US20050165469A1 - Vascular prosthesis including torsional stabilizer and methods of use - Google Patents
Vascular prosthesis including torsional stabilizer and methods of use Download PDFInfo
- Publication number
- US20050165469A1 US20050165469A1 US10/723,565 US72356503A US2005165469A1 US 20050165469 A1 US20050165469 A1 US 20050165469A1 US 72356503 A US72356503 A US 72356503A US 2005165469 A1 US2005165469 A1 US 2005165469A1
- Authority
- US
- United States
- Prior art keywords
- vascular prosthesis
- distal
- torsional stabilizer
- vessel
- section
- 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
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/966—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/88—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/88—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils
- A61F2/885—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils comprising a coil including a plurality of spiral or helical sections with alternate directions around a central axis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2002/068—Modifying the blood flow model, e.g. by diffuser or deflector
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2002/828—Means for connecting a plurality of stents allowing flexibility of the whole structure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
- A61F2220/0016—Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0054—V-shaped
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
- A61F2250/0068—Means for introducing or releasing pharmaceutical products into the body the pharmaceutical product being in a reservoir
Definitions
- the present invention relates to an implantable vascular prosthesis configured for use in a wide range of applications, and more specifically, a ribbon-type prosthesis having a torsional stabilizer that increases frictional engagement with a vessel wall.
- Balloon expandable and self-expanding stents are well known for restoring patency in a stenosed vessel, e.g., after an angioplasty procedure, and the use of coils and stents are known techniques for treating aneurysms.
- Previously-known self-expanding stents generally are retained in a contracted delivery configuration using an outer sheath, then self-expand when the sheath is retracted.
- Such stents commonly have several drawbacks, for example, the stents may experience large length changes during expansion (referred to as “foreshortening”) and may shift within the vessel prior to engaging the vessel wall, resulting in improper placement.
- many self-expanding stents have relatively large delivery profiles because the configuration of their struts limits further compression of the stent. Accordingly, such stents may not be suitable for use in smaller vessels, such as cerebral vessels and coronary arteries.
- PCT Publication WO 00/62711 to Rivelli describes a stent comprising a helical mesh coil having a plurality of turns and including a lattice having a multiplicity of pores.
- the lattice is tapered along its length.
- the plurality of turns are wound into a reduced diameter helical shape, then constrained within a delivery sheath.
- the delivery sheath is retracted to expose the distal portion of the stent and anchor the distal end of the stent.
- the subsequent individual turns of the stent unwind to conform to the diameter of the vessel wall.
- the stent described in the foregoing publication has several drawbacks. For example, due to friction between the turns and the sheath, the individual turns of the stent may bunch up, or overlap with one another, when the delivery sheath is retracted. In addition, once the sheath is fully retracted, the turns may shift within the vessel prior to engaging the vessel wall, resulting in improper placement of the stent. Moreover, because the distal portion of the stent may provide insufficient engagement with the vessel wall during subsequent retraction of the remainder of the sheath, ambiguity concerning accuracy of the stent placement may arise.
- the drug is disposed in the matrix of a bioabsorbable polymer coated on an exterior surface of the struts of the stents, and then gradually released into a vessel wall.
- the quantity of the therapeutic agent provided by the stent generally is limited by the surface area of the struts. Increasing the surface area of the struts may enhance drug delivery capability, but may compromise the overall delivery profile of the stent. There therefore exists a need for a prosthesis having a reduced delivery profile and enhanced drug delivery capabilities.
- an implantable vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer, wherein the prosthesis is configured to be used in a wide range of applications including, but not limited to, treating aneurysms, maintaining patency in a vessel, and delivering drugs to a vessel.
- vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer that enhances frictional engagement with the vessel.
- vascular prosthesis having a distal anchoring section that allows for controlled deployment of a ribbon-type stent at a desired location within a vessel.
- an object of the present invention to provide apparatus and methods for an implantable vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer, wherein the prosthesis is configured to be used in a wide range of applications including, but not limited to, treating aneurysms, maintaining patency in a vessel, and delivering drugs to a vessel.
- a vascular prosthesis comprising a distal anchor section joined a helical mesh proximal section and including a torsional stabilizer, wherein the prosthesis is configured to engage a vessel wall and adapt to a natural curvature of the vessel wall.
- the torsional stabilizer is an extension of the proximal section and enhances contact and friction with the vessel wall.
- the vascular prosthesis may be used in a wide range of applications, such as treating aneurysms, maintaining patency in a vessel, e.g., after an angioplasty procedure, and other procedures requiring a controlled delivery of therapeutic drugs to a vessel.
- the vascular prosthesis comprises a shape memory material, such as Nitinol, and includes a distal anchor section having a generally zig-zag or cell-like configuration coupled to a proximal helical section having a helical mesh configuration formed of a plurality of turns.
- shape memory material such as Nitinol
- the prosthesis is delivered to a target vessel in a contracted state, constrained within an outer sheath, in which radially inwardly directed compressive forces are applied by the outer sheath to the distal section.
- the helical proximal section and torsional stabilizer are wound down to a smaller configuration, so that adjacent turns preferably partially overlap, and are constrained in the contracted state by the outer sheath.
- the distal section, proximal section and torsional stabilizer are provided in their respective contracted states within the outer sheath and the prosthesis is fluoroscopically advanced into a selected vessel using techniques that are per se known in the art.
- the proximal section then is positioned adjacent a target region of a vessel, such as an aneurysm or a stenosed region, with the distal section positioned distal of the target region.
- the outer sheath then is retracted proximally to cause the distal section to self-deploy and engage an inner wall of the vessel distal of the target region.
- a distal portion of the distal section may be biased radially outward, or provided with proximally-directed barbs, to facilitate secure anchoring of the distal section within the vessel.
- the outer sheath further is retracted to cause the proximal section to self-deploy and engage the vessel wall at the target region.
- each turn of the helical proximal section will unwind in a controlled manner as the outer sheath is retracted. This technique ensures that the prosthesis will not shift within the vessel during deployment.
- the vascular prosthesis of the present invention is flexible enough to conform to the shape of a delicate vessel without substantially remodeling the vessel.
- the zig-zag or cell-like configuration of the distal section may conform to a natural curvature of a vessel wall better than traditional stents having interconnected struts, which may be more rigid.
- the helical mesh configuration of the proximal section conforms to vasculature of the target region since each of the plurality of turns is free to assume a curved configuration substantially independently of one another.
- the proximal section of the vascular prosthesis has a ribbon-like structure, the proximal section may be wound down to a contracted state with a substantially reduced delivery profile, compared to slotted-tube stents. This feature makes the stent of the present invention especially useful for treating defects in smaller vessels, such as cerebral arteries.
- the plurality of turns may comprise a substantially increased surface area relative to conventional stents that have a plurality of interconnected struts.
- the increased surface area of the turns is particularly advantageous for localized drug delivery.
- the turns may be coated with a drug-laden polymer coating or, alternatively, one or more dimples or through-holes may be disposed in a lateral surface of the turns to elute drugs over an extended period of time.
- Methods of using the vascular prosthesis of the present invention for example, in the treatment of an aneurysm, also are provided.
- FIGS. 1A-1B are, respectively, side and perspective views of a vascular prosthesis of the present invention.
- FIG. 2 is a side view describing features of the junction of the prosthesis of FIG. 1 ;
- FIG. 3 is a side view of a vascular prosthesis having a distal section that is biased radially outward;
- FIG. 4 is an enlarged view of the distal end of the prosthesis of FIG. 3 ;
- FIG. 5 is a side view illustrating different drug delivery modalities
- FIG. 6 is a side sectional view of a delivery system that may be used in conjunction with the vascular prosthesis of FIG. 1 ;
- FIGS. 7A-7C are side sectional views illustrating use of the vascular prosthesis of FIG. 1 in the treatment of an aneurysm;
- FIGS. 8A-8B are, respectively, side and perspective views of an alternative embodiment of the vascular prosthesis of the present invention.
- FIGS. 9A-9B are, respectively, side and perspective views of a vascular prosthesis including a torsional stabilizer according to the present invention.
- FIG. 10 is a detailed side view of the torsional stabilizer portion of the vascular prosthesis of FIG. 9 ;
- FIG. 11 is a side view of the torsional stabilizer portion of an alternative vascular prosthesis.
- FIG. 12 is a side view of the torsional stabilizer portion of another alternative vascular prosthesis.
- the present invention is directed to an implantable vascular prosthesis configured for use in a wide range of applications, such as treating aneurysms, maintaining patency in a vessel, and allowing for the controlled delivery of therapeutic agents to a vessel wall.
- the prosthesis has a ribbon-type configuration that provides a substantially smaller delivery profile than other known devices, while having an increased surface area to allow for delivery of the therapeutic agents. Additionally, the prosthesis is configured to conform to a vessel wall without substantially remodeling the vessel, and further is configured to provide improved accuracy during deployment relative to previously known devices.
- Vascular prosthesis 20 comprises proximal section 22 and distal section 24 , each capable of assuming contracted and deployed states.
- proximal and distal sections 22 and 24 are each depicted in their respective deployed states.
- Vascular prosthesis 20 preferably is formed from a solid tubular member comprising a shape memory material, such as nickel-titanium alloy (commonly known in the art as Nitinol).
- the solid tubular member then is laser cut, using techniques that are per se known in the art, to a desired deployed configuration, as depicted in FIG. 1A .
- An appropriate heat treatment per se known in the art, then may be applied to solid regions 33 of vascular prosthesis 20 while the device is held in the desired deployed configuration.
- the treatment of the shape memory material allows vascular prosthesis 20 to self-deploy to the desired deployed configuration, depicted in FIGS. 1 , for purposes described hereinafter.
- Distal section 24 preferably has a generally zig-zag configuration in the deployed state, as shown in FIG. 1A .
- the zig-zag configuration preferably is formed by laser cutting a solid tube, as described hereinabove, to form a pattern comprising plurality of struts 31 disposed between plurality of bends 32 .
- Proximal section 22 preferably comprises a helical mesh configuration in the deployed state, as depicted in FIGS. 1 .
- the helical mesh configuration includes a plurality of substantially flat turns 26 .
- Plurality of turns 26 may include a multiplicity of openings provided in different shapes and sizes, as illustrated by larger rectangular openings 25 , smaller rectangular openings 28 and small circular openings 29 .
- the multiplicity of openings are disposed between solid regions 33 of the shape memory material used to form vascular prosthesis 20 .
- turns 26 may comprise fully covered sections 39 , as depicted hereinbelow in FIG. 7C .
- proximal section 22 depicted herein is merely for illustrative purposes. Any combination of covered sections 39 , circular openings 29 , large or small rectangular openings, or any other shape may be provided along portions of turns 26 , as desired. Plurality of turns 26 similarly may comprise exclusively one type of opening, such as small circular openings 29 . Alternatively, plurality of turns 26 may be completely solid, such that the openings are omitted altogether.
- the combination of solid regions and openings may be selectively provided along the length of proximal section 22 , for example, to selectively increase surface area and drug delivery capabilities along proximal section 22 , or to influence flow dynamics within a vessel.
- Proximal section 22 includes distal turn 34 that transitions into bend 32 of distal section 24 , thereby forming junction 23 .
- Proximal turn 35 of proximal section 22 forms a free end that permits proximal section 22 to conform to a natural configuration of a patient's vessel, as described hereinbelow with respect to FIGS. 7 .
- junction 23 is disposed between proximal and distal sections 22 and 24 of vascular prosthesis 20 .
- Junction 23 preferably comprises extension strut 47 that is coupled to at least one bend 32 of distal section 24 .
- Junction 23 extends in a proximal direction towards proximal section 22 and ultimately transitions into proximal wall 42 of distal turn 34 , as shown in FIG. 2 .
- Junction 23 further preferably comprises substantially orthogonal segment 48 , i.e., a segment that is substantially orthogonal to a longitudinal axis of vascular prosthesis 20 .
- Segment 48 transitions into extension strut 47 in the vicinity of bend 32 , and further transitions into distal wall 41 of distal turn 34 , as shown in FIG. 2 .
- Junction 23 may comprise one or more radiopaque markers 44 , such as a radiopaque marker band or coating.
- Radiopaque marker 44 facilitates positioning of junction 23 at a desired longitudinal position within a patient's vessel, and further facilitates alignment of vascular prosthesis 20 at a desired radial orientation within the vessel.
- radiopaque marker 44 may be used to orient proximal section 22 so that a desired lateral surface of proximal section 22 , e.g., comprising covered sections 39 or small circular openings 29 , deploys to overlay the arc of a vessel in which an aneurysm is situated.
- junction 32 may comprise other strut arrangements to connect distal section 24 to proximal section 22 .
- more than one extension struts 47 may be coupled between bends 32 and distal turn 34 of proximal section 22 .
- proximal and distal sections 22 and 24 may be manufactured as two distinct sections, then coupled together to form a junction.
- the junction may be formed when distal turn 34 of proximal section 22 is coupled to one or more bends 32 situated at proximal end 37 of distal section 24 .
- Distal turn 34 may be coupled to one or more bends 32 using a means for bonding, such as a solder, or the sections alternatively may be mechanically coupled together, for example, using a rivet or any other means, as will be apparent to one skilled in the art.
- a means for bonding such as a solder
- distal section 24 ′ has proximal end 37 and distal end 38 .
- Distal end 38 is biased radially outward with respect to the longitudinal axis of vascular prosthesis 20 .
- the deployed configuration of distal section 24 ′ may be established by heat treating a shape memory material, using techniques that are per se known in the art, as described above.
- Distal section 24 ′ is configured to impose an increased radial outward force upon a patient's vessel and may further improve anchoring of the prosthesis within the vessel.
- Distal end 38 of distal section 24 ′ further may comprise at least one barb 40 protruding from bend 32 and/or a distal portion of strut 31 , as depicted in FIG. 4 .
- Barb 40 is configured to extend radially outward and in a proximal direction with respect to a longitudinal axis of vascular prosthesis 20 .
- Each barb 40 may comprise sharpened tip 41 , which is configured to engage a patient's vessel when distal section 24 ′ is deployed in a vessel, as described in hereinbelow with respect to FIGS. 7 .
- illustrative turn 26 ′ of proximal section 22 comprises multiplicity of openings 28 disposed between solid regions 33 , and further comprises at least one dimple 50 and/or through hole 52 disposed in solid regions 33 .
- Each dimple 50 and through hole 52 may have therapeutic agent 54 disposed therein.
- Therapeutic agent 54 may be disposed in the matrix of a bioabsorbable polymer, and the drug may be gradually released into a localized region of an arterial wall.
- Dimples 50 may be selectively disposed on an interior surface of turn 26 ′, and/or disposed on an exterior surface of turn 26 ′, as depicted in FIG. 5 .
- One or more turns 26 may be selectively coated with elastomeric polymer 56 , such as polyurethane.
- Elastomeric polymer 56 may partially or fully cover selected regions of turns 26 .
- elastomeric polymer 56 may be disposed on one arc of the circumference of proximal section 22 to overlay an aneurysm and reduce blood flow into a sac of the aneurysm.
- therapeutic agent 54 may be disposed on elastomeric polymer 56 , which increases the working surface area of proximal section 22 .
- the therapeutic agent may be disposed directly on solid region 33 , either with or without the use of elastomeric polymer 56 .
- delivery system 60 is similar to that disclosed in U.S. Pat. No. 4,665,918 to Garza et al., and includes catheter 61 having central lumen 62 , nose cone 63 and outer sheath 64 .
- catheter 61 includes recessed portion 65 that cooperates with outer sheath 64 to retain proximal and distal sections 22 and 24 of vascular prosthesis 20 in their respective contracted states for transluminal delivery.
- Delivery system 60 also may comprise fluid delivery lumen 67 , which may be used to deliver chilled saline to vascular prosthesis 20 during delivery of the device.
- Fluid delivery lumen 67 may be disposed within catheter 61 , as depicted in FIG. 6 , and one or more ports 68 may be formed in a distal lateral surface of catheter 61 to facilitate fluid communication between lumen 67 and recessed portion 65 .
- vascular prosthesis 20 also may be used in general stenting procedures, for example, to maintain patency in a vessel after a carotid angioplasty procedure, or may be used as an intravascular drug delivery device, or may be used in other applications apparent to those skilled in the art.
- vascular prosthesis 20 of FIG. 1 is provided in the fully contracted state disposed between recessed portion 65 of catheter 61 and outer sheath 64 of FIG. 6 .
- distal section 24 is compressed to its contracted delivery state about recessed portion 65 of catheter 61
- the plurality of turns of proximal section 22 are wound down to a contracted delivery state about recessed portion 65 , as shown in FIG. 7A .
- Outer sheath 64 is disposed over proximal and distal sections 22 and 24 , as depicted, to retain both sections in their contracted states.
- guide wire 70 is percutaneously and transluminally advanced through a patient's vasculature, using techniques that are per se known in the art, until a distal end of guide wire 70 is positioned distal of aneurysm A, which is situated in vessel V.
- Delivery system 60 having vascular prosthesis 20 contracted therein, then is advanced over guide wire 70 via central lumen 62 of catheter 61 .
- Nose cone 63 serves as an atraumatic bumper during advancement of delivery system 60 .
- Delivery system 60 is advanced under fluoroscopic guidance until proximal section 22 is situated adjacent aneurysm A, as shown in FIG. 7A .
- chilled saline preferably is delivered to vascular prosthesis 20 via fluid delivery lumen 67 and port 68 .
- the chilled saline may be used to increase the flexibility of prosthesis 20 to facilitate advancement of delivery system 60 over guide wire 70 .
- outer sheath 64 is retracted proximally to cause distal section 24 to self-deploy distal of aneurysm A, as shown in FIG. 7B .
- Struts 31 of distal section 24 expand in a radial direction to engage an inner wall of vessel V.
- Barbs 40 of FIG. 3 may engage vessel V, and/or the distal end of distal section 24 may be biased radially outward with respect to the proximal end (see FIG. 3 ) to enhance the engagement between distal section 24 and the vessel wall.
- outer sheath 64 With distal section 24 anchored distal of aneurysm A, outer sheath 64 then is further retracted proximally to cause distal turn 34 of proximal section 22 to unwind and deploy to its predetermined shape, as shown in FIG. 7C . As the outer sheath is further retracted, each subsequent turn 26 unwinds one at a time and engages and conforms to an inner wall of vessel V in a controlled manner. When prosthesis system 20 is fully deployed, delivery system 60 then is proximally retracted over guide wire 70 and withdrawn from the patient's vessel, and guide wire 70 is removed.
- deploying distal section 24 prior to deploying proximal section 22 allows distal section 24 to serve as an anchoring mechanism that allows for a controlled deployment of the helical turns of proximal section 22 .
- turns 26 of proximal section 22 will be accurately deployed within vessel V, with substantially no proximal or distal shifting with respect to the vessel as outer sheath 64 is retracted.
- distal section 24 by deploying distal section 24 prior to deploying proximal section 22 , drawbacks associated with the device described in the above-referenced publication to Rivelli may be overcome. Specifically, without a distal anchoring element, the multiplicity of turns of the stent described in the Rivelli publication may experience a tendency to “bunch up,” i.e., overlay one another, as the outer sheath is retracted due to friction between the turns and the outer sheath. In the present invention, distal section 24 serves as an anchoring mechanism prior to retraction of the outer sheath over the proximal section. Accordingly, such a distal anchoring mechanism overcomes potential friction and turns 26 will be less likely to bunch up.
- vascular prosthesis 20 of the present invention is configured to be flexible enough to substantially conform to the shape of vessel V without causing the vessel to remodel.
- the zig-zag configuration of distal section 24 and the helical configuration of proximal section 22 allow for increased flexibility of prosthesis 20 .
- the pitch associated with plurality of turns 26 may be varied to vary the overall flexibility of proximal section 22 .
- a lower pitch, whereby adjacent turns 26 are spaced relatively close together, may be employed to increase flexibility of proximal section 22 .
- a lower pitch is desirable, for example, to treat cerebral aneurysms so that turns 26 may conform to the vasculature without causing remodeling of the vessel.
- a higher pitch whereby adjacent turns 26 are spaced further apart, may be employed to increase the rigidity of proximal section 22 .
- Such a design may be desirable for use in maintaining patency in a stenosed vessel by increasing rigidity of proximal section 22 .
- the width of the coil may be tapered, as described in the Rivelli publication.
- covered sections 39 may be positioned to overlay aneurysm A to significantly reduce blood flow into aneurysm A.
- smaller rectangular openings 28 or small circular openings 29 may overlay aneurysm A to reduce blood flow into the sac of the aneurysm. Over time, the intima of vessel V will grow over plurality of turns 26 of proximal section 22 to completely exclude the aneurysm A from vessel V.
- proximal section 22 depicted in FIG. 7C is merely for illustrative purposes. Any combination of covered sections 39 , circular openings 29 , large or small rectangular openings, or any other shape may be provided along turns 26 , as desired. Plurality of turns 26 similarly may exclusively comprise one type of opening, e.g., small circular openings 29 . Alternatively, plurality of turns 26 may be completely solid such that the openings are omitted altogether.
- therapeutic agents may be delivered to expedite treatment of the aneurysm or prevent restenosis.
- therapeutic agent 54 may be delivered to a desired location within vessel V, either using internal or external dimples 50 , through holes 52 , elastomeric polymer 56 and/or solid regions 33 of one or more turns 26 .
- Therapeutic agent 54 may include, for example, antiplatelet drugs, anticoagulant drugs, agents used for purposes of providing gene therapy to a target region, or any other agent, and may be tailored for a particular application. Radiopaque markers (not shown) may be selectively disposed on turns 26 in the vicinity of the therapeutic agents to facilitate alignment of the therapeutic agents with a target site of a vessel wall.
- Radiopaque markers may be selectively disposed on turns 26 in the vicinity of the therapeutic agents to facilitate alignment of the therapeutic agents with a target site of a vessel wall.
- higher doses of such agents may be provided using vascular prosthesis 20 of the present invention, relative to previously known coils or stents having interconnected struts, due to the increased surface area associated with turns 26 .
- Vascular prosthesis 120 comprises proximal section 122 and distal sections 124 .
- Distal section 124 preferably is provided in accordance with distal section 24 of FIG. 1 and comprises a generally zig-zag configuration including struts 131 and bends 132 .
- Proximal section 122 includes a plurality of individual helical turns 126 . Each turn has a distal end that is coupled to a respective bend 132 of distal section 124 at junctions 127 , as shown in FIGS. 8 . Individual helical turns 126 are aligned in a pattern such that each turn maintains its own helical curvature without overlapping with an adjacent turn, as depicted in FIG. 8 . Individual helical turns 126 of vascular prosthesis 120 may be heat treated to self-deploy to the configuration shown, and may be wound down to a small diameter in which turns 126 are constrained within delivery system 60 of FIG. 6 .
- vascular prosthesis 120 The deployment of vascular prosthesis 120 is substantially similar to the deployment of prosthesis 20 , as described in detail hereinabove with respect to FIGS. 7 , and vascular prosthesis 120 encompasses many of the advantages noted hereinabove with respect to vascular prosthesis 20 .
- vascular prosthesis 140 is described and includes torsional stabilizer 146 according to the principles present invention.
- Vascular prosthesis 140 comprises a proximal section 142 , distal section 144 and torsional stabilizer 146 .
- Proximal section 142 , distal section 144 and torsional stabilizer 146 are joined at junction 148 .
- Each of the proximal section, distal section and torsional stabilizer are capable of assuming contracted and deployed states, and each are depicted in their respective deployed states in FIGS. 9A and 9B .
- distal section 144 is configured to be deployed within a vessel before torsional stabilizer 146 , which is configured to be deployed before proximal section 142 .
- Deploying distal section 144 first allows the distal section to serve as an anchor controls subsequent deployment of the helical turns of proximal section 142 .
- Torsional stabilizer 146 provides further contact with the vessel wall, thereby providing an additional anchor that transmits torsional forces proximally during deployment of proximal section 142 .
- Distal section 144 and torsional stabilizer 146 preferably work in conjunction to balance the torsional force of the proximal section and thus stabilize the vascular prosthesis. This action is expected to further reduce shifting with respect to the vessel wall during deployment of proximal section 142 .
- the above-identified order of deployment alleviates drawbacks associated with the prior art such as the tendency of the turns of the proximal section to “bunch up” during deployment.
- vascular prosthesis including distal section 144 , proximal section 142 and torsional stabilizer 146 , preferably is formed from a solid tubular member comprising a shape memory material, such as Nitinol, processed as described above with respect to the embodiment of FIGS. 1 .
- torsional stabilizer 146 includes at least one dimple or through-hole disposed on a solid portion of the torsional stabilizer.
- distal section 144 in the deployed state has a cell-like configuration comprising a pair zig-zags 144 a, 144 b joined by struts 144 c.
- distal section 144 may include a single zig-zag configuration, such as described with respect to FIGS. 1 .
- the cell configuration of FIGS. 9 is expected to be more rigid than the single zig-zag configuration, and hence is capable of applying, and withstanding, greater radial force.
- Either configuration of distal section 144 may be formed by laser cutting a solid tube, as described hereinabove, to form the requisite pattern.
- distal section 144 may have many other configurations without departing from the scope of the present invention.
- Proximal section 142 preferably comprises a helical ribbon including plurality of turns 152 having multiplicity of openings 154 provided in varying shapes and sizes. The multiplicity of openings are disposed between solid regions 150 of the shape memory material used to form vascular prosthesis 140 .
- Proximal section 142 alternatively may comprise the helical mesh configuration of FIGS. 1 or any other suitable pattern.
- Proximal section 142 includes distal turn 156 that transitions into torsional stabilizer 146 .
- Torsional stabilizer 146 comprises strut 158 that preferably remains substantially parallel to distal section 144 .
- distal section 144 is coupled to proximal section 142 at junction 148 . More particularly, strut 144 b extends in a proximal direction forming neck 149 , which is attached to proximal section 142 at junction 148 . It will be apparent to those skilled in the art that other strut arrangements may be employed to connect distal section 144 to proximal section 142 . For example, more than one strut may be coupled between proximal section 142 and distal section 144 . Alternatively, proximal section 142 and distal section 144 may be manufactured as two distinct sections, then coupled together.
- the X-axis is substantially parallel to a longitudinal axis of vascular prosthesis 140 and the Y-axis is substantially orthogonal to the longitudinal axis of vascular prosthesis 140 .
- Torsional stabilizer 146 generally comprises the portion of the proximal section that extends past the plane of the X-axis junction 148 .
- torsional stabilizer 146 is an extension of proximal section 142 and may comprise a continuation of the helical pattern of the proximal section.
- Torsional stabilizer 146 optionally may be biased outwardly to provide increased frictional contact with the vessel wall. Torsional stabilizer 146 also may comprise one or more radiopaque markers 160 , such as a radiopaque marker band or coating. Radiopaque marker 160 facilitates positioning of torsional stabilizer 146 at a desired longitudinal position within a patient's vessel, and further facilitates alignment of vascular prosthesis 140 at a desired radial orientation within the vessel. For example, radiopaque marker 160 may be used to orient the prosthesis axially within the body vessel.
- Torsional stabilizer 162 comprises loop 164 of material that extends past the plane of the X-axis. Loop 164 is shaped substantially triangularly and includes first segment 164 a disposed substantially parallel to the Y-axis, second segment 164 b coupled to the proximal section, and third segment 164 c. As would be appreciated by those of skill in the art, torsional stabilizer 162 may include other shapes and configurations without departing from the scope of the present invention. By way of example, torsional stabilizer 162 may comprise two or more interconnected curvilinear loops.
- FIG. 12 further alternative vascular prosthesis 140 ′′ includes torsional stabilizer 168 .
- Torsional stabilizer 168 comprises loop 170 of material that extends past the plane of both the X-axis and Y-axes, and illustratively includes semicircular portion 170 a.
- torsional stabilizer 168 may include other shapes and configurations without departing from the scope of the present invention.
Abstract
The present invention is directed to an implantable vascular prosthesis configured for use in a wide range of applications, such as treating aneurysms, maintaining patency in a vessel, and allowing for the controlled delivery of therapeutic agents to a vessel wall. The prosthesis comprises a helical proximal section coupled to a distal anchoring section having a generally zig-zag or cell-like configuration. The prosthesis is configured to conform to a vessel wall without substantially remodeling the vessel, and further is configured to be precisely deployed in a vessel without shifting during deployment. The prosthesis also has a substantially small delivery profile compared to other known stents, while having an increased surface area to enhance delivery of therapeutic agents.
Description
- This application is a continuation-in-part of U.S. patent application Ser. No. 10/342,427, filed Jan. 13, 2003, which claims priority from U.S. provisional patent application Ser. No. 60/433,065, filed Dec. 24, 2002.
- The present invention relates to an implantable vascular prosthesis configured for use in a wide range of applications, and more specifically, a ribbon-type prosthesis having a torsional stabilizer that increases frictional engagement with a vessel wall.
- Today there are a wide range of intravascular prostheses on the market for use in the treatment of aneurysms, stenoses, and other vascular irregularities. Balloon expandable and self-expanding stents are well known for restoring patency in a stenosed vessel, e.g., after an angioplasty procedure, and the use of coils and stents are known techniques for treating aneurysms.
- Previously-known self-expanding stents generally are retained in a contracted delivery configuration using an outer sheath, then self-expand when the sheath is retracted. Such stents commonly have several drawbacks, for example, the stents may experience large length changes during expansion (referred to as “foreshortening”) and may shift within the vessel prior to engaging the vessel wall, resulting in improper placement. Additionally, many self-expanding stents have relatively large delivery profiles because the configuration of their struts limits further compression of the stent. Accordingly, such stents may not be suitable for use in smaller vessels, such as cerebral vessels and coronary arteries.
- Other drawbacks associated with the use of coils or stents in the treatment of aneurysms is that the coils or stents, when deployed, may have a tendency to straighten or otherwise remodel a delicate cerebral vessel, which may cause further adverse consequences. Moreover, such devices may not adequately reduce blood flow from the cerebral vessel into the sac of the aneurysm, which may increase the likelihood of rupture. Generally, if a greater surface area is employed to cover the sac, the delivery profile of the device may be compromised due to the increased surface area, and the device also may be more rigid and cause remodeling of the vessel.
- For example, PCT Publication WO 00/62711 to Rivelli describes a stent comprising a helical mesh coil having a plurality of turns and including a lattice having a multiplicity of pores. The lattice is tapered along its length. In operation, the plurality of turns are wound into a reduced diameter helical shape, then constrained within a delivery sheath. The delivery sheath is retracted to expose the distal portion of the stent and anchor the distal end of the stent. As the delivery sheath is further retracted, the subsequent individual turns of the stent unwind to conform to the diameter of the vessel wall.
- The stent described in the foregoing publication has several drawbacks. For example, due to friction between the turns and the sheath, the individual turns of the stent may bunch up, or overlap with one another, when the delivery sheath is retracted. In addition, once the sheath is fully retracted, the turns may shift within the vessel prior to engaging the vessel wall, resulting in improper placement of the stent. Moreover, because the distal portion of the stent may provide insufficient engagement with the vessel wall during subsequent retraction of the remainder of the sheath, ambiguity concerning accuracy of the stent placement may arise.
- When utilizing stents in interventional procedures, it may be advantageous to deliver therapeutic agents to a vessel wall via the surface of the stent. Such drug eluting stents have many advantages, such as controlled delivery of therapeutic agents over an extended period of time without the need for intervention, and reduced rates of restenosis after angioplasty procedures. Typically, the drug is disposed in the matrix of a bioabsorbable polymer coated on an exterior surface of the struts of the stents, and then gradually released into a vessel wall. The quantity of the therapeutic agent provided by the stent generally is limited by the surface area of the struts. Increasing the surface area of the struts may enhance drug delivery capability, but may compromise the overall delivery profile of the stent. There therefore exists a need for a prosthesis having a reduced delivery profile and enhanced drug delivery capabilities.
- In view of these drawbacks of previously known devices, it would be desirable to provide apparatus and methods for an implantable vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer, wherein the prosthesis is configured to be used in a wide range of applications including, but not limited to, treating aneurysms, maintaining patency in a vessel, and delivering drugs to a vessel.
- It also would be desirable to provide apparatus and methods for a vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer that enhances frictional engagement with the vessel.
- It further would be desirable to provide apparatus and methods for a vascular prosthesis having a distal anchoring section that allows for controlled deployment of a ribbon-type stent at a desired location within a vessel.
- It yet further would be desirable to provide apparatus and methods for a vascular prosthesis that has a substantially small delivery configuration to allow the prosthesis to be used in smaller vessels.
- In view of the foregoing, it is an object of the present invention to provide apparatus and methods for an implantable vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer, wherein the prosthesis is configured to be used in a wide range of applications including, but not limited to, treating aneurysms, maintaining patency in a vessel, and delivering drugs to a vessel.
- It is also an object of the present invention to provide apparatus and methods for a vascular prosthesis comprising a ribbon-type stent having a torsional stabilizer that provides frictional engagement with the vessel wall.
- It is another object of the present invention to provide apparatus and methods for a vascular prosthesis having a distal anchoring section that allows for controlled deployment of the prosthesis at a desired location within a vessel.
- It is a further object of the present invention to provide apparatus and methods for a vascular prosthesis that has a substantially small delivery configuration to allow the prosthesis to be used in smaller vessels.
- These and other objects of the present invention are accomplished by providing a vascular prosthesis comprising a distal anchor section joined a helical mesh proximal section and including a torsional stabilizer, wherein the prosthesis is configured to engage a vessel wall and adapt to a natural curvature of the vessel wall. The torsional stabilizer is an extension of the proximal section and enhances contact and friction with the vessel wall. The vascular prosthesis may be used in a wide range of applications, such as treating aneurysms, maintaining patency in a vessel, e.g., after an angioplasty procedure, and other procedures requiring a controlled delivery of therapeutic drugs to a vessel.
- In a preferred embodiment, the vascular prosthesis comprises a shape memory material, such as Nitinol, and includes a distal anchor section having a generally zig-zag or cell-like configuration coupled to a proximal helical section having a helical mesh configuration formed of a plurality of turns.
- The prosthesis is delivered to a target vessel in a contracted state, constrained within an outer sheath, in which radially inwardly directed compressive forces are applied by the outer sheath to the distal section. In the contracted state, the helical proximal section and torsional stabilizer are wound down to a smaller configuration, so that adjacent turns preferably partially overlap, and are constrained in the contracted state by the outer sheath.
- In a preferred method of operation, the distal section, proximal section and torsional stabilizer are provided in their respective contracted states within the outer sheath and the prosthesis is fluoroscopically advanced into a selected vessel using techniques that are per se known in the art. The proximal section then is positioned adjacent a target region of a vessel, such as an aneurysm or a stenosed region, with the distal section positioned distal of the target region. The outer sheath then is retracted proximally to cause the distal section to self-deploy and engage an inner wall of the vessel distal of the target region. A distal portion of the distal section may be biased radially outward, or provided with proximally-directed barbs, to facilitate secure anchoring of the distal section within the vessel.
- Once the distal section is securely anchored distal of the target region, the outer sheath further is retracted to cause the proximal section to self-deploy and engage the vessel wall at the target region. Advantageously, by providing a distal anchoring element prior to deploying the proximal section, each turn of the helical proximal section will unwind in a controlled manner as the outer sheath is retracted. This technique ensures that the prosthesis will not shift within the vessel during deployment.
- The vascular prosthesis of the present invention is flexible enough to conform to the shape of a delicate vessel without substantially remodeling the vessel. In particular, the zig-zag or cell-like configuration of the distal section may conform to a natural curvature of a vessel wall better than traditional stents having interconnected struts, which may be more rigid. Additionally, the helical mesh configuration of the proximal section conforms to vasculature of the target region since each of the plurality of turns is free to assume a curved configuration substantially independently of one another. Also, because the proximal section of the vascular prosthesis has a ribbon-like structure, the proximal section may be wound down to a contracted state with a substantially reduced delivery profile, compared to slotted-tube stents. This feature makes the stent of the present invention especially useful for treating defects in smaller vessels, such as cerebral arteries.
- In accordance with another aspect of the present invention, the plurality of turns may comprise a substantially increased surface area relative to conventional stents that have a plurality of interconnected struts. The increased surface area of the turns is particularly advantageous for localized drug delivery. The turns may be coated with a drug-laden polymer coating or, alternatively, one or more dimples or through-holes may be disposed in a lateral surface of the turns to elute drugs over an extended period of time.
- Methods of using the vascular prosthesis of the present invention, for example, in the treatment of an aneurysm, also are provided.
- Further features of the invention, its nature and various advantages will be more apparent from the accompanying drawings and the following detailed description of the preferred embodiments, in which:
-
FIGS. 1A-1B are, respectively, side and perspective views of a vascular prosthesis of the present invention; -
FIG. 2 is a side view describing features of the junction of the prosthesis ofFIG. 1 ; -
FIG. 3 is a side view of a vascular prosthesis having a distal section that is biased radially outward; -
FIG. 4 is an enlarged view of the distal end of the prosthesis ofFIG. 3 ; -
FIG. 5 is a side view illustrating different drug delivery modalities; -
FIG. 6 is a side sectional view of a delivery system that may be used in conjunction with the vascular prosthesis ofFIG. 1 ; -
FIGS. 7A-7C are side sectional views illustrating use of the vascular prosthesis ofFIG. 1 in the treatment of an aneurysm; -
FIGS. 8A-8B are, respectively, side and perspective views of an alternative embodiment of the vascular prosthesis of the present invention; -
FIGS. 9A-9B are, respectively, side and perspective views of a vascular prosthesis including a torsional stabilizer according to the present invention; -
FIG. 10 is a detailed side view of the torsional stabilizer portion of the vascular prosthesis ofFIG. 9 ; -
FIG. 11 is a side view of the torsional stabilizer portion of an alternative vascular prosthesis; and -
FIG. 12 is a side view of the torsional stabilizer portion of another alternative vascular prosthesis. - The present invention is directed to an implantable vascular prosthesis configured for use in a wide range of applications, such as treating aneurysms, maintaining patency in a vessel, and allowing for the controlled delivery of therapeutic agents to a vessel wall. The prosthesis has a ribbon-type configuration that provides a substantially smaller delivery profile than other known devices, while having an increased surface area to allow for delivery of the therapeutic agents. Additionally, the prosthesis is configured to conform to a vessel wall without substantially remodeling the vessel, and further is configured to provide improved accuracy during deployment relative to previously known devices.
- Referring now to
FIGS. 1 , a first embodiment of a vascular prosthesis constructed in accordance with principles of the present invention is described.Vascular prosthesis 20 comprisesproximal section 22 anddistal section 24, each capable of assuming contracted and deployed states. InFIGS. 1 , proximal anddistal sections -
Vascular prosthesis 20 preferably is formed from a solid tubular member comprising a shape memory material, such as nickel-titanium alloy (commonly known in the art as Nitinol). The solid tubular member then is laser cut, using techniques that are per se known in the art, to a desired deployed configuration, as depicted inFIG. 1A . An appropriate heat treatment, per se known in the art, then may be applied tosolid regions 33 ofvascular prosthesis 20 while the device is held in the desired deployed configuration. The treatment of the shape memory material allowsvascular prosthesis 20 to self-deploy to the desired deployed configuration, depicted inFIGS. 1 , for purposes described hereinafter. -
Distal section 24 preferably has a generally zig-zag configuration in the deployed state, as shown inFIG. 1A . The zig-zag configuration preferably is formed by laser cutting a solid tube, as described hereinabove, to form a pattern comprising plurality ofstruts 31 disposed between plurality ofbends 32. -
Proximal section 22 preferably comprises a helical mesh configuration in the deployed state, as depicted inFIGS. 1 . The helical mesh configuration includes a plurality of substantially flat turns 26. Plurality ofturns 26 may include a multiplicity of openings provided in different shapes and sizes, as illustrated by largerrectangular openings 25, smallerrectangular openings 28 and smallcircular openings 29. The multiplicity of openings are disposed betweensolid regions 33 of the shape memory material used to formvascular prosthesis 20. Alternatively, turns 26 may comprise fully coveredsections 39, as depicted hereinbelow inFIG. 7C . - As will be apparent to one skilled in the art of stent design, the configuration of
proximal section 22 depicted herein is merely for illustrative purposes. Any combination of coveredsections 39,circular openings 29, large or small rectangular openings, or any other shape may be provided along portions ofturns 26, as desired. Plurality ofturns 26 similarly may comprise exclusively one type of opening, such as smallcircular openings 29. Alternatively, plurality ofturns 26 may be completely solid, such that the openings are omitted altogether. As will be apparent to those skilled in the art, the combination of solid regions and openings may be selectively provided along the length ofproximal section 22, for example, to selectively increase surface area and drug delivery capabilities alongproximal section 22, or to influence flow dynamics within a vessel. -
Proximal section 22 includesdistal turn 34 that transitions intobend 32 ofdistal section 24, thereby formingjunction 23.Proximal turn 35 ofproximal section 22 forms a free end that permitsproximal section 22 to conform to a natural configuration of a patient's vessel, as described hereinbelow with respect toFIGS. 7 . - Referring now to
FIG. 2 , features ofjunction 23 of FIGS. 1 are described in greater detail.Junction 23 is disposed between proximal anddistal sections vascular prosthesis 20.Junction 23 preferably comprisesextension strut 47 that is coupled to at least onebend 32 ofdistal section 24.Junction 23 extends in a proximal direction towardsproximal section 22 and ultimately transitions intoproximal wall 42 ofdistal turn 34, as shown inFIG. 2 . -
Junction 23 further preferably comprises substantiallyorthogonal segment 48, i.e., a segment that is substantially orthogonal to a longitudinal axis ofvascular prosthesis 20.Segment 48 transitions intoextension strut 47 in the vicinity ofbend 32, and further transitions intodistal wall 41 ofdistal turn 34, as shown inFIG. 2 . -
Junction 23 may comprise one or moreradiopaque markers 44, such as a radiopaque marker band or coating.Radiopaque marker 44 facilitates positioning ofjunction 23 at a desired longitudinal position within a patient's vessel, and further facilitates alignment ofvascular prosthesis 20 at a desired radial orientation within the vessel. For example,radiopaque marker 44 may be used to orientproximal section 22 so that a desired lateral surface ofproximal section 22, e.g., comprising coveredsections 39 or smallcircular openings 29, deploys to overlay the arc of a vessel in which an aneurysm is situated. - It will be apparent to those skilled in the art that
junction 32 may comprise other strut arrangements to connectdistal section 24 toproximal section 22. For example, more than one extension struts 47 may be coupled betweenbends 32 anddistal turn 34 ofproximal section 22. Alternatively, proximal anddistal sections distal turn 34 ofproximal section 22 is coupled to one ormore bends 32 situated atproximal end 37 ofdistal section 24.Distal turn 34 may be coupled to one ormore bends 32 using a means for bonding, such as a solder, or the sections alternatively may be mechanically coupled together, for example, using a rivet or any other means, as will be apparent to one skilled in the art. - Referring now to
FIG. 3 , an alternative embodiment ofdistal section 24 of FIGS. 1 is described. InFIG. 3 ,distal section 24′ hasproximal end 37 anddistal end 38.Distal end 38 is biased radially outward with respect to the longitudinal axis ofvascular prosthesis 20. The deployed configuration ofdistal section 24′ may be established by heat treating a shape memory material, using techniques that are per se known in the art, as described above.Distal section 24′ is configured to impose an increased radial outward force upon a patient's vessel and may further improve anchoring of the prosthesis within the vessel. -
Distal end 38 ofdistal section 24′ further may comprise at least onebarb 40 protruding frombend 32 and/or a distal portion ofstrut 31, as depicted inFIG. 4 .Barb 40 is configured to extend radially outward and in a proximal direction with respect to a longitudinal axis ofvascular prosthesis 20. Eachbarb 40 may comprise sharpenedtip 41, which is configured to engage a patient's vessel whendistal section 24′ is deployed in a vessel, as described in hereinbelow with respect toFIGS. 7 . - Referring now to
FIG. 5 , different drug delivery modalities that may be used in conjunction withvascular prosthesis 20 of the present invention are described. InFIG. 5 ,illustrative turn 26′ ofproximal section 22 comprises multiplicity ofopenings 28 disposed betweensolid regions 33, and further comprises at least one dimple 50 and/or throughhole 52 disposed insolid regions 33. Each dimple 50 and throughhole 52 may havetherapeutic agent 54 disposed therein.Therapeutic agent 54 may be disposed in the matrix of a bioabsorbable polymer, and the drug may be gradually released into a localized region of an arterial wall. Dimples 50 may be selectively disposed on an interior surface ofturn 26′, and/or disposed on an exterior surface ofturn 26′, as depicted inFIG. 5 . - One or more turns 26 may be selectively coated with
elastomeric polymer 56, such as polyurethane.Elastomeric polymer 56 may partially or fully cover selected regions ofturns 26. For example,elastomeric polymer 56 may be disposed on one arc of the circumference ofproximal section 22 to overlay an aneurysm and reduce blood flow into a sac of the aneurysm. Additionally,therapeutic agent 54 may be disposed onelastomeric polymer 56, which increases the working surface area ofproximal section 22. Alternatively, the therapeutic agent may be disposed directly onsolid region 33, either with or without the use ofelastomeric polymer 56. - Referring now to
FIG. 6 , a delivery system suitable for use with the vascular prosthesis of the present invention is described. InFIG. 6 , delivery system 60 is similar to that disclosed in U.S. Pat. No. 4,665,918 to Garza et al., and includescatheter 61 havingcentral lumen 62,nose cone 63 andouter sheath 64.Catheter 61 includes recessedportion 65 that cooperates withouter sheath 64 to retain proximal anddistal sections vascular prosthesis 20 in their respective contracted states for transluminal delivery. - Delivery system 60 also may comprise
fluid delivery lumen 67, which may be used to deliver chilled saline tovascular prosthesis 20 during delivery of the device.Fluid delivery lumen 67 may be disposed withincatheter 61, as depicted inFIG. 6 , and one ormore ports 68 may be formed in a distal lateral surface ofcatheter 61 to facilitate fluid communication betweenlumen 67 and recessedportion 65. - Turning now to
FIGS. 7 , a preferred method of usingvascular prosthesis 20 of the present invention, for example, in the treatment of an aneurysm, is described. It will be apparent from the method steps described herein thatvascular prosthesis 20 also may be used in general stenting procedures, for example, to maintain patency in a vessel after a carotid angioplasty procedure, or may be used as an intravascular drug delivery device, or may be used in other applications apparent to those skilled in the art. - In
FIG. 7A ,vascular prosthesis 20 ofFIG. 1 is provided in the fully contracted state disposed between recessedportion 65 ofcatheter 61 andouter sheath 64 ofFIG. 6 . Specifically,distal section 24 is compressed to its contracted delivery state about recessedportion 65 ofcatheter 61, and the plurality of turns ofproximal section 22 are wound down to a contracted delivery state about recessedportion 65, as shown inFIG. 7A .Outer sheath 64 is disposed over proximal anddistal sections - First,
guide wire 70 is percutaneously and transluminally advanced through a patient's vasculature, using techniques that are per se known in the art, until a distal end ofguide wire 70 is positioned distal of aneurysm A, which is situated in vessel V. Delivery system 60, havingvascular prosthesis 20 contracted therein, then is advanced overguide wire 70 viacentral lumen 62 ofcatheter 61.Nose cone 63 serves as an atraumatic bumper during advancement of delivery system 60. Delivery system 60 is advanced under fluoroscopic guidance untilproximal section 22 is situated adjacent aneurysm A, as shown inFIG. 7A . - During advancement of delivery system 60 though a patient's vasculature, chilled saline preferably is delivered to
vascular prosthesis 20 viafluid delivery lumen 67 andport 68. The chilled saline may be used to increase the flexibility ofprosthesis 20 to facilitate advancement of delivery system 60 overguide wire 70. - In a next step,
outer sheath 64 is retracted proximally to causedistal section 24 to self-deploy distal of aneurysm A, as shown inFIG. 7B .Struts 31 ofdistal section 24 expand in a radial direction to engage an inner wall ofvessel V. Barbs 40 ofFIG. 3 may engage vessel V, and/or the distal end ofdistal section 24 may be biased radially outward with respect to the proximal end (seeFIG. 3 ) to enhance the engagement betweendistal section 24 and the vessel wall. - With
distal section 24 anchored distal of aneurysm A,outer sheath 64 then is further retracted proximally to causedistal turn 34 ofproximal section 22 to unwind and deploy to its predetermined shape, as shown inFIG. 7C . As the outer sheath is further retracted, eachsubsequent turn 26 unwinds one at a time and engages and conforms to an inner wall of vessel V in a controlled manner. Whenprosthesis system 20 is fully deployed, delivery system 60 then is proximally retracted overguide wire 70 and withdrawn from the patient's vessel, and guidewire 70 is removed. - In accordance with one aspect of the present invention, deploying
distal section 24 prior to deployingproximal section 22 allowsdistal section 24 to serve as an anchoring mechanism that allows for a controlled deployment of the helical turns ofproximal section 22. Advantageously, turns 26 ofproximal section 22 will be accurately deployed within vessel V, with substantially no proximal or distal shifting with respect to the vessel asouter sheath 64 is retracted. - Moreover, by deploying
distal section 24 prior to deployingproximal section 22, drawbacks associated with the device described in the above-referenced publication to Rivelli may be overcome. Specifically, without a distal anchoring element, the multiplicity of turns of the stent described in the Rivelli publication may experience a tendency to “bunch up,” i.e., overlay one another, as the outer sheath is retracted due to friction between the turns and the outer sheath. In the present invention,distal section 24 serves as an anchoring mechanism prior to retraction of the outer sheath over the proximal section. Accordingly, such a distal anchoring mechanism overcomes potential friction and turns 26 will be less likely to bunch up. - In accordance with another aspect of the present invention,
vascular prosthesis 20 of the present invention is configured to be flexible enough to substantially conform to the shape of vessel V without causing the vessel to remodel. In particular, the zig-zag configuration ofdistal section 24 and the helical configuration ofproximal section 22 allow for increased flexibility ofprosthesis 20. The pitch associated with plurality ofturns 26 may be varied to vary the overall flexibility ofproximal section 22. A lower pitch, whereby adjacent turns 26 are spaced relatively close together, may be employed to increase flexibility ofproximal section 22. A lower pitch is desirable, for example, to treat cerebral aneurysms so that turns 26 may conform to the vasculature without causing remodeling of the vessel. Conversely, a higher pitch, whereby adjacent turns 26 are spaced further apart, may be employed to increase the rigidity ofproximal section 22. Such a design may be desirable for use in maintaining patency in a stenosed vessel by increasing rigidity ofproximal section 22. As a yet further embodiment, the width of the coil may be tapered, as described in the Rivelli publication. - In accordance with another aspect of the present invention, covered
sections 39 may be positioned to overlay aneurysm A to significantly reduce blood flow into aneurysm A. Alternatively, smallerrectangular openings 28 or smallcircular openings 29 may overlay aneurysm A to reduce blood flow into the sac of the aneurysm. Over time, the intima of vessel V will grow over plurality ofturns 26 ofproximal section 22 to completely exclude the aneurysm A from vessel V. - As noted hereinabove, the configuration of
proximal section 22 depicted inFIG. 7C is merely for illustrative purposes. Any combination of coveredsections 39,circular openings 29, large or small rectangular openings, or any other shape may be provided along turns 26, as desired. Plurality ofturns 26 similarly may exclusively comprise one type of opening, e.g., smallcircular openings 29. Alternatively, plurality ofturns 26 may be completely solid such that the openings are omitted altogether. - In accordance with yet another aspect of the present invention, therapeutic agents may be delivered to expedite treatment of the aneurysm or prevent restenosis. As described hereinabove with respect to
FIG. 5 ,therapeutic agent 54 may be delivered to a desired location within vessel V, either using internal or external dimples 50, throughholes 52,elastomeric polymer 56 and/orsolid regions 33 of one or more turns 26. -
Therapeutic agent 54 may include, for example, antiplatelet drugs, anticoagulant drugs, agents used for purposes of providing gene therapy to a target region, or any other agent, and may be tailored for a particular application. Radiopaque markers (not shown) may be selectively disposed onturns 26 in the vicinity of the therapeutic agents to facilitate alignment of the therapeutic agents with a target site of a vessel wall. Advantageously, higher doses of such agents may be provided usingvascular prosthesis 20 of the present invention, relative to previously known coils or stents having interconnected struts, due to the increased surface area associated withturns 26. - Referring now to
FIGS. 8 , an alternative embodiment of the vascular prosthesis of the present invention is described.Vascular prosthesis 120 comprisesproximal section 122 anddistal sections 124.Distal section 124 preferably is provided in accordance withdistal section 24 ofFIG. 1 and comprises a generally zig-zagconfiguration including struts 131 and bends 132. -
Proximal section 122 includes a plurality of individual helical turns 126. Each turn has a distal end that is coupled to arespective bend 132 ofdistal section 124 atjunctions 127, as shown inFIGS. 8 . Individual helical turns 126 are aligned in a pattern such that each turn maintains its own helical curvature without overlapping with an adjacent turn, as depicted inFIG. 8 . Individual helical turns 126 ofvascular prosthesis 120 may be heat treated to self-deploy to the configuration shown, and may be wound down to a small diameter in which turns 126 are constrained within delivery system 60 ofFIG. 6 . The deployment ofvascular prosthesis 120 is substantially similar to the deployment ofprosthesis 20, as described in detail hereinabove with respect toFIGS. 7 , andvascular prosthesis 120 encompasses many of the advantages noted hereinabove with respect tovascular prosthesis 20. - Referring to
FIGS. 9A and 9B ,vascular prosthesis 140 is described and includestorsional stabilizer 146 according to the principles present invention.Vascular prosthesis 140 comprises aproximal section 142,distal section 144 andtorsional stabilizer 146.Proximal section 142,distal section 144 andtorsional stabilizer 146 are joined atjunction 148. Each of the proximal section, distal section and torsional stabilizer are capable of assuming contracted and deployed states, and each are depicted in their respective deployed states inFIGS. 9A and 9B . - In operation,
distal section 144 is configured to be deployed within a vessel beforetorsional stabilizer 146, which is configured to be deployed beforeproximal section 142. Deployingdistal section 144 first allows the distal section to serve as an anchor controls subsequent deployment of the helical turns ofproximal section 142.Torsional stabilizer 146 provides further contact with the vessel wall, thereby providing an additional anchor that transmits torsional forces proximally during deployment ofproximal section 142.Distal section 144 andtorsional stabilizer 146 preferably work in conjunction to balance the torsional force of the proximal section and thus stabilize the vascular prosthesis. This action is expected to further reduce shifting with respect to the vessel wall during deployment ofproximal section 142. Advantageously, the above-identified order of deployment alleviates drawbacks associated with the prior art such as the tendency of the turns of the proximal section to “bunch up” during deployment. - The vascular prosthesis, including
distal section 144,proximal section 142 andtorsional stabilizer 146, preferably is formed from a solid tubular member comprising a shape memory material, such as Nitinol, processed as described above with respect to the embodiment ofFIGS. 1 . According to some embodiments,torsional stabilizer 146 includes at least one dimple or through-hole disposed on a solid portion of the torsional stabilizer. - Referring still to
FIGS. 9 , in the deployed statedistal section 144 has a cell-like configuration comprising a pair zig-zags 144 a, 144 b joined bystruts 144 c. Alternatively,distal section 144 may include a single zig-zag configuration, such as described with respect toFIGS. 1 . The cell configuration of FIGS. 9 is expected to be more rigid than the single zig-zag configuration, and hence is capable of applying, and withstanding, greater radial force. Either configuration ofdistal section 144 may be formed by laser cutting a solid tube, as described hereinabove, to form the requisite pattern. Of course, as would be understood by those of ordinary skill in the art,distal section 144 may have many other configurations without departing from the scope of the present invention. -
Proximal section 142 preferably comprises a helical ribbon including plurality ofturns 152 having multiplicity ofopenings 154 provided in varying shapes and sizes. The multiplicity of openings are disposed betweensolid regions 150 of the shape memory material used to formvascular prosthesis 140.Proximal section 142 alternatively may comprise the helical mesh configuration of FIGS. 1 or any other suitable pattern.Proximal section 142 includesdistal turn 156 that transitions intotorsional stabilizer 146.Torsional stabilizer 146 comprisesstrut 158 that preferably remains substantially parallel todistal section 144. - Referring to
FIGS. 9 and 10 ,distal section 144 is coupled toproximal section 142 atjunction 148. More particularly, strut 144 b extends in a proximaldirection forming neck 149, which is attached toproximal section 142 atjunction 148. It will be apparent to those skilled in the art that other strut arrangements may be employed to connectdistal section 144 toproximal section 142. For example, more than one strut may be coupled betweenproximal section 142 anddistal section 144. Alternatively,proximal section 142 anddistal section 144 may be manufactured as two distinct sections, then coupled together. - In
FIG. 10 , the distal section and proximal section are mapped onto an X-Y coordinate system withjunction 148 substantially defining an origin (X=0, Y=0). The X-axis is substantially parallel to a longitudinal axis ofvascular prosthesis 140 and the Y-axis is substantially orthogonal to the longitudinal axis ofvascular prosthesis 140.Torsional stabilizer 146 generally comprises the portion of the proximal section that extends past the plane of theX-axis junction 148. According to one aspect of the present invention,torsional stabilizer 146 is an extension ofproximal section 142 and may comprise a continuation of the helical pattern of the proximal section. -
Torsional stabilizer 146 optionally may be biased outwardly to provide increased frictional contact with the vessel wall.Torsional stabilizer 146 also may comprise one or moreradiopaque markers 160, such as a radiopaque marker band or coating.Radiopaque marker 160 facilitates positioning oftorsional stabilizer 146 at a desired longitudinal position within a patient's vessel, and further facilitates alignment ofvascular prosthesis 140 at a desired radial orientation within the vessel. For example,radiopaque marker 160 may be used to orient the prosthesis axially within the body vessel. - In
FIG. 11 , alternativevascular prosthesis 140′ is shown havingtorsional stabilizer 162 in accordance with the principles of the present invention.Torsional stabilizer 162 comprisesloop 164 of material that extends past the plane of the X-axis.Loop 164 is shaped substantially triangularly and includes first segment 164 a disposed substantially parallel to the Y-axis, second segment 164 b coupled to the proximal section, andthird segment 164 c. As would be appreciated by those of skill in the art,torsional stabilizer 162 may include other shapes and configurations without departing from the scope of the present invention. By way of example,torsional stabilizer 162 may comprise two or more interconnected curvilinear loops. - In
FIG. 12 , further alternativevascular prosthesis 140″ includestorsional stabilizer 168.Torsional stabilizer 168 comprisesloop 170 of material that extends past the plane of both the X-axis and Y-axes, and illustratively includes semicircular portion 170 a. Of course, as would be appreciated by those of skill in the art,torsional stabilizer 168 may include other shapes and configurations without departing from the scope of the present invention. - While preferred illustrative embodiments of the invention are described above, it will be apparent to one skilled in the art that various changes and modifications may be made therein without departing from the invention. The appended claims are intended to cover all such changes and modifications that fall within the true spirit and scope of the invention.
Claims (20)
1. A vascular prosthesis for implantation in a body vessel having a vessel wall, the vascular prosthesis comprising:
a proximal section comprising a plurality of helical turns and a distal end;
a distal section joined to the distal end, the distal section forming a self-expanding anchor; and
a torsional stabilizer coupled to the distal end of the proximal section.
2. The vascular prosthesis of claim 1 , wherein the proximal section, distal section and torsional stabilizer each are capable of assuming a contracted state suitable for transluminal insertion into the body vessel and a deployed state wherein the proximal section, distal section and torsional stabilizer engage the vessel wall.
3. The vascular prosthesis of claim 2 , wherein the distal section is configured to be deployed within the body vessel before the proximal section and torsional stabilizer are deployed.
4. The vascular prosthesis of claim 2 , wherein the torsional stabilizer is configured to be deployed before the proximal section is deployed, but after the distal section is deployed.
5. The vascular prosthesis of claim 2 , wherein the distal section is configured to engage the vessel wall to retain the vascular prosthesis in position during deployment of the torsional stabilizer and proximal section.
6. The vascular prosthesis of claim 1 , wherein the torsional stabilizer enhances frictional engagement with the vessel wall.
7. The vascular prosthesis of claim 1 , wherein the torsional stabilizer comprises a loop.
8. The vascular prosthesis of claim 1 , wherein the torsional stabilizer comprises a continuation of the proximal section.
9. The vascular prosthesis of claim 1 , wherein the torsional stabilizer is configured to partially overlap the distal section.
10. The vascular prosthesis of claim 1 , wherein, in a fully deployed configuration, the torsional stabilizer and the distal section are oriented substantially parallel to one another.
11. The vascular prosthesis of claim 1 , wherein the torsional stabilizer is biased outwardly to provide increased frictional contact with the vessel wall.
12. The vascular prosthesis of claim 1 , wherein the proximal section, distal section and torsional stabilizer comprise a nickel titanium alloy.
13. The vascular prosthesis of claim 1 , wherein the proximal and distal sections may be manufactured as two distinct sections, then coupled together.
14. The vascular prosthesis of claim 1 , further comprising at least one through-hole disposed on a solid portion of the torsional stabilizer, the through-hole configured to contain a therapeutic agent.
15. The vascular prosthesis of claim 1 , wherein the torsional stabilizer is used to orient the prosthesis axially within the body vessel.
16. A vascular prosthesis for implantation in a body vessel having a vessel wall, the vascular prosthesis including a longitudinal axis, the vascular prosthesis comprising:
a proximal section comprising a plurality of helical turns and a distal end;
a self-expanding distal section coupled to the distal end of the helical body at a junction; and
a torsional stabilizer coupled to the distal end of the proximal section.
17. The vascular prosthesis of claim 16 , wherein the junction defines an origin of an X-Y coordinate system, wherein an X-axis is substantially parallel to a longitudinal axis of vascular prosthesis and a Y-axis is substantially orthogonal to the longitudinal axis of vascular prosthesis.
18. The vascular prosthesis of claim 16 , wherein the torsional stabilizer extends past a plane of the X-axis.
19. The vascular prosthesis of claim 16 , wherein the torsional stabilizer extends past a plane of the Y-axis.
20. The vascular prosthesis of claim 16 , wherein the torsional stabilizer includes one or more radiopaque markers to facilitate alignment of the vascular prosthesis at a desired radial orientation within the vessel.
Priority Applications (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/723,565 US20050165469A1 (en) | 2002-12-24 | 2003-11-25 | Vascular prosthesis including torsional stabilizer and methods of use |
AU2003300323A AU2003300323A1 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
US10/746,668 US7862608B2 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
EP03814356A EP1581147A4 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
CA002508247A CA2508247A1 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
JP2005510057A JP2006513010A (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
PCT/US2003/041122 WO2004058100A2 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US43651602P | 2002-12-24 | 2002-12-24 | |
US10/342,427 US7846198B2 (en) | 2002-12-24 | 2003-01-13 | Vascular prosthesis and methods of use |
US10/723,565 US20050165469A1 (en) | 2002-12-24 | 2003-11-25 | Vascular prosthesis including torsional stabilizer and methods of use |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/342,427 Continuation-In-Part US7846198B2 (en) | 2002-12-24 | 2003-01-13 | Vascular prosthesis and methods of use |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/746,668 Continuation-In-Part US7862608B2 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
Publications (1)
Publication Number | Publication Date |
---|---|
US20050165469A1 true US20050165469A1 (en) | 2005-07-28 |
Family
ID=32685982
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/723,565 Abandoned US20050165469A1 (en) | 2002-12-24 | 2003-11-25 | Vascular prosthesis including torsional stabilizer and methods of use |
US10/746,668 Expired - Fee Related US7862608B2 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/746,668 Expired - Fee Related US7862608B2 (en) | 2002-12-24 | 2003-12-23 | Vascular prosthesis and methods of use |
Country Status (6)
Country | Link |
---|---|
US (2) | US20050165469A1 (en) |
EP (1) | EP1581147A4 (en) |
JP (1) | JP2006513010A (en) |
AU (1) | AU2003300323A1 (en) |
CA (1) | CA2508247A1 (en) |
WO (1) | WO2004058100A2 (en) |
Cited By (37)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040186556A1 (en) * | 2002-12-24 | 2004-09-23 | Novostent Corporation | Vascular prosthesis and methods of use |
US20050197690A1 (en) * | 2004-03-02 | 2005-09-08 | Masoud Molaei | Medical devices including metallic films and methods for making same |
US20060116748A1 (en) * | 2003-04-14 | 2006-06-01 | Aaron Kaplan | Stepped balloon catheter for treating vascular bifurcations |
US20060142845A1 (en) * | 2004-12-29 | 2006-06-29 | Masoud Molaei | Medical devices including metallic films and methods for making same |
US20060142851A1 (en) * | 2004-12-29 | 2006-06-29 | Masoud Molaei | Medical devices including metallic films and methods for making same |
US20070005126A1 (en) * | 2005-06-30 | 2007-01-04 | Boston Scientific Scimed, Inc. | Hybrid stent |
US20070276460A1 (en) * | 2003-04-14 | 2007-11-29 | Davis H R | Helical ostium support for treating vascular bifurcations |
US20080221665A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US20080221663A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US20080221658A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US20080221657A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Delivery system and method for vascular prosthesis |
US20080294267A1 (en) * | 2007-05-25 | 2008-11-27 | C.R. Bard, Inc. | Twisted stent |
US7481834B2 (en) * | 2003-04-14 | 2009-01-27 | Tryton Medical, Inc. | Stent for placement at luminal os |
US20090149946A1 (en) * | 2007-12-05 | 2009-06-11 | Cook Incorporated | Stent having at least one barb and methods of manufacture |
US20090306755A1 (en) * | 2006-04-20 | 2009-12-10 | Site Specific Therapies Ltd. | Apparatus and method for maintaining fluid flow through body passages |
US7717953B2 (en) | 2004-10-13 | 2010-05-18 | Tryton Medical, Inc. | Delivery system for placement of prosthesis at luminal OS |
US7731747B2 (en) | 2003-04-14 | 2010-06-08 | Tryton Medical, Inc. | Vascular bifurcation prosthesis with multiple thin fronds |
US7803180B2 (en) | 2005-04-04 | 2010-09-28 | Flexible Stenting Solutions, Inc. | Flexible stent |
US7972372B2 (en) * | 2003-04-14 | 2011-07-05 | Tryton Medical, Inc. | Kit for treating vascular bifurcations |
US8083791B2 (en) | 2003-04-14 | 2011-12-27 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US8152841B2 (en) * | 2005-05-16 | 2012-04-10 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US8366763B2 (en) | 2009-07-02 | 2013-02-05 | Tryton Medical, Inc. | Ostium support for treating vascular bifurcations |
US8500794B2 (en) | 2007-08-02 | 2013-08-06 | Flexible Stenting Solutions, Inc. | Flexible stent |
US8591568B2 (en) | 2004-03-02 | 2013-11-26 | Boston Scientific Scimed, Inc. | Medical devices including metallic films and methods for making same |
US8864815B2 (en) | 2004-12-29 | 2014-10-21 | Boston Scientific Scimed, Inc. | Medical devices including metallic film and at least one filament |
US9108018B2 (en) | 2006-04-20 | 2015-08-18 | Limflow Gmbh | Methods for fluid flow through body passages |
US9149376B2 (en) | 2008-10-06 | 2015-10-06 | Cordis Corporation | Reconstrainable stent delivery system |
US9314329B2 (en) | 2013-03-08 | 2016-04-19 | Limflow Gmbh | Methods and systems for providing or maintaining fluid flow through body passages |
US9545263B2 (en) | 2014-06-19 | 2017-01-17 | Limflow Gmbh | Devices and methods for treating lower extremity vasculature |
US9707108B2 (en) | 2010-11-24 | 2017-07-18 | Tryton Medical, Inc. | Support for treating vascular bifurcations |
DE102016118600A1 (en) * | 2016-09-30 | 2018-04-05 | Acandis Gmbh & Co. Kg | Medical device, band-shaped lattice structure, set and method of making the same |
US10398580B2 (en) | 2004-09-08 | 2019-09-03 | Limflow Gmbh | Minimally invasive surgical apparatus and methods |
US10500077B2 (en) | 2012-04-26 | 2019-12-10 | Poseidon Medical Inc. | Support for treating vascular bifurcations |
US10543308B2 (en) | 2017-04-10 | 2020-01-28 | Limflow Gmbh | Methods for routing a guidewire from a first vessel and through a second vessel in lower extremity vasculature |
US10835367B2 (en) | 2013-03-08 | 2020-11-17 | Limflow Gmbh | Devices for fluid flow through body passages |
US11116943B2 (en) | 2018-10-09 | 2021-09-14 | Limflow Gmbh | Methods for accessing pedal veins |
US11612397B2 (en) | 2019-11-01 | 2023-03-28 | Limflow Gmbh | Devices and methods for increasing blood perfusion to a distal extremity |
Families Citing this family (103)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7713297B2 (en) | 1998-04-11 | 2010-05-11 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US8382821B2 (en) * | 1998-12-03 | 2013-02-26 | Medinol Ltd. | Helical hybrid stent |
US20040267349A1 (en) | 2003-06-27 | 2004-12-30 | Kobi Richter | Amorphous metal alloy medical devices |
CA2455349C (en) | 2001-06-18 | 2011-02-15 | Rex Medical, L.P. | Vein filter |
US20060292206A1 (en) | 2001-11-26 | 2006-12-28 | Kim Steven W | Devices and methods for treatment of vascular aneurysms |
US20030195609A1 (en) * | 2002-04-10 | 2003-10-16 | Scimed Life Systems, Inc. | Hybrid stent |
US7481821B2 (en) | 2002-11-12 | 2009-01-27 | Thomas J. Fogarty | Embolization device and a method of using the same |
US7901448B2 (en) * | 2002-12-24 | 2011-03-08 | Novostent Corporation | Vascular prothesis having interdigitating edges and methods of use |
US20050033410A1 (en) * | 2002-12-24 | 2005-02-10 | Novostent Corporation | Vascular prothesis having flexible configuration |
US20040260382A1 (en) * | 2003-02-12 | 2004-12-23 | Fogarty Thomas J. | Intravascular implants and methods of using the same |
ES2346059T3 (en) * | 2003-03-26 | 2010-10-08 | Biosensors International Group Ltd. | IMPLANT SUPPLY CATHETER WITH ELECTROLYTICALLY EROSIONABLE JOINTS. |
US8239045B2 (en) | 2003-06-04 | 2012-08-07 | Synecor Llc | Device and method for retaining a medical device within a vessel |
AU2004251673B2 (en) | 2003-06-04 | 2010-01-28 | Synecor Llc | Intravascular electrophysiological system and methods |
US7617007B2 (en) | 2003-06-04 | 2009-11-10 | Synecor Llc | Method and apparatus for retaining medical implants within body vessels |
US7082336B2 (en) | 2003-06-04 | 2006-07-25 | Synecor, Llc | Implantable intravascular device for defibrillation and/or pacing |
US9155639B2 (en) | 2009-04-22 | 2015-10-13 | Medinol Ltd. | Helical hybrid stent |
US20050015110A1 (en) | 2003-07-18 | 2005-01-20 | Fogarty Thomas J. | Embolization device and a method of using the same |
US7747335B2 (en) | 2003-12-12 | 2010-06-29 | Synecor Llc | Implantable medical device having pre-implant exoskeleton |
US9510929B2 (en) | 2004-01-22 | 2016-12-06 | Argon Medical Devices, Inc. | Vein filter |
US20110208233A1 (en) * | 2004-01-22 | 2011-08-25 | Mcguckin Jr James F | Device for preventing clot migration from left atrial appendage |
US8211140B2 (en) | 2004-01-22 | 2012-07-03 | Rex Medical, L.P. | Vein filter |
US7976562B2 (en) | 2004-01-22 | 2011-07-12 | Rex Medical, L.P. | Method of removing a vein filter |
US8162972B2 (en) | 2004-01-22 | 2012-04-24 | Rex Medical, Lp | Vein filter |
US8062326B2 (en) * | 2004-01-22 | 2011-11-22 | Rex Medical, L.P. | Vein filter |
US8500774B2 (en) | 2004-01-22 | 2013-08-06 | Rex Medical, L.P. | Vein filter |
US20060004438A1 (en) * | 2004-04-30 | 2006-01-05 | Novostent Corporation | Prosthesis, delivery system and method for neurovascular aneurysm repair |
US7763065B2 (en) | 2004-07-21 | 2010-07-27 | Reva Medical, Inc. | Balloon expandable crush-recoverable stent device |
US7018403B1 (en) * | 2004-09-14 | 2006-03-28 | Advanced Cardiovascular Systems, Inc. | Inclined stent pattern for vulnerable plaque |
BRPI0516955A (en) * | 2004-09-24 | 2008-09-30 | Ingeneus Inc | genetic assay |
CA2844155A1 (en) | 2004-09-27 | 2006-04-06 | Rex Medical, L.P. | Vein filter |
US7914570B2 (en) * | 2004-10-07 | 2011-03-29 | Boston Scientific Scimed, Inc. | Non-shortening helical stent |
US8292944B2 (en) | 2004-12-17 | 2012-10-23 | Reva Medical, Inc. | Slide-and-lock stent |
US20060136035A1 (en) * | 2004-12-20 | 2006-06-22 | Vascular Architects, Inc. A Delaware Corporation | Coiled endoluminal prosthesis system and delivery catheter |
US20060136033A1 (en) * | 2004-12-20 | 2006-06-22 | Vascular Architects, Inc. | Coiled stent delivery system and method |
US20060136034A1 (en) * | 2004-12-20 | 2006-06-22 | Vascular Architects, Inc. | Delivery catheter and method |
US9056157B2 (en) * | 2005-03-24 | 2015-06-16 | Medtronic Vascular, Inc. | Hybrid biodegradable/non-biodegradable stent, delivery system and method of treating a vascular condition |
US7914574B2 (en) | 2005-08-02 | 2011-03-29 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US9149378B2 (en) | 2005-08-02 | 2015-10-06 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US8956400B2 (en) * | 2005-10-14 | 2015-02-17 | Flexible Stenting Solutions, Inc. | Helical stent |
US20070173787A1 (en) * | 2005-11-01 | 2007-07-26 | Huang Mark C T | Thin-film nitinol based drug eluting stent |
US20070224235A1 (en) | 2006-03-24 | 2007-09-27 | Barron Tenney | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8187620B2 (en) | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
US7955383B2 (en) * | 2006-04-25 | 2011-06-07 | Medtronics Vascular, Inc. | Laminated implantable medical device having a metallic coating |
US7691400B2 (en) * | 2006-05-05 | 2010-04-06 | Medtronic Vascular, Inc. | Medical device having coating with zeolite drug reservoirs |
US7537608B2 (en) * | 2006-05-23 | 2009-05-26 | Boston Scientific Scimed, Inc. | Stent with variable crimping diameter |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
CA2655793A1 (en) | 2006-06-29 | 2008-01-03 | Boston Scientific Limited | Medical devices with selective coating |
US10076401B2 (en) | 2006-08-29 | 2018-09-18 | Argon Medical Devices, Inc. | Vein filter |
JP2010503469A (en) | 2006-09-14 | 2010-02-04 | ボストン サイエンティフィック リミテッド | Medical device having drug-eluting film |
GB0621048D0 (en) * | 2006-10-23 | 2006-11-29 | Anson Medical Ltd | Helical stent graft |
US7981150B2 (en) | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
US8187315B1 (en) | 2006-12-08 | 2012-05-29 | Cardica, Inc. | Partial stent for treatment of a vascular aneurysm |
US7704275B2 (en) | 2007-01-26 | 2010-04-27 | Reva Medical, Inc. | Circumferentially nested expandable device |
US20080206441A1 (en) * | 2007-02-27 | 2008-08-28 | Medtronic Vascular, Inc. | Ion Beam Etching a Surface of an Implantable Medical Device |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
US8067054B2 (en) | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US7976915B2 (en) | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US8002823B2 (en) | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7942926B2 (en) | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
WO2009012353A2 (en) | 2007-07-19 | 2009-01-22 | Boston Scientific Limited | Endoprosthesis having a non-fouling surface |
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US8815273B2 (en) | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
WO2009018340A2 (en) | 2007-07-31 | 2009-02-05 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
JP2010535541A (en) | 2007-08-03 | 2010-11-25 | ボストン サイエンティフィック リミテッド | Coating for medical devices with large surface area |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US8029554B2 (en) | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
US8216632B2 (en) | 2007-11-02 | 2012-07-10 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7833266B2 (en) | 2007-11-28 | 2010-11-16 | Boston Scientific Scimed, Inc. | Bifurcated stent with drug wells for specific ostial, carina, and side branch treatment |
US7988721B2 (en) | 2007-11-30 | 2011-08-02 | Reva Medical, Inc. | Axially-radially nested expandable device |
CA2711813A1 (en) * | 2008-01-11 | 2009-07-16 | Rex Medical, L.P. | Vein filter |
EP2271380B1 (en) | 2008-04-22 | 2013-03-20 | Boston Scientific Scimed, Inc. | Medical devices having a coating of inorganic material |
WO2009132176A2 (en) | 2008-04-24 | 2009-10-29 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
US10716573B2 (en) | 2008-05-01 | 2020-07-21 | Aneuclose | Janjua aneurysm net with a resilient neck-bridging portion for occluding a cerebral aneurysm |
US10028747B2 (en) | 2008-05-01 | 2018-07-24 | Aneuclose Llc | Coils with a series of proximally-and-distally-connected loops for occluding a cerebral aneurysm |
EP2303350A2 (en) | 2008-06-18 | 2011-04-06 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7951193B2 (en) | 2008-07-23 | 2011-05-31 | Boston Scientific Scimed, Inc. | Drug-eluting stent |
JP5713900B2 (en) * | 2008-08-19 | 2015-05-07 | ティシュージェン, インク. | Self-expanding medical device |
WO2010024868A1 (en) * | 2008-08-27 | 2010-03-04 | Cook Incorporated | Multi-section stent |
CA2737753C (en) | 2008-10-10 | 2017-03-14 | Reva Medical, Inc. | Expandable slide and lock stent |
US8231980B2 (en) | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
WO2010077966A1 (en) | 2008-12-17 | 2010-07-08 | Abbott Laboratories Vascular Enterprises Limited | Methods and apparatus for filtering a body lumen |
US8071156B2 (en) | 2009-03-04 | 2011-12-06 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8287937B2 (en) | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
US8114149B2 (en) * | 2009-10-20 | 2012-02-14 | Svelte Medical Systems, Inc. | Hybrid stent with helical connectors |
US9649211B2 (en) | 2009-11-04 | 2017-05-16 | Confluent Medical Technologies, Inc. | Alternating circumferential bridge stent design and methods for use thereof |
EP2496189A4 (en) | 2009-11-04 | 2016-05-11 | Nitinol Devices And Components Inc | Alternating circumferential bridge stent design and methods for use thereof |
US9358140B1 (en) | 2009-11-18 | 2016-06-07 | Aneuclose Llc | Stent with outer member to embolize an aneurysm |
CA2795292A1 (en) | 2010-04-10 | 2011-10-13 | Reva Medical, Inc. | Expandable slide and lock stent |
DE102010018539A1 (en) * | 2010-04-28 | 2011-11-03 | Acandis Gmbh & Co. Kg | A method of manufacturing a medical device for endoluminal treatments and starting product for the manufacture of a medical device |
US9301864B2 (en) | 2010-06-08 | 2016-04-05 | Veniti, Inc. | Bi-directional stent delivery system |
US8864811B2 (en) | 2010-06-08 | 2014-10-21 | Veniti, Inc. | Bi-directional stent delivery system |
CN103124539B (en) * | 2010-08-02 | 2016-02-24 | 科迪斯公司 | There is the flexible helical stent of different coil region |
US9233014B2 (en) | 2010-09-24 | 2016-01-12 | Veniti, Inc. | Stent with support braces |
US8968386B2 (en) * | 2012-07-11 | 2015-03-03 | The Cleveland Clinic Foundation | Stent and method for maintaining the area of a body lumen |
WO2014159337A1 (en) | 2013-03-14 | 2014-10-02 | Reva Medical, Inc. | Reduced - profile slide and lock stent |
WO2014150223A1 (en) * | 2013-03-15 | 2014-09-25 | Children's Medical Center Corporation | Methods and apparatuses for treating vessels |
US9907684B2 (en) | 2013-05-08 | 2018-03-06 | Aneuclose Llc | Method of radially-asymmetric stent expansion |
US8998986B1 (en) * | 2013-07-05 | 2015-04-07 | Zdzislaw B. Malinowski | Nasal stent |
US10172729B2 (en) | 2015-10-12 | 2019-01-08 | Reflow Medical, Inc. | Stents having protruding drug-delivery features and associated systems and methods |
US10321984B2 (en) * | 2016-02-19 | 2019-06-18 | Cook Medical Technologies Llc | Spiral flow inducing stent and canula cut method of making same |
CN107126299A (en) * | 2017-06-08 | 2017-09-05 | 有研医疗器械(北京)有限公司 | A kind of high submissive type thoracic aorta covered bracket and its shaper and method |
CN117503441B (en) * | 2024-01-08 | 2024-03-29 | 惠凯医疗科技(苏州)有限公司 | Recoverable medicine support and support system |
Citations (62)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4553545A (en) * | 1981-09-16 | 1985-11-19 | Medinvent S.A. | Device for application in blood vessels or other difficultly accessible locations and its use |
US4655771A (en) * | 1982-04-30 | 1987-04-07 | Shepherd Patents S.A. | Prosthesis comprising an expansible or contractile tubular body |
US4665918A (en) * | 1986-01-06 | 1987-05-19 | Garza Gilbert A | Prosthesis system and method |
US4739762A (en) * | 1985-11-07 | 1988-04-26 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US4760849A (en) * | 1985-04-10 | 1988-08-02 | Medinvent S.A. | Planar blank and a coil spring manufactured therefrom |
US4768507A (en) * | 1986-02-24 | 1988-09-06 | Medinnovations, Inc. | Intravascular stent and percutaneous insertion catheter system for the dilation of an arterial stenosis and the prevention of arterial restenosis |
US4886062A (en) * | 1987-10-19 | 1989-12-12 | Medtronic, Inc. | Intravascular radially expandable stent and method of implant |
US5019090A (en) * | 1988-09-01 | 1991-05-28 | Corvita Corporation | Radially expandable endoprosthesis and the like |
US5104404A (en) * | 1989-10-02 | 1992-04-14 | Medtronic, Inc. | Articulated stent |
US5147370A (en) * | 1991-06-12 | 1992-09-15 | Mcnamara Thomas O | Nitinol stent for hollow body conduits |
US5246445A (en) * | 1990-04-19 | 1993-09-21 | Instent Inc. | Device for the treatment of constricted ducts in human bodies |
US5314444A (en) * | 1987-03-13 | 1994-05-24 | Cook Incorporated | Endovascular stent and delivery system |
US5344426A (en) * | 1990-04-25 | 1994-09-06 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5383892A (en) * | 1991-11-08 | 1995-01-24 | Meadox France | Stent for transluminal implantation |
US5421955A (en) * | 1991-10-28 | 1995-06-06 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
US5423885A (en) * | 1992-01-31 | 1995-06-13 | Advanced Cardiovascular Systems, Inc. | Stent capable of attachment within a body lumen |
US5441515A (en) * | 1993-04-23 | 1995-08-15 | Advanced Cardiovascular Systems, Inc. | Ratcheting stent |
US5443500A (en) * | 1989-01-26 | 1995-08-22 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US5476505A (en) * | 1993-11-18 | 1995-12-19 | Advanced Cardiovascular Systems, Inc. | Coiled stent and delivery system |
US5540713A (en) * | 1991-10-11 | 1996-07-30 | Angiomed Ag | Apparatus for widening a stenosis in a body cavity |
US5551954A (en) * | 1991-10-04 | 1996-09-03 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
US5556413A (en) * | 1994-03-11 | 1996-09-17 | Advanced Cardiovascular Systems, Inc. | Coiled stent with locking ends |
US5607478A (en) * | 1996-03-14 | 1997-03-04 | Meadox Medicals Inc. | Yarn wrapped PTFE tubular prosthesis |
US5716396A (en) * | 1993-09-16 | 1998-02-10 | Cordis Corporation | Endoprosthesis having multiple laser welded junctions method and procedure |
US5817152A (en) * | 1994-10-19 | 1998-10-06 | Birdsall; Matthew | Connected stent apparatus |
US5824052A (en) * | 1997-03-18 | 1998-10-20 | Endotex Interventional Systems, Inc. | Coiled sheet stent having helical articulation and methods of use |
US5824053A (en) * | 1997-03-18 | 1998-10-20 | Endotex Interventional Systems, Inc. | Helical mesh endoprosthesis and methods of use |
US5830179A (en) * | 1996-04-09 | 1998-11-03 | Endocare, Inc. | Urological stent therapy system and method |
US5833699A (en) * | 1996-04-10 | 1998-11-10 | Chuter; Timothy A. M. | Extending ribbon stent |
US5876432A (en) * | 1994-04-01 | 1999-03-02 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US6086604A (en) * | 1994-02-25 | 2000-07-11 | Fischell; Robert E. | Stent having a multiplicity of undulating longitudinals |
US6156062A (en) * | 1997-12-03 | 2000-12-05 | Ave Connaught | Helically wrapped interlocking stent |
US6238430B1 (en) * | 1999-02-26 | 2001-05-29 | Vascular Architects, Inc. | Catheter assembly with controlled release endoluminal prosthesis and method for placing |
US6273908B1 (en) * | 1997-10-24 | 2001-08-14 | Robert Ndondo-Lay | Stents |
US6331189B1 (en) * | 1999-10-18 | 2001-12-18 | Medtronic, Inc. | Flexible medical stent |
US6334870B1 (en) * | 1997-04-25 | 2002-01-01 | Scimed Life Systems, Inc. | Stent configurations including spirals |
US20020004676A1 (en) * | 1996-12-09 | 2002-01-10 | George Wallace | Intracranial stent and method of use |
US6348065B1 (en) * | 1995-03-01 | 2002-02-19 | Scimed Life Systems, Inc. | Longitudinally flexible expandable stent |
US6409754B1 (en) * | 1999-07-02 | 2002-06-25 | Scimed Life Systems, Inc. | Flexible segmented stent |
US20020095206A1 (en) * | 1997-06-13 | 2002-07-18 | Addonizio Scott J. | Stent having helical elements |
US6423091B1 (en) * | 2000-05-16 | 2002-07-23 | Cordis Corporation | Helical stent having flat ends |
US6425915B1 (en) * | 1997-03-18 | 2002-07-30 | Endotex Interventional Systems, Inc. | Helical mesh endoprosthesis and methods of use |
US6432128B1 (en) * | 1996-09-18 | 2002-08-13 | Micro Therapeutics, Inc. | Intracranial stent and method of use |
US6503270B1 (en) * | 1998-12-03 | 2003-01-07 | Medinol Ltd. | Serpentine coiled ladder stent |
US6508834B1 (en) * | 1994-03-17 | 2003-01-21 | Medinol Ltd. | Articulated stent |
US6520984B1 (en) * | 2000-04-28 | 2003-02-18 | Cardiovasc, Inc. | Stent graft assembly and method |
US6533805B1 (en) * | 1996-04-01 | 2003-03-18 | General Surgical Innovations, Inc. | Prosthesis and method for deployment within a body lumen |
US6540775B1 (en) * | 2000-06-30 | 2003-04-01 | Cordis Corporation | Ultraflexible open cell stent |
US6562065B1 (en) * | 1998-03-30 | 2003-05-13 | Conor Medsystems, Inc. | Expandable medical device with beneficial agent delivery mechanism |
US6565600B2 (en) * | 1997-03-10 | 2003-05-20 | Cordis Corporation | Articulated expandable intraluminal stent |
US6572643B1 (en) * | 2000-07-19 | 2003-06-03 | Vascular Architects, Inc. | Endoprosthesis delivery catheter assembly and method |
US6576006B2 (en) * | 1996-07-15 | 2003-06-10 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system |
US6596021B1 (en) * | 1999-10-26 | 2003-07-22 | Biotronik Mess -Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin | Stent |
US6607554B2 (en) * | 2001-06-29 | 2003-08-19 | Advanced Cardiovascular Systems, Inc. | Universal stent link design |
US6635084B2 (en) * | 1994-03-17 | 2003-10-21 | Medinol, Ltd. | Flexible expandable stent |
US6656220B1 (en) * | 2002-06-17 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US20040034402A1 (en) * | 2002-07-26 | 2004-02-19 | Syntheon, Llc | Helical stent having flexible transition zone |
US20040044401A1 (en) * | 2002-08-30 | 2004-03-04 | Bales Thomas O. | Helical stent having improved flexibility and expandability |
US6736844B1 (en) * | 1997-03-04 | 2004-05-18 | Bernard Glatt | Helical stent and method for making same |
US6746475B1 (en) * | 1999-04-15 | 2004-06-08 | Scimed Life Systems, Inc. | Stent with variable stiffness |
US20040172123A1 (en) * | 2002-12-20 | 2004-09-02 | Biotronik Gmbh & Co. Kg | Stent |
Family Cites Families (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5041126A (en) * | 1987-03-13 | 1991-08-20 | Cook Incorporated | Endovascular stent and delivery system |
US4969458A (en) * | 1987-07-06 | 1990-11-13 | Medtronic, Inc. | Intracoronary stent and method of simultaneous angioplasty and stent implant |
US5342387A (en) * | 1992-06-18 | 1994-08-30 | American Biomed, Inc. | Artificial support for a blood vessel |
DE69432145T2 (en) * | 1993-03-11 | 2004-01-15 | Medinol Ltd | STENT |
ES2157977T3 (en) * | 1993-07-23 | 2001-09-01 | Cook Inc | FLEXIBLE PROBE THAT HAS A CONFORMED CONFIGURATION FROM A MATERIAL SHEET. |
US5575818A (en) * | 1995-02-14 | 1996-11-19 | Corvita Corporation | Endovascular stent with locking ring |
BE1009278A3 (en) * | 1995-04-12 | 1997-01-07 | Corvita Europ | Guardian self-expandable medical device introduced in cavite body, and medical device with a stake as. |
KR100325267B1 (en) | 1995-04-26 | 2003-10-11 | 메디놀 리미티드 | Articulating stent |
US5603722A (en) * | 1995-06-06 | 1997-02-18 | Quanam Medical Corporation | Intravascular stent |
US5954744A (en) * | 1995-06-06 | 1999-09-21 | Quanam Medical Corporation | Intravascular stent |
WO1997021399A1 (en) * | 1995-12-11 | 1997-06-19 | Ali Hassan | Device for stabilising angioplastically treated partial regions of a vessel wall (stent) |
NZ331269A (en) * | 1996-04-10 | 2000-01-28 | Advanced Cardiovascular System | Expandable stent, its structural strength varying along its length |
US6592617B2 (en) * | 1996-04-30 | 2003-07-15 | Boston Scientific Scimed, Inc. | Three-dimensional braided covered stent |
US5817126A (en) * | 1997-03-17 | 1998-10-06 | Surface Genesis, Inc. | Compound stent |
EP1087801B1 (en) * | 1998-06-26 | 2002-01-16 | Quanam Medical Corporation | Topoisomerase inhibitors for prevention of restenosis |
WO2001089421A2 (en) * | 2000-05-22 | 2001-11-29 | Orbus Medical Technologies Inc. | Self-expanding stent |
US7846198B2 (en) * | 2002-12-24 | 2010-12-07 | Novostent Corporation | Vascular prosthesis and methods of use |
US20050165469A1 (en) * | 2002-12-24 | 2005-07-28 | Michael Hogendijk | Vascular prosthesis including torsional stabilizer and methods of use |
US20070185560A1 (en) * | 2005-11-28 | 2007-08-09 | Cook Incorporated | Expandable stent |
-
2003
- 2003-11-25 US US10/723,565 patent/US20050165469A1/en not_active Abandoned
- 2003-12-23 EP EP03814356A patent/EP1581147A4/en not_active Ceased
- 2003-12-23 US US10/746,668 patent/US7862608B2/en not_active Expired - Fee Related
- 2003-12-23 JP JP2005510057A patent/JP2006513010A/en active Pending
- 2003-12-23 CA CA002508247A patent/CA2508247A1/en not_active Abandoned
- 2003-12-23 AU AU2003300323A patent/AU2003300323A1/en not_active Abandoned
- 2003-12-23 WO PCT/US2003/041122 patent/WO2004058100A2/en active Search and Examination
Patent Citations (70)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4553545A (en) * | 1981-09-16 | 1985-11-19 | Medinvent S.A. | Device for application in blood vessels or other difficultly accessible locations and its use |
US4655771A (en) * | 1982-04-30 | 1987-04-07 | Shepherd Patents S.A. | Prosthesis comprising an expansible or contractile tubular body |
US4655771B1 (en) * | 1982-04-30 | 1996-09-10 | Medinvent Ams Sa | Prosthesis comprising an expansible or contractile tubular body |
US4760849A (en) * | 1985-04-10 | 1988-08-02 | Medinvent S.A. | Planar blank and a coil spring manufactured therefrom |
US4739762A (en) * | 1985-11-07 | 1988-04-26 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US4739762B1 (en) * | 1985-11-07 | 1998-10-27 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4665918A (en) * | 1986-01-06 | 1987-05-19 | Garza Gilbert A | Prosthesis system and method |
US4768507A (en) * | 1986-02-24 | 1988-09-06 | Medinnovations, Inc. | Intravascular stent and percutaneous insertion catheter system for the dilation of an arterial stenosis and the prevention of arterial restenosis |
US5314444A (en) * | 1987-03-13 | 1994-05-24 | Cook Incorporated | Endovascular stent and delivery system |
US4886062A (en) * | 1987-10-19 | 1989-12-12 | Medtronic, Inc. | Intravascular radially expandable stent and method of implant |
US5019090A (en) * | 1988-09-01 | 1991-05-28 | Corvita Corporation | Radially expandable endoprosthesis and the like |
US5443500A (en) * | 1989-01-26 | 1995-08-22 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US5104404A (en) * | 1989-10-02 | 1992-04-14 | Medtronic, Inc. | Articulated stent |
US5246445A (en) * | 1990-04-19 | 1993-09-21 | Instent Inc. | Device for the treatment of constricted ducts in human bodies |
US5344426A (en) * | 1990-04-25 | 1994-09-06 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5147370A (en) * | 1991-06-12 | 1992-09-15 | Mcnamara Thomas O | Nitinol stent for hollow body conduits |
US5551954A (en) * | 1991-10-04 | 1996-09-03 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
US5540713A (en) * | 1991-10-11 | 1996-07-30 | Angiomed Ag | Apparatus for widening a stenosis in a body cavity |
US5421955B1 (en) * | 1991-10-28 | 1998-01-20 | Advanced Cardiovascular System | Expandable stents and method for making same |
US5421955A (en) * | 1991-10-28 | 1995-06-06 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
US5383892A (en) * | 1991-11-08 | 1995-01-24 | Meadox France | Stent for transluminal implantation |
US5423885A (en) * | 1992-01-31 | 1995-06-13 | Advanced Cardiovascular Systems, Inc. | Stent capable of attachment within a body lumen |
US5441515A (en) * | 1993-04-23 | 1995-08-15 | Advanced Cardiovascular Systems, Inc. | Ratcheting stent |
US5716396A (en) * | 1993-09-16 | 1998-02-10 | Cordis Corporation | Endoprosthesis having multiple laser welded junctions method and procedure |
US5476505A (en) * | 1993-11-18 | 1995-12-19 | Advanced Cardiovascular Systems, Inc. | Coiled stent and delivery system |
US6086604A (en) * | 1994-02-25 | 2000-07-11 | Fischell; Robert E. | Stent having a multiplicity of undulating longitudinals |
US5556413A (en) * | 1994-03-11 | 1996-09-17 | Advanced Cardiovascular Systems, Inc. | Coiled stent with locking ends |
US6589276B2 (en) * | 1994-03-17 | 2003-07-08 | Medinol Ltd. | Articulated stent |
US6508834B1 (en) * | 1994-03-17 | 2003-01-21 | Medinol Ltd. | Articulated stent |
US6635084B2 (en) * | 1994-03-17 | 2003-10-21 | Medinol, Ltd. | Flexible expandable stent |
US5876432A (en) * | 1994-04-01 | 1999-03-02 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US5817152A (en) * | 1994-10-19 | 1998-10-06 | Birdsall; Matthew | Connected stent apparatus |
US6348065B1 (en) * | 1995-03-01 | 2002-02-19 | Scimed Life Systems, Inc. | Longitudinally flexible expandable stent |
US5607478A (en) * | 1996-03-14 | 1997-03-04 | Meadox Medicals Inc. | Yarn wrapped PTFE tubular prosthesis |
US6533805B1 (en) * | 1996-04-01 | 2003-03-18 | General Surgical Innovations, Inc. | Prosthesis and method for deployment within a body lumen |
US5830179A (en) * | 1996-04-09 | 1998-11-03 | Endocare, Inc. | Urological stent therapy system and method |
US5833699A (en) * | 1996-04-10 | 1998-11-10 | Chuter; Timothy A. M. | Extending ribbon stent |
US6576006B2 (en) * | 1996-07-15 | 2003-06-10 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system |
US6432128B1 (en) * | 1996-09-18 | 2002-08-13 | Micro Therapeutics, Inc. | Intracranial stent and method of use |
US20020004676A1 (en) * | 1996-12-09 | 2002-01-10 | George Wallace | Intracranial stent and method of use |
US6736844B1 (en) * | 1997-03-04 | 2004-05-18 | Bernard Glatt | Helical stent and method for making same |
US6565600B2 (en) * | 1997-03-10 | 2003-05-20 | Cordis Corporation | Articulated expandable intraluminal stent |
US5824052A (en) * | 1997-03-18 | 1998-10-20 | Endotex Interventional Systems, Inc. | Coiled sheet stent having helical articulation and methods of use |
US5824053A (en) * | 1997-03-18 | 1998-10-20 | Endotex Interventional Systems, Inc. | Helical mesh endoprosthesis and methods of use |
US6425915B1 (en) * | 1997-03-18 | 2002-07-30 | Endotex Interventional Systems, Inc. | Helical mesh endoprosthesis and methods of use |
US6334870B1 (en) * | 1997-04-25 | 2002-01-01 | Scimed Life Systems, Inc. | Stent configurations including spirals |
US20020095206A1 (en) * | 1997-06-13 | 2002-07-18 | Addonizio Scott J. | Stent having helical elements |
US6273908B1 (en) * | 1997-10-24 | 2001-08-14 | Robert Ndondo-Lay | Stents |
US6156062A (en) * | 1997-12-03 | 2000-12-05 | Ave Connaught | Helically wrapped interlocking stent |
US6562065B1 (en) * | 1998-03-30 | 2003-05-13 | Conor Medsystems, Inc. | Expandable medical device with beneficial agent delivery mechanism |
US6503270B1 (en) * | 1998-12-03 | 2003-01-07 | Medinol Ltd. | Serpentine coiled ladder stent |
US6660032B2 (en) * | 1999-02-26 | 2003-12-09 | Vascular Architects, Inc. | Expandable coil endoluminal prosthesis |
US6238430B1 (en) * | 1999-02-26 | 2001-05-29 | Vascular Architects, Inc. | Catheter assembly with controlled release endoluminal prosthesis and method for placing |
US20010020182A1 (en) * | 1999-02-26 | 2001-09-06 | Klumb Katherine J. | Expandable coil endoluminal prosthesis |
US6248122B1 (en) * | 1999-02-26 | 2001-06-19 | Vascular Architects, Inc. | Catheter with controlled release endoluminal prosthesis |
US6645237B2 (en) * | 1999-02-26 | 2003-11-11 | Vascular Architects, Inc. | Expandable coiled endoluminal prosthesis |
US6746475B1 (en) * | 1999-04-15 | 2004-06-08 | Scimed Life Systems, Inc. | Stent with variable stiffness |
US6409754B1 (en) * | 1999-07-02 | 2002-06-25 | Scimed Life Systems, Inc. | Flexible segmented stent |
US6331189B1 (en) * | 1999-10-18 | 2001-12-18 | Medtronic, Inc. | Flexible medical stent |
US6596021B1 (en) * | 1999-10-26 | 2003-07-22 | Biotronik Mess -Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin | Stent |
US6520984B1 (en) * | 2000-04-28 | 2003-02-18 | Cardiovasc, Inc. | Stent graft assembly and method |
US6423091B1 (en) * | 2000-05-16 | 2002-07-23 | Cordis Corporation | Helical stent having flat ends |
US6540775B1 (en) * | 2000-06-30 | 2003-04-01 | Cordis Corporation | Ultraflexible open cell stent |
US6572643B1 (en) * | 2000-07-19 | 2003-06-03 | Vascular Architects, Inc. | Endoprosthesis delivery catheter assembly and method |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US6607554B2 (en) * | 2001-06-29 | 2003-08-19 | Advanced Cardiovascular Systems, Inc. | Universal stent link design |
US6656220B1 (en) * | 2002-06-17 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US20040034402A1 (en) * | 2002-07-26 | 2004-02-19 | Syntheon, Llc | Helical stent having flexible transition zone |
US20040044401A1 (en) * | 2002-08-30 | 2004-03-04 | Bales Thomas O. | Helical stent having improved flexibility and expandability |
US20040172123A1 (en) * | 2002-12-20 | 2004-09-02 | Biotronik Gmbh & Co. Kg | Stent |
Cited By (86)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7862608B2 (en) | 2002-12-24 | 2011-01-04 | Novostent Corporation | Vascular prosthesis and methods of use |
US20040186556A1 (en) * | 2002-12-24 | 2004-09-23 | Novostent Corporation | Vascular prosthesis and methods of use |
US8641751B2 (en) | 2003-04-14 | 2014-02-04 | Tryton Medical, Inc. | Vascular bifurcation prosthesis with multiple linked thin fronds |
US8641755B2 (en) | 2003-04-14 | 2014-02-04 | Tryton Medical, Inc. | Prosthesis for treating vascular bifurcations |
US7481834B2 (en) * | 2003-04-14 | 2009-01-27 | Tryton Medical, Inc. | Stent for placement at luminal os |
US9775728B2 (en) | 2003-04-14 | 2017-10-03 | Tryton Medical, Inc. | Vascular bifurcation prosthesis |
US20070203571A1 (en) * | 2003-04-14 | 2007-08-30 | Tryton Medical, Inc. | Prosthesis for treating vascular bifurcations |
US20070276460A1 (en) * | 2003-04-14 | 2007-11-29 | Davis H R | Helical ostium support for treating vascular bifurcations |
US8083791B2 (en) | 2003-04-14 | 2011-12-27 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US8876884B2 (en) | 2003-04-14 | 2014-11-04 | Tryton Medical, Inc. | Prosthesis and deployment catheter for treating vascular bifurcations |
US20060116748A1 (en) * | 2003-04-14 | 2006-06-01 | Aaron Kaplan | Stepped balloon catheter for treating vascular bifurcations |
US7758630B2 (en) | 2003-04-14 | 2010-07-20 | Tryton Medical, Inc. | Helical ostium support for treating vascular bifurcations |
US7972372B2 (en) * | 2003-04-14 | 2011-07-05 | Tryton Medical, Inc. | Kit for treating vascular bifurcations |
US8109987B2 (en) | 2003-04-14 | 2012-02-07 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US8672994B2 (en) | 2003-04-14 | 2014-03-18 | Tryton Medical, Inc. | Prosthesis for treating vascular bifurcations |
US8529618B2 (en) | 2003-04-14 | 2013-09-10 | Tryton Medical, Inc. | Ostium support for treating vascular bifurcations |
US8257432B2 (en) | 2003-04-14 | 2012-09-04 | Tryton Medical, Inc. | Vascular bifurcation prosthesis with at least one frond |
US8187314B2 (en) | 2003-04-14 | 2012-05-29 | Tryton Medical, Inc. | Prothesis and deployment catheter for treating vascular bifurcations |
US7731747B2 (en) | 2003-04-14 | 2010-06-08 | Tryton Medical, Inc. | Vascular bifurcation prosthesis with multiple thin fronds |
US8998973B2 (en) | 2004-03-02 | 2015-04-07 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US8591568B2 (en) | 2004-03-02 | 2013-11-26 | Boston Scientific Scimed, Inc. | Medical devices including metallic films and methods for making same |
US20050197690A1 (en) * | 2004-03-02 | 2005-09-08 | Masoud Molaei | Medical devices including metallic films and methods for making same |
US10398580B2 (en) | 2004-09-08 | 2019-09-03 | Limflow Gmbh | Minimally invasive surgical apparatus and methods |
US11446170B2 (en) | 2004-09-08 | 2022-09-20 | Limflow Gmbh | Minimally invasive surgical apparatus and methods |
US7972369B2 (en) | 2004-10-13 | 2011-07-05 | Tryton Medical, Inc. | Method for delivering a luminal prosthesis |
US7717953B2 (en) | 2004-10-13 | 2010-05-18 | Tryton Medical, Inc. | Delivery system for placement of prosthesis at luminal OS |
US8252038B2 (en) | 2004-10-13 | 2012-08-28 | Tryton Medical, Inc. | System for delivering a prosthesis to a luminal OS |
US8926685B2 (en) | 2004-10-13 | 2015-01-06 | Tryton Medical, Inc. | Prosthesis for placement at a luminal OS |
US8632580B2 (en) | 2004-12-29 | 2014-01-21 | Boston Scientific Scimed, Inc. | Flexible medical devices including metallic films |
US8992592B2 (en) | 2004-12-29 | 2015-03-31 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US20060142845A1 (en) * | 2004-12-29 | 2006-06-29 | Masoud Molaei | Medical devices including metallic films and methods for making same |
US20060142851A1 (en) * | 2004-12-29 | 2006-06-29 | Masoud Molaei | Medical devices including metallic films and methods for making same |
US8864815B2 (en) | 2004-12-29 | 2014-10-21 | Boston Scientific Scimed, Inc. | Medical devices including metallic film and at least one filament |
US7803180B2 (en) | 2005-04-04 | 2010-09-28 | Flexible Stenting Solutions, Inc. | Flexible stent |
US20140379066A1 (en) * | 2005-04-04 | 2014-12-25 | Flexible Stenting Solutions, Inc. | Flexible stent |
US9592137B2 (en) * | 2005-04-04 | 2017-03-14 | Flexible Stenting Solutions, Inc. | Flexible stent |
US8152841B2 (en) * | 2005-05-16 | 2012-04-10 | Boston Scientific Scimed, Inc. | Medical devices including metallic films |
US20070005126A1 (en) * | 2005-06-30 | 2007-01-04 | Boston Scientific Scimed, Inc. | Hybrid stent |
US7637939B2 (en) | 2005-06-30 | 2009-12-29 | Boston Scientific Scimed, Inc. | Hybrid stent |
US10136987B2 (en) | 2006-04-20 | 2018-11-27 | Limflow Gmbh | Devices for fluid flow through body passages |
US9782201B2 (en) | 2006-04-20 | 2017-10-10 | Limflow Gmbh | Methods for fluid flow through body passages |
US9108018B2 (en) | 2006-04-20 | 2015-08-18 | Limflow Gmbh | Methods for fluid flow through body passages |
US20090306755A1 (en) * | 2006-04-20 | 2009-12-10 | Site Specific Therapies Ltd. | Apparatus and method for maintaining fluid flow through body passages |
US10390933B2 (en) | 2006-04-20 | 2019-08-27 | Limflow Gmbh | Devices for fluid flow through body vessels |
US9532803B2 (en) | 2006-04-20 | 2017-01-03 | Limflow Gmbh | Devices for fluid flow through body passages |
US8439963B2 (en) * | 2006-04-20 | 2013-05-14 | Limflow Gmbh | Apparatus and method for maintaining fluid flow through body passages |
US11241304B2 (en) | 2006-04-20 | 2022-02-08 | Limflow Gmbh | Method for fluid flow through body passages |
US9326792B2 (en) | 2006-04-20 | 2016-05-03 | Limflow Gmbh | Methods for fluid flow through body passages |
US20080221658A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US9017395B2 (en) * | 2007-03-09 | 2015-04-28 | Novostent Corporation | Vascular prosthesis and methods of use |
US20080221657A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Delivery system and method for vascular prosthesis |
US8002815B2 (en) | 2007-03-09 | 2011-08-23 | Novostent Corporation | Delivery system and method for vascular prosthesis |
US20080221663A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US8348994B2 (en) | 2007-03-09 | 2013-01-08 | Novostent Corporation | Vascular prosthesis with alternating helical sections |
US20080221665A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US9265636B2 (en) | 2007-05-25 | 2016-02-23 | C. R. Bard, Inc. | Twisted stent |
US20080294267A1 (en) * | 2007-05-25 | 2008-11-27 | C.R. Bard, Inc. | Twisted stent |
US8500794B2 (en) | 2007-08-02 | 2013-08-06 | Flexible Stenting Solutions, Inc. | Flexible stent |
US20090149946A1 (en) * | 2007-12-05 | 2009-06-11 | Cook Incorporated | Stent having at least one barb and methods of manufacture |
US9149376B2 (en) | 2008-10-06 | 2015-10-06 | Cordis Corporation | Reconstrainable stent delivery system |
US10010438B2 (en) | 2008-10-06 | 2018-07-03 | Flexible Stenting Solutions, Inc. | Reconstrainable stent delivery system |
US8366763B2 (en) | 2009-07-02 | 2013-02-05 | Tryton Medical, Inc. | Ostium support for treating vascular bifurcations |
US9149373B2 (en) | 2009-07-02 | 2015-10-06 | Tryton Medical, Inc. | Method of treating vascular bifurcations |
US8382818B2 (en) | 2009-07-02 | 2013-02-26 | Tryton Medical, Inc. | Ostium support for treating vascular bifurcations |
US9707108B2 (en) | 2010-11-24 | 2017-07-18 | Tryton Medical, Inc. | Support for treating vascular bifurcations |
US10500072B2 (en) | 2010-11-24 | 2019-12-10 | Poseidon Medical Inc. | Method of treating vascular bifurcations |
US10500077B2 (en) | 2012-04-26 | 2019-12-10 | Poseidon Medical Inc. | Support for treating vascular bifurcations |
US9314329B2 (en) | 2013-03-08 | 2016-04-19 | Limflow Gmbh | Methods and systems for providing or maintaining fluid flow through body passages |
US9706998B2 (en) | 2013-03-08 | 2017-07-18 | Limflow Gmbh | Methods for targeting body passages |
US10524894B1 (en) | 2013-03-08 | 2020-01-07 | Limflow Gmbh | Methods for effecting retroperfusion in a body passage |
US10405967B1 (en) | 2013-03-08 | 2019-09-10 | Limflow Gmbh | Methods for puncturing an expandable member to confirm advancement into a body passage |
US10835367B2 (en) | 2013-03-08 | 2020-11-17 | Limflow Gmbh | Devices for fluid flow through body passages |
US11471262B2 (en) | 2013-03-08 | 2022-10-18 | Limflow Gmbh | Methods for targeting a body passage to effect fluid flow |
US10285800B2 (en) | 2013-03-08 | 2019-05-14 | Limflow Gmbh | Systems for providing or maintaining fluid flow through body passages |
US10596356B2 (en) | 2014-06-19 | 2020-03-24 | Limflow Gmbh | Methods for placing a stent-graft to cover collateral vessels in lower extremity vasculature |
US9545263B2 (en) | 2014-06-19 | 2017-01-17 | Limflow Gmbh | Devices and methods for treating lower extremity vasculature |
DE102016118600B4 (en) | 2016-09-30 | 2022-03-31 | Acandis Gmbh | Medical device, ribbon-shaped lattice structure, kit and method for manufacturing the same |
DE102016118600A1 (en) * | 2016-09-30 | 2018-04-05 | Acandis Gmbh & Co. Kg | Medical device, band-shaped lattice structure, set and method of making the same |
US10543308B2 (en) | 2017-04-10 | 2020-01-28 | Limflow Gmbh | Methods for routing a guidewire from a first vessel and through a second vessel in lower extremity vasculature |
US11826504B2 (en) | 2017-04-10 | 2023-11-28 | Limflow Gmbh | Methods for routing a guidewire from a first vessel and through a second vessel in lower extremity vasculature |
US11311700B2 (en) | 2018-10-09 | 2022-04-26 | Limflow Gmbh | Methods for accessing pedal veins |
US11129965B2 (en) | 2018-10-09 | 2021-09-28 | Limflow Gmbh | Devices and methods for catheter alignment |
US11116943B2 (en) | 2018-10-09 | 2021-09-14 | Limflow Gmbh | Methods for accessing pedal veins |
US11478614B2 (en) | 2018-10-09 | 2022-10-25 | Limflow Gmbh | Method for accessing pedal veins for deep vein arterialization |
US11850379B2 (en) | 2018-10-09 | 2023-12-26 | Limflow Gmbh | Devices and methods for catheter alignment |
US11612397B2 (en) | 2019-11-01 | 2023-03-28 | Limflow Gmbh | Devices and methods for increasing blood perfusion to a distal extremity |
Also Published As
Publication number | Publication date |
---|---|
WO2004058100A2 (en) | 2004-07-15 |
WO2004058100A3 (en) | 2005-10-27 |
EP1581147A4 (en) | 2006-12-06 |
EP1581147A2 (en) | 2005-10-05 |
AU2003300323A1 (en) | 2004-07-22 |
US20040186556A1 (en) | 2004-09-23 |
AU2003300323A8 (en) | 2004-07-22 |
US7862608B2 (en) | 2011-01-04 |
JP2006513010A (en) | 2006-04-20 |
CA2508247A1 (en) | 2004-07-15 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7846198B2 (en) | Vascular prosthesis and methods of use | |
US20050165469A1 (en) | Vascular prosthesis including torsional stabilizer and methods of use | |
US11491003B2 (en) | Constrainable stent graft, delivery system and methods of use | |
US10390930B2 (en) | Method for aortic branched vessel repair | |
JP2006513010A5 (en) | ||
US8348994B2 (en) | Vascular prosthesis with alternating helical sections | |
EP3585320B1 (en) | Delivery system for radially constricting a stent graft | |
US9017395B2 (en) | Vascular prosthesis and methods of use | |
US7806923B2 (en) | Side branch stent having a proximal split ring | |
JP5491491B2 (en) | Stent prosthesis with selective flared crown | |
US20050033410A1 (en) | Vascular prothesis having flexible configuration | |
US20090149946A1 (en) | Stent having at least one barb and methods of manufacture | |
US20080065205A1 (en) | Retrievable implant and method for treatment of mitral regurgitation | |
JP2005510293A (en) | Intravascular aneurysm repair system | |
JP2003093519A (en) | Intravascular stent | |
US20080221658A1 (en) | Vascular prosthesis and methods of use | |
CN111295161B (en) | Expandable stent and method for promoting natural intracranial angiogenesis process, and use of the stent in the method | |
US7901448B2 (en) | Vascular prothesis having interdigitating edges and methods of use | |
JP2011183218A (en) | Endovascular aneurysm repair system | |
US20040158314A1 (en) | Ribbon-type vascular prosthesis having stress-relieving articulation and methods of use | |
JP2007526803A (en) | Ribbon-shaped vascular prosthesis with stress relief joint and method of use |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: NOVOSTENT CORPORATION, CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:HOGENDIJK, MICHAEL;REEL/FRAME:015572/0557 Effective date: 20041217 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |