US20070010811A1 - energy delivery device for treating tissue - Google Patents

energy delivery device for treating tissue Download PDF

Info

Publication number
US20070010811A1
US20070010811A1 US11/531,081 US53108106A US2007010811A1 US 20070010811 A1 US20070010811 A1 US 20070010811A1 US 53108106 A US53108106 A US 53108106A US 2007010811 A1 US2007010811 A1 US 2007010811A1
Authority
US
United States
Prior art keywords
delivery device
electrode
energy delivery
sensor
tissue
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11/531,081
Inventor
Roger Stern
Mitchell Levinson
Bryan Weber
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Solta Medical Inc
Original Assignee
Thermage Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US09/522,275 external-priority patent/US6413255B1/en
Application filed by Thermage Inc filed Critical Thermage Inc
Priority to US11/531,081 priority Critical patent/US20070010811A1/en
Publication of US20070010811A1 publication Critical patent/US20070010811A1/en
Assigned to SILICON VALLEY BANK reassignment SILICON VALLEY BANK SECURITY AGREEMENT Assignors: SOLTA MEDICAL, INC.
Priority to US12/507,405 priority patent/US8603088B2/en
Assigned to SILICON VALLEY BANK reassignment SILICON VALLEY BANK SECURITY INTEREST - MEZZANINE LOAN Assignors: SOLTA MEDICAL, INC.
Priority to US14/074,927 priority patent/US9636175B2/en
Assigned to SOLTA MEDICAL, INC. reassignment SOLTA MEDICAL, INC. RELEASE OF SECURITY INTEREST IN PATENTS Assignors: SILICON VALLEY BANK
Priority to US15/483,556 priority patent/US20170209212A1/en
Priority to US16/196,114 priority patent/US20190090947A1/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14Probes or electrodes therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14Probes or electrodes therefor
    • A61B18/1402Probes for open surgery
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14Probes or electrodes therefor
    • A61B18/148Probes or electrodes therefor having a short, rigid shaft for accessing the inner body transcutaneously, e.g. for neurosurgery or arthroscopy
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/40Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals
    • A61N1/403Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals for thermotherapy, e.g. hyperthermia
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A61B2018/00023Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00452Skin
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00696Controlled or regulated parameters
    • A61B2018/00702Power or energy
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00773Sensed parameters
    • A61B2018/00779Power or energy
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00773Sensed parameters
    • A61B2018/00791Temperature
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00773Sensed parameters
    • A61B2018/00875Resistance or impedance
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14Probes or electrodes therefor
    • A61B2018/1495Electrodes being detachable from a support structure
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/06Measuring instruments not otherwise provided for
    • A61B2090/064Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/06Measuring instruments not otherwise provided for
    • A61B2090/064Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension
    • A61B2090/065Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension for measuring contact or contact pressure

Definitions

  • This invention relates generally to an electrode delivery device for treating tissue for treating skin and underlying tissues.
  • the human skin is composed of two elements: the epidermis and the underlying dermis.
  • the epidermis with the stratum corneum serves as a biological barrier to the environment.
  • pigment-forming cells called melanocytes are present in the basilar layer of the epidermis. They are the main determinants of skin color.
  • the underlying dermis provides the main structural support of the skin. It is composed mainly of an extra-cellular protein called collagen. Collagen is produced by fibroblasts and synthesized as a triple helix with three polypeptide chains that are connected with heat labile and heat stable chemical bonds. When collagen-containing tissue is heated, alterations in the physical properties of this protein matrix occur at a characteristic temperature. The structural transition of collagen contraction occurs at a specific “shrinkage” temperature. The shrinkage and remodeling of the collagen matrix with heat is the basis for the technology.
  • Collagen crosslinks are either intramolecular (covalent or hydrogen bond) or intermolecular (covalent or ionic bonds).
  • the thermal cleavage of intramolecular hydrogen crosslinks is a scalar process that is created by the balance between cleavage events and relaxation events (reforming of hydrogen bonds). No external force is required for this process to occur.
  • intermolecular stress is created by the thermal cleavage of intramolecular hydrogen bonds.
  • the contraction of the tertiary structure of the molecule creates the initial intermolecular vector of contraction.
  • Collagen fibrils in a matrix exhibit a variety of spatial orientations.
  • the matrix is lengthened if the sum of all vectors acts to distract the fibril. Contraction of the matrix is facilitated if the sum of all extrinsic vectors acts to shorten the fibril.
  • Thermal disruption of intramolecular hydrogen bonds and mechanical cleavage of intermolecular crosslinks is also affected by relaxation events that restore preexisting configurations. However, a permanent change of molecular length will occur if crosslinks are reformed after lengthening or contraction of the collagen fibril. The continuous application of an external mechanical force will increase the probability of crosslinks forming after lengthening or contraction of the fibril.
  • Hydrogen bond cleavage is a quantum mechanical event that requires a threshold of energy.
  • the amount of (intramolecular) hydrogen bond cleavage required corresponds to the combined ionic and covalent intermolecular bond strengths within the collagen fibril. Until this threshold is reached, little or no change in the quaternary structure of the collagen fibril will occur. When the intermolecular stress is adequate, cleavage of the ionic and covalent bonds will occur. Typically, the intermolecular cleavage of ionic and covalent bonds will occur with a ratcheting effect from the realignment of polar and nonpolar regions in the lengthened or contracted fibril.
  • Cleavage of collagen bonds also occurs at lower temperatures but at a lower rate.
  • Low-level thermal cleavage is frequently associated with relaxation phenomena in which bonds are reformed without a net change in molecular length.
  • An external force that mechanically cleaves the fibril will reduce the probability of relaxation phenomena and provides a means to lengthen or contract the collagen matrix at lower temperatures while reducing the potential of surface ablation.
  • Soft tissue remodeling is a biophysical phenomenon that occurs at cellular and molecular levels.
  • Molecular contraction or partial denaturization of collagen involves the application of an energy source, which destabilizes the longitudinal axis of the molecule by cleaving the heat labile bonds of the triple helix.
  • stress is created to break the intermolecular bonds of the matrix. This is essentially an immediate extra-cellular process, whereas cellular contraction requires a lag period for the migration and multiplication of fibroblasts into the wound as provided by the wound healing sequence.
  • the wound healing response to injury involves an initial inflammatory process that subsequently leads to the deposition of scar tissue.
  • the initial inflammatory response consists of the infiltration by white blood cells or leukocytes that dispose of cellular debris. Seventy-two hours later, proliferation of fibroblasts at the injured site occurs. These cells differentiate into contractile myofibroblasts, which are the source of cellular soft tissue contraction. Following cellular contraction, collagen is laid down as a static supporting matrix in the tightened soft tissue structure. The deposition and subsequent remodeling of this nascent scar matrix provides the means to alter the consistency and geometry of soft tissue for aesthetic purposes.
  • edge effect phenomenon One of the key shortcomings of currently available RF technology for treating the skin is the edge effect phenomenon.
  • the edge effect In general, when RF energy is being applied or delivered to tissue through an electrode which is in contact with that tissue, the current patterns concentrate around the edges of the electrode, sharp edges in particular. This effect is generally known as the edge effect.
  • the effect In the case of a circular disc electrode, the effect manifests as a higher current density around the perimeter of that circular disc and a relatively low current density in the center.
  • For a square- shaped electrode there is typically a high current density around the entire perimeter, and an even higher current density at the corners where there is a sharp edge.
  • Edge effects cause problems in treating the skin for several reasons. First, they result in a non-uniform thermal effect over the electrode surface. In various treatments of the skin, it is important to have a uniform thermal effect over a relatively large surface area, particularly for dermatologic treatments. Large in this case being on the order of several square millimeters or even several square centimeters. In electrosurgical applications for cutting tissue, there typically is a point type applicator designed with the goal of getting a hot spot at that point for cutting or even coagulating tissue. However, this point design is undesirable for creating a reasonably gentle thermal effect over a large surface area. What is needed is an electrode design to deliver uniform thermal energy to skin and underlying tissue without hot spots.
  • a uniform thermal effect is particularly important when cooling is combined with heating in skin/tissue treatment procedure.
  • a non-uniform thermal pattern makes cooling of the skin difficult and hence the resulting treatment process as well.
  • the tissue at the electrode surface tends to be warmest with a decrease in temperature moving deeper into the tissue.
  • One approach to overcome this thermal gradient and create a thermal effect at a set distance away from the electrode is to cool the layers of skin that are in contact with the electrode.
  • cooling of the skin is made difficult if there is a non-uniform heating pattern.
  • an object of the present invention is to provide an RF handpiece which provides a substantially uniform delivery of energy to a target tissue site.
  • Another object of the present invention is to provide an RF handpiece which includes at least one RF electrode that is capacitively coupled to a skin surface when at least a portion of the RF electrode is in contact with the skin surface.
  • Yet another object of the present invention is to provide an RF handpiece that provides a uniform thermal effect in tissue at a selected depth, while preventing or minimizing thermal damage to a skin surface and other non-target tissue.
  • a further object of the present invention is to provide an RF handpiece configured to reduce or eliminate the edge effects and hot spots of RF electrodes applied to skin surfaces.
  • Another object of the present invention is to provide an RF handpiece configured to provide an atomizing delivery of a cooling fluidic medium to the RF electrode.
  • Still another object of the present invention is to provide an RF handpiece configured to evaporatively cool the back surface of the RF electrode, and conductively cool a skin surface adjacent to a front surface of the RF electrode.
  • a further object of the present invention is to provide an RF handpiece configured to controllably deliver a cooling fluidic medium to the back surface of the RF electrode at substantially any orientation of the front surface of the RF electrode relative to a direction of gravity.
  • Yet another object of the present invention is to provide an RF handpiece that includes an RF electrode with both conductive and dielectric portions.
  • Another object of the present invention is to provide an RF handpiece that includes a force sensor that zeros out gravity effects created by the weight of the electrode assembly of the RF handpiece in any orientation of the front surface of the RF electrode relative to a direction of gravity.
  • the handpiece assembly includes a handpiece housing and a cooling fluidic medium valve member.
  • An electrode assembly is coupled to the handpiece housing.
  • the electrode assembly has a least one RF electrode that is capacitively coupled to a skin surface when at least a portion of the RF electrode is in contact with the skin surface.
  • a handpiece assembly in another embodiment, includes a handpiece housing and a cooling fluidic medium valve member with an inlet and an outlet.
  • An electrode assembly is removeably coupled to the handpiece housing.
  • the electrode assembly has a least one RF electrode with a front surface and a back surface. The RF electrode is capacitively coupled to a skin surface when at least a portion of the RF electrode is in contact with the skin surface.
  • a handpiece in another embodiment, includes a handpiece assembly with a handpiece housing.
  • An insert is at least partially positionable in the handpiece housing.
  • An RF electrode is coupled to the insert.
  • the RF electrode has a back surface that faces the handpiece housing and an opposing front surface.
  • a cooling fluidic medium dispensing assembly is coupled to the handpiece housing and the insert.
  • a handpiece in another embodiment, includes a handpiece assembly with a handpiece housing.
  • An insert is detachably coupled to the handpiece housing.
  • the insert includes an RF electrode with a conductive portion and a dielectric.
  • a handpiece in another embodiment, includes a handpiece assembly with a handpiece housing.
  • An insert is detachably coupled to the handpiece housing.
  • An RF electrode is positioned in the insert.
  • the RF electrode includes a flex circuit.
  • a handpiece in another embodiment, includes a handpiece assembly with a handpiece housing.
  • An insert is detachably coupled to the handpiece housing.
  • the insert includes a flex circuit and an RF electrode that with a conductive portion and a dielectric.
  • an electrode assembly is adapted to be coupled with a handpiece and powered to treat skin and underlying tissues.
  • a sensor is coupled to the energy delivery device.
  • the sensor may comprise, for example, a force sensor or a thermal sensor.
  • FIG. 1 is a cross-sectional view of one embodiment of the handpiece of the present invention.
  • FIG. 2 is an exploded view of the FIG. 1 insert assembly.
  • FIG. 3 is a close-up view of one embodiment of an RF electrode of the present invention.
  • FIG. 4 is another cross-sectional view of a portion of the handpiece housing from FIG. 1 .
  • FIG. 5 is a cross-sectional view of the insert from FIG. 1 .
  • one embodiment of the present invention is a handpiece 10 with a handpiece assembly 12 .
  • Handpiece assembly 12 includes a handpiece housing 14 and a cooling fluidic medium valve member 16 .
  • An electrode assembly 18 is coupled to handpiece housing 14 .
  • Electrode assembly 18 has a least one RF electrode 20 that is capacitively coupled to a skin surface when at least a portion of RF electrode 20 is in contact with the skin surface.
  • RF electrode 20 can have a thickness in the range of 0.010 to 1.0 mm.
  • Handpiece 10 provides a more uniform thermal effect in tissue at a selected depth, while preventing or minimizing thermal damage to the skin surface and other non-target tissue.
  • Handpiece 10 is coupled to an RF generator.
  • RF electrode 20 can be operated either in mono-polar or bi-polar modes.
  • Handpiece 10 is configured to reduce, or preferably eliminate edge effects and hot spots. The result is an improved aesthetic result/clinical outcome with an elimination/reduction in adverse effects and healing time.
  • a fluid delivery member 22 is coupled to cooling fluidic medium valve member 16 .
  • Fluid delivery member 22 and cooling fluidic medium valve member 16 collectively form a cooling fluidic medium dispensing assembly.
  • Fluid delivery member 16 is configured to provide an atomizing delivery of a cooling fluidic medium to RF electrode 20 .
  • the atomizing delivery is a mist or fine spray.
  • a phase transition, from liquid to gas, of the cooling fluidic medium occurs when it hits the surface of RF electrode 20 . The transition from liquid to gas creates the cooling. If the transition before the cooling fluidic medium hits RF electrode 20 the cooling of RF electrode 20 will not be as effective.
  • the cooling fluidic medium is a cryogenic spray, commercially available from Honeywell, Morristown, N.J.
  • a specific example of a suitable cryogenic spray is R134A 2 , available from Refron, Inc., 38-18 33 rd St., Long Island City, N.Y. 11101.
  • the use of a cryogenic cooling fluidic medium provides the capability to use a number of different types of algorithms for skin treatment.
  • the cryogenic cooling fluidic medium can be applied milliseconds before and after the delivery of RF energy to the desired tissue. This is achieved with the use of cooling fluidic medium valve member 16 coupled to a cryogen supply, including but not limited to a compressed gas canister.
  • cooling fluidic medium valve member 16 can be coupled to a computer control system and/or manually controlled by the physician by means of a foot switch or similar device.
  • cryogenic cooling fluidic medium A key advantage of providing a spray, or atomization, of cryogenic cooling fluidic medium is the availability to implement rapid on and off control.
  • Cryogenic cooling fluidic medium allows more precise temporal control of the cooling process. This is because cooling only occurs when the refrigerant is sprayed and is in an evaporative state, the latter being a very fast short-lived event. Thus, cooling ceases rapidly after the cryogenic cooling fluidic medium is stopped. The overall effect is to confer very precise time on-off control of cryogenic cooling fluidic medium.
  • fluid delivery member 22 can be positioned in handpiece housing 14 or electrode assembly 18 .
  • Fluid delivery member 22 is configured to controllably deliver a cooling fluidic medium to a back surface 24 of RF electrode 20 and maintain back surface 24 at a desired temperature.
  • the cooling fluidic medium evaporatively cools RF electrode 20 and maintains a substantially uniform temperature of front surface 26 of RF electrode 20 .
  • Front surface 26 can be sufficiently flexible and conformable to the skin, but still have sufficient strength and/or structure to provide good thermal coupling when pressed against the skin surface.
  • RF electrode 20 then conductively cools a skin surface that is adjacent to a front surface 26 of RF electrode 20 .
  • Suitable fluidic media include a variety of refrigerants such as R134A and freon.
  • Fluid delivery member 22 is configured to controllably deliver the cooling fluidic medium to back surface 24 at substantially any orientation of front surface 26 relative to a direction of gravity. A geometry and positioning of fluid delivery member 22 are selected to provide a substantially uniform distribution of cooling fluidic medium on back surface 24 .
  • the delivery of the cooling fluidic medium can be by spray of droplets or fine mist, flooding back surface 24 , and the like. Cooling occurs at the interface of the cooling fluidic medium with atmosphere, which is where evaporation occurs.
  • cooling fluidic medium If there is a thick layer of fluid on back surface 24 the heat removed from the treated skin will need to pass through the thick layer of cooling fluidic medium, increasing thermal resistance. To maximize cooling rates, it is desirable to apply a very thin layer of cooling fluidic medium. If RF electrode 20 is not horizontal, and if there is a thick layer of cooling fluidic medium, or if there are large drops of cooling fluidic medium on back surface 24 , the cooling fluidic medium can run down the surface of RF electrode 20 and pool at one edge or corner, causing uneven cooling. Therefore, it is desirable to apply a thin layer of cooling fluidic medium with a fine spray.
  • RF electrode 20 has a conductive portion 28 and a dielectric portion 30 .
  • Conductive portion 28 can be a metal including but not limited to copper, gold, silver, aluminum and the like.
  • Dielectric portion 30 can be made of a variety of different materials including but not limited to polyimide, and the like. Other dielectric materials include but are not limited to silicon, sapphire, diamond, zirconium-toughened alumina (ZTA), alumina and the like. Dielectric portion 30 can be positioned around at least a portion, or the entirety of a periphery of conductive portion 28 .
  • Suitable materials for a dielectric portion 30 include, but are not limited to, Teflon® and the like, silicon nitride, polysilanes, polysilazanes, polyimides, Kapton and other polymers, antenna dielectrics and other dielectric materials well known in the art.
  • RF electrode 20 is made of a composite material, including but not limited to gold-plated copper, copper-polyimide, silicon/silicon-nitride and the like.
  • Dielectric portion 30 creates an increased impedance to the flow of electrical current through RF electrode 20 .
  • This increased impedance causes current to travel a path straight down through conductive portion 28 to the skin surface. Electric field edge effects, caused by a concentration of current flowing out of the edges of RF electrode 20 , are reduced.
  • Dielectric portion 30 produces a more uniform impedance through RF electrode 20 and causes a more uniform current to flow through conductive portion 28 .
  • the resulting effect minimizes or even eliminates, edge effects around the edges of RF electrode 20 .
  • conductive portion 28 adheres to dielectric portion 30 which can be substrate with a thickness, by way of example and without limitation, of about 0.001′′.
  • dielectric portion 30 is in contact with the tissue, the skin, and conductive portion 28 is separated from the skin.
  • the thickness of the dielectric portion 30 can be decreased by growing conductive portion 28 on dielectric portion 30 using a variety of techniques, including but not limited to, sputtering, electro deposition, chemical vapor deposition, plasma deposition and other deposition techniques known in the art. Additionally, these same processes can be used to deposit dielectric portion 30 onto conductive portion 28 .
  • dielectric portion 30 is an oxide layer which can be grown on conductive portion 28 . An oxide layer has a low thermal resistance and improves the cooling efficiency of the skin compared with many other dielectrics such as polymers.
  • Fluid delivery member 22 has an inlet 32 and an outlet 34 .
  • Outlet 34 can have a smaller cross-sectional area than a cross-sectional area of inlet 32 .
  • fluid delivery member 22 is a nozzle 36 .
  • Cooling fluidic medium valve member 16 can be configured to provide a pulsed delivery of the cooling fluidic medium. Pulsing the delivery of cooling fluidic medium is a simple way to control the rate of cooling fluidic medium application.
  • cooling fluidic medium valve member 16 is a solenoid valve.
  • An example of a suitable solenoid valve is a solenoid pinch valve manufactured by the N-Research Corporation, West Caldwell, N.J. If the fluid is pressurized, then opening of the valve results in fluid flow. If the fluid is maintained at a constant pressure, then the flow rate is constant and a simple open/close solenoid valve can be used, the effective flow rate being determined by the pulse duty cycle.
  • the duty cycle can be achieved by turning on the valve for a short duration of time at a set frequency.
  • the duration of the open time can be 1 to 50 milliseconds or longer.
  • the frequency of pulsing can be 1 to 50 Hz or faster.
  • cooling fluidic medium flow rate can be controlled by a metering valve or controllable-rate pump such as a peristaltic pump.
  • a metering valve or controllable-rate pump such as a peristaltic pump.
  • Electrode assembly 18 is sufficiently sealed so that the cooling fluidic medium does not leak from back surface 24 onto a skin surface in contact with a front surface of RF electrode 20 . This helps provide an even energy delivery through the skin surface.
  • electrode assembly 18 and more specifically RF electrode 20 , has a geometry that creates a reservoir at back surface 24 to hold and gather cooling fluidic medium that has collected at back surface 24 . Back surface 24 can be formed with “hospital corners” to create this reservoir.
  • electrode assembly 18 includes a vent 38 that permits vaporized cooling fluidic medium to escape from electrode assembly 18 . This reduces the chance of cooling fluidic medium collecting at back surface 24 . This can occur when cooling fluidic medium is delivered to back surface 24 in vapor form and then, following cooling of back surface 24 , the vapor condenses to a liquid.
  • Vent 38 prevents pressure from building up in electrode assembly 18 .
  • Vent 38 can be a pressure relief valve that is vented to the atmosphere or a vent line.
  • the cooling fluidic medium comes into contact with RF electrode 20 and evaporates, the resulting gas pressurizes the inside of electrode assembly 18 . This can cause RF electrode 20 to partially inflate and bow out from front surface 26 .
  • the inflated RF electrode 20 can enhance the thermal contact with the skin and also result in some degree of conformance of RF electrode 20 to the skin surface.
  • An electronic controller can be provided. The electronic controller sends a signal to open vent 38 when a programmed pressure has been reached.
  • thermal sensors 42 are coupled to RF electrode. Suitable thermal sensors 42 include but are not limited to thermocouples, thermistors, infrared photo-emitters and a thermally sensitive diode. In one embodiment, a thermal sensor 42 is positioned at each comer of RF electrode 20 . A sufficient number of thermal sensors 42 are provided in order to acquire sufficient thermal data of the skin surface. Thermal sensors 42 are electrically isolated from RF electrode 20 .
  • Thermal sensors 42 measure temperature and can provide feedback for monitoring temperature of RF electrode 20 and/or the tissue during treatment.
  • Thermal sensors 42 can be thermistors, thermocouples, thermally sensitive diodes, capacitors, inductors or other devices for measuring temperature.
  • thermal sensors 42 provide electronic feedback to a microprocessor of the RF generator coupled to RF electrode 20 in order to facilitate control of the treatment.
  • the measurements from thermal sensors 42 can be used to help control the rate of application of cooling fluidic medium.
  • the cooling control algorithm can be used to apply cooling fluidic medium to RF electrode 20 at a high flow rate until the temperature fell below a target temperature, and then slow down or stop.
  • a PID, or proportional-integral-differential, algorithm can be used to precisely control RF electrode 20 temperature to a predetermined value.
  • Thermal sensors 42 can be positioned placed on back surface 24 of RF electrode 20 away from the tissue. This configuration is preferable ideal for controlling the temperature of the RF electrode 20 . Alternatively, thermal sensors 42 can be positioned on front surface 26 of RF electrode 10 in direct contact with the tissue. This embodiment can be more suitable for monitoring tissue temperature. Algorithms are utilized with thermal sensors 42 to calculate a temperature profile of the treated tissue. Thermal sensors 42 can be used to develop a temperature profile of the skin which is then used for process control purposes to assure that the proper amounts of heating and cooling are delivered to achieve a desired elevated deep tissue temperature while maintaining skin tissue layers below a threshold temperature and avoid thermal injury. The physician can use the measured temperature profile to assure that he stays within the boundary of an ideal/average profile for a given type of treatment.
  • Thermal sensors 42 can be used for additional purposes. When the temperature of thermal sensors 42 is monitored it is possible to detect when RF electrode 20 is in contact with the skin surface. This can be achieved by detecting a direct change in temperature when skin contact is made or examining the rate of change of temperature which is affected by contact with the skin. Similarly, if there is more than one thermal sensor 42 , the thermal sensors 42 can be used to detect whether a portion of RF electrode 20 is lifted or out of contact with skin. This can be important because the current density (amperes per unit area) delivered to the skin can vary if the contact area changes. In particular, if part of the surface of RF electrode 20 is not in contact with the skin, the resulting current density is higher than expected.
  • a force sensor 44 is also coupled to electrode assembly 18 .
  • Force sensor 44 detects an amount of force applied by electrode assembly 18 , via the physician, against an applied skin surface. Force sensor 44 zeros out gravity effects of the weight of electrode assembly 18 in any orientation of front surface 26 of RF electrode 20 relative to a direction of gravity. Additionally, force sensor 44 provides an indication when RF electrode 20 is in contact with a skin surface. Force sensor 44 also provides a signal indicating that a force applied by RF electrode 20 to a contacted skin surface is, (i) below a minimum threshold or (ii) above a maximum threshold.
  • An activation button 46 is used in conjunction with the force sensor. Just prior to activating RF electrode 20 , the physician holds handpiece 10 in position just off the surface of the skin. The orientation of handpiece 10 can be any angle relative to the angle of gravity. To arm handpiece 10 , the physician can press activation button 46 which tares force sensor 44 , by setting it to read zero. This cancels the force due to gravity in that particular treatment orientation. This method allows consistent force application of RF electrode 20 to the skin surface regardless of the angle of handpiece 10 relative to the direction of gravity.
  • RF electrode 20 can be a flex circuit, which can include trace components. Additionally, thermal sensor 42 and force sensor 44 can be part of the flex circuit. Further, the flex circuit can include a dielectric that forms a part of RF electrode 20 .
  • Electrode assembly 18 can be moveable positioned within handpiece housing 12 . In one embodiment, electrode assembly 18 is slideably moveable along a longitudinal axis of handpiece housing 12 . Electrode assembly 18 can be rotatably mounted in handpiece housing 12 . Additionally, RF electrode 20 can be rotatably positioned in electrode assembly 18 . Electrode assembly 18 can be removably coupled to handpiece housing 12 as a disposable or non-disposable insert 52 , see FIG. 5 . For purposes of this disclosure, electrode assembly 18 is the same as insert 52 . Once movably mounted to handpiece housing 12 , insert 52 can be coupled to handpiece housing 12 via force sensor 44 . Force sensor 44 can be of the type that is capable of measuring both compressive and tensile forces. In other embodiments, force sensor 44 only measures compressive forces, or only measures tensile forces.
  • Insert 52 can be spring-loaded with a spring 48 .
  • spring 48 biases RF electrode 20 in a direction toward handpiece housing 12 . This pre-loads force sensor 44 and keeps insert 52 pressed against force sensor 44 . The pre-load force is tared when activation button 46 is pressed just prior to application of RF electrode 20 to the skin surface.
  • a shroud 50 is optionally coupled to handpiece 10 .
  • Shroud 50 serves to keep the user from touching insert 52 during use which can cause erroneous force readings.
  • a non-volatile memory 54 can be included with insert 52 . Additionally, non-volatile memory can be included with handpiece housing 12 . Non-volatile memory 54 can be an EPROM and the like. Additionally, a second non-volatile memory 56 can be included in handpiece housing 12 for purposes of storing handpiece 10 information such as but not limited to, handpiece model number or version, handpiece software version, number of RF applications that handpiece 10 has delivered, expiration date and manufacture date. Handpiece housing 12 can also contain a microprocessor 58 for purposes of acquiring and analyzing data from various sensors on handpiece housing 12 or insert 52 including but not limited to thermal sensors 42 , force sensors 44 , fluid pressure gauges, switches, buttons and the like. Microprocessor 58 can also control components on handpiece 10 including but not limited to lights, LEDs, valves, pumps or other electronic components. Microprocessor 58 can also communicate data to a microprocessor of the RF generator.
  • Non-volatile memory 54 can store a variety of data that can facilitate control and operation of handpiece 10 and its associated system including but not limited to, (i) controlling the amount of current delivered by RF electrode 20 , (ii) controlling the duty cycle of the fluid delivery member 22 , (iii) controlling the energy delivery duration time of the RF electrode 20 , (iv) controlling the temperature of RF electrode 20 relative to a target temperature, (v) providing a maximum number of firings of RF electrode 20 , (vi) providing a maximum allowed voltage that is deliverable by RF electrode 20 , (vii) providing a history of RF electrode 20 use, (viii) providing a controllable duty cycle to fluid delivery member 22 for the delivery of the cooling fluidic medium to back surface 24 of RF electrode 20 , (ix) providing a controllable delivery rate of cooling fluidic medium delivered from fluid delivery member 22 to back surface 24 , and the like.
  • Handpiece 10 can be used to deliver thermal energy to modify tissue including, but not limited to, collagen containing tissue, in the epidermal, dermal and subcutaneous tissue layers, including adipose tissue.
  • the modification of the tissue includes modifying a physical feature of the tissue, a structure of the tissue or a physical property of the tissue.
  • the modification can be achieved by delivering sufficient energy to cause collagen shrinkage, and/or a wound healing response including the deposition of new or nascent collagen.
  • Handpiece 10 can be utilized for performing a number of treatments of the skin and underlying tissue including but not limited to, (i) dermal remodeling and tightening, (ii) wrinkle reduction, (iii) elastosis reduction, (iv) sebaceous gland removal/deactivation, (v) hair follicle removal, (vi) adipose tissue remodeling/removal, (vii) spider vein removal, and the like.
  • handpiece 10 can be utilized in a variety of treatment processes, including but not limited to, (i) pre-cooling, before the delivery of energy to the tissue has begun, (ii) an on phase or energy delivery phase in conjunction with cooling and (iii) post cooling after the delivery of energy to tissue has stopped.
  • Handpiece 10 can be used to pre-cool the surface layers of the target tissue so that when RF electrode 20 is in contact with the tissue, or prior to turning on the RF energy source, the superficial layers of the target tissue are already cooled.
  • RF energy source is turned on or delivery of RF to the tissue otherwise begins, resulting in heating of the tissues, the tissue that has been cooled is protected from thermal effects including thermal damage.
  • the tissue that has not been cooled will warm up to therapeutic temperatures resulting in the desired therapeutic effect.
  • Pre-cooling gives time for the thermal effects of cooling to propagate down into the tissue. More specifically, pre-cooling allows the achievement of a desired tissue depth thermal profile, with a minimum desired temperature being achieved at a selectable depth.
  • the amount or duration of pre-cooling can be used to select the depth of the protected zone of untreated tissue. Longer durations of pre-cooling produce a deeper protected zone and hence a deeper level in tissue for the start of the treatment zone. The opposite is true for shorter periods of pre-cooling.
  • the temperature of front surface 26 of RF electrode 20 also affects the temperature profile. The colder the temperature of front surface 26 , the faster and deeper the cooling, and vice verse.
  • Post-cooling can be important because it prevents and/or reduces heat delivered to the deeper layers from conducting upward and heating the more superficial layers possibly to therapeutic or damaging temperature range even though external energy delivery to the tissue has ceased. In order to prevent this and related thermal phenomena, it can be desirable to maintain cooling of the treatment surface for a period of time after application of the RF energy has ceased. In various embodiments, varying amounts of post cooling can be combined with real-time cooling and/or pre-cooling.
  • handpiece 10 can be used in a varied number of pulse on-off type cooling sequences and algorithms may be employed.
  • the treatment algorithm provides for pre-cooling of the tissue by starting a spray of cryogenic cooling fluidic medium, followed by a short pulse of RF energy into the tissue.
  • the spray of cryogenic cooling fluidic medium continues while the RF energy is delivered, and is stopping shortly thereafter, e.g. on the order of milliseconds.
  • the treatment sequence can include a pulsed sequence of cooling on, heat, cooling off, cooling on, heat, cool off, and with cooling and heating durations on orders of tens of milliseconds.
  • Cryogenic cooling fluidic medium spray duration, and intervals between sprays can be in the tens of milliseconds ranges, which allows surface cooling while still delivering the desired thermal effect into the deeper target tissue.
  • the target tissue zone for therapy also called therapeutic zone or thermal effect zone
  • the target tissue zone for therapy can be at a tissue depth from approximately 100 ⁇ m beneath the surface of the skin down to as deep as 10 millimeters, depending upon the type of treatment.
  • it can be desirable to cool both the epidermis and the superficial layers of the dermis of the skin that lies beneath the epidermis, to a cooled depth range between 100 ⁇ m two millimeters.
  • Different treatment algorithms can incorporate different amounts of pre-cooling, heating and post cooling phases in order to produce a desired tissue effect at a desired depth.
  • cooling and heating duty cycles can be controlled and dynamically varied by an electronic control system known in the art. Specifically the control system can be used to control cooling fluidic medium valve member 16 and the RF power source.

Abstract

An electrode assembly adapted to be coupled with a handpiece and powered to treat skin and underlying tissues. A sensor is coupled to the energy delivery device. The sensor may comprise, for example, a force sensor or a thermal sensor.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application is a continuation of U.S. application Ser. No. 10/072,610, which is a continuation-in-part of U.S. application Ser. No. 09/522,275, filed Mar. 9, 2000, now U.S. Pat. No. 6,413,255, which claims the benefit of U.S. application Ser. No. 60/123,440, filed Mar. 9, 1999. The disclosure of each of these applications is hereby incorporated by reference herein in its entirety.
  • FIELD OF THE INVENTION
  • This invention relates generally to an electrode delivery device for treating tissue for treating skin and underlying tissues.
  • BACKGROUND OF THE INVENTION
  • The human skin is composed of two elements: the epidermis and the underlying dermis. The epidermis with the stratum corneum serves as a biological barrier to the environment. In the basilar layer of the epidermis, pigment-forming cells called melanocytes are present. They are the main determinants of skin color.
  • The underlying dermis provides the main structural support of the skin. It is composed mainly of an extra-cellular protein called collagen. Collagen is produced by fibroblasts and synthesized as a triple helix with three polypeptide chains that are connected with heat labile and heat stable chemical bonds. When collagen-containing tissue is heated, alterations in the physical properties of this protein matrix occur at a characteristic temperature. The structural transition of collagen contraction occurs at a specific “shrinkage” temperature. The shrinkage and remodeling of the collagen matrix with heat is the basis for the technology.
  • Collagen crosslinks are either intramolecular (covalent or hydrogen bond) or intermolecular (covalent or ionic bonds). The thermal cleavage of intramolecular hydrogen crosslinks is a scalar process that is created by the balance between cleavage events and relaxation events (reforming of hydrogen bonds). No external force is required for this process to occur. As a result, intermolecular stress is created by the thermal cleavage of intramolecular hydrogen bonds. Essentially, the contraction of the tertiary structure of the molecule creates the initial intermolecular vector of contraction.
  • Collagen fibrils in a matrix exhibit a variety of spatial orientations. The matrix is lengthened if the sum of all vectors acts to distract the fibril. Contraction of the matrix is facilitated if the sum of all extrinsic vectors acts to shorten the fibril. Thermal disruption of intramolecular hydrogen bonds and mechanical cleavage of intermolecular crosslinks is also affected by relaxation events that restore preexisting configurations. However, a permanent change of molecular length will occur if crosslinks are reformed after lengthening or contraction of the collagen fibril. The continuous application of an external mechanical force will increase the probability of crosslinks forming after lengthening or contraction of the fibril.
  • Hydrogen bond cleavage is a quantum mechanical event that requires a threshold of energy. The amount of (intramolecular) hydrogen bond cleavage required corresponds to the combined ionic and covalent intermolecular bond strengths within the collagen fibril. Until this threshold is reached, little or no change in the quaternary structure of the collagen fibril will occur. When the intermolecular stress is adequate, cleavage of the ionic and covalent bonds will occur. Typically, the intermolecular cleavage of ionic and covalent bonds will occur with a ratcheting effect from the realignment of polar and nonpolar regions in the lengthened or contracted fibril.
  • Cleavage of collagen bonds also occurs at lower temperatures but at a lower rate. Low-level thermal cleavage is frequently associated with relaxation phenomena in which bonds are reformed without a net change in molecular length. An external force that mechanically cleaves the fibril will reduce the probability of relaxation phenomena and provides a means to lengthen or contract the collagen matrix at lower temperatures while reducing the potential of surface ablation.
  • Soft tissue remodeling is a biophysical phenomenon that occurs at cellular and molecular levels. Molecular contraction or partial denaturization of collagen involves the application of an energy source, which destabilizes the longitudinal axis of the molecule by cleaving the heat labile bonds of the triple helix. As a result, stress is created to break the intermolecular bonds of the matrix. This is essentially an immediate extra-cellular process, whereas cellular contraction requires a lag period for the migration and multiplication of fibroblasts into the wound as provided by the wound healing sequence. In higher developed animal species, the wound healing response to injury involves an initial inflammatory process that subsequently leads to the deposition of scar tissue.
  • The initial inflammatory response consists of the infiltration by white blood cells or leukocytes that dispose of cellular debris. Seventy-two hours later, proliferation of fibroblasts at the injured site occurs. These cells differentiate into contractile myofibroblasts, which are the source of cellular soft tissue contraction. Following cellular contraction, collagen is laid down as a static supporting matrix in the tightened soft tissue structure. The deposition and subsequent remodeling of this nascent scar matrix provides the means to alter the consistency and geometry of soft tissue for aesthetic purposes.
  • In light of the preceding discussion, there are a number of dermatological procedures that lend themselves to treatments which deliver thermal energy to the skin and underlying tissue to cause a contraction of collagen, and/or initiate a would healing response. Such procedures include skin remodeling/resurfacing, wrinkle removal, and treatment of the sebaceous glands, hair follicles adipose tissue and spider veins. Currently available technologies that deliver thermal energy to the skin and underlying tissue include Radio Frequency (RF), optical (laser) and other forms of electromagnetic energy. However, these technologies have a number of technical limitations and clinical issues which limit the effectiveness of the treatment and/or preclude treatment altogether. These issues include the following: i) achieving a uniform thermal effect across a large area of tissue, ii) controlling the depth of the thermal effect to target selected tissue and prevent unwanted thermal damage to both target and non-target tissue, iii) reducing adverse tissue effects such as burns, redness blistering, iv) replacing the practice of delivery energy/treatment in a patchwork fashion with a more continuous delivery of treatment (e.g. by a sliding or painting motion), v) improving access to difficult-to-reach areas of the skin surface and vi) reducing procedure time and number of patient visits required to complete treatment. As will be discussed herein the current invention provides an apparatus for solving these and other limitations.
  • One of the key shortcomings of currently available RF technology for treating the skin is the edge effect phenomenon. In general, when RF energy is being applied or delivered to tissue through an electrode which is in contact with that tissue, the current patterns concentrate around the edges of the electrode, sharp edges in particular. This effect is generally known as the edge effect. In the case of a circular disc electrode, the effect manifests as a higher current density around the perimeter of that circular disc and a relatively low current density in the center. For a square- shaped electrode there is typically a high current density around the entire perimeter, and an even higher current density at the corners where there is a sharp edge.
  • Edge effects cause problems in treating the skin for several reasons. First, they result in a non-uniform thermal effect over the electrode surface. In various treatments of the skin, it is important to have a uniform thermal effect over a relatively large surface area, particularly for dermatologic treatments. Large in this case being on the order of several square millimeters or even several square centimeters. In electrosurgical applications for cutting tissue, there typically is a point type applicator designed with the goal of getting a hot spot at that point for cutting or even coagulating tissue. However, this point design is undesirable for creating a reasonably gentle thermal effect over a large surface area. What is needed is an electrode design to deliver uniform thermal energy to skin and underlying tissue without hot spots.
  • A uniform thermal effect is particularly important when cooling is combined with heating in skin/tissue treatment procedure. As is discussed below, a non-uniform thermal pattern makes cooling of the skin difficult and hence the resulting treatment process as well. When heating the skin with RF energy, the tissue at the electrode surface tends to be warmest with a decrease in temperature moving deeper into the tissue. One approach to overcome this thermal gradient and create a thermal effect at a set distance away from the electrode is to cool the layers of skin that are in contact with the electrode. However, cooling of the skin is made difficult if there is a non-uniform heating pattern. If the skin is sufficiently cooled such that there are no burns at the corners of a square or rectangular electrode, or at the perimeter of a circular disc electrode, then there will probably be overcooling in the center and there won't be any significant thermal effect (i.e. tissue heating) under the center of the electrode. Contrarily, if the cooling effect is decreased to the point where there is a good thermal effect in the center of the electrode, then there probably will not be sufficient cooling to protect tissue in contact with the edges of the electrode. As a result of these limitations, in the typical application of a standard electrode there is usually an area of non-uniform treatment and/or burns on the skin surface. So uniformity of the heating pattern is very important. It is particularly important in applications treating skin where collagen-containing layers are heated to produce a collagen contraction response for tightening of the skin. For this and related applications, if the collagen contraction and resulting skin tightening effect are non-uniform, then a medically undesirable result may occur.
  • There is a need for an improved RF handpiece for cosmetic applications.
  • SUMMARY OF THE INVENTION
  • Accordingly, an object of the present invention is to provide an RF handpiece which provides a substantially uniform delivery of energy to a target tissue site.
  • Another object of the present invention is to provide an RF handpiece which includes at least one RF electrode that is capacitively coupled to a skin surface when at least a portion of the RF electrode is in contact with the skin surface.
  • Yet another object of the present invention is to provide an RF handpiece that provides a uniform thermal effect in tissue at a selected depth, while preventing or minimizing thermal damage to a skin surface and other non-target tissue.
  • A further object of the present invention is to provide an RF handpiece configured to reduce or eliminate the edge effects and hot spots of RF electrodes applied to skin surfaces.
  • Another object of the present invention is to provide an RF handpiece configured to provide an atomizing delivery of a cooling fluidic medium to the RF electrode.
  • Still another object of the present invention is to provide an RF handpiece configured to evaporatively cool the back surface of the RF electrode, and conductively cool a skin surface adjacent to a front surface of the RF electrode.
  • A further object of the present invention is to provide an RF handpiece configured to controllably deliver a cooling fluidic medium to the back surface of the RF electrode at substantially any orientation of the front surface of the RF electrode relative to a direction of gravity.
  • Yet another object of the present invention is to provide an RF handpiece that includes an RF electrode with both conductive and dielectric portions.
  • Another object of the present invention is to provide an RF handpiece that includes a force sensor that zeros out gravity effects created by the weight of the electrode assembly of the RF handpiece in any orientation of the front surface of the RF electrode relative to a direction of gravity.
  • These and other objects of the present invention are achieved in a handpiece that has a handpiece assembly. The handpiece assembly includes a handpiece housing and a cooling fluidic medium valve member. An electrode assembly is coupled to the handpiece housing. The electrode assembly has a least one RF electrode that is capacitively coupled to a skin surface when at least a portion of the RF electrode is in contact with the skin surface.
  • In another embodiment of the present invention a handpiece, a handpiece assembly includes a handpiece housing and a cooling fluidic medium valve member with an inlet and an outlet. An electrode assembly is removeably coupled to the handpiece housing. The electrode assembly has a least one RF electrode with a front surface and a back surface. The RF electrode is capacitively coupled to a skin surface when at least a portion of the RF electrode is in contact with the skin surface.
  • In another embodiment of the present invention, a handpiece includes a handpiece assembly with a handpiece housing. An insert is at least partially positionable in the handpiece housing. An RF electrode is coupled to the insert. The RF electrode has a back surface that faces the handpiece housing and an opposing front surface. A cooling fluidic medium dispensing assembly is coupled to the handpiece housing and the insert.
  • In another embodiment of the present invention, a handpiece includes a handpiece assembly with a handpiece housing. An insert is detachably coupled to the handpiece housing. The insert includes an RF electrode with a conductive portion and a dielectric.
  • In another embodiment of the present invention, a handpiece includes a handpiece assembly with a handpiece housing. An insert is detachably coupled to the handpiece housing. An RF electrode is positioned in the insert. The RF electrode includes a flex circuit.
  • In another embodiment of the present invention, a handpiece includes a handpiece assembly with a handpiece housing. An insert is detachably coupled to the handpiece housing. The insert includes a flex circuit and an RF electrode that with a conductive portion and a dielectric.
  • In another embodiment, an electrode assembly is adapted to be coupled with a handpiece and powered to treat skin and underlying tissues. A sensor is coupled to the energy delivery device. The sensor may comprise, for example, a force sensor or a thermal sensor.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a cross-sectional view of one embodiment of the handpiece of the present invention.
  • FIG. 2 is an exploded view of the FIG. 1 insert assembly.
  • FIG. 3 is a close-up view of one embodiment of an RF electrode of the present invention.
  • FIG. 4 is another cross-sectional view of a portion of the handpiece housing from FIG. 1.
  • FIG. 5 is a cross-sectional view of the insert from FIG. 1.
  • DETAILED DESCRIPTION
  • Referring now to FIG. 1, one embodiment of the present invention is a handpiece 10 with a handpiece assembly 12. Handpiece assembly 12 includes a handpiece housing 14 and a cooling fluidic medium valve member 16. An electrode assembly 18 is coupled to handpiece housing 14. Electrode assembly 18 has a least one RF electrode 20 that is capacitively coupled to a skin surface when at least a portion of RF electrode 20 is in contact with the skin surface. Without limiting the scope of the present invention, RF electrode 20 can have a thickness in the range of 0.010 to 1.0 mm.
  • Handpiece 10 provides a more uniform thermal effect in tissue at a selected depth, while preventing or minimizing thermal damage to the skin surface and other non-target tissue. Handpiece 10 is coupled to an RF generator. RF electrode 20 can be operated either in mono-polar or bi-polar modes. Handpiece 10 is configured to reduce, or preferably eliminate edge effects and hot spots. The result is an improved aesthetic result/clinical outcome with an elimination/reduction in adverse effects and healing time.
  • A fluid delivery member 22 is coupled to cooling fluidic medium valve member 16. Fluid delivery member 22 and cooling fluidic medium valve member 16 collectively form a cooling fluidic medium dispensing assembly. Fluid delivery member 16 is configured to provide an atomizing delivery of a cooling fluidic medium to RF electrode 20. The atomizing delivery is a mist or fine spray. A phase transition, from liquid to gas, of the cooling fluidic medium occurs when it hits the surface of RF electrode 20. The transition from liquid to gas creates the cooling. If the transition before the cooling fluidic medium hits RF electrode 20 the cooling of RF electrode 20 will not be as effective.
  • In one embodiment, the cooling fluidic medium is a cryogenic spray, commercially available from Honeywell, Morristown, N.J. A specific example of a suitable cryogenic spray is R134A2, available from Refron, Inc., 38-18 33rd St., Long Island City, N.Y. 11101. The use of a cryogenic cooling fluidic medium provides the capability to use a number of different types of algorithms for skin treatment. For example, the cryogenic cooling fluidic medium can be applied milliseconds before and after the delivery of RF energy to the desired tissue. This is achieved with the use of cooling fluidic medium valve member 16 coupled to a cryogen supply, including but not limited to a compressed gas canister. In various embodiments, cooling fluidic medium valve member 16 can be coupled to a computer control system and/or manually controlled by the physician by means of a foot switch or similar device.
  • A key advantage of providing a spray, or atomization, of cryogenic cooling fluidic medium is the availability to implement rapid on and off control. Cryogenic cooling fluidic medium allows more precise temporal control of the cooling process. This is because cooling only occurs when the refrigerant is sprayed and is in an evaporative state, the latter being a very fast short-lived event. Thus, cooling ceases rapidly after the cryogenic cooling fluidic medium is stopped. The overall effect is to confer very precise time on-off control of cryogenic cooling fluidic medium.
  • Referring now to FIG. 2, fluid delivery member 22 can be positioned in handpiece housing 14 or electrode assembly 18. Fluid delivery member 22 is configured to controllably deliver a cooling fluidic medium to a back surface 24 of RF electrode 20 and maintain back surface 24 at a desired temperature. The cooling fluidic medium evaporatively cools RF electrode 20 and maintains a substantially uniform temperature of front surface 26 of RF electrode 20. Front surface 26 can be sufficiently flexible and conformable to the skin, but still have sufficient strength and/or structure to provide good thermal coupling when pressed against the skin surface.
  • RF electrode 20 then conductively cools a skin surface that is adjacent to a front surface 26 of RF electrode 20. Suitable fluidic media include a variety of refrigerants such as R134A and freon. Fluid delivery member 22 is configured to controllably deliver the cooling fluidic medium to back surface 24 at substantially any orientation of front surface 26 relative to a direction of gravity. A geometry and positioning of fluid delivery member 22 are selected to provide a substantially uniform distribution of cooling fluidic medium on back surface 24. The delivery of the cooling fluidic medium can be by spray of droplets or fine mist, flooding back surface 24, and the like. Cooling occurs at the interface of the cooling fluidic medium with atmosphere, which is where evaporation occurs. If there is a thick layer of fluid on back surface 24 the heat removed from the treated skin will need to pass through the thick layer of cooling fluidic medium, increasing thermal resistance. To maximize cooling rates, it is desirable to apply a very thin layer of cooling fluidic medium. If RF electrode 20 is not horizontal, and if there is a thick layer of cooling fluidic medium, or if there are large drops of cooling fluidic medium on back surface 24, the cooling fluidic medium can run down the surface of RF electrode 20 and pool at one edge or corner, causing uneven cooling. Therefore, it is desirable to apply a thin layer of cooling fluidic medium with a fine spray.
  • In various embodiments, RF electrode 20, as illustrated in FIG. 3, has a conductive portion 28 and a dielectric portion 30. Conductive portion 28 can be a metal including but not limited to copper, gold, silver, aluminum and the like. Dielectric portion 30 can be made of a variety of different materials including but not limited to polyimide, and the like. Other dielectric materials include but are not limited to silicon, sapphire, diamond, zirconium-toughened alumina (ZTA), alumina and the like. Dielectric portion 30 can be positioned around at least a portion, or the entirety of a periphery of conductive portion 28. Suitable materials for a dielectric portion 30 include, but are not limited to, Teflon® and the like, silicon nitride, polysilanes, polysilazanes, polyimides, Kapton and other polymers, antenna dielectrics and other dielectric materials well known in the art. In another embodiment, RF electrode 20 is made of a composite material, including but not limited to gold-plated copper, copper-polyimide, silicon/silicon-nitride and the like.
  • Dielectric portion 30 creates an increased impedance to the flow of electrical current through RF electrode 20. This increased impedance causes current to travel a path straight down through conductive portion 28 to the skin surface. Electric field edge effects, caused by a concentration of current flowing out of the edges of RF electrode 20, are reduced.
  • Dielectric portion 30 produces a more uniform impedance through RF electrode 20 and causes a more uniform current to flow through conductive portion 28. The resulting effect minimizes or even eliminates, edge effects around the edges of RF electrode 20.
  • In one embodiment, conductive portion 28 adheres to dielectric portion 30 which can be substrate with a thickness, by way of example and without limitation, of about 0.001″. This embodiment is similar to a standard flex circuit board material commercially available in the electronics industry. In this embodiment, dielectric portion 30 is in contact with the tissue, the skin, and conductive portion 28 is separated from the skin. The thickness of the dielectric portion 30 can be decreased by growing conductive portion 28 on dielectric portion 30 using a variety of techniques, including but not limited to, sputtering, electro deposition, chemical vapor deposition, plasma deposition and other deposition techniques known in the art. Additionally, these same processes can be used to deposit dielectric portion 30 onto conductive portion 28. In one embodiment dielectric portion 30 is an oxide layer which can be grown on conductive portion 28. An oxide layer has a low thermal resistance and improves the cooling efficiency of the skin compared with many other dielectrics such as polymers.
  • Fluid delivery member 22 has an inlet 32 and an outlet 34. Outlet 34 can have a smaller cross-sectional area than a cross-sectional area of inlet 32. In one embodiment, fluid delivery member 22 is a nozzle 36.
  • Cooling fluidic medium valve member 16 can be configured to provide a pulsed delivery of the cooling fluidic medium. Pulsing the delivery of cooling fluidic medium is a simple way to control the rate of cooling fluidic medium application. In one embodiment, cooling fluidic medium valve member 16 is a solenoid valve. An example of a suitable solenoid valve is a solenoid pinch valve manufactured by the N-Research Corporation, West Caldwell, N.J. If the fluid is pressurized, then opening of the valve results in fluid flow. If the fluid is maintained at a constant pressure, then the flow rate is constant and a simple open/close solenoid valve can be used, the effective flow rate being determined by the pulse duty cycle. A higher duty cycle, close to 100% increases cooling, while a lower duty cycle, closer to 0%, reduces cooling. The duty cycle can be achieved by turning on the valve for a short duration of time at a set frequency. The duration of the open time can be 1 to 50 milliseconds or longer. The frequency of pulsing can be 1 to 50 Hz or faster.
  • Alternatively, cooling fluidic medium flow rate can be controlled by a metering valve or controllable-rate pump such as a peristaltic pump. One advantage of pulsing is that it is easy to control using simple electronics and control algorithms.
  • Electrode assembly 18 is sufficiently sealed so that the cooling fluidic medium does not leak from back surface 24 onto a skin surface in contact with a front surface of RF electrode 20. This helps provide an even energy delivery through the skin surface. In one embodiment, electrode assembly 18, and more specifically RF electrode 20, has a geometry that creates a reservoir at back surface 24 to hold and gather cooling fluidic medium that has collected at back surface 24. Back surface 24 can be formed with “hospital corners” to create this reservoir. Optionally, electrode assembly 18 includes a vent 38 that permits vaporized cooling fluidic medium to escape from electrode assembly 18. This reduces the chance of cooling fluidic medium collecting at back surface 24. This can occur when cooling fluidic medium is delivered to back surface 24 in vapor form and then, following cooling of back surface 24, the vapor condenses to a liquid.
  • Vent 38 prevents pressure from building up in electrode assembly 18. Vent 38 can be a pressure relief valve that is vented to the atmosphere or a vent line. When the cooling fluidic medium comes into contact with RF electrode 20 and evaporates, the resulting gas pressurizes the inside of electrode assembly 18. This can cause RF electrode 20 to partially inflate and bow out from front surface 26. The inflated RF electrode 20 can enhance the thermal contact with the skin and also result in some degree of conformance of RF electrode 20 to the skin surface. An electronic controller can be provided. The electronic controller sends a signal to open vent 38 when a programmed pressure has been reached.
  • Various leads 40 are coupled to RF electrode 20. One or more thermal sensors 42 are coupled to RF electrode. Suitable thermal sensors 42 include but are not limited to thermocouples, thermistors, infrared photo-emitters and a thermally sensitive diode. In one embodiment, a thermal sensor 42 is positioned at each comer of RF electrode 20. A sufficient number of thermal sensors 42 are provided in order to acquire sufficient thermal data of the skin surface. Thermal sensors 42 are electrically isolated from RF electrode 20.
  • Thermal sensors 42 measure temperature and can provide feedback for monitoring temperature of RF electrode 20 and/or the tissue during treatment. Thermal sensors 42 can be thermistors, thermocouples, thermally sensitive diodes, capacitors, inductors or other devices for measuring temperature. Preferably, thermal sensors 42 provide electronic feedback to a microprocessor of the RF generator coupled to RF electrode 20 in order to facilitate control of the treatment.
  • The measurements from thermal sensors 42 can be used to help control the rate of application of cooling fluidic medium. For example, the cooling control algorithm can be used to apply cooling fluidic medium to RF electrode 20 at a high flow rate until the temperature fell below a target temperature, and then slow down or stop. A PID, or proportional-integral-differential, algorithm can be used to precisely control RF electrode 20 temperature to a predetermined value.
  • Thermal sensors 42 can be positioned placed on back surface 24 of RF electrode 20 away from the tissue. This configuration is preferable ideal for controlling the temperature of the RF electrode 20. Alternatively, thermal sensors 42 can be positioned on front surface 26 of RF electrode 10 in direct contact with the tissue. This embodiment can be more suitable for monitoring tissue temperature. Algorithms are utilized with thermal sensors 42 to calculate a temperature profile of the treated tissue. Thermal sensors 42 can be used to develop a temperature profile of the skin which is then used for process control purposes to assure that the proper amounts of heating and cooling are delivered to achieve a desired elevated deep tissue temperature while maintaining skin tissue layers below a threshold temperature and avoid thermal injury. The physician can use the measured temperature profile to assure that he stays within the boundary of an ideal/average profile for a given type of treatment. Thermal sensors 42 can be used for additional purposes. When the temperature of thermal sensors 42 is monitored it is possible to detect when RF electrode 20 is in contact with the skin surface. This can be achieved by detecting a direct change in temperature when skin contact is made or examining the rate of change of temperature which is affected by contact with the skin. Similarly, if there is more than one thermal sensor 42, the thermal sensors 42 can be used to detect whether a portion of RF electrode 20 is lifted or out of contact with skin. This can be important because the current density (amperes per unit area) delivered to the skin can vary if the contact area changes. In particular, if part of the surface of RF electrode 20 is not in contact with the skin, the resulting current density is higher than expected.
  • Referring now to FIG. 4, a force sensor 44 is also coupled to electrode assembly 18. Force sensor 44 detects an amount of force applied by electrode assembly 18, via the physician, against an applied skin surface. Force sensor 44 zeros out gravity effects of the weight of electrode assembly 18 in any orientation of front surface 26 of RF electrode 20 relative to a direction of gravity. Additionally, force sensor 44 provides an indication when RF electrode 20 is in contact with a skin surface. Force sensor 44 also provides a signal indicating that a force applied by RF electrode 20 to a contacted skin surface is, (i) below a minimum threshold or (ii) above a maximum threshold.
  • An activation button 46 is used in conjunction with the force sensor. Just prior to activating RF electrode 20, the physician holds handpiece 10 in position just off the surface of the skin. The orientation of handpiece 10 can be any angle relative to the angle of gravity. To arm handpiece 10, the physician can press activation button 46 which tares force sensor 44, by setting it to read zero. This cancels the force due to gravity in that particular treatment orientation. This method allows consistent force application of RF electrode 20 to the skin surface regardless of the angle of handpiece 10 relative to the direction of gravity.
  • RF electrode 20 can be a flex circuit, which can include trace components. Additionally, thermal sensor 42 and force sensor 44 can be part of the flex circuit. Further, the flex circuit can include a dielectric that forms a part of RF electrode 20.
  • Electrode assembly 18 can be moveable positioned within handpiece housing 12. In one embodiment, electrode assembly 18 is slideably moveable along a longitudinal axis of handpiece housing 12. Electrode assembly 18 can be rotatably mounted in handpiece housing 12. Additionally, RF electrode 20 can be rotatably positioned in electrode assembly 18. Electrode assembly 18 can be removably coupled to handpiece housing 12 as a disposable or non-disposable insert 52, see FIG. 5. For purposes of this disclosure, electrode assembly 18 is the same as insert 52. Once movably mounted to handpiece housing 12, insert 52 can be coupled to handpiece housing 12 via force sensor 44. Force sensor 44 can be of the type that is capable of measuring both compressive and tensile forces. In other embodiments, force sensor 44 only measures compressive forces, or only measures tensile forces.
  • Insert 52 can be spring-loaded with a spring 48. In one embodiment, spring 48 biases RF electrode 20 in a direction toward handpiece housing 12. This pre-loads force sensor 44 and keeps insert 52 pressed against force sensor 44. The pre-load force is tared when activation button 46 is pressed just prior to application of RF electrode 20 to the skin surface.
  • A shroud 50 is optionally coupled to handpiece 10. Shroud 50 serves to keep the user from touching insert 52 during use which can cause erroneous force readings.
  • A non-volatile memory 54 can be included with insert 52. Additionally, non-volatile memory can be included with handpiece housing 12. Non-volatile memory 54 can be an EPROM and the like. Additionally, a second non-volatile memory 56 can be included in handpiece housing 12 for purposes of storing handpiece 10 information such as but not limited to, handpiece model number or version, handpiece software version, number of RF applications that handpiece 10 has delivered, expiration date and manufacture date. Handpiece housing 12 can also contain a microprocessor 58 for purposes of acquiring and analyzing data from various sensors on handpiece housing 12 or insert 52 including but not limited to thermal sensors 42, force sensors 44, fluid pressure gauges, switches, buttons and the like. Microprocessor 58 can also control components on handpiece 10 including but not limited to lights, LEDs, valves, pumps or other electronic components. Microprocessor 58 can also communicate data to a microprocessor of the RF generator.
  • Non-volatile memory 54 can store a variety of data that can facilitate control and operation of handpiece 10 and its associated system including but not limited to, (i) controlling the amount of current delivered by RF electrode 20, (ii) controlling the duty cycle of the fluid delivery member 22, (iii) controlling the energy delivery duration time of the RF electrode 20, (iv) controlling the temperature of RF electrode 20 relative to a target temperature, (v) providing a maximum number of firings of RF electrode 20, (vi) providing a maximum allowed voltage that is deliverable by RF electrode 20, (vii) providing a history of RF electrode 20 use, (viii) providing a controllable duty cycle to fluid delivery member 22 for the delivery of the cooling fluidic medium to back surface 24 of RF electrode 20, (ix) providing a controllable delivery rate of cooling fluidic medium delivered from fluid delivery member 22 to back surface 24, and the like.
  • Handpiece 10 can be used to deliver thermal energy to modify tissue including, but not limited to, collagen containing tissue, in the epidermal, dermal and subcutaneous tissue layers, including adipose tissue. The modification of the tissue includes modifying a physical feature of the tissue, a structure of the tissue or a physical property of the tissue. The modification can be achieved by delivering sufficient energy to cause collagen shrinkage, and/or a wound healing response including the deposition of new or nascent collagen.
  • Handpiece 10 can be utilized for performing a number of treatments of the skin and underlying tissue including but not limited to, (i) dermal remodeling and tightening, (ii) wrinkle reduction, (iii) elastosis reduction, (iv) sebaceous gland removal/deactivation, (v) hair follicle removal, (vi) adipose tissue remodeling/removal, (vii) spider vein removal, and the like.
  • In various embodiments, handpiece 10 can be utilized in a variety of treatment processes, including but not limited to, (i) pre-cooling, before the delivery of energy to the tissue has begun, (ii) an on phase or energy delivery phase in conjunction with cooling and (iii) post cooling after the delivery of energy to tissue has stopped.
  • Handpiece 10 can be used to pre-cool the surface layers of the target tissue so that when RF electrode 20 is in contact with the tissue, or prior to turning on the RF energy source, the superficial layers of the target tissue are already cooled. When RF energy source is turned on or delivery of RF to the tissue otherwise begins, resulting in heating of the tissues, the tissue that has been cooled is protected from thermal effects including thermal damage. The tissue that has not been cooled will warm up to therapeutic temperatures resulting in the desired therapeutic effect.
  • Pre-cooling gives time for the thermal effects of cooling to propagate down into the tissue. More specifically, pre-cooling allows the achievement of a desired tissue depth thermal profile, with a minimum desired temperature being achieved at a selectable depth. The amount or duration of pre-cooling can be used to select the depth of the protected zone of untreated tissue. Longer durations of pre-cooling produce a deeper protected zone and hence a deeper level in tissue for the start of the treatment zone. The opposite is true for shorter periods of pre-cooling. The temperature of front surface 26 of RF electrode 20 also affects the temperature profile. The colder the temperature of front surface 26, the faster and deeper the cooling, and vice verse.
  • Post-cooling can be important because it prevents and/or reduces heat delivered to the deeper layers from conducting upward and heating the more superficial layers possibly to therapeutic or damaging temperature range even though external energy delivery to the tissue has ceased. In order to prevent this and related thermal phenomena, it can be desirable to maintain cooling of the treatment surface for a period of time after application of the RF energy has ceased. In various embodiments, varying amounts of post cooling can be combined with real-time cooling and/or pre-cooling.
  • In various embodiments, handpiece 10 can be used in a varied number of pulse on-off type cooling sequences and algorithms may be employed. In one embodiment, the treatment algorithm provides for pre-cooling of the tissue by starting a spray of cryogenic cooling fluidic medium, followed by a short pulse of RF energy into the tissue. In this embodiment, the spray of cryogenic cooling fluidic medium continues while the RF energy is delivered, and is stopping shortly thereafter, e.g. on the order of milliseconds. This or another treatment sequence can be repeated again. Thus in various embodiments, the treatment sequence can include a pulsed sequence of cooling on, heat, cooling off, cooling on, heat, cool off, and with cooling and heating durations on orders of tens of milliseconds. In these embodiments, every time the surface of the tissue of the skin is cooled, heat is removed from the skin surface. Cryogenic cooling fluidic medium spray duration, and intervals between sprays, can be in the tens of milliseconds ranges, which allows surface cooling while still delivering the desired thermal effect into the deeper target tissue.
  • In various embodiments, the target tissue zone for therapy, also called therapeutic zone or thermal effect zone, can be at a tissue depth from approximately 100 μm beneath the surface of the skin down to as deep as 10 millimeters, depending upon the type of treatment. For treatments involving collagen contraction, it can be desirable to cool both the epidermis and the superficial layers of the dermis of the skin that lies beneath the epidermis, to a cooled depth range between 100 μm two millimeters. Different treatment algorithms can incorporate different amounts of pre-cooling, heating and post cooling phases in order to produce a desired tissue effect at a desired depth.
  • Various duty cycles, on and off times, of cooling and heating are utilized depending on the type of treatment. The cooling and heating duty cycles can be controlled and dynamically varied by an electronic control system known in the art. Specifically the control system can be used to control cooling fluidic medium valve member 16 and the RF power source.
  • The foregoing description of a preferred embodiment of the invention has been presented for purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise forms disclosed. Obviously, many modifications and variations will be apparent to practitioners skilled in this art. It is intended that the scope of the invention be defined by the following claims and their equivalents.

Claims (13)

1. An apparatus for use with a handpiece to non-invasively treat tissue beneath a skin: surface using radiofrequency energy, the apparatus comprising:
an energy delivery device adapted to be removably coupled to the handpiece, the energy delivery device including a dielectric portion and a conductive portion disposed on the dielectric portion, the conductive portion configured to deliver the radiofrequency energy to the tissue, and the dielectric portion adapted to be positioned between the conductive portion and the skin surface such that the radiofrequency energy is transmitted from the conductive portion through the dielectric portion for capacitively coupling with the tissue to perform the non-invasive tissue treatment; and
a sensor coupled to the energy delivery device.
2. The apparatus of claim 1 wherein the sensor is a thermal sensor, a thermocouple, an optical sensor, a current sensor, voltage sensor, an impedance sensor, or a flow sensor.
3. The apparatus of claim 1 wherein the sensor is a force sensor.
4. The apparatus of claim 3 wherein the dielectric portion and the conductive portion comprise a flex circuit, and the force sensor is coupled to the flex circuit.
5. The apparatus of claim 1 wherein the sensor is a thermocouple, a thermistor, an infrared photo-emitter, or a thermally sensitive diode.
6. The apparatus of claim 1 wherein the energy delivery device further comprises a support structure, the energy delivery device is coupled to the support structure, and the sensor is carried by the support structure.
7. The apparatus of claim 1 further comprising:
a cooling media delivery member coupled to the energy delivery device, the cooling media delivery member configured to deliver a cooling media to the energy delivery device.
8. The apparatus of claim 7 further comprising:
a non-volatile memory coupled to the energy delivery device, the non-volatile memory configured to store at least one of a duty cycle for controlling the fluid delivery member, a number of times the energy delivery device has been moved relative to the skin surface, or a number of areas treated by the energy delivery device.
9. The apparatus of claim 8 wherein the non-volatile memory is mechanically coupled to the energy delivery device.
10. The apparatus of claim 1 further comprising:
a non-volatile memory coupled to the energy delivery device.
11. The apparatus of claim 10 wherein the non-volatile memory is configured to store at least one of:
a number of times the energy delivery device has been moved relative to the skin surface, or
a number of areas treated by the energy delivery device.
12. The apparatus of claim 10 wherein the non-volatile memory is mechanically coupled to the energy delivery device.
13. The apparatus of claim 1 wherein the energy delivery device is configured to reduce at least one of an edge effect, an electrode edge effect, an electrode temperature gradient an electrode current density gradient, or a tissue interface surface temperature gradient.
US11/531,081 1999-03-09 2006-09-12 energy delivery device for treating tissue Abandoned US20070010811A1 (en)

Priority Applications (5)

Application Number Priority Date Filing Date Title
US11/531,081 US20070010811A1 (en) 1999-03-09 2006-09-12 energy delivery device for treating tissue
US12/507,405 US8603088B2 (en) 1999-03-09 2009-07-22 Apparatus for transcutaneously treating tissue
US14/074,927 US9636175B2 (en) 1999-03-09 2013-11-08 Apparatus for transcutaneously treating tissue
US15/483,556 US20170209212A1 (en) 1999-03-09 2017-04-10 Apparatus for transcutaneously treating tissue
US16/196,114 US20190090947A1 (en) 1999-03-09 2018-11-20 Apparatus for transcutaneously treating tissue

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US12344099P 1999-03-09 1999-03-09
US09/522,275 US6413255B1 (en) 1999-03-09 2000-03-09 Apparatus and method for treatment of tissue
US10/072,610 US7141049B2 (en) 1999-03-09 2002-02-06 Handpiece for treatment of tissue
US11/531,081 US20070010811A1 (en) 1999-03-09 2006-09-12 energy delivery device for treating tissue

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/072,610 Continuation US7141049B2 (en) 1996-01-05 2002-02-06 Handpiece for treatment of tissue

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US12/507,405 Continuation US8603088B2 (en) 1999-03-09 2009-07-22 Apparatus for transcutaneously treating tissue

Publications (1)

Publication Number Publication Date
US20070010811A1 true US20070010811A1 (en) 2007-01-11

Family

ID=27732314

Family Applications (6)

Application Number Title Priority Date Filing Date
US10/072,610 Expired - Lifetime US7141049B2 (en) 1996-01-05 2002-02-06 Handpiece for treatment of tissue
US11/531,081 Abandoned US20070010811A1 (en) 1999-03-09 2006-09-12 energy delivery device for treating tissue
US12/507,405 Expired - Lifetime US8603088B2 (en) 1999-03-09 2009-07-22 Apparatus for transcutaneously treating tissue
US14/074,927 Expired - Fee Related US9636175B2 (en) 1999-03-09 2013-11-08 Apparatus for transcutaneously treating tissue
US15/483,556 Abandoned US20170209212A1 (en) 1999-03-09 2017-04-10 Apparatus for transcutaneously treating tissue
US16/196,114 Abandoned US20190090947A1 (en) 1999-03-09 2018-11-20 Apparatus for transcutaneously treating tissue

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US10/072,610 Expired - Lifetime US7141049B2 (en) 1996-01-05 2002-02-06 Handpiece for treatment of tissue

Family Applications After (4)

Application Number Title Priority Date Filing Date
US12/507,405 Expired - Lifetime US8603088B2 (en) 1999-03-09 2009-07-22 Apparatus for transcutaneously treating tissue
US14/074,927 Expired - Fee Related US9636175B2 (en) 1999-03-09 2013-11-08 Apparatus for transcutaneously treating tissue
US15/483,556 Abandoned US20170209212A1 (en) 1999-03-09 2017-04-10 Apparatus for transcutaneously treating tissue
US16/196,114 Abandoned US20190090947A1 (en) 1999-03-09 2018-11-20 Apparatus for transcutaneously treating tissue

Country Status (12)

Country Link
US (6) US7141049B2 (en)
EP (2) EP1808145A2 (en)
JP (1) JP2005516666A (en)
KR (1) KR100706155B1 (en)
CN (1) CN1627923A (en)
AT (1) ATE411778T1 (en)
AU (1) AU2003207858B2 (en)
BR (1) BR0307392A (en)
CA (1) CA2474421A1 (en)
DE (1) DE60324249D1 (en)
ES (1) ES2314180T3 (en)
WO (1) WO2003065916A1 (en)

Cited By (44)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050222565A1 (en) * 2004-04-01 2005-10-06 Dieter Manstein Method and apparatus for dermatological treatment and tissue reshaping
US20080009923A1 (en) * 2006-06-14 2008-01-10 Paithankar Dilip Y Treatment of Skin by Spatial Modulation of Thermal Heating
US20080077201A1 (en) * 2006-09-26 2008-03-27 Juniper Medical, Inc. Cooling devices with flexible sensors
US20080269735A1 (en) * 2007-04-26 2008-10-30 Agustina Vila Echague Optical array for treating biological tissue
US20080306418A1 (en) * 2007-06-05 2008-12-11 Reliant Technologies, Inc. Method for Reducing Pain of Dermatological Treatments
US20090043301A1 (en) * 2007-08-09 2009-02-12 Asthmatx, Inc. Monopolar energy delivery devices and methods for controlling current density in tissue
US20090281540A1 (en) * 2008-05-06 2009-11-12 Blomgren Richard D Apparatus, Systems and Methods for Treating a Human Tissue Condition
US20100179455A1 (en) * 2009-01-12 2010-07-15 Solta Medical, Inc. Tissue treatment apparatus with functional mechanical stimulation and methods for reducing pain during tissue treatments
US20100280582A1 (en) * 2009-04-30 2010-11-04 Zeltiq Aesthetics, Inc. Device, system and method of removing heat from subcutaneous lipid-rich cells
US20100298825A1 (en) * 2009-05-08 2010-11-25 Cellutions, Inc. Treatment System With A Pulse Forming Network For Achieving Plasma In Tissue
US20110202048A1 (en) * 2010-02-12 2011-08-18 Solta Medical, Inc. Methods for pain reduction with functional thermal stimulation and tissue treatment systems
US20110238051A1 (en) * 2010-01-25 2011-09-29 Zeltiq Aesthetics, Inc. Home-use applicators for non-invasively removing heat from subcutaneous lipid-rich cells via phase change coolants, and associated devices, systems and methods
US8073550B1 (en) 1997-07-31 2011-12-06 Miramar Labs, Inc. Method and apparatus for treating subcutaneous histological features
US8401668B2 (en) 2007-04-19 2013-03-19 Miramar Labs, Inc. Systems and methods for creating an effect using microwave energy to specified tissue
US8406894B2 (en) 2007-12-12 2013-03-26 Miramar Labs, Inc. Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy
US8676338B2 (en) 2010-07-20 2014-03-18 Zeltiq Aesthetics, Inc. Combined modality treatment systems, methods and apparatus for body contouring applications
US8788060B2 (en) 2009-07-16 2014-07-22 Solta Medical, Inc. Tissue treatment systems with high powered functional electrical stimulation and methods for reducing pain during tissue treatments
US8882758B2 (en) 2009-01-09 2014-11-11 Solta Medical, Inc. Tissue treatment apparatus and systems with pain mitigation and methods for mitigating pain during tissue treatments
WO2015160076A1 (en) * 2014-04-17 2015-10-22 주식회사 제이에스온 High-frequency thermotherapy device
US9277958B2 (en) 2012-02-22 2016-03-08 Candela Corporation Reduction of RF electrode edge effect
US9375345B2 (en) 2006-09-26 2016-06-28 Zeltiq Aesthetics, Inc. Cooling device having a plurality of controllable cooling elements to provide a predetermined cooling profile
US9408745B2 (en) 2007-08-21 2016-08-09 Zeltiq Aesthetics, Inc. Monitoring the cooling of subcutaneous lipid-rich cells, such as the cooling of adipose tissue
US9545523B2 (en) 2013-03-14 2017-01-17 Zeltiq Aesthetics, Inc. Multi-modality treatment systems, methods and apparatus for altering subcutaneous lipid-rich tissue
USD777338S1 (en) 2014-03-20 2017-01-24 Zeltiq Aesthetics, Inc. Cryotherapy applicator for cooling tissue
US9655770B2 (en) 2007-07-13 2017-05-23 Zeltiq Aesthetics, Inc. System for treating lipid-rich regions
US9737434B2 (en) 2008-12-17 2017-08-22 Zeltiq Aestehtics, Inc. Systems and methods with interrupt/resume capabilities for treating subcutaneous lipid-rich cells
US9844460B2 (en) 2013-03-14 2017-12-19 Zeltiq Aesthetics, Inc. Treatment systems with fluid mixing systems and fluid-cooled applicators and methods of using the same
US9861421B2 (en) 2014-01-31 2018-01-09 Zeltiq Aesthetics, Inc. Compositions, treatment systems and methods for improved cooling of lipid-rich tissue
US9889297B2 (en) 2012-02-22 2018-02-13 Candela Corporation Reduction of RF electrode edge effect
US10383787B2 (en) 2007-05-18 2019-08-20 Zeltiq Aesthetics, Inc. Treatment apparatus for removing heat from subcutaneous lipid-rich cells and massaging tissue
US10524956B2 (en) 2016-01-07 2020-01-07 Zeltiq Aesthetics, Inc. Temperature-dependent adhesion between applicator and skin during cooling of tissue
US10555831B2 (en) 2016-05-10 2020-02-11 Zeltiq Aesthetics, Inc. Hydrogel substances and methods of cryotherapy
US10568759B2 (en) 2014-08-19 2020-02-25 Zeltiq Aesthetics, Inc. Treatment systems, small volume applicators, and methods for treating submental tissue
US10675176B1 (en) 2014-03-19 2020-06-09 Zeltiq Aesthetics, Inc. Treatment systems, devices, and methods for cooling targeted tissue
US10682297B2 (en) 2016-05-10 2020-06-16 Zeltiq Aesthetics, Inc. Liposomes, emulsions, and methods for cryotherapy
US10765552B2 (en) 2016-02-18 2020-09-08 Zeltiq Aesthetics, Inc. Cooling cup applicators with contoured heads and liner assemblies
US10935174B2 (en) 2014-08-19 2021-03-02 Zeltiq Aesthetics, Inc. Stress relief couplings for cryotherapy apparatuses
US10952891B1 (en) 2014-05-13 2021-03-23 Zeltiq Aesthetics, Inc. Treatment systems with adjustable gap applicators and methods for cooling tissue
US11076879B2 (en) 2017-04-26 2021-08-03 Zeltiq Aesthetics, Inc. Shallow surface cryotherapy applicators and related technology
US11154418B2 (en) 2015-10-19 2021-10-26 Zeltiq Aesthetics, Inc. Vascular treatment systems, cooling devices, and methods for cooling vascular structures
US11382790B2 (en) 2016-05-10 2022-07-12 Zeltiq Aesthetics, Inc. Skin freezing systems for treating acne and skin conditions
US11395760B2 (en) 2006-09-26 2022-07-26 Zeltiq Aesthetics, Inc. Tissue treatment methods
US11446175B2 (en) 2018-07-31 2022-09-20 Zeltiq Aesthetics, Inc. Methods, devices, and systems for improving skin characteristics
USD971415S1 (en) 2019-12-30 2022-11-29 Cynosure, Llc Flexible applicator

Families Citing this family (299)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7473251B2 (en) * 1996-01-05 2009-01-06 Thermage, Inc. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US7229436B2 (en) 1996-01-05 2007-06-12 Thermage, Inc. Method and kit for treatment of tissue
US7267675B2 (en) * 1996-01-05 2007-09-11 Thermage, Inc. RF device with thermo-electric cooler
US10285694B2 (en) 2001-10-20 2019-05-14 Covidien Lp Surgical stapler with timer and feedback display
US7464847B2 (en) 2005-06-03 2008-12-16 Tyco Healthcare Group Lp Surgical stapler with timer and feedback display
CA2493556C (en) 2002-07-25 2012-04-03 Thomas L. Ii Buchman Electrosurgical pencil with drag sensing capability
US8361067B2 (en) 2002-09-30 2013-01-29 Relievant Medsystems, Inc. Methods of therapeutically heating a vertebral body to treat back pain
US7244257B2 (en) 2002-11-05 2007-07-17 Sherwood Services Ag Electrosurgical pencil having a single button variable control
US7235072B2 (en) 2003-02-20 2007-06-26 Sherwood Services Ag Motion detector for controlling electrosurgical output
US10105140B2 (en) 2009-11-20 2018-10-23 Covidien Lp Surgical console and hand-held surgical device
US10041822B2 (en) 2007-10-05 2018-08-07 Covidien Lp Methods to shorten calibration times for powered devices
US10022123B2 (en) 2012-07-09 2018-07-17 Covidien Lp Surgical adapter assemblies for use between surgical handle assembly and surgical end effectors
US9055943B2 (en) 2007-09-21 2015-06-16 Covidien Lp Hand held surgical handle assembly, surgical adapters for use between surgical handle assembly and surgical end effectors, and methods of use
US8968276B2 (en) 2007-09-21 2015-03-03 Covidien Lp Hand held surgical handle assembly, surgical adapters for use between surgical handle assembly and surgical end effectors, and methods of use
US11311291B2 (en) 2003-10-17 2022-04-26 Covidien Lp Surgical adapter assemblies for use between surgical handle assembly and surgical end effectors
US7156842B2 (en) 2003-11-20 2007-01-02 Sherwood Services Ag Electrosurgical pencil with improved controls
US7879033B2 (en) 2003-11-20 2011-02-01 Covidien Ag Electrosurgical pencil with advanced ES controls
US7503917B2 (en) 2003-11-20 2009-03-17 Covidien Ag Electrosurgical pencil with improved controls
US7476242B2 (en) 2004-01-30 2009-01-13 Ams Research Corporation Electrically heated/phase change probe temperature control
US20060047281A1 (en) 2004-09-01 2006-03-02 Syneron Medical Ltd. Method and system for invasive skin treatment
US11291443B2 (en) 2005-06-03 2022-04-05 Covidien Lp Surgical stapler with timer and feedback display
US7500974B2 (en) 2005-06-28 2009-03-10 Covidien Ag Electrode with rotatably deployable sheath
US7828794B2 (en) 2005-08-25 2010-11-09 Covidien Ag Handheld electrosurgical apparatus for controlling operating room equipment
US20070078502A1 (en) * 2005-10-05 2007-04-05 Thermage, Inc. Method and apparatus for estimating a local impedance factor
US7957815B2 (en) * 2005-10-11 2011-06-07 Thermage, Inc. Electrode assembly and handpiece with adjustable system impedance, and methods of operating an energy-based medical system to treat tissue
US8702691B2 (en) * 2005-10-19 2014-04-22 Thermage, Inc. Treatment apparatus and methods for delivering energy at multiple selectable depths in tissue
US8961511B2 (en) 2006-02-07 2015-02-24 Viveve, Inc. Vaginal remodeling device and methods
JP5055500B2 (en) * 2006-04-04 2012-10-24 並木精密宝石株式会社 Therapeutic antenna probe, method of use thereof, and electromagnetic therapeutic system
US20070260240A1 (en) 2006-05-05 2007-11-08 Sherwood Services Ag Soft tissue RF transection and resection device
US8317782B1 (en) * 2006-10-13 2012-11-27 Ellman International, Inc. Non-ablative radio-frequency treatment of skin tissue
US8273080B2 (en) 2006-10-16 2012-09-25 Syneron Medical Ltd. Methods and devices for treating tissue
US8142426B2 (en) 2006-10-16 2012-03-27 Syneron Medical Ltd. Methods and devices for treating tissue
US8007493B2 (en) 2006-10-16 2011-08-30 Syneron Medical Ltd. Methods and devices for treating tissue
US8133216B2 (en) 2006-10-16 2012-03-13 Syneron Medical Ltd. Methods and devices for treating tissue
US10085798B2 (en) * 2006-12-29 2018-10-02 St. Jude Medical, Atrial Fibrillation Division, Inc. Ablation electrode with tactile sensor
US8226648B2 (en) 2007-12-31 2012-07-24 St. Jude Medical, Atrial Fibrillation Division, Inc. Pressure-sensitive flexible polymer bipolar electrode
WO2008091983A2 (en) * 2007-01-25 2008-07-31 Thermage, Inc. Treatment apparatus and methods for inducing microburn patterns in tissue
US20080200969A1 (en) * 2007-02-16 2008-08-21 Thermage, Inc. Temperature sensing apparatus and methods for treatment devices used to deliver high frequency energy to tissue
WO2008131306A1 (en) 2007-04-19 2008-10-30 The Foundry, Inc. Systems and methods for creating an effect using microwave energy to specified tissue
ES2488565T3 (en) 2007-04-19 2014-08-27 Miramar Labs, Inc. Devices and systems for the non-invasive distribution of microwave therapy
JP2010524591A (en) 2007-04-19 2010-07-22 ザ ファウンドリー, インコーポレイテッド Method and apparatus for reducing sweat production
US8845630B2 (en) 2007-06-15 2014-09-30 Syneron Medical Ltd Devices and methods for percutaneous energy delivery
WO2009009661A1 (en) * 2007-07-10 2009-01-15 Thermage, Inc. Treatment apparatus and methods for delivering high frequency energy across large tissue areas
US8992516B2 (en) * 2007-07-19 2015-03-31 Avedro, Inc. Eye therapy system
US8202272B2 (en) * 2007-07-19 2012-06-19 Avedro, Inc. Eye therapy system
US8506565B2 (en) 2007-08-23 2013-08-13 Covidien Lp Electrosurgical device with LED adapter
US8287579B2 (en) * 2007-09-17 2012-10-16 Thermage, Inc. Method of using cryogenic compositions for cooling heated skin
EP3097869B1 (en) 2007-09-21 2020-03-11 Covidien LP Surgical device
US9023014B2 (en) 2007-09-21 2015-05-05 Covidien Lp Quick connect assembly for use between surgical handle assembly and surgical accessories
US8517241B2 (en) 2010-04-16 2013-08-27 Covidien Lp Hand-held surgical devices
US10779818B2 (en) 2007-10-05 2020-09-22 Covidien Lp Powered surgical stapling device
US10498269B2 (en) 2007-10-05 2019-12-03 Covidien Lp Powered surgical stapling device
EP2227197A4 (en) 2007-12-05 2011-06-22 Avedro Inc Eye therapy system
US8235987B2 (en) 2007-12-05 2012-08-07 Tyco Healthcare Group Lp Thermal penetration and arc length controllable electrosurgical pencil
US20090149930A1 (en) * 2007-12-07 2009-06-11 Thermage, Inc. Apparatus and methods for cooling a treatment apparatus configured to non-invasively deliver electromagnetic energy to a patient's tissue
MX2010006363A (en) 2007-12-12 2010-10-26 Miramar Labs Inc Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy.
US8180458B2 (en) * 2007-12-17 2012-05-15 Thermage, Inc. Method and apparatus for digital signal processing for radio frequency surgery measurements
EP2561819B1 (en) 2008-01-17 2015-01-07 Syneron Medical Ltd. Hair removal apparatus for personal use
US8348935B2 (en) * 2008-01-23 2013-01-08 Avedro, Inc. System and method for reshaping an eye feature
US8409189B2 (en) * 2008-01-23 2013-04-02 Avedro, Inc. System and method for reshaping an eye feature
US8469952B2 (en) 2008-01-23 2013-06-25 Avedro, Inc. System and method for positioning an eye therapy device
MX2010007407A (en) 2008-01-24 2010-08-16 Syneron Medical Ltd A device, apparatus, and method of adipose tissue treatment.
US20120022512A1 (en) * 2008-01-24 2012-01-26 Boris Vaynberg Device, apparatus, and method of adipose tissue treatment
US8321031B1 (en) * 2008-02-04 2012-11-27 Ellman International, Inc Radio-frequency treatment of skin tissue with temperature sensing
US8636733B2 (en) 2008-03-31 2014-01-28 Covidien Lp Electrosurgical pencil including improved controls
US8663219B2 (en) 2008-03-31 2014-03-04 Covidien Lp Electrosurgical pencil including improved controls
US8597292B2 (en) 2008-03-31 2013-12-03 Covidien Lp Electrosurgical pencil including improved controls
EP2907465A1 (en) 2008-04-17 2015-08-19 Miramar Labs, Inc. Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy
US8515553B2 (en) * 2008-04-28 2013-08-20 Thermage, Inc. Methods and apparatus for predictively controlling the temperature of a coolant delivered to a treatment device
US20090275936A1 (en) * 2008-05-01 2009-11-05 David Muller System and method for applying therapy to an eye using energy conduction
US8121704B2 (en) * 2008-06-19 2012-02-21 Thermage, Inc. Leakage-resistant tissue treatment apparatus and methods of using same
US8285392B2 (en) * 2008-06-19 2012-10-09 Thermage, Inc. Leakage-resistant tissue treatment apparatus and methods of using such tissue treatment apparatus
US8162937B2 (en) 2008-06-27 2012-04-24 Tyco Healthcare Group Lp High volume fluid seal for electrosurgical handpiece
US8986323B2 (en) 2008-08-22 2015-03-24 Envy Medical, Inc. Microdermabrasion system upgrade kit
US8945104B2 (en) 2008-08-22 2015-02-03 Envy Medical, Inc. Microdermabrasion system with combination skin therapies
EP2330998A4 (en) * 2008-09-11 2013-01-23 Syneron Medical Ltd A device, apparatus, and method of adipose tissue treatment
EP2341860A4 (en) * 2008-09-11 2013-02-20 Avedro Inc Eye therapy system
MX2011002656A (en) * 2008-09-11 2011-10-24 Syneron Medical Ltd A safe skin treatment apparatus for personal use and method for its use.
JP2012502763A (en) * 2008-09-19 2012-02-02 アヴェドロ・インコーポレーテッド Eye therapy system
BRPI0917921A2 (en) 2008-09-21 2015-11-10 Syneron Medical Ltd method and apparatus for personal skin care
US10028753B2 (en) 2008-09-26 2018-07-24 Relievant Medsystems, Inc. Spine treatment kits
WO2010039854A1 (en) 2008-09-30 2010-04-08 Neal Marshall Eye therapy system
US8460278B2 (en) 2008-10-01 2013-06-11 Avedro, Inc. Eye therapy system
US8882757B2 (en) 2008-11-11 2014-11-11 Avedro, Inc. Eye therapy system
US8231620B2 (en) 2009-02-10 2012-07-31 Tyco Healthcare Group Lp Extension cutting blade
EP2730313A1 (en) 2009-02-25 2014-05-14 Syneron Medical Ltd. Electrical skin rejuvenation
EP2413831B1 (en) * 2009-04-01 2015-03-25 The General Hospital Corporation Apparatus for fat removal
US8712536B2 (en) 2009-04-02 2014-04-29 Avedro, Inc. Eye therapy system
US8882768B2 (en) 2009-04-24 2014-11-11 Megadyne Medical Products, Inc. Hand piece with adjustable utility conduit
US8882767B2 (en) 2009-04-24 2014-11-11 Megadyne Medical Products, Inc. Electrosurgical instrument with adjustable utility conduit
US8211103B2 (en) * 2009-04-24 2012-07-03 Megadyne Medical Products, Inc. Electrosurgical instrument with adjustable power cable
AU2010295586B2 (en) 2009-09-18 2016-02-18 Viveve, Inc. Vaginal remodeling device and methods
WO2011050164A1 (en) 2009-10-21 2011-04-28 Avedro, Inc. Eye therapy
US8177778B2 (en) * 2009-10-30 2012-05-15 Avedro, Inc. System and method for stabilizing corneal tissue after treatment
US9060798B2 (en) * 2009-11-16 2015-06-23 Covidien Lp Surgical forceps capable of adjusting sealing pressure based on vessel size
US9050133B1 (en) 2009-12-22 2015-06-09 Envy Medical, Inc. Skin treatment system with adjustable height wand
EP3556330A1 (en) 2010-03-19 2019-10-23 Avedro, Inc. Systems for applying and monitoring eye therapy
WO2011133539A2 (en) * 2010-04-19 2011-10-27 The Procter & Gamble Company Combined energy and topical composition application for regulating the condition of mammalian skin
EP2394693A1 (en) * 2010-06-10 2011-12-14 Golsen Limited Electrical impulse stimulation device for the healing of wounds
US8292150B2 (en) 2010-11-02 2012-10-23 Tyco Healthcare Group Lp Adapter for powered surgical devices
DE102010060336B4 (en) * 2010-11-04 2015-03-26 Erbe Elektromedizin Gmbh Electrode device of an electrosurgical instrument
DE102011014624B4 (en) 2011-03-21 2013-09-05 Viemedic Schönheitstechnik GmbH Device for the cosmetic treatment of facial skin
US9044308B2 (en) 2011-05-24 2015-06-02 Avedro, Inc. Systems and methods for reshaping an eye feature
EP2713849B1 (en) 2011-06-02 2017-02-15 Avedro, Inc. Systems for monitoring time based photo active agent delivery or photo active marker presence
US8768455B2 (en) * 2011-06-13 2014-07-01 Triune Ip Llc Topical applicator
US9314301B2 (en) 2011-08-01 2016-04-19 Miramar Labs, Inc. Applicator and tissue interface module for dermatological device
US11207089B2 (en) 2011-10-25 2021-12-28 Covidien Lp Apparatus for endoscopic procedures
US9492146B2 (en) 2011-10-25 2016-11-15 Covidien Lp Apparatus for endoscopic procedures
US8672206B2 (en) 2011-10-25 2014-03-18 Covidien Lp Apparatus for endoscopic procedures
US9480492B2 (en) 2011-10-25 2016-11-01 Covidien Lp Apparatus for endoscopic procedures
US9364231B2 (en) 2011-10-27 2016-06-14 Covidien Lp System and method of using simulation reload to optimize staple formation
KR101290606B1 (en) * 2011-12-29 2013-07-30 김선환 Stimulating Apparatus for Curing Skin Tissue
WO2013101772A1 (en) 2011-12-30 2013-07-04 Relievant Medsystems, Inc. Systems and methods for treating back pain
CN105919666A (en) 2012-03-16 2016-09-07 女康乐公司 Therapy equipment for repairing female vaginal tissue
US9868198B2 (en) 2012-06-01 2018-01-16 Covidien Lp Hand held surgical handle assembly, surgical adapters for use between surgical handle assembly and surgical loading units, and methods of use
US10080563B2 (en) 2012-06-01 2018-09-25 Covidien Lp Loading unit detection assembly and surgical device for use therewith
US9597104B2 (en) 2012-06-01 2017-03-21 Covidien Lp Handheld surgical handle assembly, surgical adapters for use between surgical handle assembly and surgical end effectors, and methods of use
GB201210296D0 (en) 2012-06-12 2012-07-25 Gyrus Medical Ltd Electrosurgical instrument & system
US9364220B2 (en) 2012-06-19 2016-06-14 Covidien Lp Apparatus for endoscopic procedures
US10492814B2 (en) 2012-07-09 2019-12-03 Covidien Lp Apparatus for endoscopic procedures
US9839480B2 (en) 2012-07-09 2017-12-12 Covidien Lp Surgical adapter assemblies for use between surgical handle assembly and surgical end effectors
JP6271541B2 (en) 2012-07-16 2018-01-31 アヴェドロ・インコーポレーテッドAvedro,Inc. System and method for corneal cross-linking by pulsed light
US9402604B2 (en) 2012-07-20 2016-08-02 Covidien Lp Apparatus for endoscopic procedures
DE102012015482A1 (en) * 2012-08-07 2014-02-13 Cinogy Gmbh Electrode arrangement for a disabled plasma
CA2881462C (en) 2012-08-09 2020-07-14 University Of Iowa Research Foundation Catheters, catheter systems, and methods for puncturing through a tissue structure
US10588691B2 (en) 2012-09-12 2020-03-17 Relievant Medsystems, Inc. Radiofrequency ablation of tissue within a vertebral body
US9421014B2 (en) 2012-10-18 2016-08-23 Covidien Lp Loading unit velocity and position feedback
CA2889478C (en) 2012-11-05 2020-11-24 Relievant Medsystems, Inc. Systems and methods for creating curved paths through bone and modulating nerves within the bone
US9782187B2 (en) 2013-01-18 2017-10-10 Covidien Lp Adapter load button lockout
US10918364B2 (en) 2013-01-24 2021-02-16 Covidien Lp Intelligent adapter assembly for use with an electromechanical surgical system
US9216013B2 (en) 2013-02-18 2015-12-22 Covidien Lp Apparatus for endoscopic procedures
US9421003B2 (en) 2013-02-18 2016-08-23 Covidien Lp Apparatus for endoscopic procedures
US9492189B2 (en) 2013-03-13 2016-11-15 Covidien Lp Apparatus for endoscopic procedures
EP2968925B1 (en) 2013-03-14 2020-02-19 Cynosure, LLC Electrosurgical systems
US10492849B2 (en) 2013-03-15 2019-12-03 Cynosure, Llc Surgical instruments and systems with multimodes of treatments and electrosurgical operation
KR101743706B1 (en) 2013-03-28 2017-06-07 주식회사 루트로닉 A treatment apparatus using radio frequency energy
WO2014168832A1 (en) 2013-04-08 2014-10-16 Farhan Taghizadeh System and method for providing treatment feedback for a thermal treatment device
US9700318B2 (en) 2013-04-09 2017-07-11 Covidien Lp Apparatus for endoscopic procedures
US9775610B2 (en) 2013-04-09 2017-10-03 Covidien Lp Apparatus for endoscopic procedures
US9801646B2 (en) 2013-05-30 2017-10-31 Covidien Lp Adapter load button decoupled from loading unit sensor
WO2014205145A1 (en) 2013-06-18 2014-12-24 Avedro, Inc. Systems and methods for determining biomechanical properties of the eye for applying treatment
US9498114B2 (en) 2013-06-18 2016-11-22 Avedro, Inc. Systems and methods for determining biomechanical properties of the eye for applying treatment
US9797486B2 (en) 2013-06-20 2017-10-24 Covidien Lp Adapter direct drive with manual retraction, lockout and connection mechanisms
WO2015013502A2 (en) 2013-07-24 2015-01-29 Miramar Labs, Inc. Apparatus and methods for the treatment of tissue using microwave energy
US9724151B2 (en) 2013-08-08 2017-08-08 Relievant Medsystems, Inc. Modulating nerves within bone using bone fasteners
US9955966B2 (en) 2013-09-17 2018-05-01 Covidien Lp Adapter direct drive with manual retraction, lockout, and connection mechanisms for improper use prevention
US10271840B2 (en) 2013-09-18 2019-04-30 Covidien Lp Apparatus and method for differentiating between tissue and mechanical obstruction in a surgical instrument
US9974540B2 (en) 2013-10-18 2018-05-22 Covidien Lp Adapter direct drive twist-lock retention mechanism
US9295522B2 (en) 2013-11-08 2016-03-29 Covidien Lp Medical device adapter with wrist mechanism
US10236616B2 (en) 2013-12-04 2019-03-19 Covidien Lp Adapter assembly for interconnecting surgical devices and surgical attachments, and surgical systems thereof
US9918713B2 (en) 2013-12-09 2018-03-20 Covidien Lp Adapter assembly for interconnecting electromechanical surgical devices and surgical loading units, and surgical systems thereof
US9937626B2 (en) 2013-12-11 2018-04-10 Covidien Lp Wrist and jaw assemblies for robotic surgical systems
US10220522B2 (en) 2013-12-12 2019-03-05 Covidien Lp Gear train assemblies for robotic surgical systems
US9808245B2 (en) 2013-12-13 2017-11-07 Covidien Lp Coupling assembly for interconnecting an adapter assembly and a surgical device, and surgical systems thereof
WO2015103574A1 (en) 2014-01-06 2015-07-09 Iowa Approach Inc. Apparatus and methods for renal denervation ablation
JP6611722B2 (en) * 2014-01-06 2019-11-27 ファラパルス,インコーポレイテッド Devices and methods for delivering therapeutic electrical impulses
US10219869B2 (en) 2014-02-12 2019-03-05 Covidien Lp Surgical end effectors and pulley assemblies thereof
US9301691B2 (en) 2014-02-21 2016-04-05 Covidien Lp Instrument for optically detecting tissue attributes
EP3125785B1 (en) 2014-03-31 2020-03-04 Covidien LP Wrist and jaw assemblies for robotic surgical systems
US10164466B2 (en) 2014-04-17 2018-12-25 Covidien Lp Non-contact surgical adapter electrical interface
US10080552B2 (en) 2014-04-21 2018-09-25 Covidien Lp Adapter assembly with gimbal for interconnecting electromechanical surgical devices and surgical loading units, and surgical systems thereof
EP4238521A3 (en) 2014-05-07 2023-11-29 Farapulse, Inc. Methods and apparatus for selective tissue ablation
WO2015192027A1 (en) 2014-06-12 2015-12-17 Iowa Approach Inc. Method and apparatus for rapid and selective transurethral tissue ablation
WO2015192018A1 (en) 2014-06-12 2015-12-17 Iowa Approach Inc. Method and apparatus for rapid and selective tissue ablation with cooling
US9839425B2 (en) 2014-06-26 2017-12-12 Covidien Lp Adapter assembly for interconnecting electromechanical surgical devices and surgical loading units, and surgical systems thereof
US9763661B2 (en) 2014-06-26 2017-09-19 Covidien Lp Adapter assembly for interconnecting electromechanical surgical devices and surgical loading units, and surgical systems thereof
US10163589B2 (en) 2014-06-26 2018-12-25 Covidien Lp Adapter assemblies for interconnecting surgical loading units and handle assemblies
US10561418B2 (en) 2014-06-26 2020-02-18 Covidien Lp Adapter assemblies for interconnecting surgical loading units and handle assemblies
US9987095B2 (en) 2014-06-26 2018-06-05 Covidien Lp Adapter assemblies for interconnecting electromechanical handle assemblies and surgical loading units
US10603128B2 (en) 2014-10-07 2020-03-31 Covidien Lp Handheld electromechanical surgical system
EP3206613B1 (en) 2014-10-14 2019-07-03 Farapulse, Inc. Apparatus for rapid and safe pulmonary vein cardiac ablation
US10729443B2 (en) 2014-10-21 2020-08-04 Covidien Lp Adapter, extension, and connector assemblies for surgical devices
US10226254B2 (en) 2014-10-21 2019-03-12 Covidien Lp Adapter, extension, and connector assemblies for surgical devices
US9949737B2 (en) 2014-10-22 2018-04-24 Covidien Lp Adapter assemblies for interconnecting surgical loading units and handle assemblies
US10085750B2 (en) 2014-10-22 2018-10-02 Covidien Lp Adapter with fire rod J-hook lockout
WO2016069628A1 (en) 2014-10-27 2016-05-06 Avedro, Inc. Systems and methods for cross-linking treatments of an eye
US10114205B2 (en) 2014-11-13 2018-10-30 Avedro, Inc. Multipass virtually imaged phased array etalon
US10111665B2 (en) 2015-02-19 2018-10-30 Covidien Lp Electromechanical surgical systems
US10190888B2 (en) 2015-03-11 2019-01-29 Covidien Lp Surgical stapling instruments with linear position assembly
US11432902B2 (en) 2015-04-10 2022-09-06 Covidien Lp Surgical devices with moisture control
US10327779B2 (en) 2015-04-10 2019-06-25 Covidien Lp Adapter, extension, and connector assemblies for surgical devices
US10226239B2 (en) 2015-04-10 2019-03-12 Covidien Lp Adapter assembly with gimbal for interconnecting electromechanical surgical devices and surgical loading units, and surgical systems thereof
US11278286B2 (en) 2015-04-22 2022-03-22 Covidien Lp Handheld electromechanical surgical system
US10426468B2 (en) 2015-04-22 2019-10-01 Covidien Lp Handheld electromechanical surgical system
WO2016172695A1 (en) 2015-04-24 2016-10-27 Avedro, Inc. Systems and methods for photoactivating a photosensitizer applied to an eye
US10028657B2 (en) 2015-05-22 2018-07-24 Avedro, Inc. Systems and methods for monitoring cross-linking activity for corneal treatments
JP6933377B2 (en) 2015-07-21 2021-09-08 アヴェドロ・インコーポレーテッドAvedro,Inc. Eye treatment systems and methods using photosensitizers
US10751058B2 (en) 2015-07-28 2020-08-25 Covidien Lp Adapter assemblies for surgical devices
CA2994442C (en) 2015-09-25 2024-01-02 Covidien Lp Robotic surgical assemblies and instrument drive connectors thereof
US10371238B2 (en) 2015-10-09 2019-08-06 Covidien Lp Adapter assembly for surgical device
US10413298B2 (en) 2015-10-14 2019-09-17 Covidien Lp Adapter assembly for surgical devices
US10292705B2 (en) 2015-11-06 2019-05-21 Covidien Lp Surgical apparatus
US10939952B2 (en) 2015-11-06 2021-03-09 Covidien Lp Adapter, extension, and connector assemblies for surgical devices
US10729435B2 (en) 2015-11-06 2020-08-04 Covidien Lp Adapter assemblies for interconnecting surgical loading units and handle assemblies
US10617411B2 (en) 2015-12-01 2020-04-14 Covidien Lp Adapter assembly for surgical device
US10433841B2 (en) 2015-12-10 2019-10-08 Covidien Lp Adapter assembly for surgical device
US10420554B2 (en) 2015-12-22 2019-09-24 Covidien Lp Personalization of powered surgical devices
US10253847B2 (en) 2015-12-22 2019-04-09 Covidien Lp Electromechanical surgical devices with single motor drives and adapter assemblies therfor
US10172673B2 (en) 2016-01-05 2019-01-08 Farapulse, Inc. Systems devices, and methods for delivery of pulsed electric field ablative energy to endocardial tissue
US20170189097A1 (en) 2016-01-05 2017-07-06 Iowa Approach Inc. Systems, apparatuses and methods for delivery of ablative energy to tissue
US10130423B1 (en) 2017-07-06 2018-11-20 Farapulse, Inc. Systems, devices, and methods for focal ablation
US10660702B2 (en) 2016-01-05 2020-05-26 Farapulse, Inc. Systems, devices, and methods for focal ablation
US10314579B2 (en) 2016-01-07 2019-06-11 Covidien Lp Adapter assemblies for interconnecting surgical loading units and handle assemblies
US10524797B2 (en) 2016-01-13 2020-01-07 Covidien Lp Adapter assembly including a removable trocar assembly
US10660623B2 (en) 2016-01-15 2020-05-26 Covidien Lp Centering mechanism for articulation joint
US10508720B2 (en) 2016-01-21 2019-12-17 Covidien Lp Adapter assembly with planetary gear drive for interconnecting electromechanical surgical devices and surgical loading units, and surgical systems thereof
US10398439B2 (en) 2016-02-10 2019-09-03 Covidien Lp Adapter, extension, and connector assemblies for surgical devices
US10799239B2 (en) 2016-05-09 2020-10-13 Covidien Lp Adapter assembly with pulley system and worm gear drive for interconnecting electromechanical surgical devices and surgical end effectors
US10736637B2 (en) 2016-05-10 2020-08-11 Covidien Lp Brake for adapter assemblies for surgical devices
US10588610B2 (en) 2016-05-10 2020-03-17 Covidien Lp Adapter assemblies for surgical devices
US10702302B2 (en) 2016-05-17 2020-07-07 Covidien Lp Adapter assembly including a removable trocar assembly
US10463374B2 (en) 2016-05-17 2019-11-05 Covidien Lp Adapter assembly for a flexible circular stapler
AU2017272081B2 (en) 2016-05-26 2021-03-25 Covidien Lp Robotic surgical assemblies
WO2017218734A1 (en) 2016-06-16 2017-12-21 Iowa Approach, Inc. Systems, apparatuses, and methods for guide wire delivery
US20180333195A1 (en) * 2017-05-18 2018-11-22 Megadyne Medical Products, Inc. Hand-held instrument with body-swivel
US10653398B2 (en) 2016-08-05 2020-05-19 Covidien Lp Adapter assemblies for surgical devices
JP7049326B2 (en) 2016-10-04 2022-04-06 アヴェント インコーポレイテッド Cooled RF probe
US11116594B2 (en) 2016-11-08 2021-09-14 Covidien Lp Surgical systems including adapter assemblies for interconnecting electromechanical surgical devices and end effectors
USD843053S1 (en) * 2016-11-08 2019-03-12 Fenghua Bida Machinery Manufacture Co., Ltd. Cosmetic sprayer
KR101905830B1 (en) 2016-11-15 2018-10-08 울산과학기술원 Cryoanesthesia device, method for controlling cryoanesthesia device and temperature controller of coolant in cryoanesthesia device
US10631945B2 (en) 2017-02-28 2020-04-28 Covidien Lp Autoclavable load sensing device
US10299790B2 (en) 2017-03-03 2019-05-28 Covidien Lp Adapter with centering mechanism for articulation joint
US11272929B2 (en) 2017-03-03 2022-03-15 Covidien Lp Dynamically matching input and output shaft speeds of articulating adapter assemblies for surgical instruments
US10660641B2 (en) 2017-03-16 2020-05-26 Covidien Lp Adapter with centering mechanism for articulation joint
US11896823B2 (en) 2017-04-04 2024-02-13 Btl Healthcare Technologies A.S. Method and device for pelvic floor tissue treatment
US9987081B1 (en) 2017-04-27 2018-06-05 Iowa Approach, Inc. Systems, devices, and methods for signal generation
US10617867B2 (en) 2017-04-28 2020-04-14 Farapulse, Inc. Systems, devices, and methods for delivery of pulsed electric field ablative energy to esophageal tissue
US11324502B2 (en) 2017-05-02 2022-05-10 Covidien Lp Surgical loading unit including an articulating end effector
US10603035B2 (en) 2017-05-02 2020-03-31 Covidien Lp Surgical loading unit including an articulating end effector
US10390858B2 (en) 2017-05-02 2019-08-27 Covidien Lp Powered surgical device with speed and current derivative motor shut off
US11311295B2 (en) 2017-05-15 2022-04-26 Covidien Lp Adaptive powered stapling algorithm with calibration factor
US20180333194A1 (en) * 2017-05-16 2018-11-22 Megadyne Medical Products, Inc. Swivel instrument with flex circuit
WO2018221848A1 (en) 2017-05-30 2018-12-06 주식회사 리센스메디컬 Medical cooling device
KR20180131354A (en) 2017-05-30 2018-12-10 주식회사 리센스메디컬 Disposable cooling medium
US10772700B2 (en) 2017-08-23 2020-09-15 Covidien Lp Contactless loading unit detection
WO2019050878A2 (en) 2017-09-06 2019-03-14 Covidien Lp Boundary scaling of surgical robots
WO2019055512A1 (en) 2017-09-12 2019-03-21 Farapulse, Inc. Systems, apparatuses, and methods for ventricular focal ablation
KR102517065B1 (en) 2017-12-29 2023-04-03 주식회사 리센스메디컬 Cooling generator
WO2019136041A1 (en) 2018-01-04 2019-07-11 Covidien Lp Robotic surgical instrument including high articulation wrist assembly with torque transmission and mechanical manipulation
US11478298B2 (en) * 2018-01-24 2022-10-25 Medtronic Ardian Luxembourg S.A.R.L. Controlled irrigation for neuromodulation systems and associated methods
CN117137607A (en) 2018-02-07 2023-12-01 赛诺秀有限责任公司 Method and apparatus for controlled RF processing and RF generator system
US11160556B2 (en) 2018-04-23 2021-11-02 Covidien Lp Threaded trocar for adapter assemblies
KR102160855B1 (en) * 2018-04-27 2020-09-28 울산과학기술원 Medical cooling method and medical cooling device
PT3785682T (en) 2018-04-27 2023-03-28 Recensmedical Inc Cooling apparatus and cooling method
US11399839B2 (en) 2018-05-07 2022-08-02 Covidien Lp Surgical devices including trocar lock and trocar connection indicator
US11534172B2 (en) 2018-05-07 2022-12-27 Covidien Lp Electromechanical surgical stapler including trocar assembly release mechanism
EP3790485A1 (en) 2018-05-07 2021-03-17 Farapulse, Inc. Epicardial ablation catheter
JP7379377B2 (en) 2018-05-07 2023-11-14 ファラパルス,インコーポレイテッド Systems, devices, and methods for filtering high voltage noise induced by pulsed electric field ablation
WO2019217433A1 (en) 2018-05-07 2019-11-14 Farapulse, Inc. Systems, apparatuses and methods for delivery of ablative energy to tissue
US11896230B2 (en) 2018-05-07 2024-02-13 Covidien Lp Handheld electromechanical surgical device including load sensor having spherical ball pivots
KR102048384B1 (en) * 2018-05-23 2020-01-08 (주)클래시스 Fluid rf electrode assembly for beauty treatment of skin and handpiece for beauty treatment of skin using the same
CN112236193A (en) 2018-06-11 2021-01-15 人工智能赢美有限公司 Artificial intelligence for improved skin tightening
US20190388091A1 (en) 2018-06-21 2019-12-26 Covidien Lp Powered surgical devices including strain gauges incorporated into flex circuits
AU2019204574A1 (en) 2018-06-27 2020-01-23 Viveve, Inc. Methods for treating urinary stress incontinence
US11241233B2 (en) 2018-07-10 2022-02-08 Covidien Lp Apparatus for ensuring strain gauge accuracy in medical reusable device
CN112955099A (en) * 2018-07-27 2021-06-11 雷森斯医疗有限公司 Medical cooling device and cooling method using same
US11596496B2 (en) 2018-08-13 2023-03-07 Covidien Lp Surgical devices with moisture control
US11076858B2 (en) 2018-08-14 2021-08-03 Covidien Lp Single use electronics for surgical devices
KR102251808B1 (en) 2018-08-17 2021-05-20 박성일 Trigger type hand piece
US11666479B2 (en) 2018-08-19 2023-06-06 Recensmedical, Inc. Device for cooling anesthesia by chilled fluidic cooling medium
US11403386B2 (en) 2018-08-31 2022-08-02 Bausch Health Ireland Limited Encrypted memory device
US10687892B2 (en) 2018-09-20 2020-06-23 Farapulse, Inc. Systems, apparatuses, and methods for delivery of pulsed electric field ablative energy to endocardial tissue
US11510669B2 (en) 2020-09-29 2022-11-29 Covidien Lp Hand-held surgical instruments
US11717276B2 (en) 2018-10-30 2023-08-08 Covidien Lp Surgical devices including adapters and seals
KR20200070095A (en) * 2018-12-07 2020-06-17 울산과학기술원 Cooling device and cooling method
KR102140561B1 (en) * 2019-01-07 2020-08-03 (주)클래시스 Rf electrode assembly for beauty treatment of skin and handpiece for beauty treatment of skin using the same
US11241228B2 (en) 2019-04-05 2022-02-08 Covidien Lp Surgical instrument including an adapter assembly and an articulating surgical loading unit
US11369378B2 (en) 2019-04-18 2022-06-28 Covidien Lp Surgical instrument including an adapter assembly and an articulating surgical loading unit
USD921211S1 (en) 2019-06-21 2021-06-01 Recensmedical, Inc. Medical cooling device
USD921911S1 (en) 2019-06-21 2021-06-08 Recensmedical, Inc. Medical cooling device
US11058429B2 (en) 2019-06-24 2021-07-13 Covidien Lp Load sensing assemblies and methods of manufacturing load sensing assemblies
US11464541B2 (en) 2019-06-24 2022-10-11 Covidien Lp Retaining mechanisms for trocar assembly
US11446035B2 (en) 2019-06-24 2022-09-20 Covidien Lp Retaining mechanisms for trocar assemblies
US11426168B2 (en) 2019-07-05 2022-08-30 Covidien Lp Trocar coupling assemblies for a surgical stapler
US11123101B2 (en) 2019-07-05 2021-09-21 Covidien Lp Retaining mechanisms for trocar assemblies
USD1005484S1 (en) 2019-07-19 2023-11-21 Cynosure, Llc Handheld medical instrument and docking base
EP4027912A4 (en) 2019-09-12 2023-08-16 Relievant Medsystems, Inc. Systems and methods for tissue modulation
US10625080B1 (en) 2019-09-17 2020-04-21 Farapulse, Inc. Systems, apparatuses, and methods for detecting ectopic electrocardiogram signals during pulsed electric field ablation
US11497541B2 (en) 2019-11-20 2022-11-15 Boston Scientific Scimed, Inc. Systems, apparatuses, and methods for protecting electronic components from high power noise induced by high voltage pulses
US11065047B2 (en) 2019-11-20 2021-07-20 Farapulse, Inc. Systems, apparatuses, and methods for protecting electronic components from high power noise induced by high voltage pulses
US10842572B1 (en) 2019-11-25 2020-11-24 Farapulse, Inc. Methods, systems, and apparatuses for tracking ablation devices and generating lesion lines
US11564732B2 (en) 2019-12-05 2023-01-31 Covidien Lp Tensioning mechanism for bipolar pencil
US11737747B2 (en) 2019-12-17 2023-08-29 Covidien Lp Hand-held surgical instruments
US11583275B2 (en) 2019-12-27 2023-02-21 Covidien Lp Surgical instruments including sensor assembly
TW202139937A (en) * 2020-03-05 2021-11-01 愛爾蘭商博士健康愛爾蘭有限公司 Electrode assemblies with non-contact temperature sensing for thermal measursements
US11504117B2 (en) 2020-04-02 2022-11-22 Covidien Lp Hand-held surgical instruments
US11278341B2 (en) 2020-07-14 2022-03-22 Recensmedical, Inc. Method of safely using controlled cooling systems and devices
KR102409465B1 (en) 2020-07-28 2022-06-16 원텍 주식회사 Apparatus for delivering high frequency energy
USD968626S1 (en) 2020-08-07 2022-11-01 Recensmedical, Inc. Medical cooling device
USD977633S1 (en) 2020-08-07 2023-02-07 Recensmedical, Inc. Cradle for a medical cooling device
USD968627S1 (en) 2020-08-07 2022-11-01 Recensmedical, Inc. Medical cooling device
US11660091B2 (en) 2020-09-08 2023-05-30 Covidien Lp Surgical device with seal assembly
US11571192B2 (en) 2020-09-25 2023-02-07 Covidien Lp Adapter assembly for surgical devices
KR102375903B1 (en) * 2021-05-10 2022-03-17 텐텍 주식회사 Handpieces for skin treatment using high frequency
CN113350696B (en) * 2021-06-10 2024-01-19 上海茜茜纤美美容科技有限公司 Ion explosion hand tool and system
US11786248B2 (en) 2021-07-09 2023-10-17 Covidien Lp Surgical stapling device including a buttress retention assembly
US11819209B2 (en) 2021-08-03 2023-11-21 Covidien Lp Hand-held surgical instruments
US11862884B2 (en) 2021-08-16 2024-01-02 Covidien Lp Surgical instrument with electrical connection
KR20230128909A (en) 2022-02-28 2023-09-05 원텍 주식회사 A skin treatment device capable of automatically outputting high-frequency energy and control method

Citations (91)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3327712A (en) * 1961-09-15 1967-06-27 Ira H Kaufman Photocoagulation type fiber optical surgical device
US3658051A (en) * 1967-11-13 1972-04-25 Kenneth Sheldon Maclean Method of treating living things using high intensity pulsed magnetic field
US3800802A (en) * 1972-01-07 1974-04-02 Int Medical Electronics Ltd Short-wave therapy apparatus
US3818129A (en) * 1971-06-30 1974-06-18 Hitachi Ltd Laser imaging device
US3930504A (en) * 1973-12-12 1976-01-06 Clinitex, Inc. Portable light coagulator
US4093975A (en) * 1977-01-05 1978-06-06 Roberts Wallace A High-voltage apparatus for skin therapy
US4140130A (en) * 1977-05-31 1979-02-20 Storm Iii Frederick K Electrode structure for radio frequency localized heating of tumor bearing tissue
US4186729A (en) * 1977-11-25 1980-02-05 Donald L. Morton & Associates Deep heating electrode
US4315503A (en) * 1976-11-17 1982-02-16 Electro-Biology, Inc. Modification of the growth, repair and maintenance behavior of living tissues and cells by a specific and selective change in electrical environment
US4316474A (en) * 1979-08-17 1982-02-23 Firma Electric Electronic Service Jens Spethmann High frequency radiation therapy apparatus
US4321930A (en) * 1977-06-28 1982-03-30 Duke University, Inc. Apparatus for monitoring metabolism in body organs
US4388924A (en) * 1981-05-21 1983-06-21 Weissman Howard R Method for laser depilation
US4444190A (en) * 1980-11-24 1984-04-24 Mutzhas Maximilian F Device for the phototherapeutic treatment of hyperbilirubinemia
US4497018A (en) * 1983-05-05 1985-01-29 Candela Corporation Series inverter for capacitor charging
US4506196A (en) * 1980-11-13 1985-03-19 Candela Corporation Series inverter for capacitor charging
US4522210A (en) * 1982-04-02 1985-06-11 Philippe Simonin Method of skin treatment and device for carrying out the said method
US4564011A (en) * 1982-03-22 1986-01-14 Leon Goldman Laser optic device and method
US4589423A (en) * 1980-04-02 1986-05-20 Bsd Medical Corporation Apparatus for creating hyperthermia in tissue
US4645980A (en) * 1982-08-11 1987-02-24 Yang Tai Her Lighting system having photosensing timing switch circuit
US4647830A (en) * 1980-11-13 1987-03-03 Candela Corporation Series inverter circuit with timing responsive to reflective current
US4653495A (en) * 1984-01-13 1987-03-31 Kabushiki Kaisha Toshiba Laser medical apparatus
US4671286A (en) * 1983-03-04 1987-06-09 Compagnie Francaise d'Electronique Medicale International SA (C.O.F.R.E.M. International SA) RF therapy apparatus
US4672969A (en) * 1983-10-06 1987-06-16 Sonomo Corporation Laser healing method
US4726377A (en) * 1985-05-02 1988-02-23 Jegers Viktor J Modular control for tanning beds
US4733660A (en) * 1984-08-07 1988-03-29 Medical Laser Research And Development Corporation Laser system for providing target specific energy deposition and damage
US4798215A (en) * 1984-03-15 1989-01-17 Bsd Medical Corporation Hyperthermia apparatus
US4810658A (en) * 1984-06-13 1989-03-07 Ares-Serono Research & Development Photometric instruments, their use in methods of optical analysis, and ancillary devices therefor
US4829262A (en) * 1984-10-25 1989-05-09 Candela Laser Corporation Long pulse tunable light amplifier
US4835749A (en) * 1985-09-11 1989-05-30 Welton Truett T Safe tanning lamp control system
US4901720A (en) * 1986-04-08 1990-02-20 C. R. Bard, Inc. Power control for beam-type electrosurgical unit
US5008579A (en) * 1989-03-03 1991-04-16 E. F. Johnson Co. Light emitting polymer electrical energy source
US5011483A (en) * 1989-06-26 1991-04-30 Dennis Sleister Combined electrosurgery and laser beam delivery device
US5012816A (en) * 1989-08-31 1991-05-07 Gabor Lederer Electronic acupuncture device
US5083093A (en) * 1990-06-22 1992-01-21 Varian Associates, Inc. Circuit for coupling energy to pulse forming network or capacitor
US5085227A (en) * 1989-02-15 1992-02-04 Gerard Ramon Conductive cutaneous coating for applying electric currents for therapeutic or beauty treatment
US5097844A (en) * 1980-04-02 1992-03-24 Bsd Medical Corporation Hyperthermia apparatus having three-dimensional focusing
US5113462A (en) * 1990-06-01 1992-05-12 Candela Laser Corporation High energy fiber optica coupler
US5186181A (en) * 1990-07-27 1993-02-16 Cafiero Franconi Radio frequency thermotherapy
US5194723A (en) * 1991-12-24 1993-03-16 Maxwell Laboratories, Inc. Photoacoustic control of a pulsed light material removal process
US5281798A (en) * 1991-12-24 1994-01-25 Maxwell Laboratories, Inc. Method and system for selective removal of material coating from a substrate using a flashlamp
US5282797A (en) * 1989-05-30 1994-02-01 Cyrus Chess Method for treating cutaneous vascular lesions
US5290274A (en) * 1992-06-16 1994-03-01 Laser Medical Technology, Inc. Laser apparatus for medical and dental treatments
US5290273A (en) * 1991-08-12 1994-03-01 Tan Oon T Laser treatment method for removing pigement containing lesions from the skin of a living human
US5312395A (en) * 1990-03-14 1994-05-17 Boston University Method of treating pigmented lesions using pulsed irradiation
US5383874A (en) * 1991-11-08 1995-01-24 Ep Technologies, Inc. Systems for identifying catheters and monitoring their use
US5396887A (en) * 1993-09-23 1995-03-14 Cardiac Pathways Corporation Apparatus and method for detecting contact pressure
US5400791A (en) * 1991-10-11 1995-03-28 Candela Laser Corporation Infrared fundus video angiography system
US5401272A (en) * 1992-09-25 1995-03-28 Envision Surgical Systems, Inc. Multimodality probe with extendable bipolar electrodes
US5405368A (en) * 1992-10-20 1995-04-11 Esc Inc. Method and apparatus for therapeutic electromagnetic treatment
US5484432A (en) * 1985-09-27 1996-01-16 Laser Biotech, Inc. Collagen treatment apparatus
US5489279A (en) * 1994-03-21 1996-02-06 Dusa Pharmaceuticals, Inc. Method of applying photodynamic therapy to dermal lesion
US5507790A (en) * 1994-03-21 1996-04-16 Weiss; William V. Method of non-invasive reduction of human site-specific subcutaneous fat tissue deposits by accelerated lipolysis metabolism
US5509916A (en) * 1994-08-12 1996-04-23 Valleylab Inc. Laser-assisted electrosurgery system
US5514130A (en) * 1994-10-11 1996-05-07 Dorsal Med International RF apparatus for controlled depth ablation of soft tissue
US5595568A (en) * 1995-02-01 1997-01-21 The General Hospital Corporation Permanent hair removal using optical pulses
US5620478A (en) * 1992-10-20 1997-04-15 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5626631A (en) * 1992-10-20 1997-05-06 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5707403A (en) * 1993-02-24 1998-01-13 Star Medical Technologies, Inc. Method for the laser treatment of subsurface blood vessels
US5720772A (en) * 1992-10-20 1998-02-24 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5723803A (en) * 1993-09-30 1998-03-03 Yamaha Corporation Automatic performance apparatus
US5725565A (en) * 1995-12-04 1998-03-10 Smith; Daniel E. Tanning bed safety device
US5728141A (en) * 1994-05-04 1998-03-17 Indiba, S.A. Electrotherapy apparatus
US5735844A (en) * 1995-02-01 1998-04-07 The General Hospital Corporation Hair removal using optical pulses
US5755753A (en) * 1995-05-05 1998-05-26 Thermage, Inc. Method for controlled contraction of collagen tissue
US5885273A (en) * 1995-03-29 1999-03-23 Esc Medical Systems, Ltd. Method for depilation using pulsed electromagnetic radiation
US6009876A (en) * 1997-05-20 2000-01-04 Yavitz; Edward Q. Method for modifying and reshaping collagen beneath the surface of skin
US6014579A (en) * 1997-07-21 2000-01-11 Cardiac Pathways Corp. Endocardial mapping catheter with movable electrode
USRE36634E (en) * 1991-12-12 2000-03-28 Ghaffari; Shahriar Optical system for treatment of vascular lesions
US6047215A (en) * 1998-03-06 2000-04-04 Sonique Surgical Systems, Inc. Method and apparatus for electromagnetically assisted liposuction
US6053909A (en) * 1998-03-27 2000-04-25 Shadduck; John H. Ionothermal delivery system and technique for medical procedures
US6053910A (en) * 1996-10-30 2000-04-25 Megadyne Medical Products, Inc. Capacitive reusable electrosurgical return electrode
US6171332B1 (en) * 1992-10-23 2001-01-09 Photo Therapeutics Limited Light source
US6214034B1 (en) * 1996-09-04 2001-04-10 Radiancy, Inc. Method of selective photothermolysis
US6350276B1 (en) * 1996-01-05 2002-02-26 Thermage, Inc. Tissue remodeling apparatus containing cooling fluid
US6377855B1 (en) * 1995-05-05 2002-04-23 Thermage, Inc. Method and apparatus for controlled contraction of collagen tissue
US6387380B1 (en) * 1995-05-05 2002-05-14 Thermage, Inc. Apparatus for controlled contraction of collagen tissue
US6514243B1 (en) * 1992-10-20 2003-02-04 Lumenis Ltd. Method and apparatus for electromagnetic treatment of the skin, including hair depilation
US6533781B2 (en) * 1997-12-23 2003-03-18 Team Medical Llc Electrosurgical instrument
US6544258B2 (en) * 1996-10-30 2003-04-08 Mega-Dyne Medical Products, Inc. Pressure sore pad having self-limiting electrosurgical return electrode properties and optional heating/cooling capabilities
US6567262B2 (en) * 2001-06-01 2003-05-20 Active Cool Ltd. Liquid cooled TEC based system and method for cooling heat sensitive elements
US20040002704A1 (en) * 1996-01-05 2004-01-01 Knowlton Edward W. Treatment apparatus with electromagnetic energy delivery device and non-volatile memory
US20040000316A1 (en) * 1996-01-05 2004-01-01 Knowlton Edward W. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US20040002705A1 (en) * 1996-01-05 2004-01-01 Knowlton Edward W. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US6684107B1 (en) * 2001-08-01 2004-01-27 Voyager Medical Corporation Wrinkle-reducing system
US6690976B2 (en) * 2000-04-13 2004-02-10 Celsion Corporation Thermotherapy method for treatment and prevention of breast cancer and cancer in other organs
US20040030332A1 (en) * 1996-01-05 2004-02-12 Knowlton Edward W. Handpiece with electrode and non-volatile memory
US20040034346A1 (en) * 1996-01-05 2004-02-19 Stern Roger A. RF device with thermo-electric cooler
US6702808B1 (en) * 2000-09-28 2004-03-09 Syneron Medical Ltd. Device and method for treating skin
US6981970B2 (en) * 2002-12-16 2006-01-03 Msq (M2) Ltd. Device and method for treating skin
US6997923B2 (en) * 2000-12-28 2006-02-14 Palomar Medical Technologies, Inc. Method and apparatus for EMR treatment
US7022121B2 (en) * 1999-03-09 2006-04-04 Thermage, Inc. Handpiece for treatment of tissue

Family Cites Families (149)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3831604A (en) 1973-04-18 1974-08-27 C Neefe Method of reshaping the cornea
US4074718A (en) 1976-03-17 1978-02-21 Valleylab, Inc. Electrosurgical instrument
US4164226A (en) 1976-08-25 1979-08-14 Robert Tapper Iontophoretic burn-protection electrode structure
USRE32849E (en) 1978-04-13 1989-01-31 Litton Systems, Inc. Method for fabricating multi-layer optical films
US4346715A (en) 1978-07-12 1982-08-31 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Hyperthermia heating apparatus
CA1105565A (en) * 1978-09-12 1981-07-21 Kaufman (John G.) Hospital Products Ltd. Electrosurgical electrode
US4341227A (en) 1979-01-11 1982-07-27 Bsd Corporation System for irradiating living tissue or simulations thereof
US4585237A (en) 1979-01-15 1986-04-29 Hastings Manufacturing Company Piston and oil control ring therefor
US4290435A (en) 1979-09-07 1981-09-22 Thermatime A.G. Internally cooled electrode for hyperthermal treatment and method of use
US4343301A (en) 1979-10-04 1982-08-10 Robert Indech Subcutaneous neural stimulation or local tissue destruction
US4375220A (en) 1980-05-09 1983-03-01 Matvias Fredrick M Microwave applicator with cooling mechanism for intracavitary treatment of cancer
US4381007A (en) 1981-04-30 1983-04-26 The United States Of America As Represented By The United States Department Of Energy Multipolar corneal-shaping electrode with flexible removable skirt
US4441486A (en) 1981-10-27 1984-04-10 Board Of Trustees Of Leland Stanford Jr. University Hyperthermia system
US4756310A (en) 1982-05-28 1988-07-12 Hemodynamics Technology, Inc. System for cooling an area of the surface of an object
JPS599626A (en) * 1982-07-08 1984-01-19 Ricoh Co Ltd Optical deflector
CA1244889A (en) 1983-01-24 1988-11-15 Kureha Chemical Ind Co Ltd Device for hyperthermia
US4545368A (en) 1983-04-13 1985-10-08 Rand Robert W Induction heating method for use in causing necrosis of neoplasm
US4646737A (en) 1983-06-13 1987-03-03 Laserscope, Inc. Localized heat applying medical device
JPS6055966A (en) 1983-09-05 1985-04-01 オリンパス光学工業株式会社 Medical electrode apparatus
US4556070A (en) 1983-10-31 1985-12-03 Varian Associates, Inc. Hyperthermia applicator for treatment with microwave energy and ultrasonic wave energy
JPS6137260A (en) 1984-07-31 1986-02-22 菊地 真 Heating apparatus for hyperthermia
US4754754A (en) 1984-08-20 1988-07-05 Garito Jon C Electrosurgical handpiece for blades and needles
US4655215A (en) * 1985-03-15 1987-04-07 Harold Pike Hand control for electrosurgical electrodes
IT206759Z2 (en) 1985-07-08 1987-10-01 Indiba Sa ELECTRONIC DEVICE FOR COSMETIC MEDICAL THERAPY.
US5137530A (en) 1985-09-27 1992-08-11 Sand Bruce J Collagen treatment apparatus
US4976709A (en) 1988-12-15 1990-12-11 Sand Bruce J Method for collagen treatment
US5304169A (en) 1985-09-27 1994-04-19 Laser Biotech, Inc. Method for collagen shrinkage
GB8529446D0 (en) 1985-11-29 1986-01-08 Univ Aberdeen Divergent ultrasound arrays
US4891820A (en) 1985-12-19 1990-01-02 Rofin-Sinar, Inc. Fast axial flow laser circulating system
US4709372A (en) 1985-12-19 1987-11-24 Spectra-Physics, Inc. Fast axial flow laser circulating system
US4709701A (en) 1986-04-15 1987-12-01 Medical Research & Development Associates Apparatus for medical treatment by hyperthermia
JPS62280781A (en) * 1986-05-30 1987-12-05 Mita Ind Co Ltd Developing device for image forming machine
US4962761A (en) 1987-02-24 1990-10-16 Golden Theodore A Thermal bandage
US5003991A (en) 1987-03-31 1991-04-02 Olympus Optical Co., Ltd. Hyperthermia apparatus
JPS6456060A (en) 1987-08-27 1989-03-02 Hayashibara Takeshi Low frequency medical treatment device
JPH0669429B2 (en) * 1987-12-16 1994-09-07 リンナイ株式会社 Bath
US4957480A (en) 1988-02-02 1990-09-18 Universal Health Products, Inc. Method of facial toning
US5143063A (en) 1988-02-09 1992-09-01 Fellner Donald G Method of removing adipose tissue from the body
US4864098A (en) 1988-05-19 1989-09-05 Rofin-Sinar, Inc. High powered beam dump
US4881543A (en) 1988-06-28 1989-11-21 Massachusetts Institute Of Technology Combined microwave heating and surface cooling of the cornea
US6066130A (en) * 1988-10-24 2000-05-23 The General Hospital Corporation Delivering laser energy
US5486172A (en) 1989-05-30 1996-01-23 Chess; Cyrus Apparatus for treating cutaneous vascular lesions
US5041110A (en) * 1989-07-10 1991-08-20 Beacon Laboratories, Inc. Cart for mobilizing and interfacing use of an electrosurgical generator and inert gas supply
US5364394A (en) 1989-12-21 1994-11-15 Mehl Thomas L Method of removing hair from the body and inhibiting future growth
US5131904A (en) 1990-05-04 1992-07-21 Richard Markoll Treatment of arthritis with magnetic field therapy and apparatus therefor
US5100402A (en) 1990-10-05 1992-03-31 Megadyne Medical Products, Inc. Electrosurgical laparoscopic cauterization electrode
US5304171A (en) 1990-10-18 1994-04-19 Gregory Kenton W Catheter devices and methods for delivering
US5300097A (en) 1991-02-13 1994-04-05 Lerner Ethan A Fiber optic psoriasis treatment device
US5190031A (en) 1991-03-11 1993-03-02 Raul Guibert Universal thermotherapy applicator
US5107832A (en) 1991-03-11 1992-04-28 Raul Guibert Universal thermotherapy applicator
US5136676A (en) 1991-05-01 1992-08-04 Coherent, Inc. Coupler for a laser delivery system
US5190517A (en) 1991-06-06 1993-03-02 Valleylab Inc. Electrosurgical and ultrasonic surgical system
US5234428A (en) * 1991-06-11 1993-08-10 Kaufman David I Disposable electrocautery/cutting instrument with integral continuous smoke evacuation
US5249192A (en) 1991-06-27 1993-09-28 Laserscope Multiple frequency medical laser
FR2680965B1 (en) 1991-09-05 1993-11-12 Gabriel Bernaz APPARATUS AND METHOD FOR TREATING SKIN.
US5370642A (en) 1991-09-25 1994-12-06 Keller; Gregory S. Method of laser cosmetic surgery
US5249575A (en) 1991-10-21 1993-10-05 Adm Tronics Unlimited, Inc. Corona discharge beam thermotherapy system
US6210402B1 (en) * 1995-11-22 2001-04-03 Arthrocare Corporation Methods for electrosurgical dermatological treatment
US5366443A (en) 1992-01-07 1994-11-22 Thapliyal And Eggers Partners Method and apparatus for advancing catheters through occluded body lumens
US5230334A (en) 1992-01-22 1993-07-27 Summit Technology, Inc. Method and apparatus for generating localized hyperthermia
AU3927993A (en) 1992-03-20 1993-10-21 General Hospital Corporation, The Laser illuminator
US5423807A (en) 1992-04-16 1995-06-13 Implemed, Inc. Cryogenic mapping and ablation catheter
US5562720A (en) 1992-05-01 1996-10-08 Vesta Medical, Inc. Bipolar/monopolar endometrial ablation device and method
US5496314A (en) 1992-05-01 1996-03-05 Hemostatic Surgery Corporation Irrigation and shroud arrangement for electrically powered endoscopic probes
WO1994002077A2 (en) 1992-07-15 1994-02-03 Angelase, Inc. Ablation catheter system
US5556377A (en) 1992-08-12 1996-09-17 Vidamed, Inc. Medical probe apparatus with laser and/or microwave monolithic integrated circuit probe
EP0588249B1 (en) * 1992-09-18 1995-11-22 BASF Aktiengesellschaft Process for the preparation of N-hydroxy-N'-diazeniumoxides
US5334193A (en) 1992-11-13 1994-08-02 American Cardiac Ablation Co., Inc. Fluid cooled ablation catheter
US5342357A (en) 1992-11-13 1994-08-30 American Cardiac Ablation Co., Inc. Fluid cooled electrosurgical cauterization system
US5348554A (en) 1992-12-01 1994-09-20 Cardiac Pathways Corporation Catheter for RF ablation with cooled electrode
US5360447A (en) 1993-02-03 1994-11-01 Coherent, Inc. Laser assisted hair transplant method
US5527350A (en) 1993-02-24 1996-06-18 Star Medical Technologies, Inc. Pulsed infrared laser treatment of psoriasis
US5476495A (en) * 1993-03-16 1995-12-19 Ep Technologies, Inc. Cardiac mapping and ablation systems
US5395363A (en) * 1993-06-29 1995-03-07 Utah Medical Products Diathermy coagulation and ablation apparatus and method
US5397327A (en) 1993-07-27 1995-03-14 Coherent, Inc. Surgical laser handpiece for slit incisions
US5496312A (en) 1993-10-07 1996-03-05 Valleylab Inc. Impedance and temperature generator control
US5628744A (en) 1993-12-21 1997-05-13 Laserscope Treatment beam handpiece
US5462521A (en) 1993-12-21 1995-10-31 Angeion Corporation Fluid cooled and perfused tip for a catheter
US5571216A (en) 1994-01-19 1996-11-05 The General Hospital Corporation Methods and apparatus for joining collagen-containing materials
US5556612A (en) 1994-03-15 1996-09-17 The General Hospital Corporation Methods for phototherapeutic treatment of proliferative skin diseases
JP3263275B2 (en) * 1994-04-05 2002-03-04 ザ リージェンツ オブ ザ ユニバーシティ オブ カリフォルニア Apparatus for laser treatment of living tissue and laser treatment apparatus for flame-like nevus
US5456260A (en) 1994-04-05 1995-10-10 The General Hospital Corporation Fluorescence detection of cell proliferation
US5464436A (en) 1994-04-28 1995-11-07 Lasermedics, Inc. Method of performing laser therapy
US5458596A (en) 1994-05-06 1995-10-17 Dorsal Orthopedic Corporation Method and apparatus for controlled contraction of soft tissue
US5730719A (en) * 1994-05-09 1998-03-24 Somnus Medical Technologies, Inc. Method and apparatus for cosmetically remodeling a body structure
US5531739A (en) 1994-09-23 1996-07-02 Coherent, Inc. Method of treating veins
US5522813A (en) 1994-09-23 1996-06-04 Coherent, Inc. Method of treating veins
US5746735A (en) * 1994-10-26 1998-05-05 Cynosure, Inc. Ultra long pulsed dye laser device for treatment of ectatic vessels and method therefor
CA2206039A1 (en) * 1994-12-09 1996-06-13 Cynosure Inc. Near-infrared selective photothermolysis for vascular targets
US5558667A (en) * 1994-12-14 1996-09-24 Coherent, Inc. Method and apparatus for treating vascular lesions
US5880880A (en) * 1995-01-13 1999-03-09 The General Hospital Corp. Three-dimensional scanning confocal laser microscope
US5599342A (en) 1995-01-27 1997-02-04 Candela Laser Corporation Method for treating pigmentation abnormalities using pulsed laser radiation with an elongated cross-section and apparatus for providing same
US5630426A (en) 1995-03-03 1997-05-20 Neovision Corporation Apparatus and method for characterization and treatment of tumors
US5554172A (en) * 1995-05-09 1996-09-10 The Larren Corporation Directed energy surgical method and assembly
WO1996037155A1 (en) * 1995-05-22 1996-11-28 Silicon Microdevices, Inc. Micromechanical device and method for enhancing delivery of compounds through the skin
US5624435A (en) * 1995-06-05 1997-04-29 Cynosure, Inc. Ultra-long flashlamp-excited pulse dye laser for therapy and method therefor
US5879376A (en) * 1995-07-12 1999-03-09 Luxar Corporation Method and apparatus for dermatology treatment
US5964749A (en) * 1995-09-15 1999-10-12 Esc Medical Systems Ltd. Method and apparatus for skin rejuvenation and wrinkle smoothing
US6228078B1 (en) * 1995-11-22 2001-05-08 Arthrocare Corporation Methods for electrosurgical dermatological treatment
US5837001A (en) * 1995-12-08 1998-11-17 C. R. Bard Radio frequency energy delivery system for multipolar electrode catheters
US5879346A (en) * 1995-12-18 1999-03-09 Esc Medical Systems, Ltd. Hair removal by selective photothermolysis with an alexandrite laser
US7229436B2 (en) 1996-01-05 2007-06-12 Thermage, Inc. Method and kit for treatment of tissue
US7189230B2 (en) 1996-01-05 2007-03-13 Thermage, Inc. Method for treating skin and underlying tissue
DE69732362T2 (en) * 1996-02-15 2006-03-23 Biosense Webster, Inc., Diamond Bar Method for calibrating a probe
US5609573A (en) 1996-02-28 1997-03-11 Conmed Corporation Electrosurgical suction/irrigation instrument
CN1220591A (en) * 1996-04-09 1999-06-23 希诺索尔公司 Alexandrite laser system for treatment of dermatological specimens
US5871479A (en) * 1996-11-07 1999-02-16 Cynosure, Inc. Alexandrite laser system for hair removal and method therefor
US5743901A (en) * 1996-05-15 1998-04-28 Star Medical Technologies, Inc. High fluence diode laser device and method for the fabrication and use thereof
US5976123A (en) * 1996-07-30 1999-11-02 Laser Aesthetics, Inc. Heart stabilization
US6228075B1 (en) * 1996-11-07 2001-05-08 Cynosure, Inc. Alexandrite laser system for hair removal
US7204832B2 (en) * 1996-12-02 2007-04-17 Pálomar Medical Technologies, Inc. Cooling system for a photo cosmetic device
US6015404A (en) * 1996-12-02 2000-01-18 Palomar Medical Technologies, Inc. Laser dermatology with feedback control
US6162211A (en) * 1996-12-05 2000-12-19 Thermolase Corporation Skin enhancement using laser light
US5906609A (en) * 1997-02-05 1999-05-25 Sahar Technologies Method for delivering energy within continuous outline
EP0991372B1 (en) * 1997-05-15 2004-08-04 Palomar Medical Technologies, Inc. Apparatus for dermatology treatment
US5885274A (en) * 1997-06-24 1999-03-23 New Star Lasers, Inc. Filament lamp for dermatological treatment
GB9900964D0 (en) * 1999-01-15 1999-03-10 Gyrus Medical Ltd An electrosurgical system
US6168590B1 (en) * 1997-08-12 2001-01-02 Y-Beam Technologies, Inc. Method for permanent hair removal
WO1999008614A1 (en) * 1997-08-13 1999-02-25 Surx, Inc. Noninvasive devices, methods, and systems for shrinking of tissues
US6007532A (en) * 1997-08-29 1999-12-28 3M Innovative Properties Company Method and apparatus for detecting loss of contact of biomedical electrodes with patient skin
IL122840A (en) * 1997-12-31 2002-04-21 Radiancy Inc Apparatus and methods for removing hair
CA2323479A1 (en) * 1998-03-12 1999-09-16 Palomar Medical Technologies, Inc. System for electromagnetic radiation of the skin
ES2640937T3 (en) * 1998-03-27 2017-11-07 The General Hospital Corporation Procedure for selective targeting of sebaceous glands
US6139543A (en) * 1998-07-22 2000-10-31 Endovasix, Inc. Flow apparatus for the disruption of occlusions
US6212433B1 (en) * 1998-07-28 2001-04-03 Radiotherapeutics Corporation Method for treating tumors near the surface of an organ
US6139569A (en) 1998-07-31 2000-10-31 Surx, Inc. Interspersed heating/cooling to shrink tissues for incontinence
US6126655A (en) * 1998-08-11 2000-10-03 The General Hospital Corporation Apparatus and method for selective laser-induced heating of biological tissue
US6936044B2 (en) * 1998-11-30 2005-08-30 Light Bioscience, Llc Method and apparatus for the stimulation of hair growth
US6183773B1 (en) * 1999-01-04 2001-02-06 The General Hospital Corporation Targeting of sebaceous follicles as a treatment of sebaceous gland disorders
US6200308B1 (en) * 1999-01-29 2001-03-13 Candela Corporation Dynamic cooling of tissue for radiation treatment
ES2240078T3 (en) * 1999-03-09 2005-10-16 Thermage, Inc. APPARATUS FOR TREATMENT OF FABRICS.
US20020156471A1 (en) * 1999-03-09 2002-10-24 Stern Roger A. Method for treatment of tissue
US6383176B1 (en) * 1999-03-15 2002-05-07 Altus Medical, Inc. Hair removal device and method
US6569155B1 (en) * 1999-03-15 2003-05-27 Altus Medical, Inc. Radiation delivery module and dermal tissue treatment method
US6533775B1 (en) * 1999-05-05 2003-03-18 Ioana M. Rizoiu Light-activated hair treatment and removal device
US6235024B1 (en) * 1999-06-21 2001-05-22 Hosheng Tu Catheters system having dual ablation capability
US6451007B1 (en) * 1999-07-29 2002-09-17 Dale E. Koop Thermal quenching of tissue
US20020016601A1 (en) * 2000-01-03 2002-02-07 Shadduck John H. Instruments and techniques for inducing neocollagenesis in skin treatments
US6706032B2 (en) * 2000-06-08 2004-03-16 Massachusetts Institute Of Technology Localized molecular and ionic transport to and from tissues
US6702838B1 (en) * 2000-09-18 2004-03-09 Lumenis Inc. Method of treating hypotrophic scars enlarged pores
US6529543B1 (en) * 2000-11-21 2003-03-04 The General Hospital Corporation Apparatus for controlling laser penetration depth
US7217266B2 (en) * 2001-05-30 2007-05-15 Anderson R Rox Apparatus and method for laser treatment with spectroscopic feedback
WO2003003903A2 (en) * 2001-07-02 2003-01-16 Palomar Medical Technologies, Inc. Laser device for medical/cosmetic procedures
US6939344B2 (en) * 2001-08-02 2005-09-06 Syneron Medical Ltd. Method for controlling skin temperature during thermal treatment
US7094252B2 (en) * 2001-08-21 2006-08-22 Cooltouch Incorporated Enhanced noninvasive collagen remodeling
US6685927B2 (en) * 2001-09-27 2004-02-03 Ceramoptec Industries, Inc. Topical application of chromophores for hair removal
US7044959B2 (en) * 2002-03-12 2006-05-16 Palomar Medical Technologies, Inc. Method and apparatus for hair growth management
US7322972B2 (en) * 2002-04-10 2008-01-29 The Regents Of The University Of California In vivo port wine stain, burn and melanin depth determination using a photoacoustic probe
DE102009048801B4 (en) 2009-10-08 2022-06-23 Andreas Stihl Ag & Co. Kg Spark plug connector and arrangement of a spark plug and a spark plug connector

Patent Citations (99)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3327712A (en) * 1961-09-15 1967-06-27 Ira H Kaufman Photocoagulation type fiber optical surgical device
US3658051A (en) * 1967-11-13 1972-04-25 Kenneth Sheldon Maclean Method of treating living things using high intensity pulsed magnetic field
US3818129A (en) * 1971-06-30 1974-06-18 Hitachi Ltd Laser imaging device
US3800802A (en) * 1972-01-07 1974-04-02 Int Medical Electronics Ltd Short-wave therapy apparatus
US3930504A (en) * 1973-12-12 1976-01-06 Clinitex, Inc. Portable light coagulator
US4315503A (en) * 1976-11-17 1982-02-16 Electro-Biology, Inc. Modification of the growth, repair and maintenance behavior of living tissues and cells by a specific and selective change in electrical environment
US4093975A (en) * 1977-01-05 1978-06-06 Roberts Wallace A High-voltage apparatus for skin therapy
US4140130A (en) * 1977-05-31 1979-02-20 Storm Iii Frederick K Electrode structure for radio frequency localized heating of tumor bearing tissue
US4321930A (en) * 1977-06-28 1982-03-30 Duke University, Inc. Apparatus for monitoring metabolism in body organs
US4380240A (en) * 1977-06-28 1983-04-19 Duke University, Inc. Apparatus for monitoring metabolism in body organs
US4186729A (en) * 1977-11-25 1980-02-05 Donald L. Morton & Associates Deep heating electrode
US4316474A (en) * 1979-08-17 1982-02-23 Firma Electric Electronic Service Jens Spethmann High frequency radiation therapy apparatus
US5097844A (en) * 1980-04-02 1992-03-24 Bsd Medical Corporation Hyperthermia apparatus having three-dimensional focusing
US4589423A (en) * 1980-04-02 1986-05-20 Bsd Medical Corporation Apparatus for creating hyperthermia in tissue
US4506196A (en) * 1980-11-13 1985-03-19 Candela Corporation Series inverter for capacitor charging
US4647830A (en) * 1980-11-13 1987-03-03 Candela Corporation Series inverter circuit with timing responsive to reflective current
US4444190A (en) * 1980-11-24 1984-04-24 Mutzhas Maximilian F Device for the phototherapeutic treatment of hyperbilirubinemia
US4388924A (en) * 1981-05-21 1983-06-21 Weissman Howard R Method for laser depilation
US4564011A (en) * 1982-03-22 1986-01-14 Leon Goldman Laser optic device and method
US4522210A (en) * 1982-04-02 1985-06-11 Philippe Simonin Method of skin treatment and device for carrying out the said method
US4645980A (en) * 1982-08-11 1987-02-24 Yang Tai Her Lighting system having photosensing timing switch circuit
US4671286A (en) * 1983-03-04 1987-06-09 Compagnie Francaise d'Electronique Medicale International SA (C.O.F.R.E.M. International SA) RF therapy apparatus
US4497018A (en) * 1983-05-05 1985-01-29 Candela Corporation Series inverter for capacitor charging
US4672969A (en) * 1983-10-06 1987-06-16 Sonomo Corporation Laser healing method
US4653495A (en) * 1984-01-13 1987-03-31 Kabushiki Kaisha Toshiba Laser medical apparatus
US4798215A (en) * 1984-03-15 1989-01-17 Bsd Medical Corporation Hyperthermia apparatus
US4810658A (en) * 1984-06-13 1989-03-07 Ares-Serono Research & Development Photometric instruments, their use in methods of optical analysis, and ancillary devices therefor
US4733660A (en) * 1984-08-07 1988-03-29 Medical Laser Research And Development Corporation Laser system for providing target specific energy deposition and damage
US4829262A (en) * 1984-10-25 1989-05-09 Candela Laser Corporation Long pulse tunable light amplifier
US4726377A (en) * 1985-05-02 1988-02-23 Jegers Viktor J Modular control for tanning beds
US4729375A (en) * 1985-05-02 1988-03-08 Sun Time, Inc. Modular control for tanning beds
US4835749A (en) * 1985-09-11 1989-05-30 Welton Truett T Safe tanning lamp control system
US5618284A (en) * 1985-09-27 1997-04-08 Sunrise Technologies Collagen treatment apparatus
US5484432A (en) * 1985-09-27 1996-01-16 Laser Biotech, Inc. Collagen treatment apparatus
US4901720A (en) * 1986-04-08 1990-02-20 C. R. Bard, Inc. Power control for beam-type electrosurgical unit
US5085227A (en) * 1989-02-15 1992-02-04 Gerard Ramon Conductive cutaneous coating for applying electric currents for therapeutic or beauty treatment
US5008579A (en) * 1989-03-03 1991-04-16 E. F. Johnson Co. Light emitting polymer electrical energy source
US5282797A (en) * 1989-05-30 1994-02-01 Cyrus Chess Method for treating cutaneous vascular lesions
US5011483A (en) * 1989-06-26 1991-04-30 Dennis Sleister Combined electrosurgery and laser beam delivery device
US5012816A (en) * 1989-08-31 1991-05-07 Gabor Lederer Electronic acupuncture device
US5312395A (en) * 1990-03-14 1994-05-17 Boston University Method of treating pigmented lesions using pulsed irradiation
US5113462A (en) * 1990-06-01 1992-05-12 Candela Laser Corporation High energy fiber optica coupler
US5083093A (en) * 1990-06-22 1992-01-21 Varian Associates, Inc. Circuit for coupling energy to pulse forming network or capacitor
US5186181A (en) * 1990-07-27 1993-02-16 Cafiero Franconi Radio frequency thermotherapy
US5290273A (en) * 1991-08-12 1994-03-01 Tan Oon T Laser treatment method for removing pigement containing lesions from the skin of a living human
US5400791A (en) * 1991-10-11 1995-03-28 Candela Laser Corporation Infrared fundus video angiography system
US5383874A (en) * 1991-11-08 1995-01-24 Ep Technologies, Inc. Systems for identifying catheters and monitoring their use
USRE36634E (en) * 1991-12-12 2000-03-28 Ghaffari; Shahriar Optical system for treatment of vascular lesions
US5281798A (en) * 1991-12-24 1994-01-25 Maxwell Laboratories, Inc. Method and system for selective removal of material coating from a substrate using a flashlamp
US5194723A (en) * 1991-12-24 1993-03-16 Maxwell Laboratories, Inc. Photoacoustic control of a pulsed light material removal process
US5290274A (en) * 1992-06-16 1994-03-01 Laser Medical Technology, Inc. Laser apparatus for medical and dental treatments
US5401272A (en) * 1992-09-25 1995-03-28 Envision Surgical Systems, Inc. Multimodality probe with extendable bipolar electrodes
US5720772A (en) * 1992-10-20 1998-02-24 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US6514243B1 (en) * 1992-10-20 2003-02-04 Lumenis Ltd. Method and apparatus for electromagnetic treatment of the skin, including hair depilation
US6174325B1 (en) * 1992-10-20 2001-01-16 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5755751A (en) * 1992-10-20 1998-05-26 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5405368A (en) * 1992-10-20 1995-04-11 Esc Inc. Method and apparatus for therapeutic electromagnetic treatment
US5620478A (en) * 1992-10-20 1997-04-15 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US5626631A (en) * 1992-10-20 1997-05-06 Esc Medical Systems Ltd. Method and apparatus for therapeutic electromagnetic treatment
US6171332B1 (en) * 1992-10-23 2001-01-09 Photo Therapeutics Limited Light source
US5707403A (en) * 1993-02-24 1998-01-13 Star Medical Technologies, Inc. Method for the laser treatment of subsurface blood vessels
US5396887A (en) * 1993-09-23 1995-03-14 Cardiac Pathways Corporation Apparatus and method for detecting contact pressure
US5723803A (en) * 1993-09-30 1998-03-03 Yamaha Corporation Automatic performance apparatus
US5507790A (en) * 1994-03-21 1996-04-16 Weiss; William V. Method of non-invasive reduction of human site-specific subcutaneous fat tissue deposits by accelerated lipolysis metabolism
US5489279A (en) * 1994-03-21 1996-02-06 Dusa Pharmaceuticals, Inc. Method of applying photodynamic therapy to dermal lesion
US5728141A (en) * 1994-05-04 1998-03-17 Indiba, S.A. Electrotherapy apparatus
US5509916A (en) * 1994-08-12 1996-04-23 Valleylab Inc. Laser-assisted electrosurgery system
US5514130A (en) * 1994-10-11 1996-05-07 Dorsal Med International RF apparatus for controlled depth ablation of soft tissue
US5735844A (en) * 1995-02-01 1998-04-07 The General Hospital Corporation Hair removal using optical pulses
US5595568A (en) * 1995-02-01 1997-01-21 The General Hospital Corporation Permanent hair removal using optical pulses
US5885273A (en) * 1995-03-29 1999-03-23 Esc Medical Systems, Ltd. Method for depilation using pulsed electromagnetic radiation
US6377855B1 (en) * 1995-05-05 2002-04-23 Thermage, Inc. Method and apparatus for controlled contraction of collagen tissue
US6377854B1 (en) * 1995-05-05 2002-04-23 Thermage, Inc. Method for controlled contraction of collagen in fibrous septae in subcutaneous fat layers
US6387380B1 (en) * 1995-05-05 2002-05-14 Thermage, Inc. Apparatus for controlled contraction of collagen tissue
US6381497B1 (en) * 1995-05-05 2002-04-30 Thermage, Inc. Method for smoothing contour irregularity of skin surface by controlled contraction of collagen tissue
US5755753A (en) * 1995-05-05 1998-05-26 Thermage, Inc. Method for controlled contraction of collagen tissue
US6381498B1 (en) * 1995-05-05 2002-04-30 Thermage, Inc. Method and apparatus for controlled contraction of collagen tissue
US5725565A (en) * 1995-12-04 1998-03-10 Smith; Daniel E. Tanning bed safety device
US20040034346A1 (en) * 1996-01-05 2004-02-19 Stern Roger A. RF device with thermo-electric cooler
US20040002704A1 (en) * 1996-01-05 2004-01-01 Knowlton Edward W. Treatment apparatus with electromagnetic energy delivery device and non-volatile memory
US6350276B1 (en) * 1996-01-05 2002-02-26 Thermage, Inc. Tissue remodeling apparatus containing cooling fluid
US20040002705A1 (en) * 1996-01-05 2004-01-01 Knowlton Edward W. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US20040030332A1 (en) * 1996-01-05 2004-02-12 Knowlton Edward W. Handpiece with electrode and non-volatile memory
US20040000316A1 (en) * 1996-01-05 2004-01-01 Knowlton Edward W. Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US6214034B1 (en) * 1996-09-04 2001-04-10 Radiancy, Inc. Method of selective photothermolysis
US6053910A (en) * 1996-10-30 2000-04-25 Megadyne Medical Products, Inc. Capacitive reusable electrosurgical return electrode
US6544258B2 (en) * 1996-10-30 2003-04-08 Mega-Dyne Medical Products, Inc. Pressure sore pad having self-limiting electrosurgical return electrode properties and optional heating/cooling capabilities
US6009876A (en) * 1997-05-20 2000-01-04 Yavitz; Edward Q. Method for modifying and reshaping collagen beneath the surface of skin
US6014579A (en) * 1997-07-21 2000-01-11 Cardiac Pathways Corp. Endocardial mapping catheter with movable electrode
US6533781B2 (en) * 1997-12-23 2003-03-18 Team Medical Llc Electrosurgical instrument
US6047215A (en) * 1998-03-06 2000-04-04 Sonique Surgical Systems, Inc. Method and apparatus for electromagnetically assisted liposuction
US6053909A (en) * 1998-03-27 2000-04-25 Shadduck; John H. Ionothermal delivery system and technique for medical procedures
US7022121B2 (en) * 1999-03-09 2006-04-04 Thermage, Inc. Handpiece for treatment of tissue
US6690976B2 (en) * 2000-04-13 2004-02-10 Celsion Corporation Thermotherapy method for treatment and prevention of breast cancer and cancer in other organs
US6702808B1 (en) * 2000-09-28 2004-03-09 Syneron Medical Ltd. Device and method for treating skin
US6997923B2 (en) * 2000-12-28 2006-02-14 Palomar Medical Technologies, Inc. Method and apparatus for EMR treatment
US6567262B2 (en) * 2001-06-01 2003-05-20 Active Cool Ltd. Liquid cooled TEC based system and method for cooling heat sensitive elements
US6684107B1 (en) * 2001-08-01 2004-01-27 Voyager Medical Corporation Wrinkle-reducing system
US6981970B2 (en) * 2002-12-16 2006-01-03 Msq (M2) Ltd. Device and method for treating skin

Cited By (77)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8073550B1 (en) 1997-07-31 2011-12-06 Miramar Labs, Inc. Method and apparatus for treating subcutaneous histological features
US20110046615A1 (en) * 2004-04-01 2011-02-24 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US20050222565A1 (en) * 2004-04-01 2005-10-06 Dieter Manstein Method and apparatus for dermatological treatment and tissue reshaping
US9877778B2 (en) 2004-04-01 2018-01-30 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US9095357B2 (en) 2004-04-01 2015-08-04 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US9510899B2 (en) 2004-04-01 2016-12-06 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US10575897B2 (en) 2004-04-01 2020-03-03 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US10912604B2 (en) 2004-04-01 2021-02-09 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US7824394B2 (en) 2004-04-01 2010-11-02 The General Hospital Corporation Method and apparatus for dermatological treatment and tissue reshaping
US20080009923A1 (en) * 2006-06-14 2008-01-10 Paithankar Dilip Y Treatment of Skin by Spatial Modulation of Thermal Heating
US9486285B2 (en) 2006-06-14 2016-11-08 Candela Corporation Treatment of skin by spatial modulation of thermal heating
US8246611B2 (en) 2006-06-14 2012-08-21 Candela Corporation Treatment of skin by spatial modulation of thermal heating
US10292859B2 (en) 2006-09-26 2019-05-21 Zeltiq Aesthetics, Inc. Cooling device having a plurality of controllable cooling elements to provide a predetermined cooling profile
US11219549B2 (en) 2006-09-26 2022-01-11 Zeltiq Aesthetics, Inc. Cooling device having a plurality of controllable cooling elements to provide a predetermined cooling profile
US11179269B2 (en) 2006-09-26 2021-11-23 Zeltiq Aesthetics, Inc. Cooling device having a plurality of controllable cooling elements to provide a predetermined cooling profile
US20080077201A1 (en) * 2006-09-26 2008-03-27 Juniper Medical, Inc. Cooling devices with flexible sensors
US11395760B2 (en) 2006-09-26 2022-07-26 Zeltiq Aesthetics, Inc. Tissue treatment methods
US9375345B2 (en) 2006-09-26 2016-06-28 Zeltiq Aesthetics, Inc. Cooling device having a plurality of controllable cooling elements to provide a predetermined cooling profile
US9427285B2 (en) 2007-04-19 2016-08-30 Miramar Labs, Inc. Systems and methods for creating an effect using microwave energy to specified tissue
US8401668B2 (en) 2007-04-19 2013-03-19 Miramar Labs, Inc. Systems and methods for creating an effect using microwave energy to specified tissue
US20080269735A1 (en) * 2007-04-26 2008-10-30 Agustina Vila Echague Optical array for treating biological tissue
US20080269734A1 (en) * 2007-04-26 2008-10-30 Agustina Vila Echague Optical Array for Treating Biological Tissue
US10383787B2 (en) 2007-05-18 2019-08-20 Zeltiq Aesthetics, Inc. Treatment apparatus for removing heat from subcutaneous lipid-rich cells and massaging tissue
US11291606B2 (en) 2007-05-18 2022-04-05 Zeltiq Aesthetics, Inc. Treatment apparatus for removing heat from subcutaneous lipid-rich cells and massaging tissue
US20080306418A1 (en) * 2007-06-05 2008-12-11 Reliant Technologies, Inc. Method for Reducing Pain of Dermatological Treatments
US9364287B2 (en) 2007-06-05 2016-06-14 Reliant Technologies, Inc. Method for reducing pain of dermatological treatments
US9655770B2 (en) 2007-07-13 2017-05-23 Zeltiq Aesthetics, Inc. System for treating lipid-rich regions
US20090043301A1 (en) * 2007-08-09 2009-02-12 Asthmatx, Inc. Monopolar energy delivery devices and methods for controlling current density in tissue
US10675178B2 (en) 2007-08-21 2020-06-09 Zeltiq Aesthetics, Inc. Monitoring the cooling of subcutaneous lipid-rich cells, such as the cooling of adipose tissue
US11583438B1 (en) 2007-08-21 2023-02-21 Zeltiq Aesthetics, Inc. Monitoring the cooling of subcutaneous lipid-rich cells, such as the cooling of adipose tissue
US9408745B2 (en) 2007-08-21 2016-08-09 Zeltiq Aesthetics, Inc. Monitoring the cooling of subcutaneous lipid-rich cells, such as the cooling of adipose tissue
US8406894B2 (en) 2007-12-12 2013-03-26 Miramar Labs, Inc. Systems, apparatus, methods and procedures for the noninvasive treatment of tissue using microwave energy
US20090281540A1 (en) * 2008-05-06 2009-11-12 Blomgren Richard D Apparatus, Systems and Methods for Treating a Human Tissue Condition
US8348938B2 (en) 2008-05-06 2013-01-08 Old Dominian University Research Foundation Apparatus, systems and methods for treating a human tissue condition
US9737434B2 (en) 2008-12-17 2017-08-22 Zeltiq Aestehtics, Inc. Systems and methods with interrupt/resume capabilities for treating subcutaneous lipid-rich cells
US8882758B2 (en) 2009-01-09 2014-11-11 Solta Medical, Inc. Tissue treatment apparatus and systems with pain mitigation and methods for mitigating pain during tissue treatments
US8506506B2 (en) 2009-01-12 2013-08-13 Solta Medical, Inc. Tissue treatment apparatus with functional mechanical stimulation and methods for reducing pain during tissue treatments
US20100179455A1 (en) * 2009-01-12 2010-07-15 Solta Medical, Inc. Tissue treatment apparatus with functional mechanical stimulation and methods for reducing pain during tissue treatments
US9861520B2 (en) 2009-04-30 2018-01-09 Zeltiq Aesthetics, Inc. Device, system and method of removing heat from subcutaneous lipid-rich cells
US20100280582A1 (en) * 2009-04-30 2010-11-04 Zeltiq Aesthetics, Inc. Device, system and method of removing heat from subcutaneous lipid-rich cells
US8702774B2 (en) 2009-04-30 2014-04-22 Zeltiq Aesthetics, Inc. Device, system and method of removing heat from subcutaneous lipid-rich cells
US11224536B2 (en) 2009-04-30 2022-01-18 Zeltiq Aesthetics, Inc. Device, system and method of removing heat from subcutaneous lipid-rich cells
US11452634B2 (en) 2009-04-30 2022-09-27 Zeltiq Aesthetics, Inc. Device, system and method of removing heat from subcutaneous lipid-rich cells
US20100298825A1 (en) * 2009-05-08 2010-11-25 Cellutions, Inc. Treatment System With A Pulse Forming Network For Achieving Plasma In Tissue
US8788060B2 (en) 2009-07-16 2014-07-22 Solta Medical, Inc. Tissue treatment systems with high powered functional electrical stimulation and methods for reducing pain during tissue treatments
US9844461B2 (en) 2010-01-25 2017-12-19 Zeltiq Aesthetics, Inc. Home-use applicators for non-invasively removing heat from subcutaneous lipid-rich cells via phase change coolants
US20110238051A1 (en) * 2010-01-25 2011-09-29 Zeltiq Aesthetics, Inc. Home-use applicators for non-invasively removing heat from subcutaneous lipid-rich cells via phase change coolants, and associated devices, systems and methods
US9314368B2 (en) 2010-01-25 2016-04-19 Zeltiq Aesthetics, Inc. Home-use applicators for non-invasively removing heat from subcutaneous lipid-rich cells via phase change coolants, and associates devices, systems and methods
US20110202048A1 (en) * 2010-02-12 2011-08-18 Solta Medical, Inc. Methods for pain reduction with functional thermal stimulation and tissue treatment systems
US10092346B2 (en) 2010-07-20 2018-10-09 Zeltiq Aesthetics, Inc. Combined modality treatment systems, methods and apparatus for body contouring applications
US8676338B2 (en) 2010-07-20 2014-03-18 Zeltiq Aesthetics, Inc. Combined modality treatment systems, methods and apparatus for body contouring applications
US9277958B2 (en) 2012-02-22 2016-03-08 Candela Corporation Reduction of RF electrode edge effect
US9889297B2 (en) 2012-02-22 2018-02-13 Candela Corporation Reduction of RF electrode edge effect
US9844460B2 (en) 2013-03-14 2017-12-19 Zeltiq Aesthetics, Inc. Treatment systems with fluid mixing systems and fluid-cooled applicators and methods of using the same
US9545523B2 (en) 2013-03-14 2017-01-17 Zeltiq Aesthetics, Inc. Multi-modality treatment systems, methods and apparatus for altering subcutaneous lipid-rich tissue
US10575890B2 (en) 2014-01-31 2020-03-03 Zeltiq Aesthetics, Inc. Treatment systems and methods for affecting glands and other targeted structures
US10806500B2 (en) 2014-01-31 2020-10-20 Zeltiq Aesthetics, Inc. Treatment systems, methods, and apparatuses for improving the appearance of skin and providing other treatments
US10912599B2 (en) 2014-01-31 2021-02-09 Zeltiq Aesthetics, Inc. Compositions, treatment systems and methods for improved cooling of lipid-rich tissue
US10201380B2 (en) 2014-01-31 2019-02-12 Zeltiq Aesthetics, Inc. Treatment systems, methods, and apparatuses for improving the appearance of skin and providing other treatments
US9861421B2 (en) 2014-01-31 2018-01-09 Zeltiq Aesthetics, Inc. Compositions, treatment systems and methods for improved cooling of lipid-rich tissue
US11819257B2 (en) 2014-01-31 2023-11-21 Zeltiq Aesthetics, Inc. Compositions, treatment systems and methods for improved cooling of lipid-rich tissue
US10675176B1 (en) 2014-03-19 2020-06-09 Zeltiq Aesthetics, Inc. Treatment systems, devices, and methods for cooling targeted tissue
USD777338S1 (en) 2014-03-20 2017-01-24 Zeltiq Aesthetics, Inc. Cryotherapy applicator for cooling tissue
WO2015160076A1 (en) * 2014-04-17 2015-10-22 주식회사 제이에스온 High-frequency thermotherapy device
US10952891B1 (en) 2014-05-13 2021-03-23 Zeltiq Aesthetics, Inc. Treatment systems with adjustable gap applicators and methods for cooling tissue
US10935174B2 (en) 2014-08-19 2021-03-02 Zeltiq Aesthetics, Inc. Stress relief couplings for cryotherapy apparatuses
US10568759B2 (en) 2014-08-19 2020-02-25 Zeltiq Aesthetics, Inc. Treatment systems, small volume applicators, and methods for treating submental tissue
US11154418B2 (en) 2015-10-19 2021-10-26 Zeltiq Aesthetics, Inc. Vascular treatment systems, cooling devices, and methods for cooling vascular structures
US10524956B2 (en) 2016-01-07 2020-01-07 Zeltiq Aesthetics, Inc. Temperature-dependent adhesion between applicator and skin during cooling of tissue
US10765552B2 (en) 2016-02-18 2020-09-08 Zeltiq Aesthetics, Inc. Cooling cup applicators with contoured heads and liner assemblies
US10555831B2 (en) 2016-05-10 2020-02-11 Zeltiq Aesthetics, Inc. Hydrogel substances and methods of cryotherapy
US11382790B2 (en) 2016-05-10 2022-07-12 Zeltiq Aesthetics, Inc. Skin freezing systems for treating acne and skin conditions
US10682297B2 (en) 2016-05-10 2020-06-16 Zeltiq Aesthetics, Inc. Liposomes, emulsions, and methods for cryotherapy
US11076879B2 (en) 2017-04-26 2021-08-03 Zeltiq Aesthetics, Inc. Shallow surface cryotherapy applicators and related technology
US11446175B2 (en) 2018-07-31 2022-09-20 Zeltiq Aesthetics, Inc. Methods, devices, and systems for improving skin characteristics
USD971415S1 (en) 2019-12-30 2022-11-29 Cynosure, Llc Flexible applicator
USD1014763S1 (en) 2019-12-30 2024-02-13 Cynosure, Llc Flexible applicator

Also Published As

Publication number Publication date
AU2003207858B2 (en) 2006-08-10
US20170209212A1 (en) 2017-07-27
WO2003065916A1 (en) 2003-08-14
US20140066918A1 (en) 2014-03-06
CN1627923A (en) 2005-06-15
JP2005516666A (en) 2005-06-09
AU2003207858A1 (en) 2003-09-02
US20090287207A1 (en) 2009-11-19
EP1808145A2 (en) 2007-07-18
US8603088B2 (en) 2013-12-10
US9636175B2 (en) 2017-05-02
KR100706155B1 (en) 2007-04-11
ATE411778T1 (en) 2008-11-15
US7141049B2 (en) 2006-11-28
CA2474421A1 (en) 2003-08-14
BR0307392A (en) 2004-11-09
EP1471845B1 (en) 2008-10-22
US20190090947A1 (en) 2019-03-28
US20040111087A1 (en) 2004-06-10
EP1471845A1 (en) 2004-11-03
ES2314180T3 (en) 2009-03-16
AU2003207858A2 (en) 2003-09-02
DE60324249D1 (en) 2008-12-04
KR20040093706A (en) 2004-11-08

Similar Documents

Publication Publication Date Title
US20190090947A1 (en) Apparatus for transcutaneously treating tissue
US7022121B2 (en) Handpiece for treatment of tissue
US8685017B2 (en) Method and kit for treatment of tissue
US7452358B2 (en) RF electrode assembly for handpiece
US7267675B2 (en) RF device with thermo-electric cooler
US7189230B2 (en) Method for treating skin and underlying tissue
US7481809B2 (en) Handpiece with RF electrode and non-volatile memory
US7006874B2 (en) Treatment apparatus with electromagnetic energy delivery device and non-volatile memory
US8221410B2 (en) Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient
US20060206110A1 (en) Handpiece with RF electrode and non-volative memory

Legal Events

Date Code Title Description
AS Assignment

Owner name: SILICON VALLEY BANK, CALIFORNIA

Free format text: SECURITY AGREEMENT;ASSIGNOR:SOLTA MEDICAL, INC.;REEL/FRAME:022824/0837

Effective date: 20090304

STCB Information on status: application discontinuation

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

AS Assignment

Owner name: SILICON VALLEY BANK, CALIFORNIA

Free format text: SECURITY INTEREST - MEZZANINE LOAN;ASSIGNOR:SOLTA MEDICAL, INC.;REEL/FRAME:030281/0524

Effective date: 20120829

AS Assignment

Owner name: SOLTA MEDICAL, INC., CALIFORNIA

Free format text: RELEASE OF SECURITY INTEREST IN PATENTS;ASSIGNOR:SILICON VALLEY BANK;REEL/FRAME:032126/0475

Effective date: 20140123