CA2303021C - Expandable ligator catheter having multiple electrode leads, and method - Google Patents

Expandable ligator catheter having multiple electrode leads, and method Download PDF

Info

Publication number
CA2303021C
CA2303021C CA002303021A CA2303021A CA2303021C CA 2303021 C CA2303021 C CA 2303021C CA 002303021 A CA002303021 A CA 002303021A CA 2303021 A CA2303021 A CA 2303021A CA 2303021 C CA2303021 C CA 2303021C
Authority
CA
Canada
Prior art keywords
leads
catheter
lead
anatomical structure
distal
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.)
Expired - Fee Related
Application number
CA002303021A
Other languages
French (fr)
Other versions
CA2303021A1 (en
Inventor
Arthur W. Zikorus
Mark P. Parker
Christopher S. Jones
Douglas M. Petty
Brian E. Farley
Joseph M. Tartaglia
Dawn A. Henderson
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.)
VNUS Medical Technologies LLC
Original Assignee
VNUS Medical Technologies LLC
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 US08/927,251 external-priority patent/US6200312B1/en
Application filed by VNUS Medical Technologies LLC filed Critical VNUS Medical Technologies LLC
Publication of CA2303021A1 publication Critical patent/CA2303021A1/en
Application granted granted Critical
Publication of CA2303021C publication Critical patent/CA2303021C/en
Anticipated expiration legal-status Critical
Expired - Fee Related legal-status Critical Current

Links

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
    • A61B18/1492Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22038Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with a guide wire
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22051Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22051Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
    • A61B2017/22065Functions of balloons
    • A61B2017/22067Blocking; Occlusion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053Mechanical features of the instrument of device
    • A61B2018/00214Expandable means emitting energy, e.g. by elements carried thereon
    • 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
    • A61B2018/00053Mechanical features of the instrument of device
    • A61B2018/00214Expandable means emitting energy, e.g. by elements carried thereon
    • A61B2018/0022Balloons
    • 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
    • A61B2018/00345Vascular system
    • A61B2018/00404Blood vessels other than those in or around the heart
    • 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
    • A61B2018/00482Digestive system
    • A61B2018/00488Esophagus
    • 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
    • A61B2018/00571Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00589Coagulation
    • 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
    • A61B2018/00898Alarms or notifications created in response to an abnormal condition
    • 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
    • A61B18/1206Generators therefor
    • A61B2018/124Generators therefor switching the output to different electrodes, e.g. sequentially
    • 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
    • A61B18/1206Generators therefor
    • A61B2018/1246Generators therefor characterised by the output polarity
    • A61B2018/1253Generators therefor characterised by the output polarity monopolar
    • 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
    • A61B18/1206Generators therefor
    • A61B2018/1246Generators therefor characterised by the output polarity
    • A61B2018/126Generators therefor characterised by the output polarity bipolar
    • 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
    • A61B90/36Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37Surgical systems with images on a monitor during operation
    • A61B2090/378Surgical systems with images on a monitor during operation using ultrasound
    • A61B2090/3782Surgical systems with images on a monitor during operation using ultrasound transmitter or receiver in catheter or minimal invasive instrument
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2218/00Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2218/001Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body having means for irrigation and/or aspiration of substances to and/or from the surgical site
    • A61B2218/002Irrigation

Abstract

A catheter (10) includes a plurality of primary leads (30) to deliver energy for ligating a hollow anatomical structure (52). Each of the primary leads (30) includes an electrode (34) located at the working end (15) of the catheter (10). Separation is maintained between the primary leads (30) such that each primary lead (30) can individually receive power of selected polarity. The primary leads (30) are constructed to expand outwardly to place the electrodes (34) into apposition with a hollow anatomical structure (52). High frequency energy can be applied from the leads (30) to create a heating effect in the surrounding tissue of the anatomical structure (52). The diameter of the hollow anatomical structure (52) is reduced by the heating effect, and the electrodes (34) of the primary leads (30) are moved closer to one another. Where the hollow anatomical structure is a vein (52), energy is applied until the diameter of the vein (52) is reduced to the point where the vein (52) is occluded. In one embodiment, a balloon (64) is inflated to occlude the structure (52) before the application of energy. Where the structure is a vein (52), the inflated balloon (64) obstructs blood flow and facilitates the infusion of saline, medication, or a high-impedance fluid to the vein (52) in order to reduce the occurrence of coagulation and to improve the heating of the vein by the catheter (10). The catheter (10) can include a lumen (48) to accommodate a guide wire (53) or to allow fluid delivery.

Description

EXPANDABLE VEIN LIGATOR CATHETER
AND METHOD OF USE
BACKGROUND OF THE INVENTION
The invention relates generally to a method and apparatus for applying energy to shrink a hollow anatomical structure such as a vein, and more particularly, to a method and apparatus using an electrode device having multiple leads for applying said energy.
The human venous system of the lower limbs consists essentially of the superficial venous system and the deep venous system with perforating veins connecting the two systems. The superficial system includes the long or great saphenous vein and the short saphenous vein. The deep venous system includes the anterior and posterior tibial veins which unite to form the popliteal vein, which in turn becomes the femoral vein when joined by the short saphenous vein.
The venous system contains numerous one-way valves for directing blood flow back to the heart. Venous valves are usually bicuspid valves, with each cusp forming a sack or reservoir for blood which, under retrograde blood pressure, forces the free surfaces of the cusps together to prevent retrograde flow of the blood and allows only antegrade blood flow to the heart. When an incompetent valve is in the flow path, the valve is unable to close because the cusps do not form a proper seal and retrograde flow of the blood cannot be stopped. When a venous valve fails, increased strain and pressure occur within the lower venous sections and overlying tissues, sometimes leading to additional valvular failure.
Two venous conditions which often result from valve failure are varicose veins and more symptomatic chronic venous insufficiency.
The varicose vein condition includes dilation and tortuosity of the superficial veins of the lower limbs, resulting in unsightly discoloration, pain, swelling, and possibly ulceration. Varicose veins often involve incompetence of one or more venous valves, which allow reflux of blood within the superficial system. This can also worsen deep venous reflux and perforator reflux. Current treatments of vein insufficiency include surgical procedures such as vein stripping, ligation, and occasionally, vein-segment transplant.
Ligation involves the cauterization or coagulation of vascular lamina using electrical energy applied through an electrode device. An electrode device is introduced into the vein lumen and positioned so that it contacts the vein wall.
Once properly positioned, RF energy is applied to the electrode device thereby causing the vein wall to shrink in cross-sectional diameter. A reduction in cross-sectional diameter, as for example from 5 mm (0.2 in) to 1 mm (0.04 in), significantly reduces the flow of blood through the vein and results in an effective ligation. Though not required for effective ligation, the vein wall may completely collapse thereby resulting in a full-lumen obstruction that blocks the flow of blood through the vein.
One apparatus for performing venous ligation includes a tubular shaft having an electrode device attached at the distal tip. Running through the shaft, from the distal end to the proximal end, are electrical leads. At the proximal end of the shaft, the leads terminate at an electrical connector, while at the distal end of the shaft the leads are connected to the electrode device. The electrical connector provides the interface between the leads and a power source, typically an RF generator. The RF generator operates under the guidance of a control device, usually a microprocessor.
The ligation apparatus may be operated in either a monopolar and bipolar configuration. In the monopolar configuration, the electrode device consists of an electrode that is either positively or negatively charged. A return path for the current passing through the electrode is provided externally from the body, as for example by placing the patient in physical contact with a large low-impedance pad. The current flows from the ligation device to the low impedance pad. In a bipolar configuration, the electrode device consists of a pair of oppositely charged electrodes separated by a dielectric material. Accordingly, in the bipolar mode, the return path for current is provided by the electrode device itself. The current flows from one electrode, through the tissue, and returns by way of the oppositely charged electrode.
To protect against tissue damage; l. e. , charring, due to cauterization caused by overheating, a temperature sensing device is attached to the electrode device. The temperature sensing device may be a thermocouple that monitors the temperature of the venous tissue. The thermocouple interfaces with the RF
generator and the controller through the shaft and provides electrical signals to the controller which monitors the temperature and adjusts the energy applied to the tissue, through the electrode device, accordingly.
The overall effectiveness of a ligation apparatus is largely dependent on the electrode device contained within the apparatus. Monopolar and bipolar electrode devices that comprise solid devices having a fixed shape and size limit the effectiveness of the ligating apparatus for several reasons. Firstly, a fixed-size electrode device typically contacts the vein wall at only one point on the circumference or inner diameter of the vein wall. As a result, the application of RF energy is highly concentrated within the contacting venous tissue, while the flow of RF current through the remainder of the venous tissue is disproportionately weak. Accordingly, the regions of the vein wall near the point of contact collapse at a faster rate then other regions of the vein wall, resulting in non-uniform shrinkage of the vein lumen. Furthermore, the overall strength of the occlusion may be inadequate and the lumen may eventually reopen. To avoid an inadequate occlusion RF energy must be applied for an extended period of time. Application of RF energy as such increases the temperature of the blood and usually results in a significant amount of heat-induced coagulum forming on the electrode and in the vein which is not desirable.
Secondly, the effectiveness of a ligating apparatus having a fixed electrode device is limited to certain sized veins. An attempt to ligate a vein having a diameter that is substantially greater than the electrode device can result in not only non-uniform shrinkage of the vein wall as just described, but also insufficient shrinkage of the vein. The greater the diameter of the vein relative to the diameter of the electrode device, the weaker the energy applied to the vein wall at points distant from the point of contact. Accordingly the vein wall is likely to not completely collapse prior to the venous tissue becoming over cauterized at the point of electrode contact. While coagulation as such may initially occlude the vein, such occlusion may only be temporary in that the coagulated blood may eventually dissolve and the vein partially open. One solution for this inadequacy is an apparatus having interchangeable electrode devices with various diameters.
Such a solution, however, is both economically inefficient and tedious to use.
Hence those skilled in the art have recognized a need for an expandable electrode device and a method capable of evenly distributing RF energy along a circumferential band of a vein wall where the vein wall is greater in diameter than the electrode device, and thereby provide more predictable and effective occlusion of veins while minimizing the formation of heat-induced coagulum. The invention fulfills these needs and others.
SUMMARY OF THE INVENTION
Briefly, and in general terms, the present invention provides an apparatus and method for applying energy along a generally circumferential band of a vein wall. The application of energy as such results in a more uniform and predictable shrinkage of the vein wall.
In one aspect of the invention, an apparatus for delivering energy to ligate an anatomical structure comprises a catheter having a sheath, a working end, and an opening formed at the working end of the catheter; an inner member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another; a plurality of leads, each lead having a distal end, the plurality of leads being coupled with the inner member such that the distal ends of the plurality of leads extend out of the opening at the working end of the catheter when the position of the sheath changes in one direction relative to the inner member, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening; wherein the distal ends of the leads are configured to deliver energy to the anatomical structure.
In another aspect of the invention, the apparatus includes a secondary lead having a secondary distal end. The secondary lead is coupled with the inner 5 member such that the distal end of the secondary lead is extended out of the opening at the working end of the catheter when the position of the inner member changes in one direction relative to the sheath.
In another aspect of the invention, the distal ends of the leads are electrically connected to a power source such that the polarity of each lead can be switched. Where there is a secondary lead electrode, the plurality of leads can be connected to the power source such that the polarity of the leads can be changed independently of the polarity of the secondary lead.
In another aspect, the leads include primary leads which generally surround the secondary lead at the working end of the catheter. The distal ends of the primary leads are located between the distal end of the secondary lead and the inner member.
In yet another aspect, the invention comprises a method of applying energy to a hollow anatomical structure from within the structure. The method includes the step of introducing a catheter into the anatomical structure; the catheter having a working end and a plurality of leads, each lead having a distal end, and each lead being connected to a power source. The method also includes the step of expanding the leads outwardly through the distal orifice and expanding the leads until each electrode contacts the anatomical structure. The method further includes the step of applying energy to the anatomical structure from the distal end of the leads, until the anatomical structure collapses.
In another aspect of the invention, the method also includes the step of introducing a catheter into the anatomical structure where the catheter has a secondary lead that has a distal portion that is greater in length than the primary-lead distal portions and is generally surrounded by the primary leads. The secondary lead also has an electrode at the distal end. The method also includes the steps of extending the primary and secondary leads through the orifice until each primary-lead electrode contacts the anatomical structure, and controlling the power source so that adjacent primary leads are of opposite polarity while maintaining the secondary lead so that it is electrically neutral. Upon collapse of the anatomical structure around the primary leads, the polarity of the primary leads is switched so that they are all of the same polarity. Upon switching the polarity of the primary leads so that they are of the same polarity, controlling the power source so that the secondary lead is of opposite polarity relative to the primary leads. The method, in a further aspect, comprises the step of moving the 10 catheter in the anatomical structure while continuing to apply energy to the anatomical structure to lengthen the area of ligation.
In another aspect of the invention, external compression is used to initially force the wall of the vein to collapse toward the catheter. The application of energy molds the vein to durably assume the collapsed state initially achieved mechanically by the external compression. A tourniquet can be used to externally compress or flatten the anatomical structure and initially reduce the diameter of the hollow anatomical structure. The pressure applied by the tourniquet can exsanguinate blood from the venous treatment site, and pre-shape the vein in preparation to be molded to a ligated state. An ultrasound window formed in the 20 tourniquet can be used to facilitate ultrasound imaging of the anatomical structure being treated through the window.
In yet another aspect of the invention, a balloon is provided to occlude the vein before the application of energy, such that the need for an external compression by a tourniquet is not required to stop blood flow. This also allows 25 the vein to be occluded even for the deep veins where a compressive tourniquet may not be able to compress the vein to occlusion.
In yet another aspect of the invention, a flexible covering, relatively impermeable to fluid, spans the area between the leads along the circumference of the catheter when the leads are extended out, such that the webbed covering 30 blocks blood flow within the vein.

In yet another aspect of the invention, a flexible balloon-like covering is located on the catheter, having openings to the concave side and a convex side facing the working end of the catheter. The covering fills with blood and expands. When the covering balloons out to the diameter of the vein, blood flow is stopped.
In yet another aspect of the invention, mechanically blocking blood flow with the catheter is combined with infusion of a high-impedance fluid. The fluid may also be an anticoagulant. The fluid displaces any remaining blood from the venous treatment site and prevents energy from being dissipated away from the vein which is in apposition with the electrodes.
According to one embodiment there is disclosed an apparatus for applying energy from a power source to a hollow anatomical structure having an inner wall, the apparatus comprising: a catheter having a working end with a distal tip with an orifice formed therein; a plurality of leads disposed at the working end, each lead having a distal portion with an uninsulated distal end, each lead electrically connected to the power source; means for extending the leads through the distal orifice; and means for expanding the leads outwardly into non-penetrating contact with the inner wall when the leads have been extended; whereby the leads move away from each other and into contact with the anatomical structure when extended out the distal orifice.
According to a further embodiment there is disclosed the apparatus wherein the leads are disposed in relation to the working end such that the distal portions of the leads move away from each other when extended through the distal orifice to form a substantially symmetric arrangement of substantially evenly spaced distal ends.
According to a further embodiment there is disclosed the apparatus wherein the leads are disposed in relation to the working end such that when the leads are extended through the distal orifice, the distance between two mutually opposed distal ends is greater than the diameter of the working end.
According to a further embodiment there is disclosed the apparatus wherein the distal end of each lead includes a hemispherical shape having an uninsulated rounded convex surface, wherein the remainder of the hemispherical shape is insulated.
According to a further embodiment there is disclosed the apparatus wherein the leads are mounted at the working end in a cantilever arrangement.

7a According to a fiufiher embodiment there is disclosed the apparatus wherein the extending means include a conductive ring, and at least one of the leads is connected to the ring, and the conductive ring is connected to a power source.
According to a further embodiment there is disclosed the apparatus wherein the S expansion means include a bend formed in each lead such that each lead tends to move outward away from the other leads.
According to a further embodiment there is disclosed the apparatus wherein the expansion means include a bend formed with an angle less than ninety degrees for each lead.
According to a further embodiment there is disclosed the apparatus wherein each lead comprises a rectangular cross section mounted in relation to the catheter such that the thinner dimension of the rectangular cross section is aligned with the direction of expansion of the lead.
According to a further embodiment there is disclosed the apparatus further comprising a secondary lead connected to the extending means, the secondary lead having a distal end and a length such that the distal end of the secondary lead extends past the distal end of the leads, wherein the extending means extends the leads and the secondary lead through the distal orifice.
According to a further embodiment there is disclosed the apparatus described further comprising a spherically shaped electrode mounted at the distal end of the secondary lead.
According to a further embodiment there is disclosed the apparatus described further comprising: a controller that controls the output of the power source to the leads and the secondary lead; wherein the controller is adapted to switch the electrical polarity of the distal ends of the leads to a common polarity and switch the polarity of the secondary lead to a polarity opposite that of the leads. According to a further embodiment there is disclosed the apparatus wherein the secondary lead is centrally located with respect to the leads.
According to a further embodiment there is disclosed the apparatus described wherein the secondary lead includes a guide wire lumen for receiving a guide wire.
According to a further embodiment there is disclosed the apparatus wherein the extending means comprise: an outer sheath mounted on the catheter, the outer sheath being movable; and an alignment device positioned inside the outer sheath, the alignment 7b device maintaining separation between the leads; wherein movement of the outer sheath in relation to the alignment device extends the leads through the orifice.
According to a further embodiment there is disclosed the apparatus wherein the extension means comprise: an outer sheath mounted on the catheter; an alignment device positioned inside the outer sheath, the leads being mounted to the alignment device such that the alignment device maintains separation between the leads; a movable inner sheath to which the leads are attached, the inner sheath being movable in relation to the outer sheath; wherein movement of the inner sheath in relation to the outer sheath extends the leads through the orifice.
According to a further embodiment there is disclosed the apparatus further comprising a switch connected to the power source, wherein the leads are adapted to be electrically connected to the power source, and the polarity of the leads are selectively changed by the switch.
According to a further embodiment there is disclosed the apparatus further comprising: a controller that controls the power source; and a temperature sensor mounted to a distal end of a lead, the temperature sensor providing temperature signals to the controller; wherein the controller controls the power source in response to signals from the temperature sensor.
According to a further embodiment there is disclosed an apparatus for applying energy from a power source to an inner wall of a hollow anatomical structure, the apparatus comprising: a catheter having a working end with a distal tip with an orifice formed therein; a plurality of leads disposed at the working end, each lead having an uninsulated distal end, each lead electrically connected to the power source and each lead mounted at a proximal end to the working end in a cantilever arrangement; and means for extending the leads through the distal orifice; wherein each lead comprises a bend formed in the lead such that when the leads have been extended through the orifice, the leads expand outwardly moving away from each other into non-penetrating contact with the inner wall to form a substantially symmetric arrangement of substantially evenly spaced distal ends.
According to a further embodiment there is disclosed the apparatus wherein each lead comprises an electrode mounted at its distal end, the electrode having a hemispherical shape.

According to a further embodiment there is disclosed the apparatus wherein each lead comprises an electrode mounted at its distal end, the electrode having a spherical shape.
According to a further embodiment there is disclosed the apparatus wherein each lead comprises a rectangular cross section mounted in relation to the catheter such that the thinner dimension of the rectangular cross section is aligned with the direction of expansion of the lead.
According to a further embodiment there is disclosed the apparatus further comprising a secondary lead mounted to the working end, the secondary lead having a distal end and a length exceeding that of the leads, the extension means also for extending the secondary lead through the distal orifice.
According to a further embodiment there is disclosed the apparatus described further comprising a spherically shaped electrode mounted at the distal end of the secondary lead.
According to a further embodiment there is disclosed the apparatus further comprising: a controller that controls the output of the power source to the electrodes of the leads and the secondary lead; wherein the controller is adapted to switch the electrical polarity of the distal ends of the leads to a common polarity and switch the polarity of the secondary lead to a polarity opposite that of the leads.
According to a further embodiment there is disclosed the apparatus wherein the secondary lead is centrally located with respect to the leads.
According to a further embodiment there is disclosed the use of a catheter to apply energy from a power source from within a hollow anatomical structure for a period of time sufficient to cause the collapse of the hollow anatomical structure wherein the catheter comprises a working end and a plurality of leads disposed at the working end, each lead having a distal end and being connected to the power source, and wherein the distal ends of the leads move away from each other and are adapted for non-penetrating contact with the anatomical structure .
According to a further embodiment there is disclosed the use wherein the step of expanding the leads comprises the step of expanding the leads such that the distal ends of the leads are spaced such that the distal ends of the leads are no more than 5 millimeters apart along the hollow anatomical structure.

7d According to a further embodiment there is disclosed the use further comprising the step of extending the leads through an orifice formed in the working end of the catheter, wherein the distance between two mutually opposed distal ends is greater than the diameter of the working end in the step of expanding the distal ends when the leads are extended through the distal orifice.
According to a further embodiment there is disclosed the use wherein separation between the leads is maintained with an alignment device positioned inside an outer sheath of the catheter; and further comprising the step of moving the outer sheath in relation to the alignment device to extend the leads out the orifice.
According to a further embodiment there is disclosed the use wherein separation between the leads is maintained with an alignment device positioned inside an outer sheath of the catheter, and the leads are attached to an inner sheath; and further comprising the step of moving the outer sheath in relation to the inner sheath to extend the leads through the orifice.
According to a further embodiment there is disclosed the use wherein a secondary lead is mounted to the working end, the secondary lead having a distal end and having a length exceeding that of the leads; and wherein the step of extending the plurality of leads further includes the step of extending the secondary lead through the distal orifice.
According to a further embodiment there is disclosed the use wherein the step of applying energy from within the anatomical structure comprises the steps of controlling the power source so that adjacent leads are of opposite polarity while maintaining the secondary lead so that it is electrically neutral; switching the polarity of the leads so that they are all of the same polarity upon collapse of the anatomical structure around the leads; and controlling the power source so that the secondary lead is of opposite polarity relative to the leads upon switching the polarity of the leads so that they are of the same polarity.
According to a further embodiment there is disclosed the use of the catheter wherein the catheter is adapted to be moved while energy is applied from within the anatomical structure.
According to a further embodiment there is disclosed the use wherein the step of introducing a catheter having a plurality of leads into the hollow anatomical structure comprises the step of introducing a plurality of leads that are mounted to the working end in a cantilever arrangement.

7e According to a further embodiment there is disclosed the use wherein the step of expanding the leads away from each other comprises the step of forming a bend in each lead, the bend formed in the direction away from the other leads such that each lead tends to move outward away from the other leads.
According to a further embodiment there is disclosed the use further comprising the steps of: sensing the temperature at the distal end of a lead;
andcontrolling the application of power to the leads in response to the temperature sensed at the distal end.
According to a further embodiment there is disclosed the use of the wherein when the application of energy occurs, the hollow anatomical structure is a previously flushed hollow anatomical structure.
According to a further embodiment there is disclosed the use of the catheter wherein the hollow anatomical structure from within which the application of energy occurs, is a previously compressed hollow anatomical structure.
According to a further embodiment there is disclosed the use of the catheter further comprising a step following the expansion of the leads wherein the step of expanding the leads is followed by a step wherein the hollow anatomical structure becomes compressed.
According to a further embodiment there is disclosed the use of the catheter further comprising the use of a tourniquet to compress the hollow anatomical structure and permit monitoring of the hollow anatomical structure through a window in the tourniquet.
According to a further embodiment there is disclosed the use of the catheter wherein the hollow anatomical structure is a compressed anatomical structure wherein the compression has reduced the diameter of the hollow anatomical structure to a desired diameter for ligation and the compression of the anatomical structure urges the expanded Ieads towards one another According to a further embodiment there is disclosed the use of the catheter wherein at the time of the application of energy from within the hollow anatomical structure, the hollow anatomical structure is a previously exsanguinated hollow anatomical structure.
According to a further embodiment there is disclosed the use of the catheter further comprising the use of an introduced fluid to exsanguinate the hollow anatomical structure.
According to a further embodiment there is disclosed the use of the catheter wherein the hollow anatomical structure becomes compressed during the exsanguination process.

7f According to one embodiment there is disclosed an apparatus for delivering energy to ligate an anatomical structure, the anatomical structure having an inner wall, the apparatus comprising: a catheter having a sheath, a working end, and an opening formed at the working end of the catheter; an inner member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another; a plurality of leads, each lead having a distal end, the plurality of leads being attached to the inner member such that the distal ends of the plurality of leads extend out of the opening at the working end of the catheter when the position of the sheath changes in one direction relative to the inner member, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening and into non-penetrating apposition with the inner wall of the hollow anatomical structure; wherein the distal ends of the leads are configured to deliver energy to the anatomical structure.
According to a further embodiment there is disclosed the apparatus further comprising an actuation mechanism located remotely from the working end of the catheter, the actuation mechanism being coupled to the sheath and the inner member such that an operator manually controls the movement of the sheath and the inner member relative to one another.
According to a further embodiment there is disclosed the apparatus wherein the actuation mechanism is coupled to the sheath such that the sheath is moved relative to the inner member.
According to a fizrther embodiment there is disclosed the apparatus wherein the actuation mechanism is coupled to the inner member such that the inner member is moved relative to the sheath.
According to a further embodiment there is disclosed the apparatus wherein the anatomical structure is a vein, and the leads are formed to have sufficient force to move into apposition with the vein wall, and the formed leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
According to a further embodiment there is disclosed the apparatus further comprising a secondary lead having a distal secondary end, the secondary lead being attached with the inner member such that the distal secondary end of secondary lead is extended out of the opening at the working end of the catheter when the position of the 7g inner member changes in one direction relative to the sheath, wherein the distal ends of the leads are located between the distal secondary end of the secondary lead and the inner member.
According to a further embodiment there is disclosed the apparatus wherein the leads are electrically connected to a power source such that the polarity of each lead can be switched.
According to a further embodiment there is disclosed the apparatus wherein the plurality of leads and the secondary lead are electrically connected to a power source such that the polarity of the plurality of leads can be changed independently of the polarity of the secondary lead.
According to a further embodiment there is disclosed the apparatus wherein the plurality of leads and the secondary lead are electrically connected to a power source, wherein the polarity of the plurality of leads can be switched to have either the same polarity or to have opposing polarities for adjacent distal ends of the leads, and the polarity of the secondary lead can be switched between having a polarity and being neutral.
According to a further embodiment there is disclosed the apparatus wherein the distal secondary end includes a generally spherical shape having a cross-sectional dimension approximately equal to the dimension of the opening at the working end of the catheter.
According to a fiu-ther embodiment there is disclosed the apparatus wherein the distal ends of the leads are configured to form a shape having a cross-sectional dimension no greater than the dimension of the distal secondary end when the distal ends are moved toward the longitudinal axis defined by the sheath.
According to a further embodiment there is disclosed the apparatus wherein the distal ends of the leads are configured to form, in combination with the secondary lead, a shape having a cross-sectional dimension no greater than the dimension of the distal secondary end when the distal ends are moved toward the longitudinal axis defined by the sheath.
According to a further embodiment there is disclosed the apparatus wherein the secondary lead includes a secondary lumen and a secondary opening formed in the distal secondary end such that the secondary opening is in fluid communication with the secondary lumen.

7h According to a further embodiment there is disclosed the apparatus wherein secondary lumen is configured to accept a guide wire.
According to a further embodiment there is disclosed the apparatus wherein the distal end of the leads each include a rounded convex surface which is uninsulated.
According to a further embodiment there is disclosed the apparatus wherein a temperature sensor is located on at least one of the distal ends of the plurality of leads.
According to a further embodiment there is disclosed the apparatus wherein the distal ends of the leads are arranged to occupy a plane perpendicular to the longitudinal axis defined by the sheath.
According to a further embodiment there is disclosed the apparatus wherein the distal ends of the leads are configured to form a generally spherical shape when the distal ends are moved toward the longitudinal axis defined by the sheath.
According to a further embodiment there is disclosed the apparatus wherein the working end of the catheter includes a tip having a soft durometer, the opening being formed in the tip.
According to a further embodiment there is disclosed the apparatus wherein the leads are electrically connected to a power source such that the polarity of each lead can be switched.
According to a further embodiment there is disclosed the apparatus wherein the leads are electrically connected to a power source such that the polarity of each lead is the same.
According to a further embodiment there is disclosed the apparatus wherein the leads are electrically connected to a power source such that the polarity of a first lead of the plurality of leads is opposite to the leads with distal ends adjacent to the distal end of the first lead.
According to a further embodiment there is disclosed the apparatus wherein a ring is attached to the inner member, and at least one lead of the plurality of leads is connected to the ring.
According to a further embodiment there is disclosed the apparatus wherein the ring is conductive and electrically connected to a power source so that the distal end of the one lead can deliver energy to ligate the anatomical structure.
According to one embodiment there is disclosed an apparatus for ligating a hollow anatomical structure having an inner wall, comprising: a catheter having a sheath and a working end, wherein a tip, a port and an opening are located at the working end of the catheter, and the port is in fluid communication with a lumen; a balloon located at the working end of the catheter, wherein the port is located between the balloon and the tip; an inner member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another; a plurality of leads, each lead having a distal end, the plurality of leads being coupled with the inner member such that the distal ends of the plurality of leads become extended out of the opening at the working end of the catheter when the sheath is moved relative to the inner member, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening and into non-penetrating apposition with the inner wall of the hollow anatomical structure; wherein the distal end of each lead is capable of delivering energy to the anatomical structure.
According to a further embodiment there is disclosed the apparatus wherein the anatomical structure is a vein, and the formed leads have sufficient force to move into apposition with the vein wall, and the formed leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
According to a further embodiment there is disclosed the apparatus further comprising a secondary lead having a distal secondary end, the secondary lead being coupled with the inner member such that the distal secondary end of secondary lead is extended out of the opening at the working end of the catheter when the inner member is moved relative to the sheath, wherein the distal ends of the leads are located between the distal secondary end of the secondary lead and the inner member.
According to a further embodiment there is disclosed the apparatus wherein the leads are electrically connected to a power source such that the polarity of each lead can be switched.
According to a further embodiment there is disclosed the apparatus wherein the plurality of leads and the secondary lead are electrically connected to a power source such that the polarity of the plurality of leads can be changed independently of the polarity of the secondary lead.
According to a further embodiment there is disclosed the apparatus, wherein the plurality of leads and the secondary lead are electrically connected to a power source, wherein the polarity of the plurality of leads can be switched to have either the same polarity or to have opposing polarities for adjacent distal ends of the leads, and the polarity of the secondary lead can be switched between having a polarity and being neutral.
According to a further embodiment there is disclosed the apparatus wherein the balloon includes openings exposed to the fluid in the anatomical structure, and the openings allow fluid from the hollow anatomical structure to flow into and expand the balloon.
According to one embodiment there is disclosed an apparatus for ligating a hollow anatomical structure, comprising: a catheter having a sheath and a working end, wherein a tip and a port are located at the working end of the catheter, and the port is in fluid communication with a lumen; a balloon located at the working end of the catheter; a plurality of bowable arms located between the ballon and the tip at the working end of the catheter, each arm having a section configured to come into non-penetrating contact with the anatomical structure; a plurality of electrodes, wherein at least one electrode is located on the section of at least one arm, and wherein the electrode is capable of delivering energy to the anatomical structure.
According to a further embodiment there is disclosed the apparatus wherein the balloon includes openings exposed to the fluid in the anatomical structure, and the openings allow fluid in the anatomical structure to flow into and expand the balloon.
According to a further embodiment there is disclosed the apparatus wherein the anatomical structure is a vein, and the leads have sufficient force to move into apposition with the vein wall; and the leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
According to a further embodiment there is disclosed the apparatus further comprising at least one aperture formed in the working end of the catheter to allow the delivery of fluid therethrough.
According to a further embodiment there is disclosed the apparatus wherein the fluid is a dielectric fluid.
According to a further embodiment there is disclosed the apparatus wherein the fluid includes heparin and water.
According to one embodiment there is disclosed an apparatus for ligating a hollow anatomical structure having an inner wall, comprising: a catheter having a sheath, a working end, and an opening are located at the working end of the catheter; an inner 7k member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another; a plurality of leads, each lead having a distal end, the plurality of leads being coupled with the inner member such that the distal ends of the plurality of leads become extended out of the opening at the working end of the catheter when the inner member is moved relative to the sheath, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening and into non-penetrating apposition with the inner wall of the hollow anatomical structure, the distal end of each lead is capable of delivering energy to the anatomical structure; a flexible, impermeable cover spanning the area between the leads along the circumference of the catheter when the Ieads are extended out the opening, such that the cover blocks fluid flow within the hollow anatomical structure.
According to a further embodiment there is disclosed the apparatus further comprising at least one aperature formed in the working end of the catheter to allow the delivery of fluid therethorugh.
According to a further embodiment there is disclosed the apparatus wherein the fluid is a dielectric fluid.
According to a further embodiment there is disclosed the apparatus wherein the fluid includes heparin and water.
According to a further embodiment there is disclosed the apparatus wherein the anatomical structure is a vein, and the formed leads have sufficient force to move into apposition with the vein wall, and the formed leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
According to a further embodiment there is disclosed the use of a catheter to apply energy from a power source from within a hollow anatomical structure for a time sufficient to cause the collapse of the hollow anatomical structure, wherein the catheter has a working end and a plurality of leads disposed at the working end, each lead having a distal end and being connected to the power source, and the distal ends of the leads being adapted for non-penetrating contact with the hollow anatomical structure, and the catheter is adapted so that expanding the circumference of the catheter adjacent the distal ends of the leads creates an obstruction sufficient to block the hollow anatomical structure.

According to a further embodiment there is disclosed the use of the catheter wherein the adaptation of the catheter comprises providing an inflatable balloon on the catheter.
According to a further embodiment there is disclosed the use of the catheter further comprising the use of an introduced fluid to displace fluids present around the working end of the catheter in the hollow anatomical structure.
According to a further embodiment there is disclosed the use of the catheter wherein the introduced fluid is a dielectric fluid.
According to a further embodiment there is disclosed the use of the wherein the introduced fluid comprises heparin.
According to a further embodiment there is disclosed the use of the catheter further comprising the use of heparin and saline to displace fluids present around the working end of the catheter in the anatomical structure.
According to a further embodiment there is disclosed the use of the catheter 1 S wherein the hollow anatomical structure is a vein and the catheter is adapted so that the leads in the step of expanding are adapted to have sufficient force to move into apposition with the vein wall, but to not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied to the distal end of the leads.
These and other aspects and advantages of the present invention will become apparent from the following more detailed description, when taken in conjunction with the accompanying drawings which illustrate, by way of example, embodiments of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a diagram of an energy application system with a partial cutaway view of a catheter showing both the working end and the connecting end and incorporating a preferred embodiment of the present invention;
FIG. 2 is a cross-sectional view of the working end of a first embodiment of a catheter in accordance with the invention depicting the electrodes in a fully extended position;
FIG. 2a is an end view of the working end of the first embodiment of the catheter taken along line 2a--2a of FIG. 2;

7m FIG. 3 is a cross-sectional view of the working end of the first embodiment depicting the electrodes in a fully retracted position;
FIG. 4 is a cross-sectional view of the working end of a second catheter in accordance with principles of the invention depicting the electrodes in a fully extended S position;
FIG. 4a is an end view of the second embodiment of the invention taken along line 4a-4a of FIG. 4;
FIG. 5 is a cross-sectional view of the working end of the second embodiment of the catheter of FIG. 4 depicting the electrodes in a fully retracted position;
FIG. 6 is a cross-sectional view of an anatomical structure containing the catheter of FIG. 2 with the electrodes in apposition with the anatomical structure;
FIG. 6a is an end view of the anatomical structure containing the catheter taken along line 6a-6a of FIG. 6;
FIGS. 7a through 7c are cross-sectional views of the anatomical structure containing a catheter in accordance with the first embodiment of the invention and depicting the anatomical structure at various stages of ligation;
FIG. 8 is a cross-sectional view of an anatomical structure containing a catheter in accordance with the second embodiment of the invention as depicted in FIG 4;
FIG. 8a is an end view of the anatomical structure containing the catheter taken along line 8a-8a of FIG. 8; and FIGS. 9a and 9b are cross-sectional views of the anatomical structure containing the catheter in accordance with the second embodiment of the invention and depicting the anatomical structure at various stages of ligation;
FIG. 10 is a cross-sectional view of the working end of a third embodiment of a catheter in accordance with the invention depicting the electrodes in a fully extended position;
FIG. 10a is an end view of the working end of the third embodiment of the catheter taken along line l0a-l0a of FIG. 10;
FIG. 11 is a cross-sectional view of the working end of the third embodiment depicting the electrodes in a fully retracted position;
FIG. 12 is a cross-sectional view of an anatomical structure containing the catheter of FIG. 10 with the electrodes in apposition with the anatomical structure;
FIG. 13 is a cross-sectional view of the anatomical structure containing the catheter of FIG. 10 where the anatomical structure is being ligated by the application of energy from the electrodes;
FIG. 14 is a cross-sectional view of an anatomical structure containing the catheter of FIG. 10 with the electrodes in apposition with the anatomical structure where external compression is being applied to reduce the diameter of the hollow structure before the application of energy from the electrodes to ligate the structure;
FIG. IS is a side view of another embodiment of an electrode catheter having a balloon and a coaxial fluid channel;
FIG. 16 is a partial cross-sectional view of the balloon and catheter of FIG.
15;
FIG. 17 is a cross-sectional view of an anatomical structure containing another embodiment of the catheter having a balloon and bowable arms with electrodes;
FIG. 18 is a side view of another embodiment of an electrode catheter having a covering spanning the splayed leads of the electrodes extended out the catheter; and FIG. 19 is a side view of another embodiment of an electrode catheter having a balloon and a coaxial fluid channel;
FIG. 20 is a side view of another embodiment of an electrode catheter having a balloon and a coaxial fluid channel;
FIG. 21 is a .partial cross-sectional side view of another embodiment of an electrode catheter having an expandable section; and FIG. 22 is a partial cross-sectional side view of the embodiment of an electrode catheter of FIG. 21 in an expanded condition.
DETAILED DESCRIPTION OF THE EMBODIMENTS
Turning now to the drawings with more particularity wherein like reference numerals indicate like or corresponding elements among the figures, shown in FIG. 1 is a catheter 10 for applying energy to an anatomical structure such as a vein. The catheter 10 includes an outer sheath 12 having a distal orifice 14 at its working end 15. The connector end 17 of the outer sheath 12 is attached to a handle 16 that includes an electrical connector 18 for interfacing with a power 5 source 22, typically an RF generator, and a microprocessor controller 23.
The power source 22 and microprocessor 23 are usually contained in one unit. The controller 23 controls the power source 22 in response to external commands and data from a sensor, such as a thermocouple, located at an intraluminal venous treatment site. In another embodiment, the user can select a constant power 10 output so that automated temperature control is not present and the user can manually adjust the power output in view of the temperature on a display readout.
The catheter 10 includes an expandable electrode device 24 (partially shown) that moves in and out of the outer sheath 12 by way of the distal orifice 14. The electrode device includes a plurality of electrodes which can be expanded by 15 moving the electrodes within the shaft, or by moving the outer shaft relative to the electrodes. Although FIG. 1 illustrates a plurality of electrodes surrounding a single central electrode, different electrode configurations will be described for the catheter.
Contained within the outer sheath 12 is an inner sheath 28 or inner member. A fluid port 21 communicates with the interior of the outer sheath 12.
The catheter 10 can be periodically flushed out with saline through the port 21.
The flushing fluid can travel between the outer sheath and the inner sheath.
The port also allows for the delivery of drug therapies. Flushing out the catheter prevents the buildup of biological fluid, such as blood, within the catheter 10.
The treatment area of the hollow anatomical structure such as a vein can be flushed with a fluid such as saline, or a dielectric fluid, in order to evacuate blood from the treatment area of the vein so as to prevent the formation of coagulum or thrombosis. The use of a dielectric fluid can minimize unintended heating effects away from the treatment area. The dielectric fluid prevents the current of RF
energy from flowing away from the vein wall.
In one embodiment, the catheter 10 includes a lumen which begins at the distal tip of the outer sheath 12 and runs substantially along the axis of the outer sheath 12 before terminating at the guide-wire port 20 of the handle 16. A
guide wire can be introduced through the lumen of the catheter 10 for use in guiding the 5 catheter to the desired treatment site. Where the catheter is sized to treat smaller veins, the outer diameter of the catheter may not allow for a fluid flush between the outer sheath 12 and the inner sheath 28. However, a fluid flush can be introduced through the lumen for the guide wire in such an embodiment.
Referring now to FIGS. 2, 2a, 3, 4, 4a and 5, the outer sheath 12 includes a shell 44 and a tip portion 46. To provide an atraumatic tip for the catheter 10 as it is manipulated through the vein, the tip 46 is preferably tapered inward at its distal end or is "nosecone" shaped. The tip 46, however, can have other shapes that facilitate tracking of the catheter 10 over a guide wire and through the bends in the venous vascular system. The nosecone-shaped tip 46 can, for example, be fabricated from a polymer having a soft durometer, such as 70 Shore A. The shell 44 comprises a biocompatible material having a low coefficient of friction.
In one configuration, the outer sheath 12 is sized to fit within a venous lumen and for example may be between 5 and 9 French, which corresponds to a diameter of between 1.7 mm (0.07 in) and 3.0 mm (1.2 in), or other sizes as appropriate.
The electrode device 24 contains a number of leads, including insulated primary leads 30 and, in some embodiments, a secondary lead 31. Preferably, the leads are connected to the power source 22 (FIG. 1) such that the polarity of the leads may be switched as desired. Alternately, a microprocessor controller can be used to switch the polarity, as well as control other characteristics of the power for the electrode device. Thus the electrode device can operate in either a bipolar or a monopolar configuration. When adjacent primary leads 30 have opposite polarity the electrode device 24 operates as a bipolar electrode device. When the primary leads 30 are commonly charged the electrode device 24 can operate as a monopolar electrode device. When the primary leads 30 are commonly charged, and a secondary lead 31 has an opposite polarity, the electrode device 24 operates as a bipolar electrode device. The embodiment of the invention shown in FIGS.

and 3 depict an electrode device 24 having four primary leads 30 and a secondary lead 31, while the embodiment of the invention shown in FIGS. 4 and 5 depict an electrode device 24 having only four primary leads. The invention is not limited to four primary leads 30; more or fewer leads may be used in either embodiment.
The number of leads can be dependent on the size or diameter of the hollow anatomical structure to be treated. The apposed electrodes should be kept within a certain distance of one another. Larger vessels may require more primary leads to ensure proper current density and proper heat distribution.
The insulation on each of the leads 30, 31 may be removed at the distal end 32, 33 to expose the conductive wire. In the first configuration as shown in FIGS. 2, 2a, and 3, the electrode 34 has a hemispherical shape. In a second configuration, the electrode can have either a generally spherical shape or a spoon shape. As shown in FIGS. 6 and 6a , the electrodes have a spoon shape which can be combined to form a sphere or other shape so as to minimize its profile when the vein collapses. The electrodes 34 are either integrally formed at the distal end 32, soldered, or otherwise formed to the distal end of each primary lead 30. It is to be understood that when the distal end 32 is referred to as acting as an electrode, this is not limited to where the electrode 34 is integrally formed at the distal end 32. For example, the distal end can apply energy to the surrounding tissue where there is an electrode integrally formed at the distal end, or where an electrode is separately soldered to the distal end, or where there is another energy delivery device located at the distal end. The electrode 34 typically has a diameter greater than the diameter of the primary Lead 30. For example, the primary lead 30 may have a diameter ranging from 0.18 mm (0.007 in.) to 0.28 mm (0.011 in.), while the electrode 34 has a diameter of 0.36 mm (0.014 in.) to 0.51 mm (0.020 in.). The primary leads 30 and the electrodes 34 are preferably made from a biologically-compatible material such as stainless steel. The insulation surrounding the primary leads 30 generally has a thickness of between 0.03 mm (0.001 in.) and 0.06 mm (0.0025 in.), resulting in a combined lead-insulation diameter of between 0.23 mm (0.009 in.) and 0.41 mm (0.016 in.). In an alternate configuration, as shown in FIGS. 2 and 3, each primary lead 30 is strip-shaped with a width from 0. 76 mm (0.03 in. ) to 1. 0 mm (0.04 in) and a thickness of approximately 0.13 mm (0.005 in.), while the. secondary lead 31 is typically tubular-shaped. It should be noted that these dimensions are provided for illustrative purposes, and not by way of limitation. A hemispherical electrode 34 is shaped at the distal end, as for example, by sanding down a sixteenth-inch ( 1.6 mm) diameter sphere which is soldered to the distal end 32 of the primary lead 30. The electrodes can also be constructed by stamping the desired shape or configuration from the conductive lead. The electrode is integral with the lead, and the remainder of the lead is insulated. The distal end 33 of the secondary lead 31 preferably includes a generally spherically-shaped electrode 35.
An alignment device 36 arranges the leads 30, 31 such that they are mounted to the catheter at only their proximal ends and so that separation is maintained between the leads within, and distal to the alignment device. The leads can form cantilevers when mounted on the alignment, device. A preferred configuration of the alignment device 36 includes a plurality of off center, axially-aligned lumina 38 which are substantially symmetrically positioned relative to the axis of the alignment device 36. The alignment device 36 is formed, for example, by extruding the plurality of axially-aligned lumina 38 through a solid cylinder composed of a dielectric material, such as polyamide. Each lead 30 passes through an individual off center lumen 38 and exits out the rear of the alignment device 36. The alignment device 36 may further include a central lumen 48 that may be aligned with the axis. In some embodiments the central lumen 48 is used for accepting a guide wire or for the delivery or perfusion of medicant and cooling solution to the treatment area during application of RF energy. In other embodiments, the central lumen 48 may be used for the secondary lead 31. The alignment device 36 may also further include an auxiliary lumen 47 for additional leads, such as the leads of a thermocouple used as a temperature sensor. The alignment device 36 comprises a dielectric material to prevent or minimize any coupling effect the leads 30, 31 may have with each other and, if present, the guide wire. The length of the alignment device is, for example, 12.5 mm (0.5 in.) to 19.0 mm (0.75 in.) in one embodiment. However, these dimensions are provided for purposes of illustration and not by way of limitation.
In the embodiment of the invention shown in FIGS. 2, 2a and 3, the inner sheath 28 is attached to the alignment device 36 and extends beyond the rear 37 of the alignment device. Preferably, the inner sheath 28 completely surrounds the exterior wall of the alignment device 36 and is mounted to it by adhesive or press fit or in other manner such that it remains in a fixed position relative to the inner sheath. The inner sheath and alignment device can act as an inner member relative to the outer sheath. The inner sheath 28 comprises a biocompatible material with a low coefficient of friction. The inner sheath 28 provides a pathway for the interconnection between the leads 30, 31 and the electrical connector 18 (FIG. 1). This interconnection may occur in any of several ways.
The leads 30, 31 themselves may be continuous and run the entire length of the inner sheath 28. In the alternative (not shown), the positively charged leads 30, 31 may couple with a common positively charged conductor housed in the inner sheath 28. Likewise, the negatively charged leads 30, 31 may couple with a common negative conductor. Preferably, the leads 30, 31 are connected to a conductor that allows for the polarity of the leads to be switched. The conductor may comprise, for example, a 36 gauge copper lead with a polyurethane coating.
The coupling may occur at any point within the inner sheath 28. To reduce the amount of wire contained in the catheter, it is advantageous to couple the leads 30, 31 at the point where the leads exit the rear 37 of the alignment device 36.
To add further stability to the electrode device 24, it is preferred that bonding material 40 surround the leads 30, 31 at the front end of the alignment device 36.
In this embodiment, the leads 30, 31 exit through the distal orifice 14 as the outer sheath 12 is retracted backwards over the alignment device 36. The inwardly tapered tip 46 impedes the retracting movement of the outer sheath 12 to prevent the exposure of the alignment device 36.

FIG. 3 shows the leads 30 and 31 in the retracted position where all leads are within the nosecone-shaped tip portion 46 and the outer shell 44. The alignment device 36 has been moved relative to the outer shell 44. The soft nosecone provides an atraumatic tip for when the catheter is maneuvered through 5 the tortuous venous system. The electrode at the distal end of the secondary lead 31 can be sized to approximately the same size as the opening formed in the nosecone 46. The nosecone forms a closed atraumatic tip together with the electrode of the secondary lead when the alignment device is retracted into the outer sheath of the catheter. This can present an atraumatic tip even where the 10 nosecone is not constructed from a material having a soft durometer.
Referring now to FIGS. 4 and 5, in another embodiment, the alignment device 36 is attached to the outer sheath 12 and thereby remains immobile in relation to it. The inner sheath 28 is movably positioned at the rear of the alignment device 36 and again provides a pathway for the interconnection between 15 the primary leads 30 and the electrical connector 18 (FIG. 1). In some embodiments the inner sheath 28 contains a guide-wire tube 49 that runs the entire length of the inner sheath. The guide-wire tube 49 is aligned to communicate with the central lumen 48 of the alignment device 36 at one end and with the guide-wire port 20 (FIG. 1) at the other end. The primary leads 30 may be continuous and run the entire length of the inner sheath 28 or they may be coupled to common leads as previously described. The primary leads 30 are secured to the front end 27 of the inner sheath 28, as for example with a potting material 50, so that the movement of the inner sheath 28 results in a corresponding movement of the primary leads 30 through the lumina 38 of the alignment device 36. In this embodiment, the primary leads 30 are not secured to the alignment device 36 and in essence are free-floating leads in the axial direction. The primary leads travel through the alignment device 36 and exit through the distal orifice 14 as the front end of the inner sheath 28 is moved toward the rear 37 of the alignment device 36.
In the above embodiments, the primary leads 30 are formed, e. g. , arced or bent, to move away from each other and thereby avoid contact. The "distal portion" of the primary leads 30 is the portion of the lead which extends from the front end of the alignment device 36 when the leads are fully extended through the distal orifice 14. It is preferred that the distal portions 42 are formed to move radially outward from each other relative to the axis of the alignment device and form a symmetrical arrangement. This is shown in both the embodiments of FIG. 2a and FIG. 4a. The degree of arc or bend in the primary leads 30 may be any that is sufficient to radially expand the leads as they exit the outer sheath 12 through the distal orifice 14. It is essential that the degree of the arc or bend be sufficient to provide enough force so that the primary leads 30 expand through blood and the electrodes 34 come in apposition with the vein wall. The electrodes are preferably partially embedded in the vein wall to assure full contact. The rounded portion of the electrode is embedded into the vein wall to achieve full 15 surface apposition so that the entire uninsulated surface area of the electrode is in contact with venous tissue for effective current distribution. The surface area of the electrodes in contact with the venous tissue preferably is sufficient to avoid a high current density which may lead to spot heating of the venous tissue. The heating effect is preferably distributed along a circumferential band of the vein.
The apposed electrodes should be spaced no more than 4 or 5 millimeters from one another along the circumference of the vein. Thus, the electrode arrangement is related to the size or diameter of the vein being treated. Other properties of the primary leads 30, such as lead shape and insulation thickness, affect the push force of the lead and the degree of arc or bend must be adjusted to compensate for these factors. For example, in one configuration of the electrode device 24, a wire having a diameter of between 0.18 mm (0.007 in) and 0.28 mm (0.011 in) with a total insulation thickness of between 0.05 mm (0.002 in) to 0.13 mm (0.005 in} is arced or bent at an acute angle to provide sufficient apposition with the anatomical structure. It is to be understood that these dimensions are provided for illustrative purposes, and not by way of limitation.
Other techniques for expanding the leads outwardly once they have been extended from the working end of the catheter may be possible. For example, the leads may be straight but are mounted in the alignment device at an angle such that they are normally directed outward.
For increased appositional force, it is preferred that the primary leads 30 be strip-shaped, that is rectangular in cross section, with dimensions, for example, of a width from 0.76 mm (0.030 in. ) to 1.0 mm (0.039 in) and a thickness of approximately 0.13 mm (0.005 in.). The rectangular cross section provides increased resistance to bending in the width dimension but allows bending more freely in the thickness dimension. This strip-shaped configuration of the primary leads 30 is shown in FIGS. 2, 2a, and 3 and provides for increased stability in the lateral direction while allowing the necessary bending in the radial direction. In FIGS. 2, 2a, and 3, each primary lead comprises a rectangular cross section mounted in relation to the catheter such that the thinner dimension of the rectangular cross section is aligned with the direction of expansion of the lead.
The leads are less likely to bend sideways when expanded outward, and a uniform spacing between leads is more assured. Uniform spacing promotes uniform heating around the venous tissue which is in apposition with the electrodes at the distal ends of the leads.
The length of the distal portion of the leads 30 also affects the configuration of the electrode device 24. The maximum distance between two mutually opposed electrodes 34; i.e., the effective diameter of the electrode device 24, is affected by the bend degree and length of the distal portion 42.
The longer the length of the distal portion 42 the greater the diameter of the electrode 25 device 24. Accordingly, by changing the distal portion 42 length and arc or bend degree, the catheter 10 can be configured for use in differently sized anatomical structures.
Different numbers of leads 30, 31 can be employed with the catheter. The number of leads 30, 31 is limited by the diameter of the alignment device 36 and the number of lumina 36, 38, 47 that can be extruded through the alignment device. In a bipolar configuration, an even number of primary leads 30 are preferably available to form a number of oppositely charged electrode pairs.
The electrodes in apposition with the anatomical structure should be maintained within a certain distance of each other. In a monopolar configuration, any number of 5 commonly charged leads 30 can be present. In the monopoiar mode, distribution of RF energy through the anatomical tissue is obtained by creating a return path for current through the tissue by providing a return device at a point external from the tissue, such as a large metal pad.
Now referring again to FIG. 1, an actuator 25 controls the extension of the electrode device 24 through the distal orifice 14. The actuator 25 may take the form of a switch, lever, threaded control knob, or other suitable mechanism, and is preferably one that can provide fine control over the movement of the outer sheath 12 or the inner sheath 28, as the case may be. In one embodiment of the invention, the actuator 25 (FIG. 1) interfaces with the outer sheath 12 (FIG.
2, 2a and 3) to move it back and forth relative to the inner sheath 28. In another embodiment the actuator 25 (FIG. 1) interfaces with the inner sheath 28 (FIGS.
4, 4a and 5) to move it back and forth relative to the outer sheath 12. The relative position between the outer sheath and inner sheath is thus controlled, but other control approaches may be used.
Referring again to FIGS. 2, 2a, 3, 4, 4a and 5, the catheter 10 includes a temperature sensor 26, such as a thermocouple. The temperature sensor 26 is mounted in place on an electrode 34 so that the sensor 26 is nearly or is substantially flush with the exposed surface of the electrode 34. The sensor 26 is shown in the drawings as protruding from the electrodes for clarity of illustration only. The sensor 26 senses the temperature of the portion of the anatomical tissue that is in apposition with the exposed electrode surface. Monitoring the temperature of the anatomical tissue provides a good indication of when shrinkage of the tissue is ready to begin. A temperature sensor 26 placed on the electrode facing the anatomical tissue provides an indication of when shrinkage occurs (70°
C or higher) and when significant amounts of heat-induced coagulum may begin to form on the electrodes. Therefore maintaining the temperature above 70 degrees Centigrade produces a therapeutic shrinkage of the anatomical structure.
Application of the RF energy from the electrodes 34 is halted or reduced when,the monitored temperature reaches or exceeds the specific temperature that was selected by the operator, typically the temperature at which anatomical tissue begins to cauterize. The temperature sensor 26 interfaces with the controller (FIG. 1) through a pair of sensor leads 45 which preferably run through the auxiliary lumen 47 and then through the inner sheath 28. The signals from the temperature sensor 26 are provided to the controller 23 which controls the magnitude of RF energy supplied to the electrodes 34 in accordance with the selected temperature criteria and the monitored temperature. Other techniques such as impedance monitoring, and ultrasonic pulse echoing can be utilized in an automated system which shuts down or regulates the application of RF energy from the electrodes to the venous section when sufficient shrinkage of the vein is 15 detected and to avoid overheating the vein. Impedance can be used to detect the onset of coagulum formation.
Referring now to FIGS. 6, 6a and 7a through 7c, in the operation of one embodiment of the catheter 10, the catheter is inserted into a hollow anatomical structure, such as a vein 52. The catheter is similar to the embodiment discussed in connection with FIGS. 2 and 3. The catheter 10 further includes an external sheath 60 through which a fluid can be delivered to the treatment site. In this embodiment, the fluid port (not shown) communicates with the interior of the external sheath 60, and fluid is delivered from between the external sheath 60 and the outer sheath 12. The external sheath 60 surrounds the outer sheath 12 to form a coaxial channel through which fluid may be flushed.
Fluoroscopy, ultrasound, an angioscope imaging technique, or other technique may be used to direct the specific placement of the catheter and confirm the position in the vein. The actuator (not shown) is then operated to shift the outer sheath relative to the inner sheath by either retracting the outer sheath 12 backward or advancing the inner sheath 28 forward to expose the leads 30, 31 through the distal orifice 14. As the leads 30, 31 exit the distal orifice 14, the primary leads 30 expand radially outward relative to the axis of the alignment device 36, while the secondary lead 31 remains substantially linear. The primary leads 30 continue to move outward until apposition with the vein wall S4 occurs S and the outward movement of the primary leads 30 is impeded. The primary leads 30 contact the vein along a generally circumferential band of the vein wall S4. This outward movement of the primary leads 30 occurs in a substantially symmetrical fashion. As a result, the primary-lead electrodes 34 are substantially evenly spaced along the circumferential band of the vein wall S4. The central-10 lead electrode 3S is suspended within the vein S2 without contacting the vein wall S4.
When the electrodes 34 are positioned at the treatment site of the vein, the power supply 22 is activated to provide suitable RF energy. One suitable frequency is S 10 kHz. One criterion used in selecting the frequency of the energy 1S to be applied is the control desired over the spread, including the depth, of the thermal effect in the venous tissue. Another criterion is compatibility with filter circuits for eliminating RF noise from thermocouple signals.
In bipolar operation, the primary leads 30 are initially charged such that adjacent leads are oppositely charged while the secondary lead is electrically 20 neutral. These multiple pairs of oppositely charged leads 30 form active electrode pairs to produce an RF field between them. Thus, discrete RF fields are set up along the circumferential band of the vein wall S4. These discrete fields form a symmetrical RF field pattern along the entire circumferential band of the vein wall S4, as adjacent electrodes 34 of opposite polarity produce RF fields between each 2S other. A uniform temperature distribution can be achieved along the vein wall being treated.
The RF energy is converted within the adjacent venous tissue into heat, and this thermal effect causes the venous tissue to shrink, reducing the diameter of the vein. A uniform temperature distribution along the vein wall being treated avoids the formation of hot spots in the treatment area while promoting controlled uniform reduction in vein diameter. The thermal effect produces structural transfiguration of the collagen fibrils in the vein. The collagen fibrils shorten and thicken in cross-section in response to the heat from the thermal effect. As shown in FIG 7a, the energy causes the vein wall 54 to collapse around the primary-lead electrodes 34. The wall 54 continues to collapse until further collapse is impeded by the electrodes 34. The electrodes are pressed farther and farther together by the shrinking vein wall 54 until they touch and at that point, further collapse or ligation of the wall 54 is impeded. Upon collapse of the vein wall 54 around the primary-lead electrodes 34, the polarity of the primary-lead electrodes is switched so that all primary-lead electrodes are commonly charged. The switching of polarity for the leads need not be instantaneous. The application of RF energy can be ceased, the polarity switched, and then RF energy is applied again at the switched polarity. The secondary-lead electrode 35 is then charged so that its polarity is opposite that of the primary-lead electrodes 34. The RF field is set up between the primary-lead electrodes 34 and the secondary-lead electrode 35.
The catheter 10 is then pulled back while energy is applied to the electrode device. As shown in FIG. 7b, while the catheter 10 is being pulled back, the primary-lead electrodes 34 remain in apposition with the vein wall 54 while the secondary-lead electrode 35 comes in contact with the portion of the vein wall previously collapsed by the primary-lead electrodes 34. Accordingly, RF energy passes through the vein wall 54 between the primary-lead electrodes 34 and the secondary-lead electrode 35 and the vein wall continues to collapse around the secondary-lead electrode 35 as the catheter 10 is being retracted. As shown in FIG. 7c, ligation in accordance with this method results in an occlusion along a 25 length of the vein 52. A lengthy occlusion, as opposed to an acute occlusion, is stronger and less susceptible to recanalization.
A similar result is achieved when the catheter 10 having both primary and secondary leads is operated in a monopolar manner. In a monopolar operation, the secondary-lead electrode 35 remains neutral, while the primary leads 30 are commonly charged and act in conjunction with an independent electrical device, such as a large low-impedance return pad (not shown) placed in external contact with the body, to form a series of discrete RF fields. These RF fields are substantially evenly spaced around the circumference of the vein and travel along the axial length of the vein wall causing the vein wall to collapse around the 5 primary-lead electrodes. Upon collapse of the vein wall, the secondary-lead electrode is charged to have the same polarity as that of the primary-lead electrodes. The electrode device is retracted and the vein wall collapses as described in the bipolar operation.
In either bipolar or monopolar operation the application of RF energy is substantially symmetrically distributed through the vein wall, regardless of the diameter of the vein 52. This symmetrical distribution of RF energy increases the predictability and uniformity of the shrinkage and the strength of the occlusion.
Furthermore, the uniform distribution of energy allows for the application of RF
energy for a short duration and thereby reduces or avoids the formation of heat-15 induced coagulum on the electrodes 34. The leads, including the non-convex outer portion of the electrode, are insulated to further prevent heating of the surrounding blood.
Fluid can be delivered before and during RF heating of the vein being treated through a coaxial channel formed between the external sheath 60 and the outer sheath 12. It is to be understood that another lumen can be formed in the catheter to deliver fluid to the treatment site. The delivered fluid displaces or exsanguinates blood from the vein so as to avoid heating and coagulation of blood. Fluid can continue to be delivered during RF treatment to prevent blood from circulating back to the treatment site. The delivery of a dielectric fluid 25 increases the surrounding impedance so that RF energy is directed into the tissue of the vein wall.
Referring now to FIGS. 8, 8a, 9a and 9b, in the operation of an alternate embodiment of the catheter 10 that may be used with a guide wire 53. As in the previous embodiment, the catheter 10 is inserted into a hollow anatomical structure, such as a vein 52. The guide wire 53 is advanced past the point where energy application is desired. The catheter 10 is then inserted over the guide wire 53 by way of the central lumen 48 and the guide wire tube 49 (FIG. 4) and is advanced over the guide wire through the vein to the desired point. The guide wire 53 is typically pulled back or removed before RF energy is applied to the electrode device 24.
The actuator 25 (FIG. 1) is then manipulated to either retract the outer sheath 12 backward, or advance the inner sheath 28 forward to expose the leads 30 through the distal orifice 14. The leads 30 exit the distal orifice i4 and expand radially outward relative to the axis of the alignment device 36. The leads 30 continue to move outward until apposition with the vein wall 54 occurs. The leads 30 contact the vein along a generally circumferential band of the vein wall 54. This outward movement of the leads occurs in a substantially symmetrical fashion. As a result, the electrodes 34 are substantially evenly spaced along the circumferential band of the vein wall 54. Alternately, the electrodes can be spaced apart in a staggered fashion such that the electrodes do not lie along the same plane. For example, adjacent electrodes can extend different lengths from the catheter so that a smaller cross-sectional profile is achieved when the electrodes are collapsed toward one another.
When the electrodes 34 are positioned at the treatment site of the vein, the power supply 22 is activated to provide suitable RF energy to the electrodes 34 so that the catheter 10 operates in either a bipolar or monopolar manner as previously described. As shown in FIGS. 9a and 9b, the energy causes the vein wall 54 to collapse around the electrodes 34 causing the leads to substantially straighten and the electrodes to cluster around each other. The wall 54 continues to collapse until further collapse is impeded by the electrodes 34 (FIG. 9b). At this point the application of energy may cease. The electrodes can be configured to form a shape with a reduced profile when collapsed together. The electrodes can also be configured and insulated to continue applying RF energy after forming a reduced profile shape by the collapse of the vein wall. The catheter 10 can be pulled back to ligate the adjacent venous segment. If a temperature sensor 26 is included, the application of energy may cease prior to complete collapse if the temperature of the venous tissue rises above an acceptable level as defined by the controller 23.
Where the catheter includes a fluid delivery lumen (not shown), fluid can be delivered before and during RF heating of the vein being treated. The fluid can displace blood from the treatment area in the vein to avoid the coagulation of blood. The fluid can be a dielectric medium. The fluid can include an anticoagulant such as heparin which can chemically discourage the coagulation of blood at the treatment site.
After completing the procedure for a selected venous section, the actuator mechanism causes the primary leads to return to the interior of the outer sheath 12. Either the outer sheath or the inner sheath is moved to change the position of the two elements relative to one another. Once the leads 30 are within the outer sheath 12, the catheter 10 may be moved to another venous section where the ligation process is repeated. Upon treatment of all venous sites, the catheter 10 is removed from the vasculature. The access point of the vein is then sutured closed, or local pressure is applied until bleeding is controlled.
Another embodiment of the catheter is illustrated in FIG. 10. The inner member or sheath 28 is contained within the outer sheath 12. The inner sheath is preferably constructed from a flexible polymer such as polyimide, polyethylene, or nylon, and can travel the entire length of the catheter. The majority of the catheter should be flexible so as to navigate the tortuous paths of the venous system. A hypotube having a flared distal end 33 and a circular cross-sectional shape is attached over the distal end of the inner sheath 28. The hypotube is preferably no more than about two to three centimeters in length. The hypotube acts as part of the conductive secondary lead 31. An uninsulated conductive electrode sphere 35 is slipped over the hypotube. The flared distal end of the hypotube prevents the electrode sphere from moving beyond the distal end of the hypotube. The sphere is permanently affixed to the hypotube, such as by soldering the sphere both front and back on the hypotube. The majority or the entire surface of the spherical electrode 35 remains uninsulated. The remainder of the hypotube is preferably insulated so that the sphere-shaped distal end can act as the electrode. For example, the hypotube can be covered with an insulating material such as a coating of parylene. The interior lumen of the hypotube is lined by the inner sheath 28 which is attached to the flaired distal end of the 5 hypotube by adhesive such as epoxy.
Surrounding the secondary lead 31 and sphere-shaped electrode 35 are a plurality of primary leads 30 which preferably have a flat rectangular strip shape and can act as arms. As illustrated in FIG. 11, the plurality of primary leads are preferably connected to common conductive rings 62. This configuration 10 maintains the position of the plurality of primary leads, while reducing the number of internal electrical connections. The rings 62 are attached to the inner sheath 28. The position of the rings and the primary leads relative to the outer sheath follows that of the inner sheath. As earlier described, the hypotube of the secondary lead 31 is also attached to the inner sheath 28. Two separate 15 conductive rings can be used so that the polarity of different primary leads can be controlled separately. For example, adjacent primary leads can be connected to one of the two separate conductive rings so that the adjacent leads can be switched to have either opposite polarities or the same polarity. The rings are preferable spaced closely together, but remain electrically isolated from one another along 20 the inner sheath. Both the rings and the hypotube are coupled with the inner sheath, and the primary leads 30 that are connected to the rings move together with and secondary lead while remaining electrically isolated from one another.
Epoxy or another suitable adhesive can be used to attach the rings to the inner sheath. The primary leads from the respective rings each alternate with each other 25 along the circumference of the inner sheath. The insulation along the underside of the leads prevents an electrical short between the rings.
The ring and primary leads are attached together to act as cantilevers where the ring forms the base and the rectangular primary leads operate as the cantilever arms. The leads 30 are connected to the ring and are formed to have an arc or bend such that the leads act as arms which tend to spring outwardly away from the catheter and toward the surrounding venous tissue. Insulation along the underside of the leads and the rings prevents unintended electrical coupling between the leads and the opposing rings. Alternately, the leads are formed straight and connected to the ring at an angle, such that the leads tend to expand or spring radially outward from the ring. The angle at which the leads are attached to the ring should be sufficient to force the primary distal ends and electrodes 34 through blood and into apposition with the vein wall. Other properties of the primary leads 30, such as lead shape and insulation thickness, affect the push force of the lead and the degree of arc or bend must be adjusted to compensate for these factors. The rectangular cross section of the leads 30 can provide increased stability in the lateral direction while allowing the necessary bending in the radial direction. The leads 30 are less likely to bend sideways when expanded outward, and a uniform spacing between leads is more assured. Uniform spacing between the leads 30 and the distal ends promotes uniform heating around the vein by the 15 electrodes 34.
The distal ends of the primary leads 30 are uninsulated to act as electrodes 34 having a spoon or hemispherical shape. The leads can be stamped to produce an integral shaped electrode at the distal end of the lead. The uninsulated outer portion of the distal end electrode 34 which is to come into apposition with the wall of the anatomical structure is preferably rounded and convex. The flattened or non-convex inner portion of the distal end is insulated to minimize any unintended thermal effect, such as on the surrounding blood in a vein. The distal end electrodes 34 are configured such that when the distal ends are forced toward the inner sheath 12, as shown in FIG. 10a, the distal ends combine to form a 25 substantially spherical shape with a profile smaller than the profile for the spherical electrode 35 at the secondary distal end.
The outer sheath 12 can slide over and surround the primary and secondary leads 30, 31. The outer sheath 12 includes an orifice which is dimensioned to have approximately the same size as the spherical electrode 35 at the secondary distal end which functions as an electrode. A close or snug fit between the electrode 35 at the secondary distal end and the orifice of the outer sheath 12 is achieved. This configuration provides an atraumatic tip for the catheter. The electrode 35 secondary distal end is preferably slightly larger than the orifice.
The inner diameter of the outer sheath 12 is approximately the same as the reduced profile of the combined primary distal end electrodes 34. The diameter of the reduced profile of the combined primary distal end electrodes 34 is preferably less than the inner diameter of the outer sheath.
A fluid port (not shown) can communicate with the interior of the outer sheath 12 so that fluid can be flushed between the outer sheath I2 and the inner sheath 28. Alternately, a fluid port can communicate with a central lumen 48 in the hypotube which can also accept a guide wire. As previously stated, the catheter 10 can be periodically flushed with saline which can prevent the buildup of biological fluid, such as blood, within the catheter 10. A guide wire can be introduced through the lumen 48 for use in guiding the catheter to the desired treatment site. As previously described, a fluid can be flushed or delivered though the lumen as well. If a central lumen is not desired, the lumen of the hypotube can be filled with solder.
Preferably, the primary leads 30 and the connecting rings are connected to a power source 22 such that the polarity of the leads may be switched as desired.
This allows for the electrode device 24 to operate in either a bipolar or a monopolar configuration. When adjacent primary leads 30 have opposite polarity, a bipolar electrode operation is available. When the primary leads 30 are commonly charged a monopolar electrode operation is available in combination with a large return electrode pad placed in contact with the patient. When the primary leads 30 are commonly charged, and a secondary lead 31 has an opposite polarity, a bipolar electrode operation is available. More or fewer leads may be used. The number of leads can be dependent on the size or diameter of the hollow anatomical structure to be treated.
Although not shown, it is to be understood that the catheter 10 can include a temperature sensor, such as a thermocouple, mounted in place on the distal end or electrode 34 so that the sensor is substantially flush with the exposed surface of the electrode 34. The sensor senses the temperature of the portion of the anatomical tissue that is in apposition with the exposed electrode surface.
Application of the RF energy from the electrodes 34 is halted or reduced when the monitored temperature reaches or exceeds the specific temperature that was selected by the operator, such as the temperature at which anatomical tissue begins to cauterize. Other techniques such as impedance monitoring, and ultrasonic pulse echoing can be utilized in an automated system which shuts down or regulates the application of RF energy from the electrodes to the venous section when sufficient shrinkage of the vein is detected and to avoid overheating the vein.
Referring now to FIGS. 12 through 14, in the operation of one embodiment of the catheter 10, the catheter is inserted into a hollow anatomical structure, such as a vein. Fluoroscopy, ultrasound, an angioscope imaging technique, or another technique may be used to direct and confirm the specific placement of the catheter in the vein. The actuator is then operated to retract the outer sheath 12 to expose the leads 30, 31. As the outer sheath no longer restrains the leads, the primary leads 30 move outward relative to the axis defined by the outer sheath, while the secondary iead 31 remains substantially linear along the axis defined by the outer sheath. The primary leads 30 continue to move outward until the distal end electrode 34 of the primary leads are placed in apposition with the vein wall 54 occurs and the outward movement of the primary leads 30 is impeded. The primary leads 30 contact the vein along a generally circumferential area of the vein wall 54. This outward movement of the primary leads 30 occurs in a substantially symmetrical fashion so that the primary distal end electrodes 34 are substantially evenly spaced. The central-lead electrode 35 is suspended within the vein without contacting the vein wall 54.
When the electrodes 34 are positioned at the treatment site of the vein, the power supply 22 is activated to provide suitable RF energy. In a bipolar operation, the primary leads 30 are initially charged such that adjacent leads are oppositely charged while the secondary lead is electrically neutral. These multiple pairs of oppositely charged leads 30 form active electrode pairs to produce an RF
field between them, and form a symmetrical RF field pattern along a circumferential band of the vein wall to achieve a uniform temperature distribution along the vein wall being treated.
The RF energy produces a thermal effect which causes the venous tissue to shrink, reducing the diameter of the vein. As shown in FIG 13, the energy causes the vein wall 54 to collapse until further collapse is impeded by the electrodes 34.
The electrodes are pressed closer together by the shrinking vein wall. The electrodes 34 are pressed together to assume a reduced profile shape which is sufficiently small so that the vein is effectively ligated. Upon collapse of the vein wall 54 around the primary-lead electrodes 34, the polarity of the primary-lead electrodes is switched so that all of the primary-lead electrodes are commonly charged. The secondary-lead electrode 35 is then charged so that its polarity is opposite that of the primary-lead electrodes 34. Where the primary electrodes and the secondary electrode 35 are spaced sufficiently close together, when the vein wail collapses around the primary lead electrodes, the electrode at the distal end of the secondary lead can also come into contact with the a portion of the vein wall so that an RF field is created between the primary electrodes 34 and the secondary electrode 35.
The catheter 10 is pulled back to ensure apposition between the electrodes at the distal ends of the leads and the vein wall. When the catheter 10 is being pulled back, the primary-lead electrodes 34 remain in apposition with the vein wall 54 while the secondary-lead electrode 35 comes in contact with the portion of the vein wall previously collapsed by the primary-lead electrodes 34. RF
energy passes through the venous tissue between the primary-lead electrodes 34 and the secondary-lead electrode 35. Ligation as the catheter is being retracted produces a lengthy occlusion which is stronger and less susceptible to recanalization than an acute point occlusion.

In a monopolar operation, the secondary-lead electrode 35 remains neutral, while the primary leads 30 are commonly charged and act in conjunction with an independent electrical device, such as a large low-impedance return pad (not shown) placed in external contact with the body, to form RF fields substantially 5 evenly spaced around the circumference of the vein. The thermal effect produced by those RF fields along the axial length of the vein wall causes the vein wall to collapse around the primary-lead electrodes. Upon collapse of the vein wall, the secondary-lead electrode is charged to have the same polarity as that of the primary-lead electrodes. The electrode device is retracted as described in the 10 bipolar operation.
In either bipolar or monopolar operation the application of RF energy is substantially symmetrically distributed through the vein wall. As previously described, the electrodes should be spaced no more than 4 or 5 millimeters apart along the circumference of the vein, which defines the target vein diameter for a 15 designed electrode catheter. Where the electrodes are substantially evenly spaced in a substantially symmetrical arrangement, and the spacing between the electrodes is maintained, a symmetrical distribution of RF energy increases the predictability and uniformity of the shrinkage and the strength of the occlusion.
As shown in FIG. 14, after the electrodes 34 come into apposition with the 20 vein wall (FIG. 12), and before the energy is applied to ligate the vein (FIG. 13), an external tourniquet, such as an elastic compressive wrap or an inflatable bladder with a window transparent to ultrasound, is used to compress the anatomy, such as a leg, surrounding the structure to reduce the diameter of the vein. Although the compressive force being applied by the tourniquet may 25 effectively ligate the vein, or otherwise occlude the vein by flattening the vein, for certain veins, this compressive force will not fully occlude the vein. A fixed diameter electrode catheter in this instance would not be effective. The electrodes 34 which are expanded outward by the formed leads 30 can accommodate this situation.

The reduction in vein diameter assists in pre-shaping the vein to prepare the vein to be molded to a ligated state. The use of an external tourniquet also exsanguinates the vein and blood is forced away from the treatment site.
Coagulation of blood during treatment can be avoided by this procedure. Energy is applied from the electrodes to the exsanguinated vein, and the vein is molded to a sufficiently reduced diameter to achieve ligation. The external tourniquet can remain in place to facilitate healing.
The catheter can be pulled back during the application of RF energy to ligate an extensive section of a vein. In doing so, instead of a single point where the diameter of the vein has been reduced, an extensive section of the vein has been painted by the RF energy from the catheter. Retracting the catheter in this manner produces a lengthy occlusion which is less susceptible to recanalization.
The combined use of the primary and secondary electrodes can effectively produce a reduced diameter along an extensive length of the vein. The catheter can be moved while the tourniquet is compressing the vein, of after the tourniquet is removed.
Where the catheter includes a fluid delivery lumen, fluid can be delivered to the vein before RF energy is applied to the vein. The delivered fluid displaces blood from the treatment site to ensure that blood is not present at the treatment site, even after the tourniquet compresses the vein.
Where the tourniquet is an inflatable bladder with a window transparent to ultrasound, an ultrasound transducer is used to monitor the flattening or reduction of the vein diameter from the compressive force being applied by the inflating bladder. The window can be formed from polyurethane, or a stand-off of gel contained between a polyurethane pouch. A gel can be applied to the window to facilitate ultrasound imaging of the vein by the transducer. Ultrasound visualization through the window allows the operator to locate the desired venous treatment area, and to determine when the vein has been effectively ligated or occluded. Ultrasound visualization assists in monitoring any pre-shaping of the vein in preparation of being molded into a ligated state by the thermal effect produced by the RF energy from the electrodes.
After completing the procedure for a selected venous section, the actuator causes the leads 30 to return to the interior of the outer sheath 12. Once the leads 30 are within the outer sheath 12, the catheter 10 may be moved to another venous section where the ligation process is repeated.
In another embodiment, as illustrated in FIG. 15, a balloon 64 is located on the catheter, and can be inflated through ports 66 to occlude the vein. The inflated balloon obstructs blood flow and facilitates the infusion of a high-impedance fluid to the vein in order to reduce the occurrence of coagulation by directing the energy into the vein wall. The inflation of the balloon to occlude the vein before the application of energy can obviate the use of the tourniquet to occlude the vein. Furthermore, this also allows the vein to be occluded even for the deep veins where a compressive tourniquet may not be able to compress the 15 vein to occlusion. It is to be understood that other mechanisms can be used to expand the diameter of the catheter to create an impermeable barrier that occludes the vein.
Fluid 61 can be delivered after inflation of the balloon 64 and before the RF heating of the vein being treated through a coaxial channel 62 formed between the external sheath 60 and the outer sheath 12. It is to be understood that another lumen can be formed in the catheter to deliver fluid to the treatment site.
For example, the lumen through which the guide wire is passed may be used for the delivery of fluid. The delivered fluid displaces or exsanguinates the remaining blood from the treatment area of the vein so as to avoid heating and coagulation of blood. Fluid can continue to be delivered during RF treatment to prevent blood from circulating back to the treatment site. The delivery of a high-dielectric fluid increases the surrounding impedance so that RF energy is directed into the tissue of the vein wall. Less energy is used because the energy is directed to the target;
i.e., the vein wall, rather than being dissipated in the blood. Therefore, the vein wall can reach the desired temperature more rapidly than in the case where energy is permitted to reach the blood, which has a cooling effect. Additionally, blood clotting is avoided with this approach, because the blood has been replaced with another fluid such as deionized water mixed with heparin to displace blood and prevent the formation of blood clots.
A partial cross-sectional view of this embodiment is shown in FIG. 16, where an inflation sheath 70 surrounds the external sheath 60 to provide a coaxial inflation lumen 72 for the balloon 64. The inflation lumen 72 is in fluid communication with the ports 66. Saline or any other suitable fluid can be used to inflate the balloon.
As shown in the FIG. 17, in one embodiment, the balloon 64 can be used in combination with bowable members or arms 76 having electrodes, where perfusion holes 78 are formed in the catheter between the balloon 64 and the bowable arms 76. The balloon 64 in this embodiment is inflated through a balloon inflation lumen 72. The use of bowable arms for treating veins is discussed in U.S. Patent No.6,036,687.
The arms can be constructed so as to spring radially outward from the catheter, yet offer little resistance in moving back toward the catheter as the vein diameter is diminished to occlusion. An anti-coagulant or saline or a high-impedance fluid can be introduced or flushed through the perfusion holes 78 in the catheter. As discussed earlier, the high-impedance fluid forces blood away from the venous treatment area and prevents the energy from being dissipated in a more conductive medium such as blood.
As shown in FIG. 18, in another embodiment, a flexible covering 80 is wrapped around or inside the leads 30 of the electrodes 34 to prevent blood flow in the vein. The covering 80 spans the area between the splayed leads along the circumference of the catheter when the leads are extended out the opening, such that the webbed covering blocks blood flow within the vein. The covering may be thought of as webbing or an umbrella to keep blood on one side away from the electrodes. When the electrodes come into apposition with the vein wall, then the gap, if any, between, the electrodes 34 and the covering 80 should be eliminated or otherwise minimized. The covering 80 should be impermeable to fluid. Suitable materials include PET and nylon. Elastomeric materials are also suitable as the leads will need to move close together as they are retracted, and interference with the movement of the leads as the vein diameter is reduced by the application of energy is preferably minimized. Although this embodiment is illustrated with only primary leads, it is to be understood that this embodiment is not so limited and that a secondary lead may be included with the catheter as well without affecting the use of the covering. As with the balloon disclosed earlier, the covering occludes the vein before the application of energy, such that the need for an external compressive tourniquet is not required to stop blood flow.
Furthermore, this also allows the vein to be occluded even for the deep veins where a compressive tourniquet may not be able to compress the vein to occlusion. A high-impedance fluid such as deionized water, or an anti-coagulant such as heparin or saline, or both, or heparin with deionized water may be infused or flushed thorugh the perfusion holes 78 before the application of energy as well.
The electrodes extend through the shaft lumen which also acts as a conduit for the fluid being flushed through the perfusion holes 78. A sclerosing fluid may also be delivered to the venous treatment site to enhance the ligation effect from the application of RF energy. The sclerosing fluid may be added in addition to, or in substitution of, the previously discussed fluids.
In the embodiment shown in FIG. I9, a covering 80 having a parachute shape can be orientated so that blood becomes trapped by the concave portion of the covering and the volume of the blood maintains the deployment of the covering. In this example, the covering is a balloon having openings ~ which allow blood to gather in the balloon, and expand the balloon. The covering 80 can be permanently attached to the catheter shaft. The catheter can still be moved along the vein, even with the balloon in an inflated state.
In the embodiment shown in FIG. 20, the covering 80 is coupled to an outer cannula 82 surrounding the catheter shaft and connected to an actuation mechanism or lever. The outer cannula 82 can be slid along the longitudinal axis of the catheter to allow one end of the parachute covering 80 to be moved axially along the catheter shaft. During insertion of the catheter, the movable end of the covering is pulled away from the connecting end of the catheter to collapse the covering against the catheter. After the catheter is delivered to the venous 5 treatment site, the cannula is slid toward the working end to deploy the covering which then fills with blood entering thorugh the openings 84, thereby occluding the vein. The covering expands as it fills with blood, and when the covering comes into contact with the vein wall, the vein is occluded. Fluid, as before, can be infused either through perfusion holes 78 or a coaxial channel.
10 In the embodiment shown in the cross-sectional view of FIG. 21, the catheter 10 includes an expandable section having a skeleton 90 disposed along a portion of the working end of the catheter. The skeleton 90 is more flexible than the surrounding shaft of the catheter, and can be constructed from a metal or polymer braid. A flexible membrane 92 covers the skeleton 90, with the ends of 15 the membrane attached to the shaft of the catheter adjacent the skeleton.
The membrane is preferably constructed from an elastomeric material. As shown in FIG 22, when the tip of the connecting end is moved toward the working end of the catheter, or vice versa, the skeleton 90 is deformed and forces the membrane 92 out into contact with the vein wall. This embodiment does not require a 20 separate lumen to provide an inflation fluid to a balloon. The skeleton 90 is preferably resilient so that it returns to its original shape once the working end and connecting end are no longer being forced toward one another. Mechanisms for moving the connecting end toward the working end of the catheter for expanding the diameter of a catheter are also discussed in U.S. Patent No. 6,036,687.
25 Although the exapandable section may be controlled separately from the extension of the elecrodes, the expandable section can be controlled by the same mechanism which extends the electrodes away from the catheter.
The description of the component parts discussed above are for a catheter 30 to be used in a vein ranging in size from 2 mm (0.08 in) to 13 mm (0.51 in) in diameter. It is to be understood that these dimensions do not limit the scope of the invention and are merely exemplary in nature. The dimensions of the component parts may be changed to configure a catheter 10 that may used in various-sized veins or other anatomical structures.
5 Although described above as positively charged, negatively charged, or as a positive conductor or negative conductor, these terms are used for purposes of illustration only. These terms are generally meant to refer to different electrode potentials and are not meant to indicate that any particular voltage is positive or negative. Furthermore, other types of energy such as light energy from fiber optics can be used to create a thermal effect in the hollow anatomical structure undergoing treatment.
While several particular forms of the invention have been illustrated and described, it will be apparent that various modifications can be made without departing from the spirit and scope of the invention. Accordingly, it is not intended that the invention be limited, except as by the appended claims.

Claims (94)

1. An apparatus for applying energy from a power source to a hollow anatomical structure having an inner wall, the apparatus comprising:
a catheter having a working end with a distal tip with an orifice formed therein;
a plurality of leads disposed at the working end, each lead having a distal portion with an uninsulated distal end, each lead electrically connected to the power source;
means for extending the leads through the distal orifice; and means for expanding the leads outwardly into non-penetrating contact with the inner wall when the leads have been extended;
whereby the leads move away from each other and into contact with the anatomical structure when extended out the distal orifice.
2. The apparatus of claim 1 wherein the leads are disposed in relation to the working end such that the distal portions of the leads move away from each other when extended through the distal orifice to form a substantially symmetric arrangement of substantially evenly spaced distal ends.
3. The apparatus of claim 2 wherein the leads are disposed in relation to the working end such that when the leads are extended through the distal orifice, the distance between two mutually opposed distal ends is greater than the diameter of the working end.
4. The apparatus of claim 1 wherein the distal end of each lead includes a hemispherical shape having an uninsulated rounded convex surface, wherein the remainder of the hemispherical shape is insulated.
5. The apparatus of claim 4 wherein the leads are mounted at the working end in a cantilever arrangement.
6. The apparatus of claim 1 wherein the extending means include a conductive ring, and at least one of the leads is connected to the ring, and the conductive ring is connected to a power source.
7. The apparatus of claim 1 wherein the expansion means include a bend formed in each lead such that each lead tends to move outward away from the other leads.
8. The apparatus claim 7 wherein the expansion means include a bend formed with an angle less than ninety degrees for each lead.
9. The apparatus of claim 1 wherein each lead comprises a rectangular cross section mounted in relation to the catheter such that the thinner dimension of the rectangular cross section is aligned with the direction of expansion of the lead.
10. The apparatus of claim 1 further comprising a secondary lead connected to the extending means, the secondary lead having a distal end and a length such that the distal end of the secondary lead extends past the distal end of the leads, wherein the extending means extends the leads and the secondary lead through the distal orifice.
11. The apparatus of claim 10 further comprising a spherically shaped electrode mounted at the distal end of the secondary lead.
12. The apparatus of claim 10 further comprising:
a controller that controls the output of the power source to the leads and the secondary lead;

wherein the controller is adapted to switch the electrical polarity of the distal ends of the leads to a common polarity and switch the polarity of the secondary lead to a polarity opposite that of the leads.
13. The apparatus of claim 10 wherein the secondary lead is centrally located with respect to the leads.
14. The apparatus of claim 10 wherein the secondary lead includes a guide wire lumen for receiving a guide wire.
15. The apparatus of claim 1 wherein the extending means comprise:
an outer sheath mounted on the catheter, the outer sheath being movable; and an alignment device positioned inside the outer sheath, the alignment device maintaining separation between the leads;
wherein movement of the outer sheath in relation to the alignment device extends the leads through the orifice.
16. The apparatus of claim 1 wherein the extension means comprise:
an outer sheath mounted on the catheter;
an alignment device positioned inside the outer sheath, the leads being mounted to the alignment device such that the alignment device maintains separation between the leads;
a movable inner sheath to which the leads are attached, the inner sheath being movable in relation to the outer sheath;
wherein movement of the inner sheath in relation to the outer sheath extends the leads through the orifice.
17. The apparatus of claim 1 further comprising a switch connected to the power source, wherein the leads are adapted to be electrically connected to the power source, and the polarity of the leads are selectively changed by the switch.
18. The apparatus of claim 1 further comprising:
a controller that controls the power source; and a temperature sensor mounted to a distal end of a lead, the temperature sensor providing temperature signals to the controller;
wherein the controller controls the power source in response to signals from the temperature sensor.
19. An apparatus for applying energy from a power source to an firmer wall of a hollow anatomical structure, the apparatus comprising:
a catheter having a working end with a distal tip with an orifice formed therein;
a plurality of leads disposed at the working end, each lead having an uninsulated distal end, each lead electrically connected to the power source and each lead mounted at a proximal end to the working end in a cantilever arrangement; and means for extending the leads through the distal orifice;
wherein each lead comprises a bend formed in the lead such that when the leads have been extended through the orifice, the leads expand outwardly moving away from each other into non-penetrating contact with the inner wall to form a substantially symmetric arrangement of substantially evenly spaced distal ends.
20. The apparatus of claim 19 wherein each lead comprises an electrode mounted at its distal end, the electrode having a hemispherical shape.
21. The apparatus of claim 19 wherein each lead comprises an electrode mounted at its distal end, the electrode having a spherical shape.
22. The apparatus of claim 19 wherein each lead comprises a rectangular cross section mounted in relation to the catheter such that the thinner dimension of the rectangular cross section is aligned with the direction of expansion of the lead.
23. The apparatus of claim 19 further comprising a secondary lead mounted to the working end, the secondary lead having a distal end and a length exceeding that of the leads, the extension means also for extending the secondary lead through the distal orifice.
24. The apparatus of claim 23 further comprising a spherically shaped electrode mounted at the distal end of the secondary lead.
25. The apparatus of claim 23 further comprising:
a controller that controls the output of the power source to the electrodes of the leads and the secondary lead;
wherein the controller is adapted to switch the electrical polarity of the distal ends of the leads to a common polarity and switch the polarity of the secondary lead to a polarity opposite that of the leads.
26. The apparatus of claim 23 wherein the secondary lead is centrally located with respect to the leads.
27. The use of a catheter to apply energy from a power source from within a hollow anatomical structure for a period of time sufficient to cause the collapse of the hollow anatomical structure wherein said catheter comprises a working end and a plurality of leads disposed at the working end, each lead having a distal end and being connected to said power source and wherein the distal ends of the leads move away from each other and are adapted for non-penetrating contact with the anatomical structure.
28. The use according to claim, 27 wherein the distal ends of the leads are spaced such that the distal ends of the leads are no more than 5 millimeters apart along the hollow anatomical structure.
29. The use according to Claim 27 wherein the lids are adapted to be extended through an orifice formed in the working end of the catheter, wherein the distance between two mutually opposed distal ends is greater than the diameter of the working end when the leads are extended through the orifice.
30. The use according to Clam 29 wherein separation between the leads is maintained with an alignment device positioned inside an outer sheath of the catheter; and the outer sheath is adapted to be moved in relation to the alignment device to extend the leads out the orifice.
31. The use according to claim 29 wherein separation between the leads is maintained with an alignment device positioned inside an outer sheath of the catheter, and the leads are attached to an inner sheath; and the outer sheath is adapted to be moved in relation to the inner sheath to extend the leads through the orifice.
32. The use according to claim 29 wherein a secondary lead is mounted to the working end, the secondary lead having a distal end and having a length exceeding that of the leads; wherein the secondary lead is adapted to be extended through the distal orifice.
33. The use according to claim 32 wherein the power source is adapted to be controlled so that adjacent leads are of opposite polarity while maintaining the secondary lead so that it is electrically neutral; wherein the polarity of the leads is adapted to be switched so that they are all of the same polarity upon collapse of the anatomical structure around the leads; and the power source is adapted to be controlled so that the secondary lead is of opposite polarity relative to the leads upon switching the polarity of the leads so that they are of the same polarity.
34. The use of the catheter according to claim 33 wherein the catheter is adapted to be moved while energy is applied from within the anatomical structure.
35. The use according to claim 27 wherein the plurality of leads are mounted to the working end in a cantilever arrangement.
36. The use according to claim 27 wherein a bend is capable of being formed in each lead, the bend formed in the direction away from the other leads such that each lead is capable of moving outward, away from the other leads.
37. The use according to claim 27 wherein the temperature at the distal end of a lead is capable of being sensed; and the application of power to the leads is adapted to be controlled in response to the temperature sensed at the distal end.
38. The use of the catheter according to claim 27 wherein when said application of energy occurs, said hollow anatomical structure is a previously flushed hollow anatomical structure.
39. The use of the catheter according to claim 27 wherein said hollow anatomical structure from within which said application of energy occurs, is a previously compressed hollow anatomical structure.
40. The use of the catheter according to claim 27 wherein the hollow anatomical structure is capable of being compressed.
41. The use of the catheter according to claim 27 wherein a tourniquet has previously been applied to compress said hollow anatomical structure and permit monitoring of said hollow anatomical structure through a window in said tourniquet.
42. The use of the catheter according to claim 27 wherein said hollow anatomical structure is a compressed anatomical structure wherein said compression has reduced the diameter of the hollow anatomical structure to a desired diameter for ligation and said leads are capable of being urged towards one another by said compression.
43. The use of the catheter according to claim 27 wherein said hollow anatomical structure is a previously exsanguinated hollow anatomical structure.
44. The use of the catheter according to claim 43 wherein an introduced fluid has been used to previously exsanguinate said hollow anatomical structure.
45. The use of the catheter according to claim 43 wherein said hollow anatomical structure becomes compressed during said exsanguination.
46. An apparatus for delivering energy to ligate an anatomical structure, the anatomical structure having an inner wall, the apparatus comprising:
a catheter having a sheath, a working end, and an opening formed at the working end of the catheter;
an inner member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another;
a plurality of leads, each lead having a distal end, the plurality of leads being attached to the inner member such that the distal ends of the plurality of leads extend out of the opening at the working end of the catheter when the position of the sheath changes in one direction relative to the inner member, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening and into non-penetrating apposition with the inner wall of the hollow anatomical structure;
wherein the distal ends of the leads are configured to deliver energy to the anatomical structure.
47. The apparatus of claim 46, further comprising an actuation mechanism located remotely from the working end of the catheter, the actuation mechanism being coupled to the sheath and the inner member such that an operator manually controls the movement of the sheath and the inner member relative to one another.
48. The apparatus of claim 47, wherein the actuation mechanism is coupled to the sheath such that the sheath is moved relative to the inner member.
49. The apparatus of claim 47, wherein the actuation mechanism is coupled to the inner member such that the inner member is moved relative to the sheath.
50. The apparatus of claim 46, wherein the anatomical structure is a vein, and the leads are formed to have sufficient force to move into opposition with the vein wall, and the formed leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
51. The apparatus of claim 46, further comprising a secondary lead having a distal secondary end, the secondary lead being attached with the inner member such that the distal secondary end of secondary lead is extended out of the opening at the working end of the catheter when the position of the inner member changes in one direction relative to the sheath, wherein the distal ends of the leads are located between the distal secondary end of the secondary lead and the inner member.
52. The apparatus of claim 51, wherein the leads are electrically connected to a power source such that the polarity of each lead can be switched.
53. The apparatus of claim 51, wherein the plurality of leads and the secondary lead are electrically connected to a power source such that the polarity of the plurality of leads can be changed independently of the plurality of the secondary lead.
54. The apparatus of claim 52, wherein the plurality of leads and the secondary lead are electrically connected to a power source, wherein the polarity of the plurality of leads leads can be switched to have either the same polarity or to have opposing polarities for adjacent distal ends of the leads, and the polarity of the secondary lead can be switched between having a polarity and being neutral.
55. The apparatus of claim 51, wherein the distal secondary end includes a generally spherical shape having a cross-sectional dimension approximately equal to the dimension of the opening at the working end of the catheter.
56. The apparatus of claim 51, wherein the distal ends of the leads are configured to form a shape having a cross-sectional dimension no greater than the dimension of the distal secondary end when the distal ends are moved toward the longitudinal axis defined by the sheath.
57. The apparatus of claim 51, wherein the distal ends of the leads are configured to form, in combination with the secondary lead, a shape having a cross-sectional dimension no greater than the dimension of the distal secondary end when the distal ends are moved toward the longitudinal axis defined by the sheath.
58. The apparatus of claim 51, wherein the secondary lead includes a secondary lumen and a secondary opening formed in the distal secondary end such that the secondary opening is in fluid communication with the secondary lumen.
59. The apparatus of claim 58, wherein secondary lumen is configured to accept a guide wire.
60. The apparatus of claim 51, wherein the distal end of the leads each include a rounded convex surface which is uninsulated.
61. The apparatus of claim 46, wherein a temperature sensor is located on at least one of the distal ends of the plurality of leads.
62. The apparatus of claim 46, wherein the distal ends of the leads are arranged to occupy a plane perpendicular to the longitudinal axis defined by the sheath.
63. The apparatus of claim 46, wherein the distal ends of the leads are configured to form a generally spherical shape when the distal ends are loved toward the longitudinal axis defined by the sheath.
64. The apparatus of claim 46, wherein the working end of the catheter includes a tip having a soft durometer, the opening being formed in the tip.
65. The apparatus of claim 46, wherein the leads are electrically connected to a power source such that the polarity of each lead can be switched.
66. The apparatus of claim 65, wherein the leads are electrically connected to a power source such that the polarity of each lead is the same.
67. The apparatus of claim 65, wherein the leads are electrically connected to a power source such that the polarity of a first lead of said plurality of leads is opposite to the leads with distal ends adjacent to the distal end of the first lead.
68. The apparatus of claim 46, wherein a ring is attached to the inner member, and at least one lead of the plurality of leads is connected to the ring.
69. The apparatus of claim 68, wherein the ring is conductive and electrically connected to a power source so that the distal end of the one lead can deliver energy to ligate the anatomical structure.
70. An apparatus for ligating a hollow anatomical structure having an inner wall, comprising:
a catheter having a sheath and a working end, wherein a tip, a port and an opening are located at the working end of the catheter, sad the port is in fluid communication with a lumen;
a balloon located at the working end of the catheter, wherein the port is located between the balloon and the tip;
an inner member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another;

a plurality of leads, each lead having a distal end, the plurality of leads being coupled with the inner member such that the distal ends of the plurality of leads become extended out of the opening at the working end of the catheter when the sheath is moved relative to the inner member, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening and into non-penetrating apposition with the inner wall of the hollow anatomical structure;
wherein the distal end of each lead is capable of delivering energy to the anatomical structure.
71. The apparatus of claim 70, wherein the anatomical structure is a vein, and the formed leads have sufficient force to move into apposition with the vein wall, and the formed leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
72. The apparatus of claim 70, further comprising a secondary lead having a distal secondary end, the secondary lead being coupled with the inner member such that the distal secondary end of secondary lead is extended out of the opening at the working end of the catheter when the inner member is moved relative to the sheath, wherein the distal ends of the leads are located between the distal secondary end of the secondary lead and the inner member.
73. The apparatus of claim 72, wherein the leads are electrically connected to a power source such that the polarity of each lead can be switched.
74. The apparatus of claim 72, wherein the plurality of leads and the secondary lead are electrically connected to a power source such that the polarity of the plurality of leads can be changed independently of the polarity of the secondary lead.
75. The apparatus of claim 72, wherein the plurality of leads and the secondary lead are electrically connected to a power source, wherein the polarity of the plurality of leads can be switched to have either the same polarity or to have opposing polarities for adjacent distal ends of the leads, and the polarity of the secondary lead can be switched between having a polarity and being neutral.
76. The apparatus of claim 72, wherein the balloon includes openings exposed to the fluid in the anatomical structure, and the openings allow fluid from the hollow anatomical structure to flow into and expand the balloon.
77. An apparatus for ligating a hollow anatomical structure, comprising:
a catheter having a sheath and a working end, wherein a tip and a port are located at the working end of the catheter, and the port is in fluid communication with a lumen;
a balloon located at the working end of the catheter;
a plurality of bowable arms located between the ballon and the tip at the working end of the catheter, each arm having a section figured to come into non-penetrating contact with the anatomical structure;
a plurality of electrodes, wherein, at least one electrode is located on the section of at least one arm, and wherein the electrode is capable of delivering energy to the anatomical structure.
78. The apparatus of claim 77, wherein the balloon includes openings exposed to the fluid in the anatomical structure, and the openings allow fluid in the anatomical structure to flow into and expand the balloon.
79. The apparatus of claim 77, wherein the anatomical structure is a vein, and the leads have sufficient force to move into apposition with the vein wall; and the leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
80. The apparatus of Claim 77, further comprising at least one aperture formed in the working end of the catheter to allow the delivery of fluid therethrough.
81. The apparatus of claim 80, wherein the fluid is a dielectric fluid.
82. The apparatus of claim 80, wherein the fluid includes heparin and water.
83. An apparatus for ligating a hollow anatomical structure having an inner wall, comprising:
a catheter having a sheath, a working end, and an opening are located at the working end of the catheter;
an inner member disposed within the sheath such that the inner member and the sheath are capable of being moved relative to one another;
a plurality of leads, each lead having a distal end, the plurality of leads being coupled with the inner member such that the distal ends of the plurality of leads become extended out of the opening at the working end of the catheter when the inner member is moved relative to the sheath, each lead being formed to move the distal end away from a longitudinal axis defined by the sheath when the plurality of leads are extended out the opening and into non-penetrating apposition with the inner wall of the hollow anatomical structure, the distal end of each lead is capable of delivering energy to the anatomical structure;
a flexible, impermeable cover spanning the area between the leads along the circumference of the catheter when the leads are extended out the opening, such that the cover blocks fluid flow within the hollow anatomical structure.
84. The apparatus of claim 83, further comprising at least one aperature formed in the working end of the catheter to allow the delivery of fluid therethrough.
85. The apparatus of claim 84, wherein the fluid is a dielectric fluid.
86. The apparatus of claim 84, wherein the fluid includes heparin and water.
87. The apparatus of claim 83, wherein the anatomical structure is a vein, and the formed leads have sufficient force to move into apposition with the vein wall, and the formed leads do not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied by the distal end of the leads.
88. The use of a catheter to apply energy from a power source from within a follow anatomical structure for a time sufficient to cause the collapse of the hollow anatomical structure, wherein said catheter has a working end and a plurality of leads disposed at the working end, each lead having a distal end and being connected to the power source, and the distal ends of the leads being adapted for non-penetrating contact with the hollow anatomical structure, and said catheter is adapted so that expanding the circumference of said catheter adjacent the distal ends of the leads creates an obstruction sufficient to block said hollow anatomical structure.
89. The use of the catheter according to claim 88 wherein said adaptation of said catheter comprises providing an inflatable balloon on said catheter.
90. The use of the catheter according to claim 88 wherein an introduced fluid is capable of being provided to displace fluids present around the working end of the catheter in said hollow anatomical structure.
91. The use of the catheter according to claim 90 wherein said introduced fluid is a dielectric fluid.
92. The use of the catheter according to claim 91 wherein said introduced fluid comprises heparin.
93. The use of the catheter according to claim 88 wherein heparin and saline are capable of being provided to displace fluids present around the working end of the catheter in said anatomical structure.
94. The use of the catheter according to claim 88 wherein said hollow anatomical structure is a vein and said catheter is adapted so that the leads in the step of expanding are adapted to have sufficient force to move into apposition with the vein wall but to not have sufficient strength to prevent the reduction of the diameter of the vein when energy is applied to the distal end of the leads.
CA002303021A 1997-09-11 1998-09-11 Expandable ligator catheter having multiple electrode leads, and method Expired - Fee Related CA2303021C (en)

Applications Claiming Priority (5)

Application Number Priority Date Filing Date Title
US08/927,251 1997-09-11
US08/927,251 US6200312B1 (en) 1997-09-11 1997-09-11 Expandable vein ligator catheter having multiple electrode leads
US08/958,766 1997-10-26
US08/958,766 US6165172A (en) 1997-09-11 1997-10-26 Expandable vein ligator catheter and method of use
PCT/US1998/019181 WO1999012489A2 (en) 1997-09-11 1998-09-11 Expandable vein ligator catheter and method of use

Publications (2)

Publication Number Publication Date
CA2303021A1 CA2303021A1 (en) 1999-03-18
CA2303021C true CA2303021C (en) 2006-05-30

Family

ID=27129940

Family Applications (1)

Application Number Title Priority Date Filing Date
CA002303021A Expired - Fee Related CA2303021C (en) 1997-09-11 1998-09-11 Expandable ligator catheter having multiple electrode leads, and method

Country Status (13)

Country Link
US (6) US6401719B1 (en)
EP (1) EP1035796A2 (en)
JP (1) JP4131609B2 (en)
CN (1) CN1154447C (en)
AU (1) AU740000B2 (en)
BR (1) BR9814738A (en)
CA (1) CA2303021C (en)
IL (1) IL135008A0 (en)
NO (1) NO328108B1 (en)
NZ (1) NZ503367A (en)
PL (1) PL339518A1 (en)
RU (1) RU2207822C2 (en)
WO (1) WO1999012489A2 (en)

Families Citing this family (272)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6705323B1 (en) 1995-06-07 2004-03-16 Conceptus, Inc. Contraceptive transcervical fallopian tube occlusion devices and methods
US6176240B1 (en) 1995-06-07 2001-01-23 Conceptus, Inc. Contraceptive transcervical fallopian tube occlusion devices and their delivery
JP4060887B2 (en) * 1996-03-05 2008-03-12 ヴィナス メディカル テクノロジーズ インコーポレイテッド Vascular catheter utilization system for heating tissue
US7604633B2 (en) 1996-04-12 2009-10-20 Cytyc Corporation Moisture transport system for contact electrocoagulation
US5957920A (en) * 1997-08-28 1999-09-28 Isothermix, Inc. Medical instruments and techniques for treatment of urinary incontinence
EP0969773B1 (en) 1997-03-04 2007-01-03 Vnus Medical Technologies, Inc. Apparatus for treating venous insufficiency using directionally applied energy
WO1998055046A1 (en) * 1997-06-05 1998-12-10 Adiana, Inc. Method and apparatus for tubal occlusion
US6179832B1 (en) * 1997-09-11 2001-01-30 Vnus Medical Technologies, Inc. Expandable catheter having two sets of electrodes
US6200312B1 (en) * 1997-09-11 2001-03-13 Vnus Medical Technologies, Inc. Expandable vein ligator catheter having multiple electrode leads
US6401719B1 (en) * 1997-09-11 2002-06-11 Vnus Medical Technologies, Inc. Method of ligating hollow anatomical structures
US6258084B1 (en) * 1997-09-11 2001-07-10 Vnus Medical Technologies, Inc. Method for applying energy to biological tissue including the use of tumescent tissue compression
US8551082B2 (en) 1998-05-08 2013-10-08 Cytyc Surgical Products Radio-frequency generator for powering an ablation device
US6740082B2 (en) * 1998-12-29 2004-05-25 John H. Shadduck Surgical instruments for treating gastro-esophageal reflux
US6889089B2 (en) * 1998-07-28 2005-05-03 Scimed Life Systems, Inc. Apparatus and method for treating tumors near the surface of an organ
US6309384B1 (en) * 1999-02-01 2001-10-30 Adiana, Inc. Method and apparatus for tubal occlusion
US8702727B1 (en) 1999-02-01 2014-04-22 Hologic, Inc. Delivery catheter with implant ejection mechanism
US8285393B2 (en) * 1999-04-16 2012-10-09 Laufer Michael D Device for shaping infarcted heart tissue and method of using the device
US6375668B1 (en) * 1999-06-02 2002-04-23 Hanson S. Gifford Devices and methods for treating vascular malformations
US6709667B1 (en) * 1999-08-23 2004-03-23 Conceptus, Inc. Deployment actuation system for intrafallopian contraception
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US6595950B1 (en) * 2000-05-11 2003-07-22 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US7815612B2 (en) 2000-05-11 2010-10-19 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US7150727B2 (en) 2000-05-11 2006-12-19 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US20050113798A1 (en) * 2000-07-21 2005-05-26 Slater Charles R. Methods and apparatus for treating the interior of a blood vessel
US20050107738A1 (en) * 2000-07-21 2005-05-19 Slater Charles R. Occludable intravascular catheter for drug delivery and method of using the same
US20030120256A1 (en) * 2001-07-03 2003-06-26 Syntheon, Llc Methods and apparatus for sclerosing the wall of a varicose vein
US7077836B2 (en) * 2000-07-21 2006-07-18 Vein Rx, Inc. Methods and apparatus for sclerosing the wall of a varicose vein
DE10042493A1 (en) 2000-08-30 2002-03-14 Ethicon Endo Surgery Europe System for treating varicose veins
US6620128B1 (en) * 2000-10-20 2003-09-16 Advanced Cardiovascular Systems, Inc. Balloon blowing process with metered volumetric inflation
AU2002239929A1 (en) * 2001-01-16 2002-07-30 Novacept Apparatus and method for treating venous reflux
WO2003026525A1 (en) * 2001-09-28 2003-04-03 Rita Medical Systems, Inc. Impedance controlled tissue ablation apparatus and method
US6669693B2 (en) * 2001-11-13 2003-12-30 Mayo Foundation For Medical Education And Research Tissue ablation device and methods of using
US6736822B2 (en) * 2002-02-20 2004-05-18 Mcclellan Scott B. Device and method for internal ligation of tubular structures
US7617005B2 (en) 2002-04-08 2009-11-10 Ardian, Inc. Methods and apparatus for thermally-induced renal neuromodulation
US7756583B2 (en) 2002-04-08 2010-07-13 Ardian, Inc. Methods and apparatus for intravascularly-induced neuromodulation
US8347891B2 (en) 2002-04-08 2013-01-08 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen
US8150519B2 (en) 2002-04-08 2012-04-03 Ardian, Inc. Methods and apparatus for bilateral renal neuromodulation
US6780182B2 (en) * 2002-05-23 2004-08-24 Adiana, Inc. Catheter placement detection system and operator interface
US20060267255A1 (en) * 2003-01-31 2006-11-30 Daniela Tomova Process for producing a performance enhanced single-layer blow-moulded container
US7223266B2 (en) 2003-02-04 2007-05-29 Cardiodex Ltd. Methods and apparatus for hemostasis following arterial catheterization
US7115127B2 (en) 2003-02-04 2006-10-03 Cardiodex, Ltd. Methods and apparatus for hemostasis following arterial catheterization
US8021359B2 (en) 2003-02-13 2011-09-20 Coaptus Medical Corporation Transseptal closure of a patent foramen ovale and other cardiac defects
JP4382087B2 (en) * 2003-03-27 2009-12-09 テルモ株式会社 Method and apparatus for treatment of patent foramen ovale
US7293562B2 (en) * 2003-03-27 2007-11-13 Cierra, Inc. Energy based devices and methods for treatment of anatomic tissue defects
CA2938411C (en) 2003-09-12 2019-03-05 Minnow Medical, Llc Selectable eccentric remodeling and/or ablation of atherosclerotic material
DE10345023A1 (en) * 2003-09-24 2005-04-21 Biotronik Gmbh & Co Kg Ablation catheter, comprising electrode holding elements in radial extended position when released
US7431717B2 (en) * 2003-09-30 2008-10-07 Serene Medical, Inc. Central nervous system administration of medications by means of pelvic venous catheterization and reversal of Batson's Plexus
US20050107867A1 (en) * 2003-11-17 2005-05-19 Taheri Syde A. Temporary absorbable venous occlusive stent and superficial vein treatment method
US8060207B2 (en) * 2003-12-22 2011-11-15 Boston Scientific Scimed, Inc. Method of intravascularly delivering stimulation leads into direct contact with tissue
US20050137646A1 (en) * 2003-12-22 2005-06-23 Scimed Life Systems, Inc. Method of intravascularly delivering stimulation leads into brain
US9238127B2 (en) 2004-02-25 2016-01-19 Femasys Inc. Methods and devices for delivering to conduit
US8048101B2 (en) 2004-02-25 2011-11-01 Femasys Inc. Methods and devices for conduit occlusion
US8048086B2 (en) 2004-02-25 2011-11-01 Femasys Inc. Methods and devices for conduit occlusion
US8052669B2 (en) 2004-02-25 2011-11-08 Femasys Inc. Methods and devices for delivery of compositions to conduits
DE102004015641B3 (en) * 2004-03-31 2006-03-09 Siemens Ag Device for elimination of complete occlusion with IVUS monitoring
US7250050B2 (en) 2004-06-07 2007-07-31 Ethicon, Inc. Tubal sterilization device having sesquipolar electrodes and method for performing sterilization using the same
US6964274B1 (en) 2004-06-07 2005-11-15 Ethicon, Inc. Tubal sterilization device having expanding electrodes and method for performing sterilization using the same
US7824408B2 (en) * 2004-08-05 2010-11-02 Tyco Healthcare Group, Lp Methods and apparatus for coagulating and/or constricting hollow anatomical structures
CA2574429A1 (en) * 2004-08-19 2006-03-02 Veinrx, Inc. An occludable intravascular catheter for drug delivery and method of using the same
US7402320B2 (en) * 2004-08-31 2008-07-22 Vnus Medical Technologies, Inc. Apparatus, material compositions, and methods for permanent occlusion of a hollow anatomical structure
US8396548B2 (en) 2008-11-14 2013-03-12 Vessix Vascular, Inc. Selective drug delivery in a lumen
US9713730B2 (en) 2004-09-10 2017-07-25 Boston Scientific Scimed, Inc. Apparatus and method for treatment of in-stent restenosis
US20060069303A1 (en) * 2004-09-30 2006-03-30 Couvillon Lucien A Jr Endoscopic apparatus with integrated hemostasis device
US20060089637A1 (en) * 2004-10-14 2006-04-27 Werneth Randell L Ablation catheter
US8435236B2 (en) * 2004-11-22 2013-05-07 Cardiodex, Ltd. Techniques for heat-treating varicose veins
US7731712B2 (en) 2004-12-20 2010-06-08 Cytyc Corporation Method and system for transcervical tubal occlusion
KR20060072734A (en) * 2004-12-23 2006-06-28 두산인프라코어 주식회사 Appareatus for supplying compressed air of construction heavy equipments
US20070156209A1 (en) * 2005-01-14 2007-07-05 Co-Repair, Inc. System for the treatment of heart tissue
US7455670B2 (en) * 2005-01-14 2008-11-25 Co-Repair, Inc. System and method for the treatment of heart tissue
US20070156210A1 (en) * 2005-01-14 2007-07-05 Co-Repair, Inc., A California Corporation Method for the treatment of heart tissue
EP2586386B1 (en) 2005-01-25 2018-10-31 Covidien LP Structure for permanent occlusion of a hollow anatomical structure
US10064540B2 (en) 2005-02-02 2018-09-04 Intuitive Surgical Operations, Inc. Visualization apparatus for transseptal access
US20080015569A1 (en) 2005-02-02 2008-01-17 Voyage Medical, Inc. Methods and apparatus for treatment of atrial fibrillation
US7860555B2 (en) * 2005-02-02 2010-12-28 Voyage Medical, Inc. Tissue visualization and manipulation system
US8137333B2 (en) 2005-10-25 2012-03-20 Voyage Medical, Inc. Delivery of biological compounds to ischemic and/or infarcted tissue
US8050746B2 (en) 2005-02-02 2011-11-01 Voyage Medical, Inc. Tissue visualization device and method variations
US9510732B2 (en) 2005-10-25 2016-12-06 Intuitive Surgical Operations, Inc. Methods and apparatus for efficient purging
US8078266B2 (en) 2005-10-25 2011-12-13 Voyage Medical, Inc. Flow reduction hood systems
US7930016B1 (en) 2005-02-02 2011-04-19 Voyage Medical, Inc. Tissue closure system
US7918787B2 (en) 2005-02-02 2011-04-05 Voyage Medical, Inc. Tissue visualization and manipulation systems
US8934962B2 (en) 2005-02-02 2015-01-13 Intuitive Surgical Operations, Inc. Electrophysiology mapping and visualization system
US7860556B2 (en) 2005-02-02 2010-12-28 Voyage Medical, Inc. Tissue imaging and extraction systems
US11478152B2 (en) 2005-02-02 2022-10-25 Intuitive Surgical Operations, Inc. Electrophysiology mapping and visualization system
ITFI20050028A1 (en) * 2005-02-21 2006-08-22 El En Spa DEVICE, CATHETER AND METHOD FOR THE CURATIVE TREATMENT OF VARICOSE VEINS
US7625372B2 (en) 2005-02-23 2009-12-01 Vnus Medical Technologies, Inc. Methods and apparatus for coagulating and/or constricting hollow anatomical structures
DE102005038694A1 (en) * 2005-04-11 2006-10-26 Erbe Elektromedizin Gmbh Endoscopic surgery device
US7674260B2 (en) 2005-04-28 2010-03-09 Cytyc Corporation Emergency hemostasis device utilizing energy
DE102005023303A1 (en) 2005-05-13 2006-11-16 Celon Ag Medical Instruments Biegeweiche application device for high-frequency therapy of biological tissue
EP2662044B1 (en) 2005-07-21 2018-10-31 Covidien LP Systems for treating a hollow anatomical structure
DE202006021214U1 (en) * 2005-07-21 2013-11-08 Covidien Lp Apparatus for treating a hollow anatomical structure
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
US8221310B2 (en) 2005-10-25 2012-07-17 Voyage Medical, Inc. Tissue visualization device and method variations
US9101742B2 (en) * 2005-10-28 2015-08-11 Baxter International Inc. Gastrointestinal applicator and method of using same
US9017361B2 (en) 2006-04-20 2015-04-28 Covidien Lp Occlusive implant and methods for hollow anatomical structure
US20070250012A1 (en) * 2006-04-24 2007-10-25 Ifung Lu Medical instrument having a medical needle-knife
US9138250B2 (en) 2006-04-24 2015-09-22 Ethicon Endo-Surgery, Inc. Medical instrument handle and medical instrument having a handle
US8211114B2 (en) 2006-04-24 2012-07-03 Ethicon Endo-Surgery, Inc. Medical instrument having a medical snare
US7837620B2 (en) 2006-04-25 2010-11-23 Ethicon Endo-Surgery, Inc. Medical tubular assembly
US7927327B2 (en) * 2006-04-25 2011-04-19 Ethicon Endo-Surgery, Inc. Medical instrument having an articulatable end effector
US20070255312A1 (en) * 2006-05-01 2007-11-01 Ifung Lu Medical instrument having an end-effector-associated member
US8019435B2 (en) 2006-05-02 2011-09-13 Boston Scientific Scimed, Inc. Control of arterial smooth muscle tone
US7758593B2 (en) * 2006-05-04 2010-07-20 Ethicon Endo-Surgery, Inc. Medical instrument handle and medical instrument having same
US7597661B2 (en) * 2006-05-11 2009-10-06 Ethicon Endo-Surgery, Inc. Medical instrument having a catheter and method for using a catheter
US7959642B2 (en) 2006-05-16 2011-06-14 Ethicon Endo-Surgery, Inc. Medical instrument having a needle knife
US7892166B2 (en) * 2006-05-18 2011-02-22 Ethicon Endo-Surgery, Inc. Medical instrument including a catheter having a catheter stiffener and method for using
US20080039746A1 (en) 2006-05-25 2008-02-14 Medtronic, Inc. Methods of using high intensity focused ultrasound to form an ablated tissue area containing a plurality of lesions
US9055906B2 (en) 2006-06-14 2015-06-16 Intuitive Surgical Operations, Inc. In-vivo visualization systems
US20080097476A1 (en) 2006-09-01 2008-04-24 Voyage Medical, Inc. Precision control systems for tissue visualization and manipulation assemblies
US10004388B2 (en) 2006-09-01 2018-06-26 Intuitive Surgical Operations, Inc. Coronary sinus cannulation
JP4201037B2 (en) * 2006-09-14 2008-12-24 ソニー株式会社 Lens barrel rotation imaging device
US8486060B2 (en) 2006-09-18 2013-07-16 Cytyc Corporation Power ramping during RF ablation
AU2007216674A1 (en) * 2006-09-21 2008-04-10 Cathrx Ltd A catheter assembly
DE102006047366A1 (en) * 2006-10-04 2008-04-10 Celon Ag Medical Instruments Flexible soft catheter for radiofrequency therapy of biological tissue
ES2560006T3 (en) 2006-10-18 2016-02-17 Vessix Vascular, Inc. Induction of desirable temperature effects on body tissue
EP2954868A1 (en) 2006-10-18 2015-12-16 Vessix Vascular, Inc. Tuned rf energy and electrical tissue characterization for selective treatment of target tissues
EP2455034B1 (en) 2006-10-18 2017-07-19 Vessix Vascular, Inc. System for inducing desirable temperature effects on body tissue
US10335131B2 (en) 2006-10-23 2019-07-02 Intuitive Surgical Operations, Inc. Methods for preventing tissue migration
US20090036840A1 (en) * 2006-11-22 2009-02-05 Cytyc Corporation Atraumatic ball tip and side wall opening
JP2008132163A (en) * 2006-11-28 2008-06-12 Olympus Medical Systems Corp Tool for treatment of body lumen occlusion
US20100063360A1 (en) * 2006-11-28 2010-03-11 Adiana, Inc. Side-arm Port Introducer
US20080183036A1 (en) 2006-12-18 2008-07-31 Voyage Medical, Inc. Systems and methods for unobstructed visualization and ablation
US8758229B2 (en) 2006-12-21 2014-06-24 Intuitive Surgical Operations, Inc. Axial visualization systems
US8131350B2 (en) 2006-12-21 2012-03-06 Voyage Medical, Inc. Stabilization of visualization catheters
US7846160B2 (en) 2006-12-21 2010-12-07 Cytyc Corporation Method and apparatus for sterilization
US20080161893A1 (en) * 2006-12-29 2008-07-03 Saurav Paul Fabric electrode head
US20080200873A1 (en) * 2007-02-16 2008-08-21 Alejandro Espinosa Methods and Apparatus for Infusing the Interior of a Blood Vessel
AU2008245600B2 (en) 2007-04-27 2013-07-04 Covidien Lp Systems and methods for treating hollow anatomical structures
EP2148608A4 (en) 2007-04-27 2010-04-28 Voyage Medical Inc Complex shape steerable tissue visualization and manipulation catheter
US8579886B2 (en) * 2007-05-01 2013-11-12 Covidien Lp Accordion style cable stand-off
US8657805B2 (en) 2007-05-08 2014-02-25 Intuitive Surgical Operations, Inc. Complex shape steerable tissue visualization and manipulation catheter
EP2155036B1 (en) 2007-05-11 2016-02-24 Intuitive Surgical Operations, Inc. Visual electrode ablation systems
US8216218B2 (en) 2007-07-10 2012-07-10 Thermage, Inc. Treatment apparatus and methods for delivering high frequency energy across large tissue areas
US8702609B2 (en) 2007-07-27 2014-04-22 Meridian Cardiovascular Systems, Inc. Image-guided intravascular therapy catheters
US8366706B2 (en) * 2007-08-15 2013-02-05 Cardiodex, Ltd. Systems and methods for puncture closure
WO2009028285A1 (en) * 2007-08-28 2009-03-05 Terumo Kabushiki Kaisha Device for opening/closing biological tissue
US8235985B2 (en) 2007-08-31 2012-08-07 Voyage Medical, Inc. Visualization and ablation system variations
US20090125023A1 (en) * 2007-11-13 2009-05-14 Cytyc Corporation Electrosurgical Instrument
US8292880B2 (en) 2007-11-27 2012-10-23 Vivant Medical, Inc. Targeted cooling of deployable microwave antenna
US8858609B2 (en) 2008-02-07 2014-10-14 Intuitive Surgical Operations, Inc. Stent delivery under direct visualization
US8157747B2 (en) * 2008-02-15 2012-04-17 Lary Research & Development, Llc Single-use indicator for a surgical instrument and a surgical instrument incorporating same
EP2271386B1 (en) * 2008-04-01 2021-12-15 Zevex, Inc. Safety occluder
US8425470B2 (en) 2008-04-01 2013-04-23 Zevex, Inc. Anti-free-flow mechanism for enteral feeding pumps
US8876787B2 (en) * 2008-04-01 2014-11-04 Zevex, Inc. Anti-free-flow mechanism for enteral feeding pumps
US9770297B2 (en) * 2008-06-04 2017-09-26 Covidien Lp Energy devices and methods for treating hollow anatomical structures
US9101735B2 (en) 2008-07-07 2015-08-11 Intuitive Surgical Operations, Inc. Catheter control systems
US10070888B2 (en) 2008-10-03 2018-09-11 Femasys, Inc. Methods and devices for sonographic imaging
US9554826B2 (en) 2008-10-03 2017-01-31 Femasys, Inc. Contrast agent injection system for sonographic imaging
US8894643B2 (en) 2008-10-10 2014-11-25 Intuitive Surgical Operations, Inc. Integral electrode placement and connection systems
US8333012B2 (en) 2008-10-10 2012-12-18 Voyage Medical, Inc. Method of forming electrode placement and connection systems
US9468364B2 (en) 2008-11-14 2016-10-18 Intuitive Surgical Operations, Inc. Intravascular catheter with hood and image processing systems
EP2355737B1 (en) 2008-11-17 2021-08-11 Boston Scientific Scimed, Inc. Selective accumulation of energy without knowledge of tissue topography
US20100198209A1 (en) * 2009-01-30 2010-08-05 Tartaglia Joseph M Hemorrhoid Therapy and Method
US7998121B2 (en) * 2009-02-06 2011-08-16 Zevex, Inc. Automatic safety occluder
WO2011055143A2 (en) * 2009-11-04 2011-05-12 Emcision Limited Lumenal remodelling device and methods
US9616246B2 (en) * 2010-01-04 2017-04-11 Covidien Lp Apparatus and methods for treating hollow anatomical structures
US8231619B2 (en) * 2010-01-22 2012-07-31 Cytyc Corporation Sterilization device and method
US8694071B2 (en) 2010-02-12 2014-04-08 Intuitive Surgical Operations, Inc. Image stabilization techniques and methods
US8728067B2 (en) * 2010-03-08 2014-05-20 Covidien Lp Microwave antenna probe having a deployable ground plane
US9814522B2 (en) 2010-04-06 2017-11-14 Intuitive Surgical Operations, Inc. Apparatus and methods for ablation efficacy
CA2795229A1 (en) 2010-04-09 2011-10-13 Vessix Vascular, Inc. Power generating and control apparatus for the treatment of tissue
US9192790B2 (en) 2010-04-14 2015-11-24 Boston Scientific Scimed, Inc. Focused ultrasonic renal denervation
US8550086B2 (en) 2010-05-04 2013-10-08 Hologic, Inc. Radiopaque implant
US8473067B2 (en) 2010-06-11 2013-06-25 Boston Scientific Scimed, Inc. Renal denervation and stimulation employing wireless vascular energy transfer arrangement
US9463062B2 (en) 2010-07-30 2016-10-11 Boston Scientific Scimed, Inc. Cooled conductive balloon RF catheter for renal nerve ablation
US9358365B2 (en) 2010-07-30 2016-06-07 Boston Scientific Scimed, Inc. Precision electrode movement control for renal nerve ablation
US9408661B2 (en) 2010-07-30 2016-08-09 Patrick A. Haverkost RF electrodes on multiple flexible wires for renal nerve ablation
US9084609B2 (en) 2010-07-30 2015-07-21 Boston Scientific Scime, Inc. Spiral balloon catheter for renal nerve ablation
US9155589B2 (en) 2010-07-30 2015-10-13 Boston Scientific Scimed, Inc. Sequential activation RF electrode set for renal nerve ablation
EP2621560B1 (en) 2010-10-01 2019-09-25 Zevex, Inc. Anti free-flow occluder and priming actuator pad
USD672455S1 (en) 2010-10-01 2012-12-11 Zevex, Inc. Fluid delivery cassette
US8974451B2 (en) 2010-10-25 2015-03-10 Boston Scientific Scimed, Inc. Renal nerve ablation using conductive fluid jet and RF energy
US9220558B2 (en) 2010-10-27 2015-12-29 Boston Scientific Scimed, Inc. RF renal denervation catheter with multiple independent electrodes
US9028485B2 (en) 2010-11-15 2015-05-12 Boston Scientific Scimed, Inc. Self-expanding cooling electrode for renal nerve ablation
US9089350B2 (en) 2010-11-16 2015-07-28 Boston Scientific Scimed, Inc. Renal denervation catheter with RF electrode and integral contrast dye injection arrangement
US9668811B2 (en) 2010-11-16 2017-06-06 Boston Scientific Scimed, Inc. Minimally invasive access for renal nerve ablation
US9326751B2 (en) 2010-11-17 2016-05-03 Boston Scientific Scimed, Inc. Catheter guidance of external energy for renal denervation
US9060761B2 (en) 2010-11-18 2015-06-23 Boston Scientific Scime, Inc. Catheter-focused magnetic field induced renal nerve ablation
US9023034B2 (en) 2010-11-22 2015-05-05 Boston Scientific Scimed, Inc. Renal ablation electrode with force-activatable conduction apparatus
US9192435B2 (en) 2010-11-22 2015-11-24 Boston Scientific Scimed, Inc. Renal denervation catheter with cooled RF electrode
US20120157993A1 (en) 2010-12-15 2012-06-21 Jenson Mark L Bipolar Off-Wall Electrode Device for Renal Nerve Ablation
WO2012100095A1 (en) 2011-01-19 2012-07-26 Boston Scientific Scimed, Inc. Guide-compatible large-electrode catheter for renal nerve ablation with reduced arterial injury
BR112013018469B1 (en) 2011-01-19 2022-03-03 Fractyl Health, Inc Devices and methods for tissue treatment
KR20130131471A (en) 2011-04-08 2013-12-03 코비디엔 엘피 Iontophoresis drug delivery system and method for denervation of the renal sympathetic nerve and iontophoretic drug delivery
WO2012148969A2 (en) 2011-04-25 2012-11-01 Brian Kelly Apparatus and methods related to constrained deployment of cryogenic balloons for limited cryogenic ablation of vessel walls
CN103813745B (en) 2011-07-20 2016-06-29 波士顿科学西美德公司 In order to visualize, be directed at and to melt transcutaneous device and the method for nerve
AU2012287189B2 (en) 2011-07-22 2016-10-06 Boston Scientific Scimed, Inc. Nerve modulation system with a nerve modulation element positionable in a helical guide
US9186210B2 (en) 2011-10-10 2015-11-17 Boston Scientific Scimed, Inc. Medical devices including ablation electrodes
EP2765940B1 (en) 2011-10-11 2015-08-26 Boston Scientific Scimed, Inc. Off-wall electrode device for nerve modulation
US9420955B2 (en) 2011-10-11 2016-08-23 Boston Scientific Scimed, Inc. Intravascular temperature monitoring system and method
US9364284B2 (en) 2011-10-12 2016-06-14 Boston Scientific Scimed, Inc. Method of making an off-wall spacer cage
US9162046B2 (en) 2011-10-18 2015-10-20 Boston Scientific Scimed, Inc. Deflectable medical devices
US9079000B2 (en) 2011-10-18 2015-07-14 Boston Scientific Scimed, Inc. Integrated crossing balloon catheter
US8951251B2 (en) 2011-11-08 2015-02-10 Boston Scientific Scimed, Inc. Ostial renal nerve ablation
US20140323859A1 (en) * 2011-11-13 2014-10-30 Nvision Medical Corporation Device and process to confirm occlusion of the fallopian tube
EP2779929A1 (en) 2011-11-15 2014-09-24 Boston Scientific Scimed, Inc. Device and methods for renal nerve modulation monitoring
US9119632B2 (en) 2011-11-21 2015-09-01 Boston Scientific Scimed, Inc. Deflectable renal nerve ablation catheter
US9265969B2 (en) 2011-12-21 2016-02-23 Cardiac Pacemakers, Inc. Methods for modulating cell function
AU2012358227B2 (en) 2011-12-23 2015-06-11 Boston Scientific Scimed, Inc. Methods and apparatuses for remodeling tissue of or adjacent to a body passage
US9433760B2 (en) 2011-12-28 2016-09-06 Boston Scientific Scimed, Inc. Device and methods for nerve modulation using a novel ablation catheter with polymeric ablative elements
US9050106B2 (en) 2011-12-29 2015-06-09 Boston Scientific Scimed, Inc. Off-wall electrode device and methods for nerve modulation
CA2865567C (en) 2012-02-27 2022-10-11 Fractyl Laboratories, Inc. Heat ablation systems, devices and methods for the treatment of tissue
EP2838598B1 (en) 2012-04-19 2020-01-15 Fractyl Laboratories, Inc. Tissue expansion devices
WO2013169927A1 (en) 2012-05-08 2013-11-14 Boston Scientific Scimed, Inc. Renal nerve modulation devices
US9381326B2 (en) 2012-06-15 2016-07-05 W. L. Gore & Associates, Inc. Vascular occlusion and drug delivery devices, systems, and methods
EP2879605A4 (en) 2012-07-30 2016-04-06 Fractyl Lab Inc Electrical energy ablation systems, devices and methods for the treatment of tissue
WO2014026055A1 (en) 2012-08-09 2014-02-13 Fractyl Laboratories Inc. Ablation systems, devices and methods for the treatment of tissue
WO2014032016A1 (en) 2012-08-24 2014-02-27 Boston Scientific Scimed, Inc. Intravascular catheter with a balloon comprising separate microporous regions
CN102784006B (en) * 2012-08-24 2015-11-25 邹英华 Be used for the treatment of hypertensive radio-frequency ablation electrode
CN104780859B (en) 2012-09-17 2017-07-25 波士顿科学西美德公司 Self-positioning electrode system and method for renal regulation
US10398464B2 (en) 2012-09-21 2019-09-03 Boston Scientific Scimed, Inc. System for nerve modulation and innocuous thermal gradient nerve block
US10549127B2 (en) 2012-09-21 2020-02-04 Boston Scientific Scimed, Inc. Self-cooling ultrasound ablation catheter
US9433528B2 (en) * 2012-09-28 2016-09-06 Zoll Circulation, Inc. Intravascular heat exchange catheter with rib cage-like coolant path
EP2903626A4 (en) 2012-10-05 2016-10-19 Fractyl Lab Inc Methods, systems and devices for performing multiple treatments on a patient
US10835305B2 (en) 2012-10-10 2020-11-17 Boston Scientific Scimed, Inc. Renal nerve modulation devices and methods
US8956340B2 (en) * 2012-12-13 2015-02-17 University Of South Florida Urethral catheter assembly with a guide wire
US10537286B2 (en) * 2013-01-08 2020-01-21 Biosense Webster (Israel) Ltd. Catheter with multiple spines of different lengths arranged in one or more distal assemblies
US9956033B2 (en) 2013-03-11 2018-05-01 Boston Scientific Scimed, Inc. Medical devices for modulating nerves
WO2014143571A1 (en) 2013-03-11 2014-09-18 Boston Scientific Scimed, Inc. Medical devices for modulating nerves
US9808311B2 (en) 2013-03-13 2017-11-07 Boston Scientific Scimed, Inc. Deflectable medical devices
CN105228546B (en) 2013-03-15 2017-11-14 波士顿科学国际有限公司 Utilize the impedance-compensated medicine equipment and method that are used to treat hypertension
EP2968919B1 (en) 2013-03-15 2021-08-25 Medtronic Ardian Luxembourg S.à.r.l. Controlled neuromodulation systems
US10265122B2 (en) 2013-03-15 2019-04-23 Boston Scientific Scimed, Inc. Nerve ablation devices and related methods of use
US9827039B2 (en) 2013-03-15 2017-11-28 Boston Scientific Scimed, Inc. Methods and apparatuses for remodeling tissue of or adjacent to a body passage
WO2014197632A2 (en) 2013-06-04 2014-12-11 Fractyl Laboratories, Inc. Methods, systems and devices for reducing the luminal surface area of the gastrointestinal tract
CN105473091B (en) 2013-06-21 2020-01-21 波士顿科学国际有限公司 Renal denervation balloon catheter with co-movable electrode supports
JP2016524949A (en) 2013-06-21 2016-08-22 ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. Medical device for renal nerve ablation having a rotatable shaft
US9707036B2 (en) 2013-06-25 2017-07-18 Boston Scientific Scimed, Inc. Devices and methods for nerve modulation using localized indifferent electrodes
WO2015002787A1 (en) 2013-07-01 2015-01-08 Boston Scientific Scimed, Inc. Medical devices for renal nerve ablation
EP3019106A1 (en) 2013-07-11 2016-05-18 Boston Scientific Scimed, Inc. Medical device with stretchable electrode assemblies
CN105377169B (en) 2013-07-11 2019-04-19 波士顿科学国际有限公司 Device and method for neuromodulation
CN105682594B (en) 2013-07-19 2018-06-22 波士顿科学国际有限公司 Helical bipolar electrodes renal denervation dominates air bag
EP3024527B1 (en) 2013-07-22 2021-11-17 Mayo Foundation for Medical Education and Research Device for self-centering a guide catheter
JP6122217B2 (en) 2013-07-22 2017-04-26 ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. Renal nerve ablation medical device
US10342609B2 (en) 2013-07-22 2019-07-09 Boston Scientific Scimed, Inc. Medical devices for renal nerve ablation
CN105473093B (en) 2013-08-22 2019-02-05 波士顿科学国际有限公司 Flexible circuit with the improved adhesion strength to renal nerve modulation sacculus
CN105555218B (en) 2013-09-04 2019-01-15 波士顿科学国际有限公司 With radio frequency (RF) foley's tube rinsed with cooling capacity
WO2015038947A1 (en) 2013-09-13 2015-03-19 Boston Scientific Scimed, Inc. Ablation balloon with vapor deposited cover layer
US11246654B2 (en) 2013-10-14 2022-02-15 Boston Scientific Scimed, Inc. Flexible renal nerve ablation devices and related methods of use and manufacture
US9687166B2 (en) 2013-10-14 2017-06-27 Boston Scientific Scimed, Inc. High resolution cardiac mapping electrode array catheter
US9770606B2 (en) 2013-10-15 2017-09-26 Boston Scientific Scimed, Inc. Ultrasound ablation catheter with cooling infusion and centering basket
EP3057520A1 (en) 2013-10-15 2016-08-24 Boston Scientific Scimed, Inc. Medical device balloon
JP6259099B2 (en) 2013-10-18 2018-01-10 ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. Balloon catheter comprising a conductive wire with flexibility, and related uses and manufacturing methods
CN105658163B (en) 2013-10-25 2020-08-18 波士顿科学国际有限公司 Embedded thermocouple in denervation flexible circuit
AU2014352874B2 (en) 2013-11-22 2019-03-14 Fractyl Health, Inc. Systems, devices and methods for the creation of a therapeutic restriction in the gastrointestinal tract
CN105899157B (en) 2014-01-06 2019-08-09 波士顿科学国际有限公司 Tear-proof flexible circuit assembly
US9907609B2 (en) 2014-02-04 2018-03-06 Boston Scientific Scimed, Inc. Alternative placement of thermal sensors on bipolar electrode
US11000679B2 (en) 2014-02-04 2021-05-11 Boston Scientific Scimed, Inc. Balloon protection and rewrapping devices and related methods of use
JP6332998B2 (en) * 2014-02-28 2018-05-30 オリンパス株式会社 Atrial ligation instrument
US10959774B2 (en) 2014-03-24 2021-03-30 Fractyl Laboratories, Inc. Injectate delivery devices, systems and methods
EP3122414B1 (en) 2014-03-26 2021-03-17 Venclose, Inc. Cable assembly
US10709490B2 (en) 2014-05-07 2020-07-14 Medtronic Ardian Luxembourg S.A.R.L. Catheter assemblies comprising a direct heating element for renal neuromodulation and associated systems and methods
US9757535B2 (en) 2014-07-16 2017-09-12 Fractyl Laboratories, Inc. Systems, devices and methods for performing medical procedures in the intestine
EP3169260B1 (en) 2014-07-16 2019-09-25 Fractyl Laboratories, Inc. System for treating diabetes and related diseases and disorders
US11185367B2 (en) 2014-07-16 2021-11-30 Fractyl Health, Inc. Methods and systems for treating diabetes and related diseases and disorders
US10206584B2 (en) 2014-08-08 2019-02-19 Medlumics S.L. Optical coherence tomography probe for crossing coronary occlusions
US10376308B2 (en) 2015-02-05 2019-08-13 Axon Therapies, Inc. Devices and methods for treatment of heart failure by splanchnic nerve ablation
US11844615B2 (en) * 2015-03-12 2023-12-19 The Regents Of The University Of Michigan Catheter and method to localize ectopic and reentrant activity in the heart
CN105147389B (en) * 2015-10-22 2018-03-16 上海魅丽纬叶医疗科技有限公司 Include the radio frequency ablation device and its ablation method of balloon occlusion type guiding catheter
EP3366246B1 (en) * 2015-10-22 2023-06-28 Shanghai Golden Leaf Med Tec Co., Ltd. Radio frequency ablation device comprising balloon blocking catheter and ablation method therefor
EP3490442A4 (en) * 2016-07-29 2020-03-25 Axon Therapies, Inc. Devices, systems, and methods for treatment of heart failure by splanchnic nerve ablation
JP6744491B2 (en) * 2016-11-15 2020-08-19 コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. Ultrasonic device for contact
US11497507B2 (en) 2017-02-19 2022-11-15 Orpheus Ventures, Llc Systems and methods for closing portions of body tissue
JP7082987B2 (en) * 2017-04-05 2022-06-09 ナショナル・ユニバーシティ・オブ・アイルランド・ガルウェイ Implantable medical device
US10492760B2 (en) 2017-06-26 2019-12-03 Andreas Hadjicostis Image guided intravascular therapy catheter utilizing a thin chip multiplexor
US11109909B1 (en) 2017-06-26 2021-09-07 Andreas Hadjicostis Image guided intravascular therapy catheter utilizing a thin ablation electrode
US10188368B2 (en) 2017-06-26 2019-01-29 Andreas Hadjicostis Image guided intravascular therapy catheter utilizing a thin chip multiplexor
CN107320175A (en) * 2017-07-07 2017-11-07 中国人民解放军第八医院 It is a kind of from light source RF coagulation tumor resection device
US10561461B2 (en) 2017-12-17 2020-02-18 Axon Therapies, Inc. Methods and devices for endovascular ablation of a splanchnic nerve
US11751939B2 (en) 2018-01-26 2023-09-12 Axon Therapies, Inc. Methods and devices for endovascular ablation of a splanchnic nerve
EP4241836A3 (en) 2019-06-20 2023-11-29 Axon Therapies, Inc. Devices for endovascular ablation of a splanchnic nerve
CN114945341A (en) 2020-01-17 2022-08-26 阿克松疗法公司 Method and apparatus for intravascular ablation of visceral nerves

Family Cites Families (97)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US373339A (en) 1887-11-15 Isidobe eskell cliffoed
US373399A (en) 1887-11-15 hamilton
US659409A (en) 1900-08-25 1900-10-09 Charles L Mosher Electric bipolar dilator.
US833759A (en) 1905-07-27 1906-10-23 John D Sourwine Surgical instrument.
US985865A (en) 1910-06-29 1911-03-07 William H Turner Jr Embalming instrument.
DE1163993B (en) 1960-03-23 1964-02-27 Philips Patentverwaltung Decimeter wave stem radiator for medical treatment
US3301258A (en) 1963-10-03 1967-01-31 Medtronic Inc Method and apparatus for treating varicose veins
US3557794A (en) 1968-07-30 1971-01-26 Us Air Force Arterial dilation device
US4043338A (en) 1973-04-30 1977-08-23 Ortho Pharmaceutical Corporation Pharmaceutical formulation applicator device
DE2324658B2 (en) 1973-05-16 1977-06-30 Richard Wolf Gmbh, 7134 Knittlingen PROBE FOR COAGULATING BODY TISSUE
US4016886A (en) 1974-11-26 1977-04-12 The United States Of America As Represented By The United States Energy Research And Development Administration Method for localizing heating in tumor tissue
US4119102A (en) 1975-07-11 1978-10-10 Leveen Harry H Radio frequency treatment of tumors while inducing hypotension
US4043339A (en) 1976-02-02 1977-08-23 The Upjohn Company Method of and vaginal insert for prostaglandin administration
FR2421628A1 (en) 1977-04-08 1979-11-02 Cgr Mev LOCALIZED HEATING DEVICE USING VERY HIGH FREQUENCY ELECTROMAGNETIC WAVES, FOR MEDICAL APPLICATIONS
US4154246A (en) 1977-07-25 1979-05-15 Leveen Harry H Field intensification in radio frequency thermotherapy
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
EP0058708B1 (en) 1980-09-03 1985-05-08 The University Court Of The University Of Edinburgh Therapeutic device
US4436715A (en) * 1981-09-14 1984-03-13 Kms Fusion, Inc. Storage and retrieval of singlet oxygen
US4564011A (en) * 1982-03-22 1986-01-14 Leon Goldman Laser optic device and method
US5370675A (en) 1992-08-12 1994-12-06 Vidamed, Inc. Medical probe device and method
EP0189329A3 (en) 1985-01-25 1987-06-03 Robert E. Fischell A tunneling catheter system for transluminal arterial angioplasty
DE3516830A1 (en) 1985-05-10 1986-11-13 Max Dr. 8520 Erlangen Hubmann CATHETER
US4660571A (en) 1985-07-18 1987-04-28 Cordis Corporation Percutaneous lead having radially adjustable electrode
US4699147A (en) 1985-09-25 1987-10-13 Cordis Corporation Intraventricular multielectrode cardial mapping probe and method for using same
AT385894B (en) 1985-10-04 1988-05-25 Basem Dr Nashef TUBULAR PROBE
US4643186A (en) 1985-10-30 1987-02-17 Rca Corporation Percutaneous transluminal microwave catheter angioplasty
US4664120A (en) 1986-01-22 1987-05-12 Cordis Corporation Adjustable isodiametric atrial-ventricular pervenous lead
IL78755A0 (en) 1986-05-12 1986-08-31 Biodan Medical Systems Ltd Applicator for insertion into a body opening for medical purposes
US4709698A (en) 1986-05-14 1987-12-01 Thomas J. Fogarty Heatable dilation catheter
US5231995A (en) 1986-11-14 1993-08-03 Desai Jawahar M Method for catheter mapping and ablation
US5215103A (en) 1986-11-14 1993-06-01 Desai Jawahar M Catheter for mapping and ablation and method therefor
US4765331A (en) 1987-02-10 1988-08-23 Circon Corporation Electrosurgical device with treatment arc of less than 360 degrees
US4807620A (en) 1987-05-22 1989-02-28 Advanced Interventional Systems, Inc. Apparatus for thermal angioplasty
SE8800019D0 (en) 1988-01-07 1988-01-07 Knut Olof Edhag FOR CARDIALLY DEFIBLATION USED INTRAVASCULES ELECTRO CABLE
JPH0240054A (en) * 1988-07-29 1990-02-08 Fuji Heavy Ind Ltd Air-fuel ratio control device for internal combustion engine for vehicle
US4966597A (en) 1988-11-04 1990-10-30 Cosman Eric R Thermometric cardiac tissue ablation electrode with ultra-sensitive temperature detection
US4945912A (en) 1988-11-25 1990-08-07 Sensor Electronics, Inc. Catheter with radiofrequency heating applicator
US5779698A (en) 1989-01-18 1998-07-14 Applied Medical Resources Corporation Angioplasty catheter system and method for making same
US5078717A (en) 1989-04-13 1992-01-07 Everest Medical Corporation Ablation catheter with selectively deployable electrodes
US5057107A (en) 1989-04-13 1991-10-15 Everest Medical Corporation Ablation catheter with selectively deployable electrodes
US4976711A (en) 1989-04-13 1990-12-11 Everest Medical Corporation Ablation catheter with selectively deployable electrodes
US4979948A (en) 1989-04-13 1990-12-25 Purdue Research Foundation Method and apparatus for thermally destroying a layer of an organ
US5022399A (en) * 1989-05-10 1991-06-11 Biegeleisen Ken P Venoscope
US5117828A (en) 1989-09-25 1992-06-02 Arzco Medical Electronics, Inc. Expandable esophageal catheter
US5122137A (en) 1990-04-27 1992-06-16 Boston Scientific Corporation Temperature controlled rf coagulation
US5188602A (en) 1990-07-12 1993-02-23 Interventional Thermodynamics, Inc. Method and device for delivering heat to hollow body organs
US5282845A (en) 1990-10-01 1994-02-01 Ventritex, Inc. Multiple electrode deployable lead
US5178618A (en) 1991-01-16 1993-01-12 Brigham And Womens Hospital Method and device for recanalization of a body passageway
CA2061220A1 (en) 1991-02-15 1992-08-16 Mir A. Imran Endocardial catheter for defibrillation, cardioversion and pacing, and a system and method utilizing the same
US5465717A (en) 1991-02-15 1995-11-14 Cardiac Pathways Corporation Apparatus and Method for ventricular mapping and ablation
US5156151A (en) 1991-02-15 1992-10-20 Cardiac Pathways Corporation Endocardial mapping and ablation system and catheter probe
US5275610A (en) 1991-05-13 1994-01-04 Cook Incorporated Surgical retractors and method of use
US5255678A (en) 1991-06-21 1993-10-26 Ecole Polytechnique Mapping electrode balloon
US5383917A (en) 1991-07-05 1995-01-24 Jawahar M. Desai Device and method for multi-phase radio-frequency ablation
US5263493A (en) 1992-02-24 1993-11-23 Boaz Avitall Deflectable loop electrode array mapping and ablation catheter for cardiac chambers
US5277201A (en) 1992-05-01 1994-01-11 Vesta Medical, Inc. Endometrial ablation apparatus and method
US5411025A (en) 1992-06-30 1995-05-02 Cordis Webster, Inc. Cardiovascular catheter with laterally stable basket-shaped electrode array
US5293869A (en) 1992-09-25 1994-03-15 Ep Technologies, Inc. Cardiac probe with dynamic support for maintaining constant surface contact during heart systole and diastole
WO1994007446A1 (en) 1992-10-05 1994-04-14 Boston Scientific Corporation Device and method for heating tissue
US5545161A (en) 1992-12-01 1996-08-13 Cardiac Pathways Corporation Catheter for RF ablation having cooled electrode with electrically insulated sleeve
WO1994021170A1 (en) 1993-03-16 1994-09-29 Ep Technologies, Inc. Flexible circuit assemblies employing ribbon cable
DE4320532C1 (en) 1993-06-21 1994-09-08 Siemens Ag Dental turbine drive with means for automatic speed control
US5405322A (en) 1993-08-12 1995-04-11 Boston Scientific Corporation Method for treating aneurysms with a thermal source
US5409000A (en) 1993-09-14 1995-04-25 Cardiac Pathways Corporation Endocardial mapping and ablation system utilizing separately controlled steerable ablation catheter with ultrasonic imaging capabilities and method
US5881727A (en) 1993-10-14 1999-03-16 Ep Technologies, Inc. Integrated cardiac mapping and ablation probe
WO1995010322A1 (en) 1993-10-15 1995-04-20 Ep Technologies, Inc. Creating complex lesion patterns in body tissue
WO1995010236A1 (en) 1993-10-15 1995-04-20 Ep Technologies, Inc. System for making long thin lesions
US5683384A (en) 1993-11-08 1997-11-04 Zomed Multiple antenna ablation apparatus
US5472441A (en) 1993-11-08 1995-12-05 Zomed International Device for treating cancer and non-malignant tumors and methods
WO1995019148A1 (en) 1994-01-18 1995-07-20 Endovascular, Inc. Apparatus and method for venous ligation
US5437664A (en) 1994-01-18 1995-08-01 Endovascular, Inc. Apparatus and method for venous ligation
US5423815A (en) 1994-01-25 1995-06-13 Fugo; Richard J. Method of ocular refractive surgery
US5458596A (en) 1994-05-06 1995-10-17 Dorsal Orthopedic Corporation Method and apparatus for controlled contraction of soft tissue
US5505730A (en) 1994-06-24 1996-04-09 Stuart D. Edwards Thin layer ablation apparatus
US5531739A (en) * 1994-09-23 1996-07-02 Coherent, Inc. Method of treating veins
US5514130A (en) 1994-10-11 1996-05-07 Dorsal Med International RF apparatus for controlled depth ablation of soft tissue
US5722401A (en) 1994-10-19 1998-03-03 Cardiac Pathways Corporation Endocardial mapping and/or ablation catheter probe
DE69517153T2 (en) 1994-11-02 2001-02-01 Olympus Optical Co INSTRUMENT WORKING WITH ENDOSCOPE
IT1278372B1 (en) 1995-02-15 1997-11-20 Sorin Biomedica Cardio Spa CATHETER, PARTICULARLY FOR THE TREATMENT OF HEART ARRHYTHMIA.
US5868740A (en) 1995-03-24 1999-02-09 Board Of Regents-Univ Of Nebraska Method for volumetric tissue ablation
WO1996032885A1 (en) 1995-04-20 1996-10-24 Desai Jawahar M Apparatus for cardiac ablation
US5709224A (en) 1995-06-07 1998-01-20 Radiotherapeutics Corporation Method and device for permanent vessel occlusion
US6090105A (en) * 1995-08-15 2000-07-18 Rita Medical Systems, Inc. Multiple electrode ablation apparatus and method
US5951547A (en) 1995-08-15 1999-09-14 Rita Medical Systems, Inc. Multiple antenna ablation apparatus and method
US5863290A (en) 1995-08-15 1999-01-26 Rita Medical Systems Multiple antenna ablation apparatus and method
US5810804A (en) 1995-08-15 1998-09-22 Rita Medical Systems Multiple antenna ablation apparatus and method with cooling element
US5817092A (en) 1995-11-09 1998-10-06 Radio Therapeutics Corporation Apparatus, system and method for delivering radio frequency energy to a treatment site
JP3981987B2 (en) * 1995-12-13 2007-09-26 三菱化学株式会社 Method for producing fatty acid lactic acid ester salt
US6036687A (en) * 1996-03-05 2000-03-14 Vnus Medical Technologies, Inc. Method and apparatus for treating venous insufficiency
US6139527A (en) * 1996-03-05 2000-10-31 Vnus Medical Technologies, Inc. Method and apparatus for treating hemorrhoids
JP4060887B2 (en) * 1996-03-05 2008-03-12 ヴィナス メディカル テクノロジーズ インコーポレイテッド Vascular catheter utilization system for heating tissue
US6077257A (en) * 1996-05-06 2000-06-20 Vidacare, Inc. Ablation of rectal and other internal body structures
US5827268A (en) 1996-10-30 1998-10-27 Hearten Medical, Inc. Device for the treatment of patent ductus arteriosus and method of using the device
US6091995A (en) 1996-11-08 2000-07-18 Surx, Inc. Devices, methods, and systems for shrinking tissues
US5916235A (en) 1997-08-13 1999-06-29 The Regents Of The University Of California Apparatus and method for the use of detachable coils in vascular aneurysms and body cavities
US6401719B1 (en) * 1997-09-11 2002-06-11 Vnus Medical Technologies, Inc. Method of ligating hollow anatomical structures
US6666858B2 (en) * 2001-04-12 2003-12-23 Scimed Life Systems, Inc. Cryo balloon for atrial ablation

Also Published As

Publication number Publication date
NZ503367A (en) 2003-01-31
US7041098B2 (en) 2006-05-09
JP2001515752A (en) 2001-09-25
AU740000B2 (en) 2001-10-25
IL135008A0 (en) 2001-05-20
WO1999012489A2 (en) 1999-03-18
US6689126B1 (en) 2004-02-10
US6398780B1 (en) 2002-06-04
RU2207822C2 (en) 2003-07-10
US20020147445A1 (en) 2002-10-10
EP1035796A2 (en) 2000-09-20
NO20001267D0 (en) 2000-03-10
US20040162555A1 (en) 2004-08-19
NO328108B1 (en) 2009-12-07
PL339518A1 (en) 2000-12-18
CN1278711A (en) 2001-01-03
US6401719B1 (en) 2002-06-11
JP4131609B2 (en) 2008-08-13
CN1154447C (en) 2004-06-23
AU9484598A (en) 1999-03-29
CA2303021A1 (en) 1999-03-18
WO1999012489A3 (en) 1999-06-17
US20020148476A1 (en) 2002-10-17
NO20001267L (en) 2000-05-09
BR9814738A (en) 2000-10-10

Similar Documents

Publication Publication Date Title
CA2303021C (en) Expandable ligator catheter having multiple electrode leads, and method
US6165172A (en) Expandable vein ligator catheter and method of use
EP1105060B1 (en) Electrocatheter for inducing vessel stenosys having two arrays of diverging electrodes
MXPA00002442A (en) Expandable vein ligator catheter and method of use

Legal Events

Date Code Title Description
EEER Examination request
MKLA Lapsed

Effective date: 20140911