer tube 282 covers the embolic filter assembly 262 in the collapsed position to facilitate insertion of the catheter 260 . Once the perfusion filter catheter 260 is in position within the patient's aorta, the outer tube 282 is pulled back to expose the embolic filter assembly 262 .
  • the embolic filter assembly 262 is deployed by retracting the inner catheter shaft 270 proximally with respect to the outer catheter shaft 280 , as shown in FIG. 22.
  • the filter support structure 264 and the filter screen 274 will expand within the aorta and the distal end 272 of the filter screen 274 will seal against the aortic wall, as shown in FIG. 21.
  • the circumferential pleats 278 of the embolic filter assembly 262 hold the majority of the filter screen 274 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 274 .
  • the embolic filter assembly 262 is returned to the collapsed position as described above and the catheter 260 is withdrawn from the patient.
  • the coaxial arrangement of the inner catheter shaft 270 and the outer catheter shaft 280 in this embodiment of the perfusion filter catheter 260 creates an annular space that can optionally be used as a lumen 288 to aspirate potential emboli that are captured by the filter screen 274 .
  • a side arm 284 with a luer fitting and a sliding hemostasis valve 286 may be added to the proximal end of the outer catheter shaft 280 , as shown in FIG. 21.
  • Active deployment of the embolic filter assembly can also be accomplished with any of the preceding embodiments by using shape memory materials, such as a nickel/titanium alloy, to construct the filter support structure and/or the actuation members.
  • shape memory materials such as a nickel/titanium alloy
  • the transition temperature of the shape memory material should be chosen to be close to normal body temperature so that extreme temperature variations will not be necessary for deployment.
  • the shape memory material of the filter support structure should be annealed in the deployed position to confer a shape memory in this configuration. Then, the embolic filter assembly should be cooled below the transition temperature of the shape memory material, so that the filter support structure is malleable and can be shaped into a collapsed position. Depending on the transition temperature, this can be done at room temperature or in iced saline solution.
  • an outer tube can be placed over the embolic filter assembly to facilitate catheter insertion and to avoid premature deployment.
  • the outer tube is pulled back to expose the embolic filter assembly and the filter support structure is heated above the transition temperature to deploy the embolic filter assembly.
  • the filter support structure can be passively heated by body heat (accounting, of course, for decreased body temperature during hypothermic cardiopulmonary support methods) or it can be self-heated by applying an electrical current through the filter support structure. When heated, the filter support structure expands to its annealed configuration within the aorta.
  • the embolic filter assembly is returned to the collapsed position by advancing the outer tube distally over the filter screen and the filter support structure, then the catheter is withdrawn from the patient.
  • perfusion filter catheter of the present invention showed retrograde deployment of the device within the aorta via femoral artery access.
  • Each of the described embodiments of the perfusion filter catheter can also be adapted for retrograde deployment via subclavian artery access or for antegrade or retrograde deployment via direct aortic puncture.
  • FIG. 24 shows a perfusion filter catheter 290 which is adapted for retrograde deployment via subclavian artery access.
  • the perfusion filter catheter 290 is depicted with a trumpet-style, passively-deployed embolic filter assembly 292 .
  • the perfusion filter catheter 290 has a tubular catheter shaft 294 with a length of approximately 60-90 cm. Because of the shorter length, as compared to the femoral version of the catheter, the outside diameter of the catheter shaft 294 can be reduced to 12-18 French size (4-6 mm outside diameter) for delivering the 3-4 liters of oxygenated blood needed to preserve organ function.
  • the reduced diameter of the catheter shaft 294 is especially advantageous for subclavian artery delivery of the catheter 290 .
  • the outer tube 296 may be adapted for use as an introducer sheath by the addition of an optional hemostasis valve 298 at the proximal end of the outer tube 296 . This eliminates the need for a separate introducer sheath for introducing the catheter 290 into the circulatory system.
  • the perfusion filter catheter 290 is introduced into the subclavian artery with the embolic filter assembly 292 in a collapsed state within the outer tube 296 , using the Seldinger technique or an arterial cutdown.
  • the embolic filter assembly 292 is advanced across the aortic arch while in the collapsed state.
  • the position of the catheter 292 may be monitored using fluoroscopy or ultrasound, such as transesophageal echography (TEE).
  • Radiopaque markers and/or sonoreflective markers may be located on the catheter 290 and/or the embolic filter assembly 292 to enhance imaging and to show the position of the catheter 290 and the deployment state of the embolic filter assembly 292 .
  • the outer tube 296 is withdrawn and the embolic filter assembly 292 is either actively or passively deployed, as shown in FIG. 24.
  • oxygenated blood may be infused into the aorta through the tubular catheter shaft 294 .
  • Any potential emboli are captured by the embolic filter assembly 292 and prevented from entering the neurovasculature or other branches downstream.
  • the embolic filter assembly 292 is returned to the collapsed position and the catheter 290 is withdrawn from the patient.
  • Retrograde deployment of the perfusion filter catheter 290 via direct aortic puncture is quite similar to introduction via subclavian artery access, except that the catheter 290 is introduced directly into the descending aorta after it has been surgically exposed, for example during open-chest or minimally invasive cardiac surgery. Because of the direct aortic insertion, the length and the diameter of the catheter shaft 294 may be further reduced.
  • FIGS. 25 - 27 show a perfusion filter catheter 300 which is adapted for antegrade deployment via direct aortic puncture.
  • the perfusion filter catheter 300 is depicted with a hybrid-style embolic filter assembly 302 , which is a compromise between the conical filter screen and the trumpet-style filter screen previously described.
  • the catheter shaft 304 can be reduced to a length of approximately 20-60 cm and an outside diameter of approximately 12-18 French size (4-6 mm outside diameter) for delivering the 3-4 liters of oxygenated blood needed to preserve organ function during cardiopulmonary bypass.
  • the catheter shaft 304 need not extend all the way to the distal end of the filter screen 310 .
  • the filter screen 310 may be entirely supported by the filter support structure 312 , particularly if the embolic filter assembly 302 is to be passively deployed.
  • a small diameter filter support member 314 may extend from the catheter shaft 304 to the distal end of the filter screen 310 .
  • the filter support member 314 may be slidably and/or rotatably received within the catheter shaft 304 . Either of these configurations allows the embolic filter assembly 302 to be folded or compressed to a size as small as the diameter of the catheter shaft 304 to facilitate insertion of the catheter 300 .
  • an outer tube 316 may be placed over the folded embolic filter assembly 302 to hold it in the collapsed position.
  • the ascending aorta of the patient is surgically exposed, using open-chest or minimally invasive surgical techniques.
  • a purse string suture 318 is placed in the ascending aorta and an aortotomy incision is made through the aortic wall.
  • the catheter 300 with the embolic filter assembly 302 in the collapsed position within the outer tube 316 , is inserted through the aortotomy and advanced antegrade into the aortic arch.
  • the outer tube 316 is withdrawn and the embolic filter assembly 302 is either actively or passively deployed, as shown in FIG. 25.
  • oxygenated blood may be infused into the aorta through the tubular catheter shaft 304 .
  • Any potential emboli are captured by the embolic filter assembly 302 and prevented from entering the neurovasculature or other branches downstream.
  • the embolic filter assembly 302 is returned to the collapsed position, the catheter 300 is withdrawn from the patient, and the purse string suture 318 is tightened to close the aortotomy.
  • each of the passive and active deployment methods described above may be used interchangeably or together in combinations with each of the embodiments of the perfusion filter catheter and each of catheter insertion methods which are described above and below.
  • many of the features of the embodiments described may be used in various combinations with one another to create new embodiments, which are considered to be a part of this disclosure, as it would be too cumbersome to describe all of the numerous possible combinations and subcombinations of the disclosed features.
  • each of the described embodiments may be passively or actively deployed by the methods described above.
  • Each embodiment of the perfusion filter catheter described can also be adapted for retrograde deployment via peripheral arterial access, such as femoral or subclavian artery access, or for antegrade or retrograde deployment via direct aortic puncture.
  • FIGS. 28 and 29 show a perfusion filter catheter 320 having an embolic filter assembly 322 with a graded porosity filter screen 324 .
  • the filter screen 324 is attached to a filter support structure 326 mounted on a catheter shaft 328 for antegrade or retrograde deployment.
  • the filter screen 324 may be made in each of the configurations disclosed herein or any other convenient shape.
  • the filter screen 324 in this embodiment is depicted as being in the shape of a frustum of a cone.
  • the filter screen 324 has an upstream end 330 and a downstream end 332 .
  • the upstream end 330 of the filter screen 324 has a finer filter mesh than the downstream end 332 .
  • the pore size of the filter screen 324 may make a gradual transition from the upstream end 330 to the downstream end 332 or there may be two or more discrete zones of varying pore size.
  • the filter mesh on the upstream end 330 has a pore size of approximately 5-50 micrometers for capturing microemboli and macroemboli and the filter mesh on the downstream end 332 has a pore size of approximately 50-100 micrometers for capturing macroemboli only.
  • the pore size of the filter screen 324 has been greatly exaggerated in FIG. 28 for clarity of illustration.
  • the perfuision filter catheter 320 is introduced into the aorta with the embolic filter assembly 322 in a collapsed state within an outer tube 334 , using one of the methods described above.
  • the embolic filter assembly 322 is advanced across the aortic arch while in the collapsed state.
  • the outer tube 334 is withdrawn and the embolic filter assembly 322 is either actively or passively deployed, as shown in FIG. 29.
  • the embolic filter assembly 292 is dimensioned so that when it is deployed, the upstream end 330 of the filter screen 324 is positioned in the vicinity of the ostia for the brachiocephalic artery and the left common carotid artery and the downstream end 332 of the filter screen 324 is positioned downstream of this position, preferably in the descending aorta.
  • This configuration assures that all of the perfusate which is destined for the neurovasculature must pass through the finer, upstream end 330 of the filter screen 324 to remove all microemboli and macroemboli.
  • the perfusate which is destined for the viscera and the lower limbs, which are more tolerant of small emboli, need only pass through the downstream end 332 of the filter screen 324 , so as to remove at least the macroemboli.
  • FIG. 30 shows a perfusion filter catheter 340 having a longitudinally fluted embolic filter assembly 342 .
  • the embolic filter assembly 342 has a filter screen 344 that is attached at its open distal end 352 to a filter support structure 346 mounted on a catheter shaft 348 for antegrade or retrograde deployment.
  • the filter screen 344 has a plurality of longitudinally oriented folds or flutes 350 .
  • FIG. 30A is a cutaway section of the embolic filter assembly 342 cut along line 30 A in FIG. 30 in order to better show the longitudinal flutes 350 .
  • the longitudinal flutes 350 provide additional surface area to the filter screen 344 to reduce pressure drop from blood flow across the embolic filter assembly 342 .
  • the longitudinal flutes 350 also serve to hold a majority of the filter screen 344 away from the aortic wall and away from the ostia of the arch vessels.
  • the longitudinally fluted embolic filter assembly 342 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 31 shows a perfusion filter catheter 360 having a longitudinally ribbed embolic filter assembly 362 .
  • the embolic filter assembly 362 has a filter screen 364 that is attached at its open distal end 372 to a filter support structure 366 mounted on a catheter shaft 368 for antegrade or retrograde deployment.
  • the filter screen 364 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen.
  • the embolic filter assembly 362 has a plurality of longitudinally oriented ribs 370 positioned around the exterior of the filter screen 364 .
  • FIG. 31A is a cutaway section of the embolic filter assembly 362 cut along line 31 A in FIG. 31 in order to better show the longitudinally oriented ribs 370 .
  • the longitudinal ribs 370 serve as standoff members to center the filter screen 364 within the aorta so as hold a majority of the filter screen 364 away from the aortic wall and away from the ostia of the arch vessels.
  • the longitudinally ribbed embolic filter assembly 362 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 32 shows a perfusion filter catheter 380 having an embolic filter assembly 382 that is surrounded by a cage 394 of standoff members 396 .
  • the embolic filter assembly 382 has a filter screen 384 that is attached at its open distal end 392 to a filter support structure 386 mounted on a catheter shaft 388 for antegrade or retrograde deployment.
  • the filter screen 384 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen.
  • the embolic filter assembly 382 further includes a plurality of standoff members 396 that form a cage 394 surrounding the filter screen 384 .
  • the standoff members 396 may be made of a resilient polymer or metal, such as an elastic or superelastic alloy, or a shape-memory material.
  • the geometry of the standoff members 396 is quite variable.
  • FIG. 32 depicts the standoff members 396 as a plurality of longitudinally oriented wires which, together, form a roughly cylindrical cage 394 .
  • Other possible configurations include circumferential members, diagonal members, and combinations thereof.
  • the standoff members 396 of the cage 394 serve to center the filter screen 384 within the aorta so as hold a majority of the filter screen 384 away from the aortic wall and away from the ostia of the arch vessels.
  • the embolic filter assembly 382 and the standoff members 396 of the cage 394 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 33 shows a perfusion filter catheter 400 having an embolic filter assembly 402 that is 10 surrounded by a cage 414 of coiled wire standoff members 416 .
  • the embolic filter assembly 402 has a filter screen 404 that is attached at its open distal end 412 to a filter support structure 406 mounted on a catheter shaft 408 for antegrade or retrograde deployment.
  • the filter screen 404 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen.
  • the embolic filter assembly 402 further includes a plurality of loosely coiled wire standoff members 416 which form a cage 414 surrounding the filter screen 404 .
  • the coiled standoff members 416 may be made of a resilient polymer or metal, such as an elastic or superelastic alloy, or a shape-memory material.
  • the coiled standoff members 416 of the cage 414 serve to center the filter screen 404 within the aorta so as hold a majority of the filter screen 404 away from the aortic wall and away from the ostia of the arch vessels.
  • the embolic filter assembly 402 and the standoff members 416 of the cage 414 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 34 shows a perfusion filter catheter 420 having an embolic filter assembly 422 that is surrounded by a cage 434 of coarse netting 436 .
  • the embolic filter assembly 422 has a filter screen 424 that is attached at its open distal end 432 to a filter support structure 426 mounted on a catheter shaft 428 for antegrade or retrograde deployment.
  • the filter screen 424 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen.
  • the embolic filter assembly 422 further includes a coarse netting 436 , which forms a roughly cylindrical cage 434 surrounding the filter screen 424 .
  • the netting 436 may be made of a resilient polymer or metal, such as an elastic or superelastic alloy, or a shape-memory material.
  • the netting 436 of the cage 434 serves to center the filter screen 424 within the aorta so as hold a majority of the filter screen 424 away from the aortic wall and away from the ostia of the arch vessels.
  • the embolic filter assembly 422 and the coarse netting 436 of the cage 434 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 35 shows a cutaway view of a perfusion filter catheter 440 having an embolic filter assembly 442 that is surrounded by a fender 454 made from a porous foam or a fibrous network 456 .
  • the embolic filter assembly 442 has a filter screen 444 that is attached at its open distal end 452 to a filter support structure 446 mounted on a catheter shaft 448 for antegrade or retrograde deployment.
  • the filter screen 444 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen.
  • the embolic filter assembly 442 further includes a roughly cylindrical fender 454 made from a highly porous foam or a fibrous network 456 , which surrounds the filter screen 444 .
  • the fender 454 may be made of a highly porous open cell polymer foam or a network of polymeric fibers.
  • the fender 454 serves to center the filter screen 444 within the aorta so as hold a majority of the filter screen 444 away from the aortic wall and away from the ostia of the arch vessels.
  • the embolic filter assembly 442 and the fender 454 can be adapted for passive or active deployment or a combination thereof.
  • FIGS. 36 and 37 show an alternate embodiment of a perfusion filter catheter 460 with a passively deployed embolic filter assembly 462 .
  • the embolic filter assembly 462 has a filter screen 464 that is attached at its open distal end 474 to a filter support structure 466 mounted on a catheter shaft 468 for antegrade or retrograde deployment.
  • the proximal end 476 of the filter screen 464 is sealingly attached to the catheter shaft 468 .
  • the filter screen 464 may be configured as a conical, trumpet or other style of filter screen.
  • the filter support structure 466 has an outer hoop 470 which is attached by a perpendicular leg 472 to the catheter shaft 468 .
  • the outer hoop 470 is made of a resilient polymer or metal, such as an elastic or superelastic alloy, or possibly a shape-memory material.
  • the filter support structure 466 in this embodiment, has no struts.
  • the distal end 478 of the catheter shaft 468 may be curved toward the center of the outer hoop 470 to help center the perfusion port 480 located at the distal end of the catheter shaft 468 within the aorta when the catheter 460 is deployed.
  • the perfusion port 480 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 482 .
  • the perfusion filter catheter 460 is prepared for use by bending the outer hoop 470 in the proximal direction or wrapping it around the catheter shaft 468 , then folding or wrapping the material of the filter screen 464 around the catheter shaft 468 .
  • An outer tube 484 is placed over the embolic filter assembly 462 to hold it in the collapsed position, as shown in FIG. 37.
  • the catheter 460 is introduced and the embolic filter assembly 462 is advanced across the aortic arch while in the collapsed state.
  • the outer tube 484 When the distal end 474 of the embolic filter assembly 462 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 484 is withdrawn and the resilient outer hoop 470 expands to deploy the embolic filter assembly 462 , as shown in FIG. 36. The outer hoop 470 and the distal end 474 of the filter screen 464 will seal against the aortic wall.
  • the embolic filter assembly 462 is returned to the collapsed position by advancing the outer tube 484 distally over the filter screen 464 and the filter support structure 466 , then the catheter 460 is withdrawn from the patient.
  • FIGS. 38 - 41 show an alternate embodiment of a perfusion filter catheter 490 with an actively deployed embolic filter assembly 492 .
  • the embolic filter assembly 492 has a filter screen 494 with a sewn tubular channel 496 which extends circumferentially around the open distal end 498 of the filter screen 494 .
  • the distal end 498 of the filter screen 494 is attached on one side to the catheter shaft 504 , and the proximal end 506 of the filter screen 494 is sealingly attached to the catheter shaft 504 .
  • the filter screen 494 may be configured as a conical, trumpet or other style of filter screen.
  • the filter support structure in this embodiment consists of a preshaped, superelastic actuation wire 500 , which, when the embolic filter assembly 492 is in the collapsed state, resides in a second lumen 502 within the catheter shaft 504 .
  • the actuation wire 500 has a bead or small loop 508 at its distal end to create a blunt, non-piercing tip.
  • the second lumen 502 of the catheter shaft 504 communicates with the tubular channel 496 at the distal end 498 of the filter screen 494 .
  • the actuation wire 500 When the actuation wire 500 is extended, it forms a hoop as it passes through the tubular channel 496 of the filter screen 494 .
  • the distal end 510 of the catheter shaft 504 may be curved toward the center of the embolic filter assembly 492 to help center the perfusion port 510 located at the distal end of the catheter shaft 504 within the aorta when the catheter 490 is deployed.
  • the perfusion port 510 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 512 during cardiopulmonary bypass.
  • the perfusion filter catheter 490 is prepared for use by withdrawing the actuation wire 500 into the second lumen 502 , then folding or wrapping the flexible material of the filter screen 494 around the catheter shaft 504 .
  • an outer tube 514 may be placed over the embolic filter assembly 492 to hold it in the collapsed position, as shown in FIG. 38.
  • the catheter 490 is introduced and the embolic filter assembly 492 is advanced across the aortic arch while in the collapsed state.
  • the outer tube 514 is withdrawn, which allows the filter screen 494 to unwrap from the catheter shaft 504 , as shown in FIG. 39.
  • the preshaped, superelastic actuation wire 500 is advanced distally so that it begins to form a hoop as it passes through the tubular channel 496 at the distal end 498 of the filter screen 494 , as shown in FIG. 40.
  • the actuation wire 500 is further advanced until it forms a complete hoop, as shown in FIG. 41, thereby sealing the distal end 498 of the filter screen 494 against the aortic wall.
  • the embolic filter assembly 492 is returned to the collapsed position as described above, then the catheter 490 is withdrawn from the patient.
  • FIGS. 42 and 43 show another alternate embodiment of a perfusion filter catheter 520 with an actively deployed embolic filter assembly 522 .
  • the embolic filter assembly 522 has a filter screen 524 with a sewn tubular channel 526 which extends circumferentially around the open distal end 528 of the filter screen 524 .
  • the distal end 528 of the filter screen 524 is attached on one side to the catheter shaft 534 , and the proximal end 536 of the filter screen 524 is sealingly attached to the catheter shaft 534 .
  • the filter screen 524 may be configured as a conical, trumpet or other style of filter screen.
  • the filter support structure in this embodiment consists of a preshaped, elastic or superelastic wire loop 530 .
  • the wire loop 530 passes through the tubular channel 526 at the distal end 528 of the filter screen 524 .
  • the wire loop 530 is withdrawn into a second lumen 532 within the catheter shaft 534 , as shown in FIG. 42.
  • the wire loop 530 acts as a purse string to close the filter screen 524 tightly around the catheter shaft 534 .
  • the wire loop 530 is advanced distally, it forms a hoop that holds the distal end 528 of the filter screen 524 open, as shown in FIG. 43.
  • the distal end 540 of the catheter shaft 534 may be curved toward the center of the embolic filter assembly 522 to help center the perfusion port 542 located at the distal end of the catheter shaft 534 within the aorta when the catheter 520 is deployed.
  • the perfusion port 540 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 544 during cardiopulmonary bypass.
  • the perfusion filter catheter 520 is prepared for use by withdrawing the wire loop 530 into the second lumen 532 , then folding or wrapping the flexible material of the filter screen 524 around the catheter shaft 534 .
  • an outer tube 538 may be placed over the embolic filter assembly 522 to hold it in the collapsed position. The catheter 520 is introduced and the embolic filter assembly 522 is advanced across the aortic arch while in the collapsed state.
  • the outer tube 538 is withdrawn, and the preshaped, superelastic wire loop 530 is advanced distally so that it forms a hoop that holds the distal end 528 of the filter screen 524 open and seals against the aortic wall.
  • the inherent adjustability of the wire loop 530 used to deploy the embolic filter assembly 522 naturally compensates for patient-to-patient variations in aortic luminal diameter.
  • the embolic filter assembly 522 is returned to the collapsed position by withdrawing the wire loop 530 into the second lumen 532 . This closes the filter screen 524 like a purse string to capture any potential emboli that are in the embolic filter assembly 522 . Then, the catheter 520 is withdrawn from the patient.
  • FIGS. 44 and 45 show another alternate embodiment of a perfusion filter catheter 550 with an actively deployed embolic filter assembly 552 .
  • the embolic filter assembly 552 has a filter screen 554 with an open distal end 558 that is attached to a toroidal balloon 560 .
  • the toroidal balloon 560 is attached on one side to the catheter shaft 564 and it is fluidly connected to an inflation lumen 562 within the catheter shaft 564 .
  • the proximal end 566 of the filter screen 554 is sealingly attached to the catheter shaft 564 .
  • the filter screen 554 may be configured as a conical, trumpet or other style of filter screen.
  • the distal end 570 of the catheter shaft 564 may be curved toward the center of the embolic filter assembly 552 to help center the perfusion port 572 located at the distal end of the catheter shaft 564 within the aorta when the catheter 550 is deployed.
  • the perfusion port 570 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 574 during cardiopulmonary bypass.
  • the perfusion filter catheter 550 is prepared for use by deflating the toroidal balloon 560 , then folding or wrapping the deflated toroidal balloon 560 and the filter screen 554 around the catheter shaft 564 .
  • an outer tube 564 may be placed over the embolic filter assembly 552 to hold it in the collapsed position, as shown in FIG. 44.
  • the catheter 550 is introduced and the embolic filter assembly 552 is advanced across the aortic arch while in the collapsed state.
  • the outer tube 564 is pulled back to expose the embolic filter assembly 552 .
  • the embolic filter assembly 202 is deployed by inflating the toroidal balloon 560 with fluid injected through the inflation lumen 562 , as shown in FIG. 45.
  • the toroidal balloon 560 seals against the inner wall of the aorta.
  • at least the outer wall of the toroidal balloon 560 is somewhat compliant when inflated in order to compensate for patient-to-patient variations in aortic luminal diameter.
  • the toroidal balloon 560 is deflated and the catheter 550 is withdrawn from the patient.
  • the embolic filter assembly of the perfusion filter catheter be deployed continuously throughout the entire period of cardiopulmonary bypass or extracorporeal perfusion. It is most critical, however, that the embolic filter assembly be deployed during periods when the potential for embolization is the highest, such as during manipulations of the heart and the aorta, during clamping and unclamping of the aorta and during the initial period after the heart is restarted following cardioplegic arrest. It has been previously stated that, for continuous deployment of a filter device in the aortic lumen, it is desirable for the filter mesh to have a surface area of 3-10 in 2 .
  • the shallow, cone-shaped aortic filter devices illustrated in the known prior art only manage to provide surface areas at the lower end of this desired range in the largest of human aortas (approximately 3.0-3.9 in 2 in aortas of 3.5-4.0 cm diameter estimated based on the drawings and descriptions in the prior art disclosures) and in no cases are there embodiments disclosed which could provide surface areas in the middle and upper end of this range or that could even meet the minimum limit of this desired range in more typically sized aortas in the range of 2.5-3.5 cm diameter. Consequently, it is the opinion of the present inventors that the prior art does not provide an adequate solution to the technical problem that it illuminates.
  • the solution to this dilemma is to provide a filter assembly that has a greater ratio of filter surface area to the cross-sectional area of the aortic lumen.
  • the cross-sectional area of the aortic lumen being approximately equal to the area of the open upstream end of the embolic filter assembly at its deployed diameter within the aorta.
  • the embolic filter assembly should provide a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 2, more preferably greater than 3, more preferably greater than 4, more preferably greater than 5 and most preferably greater than 6.
  • ratios of the filter surface area to the cross-sectional area of the aortic lumen it is possible to achieve a filter mesh surface area of 3-10 in 2 or greater in all typical adult human aortas ranging from 2.0 to 4.0 cm in diameter.
  • ratios of the filter surface area to the cross-sectional area of the aortic lumen of 8, 10, 12 and even greater are readily achievable. Higher ratios such as these are desirable as they allow a very fine filter mesh to be utilized to effectively capture both macroemboli and microemboli without compromising the aortic blood flow.
  • an embolic filter assembly structure or other means that maximizes the effective surface area of the filter mesh by holding at least a majority of the filter mesh away from the aortic wall or any other structures that might potentially obstruct flow through the filter mesh.
  • FIGS. 1 - 3 there is illustrated an embolic filter assembly that is approximately conical in shape.
  • a conical filter assembly In order to achieve a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 2, a conical filter assembly must have a filter length L of greater than the aortic diameter D.
  • a conical filter assembly To achieve a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 4, a conical filter assembly must have a filter length L of greater than twice the aortic diameter D. To achieve a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 6, a conical filter assembly must have a filter length L of greater than three times the aortic diameter D. With these ratios of the filter surface area to the cross-sectional area of the aortic lumen, it is possible to achieve a filter mesh surface area of 3-10 in 2 or greater in all typical adult human aortas ranging from 2.0 to 4.0 cm in diameter. Greater length to diameter ratios will provide more improved ratios of the filter surface area to the cross-sectional area of the aortic lumen.
  • FIGS. 7 - 8 , 15 - 17 and 25 - 27 there are illustrated embolic filter assemblies having an approximately trumpet-shaped geometry that includes an approximately conical upstream section connected to an approximately cylindrical extension with a closed downstream end.
  • This geometry provides an improvement in the ratio of the filter surface area to the cross-sectional area of the aortic lumen of approximately 15 to 50 percent compared with the simple conical geometry.
  • Further improvements of the ratio of the filter surface area to the cross-sectional area of the aortic lumen can be realized with the convoluted embolic filter assemblies illustrated in FIGS. 18 - 20 , 20 - 23 and 30 . With these convoluted geometries, ratios of the filter surface area to the cross-sectional area of the aortic lumen of 2-12 or even greater can be achieved.
  • Each of the embodiments of the invention described herein may be used for administration of standard cardiopulmonary bypass and cardioplegic arrest by combining the aortic filter catheter with a standard aortic crossclamp and a standard arterial perfusion cannula inserted into the ascending aorta between the crossclamp and the embolic filter assembly.
  • the aortic filter catheter includes an integral perfusion lumen
  • the CPB system can be simplified by the eliminating the separate arterial perfusion cannula.
  • the CPB system can be further simplified by incorporating an aortic occlusion device into the aortic filter catheter and eliminating the aortic crossclamp.
  • Such a system would allow percutaneous transluminal administration of cardiopulmonary bypass and cardioplegic arrest with protection from undesirable embolic events.
  • FIGS. 46 - 50 show the operation of an embodiment of a perfusion filter catheter 600 that combines an embolic filter assembly 602 with a toroidal balloon aortic occlusion device 604 .
  • the embolic filter assembly 602 and the toroidal balloon aortic occlusion device 604 are mounted on an elongated catheter shaft 606 that may be adapted for peripheral introduction via the femoral artery or subclavian artery or for central insertion directly into the ascending aorta.
  • the toroidal balloon aortic occlusion device 604 is connected to an inflation lumen within the elongated catheter shaft 606 .
  • a cardioplegia lumen which may also serve as a guidewire lumen, connects to a cardioplegia port 608 at the distal end of the catheter shaft 606 .
  • a perfusion lumen connects to one or more perfusion ports 610 located on the catheter shaft 606 downstream from the toroidal balloon aortic occlusion device 604 , but upstream of the embolic filter assembly 602 .
  • FIG. 46 shows the perfusion filter catheter 600 in the collapsed or undeployed state with the embolic filter assembly 602 and the toroidal balloon aortic occlusion device 604 collapsed or folded about the elongated catheter shaft 606 .
  • the perfuision filter catheter 600 is inserted in the collapsed state and advanced into the patient's ascending aorta until the embolic filter assembly 602 is positioned between the coronary ostia and the brachiocephalic artery.
  • the toroidal balloon aortic occlusion device 604 is then inflated to expand and deploy the embolic filter assembly 602 , as shown in FIG. 47.
  • the embolic filter assembly 602 may assume a simple conical shape or, more preferably, one of the surface area increasing geometries described above.
  • the embolic filter assembly 602 may include a structure or other means to hold the filter material apart from the aortic wall to maximize the effective filter area.
  • the toroidal balloon aortic occlusion device 604 When it is desired to initiate cardioplegic arrest, the toroidal balloon aortic occlusion device 604 is further inflated until it expands inward to occlude the aortic lumen, as shown in FIG. 48. A cardioplegic agent is infused through the cardioplegia port 608 and into the coronary arteries to arrest the heart. Oxygenated blood continues to be infused through the perfusion ports 610 . After completion of the surgical procedure, the toroidal balloon aortic occlusion device 604 is partially deflated, leaving the embolic filter assembly 602 deployed, as shown in FIG. 49. Oxygenated blood enters the coronary arteries to restart the heart beating.
  • embolic filter assembly 602 If any embolic materials 612 are dislodged during manipulation of the heart or when the heart resumes beating, they will be captured by the embolic filter assembly 602 .
  • the toroidal balloon aortic occlusion device 604 is deflated to collapse the embolic filter assembly 602 , as shown in FIG. 50. Any potential emboli are trapped within the embolic filter assembly 602 and can be removed along with the catheter 600 .
  • FIG. 51 shows an embodiment of a perfusion filter catheter 620 that combines an embolic filter assembly 622 with an inflatable balloon aortic occlusion device 624 .
  • the embolic filter assembly 622 may be any one of the actively or passively deployed embolic filter assemblies described herein.
  • the inflatable balloon aortic occlusion device 624 is an 5 elastomeric balloon of sufficient inflated diameter to occlude the ascending aorta and is mounted on the elongated catheter shaft 626 upstream of the embolic filter assembly 622 .
  • the inflatable balloon aortic occlusion device 624 may be positioned to occlude the inlet end of the embolic filter assembly 622 to minimize the area of contact between the perfusion filter catheter 620 and the aortic wall.
  • the inflatable balloon aortic occlusion device 624 is connected to an inflation lumen within the elongated catheter shaft 626 .
  • a cardioplegia lumen which may also serve as a guidewire lumen, connects to a cardioplegia port 628 at the distal end of the catheter shaft 626 .
  • a perfusion lumen connects to one or more perfusion ports 630 located on the catheter shaft 626 downstream from the inflatable balloon aortic occlusion device 624 , but upstream of the embolic filter assembly 622 .
  • the operation of the perfusion filter catheter 620 of FIG. 51 is quite similar to that described for the embodiment of FIGS. 46 - 50 .
  • FIG. 52 shows an embodiment of a perfusion filter catheter 640 that combines an embolic filter assembly 642 with a selectively deployable external catheter flow control valve 644 .
  • the embolic filter assembly 642 may be any one of the actively or passively deployed embolic filter assemblies described herein.
  • the selectively deployable external catheter flow control valve 644 is mounted on the elongated catheter shaft 646 upstream of the embolic filter assembly 642 .
  • the selectively deployable external catheter flow control valve 644 may be positioned to occlude the inlet end of the embolic filter assembly 642 to minimize the area of contact between the perfusion filter catheter 640 and the aortic wall.
  • the elongated catheter shaft 646 may include one or more deployment lumens as needed for actuating the external catheter flow control valve 644 .
  • a cardioplegia lumen which may also serve as a guidewire lumen, connects to a cardioplegia port 648 at the distal end of the catheter shaft 646 .
  • a perfusion lumen connects to one or more perfusion ports 650 located on the catheter shaft 646 downstream from the external catheter flow control valve 644 , but upstream of the embolic filter assembly 622 .
  • the operation of the perfusion filter catheter 640 of FIG. 52 is quite similar to that described for the embodiment of FIGS. 46 - 50 .
  • FIG. 53 shows an additional feature of the present invention that may be used in combination with many of the features and embodiments previously described.
  • FIG. 53 shows an embodiment of a perfusion filter catheter 660 with an embolic filter assembly 662 having areas of different filter porosity.
  • the embolic filter assembly 662 is mounted on an elongated catheter shaft 666 that may be adapted for peripheral introduction via the femoral artery or subclavian artery or for central insertion directly into the ascending aorta.
  • the embolic filter assembly 662 may resemble any one of the actively or passively deployed embolic filter assemblies described herein.
  • the embolic filter assembly 662 assumes one of the surface area increasing geometries described above, such as a trumpet-style embolic filter assembly 662 as shown.
  • the embolic filter assembly 662 is divided along a longitudinal dividing line into areas of different filter porosity.
  • the embolic filter assembly 662 has an upper portion 664 of finer porosity facing toward the aortic arch vessels and a lower portion 668 of courser porosity facing away from the aortic arch vessels.
  • the elongated catheter shaft 666 will have a preformed curve to help orient the upper portion 664 and the lower portion 668 of the embolic filter assembly 662 in the proper position once deployed.
  • the filter mesh of the upper portion 664 may be selected to exclude both macroemboli and microemboli, and the filter mesh of the lower portion 668 may be selected to exclude macroemboli only.
  • the upper portion 664 may be impermeable so as to act like a shunt to direct potential emboli downstream away from the aortic arch vessels.
  • FIG. 54 shows an embodiment of a perfusion filter catheter 670 with a fiberoptic system for aortic transillumination.
  • a first optical fiber 684 is positioned near a distal end of the perfusion filter catheter 670 , upstream of the embolic filter assembly 672 , so that it will emit a first laterally directed beam of light.
  • a second optical fiber 672 is positioned on the outer rim of the filter support structure 674 so that it will emit a second laterally directed beam of light.
  • An optical coupling 682 at the proximal end of the perfusion filter catheter 670 connects the optical fibers 684 , 672 to a light source 680 by way of an optical cable 678 .
  • the light beams emitted by the optical fibers 684 , 672 are visible through the aortic wall and can be used to locate and monitor the position and the deployment state of the perfusion filter catheter 670 and the embolic filter assembly 672 .
  • one or more optical fibers or other light emitting devices may be positioned on the aortic occlusion device to locate and monitor its position and state of deployment.
  • the features and embodiments of the present invention may also be combined with a bumper location device for facilitating catheter insertion and positioning by providing tactile feedback when the catheter device contacts the aortic valve.
  • Bumper location devices suitable for this application are described in commonly owned, copending U.S. patent application Ser. Nos. 60/060,158, filed Sep. 26, 1997, and No. 60/073,681, filed Feb. 4, 1998, which are hereby incorporated by reference in their entirety.

Abstract

A aortic filter catheter is used to capture potential emboli within the aorta during heart surgery and cardiopulmonary bypass. An expandable embolic filter assembly having fine filter mesh for capturing macroemboli and microemboli is mounted on a catheter shaft having a perfusion lumen with perfusion ports located upstream of the filter. The embolic filter assembly can be actively or passively deployed within the ascending aortic. The embolic filter assembly includes an aortic occlusion device, which may be a toroidal balloon, an expandable balloon or a selectively deployable external catheter flow control valve. The combined device allows percutaneous transluminal administration of cardiopulmonary bypass and cardioplegic arrest with protection from undesirable embolic events.

Description

    CROSS REFERENCE TO OTHER APPLICATIONS
  • This application is a divisional of U.S. patent application Ser. No. 09/158,405, filed Sep. 22, 1998, now U.S. Pat. No. 6,361,545, which claims the benefit of U.S. Provisional Application, serial No. 60/060,117, filed Sep. 26, 1997, which are hereby incorporated by reference in their entirety.[0001]
  • FIELD OF THE INVENTION
  • The present invention relates generally to a catheter or cannula for infusion of oxygenated blood or other fluids into a patient for cardiopulmonary support and cerebral protection. More particularly, it relates to an arterial perfusion catheter with a deployable embolic filter for protecting a patient from adverse effects due to emboli that are dislodged during cardiopulmonary bypass. [0002]
  • BACKGROUND OF THE INVENTION
  • Over the past decades tremendous advances have been made in the area of heart surgery, including such life saving surgical procedures as coronary artery bypass grafting (CABG) and cardiac valve repair or replacement surgery. Cardiopulmonary bypass (CPB) is an important enabling technology that has helped to make these advances possible. Recently, however, there has been a growing awareness within the medical community and among the patient population of the potential sequelae or adverse affects of heart surgery and of cardiopulmonary bypass. Chief among these concerns is the potential for stroke or neurologic deficit associated with heart surgery and with cardiopulmonary bypass. One of the likely causes of stroke and of neurologic deficit is the release of emboli into the blood stream during heart surgery. Potential embolic materials include atherosclerotic plaques or calcific plaques from within the ascending aorta or cardiac valves and thrombus or clots from within the chambers of the heart. These potential emboli may be dislodged during surgical manipulation of the heart and the ascending aorta or due to high velocity jetting (sometimes called the “sandblasting effect”) from the aortic perfusion cannula. Air that enters the heart chambers or the blood stream during surgery through open incisions or through the aortic perfusion cannula is another source of potential emboli. Emboli that lodge in the brain may cause a stroke or other neurologic deficit. Clinical studies have shown a correlation between the number and size of emboli passing through the carotid arteries and the frequency and severity of neurologic damage. At least one study has found that frank strokes seem to be associated with macroemboli larger than approximately 100 micrometers in size, whereas more subtle neurologic deficits seem to be associated with multiple microemboli smaller than approximately 100 micrometers in size. In order to improve the outcome of cardiac surgery and to avoid adverse neurological effects it would be very beneficial to eliminate or reduce the potential of such cerebral embolic events. [0003]
  • Several medical journal articles have been published relating to cerebral embolization and adverse cerebral outcomes associated with cardiac surgery, e.g.: Determination or Size of Aortic Emboli and Embolic Load During Coronary Artery Bypass Grafting; Barbut et al.; Ann Thorac Surg 1997;63; 1262-7; Aortic Atheromatosis and Risks of Cerebral Embolization; Barbut et al.; J Card & Vasc Anesth, Vol 10, No 1, 1996: pp 24; Aortic Atheroma is Related to Outcome but not Numbers of Emboli During Coronary Bypass; Barbut et al.; Ann Thorac Surg 1997;64;454-9; Adverse Cerebral Outcomes After Coronary Artery Bypass Surgery; Roach et al.; New England J of Med, Vol 335, No 25, 1996: pp 1857-1863; Signs of Brain Cell Injury During Open Heart Operations: Past and Present; Aberg; Ann Thorac Surg 1995;59; 1312-5; The Role of CPB Management in Neurobehavioral Outcomes After Cardiac Surgery; Murkin; Ann Thorac Surg 1995;59;1308-11; Risk Factors for Cerebral Injury and Cardiac Surgery; Mills; Ann Thorac Surg 1995;59;1296-9; Brain Microemboli Associated with Cardiopulmonary Bypass: A Histologic and Magnetic Resonance Imaging Study; Moody et al.; Ann Thorac Surg 1995;59;1304-7; CNS Dysfunction After Cardiac Surgery: Defining the Problem; Murkin; Ann Thorac Surg 1995;59; 1287+Statement of Consensus on Assessment of Neurobehavioral Outcomes After Cardiac Surgery; Murkin et al.; Ann Thorac Surg 1995;59;1289-95; Heart-Brain Interactions: Neurocardiology Comes of Age; Sherman et al.; Mayo Clin Proc 62:1158-1160, 1987; Cerebral Hemodynamics After Low-Flow Versus No-Flow Procedures; van der Linden; Ann Thorac Surg 1995;59;1321-5; Predictors of Cognitive Decline After Cardiac Operation; Newman et al.; Ann Thorac Surg 1995;59;1326-30; Cardiopulmonary Bypass: Perioperative Cerebral Blood Flow and Postoperative Cognitive Deficit; Venn et al.; Ann Thorac Surg 1995;59; 1331-5; Long-Term Neurologic Outcome After Cardiac Operation; Sotaniemi; Ann Thorac Surg 1995;59;1336-9; and Macroemboli and Microemboli During Cardiopulmonary Bypass; Blauth; Ann Thorac Surg 1995;59;1300-3. [0004]
  • The patent literature includes several references relating to vascular filter devices for reducing or eliminating the potential of embolization. These and all other patents and patent applications referred to herein are hereby incorporated herein by reference in their entirety. [0005]
  • The following U.S. patents relate to vena cava filters: U.S. Pat. Nos. 5,549,626, 5,415,630, 5,152,777, 5,375,612, 4,793,348, 4,817,600, 4,969,891, 5,059,205, 5,324,304, 5,108,418, 4,494,531. Vena cava filters are devices that are implanted into a patient's inferior vena cava for capturing thromboemboli and preventing them from entering the right heart and migrating into the pulmonary arteries. These are generally designed for permanent implantation and are only intended to capture relatively large thrombi, typically those over a centimeter in diameter, that could cause a major pulmonary embolism. As such, these are unsuitable for temporary deployment within a patient's aorta or for capturing macroemboli or microemboli associated with adverse neurological outcomes. Vena cava filters are also not adapted for simultaneously providing arterial blood perfusion in connection with cardiopulmonary bypass. [0006]
  • The following U.S. patents relate to vascular filter devices: U.S. Pat. Nos. 5,496,277, 5,108,419, 4,723,549, 3,996,938. These filter devices are not of a size suitable for deployment within a patient's aorta, nor would they provide sufficient filter surface area to allow aortic blood flow at normal physiologic flow rates without an unacceptably high pressure drop across the filter. Furthermore, these filter devices are not adapted for simultaneously providing arterial blood perfusion in connection with cardiopulmonary bypass devices. [0007]
  • The following U.S. patents relate to aortic filters or aortic filters associated with atherectomy devices: U.S. Pat. Nos. 5,662,671, 5,769,816. The following international patent applications relate to aortic filters or aortic filters associated with atherectomy devices: WO 97/17100, WO 97/42879, WO 98/02084. The following international patent application relates to a carotid artery filter: WO 98/24377. This family of U.S. and international patents includes considerable discussion on the mathematical relationship between blood flow rate, pressure drop, filter pore size and filter area and concludes that, for use in the aorta, it is desirable for the filter mesh to have a surface area of 3-10 in[0008] 2, more preferably 4-9 in2, 5-8 in2 or 6-8 in2, and most preferably 7-8 in2. While these patents state that this characteristic is desirable, none of the filter structures disclosed in the drawings and description of these patents appears capable of providing a filter surface area within these stated ranges when deployed within an average-sized human aorta. Accordingly, it would be desirable to provide a filter structure or other means that solves this technical problem by increasing the effective surface area of the filter mesh to allow blood flow at normal physiologic flow rates without an unacceptably high pressure drop.
  • SUMMARY OF THE INVENTION
  • In keeping with the foregoing discussion, the present invention takes the form of a perfusion filter catheter or cannula having an embolic filter assembly mounted on an elongated tubular catheter shaft. The elongated tubular catheter shaft is adapted for introduction into a patient's ascending aorta either by a peripheral arterial approach or by a direct aortic puncture. A fine filter mesh for capturing macroemboli and/or microemboli is mounted on the embolic filter assembly. The embolic filter assembly has an undeployed state in which the filter is compressed or wrapped tightly around the catheter shaft and a deployed state in which the embolic filter assembly expands to the size of the aortic lumen and seals against the inner wall of the aorta. The embolic filter assembly can be passively or actively deployable. Various mechanisms are disclosed for both passive and active deployment of the embolic filter assembly. Optionally, an outer tube may cover the embolic filter assembly when it is in the undeployed state. Radiopaque markers and/or sonoreflective markers, may be located on the catheter and/or the embolic filter assembly. Preferably, a perfusion lumen extends through the elongated tubular catheter shaft to one or more perfusion ports upstream of the embolic filter assembly. Oxygenated blood is perfused through the perfusion lumen and any embolic materials that might be dislodged are captured in the deployed embolic filter assembly. [0009]
  • In order to provide a sufficient flow rate of oxygenated blood for support of all critical organ systems through the filter without excessive pressure drop, it is preferred that the surface area of the filter mesh be greater than twice the cross-sectional area of the aortic lumen, more preferably three, four, five or six times greater than luminal cross section of the aorta. Preferably, the embolic filter assembly is also configured to hold at least a majority of the filter mesh away from the aortic wall when deployed to maximize the effective filter surface area. Several possible configurations are described for the embolic filter assembly that meet these parameters. The embolic filter assembly configurations described include an elongated cone, a frustum of a cone, a trumpet-shape, a modified trumpet-shape, and helically, circumferentially and longitudinally convoluted shapes. Further configurations are described having standoff members for centering the embolic filter assembly within the aorta and for holding at least a majority of the filter mesh away from the aortic walls when deployed. [0010]
  • Embodiments are also described that combine the perfusion filter catheter with an aortic occlusion device, which may be a toroidal balloon, an expandable balloon or a selectively deployable external catheter flow control valve. The combined device allows percutaneous transluminal administration of cardiopulmonary bypass and cardioplegic arrest with protection from undesirable embolic events. An embodiment of the perfusion filter catheter is described having an aortic transillumination system for locating and monitoring the position and the deployment state of the catheter and the embolic filter assembly without fluoroscopy. [0011]
  • In use, the perfusion filter catheter is introduced into the patient's aorta with the embolic filter assembly in a collapsed state either by a peripheral arterial approach or by a direct aortic puncture. The embolic filter assembly is advanced across the aortic arch and into the ascending aorta. When the embolic filter assembly is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the embolic filter assembly is either actively or passively deployed. The position of the catheter and the deployment state of the embolic filter assembly may be monitored using fluoroscopy, ultrasound, transesophageal echography (TEE) or aortic transillumination. Once the embolic filter assembly is deployed, oxygenated blood may be infused into the aorta through the perfusion lumen. Any potential emboli are captured by the embolic filter assembly and prevented from entering the neurovasculature or other branches downstream. After use, the embolic filter assembly is returned to the collapsed position and the catheter is withdrawn from the patient.[0012]
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIGS. [0013] 1-3 show a perfusion filter catheter configured for retrograde deployment via a peripheral arterial access point.
  • FIG. 1 is a cutaway perspective view of the perfusion filter catheter deployed within the aorta via femoral artery access. [0014]
  • FIG. 2 shows the distal end of the catheter with the embolic filter assembly in a deployed state. [0015]
  • FIG. 3 shows the distal end of the catheter with the embolic filter assembly in a collapsed state for insertion or withdrawal of the device from the patient. [0016]
  • FIGS. [0017] 4-6 show a method of passively deploying an embolic filter assembly on a perfusion filter catheter.
  • FIGS. 7, 7A, [0018] 8 and 8A show a flow-assisted method of passively deploying an embolic filter assembly on a perfusion filter catheter.
  • FIGS. [0019] 9-11 show a method of passively deploying a self-expanding and self-supporting embolic filter assembly on a perfusion filter catheter.
  • FIGS. [0020] 12-14 show a method of actively deploying an embolic filter assembly with a collapsible outer hoop and a plurality of actuation wires.
  • FIGS. [0021] 15-17 show a method of actively deploying an embolic filter assembly with an inflatable filter support structure.
  • FIGS. [0022] 18-20 show a method of actively deploying a spiral fluted embolic filter assembly by twisting or furling the embolic filter assembly around an inner catheter shaft.
  • FIGS. [0023] 21-23 show a method of actively deploying a circumferentially pleated embolic filter assembly on a perfusion filter catheter.
  • FIG. 24 shows a perfusion filter catheter adapted for retrograde deployment via subclavian artery access. [0024]
  • FIGS. [0025] 25-27 show a perfusion filter catheter adapted for antegrade deployment via direct aortic puncture.
  • FIGS. 28 and 29 show a perfusion filter catheter having an embolic filter assembly with a graded porosity filter screen. [0026]
  • FIGS. 30 and 30A show a perfusion filter catheter having a longitudinally fluted embolic filter assembly. [0027]
  • FIGS. 31 and 31A show a perfusion filter catheter having a longitudinally ribbed embolic filter assembly. [0028]
  • FIG. 32 shows a perfusion filter catheter having an embolic filter assembly that is surrounded by a cage of longitudinally oriented standoff members. [0029]
  • FIG. 33 shows a perfusion filter catheter having an embolic filter assembly that is surrounded by a cage of coiled wire standoff members. [0030]
  • FIG. 34 shows a perfusion filter catheter having an embolic filter assembly that is surrounded by a cage of coarse netting. [0031]
  • FIG. 35 shows a cutaway view of a perfusion filter catheter having an embolic filter assembly that is surrounded by a fender made from a porous foam or a fibrous network. [0032]
  • FIGS. 36 and 37 show an alternate embodiment of a perfusion filter catheter with a passively deployed embolic filter assembly. [0033]
  • FIGS. [0034] 38-41 show an alternate embodiment of a perfusion filter catheter with an actively deployed embolic filter assembly having a filter support structure with a preshaped, superelastic actuation wire.
  • FIGS. 42 and 43 show another alternate embodiment of a perfusion filter catheter with an actively deployed embolic filter assembly having a filter support structure with a preshaped, superelastic wire purse string loop. [0035]
  • FIGS. 44 and 45 show another alternate embodiment of a perfusion filter catheter with an actively deployed inflatable embolic filter assembly. [0036]
  • FIGS. [0037] 46-50 show the operation of an embodiment of a perfusion filter catheter that combines an embolic filter assembly with a toroidal balloon aortic occlusion device.
  • FIG. 51 shows an embodiment of a perfusion filter catheter that combines an embolic filter assembly with an inflatable balloon aortic occlusion device. [0038]
  • FIG. 52 shows an embodiment of a perfusion filter catheter that combines an embolic filter assembly with a selectively deployable external catheter flow control valve. [0039]
  • FIG. 53 shows an embodiment of a perfusion filter catheter with an embolic filter assembly having areas of different filter porosity. [0040]
  • FIG. 54 shows an embodiment of a perfusion filter catheter with a fiberoptic system for aortic transillumination.[0041]
  • DETAILED DESCRIPTION OF THE INVENTION
  • FIGS. [0042] 1-3 show a perfusion filter catheter 100 according to the present invention configured for retrograde deployment via a peripheral arterial access point. FIG. 1 is a cutaway perspective view of the perfusion filter catheter 100 deployed within the aorta of a patient via femoral artery access. FIG. 2 shows the distal end of the catheter 100 with the embolic filter assembly 102 in a deployed state. FIG. 3 shows the distal end of the catheter with the embolic filter assembly 102′ in a collapsed state for insertion or withdrawal of the device from the patient.
  • Referring now to FIG. 1, the [0043] perfusion filter catheter 100 includes an elongated tubular catheter shaft 104 with a proximal end 108 and distal end 110. The catheter shaft 104 is preferably extruded of a flexible thermoplastic material or a thermoplastic elastomer. Suitable materials for the catheter shaft 104 include, but are not limited to, polyvinylchloride, polyurethane, polyethylene, polypropylene, polyamides (nylons), and alloys or copolymers thereof, as well as braided, coiled or counterwound wire or filament reinforced composites. The tubular catheter shaft 104 may have a single lumen or multilumen construction. In the exemplary embodiment shown, the catheter 100 has a single perfusion lumen 106 extending from the proximal end 108 to the distal end 110 of the catheter shaft 104. The perfusion lumen 106 is open at the distal end 110 of the catheter shaft 104. The distal end 110 of the catheter shaft 104 may have a simple beveled or rounded distal edge, as shown, or it may include additional side ports or a flow diffuser to reduce jetting when oxygenated blood is infused through the perfusion lumen 106. The proximal end 108 of the elongated tubular catheter shaft 104 is adapted for connecting the perfusion lumen 106 to a cardiopulmonary bypass pump or other source of oxygenated blood using standard barb connectors or other connectors, such as a standard luer fitting (not shown). Preferably, the catheter shaft 104 is made with thin walled construction to maximize the internal diameter and therefore the flow rate of the perfusion lumen 106 for a given outside diameter and length of the catheter shaft 104. Thin walled construction also allows the outside diameter of the catheter shaft 104 to be minimized in order to reduce the invasiveness of the procedure and to reduce trauma at the insertion site. The perfusion lumen 106 should be configured to allow sufficient blood flow to preserve organ function without hemolysis or other damage to the blood. For standard cardiopulmonary support techniques, a catheter shaft 104 of 18-24 French size (6-8 mm outside diameter) is sufficient to deliver the requisite 3-4 liters of oxygenated blood to preserve organ function. For low flow cardiopulmonary support techniques, such as described in commonly owned, copending patent application Ser. No. 60/084,835, filed May 8, 1998 which is hereby incorporated by reference, the size of the catheter shaft 104 can be reduced to 9-18 French size (3-6 mm outside diameter) for delivering 0.5-3 liters of oxygenated blood to preserve organ function. The catheter shaft 104 should have a length sufficient to reach from the arterial access point where it is inserted to the ascending aorta of the patient. For femoral artery deployment, the catheter shaft 104 preferably has a length from approximately 80-120 cm.
  • A deployable [0044] embolic filter assembly 102 is located just proximal to the distal end 110 of the catheter shaft 104. The embolic filter assembly 102 includes a filter screen 112 made of a fine mesh material. In this exemplary embodiment and each of the other embodiments described below, the fine mesh material of the filter screen 112 may be a woven or knitted fabric, such as Dacron polyester or nylon mesh, or other textile fabrics, or it may be a nonwoven fabric, such as a spun bonded polyolefin or expanded polytetrafluoroethylene or other nonwoven materials. The fine mesh material of the filter screen 112 may be woven, knitted or otherwise formed from monofilament or multifilament fibers. The fine mesh material of the filter screen 112 may also be a fine wire mesh or a combination of wire and textile fibers. Alternatively, the fine mesh material of the filter screen 112 may be an open cell foam material. The fine mesh material of the filter screen 112 must be nontoxic and hemocompatible, that is, non-thrombogenic and non-hemolytic. Preferably, the fine mesh material of the filter screen 112 has a high percentage of open space, with a uniform pore size. The pore size of the filter screen 112 can be chosen to capture macroemboli only or to capture macroemboli and microemboli. In most cases the pore size of the filter screen 112 will preferably be in the range of 1-200 micrometers. For capturing macroemboli only, the pore size of the filter screen 112 will preferably be in the range of 50-200 micrometers, more preferably in the range of 80-100 micrometers. For capturing macroemboli and microemboli, the pore size of the filter screen 112 will preferably be in the range of 1-100 micrometers, more preferably in the range of 5-20 micrometers. In other applications, such as for treating thromboembolic disease, a larger pore size, e.g. up to 1000 micrometers (1 mm) or larger, would also be useful. In some embodiments, a combination of filter materials having different pore sizes may be used.
  • Alternatively or additionally the material of the filter screen in each embodiment of the filter catheter may be made of or coated with an adherent material or substance to capture or hold embolic debris which comes into contact with the filter screen within the embolic filter assembly. Suitable adherent materials include, but are not limited to, known biocompatible adhesives and bioadhesive materials or substances, which are hemocompatible and non-thrombogenic. Such materials are known to those having ordinary skill in the art and are described in, among other references, U.S. Pat. Nos. 4,768,523, 5,055,046, 5,066,709, 5,197,973, 5,225,196, 5,374,431, 5,578,310, 5,645,062, 5,648,167, 5,651,982, and 5,665,477. In one particularly preferred embodiment, only the upstream side of the elements of the filter screen are coated with the adherent material to positively capture the embolic debris which comes in contact with the upstream side of the filter screen after entering the filter assembly. Other bioactive substances, for example, heparin or thrombolytic agents, may be impregnated into or coated on the surface of the filter screen material or incorporated into an adhesive coating. [0045]
  • The [0046] embolic filter assembly 102 is movable between a collapsed state, as shown in FIG. 3, and an expanded or deployed state, as shown in FIGS. 1 and 2. The filter screen 112 may be attached directly to the catheter shaft 104 and it may constitute the entire embolic filter assembly 102, particularly if the filter screen 112 is made of a resilient or semirigid fabric that has enough body to be self-supporting in the deployed state. Generally, however, the embolic filter assembly 102 will also include a filter support structure 114, particularly if a highly flexible or flaccid material is used for the filter screen 112. The filter support structure 114 attaches and supports the filter screen 112 on the catheter shaft 104. In the illustrative embodiment of FIGS. 1-3, the filter support structure 114 is constructed with an outer hoop 116 and a plurality of struts 118 which extend approximately radially from a ring-shaped hub 126 that is mounted on the catheter shaft 104. In this case four struts 118 are shown, however, two, three or more struts 118 may be used. The open distal end 122 of the filter screen 112 is attached to the outer hoop 116 and the proximal end 120 of the filter screen 112 is sealingly attached to the catheter shaft 104. When the embolic filter assembly 102 is deployed, the outer hoop 116 of the filter support structure 114 holds the open distal end 122 of the filter screen 112 against the inner wall of the aorta, as shown in FIG. 1. To accommodate most normal adult aortas, the outer hoop 116 of the filter support structure 114 and the distal end 122 of the filter screen 112 have a diameter of approximately 2.5 to 4 cm, plus or minus 0.5 cm. Larger and smaller diameter filter support structures 114 may be made to accommodate patients with distended or Marfan syndrome aortas or for pediatric patients.
  • The [0047] embolic filter assembly 102 may be deployed by a passive means or by an active means. Passive means for deploying the embolic filter assembly 102 could include using the elastic memory of the filter screen 112 and/or the filter support structure 114 to deploy the embolic filter assembly 102, and/or using pressure from the blood flow in the aorta to deploy the embolic filter assembly 102. By contrast, active means for deploying the embolic filter assembly 102 could include one or more actuation members within the catheter shaft 104 for mechanically actuating the filter support structure 114 to deploy the embolic filter assembly 102 from the proximal end 108 of the catheter 100. Shape memory materials may also be used as actuation members for deploying the embolic filter assembly 102. Alternatively, active means for deploying the embolic filter assembly 102 could include one or more lumens within the catheter shaft 104 for hydraulically actuating the filter support structure 114 to deploy the embolic filter assembly 102. Passive means may be used to augment the action of the active deployment means. As shown in FIG. 3, an outer tube 124 may be provided to cover the embolic filter assembly 102 when it is in the collapsed state in order to create a smooth outer surface for insertion and withdrawal of the catheter 100 and to prevent premature deployment of the embolic filter assembly 102, particularly if passive deployment means are used.
  • The [0048] perfusion filter catheter 100 is prepared for use by folding or compressing the embolic filter assembly 102 into a collapsed state within the outer tube 124, as shown in FIG. 3. The distal end 110 of the catheter 100 is inserted into the aorta in a retrograde fashion. Preferably, this is done through a peripheral arterial access, such as the femoral artery or subclavian artery, using the Seldinger technique or an arterial cutdown. Alternatively, the catheter 100 may be introduced directly through an incision into the descending aorta after the aorta has been surgically exposed. The embolic filter assembly 102 is advanced up the descending aorta and across the aortic arch while in the collapsed state. The position of the catheter 100 may be monitored using fluoroscopy or ultrasound, such as transesophageal echography (TEE). Appropriate markers, which may include radiopaque markers and/or sonoreflective markers, may be located on the distal end 110 of the catheter 100 and/or the embolic filter assembly 102 to enhance imaging and to show the position of the catheter 100 and the deployment state of the embolic filter assembly 102. When the distal end 110 of the catheter 100 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 124 is withdrawn and the embolic filter assembly 102 is deployed, as shown in FIG. 3. Optionally, a distal portion of the catheter shaft 104 may be precurved to match the curvature of the aortic arch to aid in placement and stabilization of the catheter 100 and the embolic filter assembly 102 within the aorta. Once the embolic filter assembly 102 is deployed, oxygenated blood may be infused through the perfusion lumen 106 to augment cardiac output of the beating heart or to establish cardiopulmonary bypass so that the heart can be arrested. Any potential emboli are captured by the filter screen 112 and prevented from entering the neurovasculature or other branches downstream. After use, the embolic filter assembly 102 is returned to the collapsed position and the catheter 100 is withdrawn from the patient.
  • Preferably, the [0049] embolic filter assembly 102 is configured so that, when it is in the deployed state, at least a majority of the filter screen 112 is held away from the aortic walls so that flow through the pores of the filter screen 112 is not occluded by contact with the aortic wall. In addition, this also assures that blood flow into the side branches of the aorta will not be obstructed by the filter screen 112. In this way, each side branch of the aorta will receive the benefit of flow through the full surface area of the filter screen 112 so that blood flow is not restricted by the area of the ostium of each side branch. In the illustrative embodiment of FIGS. 1-3, the filter screen 112 has a roughly conical shape with an open distal end 122. The conical shape holds the fine mesh material of the filter screen 112 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 112.
  • Deployment of the [0050] embolic filter assembly 102 can be accomplished passively or actively. FIGS. 4-11 show various methods of passively deploying the embolic filter assembly 102 and FIGS. 12-23 show various methods of actively deploying the embolic filter assembly 102. FIGS. 4-6 show one method of passively deploying the embolic filter assembly 102. In this exemplary embodiment, the outer hoop 116 and the struts 118 of the filter support structure 114 are made of an elastic or superelastic metal or polymer, for example a superelastic nickel/titanium alloy, which is easily deformed into the collapsed state and which expands passively from the collapsed state to the deployed state. To place the embolic filter assembly 102 in the collapsed position shown in FIG. 4, the struts 118 are folded back in the proximal direction and the outer hoop 116 is folded against the catheter shaft 104 along with the material of the filter screen 112. The outer tube 124 is placed over the folded embolic filter assembly 102 to hold it in the collapsed position. Once the perfusion filter catheter 100 is in position within the patient's aorta, the outer tube 124 is pulled back, as shown in FIG. 5, to release the folded embolic filter assembly 102. The outer hoop 116 and struts 118 expand the filter screen 112 to its deployed position, shown in FIG. 6, and hold the open distal end 122 of the filter screen 112 against the inner wall of the aorta, as shown in FIG. 1. After use, the embolic filter assembly 102 is returned to the collapsed position by advancing the outer tube 124 distally over the filter screen 112 and the filter support structure 114, then the catheter 100 is withdrawn from the patient.
  • FIGS. 7, 7A, [0051] 8 and 8A show another method of passively deploying an embolic filter assembly 132 on a perfusion filter catheter 130. In this embodiment, the filter support structure includes a plurality of struts 136 which are hinged or flexibly attached at their inner, proximal ends to the catheter shaft 134. The struts 136 may be made of either a metal or a polymer. The distal end 138 of the filter screen 140 is attached to the struts 136 along an outer, distal portion of the struts 136. The proximal end 146 of the filter screen 140 is sealingly attached to the catheter shaft 134. The portion of the filter screen 140 attached to the struts 136 forms a skirt 142 along the distal edge of the filter assembly 132. The remaining portion of the filter screen 140 forms a filter pocket 144 along the proximal end of the filter assembly 132. The skirt 142 and the filter pocket 144 may be made of the same filter material or they may be made of different filter materials having different porosities. The skirt 142 of the filter screen 140 may even be made of a nonporous material.
  • The [0052] embolic filter assembly 132 is folded into the collapsed position shown in FIG. 7 by folding the struts 136 in the distal direction so they lie against the catheter shaft 134. FIG. 7A is a cutaway view of the catheter 130 with the embolic filter assembly 132 in the collapsed position. The material of the filter screen 140 is folded around or in between the struts 136. The outer tube 148 is placed over the folded embolic filter assembly 132 to hold it in the collapsed position. Once the perfusion filter catheter 130 is in position within the patient's aorta, the outer tube 148 is pulled back, as shown in FIG. 8, to release the folded embolic filter assembly 132. Blood flow within the aorta catches the skirt 142 of the filter screen 140 and forces the embolic filter assembly 132 to open into the deployed position shown in FIG. 8. FIG. 8A is a cutaway view of the catheter 130 with the embolic filter assembly 132 in the deployed position. Optionally, the struts 136 may be resiliently biased toward the deployed position to assist in passive deployment of the embolic filter assembly 132. As the embolic filter assembly 132 is passively opened by the blood flow, the skirt 142 of the filter screen 140 naturally and atraumatically seals against the aortic wall. The passive deployment of the skirt 142 also naturally compensates for patient-to-patient variations in aortic luminal diameter. The filter pocket 144 of the embolic filter assembly 132 is held away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 140.
  • FIGS. [0053] 9-11 show another method of passively deploying an embolic filter assembly 152 on a perfusion filter catheter 150. In this embodiment, the filter screen 154 is self-expanding and self-supporting, so no separate filter support structure is needed. Preferably, the embolic filter assembly 152 includes resilient wires or filaments 156 that are interwoven with the fibers of the filter screen 154. Alternatively, the resilient wires or filaments 156 may be attached to the interior or exterior surface of the filter screen 154 fabric. The resilient wires or filaments 156 may be made of either a polymer or a metal, such as an elastic or superelastic alloy. In one preferred embodiment, the resilient wires or filaments 156, and preferably the fibers of the filter screen 154 as well, are woven at an angle to the longitudinal axis of the embolic filter assembly 152, so that the embolic filter assembly 152 can expand and contract in diameter by changing the angle of the wires or filaments 156. Generally, as the embolic filter assembly 152 expands in diameter, the angle between the wires or filaments 156 and the longitudinal axis of the embolic filter assembly 152 increases and the embolic filter assembly 152 may also foreshorten. The resilient wires or filaments 156 urge the embolic filter assembly 152 to expand to the deployed position. The proximal end 158 of the filter screen 154 is sealingly attached to the catheter shaft 162.
  • The [0054] perfusion filter catheter 150 is shown in FIG. 9 with the embolic filter assembly 152 compressed into the collapsed position. The embolic filter assembly 152 compresses in diameter smoothly without folding as the resilient wires or filaments 156 and the fibers of the filter screen 154 decrease their angle with respect to the longitudinal axis of the embolic filter assembly 152. An outer tube 164 holds the embolic filter assembly 152 in the collapsed position. Once the perfusion filter catheter 150 is in position within the patient's aorta, the outer tube 164 is pulled back, which allows the embolic filter assembly 152 to expand, as shown in FIG. 10. As the embolic filter assembly 152 expands, the angle between the wires or filaments 156 and the longitudinal axis of the embolic filter assembly 152 increases and the embolic filter assembly 152 foreshortens slightly. FIG. 11 shows the embolic filter assembly 152 fully expanded in the deployed position. The resilient wires or filaments 156 are preformed so that, when deployed, the filter screen 154 has a roughly conical shape with an open distal end 160. The conical shape holds the filter screen 154 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 154. The distal end 160 of the embolic filter assembly 152 seals against the aortic wall. The self-expanding aspect of the embolic filter assembly 152 naturally compensates for patient-to-patient variations in aortic luminal diameter.
  • In alternate embodiments, the resilient wires or [0055] filaments 156 may be preformed to other geometries so that the filter screen 154 of the embolic filter assembly 152 assumes a different configuration when deployed, including each of the other configurations discussed within this patent specification.
  • FIGS. [0056] 12-14 show one method of actively deploying an embolic filter assembly 168 on a perfusion filter catheter 166. In this exemplary embodiment, the filter support structure 170 includes a collapsible outer hoop 172 and a plurality of actuation wires 174. The distal end 176 of the filter screen 180 is attached to the outer hoop 172 and the proximal end 182 of the filter screen 180 is sealingly attached to the catheter shaft 184. The actuation wires 174 are slidably received within actuation wire lumens 186 located in the outer wall of the catheter shaft 184. The actuation wires 174 exit the actuation wire lumens 186 through side ports 188 located near the distal end of the catheter shaft 184. The actuation wires 174 and the outer hoop 172 are each made of a resilient polymer or a metal, such as stainless steel, nickel/titanium alloy or the like.
  • The [0057] perfusion filter catheter 166 is shown in FIG. 12 with the embolic filter assembly 168 compressed into the collapsed position. The actuation wires 174 are withdrawn into the actuation wire lumens 186 through the side ports 188 and the outer hoop 172 is folded or collapsed against the catheter shaft 184. The material of the filter screen 180 is folded or collapsed around the catheter shaft 184. An outer tube 190 covers the embolic filter assembly 168 in the collapsed position to facilitate insertion of the catheter 166. Once the perfusion filter catheter 150 is in position within the patient's aorta, the outer tube 190 is pulled back to expose the embolic filter assembly 152. Then, the actuation wires 174 are advanced distally to expand the outer hoop 172 and the filter screen 180, as shown in FIG. 13. FIG. 14 shows the embolic filter assembly 168 fully expanded in the deployed position. In this exemplary embodiment, the filter screen 180 is configured as a frustum of a cone with an open distal end 176. The outer hoop 172 at the distal end 176 of the filter screen 180 seals against the aortic wall.
  • FIGS. [0058] 15-17 show another method of actively deploying an embolic filter assembly 202 on a perfusion filter catheter 200. In this embodiment, the filter support structure 204 includes an outer hoop 206 and a plurality of struts 208, which are all interconnected hollow tubular members. Preferably, the outer hoop 206 and the struts 208 are made of a flexible polymeric material. The filter support structure 204 is connected to an inflation lumen 210, which parallels the perfusion lumen 218 within the catheter shaft 212. At its proximal end, the inflation lumen 210 branches off from the catheter shaft 212 to a side arm 214 with a luer fitting 216 for connecting to a syringe or other inflation device. By way of example, this embodiment of the embolic filter assembly 202 is shown with a trumpet-shaped filter screen 220. The filter screen 220 includes a skirt portion 222 extending distally from a proximal, filter pocket 224. The skirt portion 222 is in the shape of a frustum of a cone with an open distal end, which is attached to the outer hoop 206. The filter pocket 224 is roughly cylindrical in shape with a closed proximal end, which is sealingly attached to the catheter shaft 212. The skirt 222 and the filter pocket 224 may be made of the same filter material or they may be made of different filter materials having different porosities. The skirt 222 of the filter screen 220 may even be made of a nonporous material.
  • The [0059] perfusion filter catheter 200 is shown in FIG. 17 with the embolic filter assembly 202 folded into a collapsed position. The outer hoop 206 and the struts 208 of the filter support structure 204 are deflated and the material of the filter screen 220 is folded or collapsed around the catheter shaft 212. An outer tube 226 covers the embolic filter assembly 202 in the collapsed position to facilitate insertion of the catheter 200. Optionally, the outer tube 226 may have a slit or a weakened longitudinal tear line along its length to facilitate removal of the outer tube 226 over the side arm 214 at the proximal end of the catheter 200. Once the perfusion filter catheter 200 is in position within the patient's aorta, the outer tube 226 is pulled back to expose the embolic filter assembly 202. Then, the embolic filter assembly 202 is deployed by inflating the outer hoop 206 and the struts 208 with fluid injected through the inflation lumen 210 to actively expand the filter support structure 204, as shown in FIG. 16. When the embolic filter assembly 202 is deployed, the outer hoop 206 of the filter support structure 204 seals against the inner wall of the aorta, as shown in FIG. 15. Preferably, at least the outer wall of the outer hoop 206 is somewhat compliant when inflated in order to compensate for patient-to-patient variations in aortic luminal diameter.
  • FIGS. [0060] 18-20 show another method of actively deploying an embolic filter assembly 232 on a perfusion filter catheter 230. In this embodiment, the filter support structure 234 includes an outer hoop 236 and a plurality of struts 238, which are connected to an inner catheter shaft 240. The outer hoop 236 and the struts 238 may be made of a resilient polymer or metal, for example a superelastic nickel/titanium alloy. The distal end 242 of the filter screen 244 is attached to the outer hoop 236. The proximal end 246 of the filter screen 244 is sealingly attached to an outer catheter shaft 250. The inner catheter shaft 240 is slidably and rotatably received within the outer catheter shaft 250. Preferably, the filter screen 244 has one or more spiral grooves or flutes 248 that wind helically around the filter screen 244.
  • The [0061] embolic filter assembly 232 is folded into the collapsed position shown in FIG. 20 by extending and rotating the inner catheter shaft 240 in a first direction with respect to the outer catheter shaft 250. This collapses the filter support structure 234 back against the inner catheter shaft 240 and furls the filter screen 244 around the inner catheter shaft 240. The spiral flutes 248 in the filter screen 244 help it to collapse smoothly around the inner catheter shaft 240. An outer tube 252 covers the embolic filter assembly 232 in the collapsed position to facilitate insertion of the catheter 230. Once the perfusion filter catheter 230 is in position within the patient's aorta, the outer tube 252 is pulled back to expose the embolic filter assembly 232. Then, the embolic filter assembly 232 is deployed by rotating the inner catheter shaft 240 in the opposite direction with respect to the outer catheter shaft 250 and allowing it to retract slightly, as shown in FIG. 19. The filter support structure 234 and the filter screen 244 will expand within the aorta and the distal end 242 of the filter screen 244 will seal against the aortic wall, as shown in FIG. 18. When it is in the deployed position, the spiral flutes 248 of the embolic filter assembly 232 hold most of the filter screen 244 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 244. After use, the embolic filter assembly 232 is returned to the collapsed position as described above and the catheter 230 is withdrawn from the patient.
  • The coaxial arrangement of the [0062] inner catheter shaft 240 and the outer catheter shaft 250 in this embodiment of the perfusion filter catheter 230 creates an annular space that can optionally be used as a lumen 258 to aspirate potential emboli that are captured by the filter screen 244. To facilitate this, a side arm 254 with a luer fitting and a sliding hemostasis valve 256 may be added to the proximal end of the outer catheter shaft 250, as shown in FIG. 18.
  • FIGS. [0063] 21-23 show another method of actively deploying an embolic filter assembly 262 on a perfusion filter catheter 260. In this embodiment, the filter support structure 234 includes an outer hoop 266 and a plurality of struts 268, which are connected to an inner catheter shaft 270. The outer hoop 266 and the struts 268 may be made of a resilient polymer or metal, for example a superelastic nickel/titanium alloy. The distal end 272 of the filter screen 274 is attached to the outer hoop 266. The proximal end 276 of the filter screen 274 is sealingly attached to an outer catheter shaft 280. The inner catheter shaft 270 is slidably received within the outer catheter shaft 280. Preferably, the filter screen 274 has a series of circumferential pleats 278 that give the filter screen 274 an accordion appearance.
  • The [0064] embolic filter assembly 262 is folded into the collapsed position shown in FIG. 23 by extending the inner catheter shaft 270 distally with respect to the outer catheter shaft 280. This collapses the filter support structure 264 back against the inner catheter shaft 270 and collapses the circumferential pleats 248 of the filter screen 274 against the inner catheter shaft 270. An outer tube 282 covers the embolic filter assembly 262 in the collapsed position to facilitate insertion of the catheter 260. Once the perfusion filter catheter 260 is in position within the patient's aorta, the outer tube 282 is pulled back to expose the embolic filter assembly 262. Then, the embolic filter assembly 262 is deployed by retracting the inner catheter shaft 270 proximally with respect to the outer catheter shaft 280, as shown in FIG. 22. The filter support structure 264 and the filter screen 274 will expand within the aorta and the distal end 272 of the filter screen 274 will seal against the aortic wall, as shown in FIG. 21. When it is in the deployed position, the circumferential pleats 278 of the embolic filter assembly 262 hold the majority of the filter screen 274 away from the aortic walls and away from the ostia of the side branches so that blood can flow freely through the pores of the filter screen 274. After use, the embolic filter assembly 262 is returned to the collapsed position as described above and the catheter 260 is withdrawn from the patient.
  • As with the previous embodiment, the coaxial arrangement of the [0065] inner catheter shaft 270 and the outer catheter shaft 280 in this embodiment of the perfusion filter catheter 260 creates an annular space that can optionally be used as a lumen 288 to aspirate potential emboli that are captured by the filter screen 274. To facilitate this, a side arm 284 with a luer fitting and a sliding hemostasis valve 286 may be added to the proximal end of the outer catheter shaft 280, as shown in FIG. 21.
  • Active deployment of the embolic filter assembly can also be accomplished with any of the preceding embodiments by using shape memory materials, such as a nickel/titanium alloy, to construct the filter support structure and/or the actuation members. The transition temperature of the shape memory material should be chosen to be close to normal body temperature so that extreme temperature variations will not be necessary for deployment. The shape memory material of the filter support structure should be annealed in the deployed position to confer a shape memory in this configuration. Then, the embolic filter assembly should be cooled below the transition temperature of the shape memory material, so that the filter support structure is malleable and can be shaped into a collapsed position. Depending on the transition temperature, this can be done at room temperature or in iced saline solution. If desired, an outer tube can be placed over the embolic filter assembly to facilitate catheter insertion and to avoid premature deployment. Once the perfusion filter catheter is in position within the patient's aorta, the outer tube is pulled back to expose the embolic filter assembly and the filter support structure is heated above the transition temperature to deploy the embolic filter assembly. Depending on the transition temperature of the shape memory material, the filter support structure can be passively heated by body heat (accounting, of course, for decreased body temperature during hypothermic cardiopulmonary support methods) or it can be self-heated by applying an electrical current through the filter support structure. When heated, the filter support structure expands to its annealed configuration within the aorta. After use, the embolic filter assembly is returned to the collapsed position by advancing the outer tube distally over the filter screen and the filter support structure, then the catheter is withdrawn from the patient. [0066]
  • The foregoing examples of the perfusion filter catheter of the present invention showed retrograde deployment of the device within the aorta via femoral artery access. Each of the described embodiments of the perfusion filter catheter can also be adapted for retrograde deployment via subclavian artery access or for antegrade or retrograde deployment via direct aortic puncture. [0067]
  • FIG. 24 shows a [0068] perfusion filter catheter 290 which is adapted for retrograde deployment via subclavian artery access. In this exemplary embodiment, the perfusion filter catheter 290 is depicted with a trumpet-style, passively-deployed embolic filter assembly 292. Because it is intended for subclavian artery access, the perfusion filter catheter 290 has a tubular catheter shaft 294 with a length of approximately 60-90 cm. Because of the shorter length, as compared to the femoral version of the catheter, the outside diameter of the catheter shaft 294 can be reduced to 12-18 French size (4-6 mm outside diameter) for delivering the 3-4 liters of oxygenated blood needed to preserve organ function. The reduced diameter of the catheter shaft 294 is especially advantageous for subclavian artery delivery of the catheter 290. To further reduce the size of the catheter system for subclavian or femoral artery delivery, the outer tube 296 may be adapted for use as an introducer sheath by the addition of an optional hemostasis valve 298 at the proximal end of the outer tube 296. This eliminates the need for a separate introducer sheath for introducing the catheter 290 into the circulatory system.
  • In use, the [0069] perfusion filter catheter 290 is introduced into the subclavian artery with the embolic filter assembly 292 in a collapsed state within the outer tube 296, using the Seldinger technique or an arterial cutdown. The embolic filter assembly 292 is advanced across the aortic arch while in the collapsed state. The position of the catheter 292 may be monitored using fluoroscopy or ultrasound, such as transesophageal echography (TEE). Radiopaque markers and/or sonoreflective markers, may be located on the catheter 290 and/or the embolic filter assembly 292 to enhance imaging and to show the position of the catheter 290 and the deployment state of the embolic filter assembly 292. When the distal end of the catheter 290 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 296 is withdrawn and the embolic filter assembly 292 is either actively or passively deployed, as shown in FIG. 24. Once the embolic filter assembly 292 is deployed, oxygenated blood may be infused into the aorta through the tubular catheter shaft 294. Any potential emboli are captured by the embolic filter assembly 292 and prevented from entering the neurovasculature or other branches downstream. After use, the embolic filter assembly 292 is returned to the collapsed position and the catheter 290 is withdrawn from the patient.
  • Retrograde deployment of the [0070] perfusion filter catheter 290 via direct aortic puncture is quite similar to introduction via subclavian artery access, except that the catheter 290 is introduced directly into the descending aorta after it has been surgically exposed, for example during open-chest or minimally invasive cardiac surgery. Because of the direct aortic insertion, the length and the diameter of the catheter shaft 294 may be further reduced.
  • FIGS. [0071] 25-27 show a perfusion filter catheter 300 which is adapted for antegrade deployment via direct aortic puncture. In this exemplary embodiment, the perfusion filter catheter 300 is depicted with a hybrid-style embolic filter assembly 302, which is a compromise between the conical filter screen and the trumpet-style filter screen previously described. Because the catheter 300 is introduced directly into the ascending aorta, the catheter shaft 304 can be reduced to a length of approximately 20-60 cm and an outside diameter of approximately 12-18 French size (4-6 mm outside diameter) for delivering the 3-4 liters of oxygenated blood needed to preserve organ function during cardiopulmonary bypass. An important modification that must be made to the catheter 300 for antegrade deployment is that the perfusion port or ports 306 which connect to the perfusion lumen 308 must exit the catheter shaft 304 proximal to the filter screen 310 so that fluid flow will come from the upstream side of the embolic filter assembly 302. The catheter shaft 304 need not extend all the way to the distal end of the filter screen 310. The filter screen 310 may be entirely supported by the filter support structure 312, particularly if the embolic filter assembly 302 is to be passively deployed. Alternatively, a small diameter filter support member 314 may extend from the catheter shaft 304 to the distal end of the filter screen 310. If the embolic filter assembly 302 is intended to be actively deployed, the filter support member 314 may be slidably and/or rotatably received within the catheter shaft 304. Either of these configurations allows the embolic filter assembly 302 to be folded or compressed to a size as small as the diameter of the catheter shaft 304 to facilitate insertion of the catheter 300. Optionally, an outer tube 316 may be placed over the folded embolic filter assembly 302 to hold it in the collapsed position.
  • In use, the ascending aorta of the patient is surgically exposed, using open-chest or minimally invasive surgical techniques. A [0072] purse string suture 318 is placed in the ascending aorta and an aortotomy incision is made through the aortic wall. The catheter 300, with the embolic filter assembly 302 in the collapsed position within the outer tube 316, is inserted through the aortotomy and advanced antegrade into the aortic arch. When the proximal end of the embolic filter assembly 302 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 316 is withdrawn and the embolic filter assembly 302 is either actively or passively deployed, as shown in FIG. 25. Once the embolic filter assembly 302 is deployed, oxygenated blood may be infused into the aorta through the tubular catheter shaft 304. Any potential emboli are captured by the embolic filter assembly 302 and prevented from entering the neurovasculature or other branches downstream. After use, the embolic filter assembly 302 is returned to the collapsed position, the catheter 300 is withdrawn from the patient, and the purse string suture 318 is tightened to close the aortotomy.
  • In general, each of the passive and active deployment methods described above may be used interchangeably or together in combinations with each of the embodiments of the perfusion filter catheter and each of catheter insertion methods which are described above and below. Likewise, many of the features of the embodiments described may be used in various combinations with one another to create new embodiments, which are considered to be a part of this disclosure, as it would be too cumbersome to describe all of the numerous possible combinations and subcombinations of the disclosed features. [0073]
  • Following are a number of alternate embodiments of the perfusion filter catheter of the present invention illustrating additional features and variations in the configuration of the invention. In general, each of the described embodiments may be passively or actively deployed by the methods described above. Each embodiment of the perfusion filter catheter described can also be adapted for retrograde deployment via peripheral arterial access, such as femoral or subclavian artery access, or for antegrade or retrograde deployment via direct aortic puncture. [0074]
  • FIGS. 28 and 29 show a [0075] perfusion filter catheter 320 having an embolic filter assembly 322 with a graded porosity filter screen 324. The filter screen 324 is attached to a filter support structure 326 mounted on a catheter shaft 328 for antegrade or retrograde deployment. The filter screen 324 may be made in each of the configurations disclosed herein or any other convenient shape. By way of example, the filter screen 324 in this embodiment is depicted as being in the shape of a frustum of a cone. The filter screen 324 has an upstream end 330 and a downstream end 332. The upstream end 330 of the filter screen 324 has a finer filter mesh than the downstream end 332. Depending on the capabilities of the fabrication process used, the pore size of the filter screen 324 may make a gradual transition from the upstream end 330 to the downstream end 332 or there may be two or more discrete zones of varying pore size. In one preferred embodiment, the filter mesh on the upstream end 330 has a pore size of approximately 5-50 micrometers for capturing microemboli and macroemboli and the filter mesh on the downstream end 332 has a pore size of approximately 50-100 micrometers for capturing macroemboli only. The pore size of the filter screen 324 has been greatly exaggerated in FIG. 28 for clarity of illustration.
  • In use, the [0076] perfuision filter catheter 320 is introduced into the aorta with the embolic filter assembly 322 in a collapsed state within an outer tube 334, using one of the methods described above. The embolic filter assembly 322 is advanced across the aortic arch while in the collapsed state. When the upstream end 336 of the catheter 320 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 334 is withdrawn and the embolic filter assembly 322 is either actively or passively deployed, as shown in FIG. 29. Preferably, the embolic filter assembly 292 is dimensioned so that when it is deployed, the upstream end 330 of the filter screen 324 is positioned in the vicinity of the ostia for the brachiocephalic artery and the left common carotid artery and the downstream end 332 of the filter screen 324 is positioned downstream of this position, preferably in the descending aorta. This configuration assures that all of the perfusate which is destined for the neurovasculature must pass through the finer, upstream end 330 of the filter screen 324 to remove all microemboli and macroemboli. Whereas, the perfusate which is destined for the viscera and the lower limbs, which are more tolerant of small emboli, need only pass through the downstream end 332 of the filter screen 324, so as to remove at least the macroemboli.
  • FIG. 30 shows a [0077] perfusion filter catheter 340 having a longitudinally fluted embolic filter assembly 342. The embolic filter assembly 342 has a filter screen 344 that is attached at its open distal end 352 to a filter support structure 346 mounted on a catheter shaft 348 for antegrade or retrograde deployment. The filter screen 344 has a plurality of longitudinally oriented folds or flutes 350. FIG. 30A is a cutaway section of the embolic filter assembly 342 cut along line 30A in FIG. 30 in order to better show the longitudinal flutes 350. The longitudinal flutes 350 provide additional surface area to the filter screen 344 to reduce pressure drop from blood flow across the embolic filter assembly 342. The longitudinal flutes 350 also serve to hold a majority of the filter screen 344 away from the aortic wall and away from the ostia of the arch vessels. The longitudinally fluted embolic filter assembly 342 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 31 shows a [0078] perfusion filter catheter 360 having a longitudinally ribbed embolic filter assembly 362. The embolic filter assembly 362 has a filter screen 364 that is attached at its open distal end 372 to a filter support structure 366 mounted on a catheter shaft 368 for antegrade or retrograde deployment. The filter screen 364 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen. The embolic filter assembly 362 has a plurality of longitudinally oriented ribs 370 positioned around the exterior of the filter screen 364. FIG. 31A is a cutaway section of the embolic filter assembly 362 cut along line 31A in FIG. 31 in order to better show the longitudinally oriented ribs 370. The longitudinal ribs 370 serve as standoff members to center the filter screen 364 within the aorta so as hold a majority of the filter screen 364 away from the aortic wall and away from the ostia of the arch vessels. The longitudinally ribbed embolic filter assembly 362 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 32 shows a [0079] perfusion filter catheter 380 having an embolic filter assembly 382 that is surrounded by a cage 394 of standoff members 396. The embolic filter assembly 382 has a filter screen 384 that is attached at its open distal end 392 to a filter support structure 386 mounted on a catheter shaft 388 for antegrade or retrograde deployment. The filter screen 384 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen. The embolic filter assembly 382 further includes a plurality of standoff members 396 that form a cage 394 surrounding the filter screen 384. The standoff members 396 may be made of a resilient polymer or metal, such as an elastic or superelastic alloy, or a shape-memory material. The geometry of the standoff members 396 is quite variable. By way of example, FIG. 32 depicts the standoff members 396 as a plurality of longitudinally oriented wires which, together, form a roughly cylindrical cage 394. Other possible configurations include circumferential members, diagonal members, and combinations thereof. The standoff members 396 of the cage 394 serve to center the filter screen 384 within the aorta so as hold a majority of the filter screen 384 away from the aortic wall and away from the ostia of the arch vessels. The embolic filter assembly 382 and the standoff members 396 of the cage 394 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 33 shows a [0080] perfusion filter catheter 400 having an embolic filter assembly 402 that is 10 surrounded by a cage 414 of coiled wire standoff members 416. The embolic filter assembly 402 has a filter screen 404 that is attached at its open distal end 412 to a filter support structure 406 mounted on a catheter shaft 408 for antegrade or retrograde deployment. The filter screen 404 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen. The embolic filter assembly 402 further includes a plurality of loosely coiled wire standoff members 416 which form a cage 414 surrounding the filter screen 404. The coiled standoff members 416 may be made of a resilient polymer or metal, such as an elastic or superelastic alloy, or a shape-memory material. The coiled standoff members 416 of the cage 414 serve to center the filter screen 404 within the aorta so as hold a majority of the filter screen 404 away from the aortic wall and away from the ostia of the arch vessels. The embolic filter assembly 402 and the standoff members 416 of the cage 414 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 34 shows a [0081] perfusion filter catheter 420 having an embolic filter assembly 422 that is surrounded by a cage 434 of coarse netting 436. The embolic filter assembly 422 has a filter screen 424 that is attached at its open distal end 432 to a filter support structure 426 mounted on a catheter shaft 428 for antegrade or retrograde deployment. The filter screen 424 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen. The embolic filter assembly 422 further includes a coarse netting 436, which forms a roughly cylindrical cage 434 surrounding the filter screen 424. The netting 436 may be made of a resilient polymer or metal, such as an elastic or superelastic alloy, or a shape-memory material. The netting 436 of the cage 434 serves to center the filter screen 424 within the aorta so as hold a majority of the filter screen 424 away from the aortic wall and away from the ostia of the arch vessels. The embolic filter assembly 422 and the coarse netting 436 of the cage 434 can be adapted for passive or active deployment by any of the methods described above.
  • FIG. 35 shows a cutaway view of a [0082] perfusion filter catheter 440 having an embolic filter assembly 442 that is surrounded by a fender 454 made from a porous foam or a fibrous network 456. The embolic filter assembly 442 has a filter screen 444 that is attached at its open distal end 452 to a filter support structure 446 mounted on a catheter shaft 448 for antegrade or retrograde deployment. The filter screen 444 may be configured as a conical, trumpet, longitudinally fluted or other style of filter screen. The embolic filter assembly 442 further includes a roughly cylindrical fender 454 made from a highly porous foam or a fibrous network 456, which surrounds the filter screen 444. The fender 454 may be made of a highly porous open cell polymer foam or a network of polymeric fibers. The fender 454 serves to center the filter screen 444 within the aorta so as hold a majority of the filter screen 444 away from the aortic wall and away from the ostia of the arch vessels. The embolic filter assembly 442 and the fender 454 can be adapted for passive or active deployment or a combination thereof.
  • FIGS. 36 and 37 show an alternate embodiment of a [0083] perfusion filter catheter 460 with a passively deployed embolic filter assembly 462. The embolic filter assembly 462 has a filter screen 464 that is attached at its open distal end 474 to a filter support structure 466 mounted on a catheter shaft 468 for antegrade or retrograde deployment. The proximal end 476 of the filter screen 464 is sealingly attached to the catheter shaft 468. The filter screen 464 may be configured as a conical, trumpet or other style of filter screen. The filter support structure 466 has an outer hoop 470 which is attached by a perpendicular leg 472 to the catheter shaft 468. Preferably, the outer hoop 470 is made of a resilient polymer or metal, such as an elastic or superelastic alloy, or possibly a shape-memory material. The filter support structure 466, in this embodiment, has no struts. Optionally, the distal end 478 of the catheter shaft 468 may be curved toward the center of the outer hoop 470 to help center the perfusion port 480 located at the distal end of the catheter shaft 468 within the aorta when the catheter 460 is deployed. Also, the perfusion port 480 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 482.
  • The [0084] perfusion filter catheter 460 is prepared for use by bending the outer hoop 470 in the proximal direction or wrapping it around the catheter shaft 468, then folding or wrapping the material of the filter screen 464 around the catheter shaft 468. An outer tube 484 is placed over the embolic filter assembly 462 to hold it in the collapsed position, as shown in FIG. 37. The catheter 460 is introduced and the embolic filter assembly 462 is advanced across the aortic arch while in the collapsed state. When the distal end 474 of the embolic filter assembly 462 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 484 is withdrawn and the resilient outer hoop 470 expands to deploy the embolic filter assembly 462, as shown in FIG. 36. The outer hoop 470 and the distal end 474 of the filter screen 464 will seal against the aortic wall. After use, the embolic filter assembly 462 is returned to the collapsed position by advancing the outer tube 484 distally over the filter screen 464 and the filter support structure 466, then the catheter 460 is withdrawn from the patient.
  • FIGS. [0085] 38-41 show an alternate embodiment of a perfusion filter catheter 490 with an actively deployed embolic filter assembly 492. The embolic filter assembly 492 has a filter screen 494 with a sewn tubular channel 496 which extends circumferentially around the open distal end 498 of the filter screen 494. The distal end 498 of the filter screen 494 is attached on one side to the catheter shaft 504, and the proximal end 506 of the filter screen 494 is sealingly attached to the catheter shaft 504. The filter screen 494 may be configured as a conical, trumpet or other style of filter screen. The filter support structure in this embodiment consists of a preshaped, superelastic actuation wire 500, which, when the embolic filter assembly 492 is in the collapsed state, resides in a second lumen 502 within the catheter shaft 504. Preferably, the actuation wire 500 has a bead or small loop 508 at its distal end to create a blunt, non-piercing tip. The second lumen 502 of the catheter shaft 504 communicates with the tubular channel 496 at the distal end 498 of the filter screen 494. When the actuation wire 500 is extended, it forms a hoop as it passes through the tubular channel 496 of the filter screen 494.
  • Optionally, the [0086] distal end 510 of the catheter shaft 504 may be curved toward the center of the embolic filter assembly 492 to help center the perfusion port 510 located at the distal end of the catheter shaft 504 within the aorta when the catheter 490 is deployed. Also, the perfusion port 510 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 512 during cardiopulmonary bypass.
  • The [0087] perfusion filter catheter 490 is prepared for use by withdrawing the actuation wire 500 into the second lumen 502, then folding or wrapping the flexible material of the filter screen 494 around the catheter shaft 504. Optionally, an outer tube 514 may be placed over the embolic filter assembly 492 to hold it in the collapsed position, as shown in FIG. 38. The catheter 490 is introduced and the embolic filter assembly 492 is advanced across the aortic arch while in the collapsed state. When the distal end 498 of the embolic filter assembly 492 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 514 is withdrawn, which allows the filter screen 494 to unwrap from the catheter shaft 504, as shown in FIG. 39.
  • Then, the preshaped, [0088] superelastic actuation wire 500 is advanced distally so that it begins to form a hoop as it passes through the tubular channel 496 at the distal end 498 of the filter screen 494, as shown in FIG. 40. The actuation wire 500 is further advanced until it forms a complete hoop, as shown in FIG. 41, thereby sealing the distal end 498 of the filter screen 494 against the aortic wall. After use, the embolic filter assembly 492 is returned to the collapsed position as described above, then the catheter 490 is withdrawn from the patient.
  • FIGS. 42 and 43 show another alternate embodiment of a [0089] perfusion filter catheter 520 with an actively deployed embolic filter assembly 522. The embolic filter assembly 522 has a filter screen 524 with a sewn tubular channel 526 which extends circumferentially around the open distal end 528 of the filter screen 524. The distal end 528 of the filter screen 524 is attached on one side to the catheter shaft 534, and the proximal end 536 of the filter screen 524 is sealingly attached to the catheter shaft 534. The filter screen 524 may be configured as a conical, trumpet or other style of filter screen. The filter support structure in this embodiment consists of a preshaped, elastic or superelastic wire loop 530. The wire loop 530 passes through the tubular channel 526 at the distal end 528 of the filter screen 524. When the embolic filter assembly 522 is in the collapsed position, the wire loop 530 is withdrawn into a second lumen 532 within the catheter shaft 534, as shown in FIG. 42. In the collapsed position, the wire loop 530 acts as a purse string to close the filter screen 524 tightly around the catheter shaft 534. When the wire loop 530 is advanced distally, it forms a hoop that holds the distal end 528 of the filter screen 524 open, as shown in FIG. 43.
  • Optionally, the [0090] distal end 540 of the catheter shaft 534 may be curved toward the center of the embolic filter assembly 522 to help center the perfusion port 542 located at the distal end of the catheter shaft 534 within the aorta when the catheter 520 is deployed. Also, the perfusion port 540 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 544 during cardiopulmonary bypass.
  • The [0091] perfusion filter catheter 520 is prepared for use by withdrawing the wire loop 530 into the second lumen 532, then folding or wrapping the flexible material of the filter screen 524 around the catheter shaft 534. Optionally, an outer tube 538 may be placed over the embolic filter assembly 522 to hold it in the collapsed position. The catheter 520 is introduced and the embolic filter assembly 522 is advanced across the aortic arch while in the collapsed state. When the distal end 528 of the embolic filter assembly 522 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 538 is withdrawn, and the preshaped, superelastic wire loop 530 is advanced distally so that it forms a hoop that holds the distal end 528 of the filter screen 524 open and seals against the aortic wall. The inherent adjustability of the wire loop 530 used to deploy the embolic filter assembly 522 naturally compensates for patient-to-patient variations in aortic luminal diameter. After use, the embolic filter assembly 522 is returned to the collapsed position by withdrawing the wire loop 530 into the second lumen 532. This closes the filter screen 524 like a purse string to capture any potential emboli that are in the embolic filter assembly 522. Then, the catheter 520 is withdrawn from the patient.
  • FIGS. 44 and 45 show another alternate embodiment of a [0092] perfusion filter catheter 550 with an actively deployed embolic filter assembly 552. The embolic filter assembly 552 has a filter screen 554 with an open distal end 558 that is attached to a toroidal balloon 560. The toroidal balloon 560 is attached on one side to the catheter shaft 564 and it is fluidly connected to an inflation lumen 562 within the catheter shaft 564. The proximal end 566 of the filter screen 554 is sealingly attached to the catheter shaft 564. The filter screen 554 may be configured as a conical, trumpet or other style of filter screen. Optionally, the distal end 570 of the catheter shaft 564 may be curved toward the center of the embolic filter assembly 552 to help center the perfusion port 572 located at the distal end of the catheter shaft 564 within the aorta when the catheter 550 is deployed. Also, the perfusion port 570 may optionally include additional side ports or a flow diffuser, as shown, to reduce jetting when oxygenated blood is infused through the perfusion lumen 574 during cardiopulmonary bypass.
  • The [0093] perfusion filter catheter 550 is prepared for use by deflating the toroidal balloon 560, then folding or wrapping the deflated toroidal balloon 560 and the filter screen 554 around the catheter shaft 564. Optionally, an outer tube 564 may be placed over the embolic filter assembly 552 to hold it in the collapsed position, as shown in FIG. 44. The catheter 550 is introduced and the embolic filter assembly 552 is advanced across the aortic arch while in the collapsed state. When the distal end 558 of the embolic filter assembly 552 is positioned in the ascending aorta between the aortic valve and the brachiocephalic artery, the outer tube 564 is pulled back to expose the embolic filter assembly 552. Then, the embolic filter assembly 202 is deployed by inflating the toroidal balloon 560 with fluid injected through the inflation lumen 562, as shown in FIG. 45. When the embolic filter assembly 552 is deployed, the toroidal balloon 560 seals against the inner wall of the aorta. Preferably, at least the outer wall of the toroidal balloon 560 is somewhat compliant when inflated in order to compensate for patient-to-patient variations in aortic luminal diameter. After use, the toroidal balloon 560 is deflated and the catheter 550 is withdrawn from the patient.
  • Ideally, it is preferable that the embolic filter assembly of the perfusion filter catheter be deployed continuously throughout the entire period of cardiopulmonary bypass or extracorporeal perfusion. It is most critical, however, that the embolic filter assembly be deployed during periods when the potential for embolization is the highest, such as during manipulations of the heart and the aorta, during clamping and unclamping of the aorta and during the initial period after the heart is restarted following cardioplegic arrest. It has been previously stated that, for continuous deployment of a filter device in the aortic lumen, it is desirable for the filter mesh to have a surface area of 3-10 in[0094] 2. The shallow, cone-shaped aortic filter devices illustrated in the known prior art only manage to provide surface areas at the lower end of this desired range in the largest of human aortas (approximately 3.0-3.9 in2 in aortas of 3.5-4.0 cm diameter estimated based on the drawings and descriptions in the prior art disclosures) and in no cases are there embodiments disclosed which could provide surface areas in the middle and upper end of this range or that could even meet the minimum limit of this desired range in more typically sized aortas in the range of 2.5-3.5 cm diameter. Consequently, it is the opinion of the present inventors that the prior art does not provide an adequate solution to the technical problem that it illuminates.
  • The solution to this dilemma is to provide a filter assembly that has a greater ratio of filter surface area to the cross-sectional area of the aortic lumen. (The cross-sectional area of the aortic lumen being approximately equal to the area of the open upstream end of the embolic filter assembly at its deployed diameter within the aorta.) Preferably, the embolic filter assembly should provide a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 2, more preferably greater than 3, more preferably greater than 4, more preferably greater than 5 and most preferably greater than 6. With these ratios of the filter surface area to the cross-sectional area of the aortic lumen, it is possible to achieve a filter mesh surface area of 3-10 in[0095] 2 or greater in all typical adult human aortas ranging from 2.0 to 4.0 cm in diameter. Furthermore, given the embolic filter assembly structures that have been disclosed herein, it is envisioned that ratios of the filter surface area to the cross-sectional area of the aortic lumen of 8, 10, 12 and even greater are readily achievable. Higher ratios such as these are desirable as they allow a very fine filter mesh to be utilized to effectively capture both macroemboli and microemboli without compromising the aortic blood flow. Along with this, it is preferable to utilize an embolic filter assembly structure or other means that maximizes the effective surface area of the filter mesh by holding at least a majority of the filter mesh away from the aortic wall or any other structures that might potentially obstruct flow through the filter mesh.
  • To further illustrate this point, the following are given as examples of embolic filter assemblies exhibiting the desired range of ratios of the filter surface area to the cross-sectional area of the aortic lumen. These examples are merely illustrative of some of the possible embodiments of the embolic filter assembly and should not be interpreted as limiting in any way to the scope of the present invention. Turning first to FIGS. [0096] 1-3, there is illustrated an embolic filter assembly that is approximately conical in shape. In order to achieve a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 2, a conical filter assembly must have a filter length L of greater than the aortic diameter D. To achieve a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 4, a conical filter assembly must have a filter length L of greater than twice the aortic diameter D. To achieve a ratio of the filter surface area to the cross-sectional area of the aortic lumen of greater than approximately 6, a conical filter assembly must have a filter length L of greater than three times the aortic diameter D. With these ratios of the filter surface area to the cross-sectional area of the aortic lumen, it is possible to achieve a filter mesh surface area of 3-10 in2 or greater in all typical adult human aortas ranging from 2.0 to 4.0 cm in diameter. Greater length to diameter ratios will provide more improved ratios of the filter surface area to the cross-sectional area of the aortic lumen.
  • Turning next to FIGS. [0097] 7-8, 15-17 and 25-27, there are illustrated embolic filter assemblies having an approximately trumpet-shaped geometry that includes an approximately conical upstream section connected to an approximately cylindrical extension with a closed downstream end. This geometry provides an improvement in the ratio of the filter surface area to the cross-sectional area of the aortic lumen of approximately 15 to 50 percent compared with the simple conical geometry. Thus, even greater ratios of the filter surface area to the cross-sectional area of the aortic lumen are readily achieved using this trumpet-shaped geometry. Further improvements of the ratio of the filter surface area to the cross-sectional area of the aortic lumen can be realized with the convoluted embolic filter assemblies illustrated in FIGS. 18-20, 20-23 and 30. With these convoluted geometries, ratios of the filter surface area to the cross-sectional area of the aortic lumen of 2-12 or even greater can be achieved.
  • Each of the embodiments of the invention described herein may be used for administration of standard cardiopulmonary bypass and cardioplegic arrest by combining the aortic filter catheter with a standard aortic crossclamp and a standard arterial perfusion cannula inserted into the ascending aorta between the crossclamp and the embolic filter assembly. Where the aortic filter catheter includes an integral perfusion lumen, the CPB system can be simplified by the eliminating the separate arterial perfusion cannula. The CPB system can be further simplified by incorporating an aortic occlusion device into the aortic filter catheter and eliminating the aortic crossclamp. Such a system would allow percutaneous transluminal administration of cardiopulmonary bypass and cardioplegic arrest with protection from undesirable embolic events. [0098]
  • FIGS. [0099] 46-50 show the operation of an embodiment of a perfusion filter catheter 600 that combines an embolic filter assembly 602 with a toroidal balloon aortic occlusion device 604. The embolic filter assembly 602 and the toroidal balloon aortic occlusion device 604 are mounted on an elongated catheter shaft 606 that may be adapted for peripheral introduction via the femoral artery or subclavian artery or for central insertion directly into the ascending aorta. The toroidal balloon aortic occlusion device 604 is connected to an inflation lumen within the elongated catheter shaft 606. A cardioplegia lumen, which may also serve as a guidewire lumen, connects to a cardioplegia port 608 at the distal end of the catheter shaft 606. A perfusion lumen connects to one or more perfusion ports 610 located on the catheter shaft 606 downstream from the toroidal balloon aortic occlusion device 604, but upstream of the embolic filter assembly 602.
  • FIG. 46 shows the [0100] perfusion filter catheter 600 in the collapsed or undeployed state with the embolic filter assembly 602 and the toroidal balloon aortic occlusion device 604 collapsed or folded about the elongated catheter shaft 606. The perfuision filter catheter 600 is inserted in the collapsed state and advanced into the patient's ascending aorta until the embolic filter assembly 602 is positioned between the coronary ostia and the brachiocephalic artery. The toroidal balloon aortic occlusion device 604 is then inflated to expand and deploy the embolic filter assembly 602, as shown in FIG. 47. The embolic filter assembly 602 may assume a simple conical shape or, more preferably, one of the surface area increasing geometries described above. In addition, the embolic filter assembly 602 may include a structure or other means to hold the filter material apart from the aortic wall to maximize the effective filter area. With the embolic filter assembly 602 deployed, cardiopulmonary bypass with embolic protection can be started through the perfusion ports 610.
  • When it is desired to initiate cardioplegic arrest, the toroidal balloon [0101] aortic occlusion device 604 is further inflated until it expands inward to occlude the aortic lumen, as shown in FIG. 48. A cardioplegic agent is infused through the cardioplegia port 608 and into the coronary arteries to arrest the heart. Oxygenated blood continues to be infused through the perfusion ports 610. After completion of the surgical procedure, the toroidal balloon aortic occlusion device 604 is partially deflated, leaving the embolic filter assembly 602 deployed, as shown in FIG. 49. Oxygenated blood enters the coronary arteries to restart the heart beating. If any embolic materials 612 are dislodged during manipulation of the heart or when the heart resumes beating, they will be captured by the embolic filter assembly 602. Once the patient is weaned off of bypass, the toroidal balloon aortic occlusion device 604 is deflated to collapse the embolic filter assembly 602, as shown in FIG. 50. Any potential emboli are trapped within the embolic filter assembly 602 and can be removed along with the catheter 600.
  • FIG. 51 shows an embodiment of a [0102] perfusion filter catheter 620 that combines an embolic filter assembly 622 with an inflatable balloon aortic occlusion device 624. The embolic filter assembly 622 may be any one of the actively or passively deployed embolic filter assemblies described herein. Preferably, the inflatable balloon aortic occlusion device 624 is an 5 elastomeric balloon of sufficient inflated diameter to occlude the ascending aorta and is mounted on the elongated catheter shaft 626 upstream of the embolic filter assembly 622. Alternatively, the inflatable balloon aortic occlusion device 624 may be positioned to occlude the inlet end of the embolic filter assembly 622 to minimize the area of contact between the perfusion filter catheter 620 and the aortic wall. The inflatable balloon aortic occlusion device 624 is connected to an inflation lumen within the elongated catheter shaft 626. A cardioplegia lumen, which may also serve as a guidewire lumen, connects to a cardioplegia port 628 at the distal end of the catheter shaft 626. A perfusion lumen connects to one or more perfusion ports 630 located on the catheter shaft 626 downstream from the inflatable balloon aortic occlusion device 624, but upstream of the embolic filter assembly 622. The operation of the perfusion filter catheter 620 of FIG. 51 is quite similar to that described for the embodiment of FIGS. 46-50.
  • FIG. 52 shows an embodiment of a perfusion filter catheter [0103] 640 that combines an embolic filter assembly 642 with a selectively deployable external catheter flow control valve 644. The embolic filter assembly 642 may be any one of the actively or passively deployed embolic filter assemblies described herein. The selectively deployable external catheter flow control valve 644 is mounted on the elongated catheter shaft 646 upstream of the embolic filter assembly 642. Alternatively, the selectively deployable external catheter flow control valve 644 may be positioned to occlude the inlet end of the embolic filter assembly 642 to minimize the area of contact between the perfusion filter catheter 640 and the aortic wall. Selectively deployable external catheter flow control valves suitable for this application are described in commonly owned, copending U.S. patent applications Ser. Nos. 08/665,635, 08/664,361 and 08/664,360, filed Jun. 17, 1996, which are hereby incorporated by reference in their entirety. The elongated catheter shaft 646 may include one or more deployment lumens as needed for actuating the external catheter flow control valve 644. A cardioplegia lumen, which may also serve as a guidewire lumen, connects to a cardioplegia port 648 at the distal end of the catheter shaft 646. A perfusion lumen connects to one or more perfusion ports 650 located on the catheter shaft 646 downstream from the external catheter flow control valve 644, but upstream of the embolic filter assembly 622. The operation of the perfusion filter catheter 640 of FIG. 52 is quite similar to that described for the embodiment of FIGS. 46-50.
  • FIG. 53 shows an additional feature of the present invention that may be used in combination with many of the features and embodiments previously described. FIG. 53 shows an embodiment of a [0104] perfusion filter catheter 660 with an embolic filter assembly 662 having areas of different filter porosity. The embolic filter assembly 662 is mounted on an elongated catheter shaft 666 that may be adapted for peripheral introduction via the femoral artery or subclavian artery or for central insertion directly into the ascending aorta. The embolic filter assembly 662 may resemble any one of the actively or passively deployed embolic filter assemblies described herein. Preferably, the embolic filter assembly 662 assumes one of the surface area increasing geometries described above, such as a trumpet-style embolic filter assembly 662 as shown. The embolic filter assembly 662 is divided along a longitudinal dividing line into areas of different filter porosity. In a preferred embodiment, the embolic filter assembly 662 has an upper portion 664 of finer porosity facing toward the aortic arch vessels and a lower portion 668 of courser porosity facing away from the aortic arch vessels. Preferably, the elongated catheter shaft 666 will have a preformed curve to help orient the upper portion 664 and the lower portion 668 of the embolic filter assembly 662 in the proper position once deployed. The filter mesh of the upper portion 664 may be selected to exclude both macroemboli and microemboli, and the filter mesh of the lower portion 668 may be selected to exclude macroemboli only. Alternatively, the upper portion 664 may be impermeable so as to act like a shunt to direct potential emboli downstream away from the aortic arch vessels.
  • Another feature that may be combined with the features and embodiments of the present invention is an aortic transillumination system for locating and monitoring the position of the catheter, the filter and the optional occlusion devices without fluoroscopy by transillumination of the aortic wall. Aortic transillumination systems using optical fibers and/or light emitting diodes or lasers suitable for this application are described in commonly owned, copending U.S. patent application Ser. No. 60/088,652, filed Jun. 9, 1998, which is hereby incorporated by reference in its entirety. By way of example, FIG. 54 shows an embodiment of a [0105] perfusion filter catheter 670 with a fiberoptic system for aortic transillumination. A first optical fiber 684 is positioned near a distal end of the perfusion filter catheter 670, upstream of the embolic filter assembly 672, so that it will emit a first laterally directed beam of light. A second optical fiber 672 is positioned on the outer rim of the filter support structure 674 so that it will emit a second laterally directed beam of light. An optical coupling 682 at the proximal end of the perfusion filter catheter 670 connects the optical fibers 684, 672 to a light source 680 by way of an optical cable 678. The light beams emitted by the optical fibers 684, 672 are visible through the aortic wall and can be used to locate and monitor the position and the deployment state of the perfusion filter catheter 670 and the embolic filter assembly 672. Similarly, in embodiments of the perfusion filter catheter utilizing an aortic occlusion device, one or more optical fibers or other light emitting devices may be positioned on the aortic occlusion device to locate and monitor its position and state of deployment.
  • Likewise, the features and embodiments of the present invention may also be combined with a bumper location device for facilitating catheter insertion and positioning by providing tactile feedback when the catheter device contacts the aortic valve. Bumper location devices suitable for this application are described in commonly owned, copending U.S. patent application Ser. Nos. 60/060,158, filed Sep. 26, 1997, and No. 60/073,681, filed Feb. 4, 1998, which are hereby incorporated by reference in their entirety. [0106]
  • While the present invention has been described herein with respect to the exemplary embodiments and the best mode for practicing the invention, it will be apparent to one of ordinary skill in the art that many modifications, improvements and subcombinations of the various embodiments, adaptations and variations can be made to the invention without departing from the spirit and scope thereof. [0107]

Claims (43)

What is claimed is:
1. An aortic filter catheter comprising:
an elongated catheter shaft,
an embolic filter assembly mounted on said catheter shaft, said embolic filter assembly including a porous filter mesh, said embolic filter assembly being expandable to engage an inner surface of a patient's aorta, and
an aortic occlusion device mounted on said elongated catheter shaft.
2. The aortic filter catheter of claim 1, wherein said aortic occlusion device is mounted on said elongated catheter shaft upstream of said embolic filter assembly.
3. The aortic filter catheter of claim 1, wherein said aortic occlusion device comprises a toroidal balloon occlusion device, said toroidal balloon occlusion device having an uninflated state, a first inflated state in which said toroidal balloon occlusion device engages the inner surface of the aorta and in which said toroidal balloon occlusion device has an open central passage permitting fluid flow therethrough, and a second inflated state in which said central passage of said toroidal balloon occlusion device closes preventing fluid flow therethrough.
4. The aortic filter catheter of claim 1, wherein said aortic occlusion device comprises an inflatable balloon expandable to occlude the aortic lumen.
5. The aortic filter catheter of claim 4, wherein said inflatable balloon is mounted on said elongated catheter shaft upstream of said embolic filter assembly.
6. The aortic filter catheter of claim 1, wherein said aortic occlusion device comprises an external catheter flow control valve expandable to occlude the aortic lumen.
7. The aortic filter catheter of claim 6, wherein said external catheter flow control valve is mounted on said elongated catheter shaft upstream of said embolic filter assembly.
8. The aortic filter catheter of claim 1, wherein said embolic filter assembly is configured to expand passively in response to blood flow in the aorta.
9. The aortic filter catheter of claim 1, wherein said embolic filter assembly is resiliently biased toward the expanded state.
10. The aortic filter catheter of claim 1, further comprising a perfusion lumen within said elongated catheter shaft, said perfusion lumen being fluidly connected to a perfusion port located on said elongated catheter shaft upstream of said filter mesh and downstream of said aortic occlusion device.
11. The aortic filter catheter of claim 10, further comprising a distal lumen within said elongated catheter shaft, said distal lumen being fluidly connected to a distal port on said elongated catheter shaft upstream of said aortic occlusion device.
12. The aortic filter catheter of claim 1, wherein said embolic filter assembly is configured with a conical upstream section and an approximately cylindrical extension extending downstream of said conical upstream section.
13. The aortic filter catheter of claim 1, wherein said embolic filter assembly includes a means to actively expand said embolic filter assembly within the aorta.
14. The aortic filter catheter of claim 13, wherein said means to actively expand said embolic filter assembly comprises a plurality of actuation members connected to an outer periphery of said embolic filter assembly.
15. The aortic filter catheter of claim 14, wherein said actuation members comprise a plurality of actuation wires slidably received within at least one actuation wire lumen within said elongated catheter shaft, said actuation wires having distal ends connected to the outer periphery of said embolic filter assembly.
16. The aortic filter catheter of claim 13, wherein said means to actively expand said embolic filter assembly comprises an extendable and retractable support wire circumscribing an outer periphery of said embolic filter assembly.
17. The aortic filter catheter of claim 16, wherein said support wire has a distal end advanceable and retractable through a channel circumscribing said outer periphery of said embolic filter assembly.
18. The aortic filter catheter of claim 16, wherein said support wire forms an expandable and retractable loop circumscribing said outer periphery of said embolic filter assembly.
19. The aortic filter catheter of claim 16, wherein said elongated catheter shaft is approximately tangential to said outer periphery of said embolic filter assembly when said embolic filter assembly is in an expanded state.
20. The aortic filter catheter of claim 1, wherein said embolic filter assembly has an outer periphery and said elongated catheter shaft is approximately tangential to said outer periphery of said embolic filter assembly when said embolic filter assembly is in an expanded state.
21. The aortic filter catheter of claim 20, wherein said elongated catheter shaft has a distal end that is curved toward a center of an inlet end of said embolic filter assembly.
22. The aortic filter catheter of claim 1, further comprising a light emitting means for directing a beam of light through a wall of the aorta.
23. The aortic filter catheter of claim 22, wherein said light emitting means is positioned on an outer periphery of said embolic filter assembly.
24. The aortic filter catheter of claim 1, wherein said embolic filter assembly comprises a first portion of porous filter mesh having a first porosity and a second portion of porous filter mesh having a second porosity different from said first porosity.
25. The aortic filter catheter of claim 24, wherein said first portion of porous filter mesh is an upstream portion of the porous filter mesh and said second portion of porous filter mesh is a downstream portion of the porous filter mesh.
26. The aortic filter catheter of claim 24, wherein said first portion of porous filter mesh is separated from said second portion of porous filter mesh along a longitudinally oriented dividing line.
27. The aortic filter catheter of claim 1, wherein said filter mesh has a convoluted configuration when said embolic filter assembly is in the expanded state.
28. The aortic filter catheter of claim 27, wherein said filter mesh has a circumferentially convoluted configuration.
29. The aortic filter catheter of claim 27, wherein said filter mesh has a longitudinally convoluted configuration.
30. The aortic filter catheter of claim 27, wherein said filter mesh has a helically convoluted configuration.
31. An aortic filter catheter comprising:
an elongated catheter shaft,
an embolic filter assembly having a porous filter mesh mounted on said catheter shaft, said embolic filter assembly being expandable to engage an inner surface of a patient's aorta, said embolic filter assembly having an inlet end that is open to fluid flow when said embolic filter assembly is in an expanded state, and
a toroidal balloon occlusion device mounted at said inlet end of said embolic filter assembly, said toroidal balloon occlusion device having an uninflated state, a first inflated state in which said toroidal balloon occlusion device engages the inner surface of the aorta and in which said toroidal balloon occlusion device has an open central passage permitting fluid flow therethrough, and a second inflated state in which said central passage of said toroidal balloon occlusion device closes preventing fluid flow therethrough.
32. The aortic filter catheter of claim 31, wherein said elongated catheter shaft is approximately tangential to said inlet end of said embolic filter assembly when said embolic filter assembly is in the expanded state.
33. The aortic filter catheter of claim 31, wherein said inlet end of said embolic filter assembly is connected to said elongated catheter shaft by a plurality of struts.
34. The aortic filter catheter of claim 31, further comprising a perfusion lumen within said elongated catheter shaft, said perfusion lumen being fluidly connected to a perfusion port located on said elongated catheter shaft upstream of said filter mesh and downstream of said toroidal balloon occlusion device.
35. The aortic filter catheter of claim 34, further comprising a distal lumen within said elongated catheter shaft, said distal lumen being fluidly connected to a distal port on said elongated catheter shaft upstream of said toroidal balloon occlusion device.
36. A method comprising:
introducing an elongated tubular shaft of an aortic filter catheter into a patient's aorta;
positioning an embolic filter assembly having a porous filter mesh mounted on said elongated tubular shaft within the patient's ascending aorta;
expanding said embolic filter assembly to engage an inner surface of the patient's ascending aorta; and
occluding the patient's ascending aorta with an aortic occlusion device mounted on said elongated tubular shaft.
37. The method of claim 36, wherein said aortic occlusion device is mounted on said elongated catheter shaft upstream of said embolic filter assembly.
38. The method of claim 36, further comprising perfusing oxygenated blood through a perfusion lumen within said elongated tubular shaft into the patient's aorta.
39. The method of claim 36, further comprising perfusing oxygenated blood through a perfusion lumen within said elongated tubular shaft into the patient's aorta upstream of said porous filter mesh and downstream of said aortic occlusion device.
40. The method of claim 36, further comprising introducing a cardioplegic agent into the patient's coronary arteries to induce cardioplegic arrest by infusing the cardioplegic agent into the patient's aorta upstream of said aortic occlusion device.
41. The method of claim 36, further comprising monitoring the position and deployment state of said aortic filter catheter by directing a beam of light from said aortic filter catheter through a wall of the patient's aorta and observing the transmitted light beam external to the aorta.
42. The method of claim 36, wherein said aortic occlusion device comprises an inflatable balloon expandable to occlude the aortic lumen.
43. The method of claim 36, wherein said aortic occlusion device comprises an external catheter flow control valve expandable to occlude the aortic lumen.
US10/108,245 1997-09-26 2002-03-26 Aortic filter catheter Abandoned US20020161394A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US10/108,245 US20020161394A1 (en) 1997-09-26 2002-03-26 Aortic filter catheter

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US6011797P 1997-09-26 1997-09-26
US09/158,405 US6361545B1 (en) 1997-09-26 1998-09-22 Perfusion filter catheter
US10/108,245 US20020161394A1 (en) 1997-09-26 2002-03-26 Aortic filter catheter

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US09/158,405 Division US6361545B1 (en) 1997-09-26 1998-09-22 Perfusion filter catheter

Publications (1)

Publication Number Publication Date
US20020161394A1 true US20020161394A1 (en) 2002-10-31

Family

ID=22027475

Family Applications (2)

Application Number Title Priority Date Filing Date
US09/158,405 Expired - Lifetime US6361545B1 (en) 1997-09-26 1998-09-22 Perfusion filter catheter
US10/108,245 Abandoned US20020161394A1 (en) 1997-09-26 2002-03-26 Aortic filter catheter

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US09/158,405 Expired - Lifetime US6361545B1 (en) 1997-09-26 1998-09-22 Perfusion filter catheter

Country Status (5)

Country Link
US (2) US6361545B1 (en)
EP (1) EP1017333A2 (en)
AU (1) AU749573B2 (en)
CA (1) CA2304463A1 (en)
WO (1) WO1999016382A2 (en)

Cited By (276)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030050685A1 (en) * 1999-08-09 2003-03-13 Nikolic Serjan D. Method for improving cardiac function
US20050015109A1 (en) * 2003-07-16 2005-01-20 Samuel Lichtenstein Methods and devices for altering blood flow through the left ventricle
EP1527740A1 (en) * 2003-10-29 2005-05-04 Medtronic Vascular, Inc. Distal protection device for filtering and occlusion
US20050119688A1 (en) * 2003-10-06 2005-06-02 Bjarne Bergheim Method and assembly for distal embolic protection
US20050143810A1 (en) * 2003-10-24 2005-06-30 Martin Dauner Cardiovascular implant, method and device for its production, and its provision for surgery
US20050240200A1 (en) * 2004-04-23 2005-10-27 Bjarne Bergheim Method and system for cardiac valve delivery
US20060020285A1 (en) * 2004-07-22 2006-01-26 Volker Niermann Method for filtering blood in a vessel with helical elements
US20060020286A1 (en) * 2004-07-22 2006-01-26 Volker Niermann Device for filtering blood in a vessel with helical elements
US20060036310A1 (en) * 2004-08-13 2006-02-16 Scimed Life Systems, Inc. Method to simultaneously load and cover self expanding stents
US20060241735A1 (en) * 2005-04-26 2006-10-26 Cardiac Pacemakers, Inc. Self-deploying vascular occlusion device
US20060253023A1 (en) * 2005-04-20 2006-11-09 Scimed Life Systems, Inc. Neurovascular intervention device
US7220271B2 (en) 2003-01-30 2007-05-22 Ev3 Inc. Embolic filters having multiple layers and controlled pore size
US20070135834A1 (en) * 2003-01-30 2007-06-14 Ev3 Inc. Embolic filters with controlled pore size
US20080065145A1 (en) * 2006-09-11 2008-03-13 Carpenter Judith T Embolic protection device and method of use
US20080275485A1 (en) * 2006-04-03 2008-11-06 Possis Medical, Inc. Guidewire with collapsible filter system and method of use
US20090248060A1 (en) * 2008-03-19 2009-10-01 Schneider M Bret Electrostatic vascular filters
US7618433B2 (en) * 1999-02-24 2009-11-17 Boston Scientific Scimed, Inc. Intravascular filter and method
US7621870B2 (en) 2002-03-12 2009-11-24 Ev3 Inc. Everted filter device
US20090326669A1 (en) * 2006-08-04 2009-12-31 Roman Preuss Insertion of vibration-damping elements in prosthetic systems for the manipulation and damping of natural frequencies
US20100030321A1 (en) * 2008-07-29 2010-02-04 Aga Medical Corporation Medical device including corrugated braid and associated method
US7674222B2 (en) 1999-08-09 2010-03-09 Cardiokinetix, Inc. Cardiac device and methods of use thereof
US7682390B2 (en) 2001-07-31 2010-03-23 Medtronic, Inc. Assembly for setting a valve prosthesis in a corporeal duct
US7712606B2 (en) 2005-09-13 2010-05-11 Sadra Medical, Inc. Two-part package for medical implant
US7740655B2 (en) 2006-04-06 2010-06-22 Medtronic Vascular, Inc. Reinforced surgical conduit for implantation of a stented valve therein
US7749249B2 (en) 2006-02-21 2010-07-06 Kardium Inc. Method and device for closing holes in tissue
US7748389B2 (en) 2003-12-23 2010-07-06 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US20100179585A1 (en) * 2006-09-11 2010-07-15 Carpenter Judith T Embolic deflection device
US20100179647A1 (en) * 2006-09-11 2010-07-15 Carpenter Judith T Methods of reducing embolism to cerebral circulation as a consequence of an index cardiac procedure
US20100179583A1 (en) * 2006-09-11 2010-07-15 Carpenter Judith T Methods of deploying and retrieving an embolic diversion device
US7758606B2 (en) 2000-06-30 2010-07-20 Medtronic, Inc. Intravascular filter with debris entrapment mechanism
US7762943B2 (en) * 2004-03-03 2010-07-27 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US7766934B2 (en) 2005-07-12 2010-08-03 Cook Incorporated Embolic protection device with an integral basket and bag
US7771452B2 (en) 2005-07-12 2010-08-10 Cook Incorporated Embolic protection device with a filter bag that disengages from a basket
US7780725B2 (en) 2004-06-16 2010-08-24 Sadra Medical, Inc. Everting heart valve
US7780726B2 (en) 2001-07-04 2010-08-24 Medtronic, Inc. Assembly for placing a prosthetic valve in a duct in the body
US7824443B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Medical implant delivery and deployment tool
US7824442B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US7837610B2 (en) 2006-08-02 2010-11-23 Kardium Inc. System for improving diastolic dysfunction
US7850708B2 (en) 2005-06-20 2010-12-14 Cook Incorporated Embolic protection device having a reticulated body with staggered struts
US7862500B2 (en) 2002-08-01 2011-01-04 Cardiokinetix, Inc. Multiple partitioning devices for heart treatment
US7871436B2 (en) 2007-02-16 2011-01-18 Medtronic, Inc. Replacement prosthetic heart valves and methods of implantation
US7887477B2 (en) 1999-08-09 2011-02-15 Cardiokinetix, Inc. Method of improving cardiac function using a porous membrane
US7892281B2 (en) 1999-11-17 2011-02-22 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US7897086B2 (en) 2004-08-05 2011-03-01 Cardiokinetix, Inc. Method of making a laminar ventricular partitioning device
US7914569B2 (en) 2005-05-13 2011-03-29 Medtronics Corevalve Llc Heart valve prosthesis and methods of manufacture and use
US20110130657A1 (en) * 2009-12-02 2011-06-02 Chomas James E Protection Device and Method Against Embolization Agent Reflux
US7955351B2 (en) 2005-02-18 2011-06-07 Tyco Healthcare Group Lp Rapid exchange catheters and embolic protection devices
WO2011068924A1 (en) * 2009-12-02 2011-06-09 Surefire Medical, Inc. Microvalve protection device and method of use for protection against embolization agent reflux
US7959672B2 (en) 2003-12-23 2011-06-14 Sadra Medical Replacement valve and anchor
US7959666B2 (en) 2003-12-23 2011-06-14 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US7972378B2 (en) 2008-01-24 2011-07-05 Medtronic, Inc. Stents for prosthetic heart valves
US7988724B2 (en) 2003-12-23 2011-08-02 Sadra Medical, Inc. Systems and methods for delivering a medical implant
US8016877B2 (en) 1999-11-17 2011-09-13 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8048153B2 (en) 2003-12-23 2011-11-01 Sadra Medical, Inc. Low profile heart valve and delivery system
US8052749B2 (en) 2003-12-23 2011-11-08 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8052750B2 (en) 2006-09-19 2011-11-08 Medtronic Ventor Technologies Ltd Valve prosthesis fixation techniques using sandwiching
US20110288529A1 (en) * 2010-05-19 2011-11-24 Fulton Richard E Augmented delivery catheter and method
US8070801B2 (en) 2001-06-29 2011-12-06 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US8075615B2 (en) 2006-03-28 2011-12-13 Medtronic, Inc. Prosthetic cardiac valve formed from pericardium material and methods of making same
US8109962B2 (en) 2005-06-20 2012-02-07 Cook Medical Technologies Llc Retrievable device having a reticulation portion with staggered struts
US8109996B2 (en) 2004-03-03 2012-02-07 Sorin Biomedica Cardio, S.R.L. Minimally-invasive cardiac-valve prosthesis
US20120046740A1 (en) * 2004-11-05 2012-02-23 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US20120046683A1 (en) * 2008-10-31 2012-02-23 Scott Wilson Devices and methods for temporarily opening a blood vessel
US8137398B2 (en) 2008-10-13 2012-03-20 Medtronic Ventor Technologies Ltd Prosthetic valve having tapered tip when compressed for delivery
US8152831B2 (en) 2005-11-17 2012-04-10 Cook Medical Technologies Llc Foam embolic protection device
US8157853B2 (en) 2008-01-24 2012-04-17 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US20120095500A1 (en) * 2010-10-14 2012-04-19 Heuser Richard R Concentric wire embolism protection device
US8182508B2 (en) 2005-10-04 2012-05-22 Cook Medical Technologies Llc Embolic protection device
US8187298B2 (en) 2005-08-04 2012-05-29 Cook Medical Technologies Llc Embolic protection device having inflatable frame
US8192478B2 (en) 1999-08-09 2012-06-05 Cardiokinetix, Inc. System for improving cardiac function
US8216269B2 (en) 2005-11-02 2012-07-10 Cook Medical Technologies Llc Embolic protection device having reduced profile
WO2012094195A1 (en) * 2011-01-07 2012-07-12 Merhi William M Angiography catheter
US8221446B2 (en) 2005-03-15 2012-07-17 Cook Medical Technologies Embolic protection device
US8231670B2 (en) 2003-12-23 2012-07-31 Sadra Medical, Inc. Repositionable heart valve and method
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US8246671B2 (en) 1999-08-09 2012-08-21 Cardiokinetix, Inc. Retrievable cardiac devices
US8246678B2 (en) 2003-12-23 2012-08-21 Sadra Medicl, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US8252052B2 (en) 2003-12-23 2012-08-28 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US8252018B2 (en) 2007-09-14 2012-08-28 Cook Medical Technologies Llc Helical embolic protection device
US8252017B2 (en) 2005-10-18 2012-08-28 Cook Medical Technologies Llc Invertible filter for embolic protection
US8287584B2 (en) 2005-11-14 2012-10-16 Sadra Medical, Inc. Medical implant deployment tool
US8313525B2 (en) 2008-03-18 2012-11-20 Medtronic Ventor Technologies, Ltd. Valve suturing and implantation procedures
US8312825B2 (en) 2008-04-23 2012-11-20 Medtronic, Inc. Methods and apparatuses for assembly of a pericardial prosthetic heart valve
US8343213B2 (en) 2003-12-23 2013-01-01 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US8377114B2 (en) 1999-08-09 2013-02-19 Cardiokinetix, Inc. Sealing and filling ventricular partitioning devices to improve cardiac function
US8377092B2 (en) 2005-09-16 2013-02-19 Cook Medical Technologies Llc Embolic protection device
US8388644B2 (en) 2008-12-29 2013-03-05 Cook Medical Technologies Llc Embolic protection device and method of use
US8398537B2 (en) 2005-06-10 2013-03-19 Cardiokinetix, Inc. Peripheral seal for a ventricular partitioning device
US8419748B2 (en) 2007-09-14 2013-04-16 Cook Medical Technologies Llc Helical thrombus removal device
US8430927B2 (en) 2008-04-08 2013-04-30 Medtronic, Inc. Multiple orifice implantable heart valve and methods of implantation
CN103079497A (en) * 2010-06-30 2013-05-01 玛芬股份有限公司 Percutaneous, ultrasound-guided introduction of medical devices
US8449605B2 (en) 2006-06-28 2013-05-28 Kardium Inc. Method for anchoring a mitral valve
US8506620B2 (en) 2005-09-26 2013-08-13 Medtronic, Inc. Prosthetic cardiac and venous valves
US8512397B2 (en) 2009-04-27 2013-08-20 Sorin Group Italia S.R.L. Prosthetic vascular conduit
US8529430B2 (en) 2002-08-01 2013-09-10 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US8539662B2 (en) 2005-02-10 2013-09-24 Sorin Group Italia S.R.L. Cardiac-valve prosthesis
US8545418B2 (en) 2004-08-25 2013-10-01 Richard R. Heuser Systems and methods for ablation of occlusions within blood vessels
US8562672B2 (en) 2004-11-19 2013-10-22 Medtronic, Inc. Apparatus for treatment of cardiac valves and method of its manufacture
US8579962B2 (en) 2003-12-23 2013-11-12 Sadra Medical, Inc. Methods and apparatus for performing valvuloplasty
US8579966B2 (en) 1999-11-17 2013-11-12 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8591570B2 (en) 2004-09-07 2013-11-26 Medtronic, Inc. Prosthetic heart valve for replacing previously implanted heart valve
US8603160B2 (en) 2003-12-23 2013-12-10 Sadra Medical, Inc. Method of using a retrievable heart valve anchor with a sheath
US8613765B2 (en) 2008-02-28 2013-12-24 Medtronic, Inc. Prosthetic heart valve systems
US8623077B2 (en) 2001-06-29 2014-01-07 Medtronic, Inc. Apparatus for replacing a cardiac valve
US8628566B2 (en) 2008-01-24 2014-01-14 Medtronic, Inc. Stents for prosthetic heart valves
US8632562B2 (en) 2005-10-03 2014-01-21 Cook Medical Technologies Llc Embolic protection device
US8652204B2 (en) 2010-04-01 2014-02-18 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US8685084B2 (en) 2011-12-29 2014-04-01 Sorin Group Italia S.R.L. Prosthetic vascular conduit and assembly method
US8696743B2 (en) 2008-04-23 2014-04-15 Medtronic, Inc. Tissue attachment devices and methods for prosthetic heart valves
US8721714B2 (en) 2008-09-17 2014-05-13 Medtronic Corevalve Llc Delivery system for deployment of medical devices
US8728155B2 (en) 2011-03-21 2014-05-20 Cephea Valve Technologies, Inc. Disk-based valve apparatus and method for the treatment of valve dysfunction
US8747458B2 (en) 2007-08-20 2014-06-10 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
US8747459B2 (en) 2006-12-06 2014-06-10 Medtronic Corevalve Llc System and method for transapical delivery of an annulus anchored self-expanding valve
US8771302B2 (en) 2001-06-29 2014-07-08 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US8784478B2 (en) 2006-10-16 2014-07-22 Medtronic Corevalve, Inc. Transapical delivery system with ventruculo-arterial overlfow bypass
US8790242B2 (en) 2009-10-26 2014-07-29 Cardiokinetix, Inc. Ventricular volume reduction
US20140214072A1 (en) * 2013-01-29 2014-07-31 St. Jude Medical, Cardiology Division, Inc. Aortic great vessel protection
US8795315B2 (en) 2004-10-06 2014-08-05 Cook Medical Technologies Llc Emboli capturing device having a coil and method for capturing emboli
US8808369B2 (en) 2009-10-05 2014-08-19 Mayo Foundation For Medical Education And Research Minimally invasive aortic valve replacement
US20140257362A1 (en) * 2013-03-07 2014-09-11 St. Jude Medical, Cardiology Division, Inc. Filtering and removing particulates from bloodstream
US8834564B2 (en) 2006-09-19 2014-09-16 Medtronic, Inc. Sinus-engaging valve fixation member
US8834563B2 (en) 2008-12-23 2014-09-16 Sorin Group Italia S.R.L. Expandable prosthetic valve having anchoring appendages
US8840661B2 (en) 2008-05-16 2014-09-23 Sorin Group Italia S.R.L. Atraumatic prosthetic heart valve prosthesis
US8840663B2 (en) 2003-12-23 2014-09-23 Sadra Medical, Inc. Repositionable heart valve method
US8858619B2 (en) 2002-04-23 2014-10-14 Medtronic, Inc. System and method for implanting a replacement valve
US8870948B1 (en) 2013-07-17 2014-10-28 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US8876796B2 (en) 2010-12-30 2014-11-04 Claret Medical, Inc. Method of accessing the left common carotid artery
US8940002B2 (en) 2010-09-30 2015-01-27 Kardium Inc. Tissue anchor system
US8940014B2 (en) 2011-11-15 2015-01-27 Boston Scientific Scimed, Inc. Bond between components of a medical device
US8945169B2 (en) 2005-03-15 2015-02-03 Cook Medical Technologies Llc Embolic protection device
US8951243B2 (en) 2011-12-03 2015-02-10 Boston Scientific Scimed, Inc. Medical device handle
US8951280B2 (en) 2000-11-09 2015-02-10 Medtronic, Inc. Cardiac valve procedure methods and devices
US8974489B2 (en) 2009-07-27 2015-03-10 Claret Medical, Inc. Dual endovascular filter and methods of use
US8986361B2 (en) 2008-10-17 2015-03-24 Medtronic Corevalve, Inc. Delivery system for deployment of medical devices
US8998976B2 (en) 2011-07-12 2015-04-07 Boston Scientific Scimed, Inc. Coupling system for medical devices
US8998981B2 (en) 2008-09-15 2015-04-07 Medtronic, Inc. Prosthetic heart valve having identifiers for aiding in radiographic positioning
US9005273B2 (en) 2003-12-23 2015-04-14 Sadra Medical, Inc. Assessing the location and performance of replacement heart valves
US9011521B2 (en) 2003-12-23 2015-04-21 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US9011478B2 (en) 2003-01-30 2015-04-21 Covidien Lp Embolic filters with a distal loop or no loop
US9050066B2 (en) 2010-06-07 2015-06-09 Kardium Inc. Closing openings in anatomical tissue
US9072511B2 (en) 2011-03-25 2015-07-07 Kardium Inc. Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve
US9078660B2 (en) 2000-08-09 2015-07-14 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US9078781B2 (en) 2006-01-11 2015-07-14 Medtronic, Inc. Sterile cover for compressible stents used in percutaneous device delivery systems
US9089422B2 (en) 2008-01-24 2015-07-28 Medtronic, Inc. Markers for prosthetic heart valves
US9089341B2 (en) 2012-02-28 2015-07-28 Surefire Medical, Inc. Renal nerve neuromodulation device
US9089668B2 (en) 2011-09-28 2015-07-28 Surefire Medical, Inc. Flow directional infusion device
US9131926B2 (en) 2011-11-10 2015-09-15 Boston Scientific Scimed, Inc. Direct connect flush system
US9138307B2 (en) 2007-09-14 2015-09-22 Cook Medical Technologies Llc Expandable device for treatment of a stricture in a body vessel
US9149358B2 (en) 2008-01-24 2015-10-06 Medtronic, Inc. Delivery systems for prosthetic heart valves
US9161836B2 (en) 2011-02-14 2015-10-20 Sorin Group Italia S.R.L. Sutureless anchoring device for cardiac valve prostheses
US20150297250A1 (en) * 2014-04-16 2015-10-22 Covidien Lp Systems and methods for catheter advancement
US20150305850A1 (en) * 2012-12-21 2015-10-29 The Regents Of The University Of California In Vivo Positionable Filtration Devices and Methods Related Thereto
US9204964B2 (en) 2009-10-01 2015-12-08 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US9226826B2 (en) 2010-02-24 2016-01-05 Medtronic, Inc. Transcatheter valve structure and methods for valve delivery
US9237886B2 (en) 2007-04-20 2016-01-19 Medtronic, Inc. Implant for treatment of a heart valve, in particular a mitral valve, material including such an implant, and material for insertion thereof
US9248017B2 (en) 2010-05-21 2016-02-02 Sorin Group Italia S.R.L. Support device for valve prostheses and corresponding kit
US9277993B2 (en) 2011-12-20 2016-03-08 Boston Scientific Scimed, Inc. Medical device delivery systems
US9289289B2 (en) 2011-02-14 2016-03-22 Sorin Group Italia S.R.L. Sutureless anchoring device for cardiac valve prostheses
US20160100928A1 (en) * 2013-05-14 2016-04-14 Transverse Medical, Inc. Catheter-based apparatuses and methods
US9326843B2 (en) 2009-01-16 2016-05-03 Claret Medical, Inc. Intravascular blood filters and methods of use
US9332992B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Method for making a laminar ventricular partitioning device
US9332993B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US9393115B2 (en) 2008-01-24 2016-07-19 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US9415225B2 (en) 2005-04-25 2016-08-16 Cardiac Pacemakers, Inc. Method and apparatus for pacing during revascularization
US9439757B2 (en) 2014-12-09 2016-09-13 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US9480548B2 (en) 2006-09-11 2016-11-01 Edwards Lifesciences Ag Embolic protection device and method of use
CN106102654A (en) * 2014-01-10 2016-11-09 企斯动哈特有限公司 Dissect independent deflector
US9510945B2 (en) 2011-12-20 2016-12-06 Boston Scientific Scimed Inc. Medical device handle
US9526609B2 (en) 2003-12-23 2016-12-27 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US9539081B2 (en) 2009-12-02 2017-01-10 Surefire Medical, Inc. Method of operating a microvalve protection device
US9539088B2 (en) 2001-09-07 2017-01-10 Medtronic, Inc. Fixation band for affixing a prosthetic heart valve to tissue
US9566144B2 (en) 2015-04-22 2017-02-14 Claret Medical, Inc. Vascular filters, deflectors, and methods
US9579194B2 (en) 2003-10-06 2017-02-28 Medtronic ATS Medical, Inc. Anchoring structure with concave landing zone
WO2017062036A1 (en) * 2015-10-09 2017-04-13 Transverse Medical, Inc. Catheter-based apparatuses and methods
US9629718B2 (en) 2013-05-03 2017-04-25 Medtronic, Inc. Valve delivery tool
US9636205B2 (en) 2009-01-16 2017-05-02 Claret Medical, Inc. Intravascular blood filters and methods of use
US9694121B2 (en) 1999-08-09 2017-07-04 Cardiokinetix, Inc. Systems and methods for improving cardiac function
US9744038B2 (en) 2008-05-13 2017-08-29 Kardium Inc. Medical device for constricting tissue or a bodily orifice, for example a mitral valve
US9770319B2 (en) 2010-12-01 2017-09-26 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
US9775704B2 (en) 2004-04-23 2017-10-03 Medtronic3F Therapeutics, Inc. Implantable valve prosthesis
US9788942B2 (en) 2015-02-03 2017-10-17 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
US20170325938A1 (en) 2016-05-16 2017-11-16 Boston Scientific Scimed, Inc. Replacement heart valve implant with invertible leaflets
US9848981B2 (en) 2007-10-12 2017-12-26 Mayo Foundation For Medical Education And Research Expandable valve prosthesis with sealing mechanism
US9861477B2 (en) 2015-01-26 2018-01-09 Boston Scientific Scimed Inc. Prosthetic heart valve square leaflet-leaflet stitch
US9889031B1 (en) 2014-03-25 2018-02-13 Surefire Medical, Inc. Method of gastric artery embolization
US9888994B2 (en) 2012-05-15 2018-02-13 Transverse Medical, Inc. Catheter-based apparatuses and methods
US20180049726A1 (en) * 2015-02-02 2018-02-22 Centre National De La Recherche Scientifique Microdevice for the In Vivo Capture of Circulating Cellular Biomarkers
US9901434B2 (en) 2007-02-27 2018-02-27 Cook Medical Technologies Llc Embolic protection device including a Z-stent waist band
US9901445B2 (en) 2014-11-21 2018-02-27 Boston Scientific Scimed, Inc. Valve locking mechanism
US9907639B2 (en) 2006-09-19 2018-03-06 Cook Medical Technologies Llc Apparatus and methods for in situ embolic protection
US9918833B2 (en) 2010-09-01 2018-03-20 Medtronic Vascular Galway Prosthetic valve support structure
US9968740B2 (en) 2014-03-25 2018-05-15 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
EP3323360A1 (en) * 2016-11-21 2018-05-23 Cook Medical Technologies LLC Implantable medical device with atraumatic tip
WO2018102651A1 (en) * 2016-12-01 2018-06-07 Mayo Foundation For Medical Education And Research Percutaneously-deployable intravascular embolic protection devices and methods
US10064696B2 (en) 2000-08-09 2018-09-04 Edwards Lifesciences Corporation Devices and methods for delivering an endocardial device
WO2018136724A3 (en) * 2017-01-20 2018-09-13 W. L. Gore & Associates, Inc. Embolic filter system
US10080652B2 (en) 2015-03-13 2018-09-25 Boston Scientific Scimed, Inc. Prosthetic heart valve having an improved tubular seal
WO2018187413A1 (en) * 2017-04-05 2018-10-11 Boston Scientific Scimed, Inc. Emboli-capturing centering device
US10136991B2 (en) 2015-08-12 2018-11-27 Boston Scientific Scimed Inc. Replacement heart valve implant
US10143552B2 (en) 2015-05-14 2018-12-04 Cephea Valve Technologies, Inc. Replacement mitral valves
US10172708B2 (en) 2012-01-25 2019-01-08 Boston Scientific Scimed, Inc. Valve assembly with a bioabsorbable gasket and a replaceable valve implant
US10179041B2 (en) 2015-08-12 2019-01-15 Boston Scientific Scimed Icn. Pinless release mechanism
US10195392B2 (en) 2015-07-02 2019-02-05 Boston Scientific Scimed, Inc. Clip-on catheter
US10201417B2 (en) 2015-02-03 2019-02-12 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
US10201418B2 (en) 2010-09-10 2019-02-12 Symetis, SA Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device
US10245136B2 (en) 2016-05-13 2019-04-02 Boston Scientific Scimed Inc. Containment vessel with implant sheathing guide
US10258465B2 (en) 2003-12-23 2019-04-16 Boston Scientific Scimed Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US10278805B2 (en) 2000-08-18 2019-05-07 Atritech, Inc. Expandable implant devices for filtering blood flow from atrial appendages
US10285809B2 (en) 2015-03-06 2019-05-14 Boston Scientific Scimed Inc. TAVI anchoring assist device
US10299922B2 (en) 2005-12-22 2019-05-28 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
US10307147B2 (en) 1999-08-09 2019-06-04 Edwards Lifesciences Corporation System for improving cardiac function by sealing a partitioning membrane within a ventricle
US10335277B2 (en) 2015-07-02 2019-07-02 Boston Scientific Scimed Inc. Adjustable nosecone
US10335577B2 (en) 2010-05-19 2019-07-02 Nfinium Vascular Technologies, Llc Augmented delivery catheter and method
US10342660B2 (en) 2016-02-02 2019-07-09 Boston Scientific Inc. Tensioned sheathing aids
US10368990B2 (en) 2017-01-23 2019-08-06 Cephea Valve Technologies, Inc. Replacement mitral valves
US10426617B2 (en) 2015-03-06 2019-10-01 Boston Scientific Scimed, Inc. Low profile valve locking mechanism and commissure assembly
US10449043B2 (en) 2015-01-16 2019-10-22 Boston Scientific Scimed, Inc. Displacement based lock and release mechanism
CN110392556A (en) * 2017-03-13 2019-10-29 东丽株式会社 Filter means
US10470881B2 (en) 2015-05-14 2019-11-12 Cephea Valve Technologies, Inc. Replacement mitral valves
US10485976B2 (en) 1998-04-30 2019-11-26 Medtronic, Inc. Intracardiovascular access (ICVA™) system
US10555809B2 (en) 2012-06-19 2020-02-11 Boston Scientific Scimed, Inc. Replacement heart valve
US10583005B2 (en) 2016-05-13 2020-03-10 Boston Scientific Scimed, Inc. Medical device handle
US10588636B2 (en) * 2017-03-20 2020-03-17 Surefire Medical, Inc. Dynamic reconfigurable microvalve protection device
EP3632374A1 (en) 2018-10-04 2020-04-08 Universitätsspital Basel Protective device for open heart aortic valve replacement surgery and kit comprising the same
US20200163685A1 (en) * 2017-03-27 2020-05-28 Transverse Medical, Inc. Filter apparatuses and methods
US10743977B2 (en) 2009-01-16 2020-08-18 Boston Scientific Scimed, Inc. Intravascular blood filter
US10751183B2 (en) 2014-09-28 2020-08-25 Edwards Lifesciences Corporation Apparatuses for treating cardiac dysfunction
US10779940B2 (en) 2015-09-03 2020-09-22 Boston Scientific Scimed, Inc. Medical device handle
US10780250B1 (en) 2016-09-19 2020-09-22 Surefire Medical, Inc. System and method for selective pressure-controlled therapeutic delivery
US10828154B2 (en) 2017-06-08 2020-11-10 Boston Scientific Scimed, Inc. Heart valve implant commissure support structure
US10849746B2 (en) 2015-05-14 2020-12-01 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
WO2020242545A1 (en) 2017-12-28 2020-12-03 Groh Mark Embolic protection catheter and related devices and methods
US10856970B2 (en) 2007-10-10 2020-12-08 Medtronic Ventor Technologies Ltd. Prosthetic heart valve for transfemoral delivery
US10898330B2 (en) 2017-03-28 2021-01-26 Edwards Lifesciences Corporation Positioning, deploying, and retrieving implantable devices
US10898325B2 (en) 2017-08-01 2021-01-26 Boston Scientific Scimed, Inc. Medical implant locking mechanism
US10939996B2 (en) 2017-08-16 2021-03-09 Boston Scientific Scimed, Inc. Replacement heart valve commissure assembly
US10993805B2 (en) 2008-02-26 2021-05-04 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US11065138B2 (en) 2016-05-13 2021-07-20 Jenavalve Technology, Inc. Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system
US11071844B2 (en) 2018-03-07 2021-07-27 Innovative Cardiovascular Solutions, Llc Embolic protection device
US11090460B2 (en) 2015-03-31 2021-08-17 Surefire Medical, Inc. Method for infusing an immunotherapy agent to a solid tumor for treatment
US11147668B2 (en) 2018-02-07 2021-10-19 Boston Scientific Scimed, Inc. Medical device delivery system with alignment feature
US11154390B2 (en) 2017-12-19 2021-10-26 Claret Medical, Inc. Systems for protection of the cerebral vasculature during a cardiac procedure
US11185405B2 (en) 2013-08-30 2021-11-30 Jenavalve Technology, Inc. Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame
US11191630B2 (en) 2017-10-27 2021-12-07 Claret Medical, Inc. Systems and methods for protecting the cerebral vasculature
US11191641B2 (en) 2018-01-19 2021-12-07 Boston Scientific Scimed, Inc. Inductance mode deployment sensors for transcatheter valve system
US11197754B2 (en) 2017-01-27 2021-12-14 Jenavalve Technology, Inc. Heart valve mimicry
US11229517B2 (en) 2018-05-15 2022-01-25 Boston Scientific Scimed, Inc. Replacement heart valve commissure assembly
US11241312B2 (en) 2018-12-10 2022-02-08 Boston Scientific Scimed, Inc. Medical device delivery system including a resistance member
US11241310B2 (en) 2018-06-13 2022-02-08 Boston Scientific Scimed, Inc. Replacement heart valve delivery device
US11246625B2 (en) 2018-01-19 2022-02-15 Boston Scientific Scimed, Inc. Medical device delivery system with feedback loop
EP3964168A1 (en) * 2013-05-10 2022-03-09 Medtronic, Inc. System for deploying a device to a distal location across a diseased vessel
US11278398B2 (en) 2003-12-23 2022-03-22 Boston Scientific Scimed, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US11285002B2 (en) 2003-12-23 2022-03-29 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a heart valve
US11304801B2 (en) 2006-09-19 2022-04-19 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
WO2022087136A1 (en) * 2020-10-20 2022-04-28 Legacy Ventures LLC Clot retrieval system
US11331187B2 (en) 2016-06-17 2022-05-17 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
US11337790B2 (en) 2017-02-22 2022-05-24 Boston Scientific Scimed, Inc. Systems and methods for protecting the cerebral vasculature
US11338117B2 (en) 2018-10-08 2022-05-24 Trisalus Life Sciences, Inc. Implantable dual pathway therapeutic agent delivery port
US11337800B2 (en) 2015-05-01 2022-05-24 Jenavalve Technology, Inc. Device and method with reduced pacemaker rate in heart valve replacement
US11351023B2 (en) 2018-08-21 2022-06-07 Claret Medical, Inc. Systems and methods for protecting the cerebral vasculature
US11357624B2 (en) 2007-04-13 2022-06-14 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
US11389168B2 (en) 2016-09-01 2022-07-19 Microvention, Inc. Temporary aortic occlusion device
US11389169B2 (en) 2016-09-01 2022-07-19 Microvention, Inc. Temporary aortic occlusion device
US11400263B1 (en) 2016-09-19 2022-08-02 Trisalus Life Sciences, Inc. System and method for selective pressure-controlled therapeutic delivery
US11439504B2 (en) 2019-05-10 2022-09-13 Boston Scientific Scimed, Inc. Replacement heart valve with improved cusp washout and reduced loading
US11439491B2 (en) 2018-04-26 2022-09-13 Claret Medical, Inc. Systems and methods for protecting the cerebral vasculature
US11439732B2 (en) 2018-02-26 2022-09-13 Boston Scientific Scimed, Inc. Embedded radiopaque marker in adaptive seal
US11504231B2 (en) 2018-05-23 2022-11-22 Corcym S.R.L. Cardiac valve prosthesis
US11517431B2 (en) 2005-01-20 2022-12-06 Jenavalve Technology, Inc. Catheter system for implantation of prosthetic heart valves
US11564794B2 (en) 2008-02-26 2023-01-31 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
CN115670738A (en) * 2022-12-28 2023-02-03 北京华脉泰科医疗器械股份有限公司 Thrombolytic catheter filter and thrombolytic filter combination kit
US11589981B2 (en) 2010-05-25 2023-02-28 Jenavalve Technology, Inc. Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent
US11607301B2 (en) 2009-01-16 2023-03-21 Boston Scientific Scimed, Inc. Intravascular blood filters and methods of use
US11771544B2 (en) 2011-05-05 2023-10-03 Symetis Sa Method and apparatus for compressing/loading stent-valves
US11850398B2 (en) 2018-08-01 2023-12-26 Trisalus Life Sciences, Inc. Systems and methods for pressure-facilitated therapeutic agent delivery
US11931252B2 (en) 2019-07-15 2024-03-19 Cephea Valve Technologies, Inc. Disk-based valve apparatus and method for the treatment of valve dysfunction

Families Citing this family (403)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5636641A (en) 1994-07-25 1997-06-10 Advanced Cardiovascular Systems, Inc. High strength member for intracorporeal use
US6736843B1 (en) 1994-07-25 2004-05-18 Advanced Cardiovascular Systems, Inc. Cylindrically-shaped balloon-expandable stent
US6270477B1 (en) * 1996-05-20 2001-08-07 Percusurge, Inc. Catheter for emboli containment
US5662671A (en) 1996-07-17 1997-09-02 Embol-X, Inc. Atherectomy device having trapping and excising means for removal of plaque from the aorta and other arteries
US7883539B2 (en) 1997-01-02 2011-02-08 Edwards Lifesciences Llc Heart wall tension reduction apparatus and method
US6183411B1 (en) * 1998-09-21 2001-02-06 Myocor, Inc. External stress reduction device and method
US6050936A (en) * 1997-01-02 2000-04-18 Myocor, Inc. Heart wall tension reduction apparatus
AU6688398A (en) 1997-03-06 1998-09-22 Percusurge, Inc. Intravascular aspiration system
US6152946A (en) * 1998-03-05 2000-11-28 Scimed Life Systems, Inc. Distal protection device and method
US6258120B1 (en) 1997-12-23 2001-07-10 Embol-X, Inc. Implantable cerebral protection device and methods of use
ATE382309T1 (en) * 1997-11-07 2008-01-15 Salviac Ltd EMBOLIC PROTECTION DEVICE
US7491216B2 (en) * 1997-11-07 2009-02-17 Salviac Limited Filter element with retractable guidewire tip
US9498604B2 (en) 1997-11-12 2016-11-22 Genesis Technologies Llc Medical device and method
US20100030256A1 (en) 1997-11-12 2010-02-04 Genesis Technologies Llc Medical Devices and Methods
US20040260333A1 (en) * 1997-11-12 2004-12-23 Dubrul William R. Medical device and method
US6332893B1 (en) 1997-12-17 2001-12-25 Myocor, Inc. Valve to myocardium tension members device and method
EP1054634A4 (en) * 1998-02-10 2006-03-29 Artemis Medical Inc Entrapping apparatus and method for use
US6602265B2 (en) * 1998-02-10 2003-08-05 Artemis Medical, Inc. Tissue separation medical device and method
US6450989B2 (en) * 1998-04-27 2002-09-17 Artemis Medical, Inc. Dilating and support apparatus with disease inhibitors and methods for use
US6260552B1 (en) * 1998-07-29 2001-07-17 Myocor, Inc. Transventricular implant tools and devices
US7044134B2 (en) 1999-11-08 2006-05-16 Ev3 Sunnyvale, Inc Method of implanting a device in the left atrial appendage
US7128073B1 (en) * 1998-11-06 2006-10-31 Ev3 Endovascular, Inc. Method and device for left atrial appendage occlusion
US6896690B1 (en) 2000-01-27 2005-05-24 Viacor, Inc. Cardiac valve procedure methods and devices
AU3844399A (en) * 1999-05-07 2000-11-21 Salviac Limited Support frame for embolic protection device
AU4606400A (en) * 1999-05-07 2000-11-21 Salviac Limited Improved filter element for embolic protection device
US6964672B2 (en) * 1999-05-07 2005-11-15 Salviac Limited Support frame for an embolic protection device
WO2000067666A1 (en) * 1999-05-07 2000-11-16 Salviac Limited Improved filter element for embolic protection device
US6918921B2 (en) * 1999-05-07 2005-07-19 Salviac Limited Support frame for an embolic protection device
US7037320B2 (en) * 2001-12-21 2006-05-02 Salviac Limited Support frame for an embolic protection device
US20020058911A1 (en) 1999-05-07 2002-05-16 Paul Gilson Support frame for an embolic protection device
US20030150821A1 (en) 1999-07-16 2003-08-14 Bates Mark C. Emboli filtration system and methods of use
CA2379414C (en) 1999-07-30 2010-09-14 Incept Llc Vascular filter having articulation region and methods of use in the ascending aorta
CA2378715C (en) * 1999-07-30 2011-09-06 Incept Llc Vascular device for emboli, thrombus and foreign body removal and methods of use
US7320697B2 (en) * 1999-07-30 2008-01-22 Boston Scientific Scimed, Inc. One piece loop and coil
US8328829B2 (en) 1999-08-19 2012-12-11 Covidien Lp High capacity debulking catheter with razor edge cutting window
US6299622B1 (en) 1999-08-19 2001-10-09 Fox Hollow Technologies, Inc. Atherectomy catheter with aligned imager
US7708749B2 (en) 2000-12-20 2010-05-04 Fox Hollow Technologies, Inc. Debulking catheters and methods
US7713279B2 (en) 2000-12-20 2010-05-11 Fox Hollow Technologies, Inc. Method and devices for cutting tissue
IL131863A0 (en) * 1999-09-10 2001-03-19 Bruckheimer Elchanan Intravascular device and method using it
DE29916162U1 (en) * 1999-09-14 2000-01-13 Cormedics Gmbh Vascular filter system
US6994092B2 (en) * 1999-11-08 2006-02-07 Ev3 Sunnyvale, Inc. Device for containing embolic material in the LAA having a plurality of tissue retention structures
EP1237487A4 (en) * 1999-12-06 2010-11-03 Simcha Milo Ultrasonic medical device
US6443971B1 (en) 1999-12-21 2002-09-03 Advanced Cardiovascular Systems, Inc. System for, and method of, blocking the passage of emboli through a vessel
GB9930654D0 (en) * 1999-12-23 2000-02-16 Halpin Richard M B Device for controlling extra-vascular haemorrhage
US6660021B1 (en) 1999-12-23 2003-12-09 Advanced Cardiovascular Systems, Inc. Intravascular device and system
US6575997B1 (en) 1999-12-23 2003-06-10 Endovascular Technologies, Inc. Embolic basket
US6402771B1 (en) 1999-12-23 2002-06-11 Guidant Endovascular Solutions Snare
US6540722B1 (en) * 1999-12-30 2003-04-01 Advanced Cardiovascular Systems, Inc. Embolic protection devices
US6695813B1 (en) 1999-12-30 2004-02-24 Advanced Cardiovascular Systems, Inc. Embolic protection devices
US7918820B2 (en) 1999-12-30 2011-04-05 Advanced Cardiovascular Systems, Inc. Device for, and method of, blocking emboli in vessels such as blood arteries
US6511503B1 (en) 1999-12-30 2003-01-28 Advanced Cardiovascular Systems, Inc. Catheter apparatus for treating occluded vessels and filtering embolic debris and method of use
US6443926B1 (en) * 2000-02-01 2002-09-03 Harold D. Kletschka Embolic protection device having expandable trap
US6540767B1 (en) * 2000-02-08 2003-04-01 Scimed Life Systems, Inc. Recoilable thrombosis filtering device and method
US6629953B1 (en) 2000-02-18 2003-10-07 Fox Hollow Technologies, Inc. Methods and devices for removing material from a vascular site
GB2369575A (en) * 2000-04-20 2002-06-05 Salviac Ltd An embolic protection system
US6334864B1 (en) * 2000-05-17 2002-01-01 Aga Medical Corp. Alignment member for delivering a non-symmetric device with a predefined orientation
US6602271B2 (en) 2000-05-24 2003-08-05 Medtronic Ave, Inc. Collapsible blood filter with optimal braid geometry
US6645221B1 (en) * 2000-05-30 2003-11-11 Zuli, Holdings Ltd. Active arterial embolization filter
US6964670B1 (en) 2000-07-13 2005-11-15 Advanced Cardiovascular Systems, Inc. Embolic protection guide wire
US6723038B1 (en) 2000-10-06 2004-04-20 Myocor, Inc. Methods and devices for improving mitral valve function
US6616684B1 (en) * 2000-10-06 2003-09-09 Myocor, Inc. Endovascular splinting devices and methods
DE10049865B8 (en) * 2000-10-09 2008-10-30 Universitätsklinikum Freiburg Device for removing an aortic valve on the human heart by means of a minimally invasive surgical procedure
US6881217B2 (en) * 2000-10-13 2005-04-19 Henry M. Israel Stent assembly
US6506203B1 (en) 2000-12-19 2003-01-14 Advanced Cardiovascular Systems, Inc. Low profile sheathless embolic protection system
AU2002231074A1 (en) * 2000-12-20 2002-07-01 Fox Hollow Technologies, Inc. Debulking catheter
US20020128680A1 (en) * 2001-01-25 2002-09-12 Pavlovic Jennifer L. Distal protection device with electrospun polymer fiber matrix
US6840950B2 (en) * 2001-02-20 2005-01-11 Scimed Life Systems, Inc. Low profile emboli capture device
US6635070B2 (en) * 2001-05-21 2003-10-21 Bacchus Vascular, Inc. Apparatus and methods for capturing particulate material within blood vessels
US6599307B1 (en) * 2001-06-29 2003-07-29 Advanced Cardiovascular Systems, Inc. Filter device for embolic protection systems
US7338510B2 (en) 2001-06-29 2008-03-04 Advanced Cardiovascular Systems, Inc. Variable thickness embolic filtering devices and method of manufacturing the same
US6951570B2 (en) * 2001-07-02 2005-10-04 Rubicon Medical, Inc. Methods, systems, and devices for deploying a filter from a filter device
US6878153B2 (en) * 2001-07-02 2005-04-12 Rubicon Medical, Inc. Methods, systems, and devices for providing embolic protection and removing embolic material
US6962598B2 (en) * 2001-07-02 2005-11-08 Rubicon Medical, Inc. Methods, systems, and devices for providing embolic protection
AU2012209037B2 (en) * 2001-08-22 2013-12-12 W. L. Gore & Associates, Inc. Apparatus and methods for treating stroke and controlling cerebral flow characteristics
US6929634B2 (en) * 2001-08-22 2005-08-16 Gore Enterprise Holdings, Inc. Apparatus and methods for treating stroke and controlling cerebral flow characteristics
US7063714B2 (en) * 2001-08-22 2006-06-20 Gore Enterprise Holdings, Inc. Apparatus and methods for treating stroke and controlling cerebral flow characteristics
US6902540B2 (en) * 2001-08-22 2005-06-07 Gerald Dorros Apparatus and methods for treating stroke and controlling cerebral flow characteristics
US20030040762A1 (en) * 2001-08-22 2003-02-27 Gerald Dorros Apparatus and methods for treating stroke and controlling cerebral flow characteristics
EP2305342A3 (en) * 2001-08-22 2013-04-03 Gore Enterprise Holdings, Inc. Apparatus and methods for treating strokes and controlling cerebral flow characteristics
US6638294B1 (en) 2001-08-30 2003-10-28 Advanced Cardiovascular Systems, Inc. Self furling umbrella frame for carotid filter
US6592606B2 (en) 2001-08-31 2003-07-15 Advanced Cardiovascular Systems, Inc. Hinged short cage for an embolic protection device
WO2003022131A2 (en) * 2001-09-07 2003-03-20 Mardil, Inc. Method and apparatus for external heart stabilization
SE523902C2 (en) * 2001-09-07 2004-06-01 Jan Otto Solem Apparatus for closing a puncture in a body vessel
US6863683B2 (en) 2001-09-19 2005-03-08 Abbott Laboratoris Vascular Entities Limited Cold-molding process for loading a stent onto a stent delivery system
US6616682B2 (en) * 2001-09-19 2003-09-09 Jomed Gmbh Methods and apparatus for distal protection during a medical procedure
US6802851B2 (en) * 2001-09-20 2004-10-12 Gordia Neurovascular, Inc. Stent aneurysm embolization method using collapsible member and embolic coils
US6811560B2 (en) * 2001-09-20 2004-11-02 Cordis Neurovascular, Inc. Stent aneurysm embolization method and device
US8262689B2 (en) 2001-09-28 2012-09-11 Advanced Cardiovascular Systems, Inc. Embolic filtering devices
EP1430839B1 (en) * 2001-09-28 2009-06-10 Kanji Inoue Free thrombus capturing tool
US20030083692A1 (en) * 2001-10-29 2003-05-01 Scimed Life Systems, Inc. Distal protection device and method of use thereof
US20040111108A1 (en) 2001-11-09 2004-06-10 Farnan Robert C. Balloon catheter with non-deployable stent
CA2464053A1 (en) 2001-11-09 2003-05-22 Novoste Corporation Baloon catheter with non-deployable stent
US6890340B2 (en) * 2001-11-29 2005-05-10 Medtronic Vascular, Inc. Apparatus for temporary intraluminal protection
EP1461112B1 (en) * 2001-12-05 2012-11-21 Sagax Inc. Endovascular device for entrapment of particulate matter and method for use
US7241304B2 (en) * 2001-12-21 2007-07-10 Advanced Cardiovascular Systems, Inc. Flexible and conformable embolic filtering devices
US7322958B2 (en) * 2001-12-27 2008-01-29 Wholey Mark H Apparatus for thromboembolic protection
US6764510B2 (en) 2002-01-09 2004-07-20 Myocor, Inc. Devices and methods for heart valve treatment
US7144408B2 (en) * 2002-03-05 2006-12-05 Salviac Limited Embolic protection system
US7063707B2 (en) * 2002-03-06 2006-06-20 Scimed Life Systems, Inc. Medical retrieval device
US20030176886A1 (en) * 2002-03-12 2003-09-18 Wholey Mark H. Vascular catheter with expanded distal tip for receiving a thromboembolic protection device and method of use
AU2003262373A1 (en) * 2002-04-19 2003-11-03 Salviac Limited A medical device
WO2003088869A2 (en) * 2002-04-19 2003-10-30 Salviac Limited A medical device
US8070769B2 (en) * 2002-05-06 2011-12-06 Boston Scientific Scimed, Inc. Inverted embolic protection filter
US7585309B2 (en) * 2002-05-16 2009-09-08 Boston Scientific Scimed, Inc. Aortic filter
DE10233085B4 (en) 2002-07-19 2014-02-20 Dendron Gmbh Stent with guide wire
US8425549B2 (en) 2002-07-23 2013-04-23 Reverse Medical Corporation Systems and methods for removing obstructive matter from body lumens and treating vascular defects
US7303575B2 (en) * 2002-08-01 2007-12-04 Lumen Biomedical, Inc. Embolism protection devices
US8114114B2 (en) * 2002-08-27 2012-02-14 Emboline, Inc. Embolic protection device
AU2003268379A1 (en) * 2002-09-03 2004-03-29 John R. Fagan Arterial embolic filter deployed from catheter
US7331973B2 (en) 2002-09-30 2008-02-19 Avdanced Cardiovascular Systems, Inc. Guide wire with embolic filtering attachment
US7252675B2 (en) 2002-09-30 2007-08-07 Advanced Cardiovascular, Inc. Embolic filtering devices
US20040093012A1 (en) 2002-10-17 2004-05-13 Cully Edward H. Embolic filter frame having looped support strut elements
US20040088000A1 (en) 2002-10-31 2004-05-06 Muller Paul F. Single-wire expandable cages for embolic filtering devices
US7112219B2 (en) 2002-11-12 2006-09-26 Myocor, Inc. Devices and methods for heart valve treatment
AU2003294293A1 (en) * 2002-11-13 2004-06-03 Viacor, Inc. Cardiac valve procedure methods and devices
US20040138694A1 (en) * 2003-01-15 2004-07-15 Scimed Life Systems, Inc. Intravascular filtering membrane and method of making an embolic protection filter device
US8080026B2 (en) 2003-01-21 2011-12-20 Angioscore, Inc. Apparatus and methods for treating hardened vascular lesions
US7163549B2 (en) * 2003-02-11 2007-01-16 Boston Scientific Scimed Inc. Filter membrane manufacturing method
US7137991B2 (en) * 2003-02-24 2006-11-21 Scimed Life Systems, Inc. Multi-wire embolic protection filtering device
US8591540B2 (en) 2003-02-27 2013-11-26 Abbott Cardiovascular Systems Inc. Embolic filtering devices
US7250041B2 (en) * 2003-03-12 2007-07-31 Abbott Cardiovascular Systems Inc. Retrograde pressure regulated infusion
US20050015048A1 (en) * 2003-03-12 2005-01-20 Chiu Jessica G. Infusion treatment agents, catheters, filter devices, and occlusion devices, and use thereof
WO2004082532A1 (en) * 2003-03-17 2004-09-30 Ev3 Sunnyvale, Inc. Thin film composite lamination
US20040199201A1 (en) * 2003-04-02 2004-10-07 Scimed Life Systems, Inc. Embolectomy devices
US8246640B2 (en) 2003-04-22 2012-08-21 Tyco Healthcare Group Lp Methods and devices for cutting tissue at a vascular location
US7331976B2 (en) * 2003-04-29 2008-02-19 Rex Medical, L.P. Distal protection device
US20040220612A1 (en) * 2003-04-30 2004-11-04 Swainston Kyle W Slidable capture catheter
US6969396B2 (en) * 2003-05-07 2005-11-29 Scimed Life Systems, Inc. Filter membrane with increased surface area
WO2004100772A2 (en) * 2003-05-12 2004-11-25 University Of Florida Devices and methods for disruption and removal of luninal occlusions
US7537600B2 (en) * 2003-06-12 2009-05-26 Boston Scientific Scimed, Inc. Valved embolic protection filter
US7699865B2 (en) * 2003-09-12 2010-04-20 Rubicon Medical, Inc. Actuating constraining mechanism
US8535344B2 (en) * 2003-09-12 2013-09-17 Rubicon Medical, Inc. Methods, systems, and devices for providing embolic protection and removing embolic material
JP3660931B2 (en) * 2003-09-22 2005-06-15 新 石丸 Thrombus embolus capture device
WO2005042081A1 (en) * 2003-10-28 2005-05-12 Peacock James C Iii Embolic filter device and related systems and methods
US7056286B2 (en) 2003-11-12 2006-06-06 Adrian Ravenscroft Medical device anchor and delivery system
US7892251B1 (en) 2003-11-12 2011-02-22 Advanced Cardiovascular Systems, Inc. Component for delivering and locking a medical device to a guide wire
WO2005058197A1 (en) * 2003-12-16 2005-06-30 Wholey Mark H Vascular catheter with an expandable section and a distal tip for delivering a thromboembolic protection device and method of use
US20050137691A1 (en) * 2003-12-23 2005-06-23 Sadra Medical Two piece heart valve and anchor
US20050137686A1 (en) * 2003-12-23 2005-06-23 Sadra Medical, A Delaware Corporation Externally expandable heart valve anchor and method
US20050159770A1 (en) * 2004-01-21 2005-07-21 Diqur Medical Systems, Llc Funnel catheter device and method of operation thereof
US20050177185A1 (en) * 2004-02-05 2005-08-11 Scimed Life Systems, Inc. Counterwound coil for embolic protection sheath
US8092483B2 (en) * 2004-03-06 2012-01-10 Medtronic, Inc. Steerable device having a corewire within a tube and combination with a functional medical component
US7988705B2 (en) * 2004-03-06 2011-08-02 Lumen Biomedical, Inc. Steerable device having a corewire within a tube and combination with a functional medical component
US7678129B1 (en) 2004-03-19 2010-03-16 Advanced Cardiovascular Systems, Inc. Locking component for an embolic filter assembly
WO2005094283A2 (en) 2004-03-25 2005-10-13 Hauser David L Vascular filter device
US8409237B2 (en) * 2004-05-27 2013-04-02 Medtronic, Inc. Emboli filter export system
EP1765451B1 (en) * 2004-06-14 2021-11-17 Edwards Lifesciences Corporation Devices for arterio-venous fistula creation
US7976516B2 (en) * 2004-06-25 2011-07-12 Lumen Biomedical, Inc. Medical device having mechanically interlocked segments
US20060047286A1 (en) * 2004-08-31 2006-03-02 Stephen West Clot retrieval device
US7566343B2 (en) 2004-09-02 2009-07-28 Boston Scientific Scimed, Inc. Cardiac valve, system, and method
US20060047301A1 (en) * 2004-09-02 2006-03-02 Ogle Matthew F Emboli removal system with oxygenated flow
US9655633B2 (en) 2004-09-10 2017-05-23 Penumbra, Inc. System and method for treating ischemic stroke
US20060058837A1 (en) * 2004-09-10 2006-03-16 Arani Bose System and method for treating ischemic stroke
US7927346B2 (en) * 2004-09-10 2011-04-19 Stryker Corporation Diversion device to increase cerebral blood flow
US8366735B2 (en) 2004-09-10 2013-02-05 Penumbra, Inc. System and method for treating ischemic stroke
US20060100658A1 (en) * 2004-11-09 2006-05-11 Hiroyuki Obana Interventional guiding sheath system and method of use
US20060241677A1 (en) 2005-01-03 2006-10-26 Eric Johnson Methods for maintaining a filtering device within a lumen
US20060173490A1 (en) * 2005-02-01 2006-08-03 Boston Scientific Scimed, Inc. Filter system and method
US20060190024A1 (en) * 2005-02-24 2006-08-24 Bei Nianjiong Recovery catheter apparatus and method
US9259305B2 (en) 2005-03-31 2016-02-16 Abbott Cardiovascular Systems Inc. Guide wire locking mechanism for rapid exchange and other catheter systems
US20060229658A1 (en) * 2005-04-07 2006-10-12 Stivland Timothy M Embolic protection filter with reduced landing zone
US8475487B2 (en) * 2005-04-07 2013-07-02 Medrad, Inc. Cross stream thrombectomy catheter with flexible and expandable cage
US20060247672A1 (en) * 2005-04-27 2006-11-02 Vidlund Robert M Devices and methods for pericardial access
US20060253148A1 (en) * 2005-05-04 2006-11-09 Leone James E Apparatus and method of using an occluder for embolic protection
US10076641B2 (en) 2005-05-11 2018-09-18 The Spectranetics Corporation Methods and systems for delivering substances into luminal walls
US20060287668A1 (en) * 2005-06-16 2006-12-21 Fawzi Natalie V Apparatus and methods for intravascular embolic protection
US20080172066A9 (en) * 2005-07-29 2008-07-17 Galdonik Jason A Embolectomy procedures with a device comprising a polymer and devices with polymer matrices and supports
US7938820B2 (en) * 2005-08-18 2011-05-10 Lumen Biomedical, Inc. Thrombectomy catheter
US8021351B2 (en) * 2005-08-18 2011-09-20 Medtronic Vascular, Inc. Tracking aspiration catheter
US7972359B2 (en) 2005-09-16 2011-07-05 Atritech, Inc. Intracardiac cage and method of delivering same
US20080188928A1 (en) * 2005-09-16 2008-08-07 Amr Salahieh Medical device delivery sheath
US20070100372A1 (en) * 2005-11-02 2007-05-03 Cook Incorporated Embolic protection device having a filter
US8007488B2 (en) * 2005-11-10 2011-08-30 Phase One Medical Llc Catheter device
US9192755B2 (en) 2005-11-10 2015-11-24 Phase One Medical, Llc Catheter device
JP2009515598A (en) * 2005-11-10 2009-04-16 フェイズ ワン メディカル リミテッド ライアビリティ カンパニー Catheter device
US20070112371A1 (en) * 2005-11-14 2007-05-17 Medtronic Vascular, Inc. Embolic protection filter having compact collapsed dimensions and method of making same
US20070135826A1 (en) 2005-12-01 2007-06-14 Steve Zaver Method and apparatus for delivering an implant without bias to a left atrial appendage
US9107733B2 (en) * 2006-01-13 2015-08-18 W. L. Gore & Associates, Inc. Removable blood conduit filter
US20070185524A1 (en) * 2006-02-03 2007-08-09 Pedro Diaz Rapid exchange emboli capture guidewire system and methods of use
US9119651B2 (en) * 2006-02-13 2015-09-01 Retro Vascular, Inc. Recanalizing occluded vessels using controlled antegrade and retrograde tracking
US20070197962A1 (en) * 2006-02-22 2007-08-23 Masuo Morikawa Catheter for removing foreign substance in blood vessel
US20070198050A1 (en) * 2006-02-22 2007-08-23 Phase One Medica, Llc Medical implant device
US20070219577A1 (en) * 2006-03-20 2007-09-20 Boston Scientific Scimed, Inc. Sprayed in delivery sheath tubes
US20070265655A1 (en) * 2006-05-09 2007-11-15 Boston Scientific Scimed, Inc. Embolic protection filter with enhanced stability within a vessel
US20070276419A1 (en) 2006-05-26 2007-11-29 Fox Hollow Technologies, Inc. Methods and devices for rotating an active element and an energy emitter on a catheter
JP4925728B2 (en) * 2006-05-30 2012-05-09 ニプロ株式会社 Device for capturing scattered foreign matter
JP4925729B2 (en) * 2006-05-30 2012-05-09 ニプロ株式会社 Percutaneous thrombectomy device
US8333000B2 (en) 2006-06-19 2012-12-18 Advanced Cardiovascular Systems, Inc. Methods for improving stent retention on a balloon catheter
US7828854B2 (en) * 2006-10-31 2010-11-09 Ethicon, Inc. Implantable repair device
EP2088961A4 (en) * 2006-11-21 2014-04-16 Medical Res Infrastructure & Health Services Fund Tel Aviv Medical Ct Branch stent graft for aortic aneurysm repair
WO2008066881A1 (en) 2006-11-29 2008-06-05 Amir Belson Embolic protection device
US20080221552A1 (en) * 2007-03-09 2008-09-11 Abbott Cardiovascular Systems Inc. Agent delivery perfusion catheter
US20080243170A1 (en) * 2007-03-30 2008-10-02 Boston Scientific Scimed, Inc. Embolic capturing devices and methods
US7780630B2 (en) * 2007-03-30 2010-08-24 Boston Scientific Scimed, Inc. Perfusion device
US7686783B2 (en) * 2007-03-30 2010-03-30 Boston Scientific Scimed, Inc. Perfusion and embolic protection
US8216209B2 (en) 2007-05-31 2012-07-10 Abbott Cardiovascular Systems Inc. Method and apparatus for delivering an agent to a kidney
US7867273B2 (en) 2007-06-27 2011-01-11 Abbott Laboratories Endoprostheses for peripheral arteries and other body vessels
US10376685B2 (en) 2007-08-31 2019-08-13 Mermaid Medical Vascular Aps Thrombus detection device and method
US8613753B2 (en) * 2007-08-31 2013-12-24 BiO2 Medical, Inc. Multi-lumen central access vena cava filter apparatus and method of using same
US9687333B2 (en) * 2007-08-31 2017-06-27 BiO2 Medical, Inc. Reduced profile central venous access catheter with vena cava filter and method
US11337714B2 (en) 2007-10-17 2022-05-24 Covidien Lp Restoring blood flow and clot removal during acute ischemic stroke
US8088140B2 (en) 2008-05-19 2012-01-03 Mindframe, Inc. Blood flow restorative and embolus removal methods
WO2009053855A2 (en) * 2007-10-27 2009-04-30 Salviac Limited Embolic filter device and method of manufacturing the same
DE102007056946A1 (en) * 2007-11-27 2009-05-28 Gunnar Pah Device for filtering blood
US20090187211A1 (en) 2007-12-21 2009-07-23 Abbott Laboratories Vena cava filter having hourglass shape
WO2009086205A2 (en) * 2007-12-21 2009-07-09 Abbott Laboratories Body lumen filter
ES2647310T3 (en) 2008-02-22 2017-12-20 Covidien Lp Device for flow restoration
US8784440B2 (en) 2008-02-25 2014-07-22 Covidien Lp Methods and devices for cutting tissue
US8070694B2 (en) 2008-07-14 2011-12-06 Medtronic Vascular, Inc. Fiber based medical devices and aspiration catheters
US9402707B2 (en) 2008-07-22 2016-08-02 Neuravi Limited Clot capture systems and associated methods
DE202009019019U1 (en) * 2008-09-04 2015-07-27 Swat Medical Ab Foldable temporary embolic protection device with elongated blood permeable unit
DK2326379T3 (en) * 2008-09-17 2013-09-08 Joanneum Res Forschungsgmbh Filament-based catheter
US8852225B2 (en) * 2008-09-25 2014-10-07 Medtronic, Inc. Emboli guarding device
WO2010039862A1 (en) * 2008-09-30 2010-04-08 Rox Medical, Inc. Methods for screening and treating patients with compromised cardiopulmonary function
CA2739665C (en) 2008-10-13 2018-01-02 Tyco Healthcare Group Lp Devices and methods for manipulating a catheter shaft
EP2196174B1 (en) 2008-12-12 2014-02-26 Abbott Laboratories Vascular Enterprises Limited Process for loading a stent onto a stent delivery system
US20100152711A1 (en) * 2008-12-15 2010-06-17 Boston Scientific Scimed, Inc. Offset coupling region
US8444669B2 (en) 2008-12-15 2013-05-21 Boston Scientific Scimed, Inc. Embolic filter delivery system and method
EP3586793B1 (en) 2009-01-09 2021-06-02 Embrella Cardiovascular, Inc. Embolic deflection device
US20100185179A1 (en) * 2009-01-21 2010-07-22 Abbott Cardiovascular Systems Inc. Needled cannula with filter device
EP2391303A4 (en) * 2009-01-29 2020-09-09 Boston Scientific Scimed, Inc. Illuminated intravascular blood filter
US20100204672A1 (en) * 2009-02-12 2010-08-12 Penumra, Inc. System and method for treating ischemic stroke
US20100228280A1 (en) * 2009-03-09 2010-09-09 Adam Groothuis Methods and devices for treatment of lumenal systems
EP2241284B1 (en) 2009-04-15 2012-09-19 National University of Ireland, Galway Intravasculature devices and balloons for use therewith
US9636204B2 (en) 2009-04-16 2017-05-02 Cvdevices, Llc Deflection devices, systems and methods for the prevention of stroke
WO2010121192A1 (en) 2009-04-16 2010-10-21 Cvdevices, Llc Devices, systems, and methods for the prevention of stroke
US9681967B2 (en) 2009-04-16 2017-06-20 Cvdevices, Llc Linked deflection devices, systems and methods for the prevention of stroke
RU2509537C2 (en) 2009-04-29 2014-03-20 ТАЙКО ХЕЛСКЕА ГРУП эЛПи Methods and devices for tissue cutting and cleansing
US8192452B2 (en) 2009-05-14 2012-06-05 Tyco Healthcare Group Lp Easily cleaned atherectomy catheters and methods of use
US9510855B2 (en) * 2009-06-15 2016-12-06 Perflow Medical Ltd. Method and apparatus for allowing blood flow through an occluded vessel
US20110022074A1 (en) * 2009-07-22 2011-01-27 Alex Powell Permanent arterial emboli dissolution filter to prevent embolic occlusion of a blood vessel
US10092427B2 (en) 2009-11-04 2018-10-09 Confluent Medical Technologies, Inc. Alternating circumferential bridge stent design and methods for use thereof
US9649211B2 (en) 2009-11-04 2017-05-16 Confluent Medical Technologies, Inc. Alternating circumferential bridge stent design and methods for use thereof
EP2913013B1 (en) 2009-12-02 2016-11-09 Covidien LP Methods and devices for cutting tissue
EP2509519B1 (en) 2009-12-11 2019-08-07 Covidien LP Material removal device having improved material capture efficiency
CN102821704A (en) * 2010-02-05 2012-12-12 斯瑞克运营有限公司 Multimode occlusion and stenosis treatment apparatus and method of use
US9199066B2 (en) 2010-03-12 2015-12-01 Quattro Vascular Pte Ltd. Device and method for compartmental vessel treatment
AU2011233575A1 (en) * 2010-04-01 2012-10-25 Xenolith Medical Ltd. Expandable devices and methods of use
EP2558005B1 (en) 2010-04-13 2022-03-30 MIVI Neuroscience, Inc Embolectomy devices for treatment of acute ischemic stroke condition
EP2380604A1 (en) 2010-04-19 2011-10-26 InnoRa Gmbh Improved coating formulations for scoring or cutting balloon catheters
CA2800920C (en) 2010-06-14 2015-04-14 Covidien Lp Material removal device
US9561094B2 (en) 2010-07-23 2017-02-07 Nfinium Vascular Technologies, Llc Devices and methods for treating venous diseases
US10130470B2 (en) 2010-08-17 2018-11-20 St. Jude Medical, Llc Sleeve for facilitating movement of a transfemoral catheter
US9439795B2 (en) 2010-09-17 2016-09-13 St. Jude Medical, Cardiology Division, Inc. Retainers for transcatheter heart valve delivery systems
US8632559B2 (en) 2010-09-21 2014-01-21 Angioscore, Inc. Method and system for treating valve stenosis
US9039749B2 (en) 2010-10-01 2015-05-26 Covidien Lp Methods and apparatuses for flow restoration and implanting members in the human body
WO2012052982A1 (en) 2010-10-22 2012-04-26 Neuravi Limited Clot engagement and removal system
AU2011319797B2 (en) 2010-10-28 2015-04-09 Covidien Lp Material removal device and method of use
CA2817213C (en) 2010-11-11 2016-06-14 Covidien Lp Flexible debulking catheters with imaging and methods of use and manufacture
US10123865B2 (en) 2010-12-16 2018-11-13 BiO2 Medical, Inc. Vascular filter assembly having low profile sheath
RU2462197C1 (en) * 2011-02-11 2012-09-27 Общество с ограниченной ответственностью "АСТОР" Method of active prophylaxis of acute cerebral circulation disorders of embologenic nature and filtering stent-graft for its realisation according to belyaev ov
WO2012120490A2 (en) 2011-03-09 2012-09-13 Neuravi Limited A clot retrieval device for removing occlusive clot from a blood vessel
US11259824B2 (en) 2011-03-09 2022-03-01 Neuravi Limited Clot retrieval device for removing occlusive clot from a blood vessel
EP2522307B1 (en) * 2011-05-08 2020-09-30 ITSO Medical AB Device for delivery of medical devices to a cardiac valve
EP2736450A1 (en) 2011-07-28 2014-06-04 St. Jude Medical, Inc. Expandable radiopaque marker for transcatheter aortic valve implantation
EP4101399A1 (en) 2011-08-05 2022-12-14 Route 92 Medical, Inc. System for treatment of acute ischemic stroke
EP2750862B1 (en) 2011-09-01 2016-07-06 Covidien LP Catheter with helical drive shaft and methods of manufacture
EP2762083B1 (en) * 2011-09-27 2017-01-18 Kanji Inoue Device for capturing debris in blood vessel
US20130096606A1 (en) * 2011-10-17 2013-04-18 William C. Bruchman Embolic protection devices and related systems and methods
JP5951955B2 (en) * 2011-10-17 2016-07-13 株式会社東海メディカルプロダクツ Filter device for embolization substance capture
US9744023B2 (en) 2011-10-25 2017-08-29 Boston Scientific Scimed, Inc. Embolic debris deflector
US8968354B2 (en) 2011-10-26 2015-03-03 Boston Scientific Scimed, Inc. Extended protection embolic filter
US20130116654A1 (en) * 2011-11-08 2013-05-09 Edwards Lifesciences Llc Aortic Occlusion Catheter
US20140303667A1 (en) * 2011-12-02 2014-10-09 Inceptus Medical, Llc Embolic protection device and methods of use
RU2014129392A (en) 2012-01-06 2016-02-27 Эмболайн, Инк. Embedded anti-embolic protection
US10426501B2 (en) 2012-01-13 2019-10-01 Crux Biomedical, Inc. Retrieval snare device and method
KR20140114856A (en) 2012-02-01 2014-09-29 콰트로 배스큘러 피티이 리미티드 Device for compartmental dilatation of blood vessels
US9179936B2 (en) 2012-02-08 2015-11-10 Quattro Vascular Pte Ltd. Constraining structure with non-linear axial struts
US9216033B2 (en) 2012-02-08 2015-12-22 Quattro Vascular Pte Ltd. System and method for treating biological vessels
WO2013119332A2 (en) 2012-02-09 2013-08-15 Stout Medical Group, L.P. Embolic device and methods of use
US10213288B2 (en) 2012-03-06 2019-02-26 Crux Biomedical, Inc. Distal protection filter
US8735702B1 (en) * 2012-03-21 2014-05-27 Deborah R. Miles Portable dissipating medium used for removal of vibrational interference in a bowed string of a violin family instrument
WO2013142201A1 (en) * 2012-03-21 2013-09-26 Nexeon Medsystems, Inc. Apparatus and methods for filtering emboli during percutaneous aortic valve replacement and repair procedures with filtration system coupled in-situ to distal end of sheath
CN104334118B (en) * 2012-04-06 2016-12-28 Pi-R-方形有限公司 Percutaneous thromboembolism protection sleeve pipe
US8882828B2 (en) * 2012-04-27 2014-11-11 Medtronic Vascular, Inc. Ring on a closed web stent-graft for use in tip capture
AU2013259912A1 (en) * 2012-05-08 2015-01-15 The Curators Of The University Of Missouri Embolic protection system
US20130338690A1 (en) * 2012-06-15 2013-12-19 Gadal Consulting, LLC Device and method for removing unwanted material in a vascular conduit
US9480561B2 (en) * 2012-06-26 2016-11-01 St. Jude Medical, Cardiology Division, Inc. Apparatus and method for aortic protection and TAVI planar alignment
US9918837B2 (en) 2012-06-29 2018-03-20 St. Jude Medical, Cardiology Division, Inc. System to assist in the release of a collapsible stent from a delivery device
US20140031857A1 (en) * 2012-07-25 2014-01-30 Boston Scientific Scimed, Inc. Embolic protection filter for transcatheter aortic valve replacement and uses thereof
US20140172006A1 (en) * 2012-08-24 2014-06-19 Synecor Llc System for facilitating transcatheter aortic valve procedures using femoral access
US9579157B2 (en) 2012-09-13 2017-02-28 Covidien Lp Cleaning device for medical instrument and method of use
CN104755124B (en) 2012-11-01 2019-04-12 玛芬股份有限公司 For determining the tool of sheath pipe transfer
US9943329B2 (en) 2012-11-08 2018-04-17 Covidien Lp Tissue-removing catheter with rotatable cutter
US9414752B2 (en) 2012-11-09 2016-08-16 Elwha Llc Embolism deflector
US8784434B2 (en) 2012-11-20 2014-07-22 Inceptus Medical, Inc. Methods and apparatus for treating embolism
US10307240B2 (en) 2012-12-11 2019-06-04 Alan Zajarias Methods and apparatus for capturing embolic debris during endovascular procedures
US20140214069A1 (en) * 2013-01-30 2014-07-31 Edwards Lifesciences Corporation Inflatable Embolic Deflector
US9888993B2 (en) 2013-03-01 2018-02-13 St. Jude Medical, Cardiology Division, Inc. Embolic protection device
US9968433B2 (en) * 2013-03-01 2018-05-15 St. Jude Medical, Cardiology Division, Inc. Embolic protection pass through tube
US10973618B2 (en) 2013-03-01 2021-04-13 St. Jude Medical, Cardiology Division, Inc. Embolic protection device
US10076404B2 (en) * 2013-03-12 2018-09-18 Boston Scientific Limited Catheter system with balloon-operated filter sheath and fluid flow maintenance
US9642635B2 (en) 2013-03-13 2017-05-09 Neuravi Limited Clot removal device
US9433429B2 (en) 2013-03-14 2016-09-06 Neuravi Limited Clot retrieval devices
WO2014140092A2 (en) 2013-03-14 2014-09-18 Neuravi Limited Devices and methods for removal of acute blockages from blood vessels
CN105208950A (en) 2013-03-14 2015-12-30 尼尔拉维有限公司 A clot retrieval device for removing occlusive clot from a blood vessel
US10143545B2 (en) 2013-03-15 2018-12-04 W. L. Gore & Associates, Inc. Vascular filtration device
CN105658174B (en) 2013-07-17 2018-01-12 湖区制造公司 High flow capacity embolic
RU2571343C2 (en) * 2013-08-22 2015-12-20 Юрий Германович Андреев Inflow or outflow occlusion device
KR20150026766A (en) * 2013-08-29 2015-03-11 김준홍 Guard catheter for guarding the RVOT wire, guard method in Mitral cerclage coronary sinus annuloplasty
CN105611903B (en) * 2013-08-30 2017-11-21 雪松-西奈医学中心 For taking out the apparatus and method of mechanical heart valve leaflets through conduit
US10398550B2 (en) 2013-09-12 2019-09-03 St. Jude Medical, Cardiology Division, Inc. Atraumatic interface in an implant delivery device
US10076399B2 (en) 2013-09-13 2018-09-18 Covidien Lp Endovascular device engagement
US10117668B2 (en) 2013-10-08 2018-11-06 The Spectranetics Corporation Balloon catheter with non-deployable stent having improved stability
EP2859864A1 (en) 2013-10-14 2015-04-15 Protembis GmbH Medical device for embolic protection
GB2523291B (en) * 2013-10-16 2016-02-24 Cook Medical Technologies Llc Vascular occluder with crossing frame elements
US10350098B2 (en) 2013-12-20 2019-07-16 Volcano Corporation Devices and methods for controlled endoluminal filter deployment
US9265512B2 (en) 2013-12-23 2016-02-23 Silk Road Medical, Inc. Transcarotid neurovascular catheter
US10226268B2 (en) * 2014-01-03 2019-03-12 Legacy Ventures LLC Clot retrieval system
US10285720B2 (en) 2014-03-11 2019-05-14 Neuravi Limited Clot retrieval system for removing occlusive clot from a blood vessel
US9820761B2 (en) 2014-03-21 2017-11-21 Route 92 Medical, Inc. Rapid aspiration thrombectomy system and method
US11278388B2 (en) 2014-05-21 2022-03-22 Swat Medical Ab Embolic protection device and method
US9060777B1 (en) 2014-05-28 2015-06-23 Tw Medical Technologies, Llc Vaso-occlusive devices and methods of use
CN106604696A (en) 2014-05-28 2017-04-26 斯瑞克欧洲控股有限责任公司 Vaso-occlusive devices and methods of use
WO2015184450A1 (en) * 2014-05-30 2015-12-03 Cardiac Valve Solutions Llc Temporary valve and filter on guide catheter
JP2017516584A (en) 2014-06-04 2017-06-22 エンフィニアム バスキュラー テクノロジーズ, エルエルシー Low radial force vascular device and method of occlusion
US10792056B2 (en) * 2014-06-13 2020-10-06 Neuravi Limited Devices and methods for removal of acute blockages from blood vessels
EP3154452A1 (en) 2014-06-13 2017-04-19 Neuravi Limited Devices for removal of acute blockages from blood vessels
WO2015200532A1 (en) * 2014-06-24 2015-12-30 Edwards Lifesciences Corporation Peripheral antegrade perfusion and occlusion device
WO2015200702A1 (en) 2014-06-27 2015-12-30 Covidien Lp Cleaning device for catheter and catheter including the same
US10265086B2 (en) 2014-06-30 2019-04-23 Neuravi Limited System for removing a clot from a blood vessel
EP2987463A1 (en) * 2014-08-21 2016-02-24 Noureddine Frid 3d filter for prevention of stroke
EP3705087B1 (en) 2014-09-14 2023-12-27 Emboline, Inc. Introducer sheath with embolic protection
US20160089172A1 (en) * 2014-09-30 2016-03-31 Boston Scientific Scimed, Inc. Devices and methods for applying suction
US9987117B2 (en) * 2014-11-06 2018-06-05 Furqan Tejani Thromboembolic protection device
US10232148B2 (en) 2014-11-17 2019-03-19 TriReme Medical, LLC Balloon catheter system and method of using same
CN106999196B (en) 2014-11-26 2020-07-28 尼尔拉维有限公司 Thrombus retrieval device for removing obstructive thrombus from blood vessel
US11253278B2 (en) 2014-11-26 2022-02-22 Neuravi Limited Clot retrieval system for removing occlusive clot from a blood vessel
US10617435B2 (en) 2014-11-26 2020-04-14 Neuravi Limited Clot retrieval device for removing clot from a blood vessel
US11065019B1 (en) 2015-02-04 2021-07-20 Route 92 Medical, Inc. Aspiration catheter systems and methods of use
US10426497B2 (en) 2015-07-24 2019-10-01 Route 92 Medical, Inc. Anchoring delivery system and methods
DE202016009165U1 (en) 2015-02-04 2023-04-26 Route 92 Medical, Inc. Rapid Aspiration Thrombectomy System
US10314667B2 (en) 2015-03-25 2019-06-11 Covidien Lp Cleaning device for cleaning medical instrument
US9592111B2 (en) 2015-04-30 2017-03-14 Mark Groh Valve replacement devices
US10159490B2 (en) 2015-05-08 2018-12-25 Stryker European Holdings I, Llc Vaso-occlusive devices
KR102139168B1 (en) * 2015-05-15 2020-07-29 텔리플렉스 메디컬 인코포레이티드 Tethered filter assemblies and methods for use thereof
US10292721B2 (en) 2015-07-20 2019-05-21 Covidien Lp Tissue-removing catheter including movable distal tip
EP3344184A4 (en) 2015-09-01 2019-05-15 Mivi Neuroscience, Inc. Thrombectomy devices and treatment of acute ischemic stroke with thrombus engagement
US10478194B2 (en) 2015-09-23 2019-11-19 Covidien Lp Occlusive devices
US10314664B2 (en) 2015-10-07 2019-06-11 Covidien Lp Tissue-removing catheter and tissue-removing element with depth stop
AU2016341439B2 (en) 2015-10-23 2021-07-08 Inari Medical, Inc. Intravascular treatment of vascular occlusion and associated devices, systems, and methods
US10716915B2 (en) 2015-11-23 2020-07-21 Mivi Neuroscience, Inc. Catheter systems for applying effective suction in remote vessels and thrombectomy procedures facilitated by catheter systems
US10617509B2 (en) 2015-12-29 2020-04-14 Emboline, Inc. Multi-access intraprocedural embolic protection device
WO2017197065A1 (en) 2016-05-13 2017-11-16 St. Jude Medical, Cardiology Division, Inc. Systems for device implantation
WO2017200866A1 (en) * 2016-05-17 2017-11-23 The Cleveland Clinic Foundation Apparatus for blocking bloodflow through a dissected aorta
US11304698B2 (en) 2016-07-25 2022-04-19 Virender K. Sharma Cardiac shunt device and delivery system
CN114587469A (en) * 2016-07-25 2022-06-07 维兰德.K.沙马 Magnetic anastomosis device and delivery system
MX2019001899A (en) 2016-08-17 2019-09-18 Neuravi Ltd A clot retrieval system for removing occlusive clot from a blood vessel.
CA3035706A1 (en) 2016-09-06 2018-03-15 Neuravi Limited A clot retrieval device for removing occlusive clot from a blood vessel
US11877752B2 (en) 2016-09-07 2024-01-23 Daniel Ezra Walzman Filterless aspiration, irrigating, macerating, rotating microcatheter and method of use
US11439492B2 (en) * 2016-09-07 2022-09-13 Daniel Ezra Walzman Lasso filter tipped microcatheter for simultaneous rotating separator, irrigator for thrombectomy and method for use
EP3522798A4 (en) 2016-10-06 2020-05-13 Mivi Neuroscience, Inc. Hydraulic displacement and removal of thrombus clots, and catheters for performing hydraulic displacement
US9994980B2 (en) 2016-10-14 2018-06-12 Inceptus Medical, Llc Braiding machine and methods of use
WO2018080590A1 (en) 2016-10-24 2018-05-03 Inari Medical Devices and methods for treating vascular occlusion
US11197750B2 (en) 2016-11-29 2021-12-14 Lake Region Manufacturing, Inc. Embolic protection device
WO2018132387A1 (en) 2017-01-10 2018-07-19 Route 92 Medical, Inc. Aspiration catheter systems and methods of use
EP3585305A1 (en) * 2017-02-23 2020-01-01 Boston Scientific Scimed, Inc. Medical drain device
WO2018156962A1 (en) 2017-02-24 2018-08-30 Inceptus Medical LLC Vascular occlusion devices and methods
EP3614933A1 (en) 2017-04-27 2020-03-04 Boston Scientific Scimed, Inc. Occlusive medical device with fabric retention barb
US10478535B2 (en) 2017-05-24 2019-11-19 Mivi Neuroscience, Inc. Suction catheter systems for applying effective aspiration in remote vessels, especially cerebral arteries
US11234723B2 (en) 2017-12-20 2022-02-01 Mivi Neuroscience, Inc. Suction catheter systems for applying effective aspiration in remote vessels, especially cerebral arteries
US11000682B2 (en) 2017-09-06 2021-05-11 Inari Medical, Inc. Hemostasis valves and methods of use
US11885051B2 (en) 2017-10-14 2024-01-30 Inceptus Medical, Llc Braiding machine and methods of use
DE102018100199A1 (en) * 2018-01-05 2019-07-11 Vm Holding Gmbh cardiac catheterization
US11154314B2 (en) 2018-01-26 2021-10-26 Inari Medical, Inc. Single insertion delivery system for treating embolism and associated systems and methods
CN112423703A (en) * 2018-03-27 2021-02-26 马杜罗探索有限责任公司 Auxiliary instrument for providing neuroprotection during interventional procedure
AU2019269606A1 (en) 2018-05-17 2020-12-03 Route 92 Medical, Inc. Aspiration catheter systems and methods of use
US11382632B2 (en) * 2018-06-27 2022-07-12 Boston Scientific Scimed, Inc. Vascular occlusion device
EP3836855A4 (en) 2018-08-13 2022-08-10 Inari Medical, Inc. System for treating embolism and associated devices and methods
EP3840670B1 (en) 2018-08-21 2023-11-15 Boston Scientific Scimed, Inc. Projecting member with barb for cardiovascular devices
US10842498B2 (en) 2018-09-13 2020-11-24 Neuravi Limited Systems and methods of restoring perfusion to a vessel
US11406416B2 (en) 2018-10-02 2022-08-09 Neuravi Limited Joint assembly for vasculature obstruction capture device
EP3880134A4 (en) * 2018-11-15 2022-07-06 Baleen Medical LLC Methods, systems, and devices for embolic protection
US20200222172A1 (en) * 2019-01-11 2020-07-16 Varun Shetty Method and system for reducing pulmonary flow
US11304792B2 (en) 2019-02-13 2022-04-19 Emboline, Inc. Catheter with integrated embolic protection device
JP2020142074A (en) 2019-03-04 2020-09-10 ニューラヴィ・リミテッド Actuated clot retrieval catheter
WO2020180866A1 (en) * 2019-03-04 2020-09-10 Boston Scientific Scimed, Inc. Systems and methods for protecting the cerebral vasculature
EP3934591A4 (en) * 2019-03-08 2022-11-23 Neovasc Tiara Inc. Retrievable prosthesis delivery system
EP3718505A1 (en) 2019-04-05 2020-10-07 Aorticlab Sarl Transcatheter anti embolic filter for arterial and venous vessels
US11077285B2 (en) 2019-06-15 2021-08-03 Maduro Discovery, Llc Catheter construction
US11707351B2 (en) 2019-08-19 2023-07-25 Encompass Technologies, Inc. Embolic protection and access system
US11540838B2 (en) 2019-08-30 2023-01-03 Boston Scientific Scimed, Inc. Left atrial appendage implant with sealing disk
EP3791815A1 (en) 2019-09-11 2021-03-17 Neuravi Limited Expandable mouth catheter
EP4044938A4 (en) 2019-10-16 2023-11-15 Inari Medical, Inc. Systems, devices, and methods for treating vascular occlusions
US11712231B2 (en) 2019-10-29 2023-08-01 Neuravi Limited Proximal locking assembly design for dual stent mechanical thrombectomy device
US11839725B2 (en) 2019-11-27 2023-12-12 Neuravi Limited Clot retrieval device with outer sheath and inner catheter
US11779364B2 (en) 2019-11-27 2023-10-10 Neuravi Limited Actuated expandable mouth thrombectomy catheter
US11517340B2 (en) 2019-12-03 2022-12-06 Neuravi Limited Stentriever devices for removing an occlusive clot from a vessel and methods thereof
US11617865B2 (en) 2020-01-24 2023-04-04 Mivi Neuroscience, Inc. Suction catheter systems with designs allowing rapid clearing of clots
US11633198B2 (en) 2020-03-05 2023-04-25 Neuravi Limited Catheter proximal joint
EP4125634A1 (en) 2020-03-24 2023-02-08 Boston Scientific Scimed Inc. Medical system for treating a left atrial appendage
US11883043B2 (en) 2020-03-31 2024-01-30 DePuy Synthes Products, Inc. Catheter funnel extension
US11759217B2 (en) 2020-04-07 2023-09-19 Neuravi Limited Catheter tubular support
US11871946B2 (en) 2020-04-17 2024-01-16 Neuravi Limited Clot retrieval device for removing clot from a blood vessel
US11717308B2 (en) 2020-04-17 2023-08-08 Neuravi Limited Clot retrieval device for removing heterogeneous clots from a blood vessel
US11730501B2 (en) 2020-04-17 2023-08-22 Neuravi Limited Floating clot retrieval device for removing clots from a blood vessel
US11737771B2 (en) 2020-06-18 2023-08-29 Neuravi Limited Dual channel thrombectomy device
US11395669B2 (en) 2020-06-23 2022-07-26 Neuravi Limited Clot retrieval device with flexible collapsible frame
US11439418B2 (en) 2020-06-23 2022-09-13 Neuravi Limited Clot retrieval device for removing clot from a blood vessel
US11864781B2 (en) 2020-09-23 2024-01-09 Neuravi Limited Rotating frame thrombectomy device
US11872354B2 (en) 2021-02-24 2024-01-16 Neuravi Limited Flexible catheter shaft frame with seam
EP4112004A1 (en) * 2021-07-01 2023-01-04 Medtronic Inc. An embolic filter
CN114271990B (en) * 2021-12-27 2022-10-14 上海傲流医疗科技有限公司 Thrombus filtering and removing net

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5102415A (en) * 1989-09-06 1992-04-07 Guenther Rolf W Apparatus for removing blood clots from arteries and veins
US5769816A (en) * 1995-11-07 1998-06-23 Embol-X, Inc. Cannula with associated filter
US5814064A (en) * 1997-03-06 1998-09-29 Scimed Life Systems, Inc. Distal protection device
US6090097A (en) * 1996-05-14 2000-07-18 Embol-X, Inc. Aortic occluder with associated filter and methods of use during cardiac surgery

Family Cites Families (33)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3996938A (en) 1975-07-10 1976-12-14 Clark Iii William T Expanding mesh catheter
US4494531A (en) 1982-12-06 1985-01-22 Cook, Incorporated Expandable blood clot filter
FR2567405B1 (en) * 1984-07-12 1988-08-12 Lefebvre Jean Marie MEDICAL FILTER
NL8502382A (en) 1985-08-30 1987-03-16 Martinus Jacobus Antonius Joha CATHETER SUITABLE FOR MULTIPLE PURPOSES.
US4650466A (en) 1985-11-01 1987-03-17 Angiobrade Partners Angioplasty device
US4710192A (en) * 1985-12-30 1987-12-01 Liotta Domingo S Diaphragm and method for occlusion of the descending thoracic aorta
US4723549A (en) 1986-09-18 1988-02-09 Wholey Mark H Method and apparatus for dilating blood vessels
US4793348A (en) 1986-11-15 1988-12-27 Palmaz Julio C Balloon expandable vena cava filter to prevent migration of lower extremity venous clots into the pulmonary circulation
US4817600A (en) 1987-05-22 1989-04-04 Medi-Tech, Inc. Implantable filter
US4873978A (en) 1987-12-04 1989-10-17 Robert Ginsburg Device and method for emboli retrieval
US5152777A (en) 1989-01-25 1992-10-06 Uresil Corporation Device and method for providing protection from emboli and preventing occulsion of blood vessels
US4969891A (en) 1989-03-06 1990-11-13 Gewertz Bruce L Removable vascular filter
US5059205A (en) 1989-09-07 1991-10-22 Boston Scientific Corporation Percutaneous anti-migration vena cava filter
US5135516A (en) * 1989-12-15 1992-08-04 Boston Scientific Corporation Lubricious antithrombogenic catheters, guidewires and coatings
FR2660189B1 (en) 1990-03-28 1992-07-31 Lefebvre Jean Marie DEVICE INTENDED TO BE IMPLANTED IN A VESSEL WITH SIDE LEGS WITH ANTAGONIST TEETH.
US5221261A (en) 1990-04-12 1993-06-22 Schneider (Usa) Inc. Radially expandable fixation member
US5275612A (en) 1990-05-10 1994-01-04 Symbiosis Corporation Insulating ferrule for disposable laparoscopic surgical instrument
US5108419A (en) 1990-08-16 1992-04-28 Evi Corporation Endovascular filter and method for use thereof
US5053008A (en) * 1990-11-21 1991-10-01 Sandeep Bajaj Intracardiac catheter
US5370647A (en) * 1991-01-23 1994-12-06 Surgical Innovations, Inc. Tissue and organ extractor
US5415630A (en) 1991-07-17 1995-05-16 Gory; Pierre Method for removably implanting a blood filter in a vein of the human body
FR2689388B1 (en) 1992-04-07 1999-07-16 Celsa Lg PERFECTIONALLY RESORBABLE BLOOD FILTER.
US5324304A (en) 1992-06-18 1994-06-28 William Cook Europe A/S Introduction catheter set for a collapsible self-expandable implant
US5452732A (en) 1994-04-26 1995-09-26 Bircoll; Mel Method of dissecting along connective tissue lines
DE69536046D1 (en) * 1994-07-08 2010-04-01 Ev3 Inc System for performing an intravascular procedure
US6013093A (en) * 1995-11-28 2000-01-11 Boston Scientific Corporation Blood clot filtering
US5549626A (en) 1994-12-23 1996-08-27 New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery Vena caval filter
DE19509464C1 (en) * 1995-03-20 1996-06-27 Horst J Dr Med Jaeger Implant for artery or vein, with anchor piece fixed to wall of vessel
US5695519A (en) * 1995-11-30 1997-12-09 American Biomed, Inc. Percutaneous filter for carotid angioplasty
US5935139A (en) * 1996-05-03 1999-08-10 Boston Scientific Corporation System for immobilizing or manipulating an object in a tract
US5662671A (en) 1996-07-17 1997-09-02 Embol-X, Inc. Atherectomy device having trapping and excising means for removal of plaque from the aorta and other arteries
US5876367A (en) 1996-12-05 1999-03-02 Embol-X, Inc. Cerebral protection during carotid endarterectomy and downstream vascular protection during other surgeries
US5846260A (en) 1997-05-08 1998-12-08 Embol-X, Inc. Cannula with a modular filter for filtering embolic material

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5102415A (en) * 1989-09-06 1992-04-07 Guenther Rolf W Apparatus for removing blood clots from arteries and veins
US5769816A (en) * 1995-11-07 1998-06-23 Embol-X, Inc. Cannula with associated filter
US6090097A (en) * 1996-05-14 2000-07-18 Embol-X, Inc. Aortic occluder with associated filter and methods of use during cardiac surgery
US6592546B1 (en) * 1996-05-14 2003-07-15 Edwards Lifesciences Corp. Aortic occluder with associated filter and methods of use during cardiac surgery
US5814064A (en) * 1997-03-06 1998-09-29 Scimed Life Systems, Inc. Distal protection device

Cited By (568)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10485976B2 (en) 1998-04-30 2019-11-26 Medtronic, Inc. Intracardiovascular access (ICVA™) system
US9119706B2 (en) 1999-02-24 2015-09-01 Boston Scientific Scimed Inc. Intravascular filter and method
US7618433B2 (en) * 1999-02-24 2009-11-17 Boston Scientific Scimed, Inc. Intravascular filter and method
US8657873B2 (en) 1999-08-09 2014-02-25 Cardiokinetix, Inc. System for improving cardiac function
US8377114B2 (en) 1999-08-09 2013-02-19 Cardiokinetix, Inc. Sealing and filling ventricular partitioning devices to improve cardiac function
US8388672B2 (en) 1999-08-09 2013-03-05 Cardiokinetix, Inc. System for improving cardiac function by sealing a partitioning membrane within a ventricle
US7887477B2 (en) 1999-08-09 2011-02-15 Cardiokinetix, Inc. Method of improving cardiac function using a porous membrane
US8257428B2 (en) 1999-08-09 2012-09-04 Cardiokinetix, Inc. System for improving cardiac function
US8500790B2 (en) 1999-08-09 2013-08-06 Cardiokinetix, Inc. Retrievable cardiac devices
US8747454B2 (en) 1999-08-09 2014-06-10 Cardiokinetix, Inc. System for improving cardiac function
US9694121B2 (en) 1999-08-09 2017-07-04 Cardiokinetix, Inc. Systems and methods for improving cardiac function
US20030050685A1 (en) * 1999-08-09 2003-03-13 Nikolic Serjan D. Method for improving cardiac function
US8246671B2 (en) 1999-08-09 2012-08-21 Cardiokinetix, Inc. Retrievable cardiac devices
US10307253B2 (en) 1999-08-09 2019-06-04 Edwards Lifesciences Corporation System for improving cardiac function by sealing a partitioning membrane within a ventricle
US7279007B2 (en) 1999-08-09 2007-10-09 Cardioklnetix, Inc. Method for improving cardiac function
US7303526B2 (en) 1999-08-09 2007-12-04 Cardiokinetix, Inc. Device for improving cardiac function
US10307147B2 (en) 1999-08-09 2019-06-04 Edwards Lifesciences Corporation System for improving cardiac function by sealing a partitioning membrane within a ventricle
US7674222B2 (en) 1999-08-09 2010-03-09 Cardiokinetix, Inc. Cardiac device and methods of use thereof
US9017394B2 (en) 1999-08-09 2015-04-28 Cardiokinetix, Inc. Retrievable cardiac devices
US9872767B2 (en) 1999-08-09 2018-01-23 Edwards Lifesciences Corporation Retrievable cardiac devices
US8192478B2 (en) 1999-08-09 2012-06-05 Cardiokinetix, Inc. System for improving cardiac function
US8672827B2 (en) 1999-08-09 2014-03-18 Cardiokinetix, Inc. Cardiac device and methods of use thereof
US8500795B2 (en) 1999-08-09 2013-08-06 Cardiokinetix, Inc. Retrievable devices for improving cardiac function
US8986329B2 (en) 1999-11-17 2015-03-24 Medtronic Corevalve Llc Methods for transluminal delivery of prosthetic valves
US8801779B2 (en) 1999-11-17 2014-08-12 Medtronic Corevalve, Llc Prosthetic valve for transluminal delivery
US7892281B2 (en) 1999-11-17 2011-02-22 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US9060856B2 (en) 1999-11-17 2015-06-23 Medtronic Corevalve Llc Transcatheter heart valves
US8998979B2 (en) 1999-11-17 2015-04-07 Medtronic Corevalve Llc Transcatheter heart valves
US9066799B2 (en) 1999-11-17 2015-06-30 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US10219901B2 (en) 1999-11-17 2019-03-05 Medtronic CV Luxembourg S.a.r.l. Prosthetic valve for transluminal delivery
US8721708B2 (en) 1999-11-17 2014-05-13 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8579966B2 (en) 1999-11-17 2013-11-12 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8603159B2 (en) 1999-11-17 2013-12-10 Medtronic Corevalve, Llc Prosthetic valve for transluminal delivery
US8876896B2 (en) 1999-11-17 2014-11-04 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8016877B2 (en) 1999-11-17 2011-09-13 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US9962258B2 (en) 1999-11-17 2018-05-08 Medtronic CV Luxembourg S.a.r.l. Transcatheter heart valves
US10335280B2 (en) 2000-01-19 2019-07-02 Medtronic, Inc. Method for ablating target tissue of a patient
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US9949831B2 (en) 2000-01-19 2018-04-24 Medtronics, Inc. Image-guided heart valve placement
US7758606B2 (en) 2000-06-30 2010-07-20 Medtronic, Inc. Intravascular filter with debris entrapment mechanism
US8777980B2 (en) 2000-06-30 2014-07-15 Medtronic, Inc. Intravascular filter with debris entrapment mechanism
US8092487B2 (en) 2000-06-30 2012-01-10 Medtronic, Inc. Intravascular filter with debris entrapment mechanism
US9078660B2 (en) 2000-08-09 2015-07-14 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US10064696B2 (en) 2000-08-09 2018-09-04 Edwards Lifesciences Corporation Devices and methods for delivering an endocardial device
US10278805B2 (en) 2000-08-18 2019-05-07 Atritech, Inc. Expandable implant devices for filtering blood flow from atrial appendages
US8951280B2 (en) 2000-11-09 2015-02-10 Medtronic, Inc. Cardiac valve procedure methods and devices
US8771302B2 (en) 2001-06-29 2014-07-08 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US8623077B2 (en) 2001-06-29 2014-01-07 Medtronic, Inc. Apparatus for replacing a cardiac valve
US8070801B2 (en) 2001-06-29 2011-12-06 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US8956402B2 (en) 2001-06-29 2015-02-17 Medtronic, Inc. Apparatus for replacing a cardiac valve
US8002826B2 (en) 2001-07-04 2011-08-23 Medtronic Corevalve Llc Assembly for placing a prosthetic valve in a duct in the body
US8628570B2 (en) 2001-07-04 2014-01-14 Medtronic Corevalve Llc Assembly for placing a prosthetic valve in a duct in the body
US9149357B2 (en) 2001-07-04 2015-10-06 Medtronic CV Luxembourg S.a.r.l. Heart valve assemblies
US7780726B2 (en) 2001-07-04 2010-08-24 Medtronic, Inc. Assembly for placing a prosthetic valve in a duct in the body
US7682390B2 (en) 2001-07-31 2010-03-23 Medtronic, Inc. Assembly for setting a valve prosthesis in a corporeal duct
US9539088B2 (en) 2001-09-07 2017-01-10 Medtronic, Inc. Fixation band for affixing a prosthetic heart valve to tissue
US10342657B2 (en) 2001-09-07 2019-07-09 Medtronic, Inc. Fixation band for affixing a prosthetic heart valve to tissue
US20100042136A1 (en) * 2002-03-12 2010-02-18 Ev3 Inc. Everted filter device
US8956384B2 (en) 2002-03-12 2015-02-17 Covidien Lp Everted filter device
US9468514B2 (en) 2002-03-12 2016-10-18 Covidien Lp Everted filter device
US8092486B2 (en) 2002-03-12 2012-01-10 Tyco Healthcare Group Lp Everted filter device
US7621870B2 (en) 2002-03-12 2009-11-24 Ev3 Inc. Everted filter device
US8858619B2 (en) 2002-04-23 2014-10-14 Medtronic, Inc. System and method for implanting a replacement valve
US8529430B2 (en) 2002-08-01 2013-09-10 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US7862500B2 (en) 2002-08-01 2011-01-04 Cardiokinetix, Inc. Multiple partitioning devices for heart treatment
US8827892B2 (en) 2002-08-01 2014-09-09 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US9592123B2 (en) 2002-08-01 2017-03-14 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US7323001B2 (en) 2003-01-30 2008-01-29 Ev3 Inc. Embolic filters with controlled pore size
US7220271B2 (en) 2003-01-30 2007-05-22 Ev3 Inc. Embolic filters having multiple layers and controlled pore size
US8137376B2 (en) 2003-01-30 2012-03-20 Tyco Healthcare Group Lp Embolic filters having multiple layers and controlled pore size
US9603692B2 (en) 2003-01-30 2017-03-28 Covidien Lp Embolic filters with controlled pore size
US9011478B2 (en) 2003-01-30 2015-04-21 Covidien Lp Embolic filters with a distal loop or no loop
US20070135834A1 (en) * 2003-01-30 2007-06-14 Ev3 Inc. Embolic filters with controlled pore size
US8409242B2 (en) 2003-01-30 2013-04-02 Covidien Lp Embolic filters with controlled pore size
US20070083076A1 (en) * 2003-07-16 2007-04-12 Samuel Lichtenstein Methods and devices for altering blood flow through the left ventricle
US7513867B2 (en) 2003-07-16 2009-04-07 Kardium, Inc. Methods and devices for altering blood flow through the left ventricle
US20050015109A1 (en) * 2003-07-16 2005-01-20 Samuel Lichtenstein Methods and devices for altering blood flow through the left ventricle
US20050119688A1 (en) * 2003-10-06 2005-06-02 Bjarne Bergheim Method and assembly for distal embolic protection
US9144485B2 (en) 2003-10-06 2015-09-29 Medtronic 3F Therapeutics, Inc. Method and assembly for distal embolic protection
US8430902B2 (en) 2003-10-06 2013-04-30 Medtronic 3F Therapeutics, Inc. Method and assembly for distal embolic protection
US9579194B2 (en) 2003-10-06 2017-02-28 Medtronic ATS Medical, Inc. Anchoring structure with concave landing zone
US20100036474A1 (en) * 2003-10-06 2010-02-11 3F Therapeutics, Inc. Method and assembly for distal embolic protection
US7604650B2 (en) * 2003-10-06 2009-10-20 3F Therapeutics, Inc. Method and assembly for distal embolic protection
US20050143810A1 (en) * 2003-10-24 2005-06-30 Martin Dauner Cardiovascular implant, method and device for its production, and its provision for surgery
EP1527740A1 (en) * 2003-10-29 2005-05-04 Medtronic Vascular, Inc. Distal protection device for filtering and occlusion
US8894703B2 (en) 2003-12-23 2014-11-25 Sadra Medical, Inc. Systems and methods for delivering a medical implant
US7988724B2 (en) 2003-12-23 2011-08-02 Sadra Medical, Inc. Systems and methods for delivering a medical implant
US9956075B2 (en) 2003-12-23 2018-05-01 Boston Scientific Scimed Inc. Methods and apparatus for endovascularly replacing a heart valve
US11278398B2 (en) 2003-12-23 2022-03-22 Boston Scientific Scimed, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8182528B2 (en) 2003-12-23 2012-05-22 Sadra Medical, Inc. Locking heart valve anchor
US10206774B2 (en) 2003-12-23 2019-02-19 Boston Scientific Scimed Inc. Low profile heart valve and delivery system
US9872768B2 (en) 2003-12-23 2018-01-23 Boston Scientific Scimed, Inc. Medical devices and delivery systems for delivering medical devices
US10478289B2 (en) 2003-12-23 2019-11-19 Boston Scientific Scimed, Inc. Replacement valve and anchor
US9011521B2 (en) 2003-12-23 2015-04-21 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US8840662B2 (en) 2003-12-23 2014-09-23 Sadra Medical, Inc. Repositionable heart valve and method
US11696825B2 (en) 2003-12-23 2023-07-11 Boston Scientific Scimed, Inc. Replacement valve and anchor
US9861476B2 (en) 2003-12-23 2018-01-09 Boston Scientific Scimed Inc. Leaflet engagement elements and methods for use thereof
US10258465B2 (en) 2003-12-23 2019-04-16 Boston Scientific Scimed Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8231670B2 (en) 2003-12-23 2012-07-31 Sadra Medical, Inc. Repositionable heart valve and method
US11185408B2 (en) 2003-12-23 2021-11-30 Boston Scientific Scimed, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US10925724B2 (en) 2003-12-23 2021-02-23 Boston Scientific Scimed, Inc. Replacement valve and anchor
US8246678B2 (en) 2003-12-23 2012-08-21 Sadra Medicl, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US10772724B2 (en) 2003-12-23 2020-09-15 Boston Scientific Scimed, Inc. Medical devices and delivery systems for delivering medical devices
US8252052B2 (en) 2003-12-23 2012-08-28 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US7748389B2 (en) 2003-12-23 2010-07-06 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US8858620B2 (en) 2003-12-23 2014-10-14 Sadra Medical Inc. Methods and apparatus for endovascularly replacing a heart valve
US8828078B2 (en) 2003-12-23 2014-09-09 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8052749B2 (en) 2003-12-23 2011-11-08 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8048153B2 (en) 2003-12-23 2011-11-01 Sadra Medical, Inc. Low profile heart valve and delivery system
US9585749B2 (en) 2003-12-23 2017-03-07 Boston Scientific Scimed, Inc. Replacement heart valve assembly
US9585750B2 (en) 2003-12-23 2017-03-07 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US10716663B2 (en) 2003-12-23 2020-07-21 Boston Scientific Scimed, Inc. Methods and apparatus for performing valvuloplasty
US11285002B2 (en) 2003-12-23 2022-03-29 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a heart valve
US8343213B2 (en) 2003-12-23 2013-01-01 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US9005273B2 (en) 2003-12-23 2015-04-14 Sadra Medical, Inc. Assessing the location and performance of replacement heart valves
US9532872B2 (en) 2003-12-23 2017-01-03 Boston Scientific Scimed, Inc. Systems and methods for delivering a medical implant
US8579962B2 (en) 2003-12-23 2013-11-12 Sadra Medical, Inc. Methods and apparatus for performing valvuloplasty
US9526609B2 (en) 2003-12-23 2016-12-27 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US10314695B2 (en) 2003-12-23 2019-06-11 Boston Scientific Scimed Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8840663B2 (en) 2003-12-23 2014-09-23 Sadra Medical, Inc. Repositionable heart valve method
US7959666B2 (en) 2003-12-23 2011-06-14 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US7959672B2 (en) 2003-12-23 2011-06-14 Sadra Medical Replacement valve and anchor
US10335273B2 (en) 2003-12-23 2019-07-02 Boston Scientific Scimed Inc. Leaflet engagement elements and methods for use thereof
US8623078B2 (en) 2003-12-23 2014-01-07 Sadra Medical, Inc. Replacement valve and anchor
US8623076B2 (en) 2003-12-23 2014-01-07 Sadra Medical, Inc. Low profile heart valve and delivery system
US8951299B2 (en) 2003-12-23 2015-02-10 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US9393113B2 (en) 2003-12-23 2016-07-19 Boston Scientific Scimed Inc. Retrievable heart valve anchor and method
US9387076B2 (en) 2003-12-23 2016-07-12 Boston Scientific Scimed Inc. Medical devices and delivery systems for delivering medical devices
US9358106B2 (en) 2003-12-23 2016-06-07 Boston Scientific Scimed Inc. Methods and apparatus for performing valvuloplasty
US10357359B2 (en) 2003-12-23 2019-07-23 Boston Scientific Scimed Inc Methods and apparatus for endovascularly replacing a patient's heart valve
US9358110B2 (en) 2003-12-23 2016-06-07 Boston Scientific Scimed, Inc. Medical devices and delivery systems for delivering medical devices
US9277991B2 (en) 2003-12-23 2016-03-08 Boston Scientific Scimed, Inc. Low profile heart valve and delivery system
US7824443B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Medical implant delivery and deployment tool
US7824442B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US10413412B2 (en) 2003-12-23 2019-09-17 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a heart valve
US9320599B2 (en) 2003-12-23 2016-04-26 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a heart valve
US9308085B2 (en) 2003-12-23 2016-04-12 Boston Scientific Scimed, Inc. Repositionable heart valve and method
US10413409B2 (en) 2003-12-23 2019-09-17 Boston Scientific Scimed, Inc. Systems and methods for delivering a medical implant
US8603160B2 (en) 2003-12-23 2013-12-10 Sadra Medical, Inc. Method of using a retrievable heart valve anchor with a sheath
US10426608B2 (en) 2003-12-23 2019-10-01 Boston Scientific Scimed, Inc. Repositionable heart valve
US9867695B2 (en) 2004-03-03 2018-01-16 Sorin Group Italia S.R.L. Minimally-invasive cardiac-valve prosthesis
US8535373B2 (en) 2004-03-03 2013-09-17 Sorin Group Italia S.R.L. Minimally-invasive cardiac-valve prosthesis
US7976455B2 (en) 2004-03-03 2011-07-12 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US8109996B2 (en) 2004-03-03 2012-02-07 Sorin Biomedica Cardio, S.R.L. Minimally-invasive cardiac-valve prosthesis
US7762943B2 (en) * 2004-03-03 2010-07-27 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US20050240200A1 (en) * 2004-04-23 2005-10-27 Bjarne Bergheim Method and system for cardiac valve delivery
US9775704B2 (en) 2004-04-23 2017-10-03 Medtronic3F Therapeutics, Inc. Implantable valve prosthesis
US10219899B2 (en) 2004-04-23 2019-03-05 Medtronic 3F Therapeutics, Inc. Cardiac valve replacement systems
US11484405B2 (en) 2004-06-16 2022-11-01 Boston Scientific Scimed, Inc. Everting heart valve
US7780725B2 (en) 2004-06-16 2010-08-24 Sadra Medical, Inc. Everting heart valve
US9744035B2 (en) 2004-06-16 2017-08-29 Boston Scientific Scimed, Inc. Everting heart valve
US8992608B2 (en) 2004-06-16 2015-03-31 Sadra Medical, Inc. Everting heart valve
US8668733B2 (en) 2004-06-16 2014-03-11 Sadra Medical, Inc. Everting heart valve
US20060020285A1 (en) * 2004-07-22 2006-01-26 Volker Niermann Method for filtering blood in a vessel with helical elements
US20060020286A1 (en) * 2004-07-22 2006-01-26 Volker Niermann Device for filtering blood in a vessel with helical elements
AU2005203022B2 (en) * 2004-07-22 2012-03-01 Cardinal Health 529, Llc Method for filtering blood in a vessel with helical elements
US9332993B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US7897086B2 (en) 2004-08-05 2011-03-01 Cardiokinetix, Inc. Method of making a laminar ventricular partitioning device
US9332992B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Method for making a laminar ventricular partitioning device
US7765670B2 (en) * 2004-08-13 2010-08-03 Boston Scientific Scimed, Inc. Method to simultaneously load and cover self expanding stents
US20060036310A1 (en) * 2004-08-13 2006-02-16 Scimed Life Systems, Inc. Method to simultaneously load and cover self expanding stents
US8545418B2 (en) 2004-08-25 2013-10-01 Richard R. Heuser Systems and methods for ablation of occlusions within blood vessels
US8591570B2 (en) 2004-09-07 2013-11-26 Medtronic, Inc. Prosthetic heart valve for replacing previously implanted heart valve
US8795315B2 (en) 2004-10-06 2014-08-05 Cook Medical Technologies Llc Emboli capturing device having a coil and method for capturing emboli
US8617236B2 (en) * 2004-11-05 2013-12-31 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US20120046740A1 (en) * 2004-11-05 2012-02-23 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US10531952B2 (en) 2004-11-05 2020-01-14 Boston Scientific Scimed, Inc. Medical devices and delivery systems for delivering medical devices
US8328868B2 (en) 2004-11-05 2012-12-11 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US9498329B2 (en) 2004-11-19 2016-11-22 Medtronic, Inc. Apparatus for treatment of cardiac valves and method of its manufacture
US8562672B2 (en) 2004-11-19 2013-10-22 Medtronic, Inc. Apparatus for treatment of cardiac valves and method of its manufacture
US11517431B2 (en) 2005-01-20 2022-12-06 Jenavalve Technology, Inc. Catheter system for implantation of prosthetic heart valves
US9486313B2 (en) 2005-02-10 2016-11-08 Sorin Group Italia S.R.L. Cardiac valve prosthesis
US8540768B2 (en) 2005-02-10 2013-09-24 Sorin Group Italia S.R.L. Cardiac valve prosthesis
US9895223B2 (en) 2005-02-10 2018-02-20 Sorin Group Italia S.R.L. Cardiac valve prosthesis
US8539662B2 (en) 2005-02-10 2013-09-24 Sorin Group Italia S.R.L. Cardiac-valve prosthesis
US8920492B2 (en) 2005-02-10 2014-12-30 Sorin Group Italia S.R.L. Cardiac valve prosthesis
US9456889B2 (en) 2005-02-18 2016-10-04 Covidien Lp Rapid exchange catheters and embolic protection devices
US7955351B2 (en) 2005-02-18 2011-06-07 Tyco Healthcare Group Lp Rapid exchange catheters and embolic protection devices
US10537418B2 (en) 2005-02-18 2020-01-21 Covidien Lp Rapid exchange catheters and embolic protection devices
US8221446B2 (en) 2005-03-15 2012-07-17 Cook Medical Technologies Embolic protection device
US8945169B2 (en) 2005-03-15 2015-02-03 Cook Medical Technologies Llc Embolic protection device
US20060253023A1 (en) * 2005-04-20 2006-11-09 Scimed Life Systems, Inc. Neurovascular intervention device
US8467854B2 (en) * 2005-04-20 2013-06-18 Scimed Life Systems, Inc. Neurovascular intervention device
US9649495B2 (en) 2005-04-25 2017-05-16 Cardiac Pacemakers, Inc. Method and apparatus for pacing during revascularization
US10549101B2 (en) 2005-04-25 2020-02-04 Cardiac Pacemakers, Inc. Method and apparatus for pacing during revascularization
US9415225B2 (en) 2005-04-25 2016-08-16 Cardiac Pacemakers, Inc. Method and apparatus for pacing during revascularization
US7935075B2 (en) * 2005-04-26 2011-05-03 Cardiac Pacemakers, Inc. Self-deploying vascular occlusion device
US20060241735A1 (en) * 2005-04-26 2006-10-26 Cardiac Pacemakers, Inc. Self-deploying vascular occlusion device
US20110184282A1 (en) * 2005-04-26 2011-07-28 Tockman Bruce A Self-deploying vascular occlusion device
US10478291B2 (en) 2005-05-13 2019-11-19 Medtronic CV Luxembourg S.a.r.l Heart valve prosthesis and methods of manufacture and use
US7914569B2 (en) 2005-05-13 2011-03-29 Medtronics Corevalve Llc Heart valve prosthesis and methods of manufacture and use
US11284997B2 (en) 2005-05-13 2022-03-29 Medtronic CV Luxembourg S.a.r.l Heart valve prosthesis and methods of manufacture and use
US8226710B2 (en) 2005-05-13 2012-07-24 Medtronic Corevalve, Inc. Heart valve prosthesis and methods of manufacture and use
US9060857B2 (en) 2005-05-13 2015-06-23 Medtronic Corevalve Llc Heart valve prosthesis and methods of manufacture and use
USD732666S1 (en) 2005-05-13 2015-06-23 Medtronic Corevalve, Inc. Heart valve prosthesis
US9504564B2 (en) 2005-05-13 2016-11-29 Medtronic Corevalve Llc Heart valve prosthesis and methods of manufacture and use
USD812226S1 (en) 2005-05-13 2018-03-06 Medtronic Corevalve Llc Heart valve prosthesis
US8398537B2 (en) 2005-06-10 2013-03-19 Cardiokinetix, Inc. Peripheral seal for a ventricular partitioning device
US8109962B2 (en) 2005-06-20 2012-02-07 Cook Medical Technologies Llc Retrievable device having a reticulation portion with staggered struts
US8845677B2 (en) 2005-06-20 2014-09-30 Cook Medical Technologies Llc Retrievable device having a reticulation portion with staggered struts
US7850708B2 (en) 2005-06-20 2010-12-14 Cook Incorporated Embolic protection device having a reticulated body with staggered struts
US7867247B2 (en) 2005-07-12 2011-01-11 Cook Incorporated Methods for embolic protection during treatment of a stenotic lesion in a body vessel
US7771452B2 (en) 2005-07-12 2010-08-10 Cook Incorporated Embolic protection device with a filter bag that disengages from a basket
US7766934B2 (en) 2005-07-12 2010-08-03 Cook Incorporated Embolic protection device with an integral basket and bag
US8187298B2 (en) 2005-08-04 2012-05-29 Cook Medical Technologies Llc Embolic protection device having inflatable frame
US7712606B2 (en) 2005-09-13 2010-05-11 Sadra Medical, Inc. Two-part package for medical implant
US8136659B2 (en) 2005-09-13 2012-03-20 Sadra Medical, Inc. Two-part package for medical implant
US9393094B2 (en) 2005-09-13 2016-07-19 Boston Scientific Scimed, Inc. Two-part package for medical implant
US10370150B2 (en) 2005-09-13 2019-08-06 Boston Scientific Scimed Inc. Two-part package for medical implant
US8377092B2 (en) 2005-09-16 2013-02-19 Cook Medical Technologies Llc Embolic protection device
US8506620B2 (en) 2005-09-26 2013-08-13 Medtronic, Inc. Prosthetic cardiac and venous valves
US8632562B2 (en) 2005-10-03 2014-01-21 Cook Medical Technologies Llc Embolic protection device
US8182508B2 (en) 2005-10-04 2012-05-22 Cook Medical Technologies Llc Embolic protection device
US8252017B2 (en) 2005-10-18 2012-08-28 Cook Medical Technologies Llc Invertible filter for embolic protection
US8216269B2 (en) 2005-11-02 2012-07-10 Cook Medical Technologies Llc Embolic protection device having reduced profile
US8287584B2 (en) 2005-11-14 2012-10-16 Sadra Medical, Inc. Medical implant deployment tool
US8152831B2 (en) 2005-11-17 2012-04-10 Cook Medical Technologies Llc Foam embolic protection device
US10314701B2 (en) 2005-12-22 2019-06-11 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
US10299922B2 (en) 2005-12-22 2019-05-28 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
US9078781B2 (en) 2006-01-11 2015-07-14 Medtronic, Inc. Sterile cover for compressible stents used in percutaneous device delivery systems
US9572557B2 (en) 2006-02-21 2017-02-21 Kardium Inc. Method and device for closing holes in tissue
US8337524B2 (en) 2006-02-21 2012-12-25 Kardium Inc. Method and device for closing holes in tissue
US7749249B2 (en) 2006-02-21 2010-07-06 Kardium Inc. Method and device for closing holes in tissue
US10058421B2 (en) 2006-03-28 2018-08-28 Medtronic, Inc. Prosthetic cardiac valve formed from pericardium material and methods of making same
US9331328B2 (en) 2006-03-28 2016-05-03 Medtronic, Inc. Prosthetic cardiac valve from pericardium material and methods of making same
US8075615B2 (en) 2006-03-28 2011-12-13 Medtronic, Inc. Prosthetic cardiac valve formed from pericardium material and methods of making same
US20080275485A1 (en) * 2006-04-03 2008-11-06 Possis Medical, Inc. Guidewire with collapsible filter system and method of use
US7846175B2 (en) 2006-04-03 2010-12-07 Medrad, Inc. Guidewire and collapsable filter system
US7740655B2 (en) 2006-04-06 2010-06-22 Medtronic Vascular, Inc. Reinforced surgical conduit for implantation of a stented valve therein
US9192468B2 (en) 2006-06-28 2015-11-24 Kardium Inc. Method for anchoring a mitral valve
US8449605B2 (en) 2006-06-28 2013-05-28 Kardium Inc. Method for anchoring a mitral valve
US8672998B2 (en) 2006-06-28 2014-03-18 Kardium Inc. Method for anchoring a mitral valve
US11033392B2 (en) 2006-08-02 2021-06-15 Kardium Inc. System for improving diastolic dysfunction
US7837610B2 (en) 2006-08-02 2010-11-23 Kardium Inc. System for improving diastolic dysfunction
US8226728B2 (en) * 2006-08-04 2012-07-24 Ceramtec Gmbh Insertion of vibration-damping elements in prosthetic systems for the manipulation and damping of natural frequencies
US20090326669A1 (en) * 2006-08-04 2009-12-31 Roman Preuss Insertion of vibration-damping elements in prosthetic systems for the manipulation and damping of natural frequencies
US8460335B2 (en) 2006-09-11 2013-06-11 Embrella Cardiovascular, Inc. Method of deflecting emboli from the cerebral circulation
US9480548B2 (en) 2006-09-11 2016-11-01 Edwards Lifesciences Ag Embolic protection device and method of use
US20100179585A1 (en) * 2006-09-11 2010-07-15 Carpenter Judith T Embolic deflection device
US9339367B2 (en) * 2006-09-11 2016-05-17 Edwards Lifesciences Ag Embolic deflection device
US10426591B2 (en) 2006-09-11 2019-10-01 Edwards Lifesciences Ag Embolic deflection device
US20080065145A1 (en) * 2006-09-11 2008-03-13 Carpenter Judith T Embolic protection device and method of use
US20100179583A1 (en) * 2006-09-11 2010-07-15 Carpenter Judith T Methods of deploying and retrieving an embolic diversion device
US20100179647A1 (en) * 2006-09-11 2010-07-15 Carpenter Judith T Methods of reducing embolism to cerebral circulation as a consequence of an index cardiac procedure
US10004601B2 (en) 2006-09-19 2018-06-26 Medtronic Ventor Technologies Ltd. Valve prosthesis fixation techniques using sandwiching
US9913714B2 (en) 2006-09-19 2018-03-13 Medtronic, Inc. Sinus-engaging valve fixation member
US9138312B2 (en) 2006-09-19 2015-09-22 Medtronic Ventor Technologies Ltd. Valve prostheses
US8052750B2 (en) 2006-09-19 2011-11-08 Medtronic Ventor Technologies Ltd Valve prosthesis fixation techniques using sandwiching
US10543077B2 (en) 2006-09-19 2020-01-28 Medtronic, Inc. Sinus-engaging valve fixation member
US8834564B2 (en) 2006-09-19 2014-09-16 Medtronic, Inc. Sinus-engaging valve fixation member
US8771345B2 (en) 2006-09-19 2014-07-08 Medtronic Ventor Technologies Ltd. Valve prosthesis fixation techniques using sandwiching
US8771346B2 (en) 2006-09-19 2014-07-08 Medtronic Ventor Technologies Ltd. Valve prosthetic fixation techniques using sandwiching
US9827097B2 (en) 2006-09-19 2017-11-28 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US9387071B2 (en) 2006-09-19 2016-07-12 Medtronic, Inc. Sinus-engaging valve fixation member
US11304802B2 (en) 2006-09-19 2022-04-19 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US10195033B2 (en) 2006-09-19 2019-02-05 Medtronic Ventor Technologies Ltd. Valve prosthesis fixation techniques using sandwiching
US8414643B2 (en) 2006-09-19 2013-04-09 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US8348995B2 (en) 2006-09-19 2013-01-08 Medtronic Ventor Technologies, Ltd. Axial-force fixation member for valve
US8348996B2 (en) 2006-09-19 2013-01-08 Medtronic Ventor Technologies Ltd. Valve prosthesis implantation techniques
US9642704B2 (en) 2006-09-19 2017-05-09 Medtronic Ventor Technologies Ltd. Catheter for implanting a valve prosthesis
US8876894B2 (en) 2006-09-19 2014-11-04 Medtronic Ventor Technologies Ltd. Leaflet-sensitive valve fixation member
US8876895B2 (en) 2006-09-19 2014-11-04 Medtronic Ventor Technologies Ltd. Valve fixation member having engagement arms
US8747460B2 (en) 2006-09-19 2014-06-10 Medtronic Ventor Technologies Ltd. Methods for implanting a valve prothesis
US9907639B2 (en) 2006-09-19 2018-03-06 Cook Medical Technologies Llc Apparatus and methods for in situ embolic protection
US9301834B2 (en) 2006-09-19 2016-04-05 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US11304801B2 (en) 2006-09-19 2022-04-19 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US11304800B2 (en) 2006-09-19 2022-04-19 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US8784478B2 (en) 2006-10-16 2014-07-22 Medtronic Corevalve, Inc. Transapical delivery system with ventruculo-arterial overlfow bypass
US8747459B2 (en) 2006-12-06 2014-06-10 Medtronic Corevalve Llc System and method for transapical delivery of an annulus anchored self-expanding valve
US9295550B2 (en) 2006-12-06 2016-03-29 Medtronic CV Luxembourg S.a.r.l. Methods for delivering a self-expanding valve
US7871436B2 (en) 2007-02-16 2011-01-18 Medtronic, Inc. Replacement prosthetic heart valves and methods of implantation
US9504568B2 (en) 2007-02-16 2016-11-29 Medtronic, Inc. Replacement prosthetic heart valves and methods of implantation
US9901434B2 (en) 2007-02-27 2018-02-27 Cook Medical Technologies Llc Embolic protection device including a Z-stent waist band
US11357624B2 (en) 2007-04-13 2022-06-14 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
US9585754B2 (en) 2007-04-20 2017-03-07 Medtronic, Inc. Implant for treatment of a heart valve, in particular a mitral valve, material including such an implant, and material for insertion thereof
US9237886B2 (en) 2007-04-20 2016-01-19 Medtronic, Inc. Implant for treatment of a heart valve, in particular a mitral valve, material including such an implant, and material for insertion thereof
US10188516B2 (en) 2007-08-20 2019-01-29 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
US8747458B2 (en) 2007-08-20 2014-06-10 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
US9393112B2 (en) 2007-08-20 2016-07-19 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
US8252018B2 (en) 2007-09-14 2012-08-28 Cook Medical Technologies Llc Helical embolic protection device
US8419748B2 (en) 2007-09-14 2013-04-16 Cook Medical Technologies Llc Helical thrombus removal device
US9398946B2 (en) 2007-09-14 2016-07-26 Cook Medical Technologies Llc Expandable device for treatment of a stricture in a body vessel
US9138307B2 (en) 2007-09-14 2015-09-22 Cook Medical Technologies Llc Expandable device for treatment of a stricture in a body vessel
US10856970B2 (en) 2007-10-10 2020-12-08 Medtronic Ventor Technologies Ltd. Prosthetic heart valve for transfemoral delivery
US10966823B2 (en) 2007-10-12 2021-04-06 Sorin Group Italia S.R.L. Expandable valve prosthesis with sealing mechanism
US9848981B2 (en) 2007-10-12 2017-12-26 Mayo Foundation For Medical Education And Research Expandable valve prosthesis with sealing mechanism
US10639182B2 (en) 2008-01-24 2020-05-05 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US10820993B2 (en) 2008-01-24 2020-11-03 Medtronic, Inc. Stents for prosthetic heart valves
US9393115B2 (en) 2008-01-24 2016-07-19 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US11607311B2 (en) 2008-01-24 2023-03-21 Medtronic, Inc. Stents for prosthetic heart valves
US10016274B2 (en) 2008-01-24 2018-07-10 Medtronic, Inc. Stent for prosthetic heart valves
US9339382B2 (en) 2008-01-24 2016-05-17 Medtronic, Inc. Stents for prosthetic heart valves
US9333100B2 (en) 2008-01-24 2016-05-10 Medtronic, Inc. Stents for prosthetic heart valves
US10646335B2 (en) 2008-01-24 2020-05-12 Medtronic, Inc. Stents for prosthetic heart valves
US8157853B2 (en) 2008-01-24 2012-04-17 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US8157852B2 (en) 2008-01-24 2012-04-17 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US9089422B2 (en) 2008-01-24 2015-07-28 Medtronic, Inc. Markers for prosthetic heart valves
US9925079B2 (en) 2008-01-24 2018-03-27 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US11284999B2 (en) 2008-01-24 2022-03-29 Medtronic, Inc. Stents for prosthetic heart valves
US11083573B2 (en) 2008-01-24 2021-08-10 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US8685077B2 (en) 2008-01-24 2014-04-01 Medtronics, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US8673000B2 (en) 2008-01-24 2014-03-18 Medtronic, Inc. Stents for prosthetic heart valves
US10758343B2 (en) 2008-01-24 2020-09-01 Medtronic, Inc. Stent for prosthetic heart valves
US7972378B2 (en) 2008-01-24 2011-07-05 Medtronic, Inc. Stents for prosthetic heart valves
US11259919B2 (en) 2008-01-24 2022-03-01 Medtronic, Inc. Stents for prosthetic heart valves
US11786367B2 (en) 2008-01-24 2023-10-17 Medtronic, Inc. Stents for prosthetic heart valves
US9149358B2 (en) 2008-01-24 2015-10-06 Medtronic, Inc. Delivery systems for prosthetic heart valves
US8628566B2 (en) 2008-01-24 2014-01-14 Medtronic, Inc. Stents for prosthetic heart valves
US10993805B2 (en) 2008-02-26 2021-05-04 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US11564794B2 (en) 2008-02-26 2023-01-31 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US11154398B2 (en) 2008-02-26 2021-10-26 JenaValve Technology. Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US8961593B2 (en) 2008-02-28 2015-02-24 Medtronic, Inc. Prosthetic heart valve systems
US8613765B2 (en) 2008-02-28 2013-12-24 Medtronic, Inc. Prosthetic heart valve systems
US11278408B2 (en) 2008-03-18 2022-03-22 Medtronic Venter Technologies, Ltd. Valve suturing and implantation procedures
US8313525B2 (en) 2008-03-18 2012-11-20 Medtronic Ventor Technologies, Ltd. Valve suturing and implantation procedures
US9592120B2 (en) 2008-03-18 2017-03-14 Medtronic Ventor Technologies, Ltd. Valve suturing and implantation procedures
US11602430B2 (en) 2008-03-18 2023-03-14 Medtronic Ventor Technologies Ltd. Valve suturing and implantation procedures
US10856979B2 (en) 2008-03-18 2020-12-08 Medtronic Ventor Technologies Ltd. Valve suturing and implantation procedures
US20090248060A1 (en) * 2008-03-19 2009-10-01 Schneider M Bret Electrostatic vascular filters
US8246649B2 (en) * 2008-03-19 2012-08-21 Schneider M Bret Electrostatic vascular filters
US10245142B2 (en) 2008-04-08 2019-04-02 Medtronic, Inc. Multiple orifice implantable heart valve and methods of implantation
US8430927B2 (en) 2008-04-08 2013-04-30 Medtronic, Inc. Multiple orifice implantable heart valve and methods of implantation
US8696743B2 (en) 2008-04-23 2014-04-15 Medtronic, Inc. Tissue attachment devices and methods for prosthetic heart valves
US8511244B2 (en) 2008-04-23 2013-08-20 Medtronic, Inc. Methods and apparatuses for assembly of a pericardial prosthetic heart valve
US8312825B2 (en) 2008-04-23 2012-11-20 Medtronic, Inc. Methods and apparatuses for assembly of a pericardial prosthetic heart valve
US9744038B2 (en) 2008-05-13 2017-08-29 Kardium Inc. Medical device for constricting tissue or a bodily orifice, for example a mitral valve
US8840661B2 (en) 2008-05-16 2014-09-23 Sorin Group Italia S.R.L. Atraumatic prosthetic heart valve prosthesis
US8491649B2 (en) 2008-07-29 2013-07-23 Aga Medical Corporation Medical device including corrugated braid and associated method
US20100030321A1 (en) * 2008-07-29 2010-02-04 Aga Medical Corporation Medical device including corrugated braid and associated method
US8998981B2 (en) 2008-09-15 2015-04-07 Medtronic, Inc. Prosthetic heart valve having identifiers for aiding in radiographic positioning
US10806570B2 (en) 2008-09-15 2020-10-20 Medtronic, Inc. Prosthetic heart valve having identifiers for aiding in radiographic positioning
US9943407B2 (en) 2008-09-15 2018-04-17 Medtronic, Inc. Prosthetic heart valve having identifiers for aiding in radiographic positioning
US11026786B2 (en) 2008-09-15 2021-06-08 Medtronic, Inc. Prosthetic heart valve having identifiers for aiding in radiographic positioning
US10321997B2 (en) 2008-09-17 2019-06-18 Medtronic CV Luxembourg S.a.r.l. Delivery system for deployment of medical devices
US8721714B2 (en) 2008-09-17 2014-05-13 Medtronic Corevalve Llc Delivery system for deployment of medical devices
US9532873B2 (en) 2008-09-17 2017-01-03 Medtronic CV Luxembourg S.a.r.l. Methods for deployment of medical devices
US11166815B2 (en) 2008-09-17 2021-11-09 Medtronic CV Luxembourg S.a.r.l Delivery system for deployment of medical devices
US8137398B2 (en) 2008-10-13 2012-03-20 Medtronic Ventor Technologies Ltd Prosthetic valve having tapered tip when compressed for delivery
US8986361B2 (en) 2008-10-17 2015-03-24 Medtronic Corevalve, Inc. Delivery system for deployment of medical devices
US20120046683A1 (en) * 2008-10-31 2012-02-23 Scott Wilson Devices and methods for temporarily opening a blood vessel
US10098733B2 (en) 2008-12-23 2018-10-16 Sorin Group Italia S.R.L. Expandable prosthetic valve having anchoring appendages
US8834563B2 (en) 2008-12-23 2014-09-16 Sorin Group Italia S.R.L. Expandable prosthetic valve having anchoring appendages
US8657849B2 (en) 2008-12-29 2014-02-25 Cook Medical Technologies Llc Embolic protection device and method of use
US8388644B2 (en) 2008-12-29 2013-03-05 Cook Medical Technologies Llc Embolic protection device and method of use
US11364106B2 (en) 2009-01-16 2022-06-21 Boston Scientific Scimed, Inc. Intravascular blood filter
US9326843B2 (en) 2009-01-16 2016-05-03 Claret Medical, Inc. Intravascular blood filters and methods of use
US9636205B2 (en) 2009-01-16 2017-05-02 Claret Medical, Inc. Intravascular blood filters and methods of use
US11284986B2 (en) 2009-01-16 2022-03-29 Claret Medical, Inc. Intravascular blood filters and methods of use
US11607301B2 (en) 2009-01-16 2023-03-21 Boston Scientific Scimed, Inc. Intravascular blood filters and methods of use
US10743977B2 (en) 2009-01-16 2020-08-18 Boston Scientific Scimed, Inc. Intravascular blood filter
US8512397B2 (en) 2009-04-27 2013-08-20 Sorin Group Italia S.R.L. Prosthetic vascular conduit
US8974489B2 (en) 2009-07-27 2015-03-10 Claret Medical, Inc. Dual endovascular filter and methods of use
US10130458B2 (en) 2009-07-27 2018-11-20 Claret Medical, Inc. Dual endovascular filter and methods of use
US11191631B2 (en) 2009-07-27 2021-12-07 Boston Scientific Scimed, Inc. Dual endovascular filter and methods of use
US9204964B2 (en) 2009-10-01 2015-12-08 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US10813758B2 (en) 2009-10-01 2020-10-27 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US10687941B2 (en) 2009-10-01 2020-06-23 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US9867703B2 (en) 2009-10-01 2018-01-16 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US8808369B2 (en) 2009-10-05 2014-08-19 Mayo Foundation For Medical Education And Research Minimally invasive aortic valve replacement
US8790242B2 (en) 2009-10-26 2014-07-29 Cardiokinetix, Inc. Ventricular volume reduction
US9039597B2 (en) 2009-10-26 2015-05-26 Cardiokinetix, Inc. Ventricular volume reduction
US10028835B2 (en) 2009-10-26 2018-07-24 Edwards Lifesciences Corporation Ventricular volume reduction
US9364327B2 (en) 2009-10-26 2016-06-14 Cardiokinetix, Inc. Ventricular volume reduction
US9808332B2 (en) 2009-12-02 2017-11-07 Surefire Medical, Inc. Dynamic microvalve protection device
US10813739B2 (en) 2009-12-02 2020-10-27 Surefire Medical, Inc. Dynamic microvalve protection device
US20110130657A1 (en) * 2009-12-02 2011-06-02 Chomas James E Protection Device and Method Against Embolization Agent Reflux
WO2011068924A1 (en) * 2009-12-02 2011-06-09 Surefire Medical, Inc. Microvalve protection device and method of use for protection against embolization agent reflux
CN102665608A (en) * 2009-12-02 2012-09-12 神火医药公司 Microvalve protection device and method of use for protection against embolization agent reflux
US20110137399A1 (en) * 2009-12-02 2011-06-09 Chomas James E Microvalve Protection Device and Method of Use for Protection Against Embolization Agent Reflux
US9539081B2 (en) 2009-12-02 2017-01-10 Surefire Medical, Inc. Method of operating a microvalve protection device
US8500775B2 (en) 2009-12-02 2013-08-06 Surefire Medical, Inc. Protection device and method against embolization agent reflux
US8696698B2 (en) 2009-12-02 2014-04-15 Surefire Medical, Inc. Microvalve protection device and method of use for protection against embolization agent reflux
US8696699B2 (en) 2009-12-02 2014-04-15 Surefire Medical, Inc. Microvalve protection device and method of use for protection against embolization agent reflux
US9295540B2 (en) 2009-12-02 2016-03-29 Surefire Medical, Inc. Dynamic microvalve protection device with associated balloon element for therapeutic intravascular procedures
US9226826B2 (en) 2010-02-24 2016-01-05 Medtronic, Inc. Transcatheter valve structure and methods for valve delivery
US11554010B2 (en) 2010-04-01 2023-01-17 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US10716665B2 (en) 2010-04-01 2020-07-21 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US8652204B2 (en) 2010-04-01 2014-02-18 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US9925044B2 (en) 2010-04-01 2018-03-27 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US11833041B2 (en) 2010-04-01 2023-12-05 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US20110288529A1 (en) * 2010-05-19 2011-11-24 Fulton Richard E Augmented delivery catheter and method
US10335577B2 (en) 2010-05-19 2019-07-02 Nfinium Vascular Technologies, Llc Augmented delivery catheter and method
US11623070B2 (en) 2010-05-19 2023-04-11 Vascular Development Corp, Llc Augmented delivery catheter and method
US9126016B2 (en) * 2010-05-19 2015-09-08 Nfusion Vascular Systems Llc Augmented delivery catheter and method
US9248017B2 (en) 2010-05-21 2016-02-02 Sorin Group Italia S.R.L. Support device for valve prostheses and corresponding kit
US11589981B2 (en) 2010-05-25 2023-02-28 Jenavalve Technology, Inc. Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent
US9918706B2 (en) 2010-06-07 2018-03-20 Kardium Inc. Closing openings in anatomical tissue
US9050066B2 (en) 2010-06-07 2015-06-09 Kardium Inc. Closing openings in anatomical tissue
US10603022B2 (en) 2010-06-07 2020-03-31 Kardium Inc. Closing openings in anatomical tissue
US10111645B2 (en) 2010-06-30 2018-10-30 Muffin Incorporated Percutaneous, ultrasound-guided introduction of medical devices
CN103079497A (en) * 2010-06-30 2013-05-01 玛芬股份有限公司 Percutaneous, ultrasound-guided introduction of medical devices
EP4151154A3 (en) * 2010-06-30 2023-06-07 Muffin Incorporated Percutaneous, ultrasound-guided introduction of medical devices
US9918833B2 (en) 2010-09-01 2018-03-20 Medtronic Vascular Galway Prosthetic valve support structure
US10835376B2 (en) 2010-09-01 2020-11-17 Medtronic Vascular Galway Prosthetic valve support structure
US11786368B2 (en) 2010-09-01 2023-10-17 Medtronic Vascular Galway Prosthetic valve support structure
US10201418B2 (en) 2010-09-10 2019-02-12 Symetis, SA Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device
US10869760B2 (en) 2010-09-10 2020-12-22 Symetis Sa Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device
US8940002B2 (en) 2010-09-30 2015-01-27 Kardium Inc. Tissue anchor system
US20120095500A1 (en) * 2010-10-14 2012-04-19 Heuser Richard R Concentric wire embolism protection device
US9770319B2 (en) 2010-12-01 2017-09-26 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
US9017364B2 (en) 2010-12-30 2015-04-28 Claret Medical, Inc. Deflectable intravascular filter
US9943395B2 (en) 2010-12-30 2018-04-17 Claret Medical, Inc. Deflectable intravascular filter
US9259306B2 (en) 2010-12-30 2016-02-16 Claret Medical, Inc. Aortic embolic protection device
US9345565B2 (en) 2010-12-30 2016-05-24 Claret Medical, Inc. Steerable dual filter cerebral protection system
US8876796B2 (en) 2010-12-30 2014-11-04 Claret Medical, Inc. Method of accessing the left common carotid artery
US9492264B2 (en) 2010-12-30 2016-11-15 Claret Medical, Inc. Embolic protection device for protecting the cerebral vasculature
US9980805B2 (en) 2010-12-30 2018-05-29 Claret Medical, Inc. Aortic embolic protection device
US10058411B2 (en) 2010-12-30 2018-08-28 Claret Madical, Inc. Method of isolating the cerebral circulation during a cardiac procedure
US9055997B2 (en) 2010-12-30 2015-06-16 Claret Medical, Inc. Method of isolating the cerebral circulation during a cardiac procedure
US11141258B2 (en) 2010-12-30 2021-10-12 Claret Medical, Inc. Method of isolating the cerebral circulation during a cardiac procedure
WO2012094195A1 (en) * 2011-01-07 2012-07-12 Merhi William M Angiography catheter
KR102094046B1 (en) * 2011-01-07 2020-03-26 이너베이티브 카디오배스큘러 솔류션스, 엘엘씨 Angiography catheter
AU2011353593B2 (en) * 2011-01-07 2015-10-08 Innovative Cardiovascular Solutions, Llc Angiography catheter
US8948848B2 (en) 2011-01-07 2015-02-03 Innovative Cardiovascular Solutions, Llc Angiography catheter
KR20140034752A (en) * 2011-01-07 2014-03-20 이너베이티브 카디오배스큘러 솔류션스, 엘엘씨 Angiography catheter
US9161836B2 (en) 2011-02-14 2015-10-20 Sorin Group Italia S.R.L. Sutureless anchoring device for cardiac valve prostheses
US9289289B2 (en) 2011-02-14 2016-03-22 Sorin Group Italia S.R.L. Sutureless anchoring device for cardiac valve prostheses
US10456255B2 (en) 2011-03-21 2019-10-29 Cephea Valve Technologies, Inc. Disk-based valve apparatus and method for the treatment of valve dysfunction
US8728155B2 (en) 2011-03-21 2014-05-20 Cephea Valve Technologies, Inc. Disk-based valve apparatus and method for the treatment of valve dysfunction
US10058318B2 (en) 2011-03-25 2018-08-28 Kardium Inc. Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve
US9072511B2 (en) 2011-03-25 2015-07-07 Kardium Inc. Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve
US11771544B2 (en) 2011-05-05 2023-10-03 Symetis Sa Method and apparatus for compressing/loading stent-valves
US8998976B2 (en) 2011-07-12 2015-04-07 Boston Scientific Scimed, Inc. Coupling system for medical devices
US9089668B2 (en) 2011-09-28 2015-07-28 Surefire Medical, Inc. Flow directional infusion device
US9131926B2 (en) 2011-11-10 2015-09-15 Boston Scientific Scimed, Inc. Direct connect flush system
US9555219B2 (en) 2011-11-10 2017-01-31 Boston Scientific Scimed, Inc. Direct connect flush system
US9642705B2 (en) 2011-11-15 2017-05-09 Boston Scientific Scimed Inc. Bond between components of a medical device
US10478300B2 (en) 2011-11-15 2019-11-19 Boston Scientific Scimed, Inc. Bond between components of a medical device
US8940014B2 (en) 2011-11-15 2015-01-27 Boston Scientific Scimed, Inc. Bond between components of a medical device
US8951243B2 (en) 2011-12-03 2015-02-10 Boston Scientific Scimed, Inc. Medical device handle
US9370421B2 (en) 2011-12-03 2016-06-21 Boston Scientific Scimed, Inc. Medical device handle
US9277993B2 (en) 2011-12-20 2016-03-08 Boston Scientific Scimed, Inc. Medical device delivery systems
US9510945B2 (en) 2011-12-20 2016-12-06 Boston Scientific Scimed Inc. Medical device handle
US8685084B2 (en) 2011-12-29 2014-04-01 Sorin Group Italia S.R.L. Prosthetic vascular conduit and assembly method
US9138314B2 (en) 2011-12-29 2015-09-22 Sorin Group Italia S.R.L. Prosthetic vascular conduit and assembly method
US10172708B2 (en) 2012-01-25 2019-01-08 Boston Scientific Scimed, Inc. Valve assembly with a bioabsorbable gasket and a replaceable valve implant
US9089341B2 (en) 2012-02-28 2015-07-28 Surefire Medical, Inc. Renal nerve neuromodulation device
US9888994B2 (en) 2012-05-15 2018-02-13 Transverse Medical, Inc. Catheter-based apparatuses and methods
US11382739B2 (en) 2012-06-19 2022-07-12 Boston Scientific Scimed, Inc. Replacement heart valve
US10555809B2 (en) 2012-06-19 2020-02-11 Boston Scientific Scimed, Inc. Replacement heart valve
US20150305850A1 (en) * 2012-12-21 2015-10-29 The Regents Of The University Of California In Vivo Positionable Filtration Devices and Methods Related Thereto
US11406485B2 (en) * 2012-12-21 2022-08-09 The Regents Of The University Of California In vivo positionable filtration devices and methods related thereto
US20140214072A1 (en) * 2013-01-29 2014-07-31 St. Jude Medical, Cardiology Division, Inc. Aortic great vessel protection
US9962252B2 (en) 2013-01-29 2018-05-08 St. Jude Medical, Cardiology Division, Inc. Aortic great vessel protection
US9186238B2 (en) * 2013-01-29 2015-11-17 St. Jude Medical, Cardiology Division, Inc. Aortic great vessel protection
US20140257362A1 (en) * 2013-03-07 2014-09-11 St. Jude Medical, Cardiology Division, Inc. Filtering and removing particulates from bloodstream
US11793637B2 (en) 2013-05-03 2023-10-24 Medtronic, Inc. Valve delivery tool
US9629718B2 (en) 2013-05-03 2017-04-25 Medtronic, Inc. Valve delivery tool
US10568739B2 (en) 2013-05-03 2020-02-25 Medtronic, Inc. Valve delivery tool
EP3964168A1 (en) * 2013-05-10 2022-03-09 Medtronic, Inc. System for deploying a device to a distal location across a diseased vessel
US20160100928A1 (en) * 2013-05-14 2016-04-14 Transverse Medical, Inc. Catheter-based apparatuses and methods
US9888995B2 (en) * 2013-05-14 2018-02-13 Transverse Medical, Inc. Catheter-based apparatuses and methods
US10154906B2 (en) 2013-07-17 2018-12-18 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US11510780B2 (en) 2013-07-17 2022-11-29 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US8870948B1 (en) 2013-07-17 2014-10-28 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US9554899B2 (en) 2013-07-17 2017-01-31 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US10149761B2 (en) 2013-07-17 2018-12-11 Cephea Valve Technlologies, Inc. System and method for cardiac valve repair and replacement
US9561103B2 (en) 2013-07-17 2017-02-07 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US10624742B2 (en) 2013-07-17 2020-04-21 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
US11185405B2 (en) 2013-08-30 2021-11-30 Jenavalve Technology, Inc. Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame
CN106102654A (en) * 2014-01-10 2016-11-09 企斯动哈特有限公司 Dissect independent deflector
US11135361B2 (en) 2014-03-25 2021-10-05 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
US9889031B1 (en) 2014-03-25 2018-02-13 Surefire Medical, Inc. Method of gastric artery embolization
US9968740B2 (en) 2014-03-25 2018-05-15 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
US20150297250A1 (en) * 2014-04-16 2015-10-22 Covidien Lp Systems and methods for catheter advancement
US10413309B2 (en) 2014-04-16 2019-09-17 Covidien Lp Systems and methods for catheter advancement
US11690720B2 (en) 2014-09-28 2023-07-04 Edwards Lifesciences Corporation Systems and methods for treating cardiac dysfunction
US10751183B2 (en) 2014-09-28 2020-08-25 Edwards Lifesciences Corporation Apparatuses for treating cardiac dysfunction
US9901445B2 (en) 2014-11-21 2018-02-27 Boston Scientific Scimed, Inc. Valve locking mechanism
US10869755B2 (en) 2014-12-09 2020-12-22 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US10433953B2 (en) 2014-12-09 2019-10-08 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US10548721B2 (en) 2014-12-09 2020-02-04 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US11147665B2 (en) 2014-12-09 2021-10-19 Cepha Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US9439757B2 (en) 2014-12-09 2016-09-13 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US9492273B2 (en) 2014-12-09 2016-11-15 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
US10449043B2 (en) 2015-01-16 2019-10-22 Boston Scientific Scimed, Inc. Displacement based lock and release mechanism
US9861477B2 (en) 2015-01-26 2018-01-09 Boston Scientific Scimed Inc. Prosthetic heart valve square leaflet-leaflet stitch
US20180049726A1 (en) * 2015-02-02 2018-02-22 Centre National De La Recherche Scientifique Microdevice for the In Vivo Capture of Circulating Cellular Biomarkers
US11457900B2 (en) * 2015-02-02 2022-10-04 Centre National De La Recherche Scientifique Microdevice for the in vivo capture of circulating cellular biomarkers
US9788942B2 (en) 2015-02-03 2017-10-17 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
US10201417B2 (en) 2015-02-03 2019-02-12 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
US10426617B2 (en) 2015-03-06 2019-10-01 Boston Scientific Scimed, Inc. Low profile valve locking mechanism and commissure assembly
US10285809B2 (en) 2015-03-06 2019-05-14 Boston Scientific Scimed Inc. TAVI anchoring assist device
US10080652B2 (en) 2015-03-13 2018-09-25 Boston Scientific Scimed, Inc. Prosthetic heart valve having an improved tubular seal
US11065113B2 (en) 2015-03-13 2021-07-20 Boston Scientific Scimed, Inc. Prosthetic heart valve having an improved tubular seal
US11090460B2 (en) 2015-03-31 2021-08-17 Surefire Medical, Inc. Method for infusing an immunotherapy agent to a solid tumor for treatment
US10449028B2 (en) 2015-04-22 2019-10-22 Claret Medical, Inc. Vascular filters, deflectors, and methods
US9566144B2 (en) 2015-04-22 2017-02-14 Claret Medical, Inc. Vascular filters, deflectors, and methods
US11337800B2 (en) 2015-05-01 2022-05-24 Jenavalve Technology, Inc. Device and method with reduced pacemaker rate in heart valve replacement
US11786373B2 (en) 2015-05-14 2023-10-17 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
US10470881B2 (en) 2015-05-14 2019-11-12 Cephea Valve Technologies, Inc. Replacement mitral valves
US11617646B2 (en) 2015-05-14 2023-04-04 Cephea Valve Technologies, Inc. Replacement mitral valves
US10849746B2 (en) 2015-05-14 2020-12-01 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
US10555808B2 (en) 2015-05-14 2020-02-11 Cephea Valve Technologies, Inc. Replacement mitral valves
US10143552B2 (en) 2015-05-14 2018-12-04 Cephea Valve Technologies, Inc. Replacement mitral valves
US11730595B2 (en) 2015-07-02 2023-08-22 Boston Scientific Scimed, Inc. Adjustable nosecone
US10335277B2 (en) 2015-07-02 2019-07-02 Boston Scientific Scimed Inc. Adjustable nosecone
US10195392B2 (en) 2015-07-02 2019-02-05 Boston Scientific Scimed, Inc. Clip-on catheter
US10179041B2 (en) 2015-08-12 2019-01-15 Boston Scientific Scimed Icn. Pinless release mechanism
US10856973B2 (en) 2015-08-12 2020-12-08 Boston Scientific Scimed, Inc. Replacement heart valve implant
US10136991B2 (en) 2015-08-12 2018-11-27 Boston Scientific Scimed Inc. Replacement heart valve implant
US10779940B2 (en) 2015-09-03 2020-09-22 Boston Scientific Scimed, Inc. Medical device handle
JP2018531771A (en) * 2015-10-09 2018-11-01 トランスバース メディカル インコーポレイテッドTransverse Medical, Inc. Catheter-based devices and methods
US10064637B2 (en) 2015-10-09 2018-09-04 Transverse Medical, INC Catheter-based apparatuses and methods
WO2017062036A1 (en) * 2015-10-09 2017-04-13 Transverse Medical, Inc. Catheter-based apparatuses and methods
US10987118B2 (en) 2015-10-09 2021-04-27 Transverse Medical Inc. Catheter-based apparatuses and methods
AU2019203364B2 (en) * 2015-10-09 2021-05-27 Transverse Medical, Inc. Catheter-based apparatuses and methods
US10342660B2 (en) 2016-02-02 2019-07-09 Boston Scientific Inc. Tensioned sheathing aids
US10583005B2 (en) 2016-05-13 2020-03-10 Boston Scientific Scimed, Inc. Medical device handle
US10245136B2 (en) 2016-05-13 2019-04-02 Boston Scientific Scimed Inc. Containment vessel with implant sheathing guide
US11382742B2 (en) 2016-05-13 2022-07-12 Boston Scientific Scimed, Inc. Medical device handle
US11065138B2 (en) 2016-05-13 2021-07-20 Jenavalve Technology, Inc. Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system
US10201416B2 (en) 2016-05-16 2019-02-12 Boston Scientific Scimed, Inc. Replacement heart valve implant with invertible leaflets
US20170325938A1 (en) 2016-05-16 2017-11-16 Boston Scientific Scimed, Inc. Replacement heart valve implant with invertible leaflets
US10709552B2 (en) 2016-05-16 2020-07-14 Boston Scientific Scimed, Inc. Replacement heart valve implant with invertible leaflets
US11331187B2 (en) 2016-06-17 2022-05-17 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
US11389168B2 (en) 2016-09-01 2022-07-19 Microvention, Inc. Temporary aortic occlusion device
US11389169B2 (en) 2016-09-01 2022-07-19 Microvention, Inc. Temporary aortic occlusion device
US10780250B1 (en) 2016-09-19 2020-09-22 Surefire Medical, Inc. System and method for selective pressure-controlled therapeutic delivery
US11400263B1 (en) 2016-09-19 2022-08-02 Trisalus Life Sciences, Inc. System and method for selective pressure-controlled therapeutic delivery
EP3323360A1 (en) * 2016-11-21 2018-05-23 Cook Medical Technologies LLC Implantable medical device with atraumatic tip
WO2018102651A1 (en) * 2016-12-01 2018-06-07 Mayo Foundation For Medical Education And Research Percutaneously-deployable intravascular embolic protection devices and methods
US11298218B2 (en) 2017-01-20 2022-04-12 W. L. Gore & Associates, Inc. Embolic filter system
WO2018136724A3 (en) * 2017-01-20 2018-09-13 W. L. Gore & Associates, Inc. Embolic filter system
JP2020506752A (en) * 2017-01-20 2020-03-05 ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティドW.L. Gore & Associates, Incorporated Embolic filter system
US11058535B2 (en) 2017-01-23 2021-07-13 Cephea Valve Technologies, Inc. Replacement mitral valves
US11090158B2 (en) 2017-01-23 2021-08-17 Cephea Valve Technologies, Inc. Replacement mitral valves
US10828153B2 (en) 2017-01-23 2020-11-10 Cephea Valve Technologies, Inc. Replacement mitral valves
US10368990B2 (en) 2017-01-23 2019-08-06 Cephea Valve Technologies, Inc. Replacement mitral valves
US10568737B2 (en) 2017-01-23 2020-02-25 Cephea Valve Technologies, Inc. Replacement mitral valves
US11633278B2 (en) 2017-01-23 2023-04-25 Cephea Valve Technologies, Inc. Replacement mitral valves
US11197754B2 (en) 2017-01-27 2021-12-14 Jenavalve Technology, Inc. Heart valve mimicry
US11337790B2 (en) 2017-02-22 2022-05-24 Boston Scientific Scimed, Inc. Systems and methods for protecting the cerebral vasculature
CN110392556A (en) * 2017-03-13 2019-10-29 东丽株式会社 Filter means
EP3597147A4 (en) * 2017-03-13 2020-11-18 Toray Industries, Inc. Filter device
US10588636B2 (en) * 2017-03-20 2020-03-17 Surefire Medical, Inc. Dynamic reconfigurable microvalve protection device
US20200163685A1 (en) * 2017-03-27 2020-05-28 Transverse Medical, Inc. Filter apparatuses and methods
US11246698B2 (en) * 2017-03-27 2022-02-15 Transverse Medical, Inc. Filter apparatuses and methods
US10898330B2 (en) 2017-03-28 2021-01-26 Edwards Lifesciences Corporation Positioning, deploying, and retrieving implantable devices
WO2018187413A1 (en) * 2017-04-05 2018-10-11 Boston Scientific Scimed, Inc. Emboli-capturing centering device
US11166803B2 (en) 2017-04-05 2021-11-09 Boston Scientific Scimed, Inc. Emboli-capturing centering device
US10828154B2 (en) 2017-06-08 2020-11-10 Boston Scientific Scimed, Inc. Heart valve implant commissure support structure
US10898325B2 (en) 2017-08-01 2021-01-26 Boston Scientific Scimed, Inc. Medical implant locking mechanism
US10939996B2 (en) 2017-08-16 2021-03-09 Boston Scientific Scimed, Inc. Replacement heart valve commissure assembly
US11191630B2 (en) 2017-10-27 2021-12-07 Claret Medical, Inc. Systems and methods for protecting the cerebral vasculature
US11154390B2 (en) 2017-12-19 2021-10-26 Claret Medical, Inc. Systems for protection of the cerebral vasculature during a cardiac procedure
WO2020242545A1 (en) 2017-12-28 2020-12-03 Groh Mark Embolic protection catheter and related devices and methods
EP3975922A4 (en) * 2017-12-28 2023-06-07 EmStop Inc. Embolic protection catheter and related devices and methods
US11191641B2 (en) 2018-01-19 2021-12-07 Boston Scientific Scimed, Inc. Inductance mode deployment sensors for transcatheter valve system
US11246625B2 (en) 2018-01-19 2022-02-15 Boston Scientific Scimed, Inc. Medical device delivery system with feedback loop
US11147668B2 (en) 2018-02-07 2021-10-19 Boston Scientific Scimed, Inc. Medical device delivery system with alignment feature
US11439732B2 (en) 2018-02-26 2022-09-13 Boston Scientific Scimed, Inc. Embedded radiopaque marker in adaptive seal
US11071844B2 (en) 2018-03-07 2021-07-27 Innovative Cardiovascular Solutions, Llc Embolic protection device
US11717390B2 (en) 2018-03-07 2023-08-08 Innovative Cardiovascular Solutions, Llc Embolic protection device
US11439491B2 (en) 2018-04-26 2022-09-13 Claret Medical, Inc. Systems and methods for protecting the cerebral vasculature
US11229517B2 (en) 2018-05-15 2022-01-25 Boston Scientific Scimed, Inc. Replacement heart valve commissure assembly
US11504231B2 (en) 2018-05-23 2022-11-22 Corcym S.R.L. Cardiac valve prosthesis
US11241310B2 (en) 2018-06-13 2022-02-08 Boston Scientific Scimed, Inc. Replacement heart valve delivery device
US11850398B2 (en) 2018-08-01 2023-12-26 Trisalus Life Sciences, Inc. Systems and methods for pressure-facilitated therapeutic agent delivery
US11351023B2 (en) 2018-08-21 2022-06-07 Claret Medical, Inc. Systems and methods for protecting the cerebral vasculature
WO2020069810A1 (en) 2018-10-04 2020-04-09 Universitätsspital Basel Protective device for open heart aortic valve replacement surgery and kit comprising the same
EP3632374A1 (en) 2018-10-04 2020-04-08 Universitätsspital Basel Protective device for open heart aortic valve replacement surgery and kit comprising the same
US11338117B2 (en) 2018-10-08 2022-05-24 Trisalus Life Sciences, Inc. Implantable dual pathway therapeutic agent delivery port
US11241312B2 (en) 2018-12-10 2022-02-08 Boston Scientific Scimed, Inc. Medical device delivery system including a resistance member
US11439504B2 (en) 2019-05-10 2022-09-13 Boston Scientific Scimed, Inc. Replacement heart valve with improved cusp washout and reduced loading
US11931252B2 (en) 2019-07-15 2024-03-19 Cephea Valve Technologies, Inc. Disk-based valve apparatus and method for the treatment of valve dysfunction
WO2022087136A1 (en) * 2020-10-20 2022-04-28 Legacy Ventures LLC Clot retrieval system
CN115670738A (en) * 2022-12-28 2023-02-03 北京华脉泰科医疗器械股份有限公司 Thrombolytic catheter filter and thrombolytic filter combination kit

Also Published As

Publication number Publication date
CA2304463A1 (en) 1999-04-08
AU9321498A (en) 1999-04-23
US6361545B1 (en) 2002-03-26
WO1999016382A3 (en) 1999-08-05
WO1999016382A2 (en) 1999-04-08
EP1017333A2 (en) 2000-07-12
AU749573B2 (en) 2002-06-27

Similar Documents

Publication Publication Date Title
US6361545B1 (en) Perfusion filter catheter
US6090097A (en) Aortic occluder with associated filter and methods of use during cardiac surgery
US6395014B1 (en) Cerebral embolic protection assembly and associated methods
US5980555A (en) Method of using cannula with associated filter during cardiac surgery
US6136016A (en) Cannula with associated filter and methods of use during cardiac surgery
AU752267B2 (en) Perfusion shunt apparatus and method
US6254563B1 (en) Perfusion shunt apparatus and method
US20040049210A1 (en) Filter apparatus for ostium of left atrial appendage
US20020077596A1 (en) Perfusion shunt apparatus and method
WO1997042879A9 (en) Aortic occluder with associated filter and methods of use during cardiac surgery
EP3331458A1 (en) Axially lengthening thrombus capture system

Legal Events

Date Code Title Description
AS Assignment

Owner name: CARDEON CORPORATION, CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MACOVIAK, JOHN A.;LEARY, JAMES L.;SAMSON, WILFRED J.;REEL/FRAME:013010/0980

Effective date: 20020612

AS Assignment

Owner name: GATX VENTURES, INC., CALIFORNIA

Free format text: SECURITY INTEREST;ASSIGNOR:CARDEON CORPORATION;REEL/FRAME:013718/0555

Effective date: 20030129

Owner name: SILICON VALLEY BANK, CALIFORNIA

Free format text: SECURITY INTEREST;ASSIGNOR:CARDEON CORPORATION;REEL/FRAME:013718/0555

Effective date: 20030129

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION