WO2008051708A2 - Ablation catheter apparatus with one or more electrodes - Google Patents
Ablation catheter apparatus with one or more electrodes Download PDFInfo
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- WO2008051708A2 WO2008051708A2 PCT/US2007/080819 US2007080819W WO2008051708A2 WO 2008051708 A2 WO2008051708 A2 WO 2008051708A2 US 2007080819 W US2007080819 W US 2007080819W WO 2008051708 A2 WO2008051708 A2 WO 2008051708A2
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- Prior art keywords
- catheter
- electrode
- distal end
- end portion
- antenna
- Prior art date
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical 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
- A61B18/14—Probes or electrodes therefor
- A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
- A61B2017/00292—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery mounted on or guided by flexible, e.g. catheter-like, means
- A61B2017/003—Steerable
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00839—Bioelectrical parameters, e.g. ECG, EEG
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/0091—Handpieces of the surgical instrument or device
- A61B2018/00916—Handpieces of the surgical instrument or device with means for switching or controlling the main function of the instrument or device
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/0091—Handpieces of the surgical instrument or device
- A61B2018/00916—Handpieces of the surgical instrument or device with means for switching or controlling the main function of the instrument or device
- A61B2018/0094—Types of switches or controllers
- A61B2018/00946—Types of switches or controllers slidable
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
- A61B2018/183—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves characterised by the type of antenna
Definitions
- the present invention generally relates to medical devices used for ablation of biological tissues, and more particularly to an ablation catheter apparatus incorporating one or more electrodes such as electrocardiogram (ECG) electrodes.
- ECG electrocardiogram
- Ablation catheters apply energy to a biological tissue site which requires ablation. Such catheters may use various energy modes, such as radiofrequency, ultrasound, laser, cryogenic, and the like.
- Radio frequency (“RF") ablation catheters generally operate in the microwave frequency range and are used to destroy or ablate biological tissues for therapeutic purposes.
- microwave ablation catheters are used to ablate cardiac tissues that cause irregular heartbeats or arrhythmia, avoiding the need for more risky and invasive open heart surgery.
- the catheter- antenna is passed through the vein for access to the atrium. Within the atrium, the antenna is positioned at the desired location where ablation is required.
- An intracardiac electrogram is used to identify conductive pathways at the cardiac tissue site that needs to be ablated.
- the ablation catheter system of this invention comprises an elongate catheter adapted for insertion into a body vessel of a patient, the catheter having a distal end portion adapted for positioning adjacent a biological tissue site requiring treatment and a proximal end portion having a connector for connection to a control unit for controlling the ablation procedure, an antenna disposed at the distal end portion of the catheter for providing output energy for tissue ablation purposes, a pair of conductors extending through the catheter from the proximal end portion and connected to the antenna for providing power to the antenna from a power supply in the control unit, and at least one electrode formed of a flexible conductive material disposed at the distal end portion of the antenna and connected to the connector at the proximal end portion of the catheter for providing an output signal to the control unit.
- the flexible conductive material is at least substantially non-metallic.
- Electrodes may be disposed at the distal end portion of the catheter.
- the electrode or electrodes are of conductive polymer material with hydrophilic characteristics for improved wetability.
- Two spaced electrode rings are mounted on or embedded in the outer surface of the cathode.
- one electrode ring may be provided and the other electrode may be a tip of conductive polymer material at the distal end of the catheter.
- layers of conductive and nonconductive polymer material may be provided at specific positions at the distal end portion of the catheter to produce multiple working electrodes.
- the electrode output signal can be connected to a suitable electrode recording system inputs in the control unit or a separate electrocardiogram unit to provide intracardiac signal mapping.
- Figures IA and IB are side elevation views of a shapeable RF ablation catheter according to one embodiment in a straight and bent configuration, respectively;
- Figures 2A and 2B are side elevation views of a shapeable RF ablation catheter according to another embodiment with a different steering mechanism from Figure 1;
- Figures 3A and 3B are cross sectional views of the distal end portion of the tip of the catheter of Figure 1 or 2 in a straight configuration and a bent configuration, respectively;
- Figure 4 is a cross-sectional view of the tip or distal end portion of one embodiment of a shapeable or bendable RF ablation catheter incorporating electrodes;
- Figure 5 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter having a modified electrode arrangement according to another embodiment
- Figure 6 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter with another electrode arrangement
- Figure 7 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter with a modified electrode arrangement according to another embodiment.
- Figure 8 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter with modified electrodes according to another embodiment.
- Certain embodiments as disclosed herein provide for systems and methods for ablation of biological tissues in body areas such as the heart, liver, and the like using a bendable radio-frequency (RF) catheter.
- the catheter is provided with electrodes of a flexible conductive material such as a conductive polymer at its distal end for providing an output signal such as an intracardiac electrocardiogram ("ECG") signal to a control unit to allow physicians to obtain tissue proximity and electrical conductivity information both before and after tissue ablation, as well as to provide other feedback during the ablation procedure.
- ECG intracardiac electrocardiogram
- FIGS. IA and IB illustrate a radio-frequency (“RF") ablation catheter system 100 of one embodiment including a shapeable catheter device 100 adapted for insertion into a body vessel of a patient and incorporating an RF antenna for delivering electromagnetic energy to a treatment site, as described in more detail below.
- RF radio-frequency
- the catheter device 100 has a flexible, elongated tubular body 120 having a proximal portion 130 and a distal or tip portion 140. Located at the proximal portion of the body is a handle chassis 160 containing steering and positioning controls (not illustrated) for the body, activated by actuator 200.
- actuator 200 Located at the proximal portion of the body is a handle chassis 160 containing steering and positioning controls (not illustrated) for the body, activated by actuator 200.
- the tip portion of the catheter body is activated to bend between the straight configuration of Figure IA and the bent configuration of Figure IB by sliding the actuator back and forth in an axial direction.
- the tip portion is bent between the straight and bent configurations by rotating the actuator or collar 220. Suitable mechanisms for controlling bending of the tip portion of catheter body 120 are described in detail in U.S. Patent No.
- a coupling or electrical connector 170 is provided at the proximal end of the catheter device for connecting the catheter to a control unit or the like containing one or more electronic devices such as an RF generator and controller (not shown) for providing power to the antenna during an ablation procedure.
- Suitable signal control units are known in the ablation catheter field and are therefore not described in detail here.
- the dimensions of the catheter body are adapted as required to suit the particular medical procedure, as is well known in the medical art.
- the catheter is used to ablate cardiac tissue.
- the catheter may be used to ablate other types of body tissue in different organs, both internal and external to the body.
- the tubular body 120 of the catheter device may be generally constructed of a polymer material which is bio-compatible with the body vessel environment. Examples of such materials include thermoplastic elastomer material such as Pebax® available from Autochem Germany, polyethylene, polyurethane, polyester, polyimide, polyamide, and the like, with varying degrees of radiopacity, hardness, and elasticity.
- the tubular body of the catheter may be formed with a plurality of segments using one or more of the aforementioned materials or equivalents, such that the catheter body 120 is progressively more flexible towards its distal end.
- the segments may be joined together by thermal bonding, butt joints, or adhesive bonding.
- Braiding reinforcement may be provided to the surface of the tubular body to attain a desirable level of stiffness and torsional strength for the catheter to advance and negotiate through the body vessel of the patient, while still allowing the distal end portion to be bent when needed.
- the distal end portion 140 may be of a softer polymer compound than the remainder of the body, with little or no braiding or reinforcement, to provide the desired flexibility for distal deflection and shaping of the apparatus.
- the catheter has a tubular body with a central bore 150 and a closed distal end or tip.
- the tip may be open in alternative embodiments.
- deflection of the distal end portion of the catheter is accomplished by use of a pre-shaped deflection member 180 which is constrained in a straight orientation in the configuration of Figure 3 A and which adopts a bent shape when extended into the bent configuration of Figure 3B.
- a pre-shaped deflection member 180 which is constrained in a straight orientation in the configuration of Figure 3 A and which adopts a bent shape when extended into the bent configuration of Figure 3B.
- other bending or shaping mechanisms may be used in alternative embodiments, as described, for example, in U.S. Patent No. 7,004,938 referenced above.
- the distal end portion 140 of the tubular body includes an RF antenna 250 comprising a flexible, helically coiled radiating antenna device 255 embedded in the flexible wall of the tubular body, as best illustrated in Figures 3A and 3B.
- the antenna device can therefore bend as the distal end portion is shaped to conform to a body vessel or the like, as illustrated in Figure 3B.
- Opposite ends of the antenna device are connected to electrical conductors or leads for connection to the proximal end connector 170 and thereby to a source of RF energy in the catheter control unit (not illustrated), as will be described in more detail below in connection with Figure 4.
- the electrical conductors which connect the RF antenna to the connector 170 may be of a flexible mesh or braided wire construction 260 or of a thin-film electrically conductive material.
- the conductors are shown schematically as a mesh construction embedded in the walls of the tubular body 120 of the catheter. In alternative arrangements, separate conductors may be used to provide power to the antenna 250.
- Figure 4 illustrates the distal end portion 310 of a first embodiment of a modified catheter having integrated electrodes 312, 314.
- the electrodes are ECG electrodes, although they may be other types of electrodes in other embodiments. Although two electrodes are illustrated in Figure 4, in other embodiments one electrode or more than two such electrodes may be provided. Some parts of the catheter of Figure 4 are identical to those in Figures 1 to 3 and like reference numerals have been used for like parts, as appropriate.
- a pair of coaxial inner and outer tubular conductors 315, 316 extend along the length of the tubular body 318, with the outer conductor 316 connected to the proximal end of RF antenna 250 and the inner conductor 315 connected to the distal end of the RF antenna adjacent the tip of the catheter.
- the structure of the remainder of the tubular body 318 which is not shown in Figure 4 may be identical to that of tubular body 120 described above, and a similar connector 170 (not illustrated) may be provided at the proximal end of the catheter for connecting the conductors to a suitable RF source.
- the distal end portion illustrated in Figure 4 will be shapeable or bendable in a similar manner and using the same or similar control devices as were described above in connection with Figures 1 to 3.
- the tubular body 318 is of dielectric material such as a non-conductive polymer and has a portion 320 of reduced outer diameter at its forward end.
- the first electrode 312 comprises a sleeve of flexible conductive material mounted over the reduced diameter end portion 320 of the tubular body and having an end portion or tip 322 extending over the open end of portion 320.
- the RF or microwave antenna 250 is embedded in the sleeve or electrode 312.
- the inner and outer conductors 315, 316 extend through the tubular body 318 as illustrated for connection to the opposite ends of the antenna coil 250.
- the second electrode 314 comprises a ring of flexible conductive material mounted over the tubular body 318 at a location spaced rearwardly from the rear end of conductive sleeve or electrode 312.
- the two electrodes may be secured over the inner tubular body 318 by adhesive, bonding, mechanical force, heat sealing or the like.
- the flexible conductive material forming the electrodes is at least substantially non-metallic material and may be a conductive polymer material which is sufficiently bendable to allow bending of the distal end portion 310 between the positions illustrated in Figures IA and IB.
- the electrode ring 314 may be mounted flush in an annular recess or gap in the outer surface of the tubular body, or may be molded integrally with the tubular body, so that it does not project outwardly from the outer surface of the body 318.
- a conductor or connector 324 extends from electrode ring 314 to the connector 170 at the proximal end of the catheter, for suitable connection to an ECG monitor or the like in a control unit (not illustrated) for the catheter.
- Conductor 324 is shown spaced from the outer surface of body 318 in Figure 4 for clarity, but may be a line of conductive ink or adhesive over the outer surface of the tubular body, or may alternatively be embedded in the body 318 outside conductor 316, One of the conductors 315 or 316 will also be connected to the ECG or other monitor for suitable monitoring of the signal detected between the two electrodes 312, 314.
- both electrodes are of a flexible, conductive polymer material, i.e. a polymer material loaded with conductive materials.
- FIG. 5 illustrates the distal end portion 325 of a catheter with a modified electrode arrangement in which the electrode ring 314 of Figure 4 is replaced by an electrode end cap 330.
- Electrodes 312, 330 are of flexible conductive material such as a conductive polymer material as in Figure 4.
- the conductive sleeve 312 in which the antenna is mounted has an outer cover layer 332 of non-conductive polymer material extending along at least part of its length and over its distal end, providing a non-conductive shield layer between the first and second electrodes 312, 330.
- a conductor or connector wire 334 extends from the connector at the proximal end of the catheter through the central lumen 150 of the tubular body 318 and into the electrode end cap 330 to provide a signal path between the electrode and the ECG monitor.
- the catheter of Figure 5 is otherwise identical to that of the previous embodiment and like reference numerals have been used as appropriate.
- Conductive sleeve 312, non-conductive layer 332, and end cap 330 may be laminated together over the tubular body 318 by any suitable means such as bonding, heat sealing, adhesive, or the like.
- Figure 6 illustrates the distal end portion 340 of a catheter having another modified electrode arrangement.
- Parts of the cathode of this embodiment are identical to those of Figures 4 and 5 and like reference numerals have been used for like parts as appropriate.
- the sleeve 335 in which the antenna coil 250 is embedded does not comprise one of the two electrodes.
- sleeve 335 is mounted over the reduced diameter end portion 320 of the tubular body 318, which is of dielectric or non-conductive material, and the antenna coil 250 is connected at its opposite ends to the distal ends of the inner and outer conductors 315, 316.
- an outer layer 336 of non-conductive material extends over the conductive sleeve 335 and has an end cap portion 338 extending over the tip of the tubular body 318.
- the electrodes in this embodiment comprise a pair of conductive rings 339, 341 mounted at spaced intervals on the outer, non-conductive layer 336.
- the ring electrodes may be of conductive polymer material.
- the first ring 339 is positioned adjacent the non-conductive end cap portion 338 and the second ring 341 is positioned adjacent the rear end of the conductive layer 336.
- a central conductor or connector wire 342 extends through the hollow central bore or lumen of the tubular body 318, through the non-conductive end cap portion 338, and bends back to terminate in the first conductive ring electrode 339.
- the part of connector wire 342 shown extending through lumen 150 may be a line of conductive ink or adhesive on the inner surface of tubular body 318.
- a second conductor or connector wire 343 extends along the outside of the tubular body 318 and is connected to the second conductive ring electrode 341. It will be understood that the connector wire 343 may comprise a line of conductive ink or adhesive on tubular body 318, or may alternatively be embedded in the tubular body 318 at location spaced outside the outer tubular conductor 316.
- the various conductive and non-conductive polymer layers of the distal end portion 340, including the electrode rings, are suitably laminated together by heat sealing, adhesive bonding, or the like.
- FIG. 6 Also shown in Figure 6 is a pull wire 355 which extends through the lumen 150 to the tip 338 and is attached to suitable steering and positioning controls (not illustrated) at the proximal end of the catheter, for controlling bending of the distal end portion.
- a pull wire mechanism is described in U.S. Patent No. 7,004,938 referenced above, the contents of which are incorporated herein by reference. It may be understood that a similar position control mechanism will be provided in the embodiments of Figures 4 to 6, or the mechanism 180 of Figure 3 may be provided in any of these embodiments.
- Figure 7 illustrates the distal end portion 400 of a catheter according to another embodiment.
- a tubular body 318 of flexible dielectric material extends the length of the catheter and has a central through bore or lumen 150 and an end portion 320 of reduced outer diameter over which the sleeve 312 containing embedded RF antenna 250 is mounted.
- sleeve 312 is of conductive polymer material and the ends of the antenna are connected to the distal end connector 170 (Figure 1) of the catheter by means of inner and outer cylindrical conductors 315, 316 extending through the tubular body 318, in the manner described above in connection with Figure 1.
- an outer cover layer 345 of non-conductive polymer material extends along the entire length of the catheter, over the tubular body 318 and sleeve 312, and has a forward end or tip 344 covering the forward end of the sleeve and tubular body.
- a pair of contact rings 346,348 are mounted in the outer cover layer 345 in the distal end portion of the catheter, with the forward contact ring 346 located over the sleeve 312 and in electrical contact with the sleeve, and the rear contact ring 348 located slightly rearwardly from sleeve 312.
- Each ring is of a flexible conductive material such as conductive polymer material.
- Rings 346,348 and outer cover layer 345 are suitably bonded together and laminated over the tubular body 318 and conductive polymer sleeve 312.
- the forward contact ring 346 is connected to the proximal end connector 170 via the conductive sleeve 312 and the outer conductor 316 which also provides power to the antenna 250.
- the rear contact ring 348 is connected to a conductive wire 350 which extends through the tubular body 318 to the proximal end connector 170 of the catheter.
- the conductors 316, 350 therefore provide the output for the ECG monitor in the control unit in this embodiment.
- the embodiment of Figure 7 also includes a temperature sensor 352 in the lumen 150 adjacent the tip of the catheter.
- the temperature sensor 352 may be a thermistor, thermocouple, or the like and has a thermocouple junction or sensor end 352 and a pair of braided wires or conductors 354 extending from the sensor 352 through the tubular body to the connector 170 at the proximal end of the catheter, where they are connected to control circuitry for monitoring the temperature at the distal end of the catheter and controlling the antenna operation.
- a pull wire 355 is attached to the tip 344 of the catheter and extends through the central lumen 150 through the length of the catheter for attachment to a suitable steering and control mechanism (not illustrated), as in the previous embodiment.
- FIG. 8 illustrates a modification of the embodiment of Figure 5, and like reference numerals are used for like parts as appropriate.
- a tubular body 318 of dielectric material having a central lumen 150 extends the entire length of the catheter, and has a reduced outer diameter portion 320 at the distal end portion 500 of the catheter.
- Conductive sleeve 312 is mounted over the portion 320 and the RF antenna 250 is embedded in sleeve 312.
- the electrodes comprise the conductive sleeve 312 and a conductive tip 330 mounted over the end of the catheter, with a layer 332 of non-conductive material such as non-conductive polymer between the electrodes 312 and 330.
- thermocouple wires 510 which extend through lumen 150 from the proximal end connector 170 of the catheter and into the conductive tip electrode 330, with a thermocouple junction 512 at the end of the double wires providing a temperature sensor.
- the thermocouple wires therefore have the dual function of providing a temperature sensor output as well as providing an ECG monitor output in combination with outer antenna conductor 316.
- the ECG output may be measured between conductor 316 and either one of the thermocouple wires 510.
- the temperature output may be used in monitoring and controlling operation of the RF antenna, as described above in connection with Figure 7.
- electrodes are mounted at the distal end portion of a shapeable or bendable catheter to allow physicians to locate a tissue region causing problems and to obtain both optimum tissue proximity and electrical conductive activities before and after ablation, as well as to obtain feedback of their actions.
- two electrodes are provided in these embodiments, only one electrode or more than two electrodes may be provided in other embodiments.
- the electrode or electrodes in these embodiments may be ECG or other types of electrodes.
- Radio-opaque markers (not illustrated) at the distal end portion of the catheter may also be used to aid in positioning the tip of the catheter, as is known in the field.
- the conductor wires connected to the electrodes and to the proximal end connector 170 of the catheter will communicate with an external ECG system and monitor (not illustrated) via a suitable connection cable which will transmit ECG signals between the electrodes and ECG system.
- the antenna conductors and thermocouple wires (if a temperature sensor is present) will be similarly connected to an appropriate antenna output control system.
- the RF antenna 250 is adapted to receive and radiate electromagnetic energy in order to treat a selected biological tissue site.
- An example of a suitable spectrum of radio frequency energy for use in the ablation catheter is that of the microwave frequency range above 300 MHz.
- the RF antenna is capable of applying substantially uniformly distributed electromagnetic field energy along the RF antenna in a direction substantially normal to the longitudinal axis of antenna 250.
- the electrodes in the embodiments of Figures 4 to 8 are made of a suitable flexible conductive material, so that they can bend with the remainder of the distal end portion during steering. Such electrodes avoid or reduce the problems encountered with metallic electrodes, since they do not absorb microwave energy to any great extent and do not become excessively hot.
- the electrodes may be of an at least substantially non-metallic material, and in one embodiment they are made from a conductive polymer material such as nylon, polyethylene, polyolef ⁇ n, polypropylene, polycarbonate, Pebax ®, TPE (thermoplastic elastomers) and blends, loaded with a selective conductive material.
- a conductive polymer material such as nylon, polyethylene, polyolef ⁇ n, polypropylene, polycarbonate, Pebax ®, TPE (thermoplastic elastomers) and blends, loaded with a selective conductive material.
- Other non-conductive parts of the catheter may be of the same polymer material or different polymer materials.
- the conductive material may be micro-carbon spheres, carbon particles, carbon nanotubes, nickel dust, or the like.
- the electrodes may be made entirely of conductive polymer material or may be a mixture of conductive and non-conductive polymer material, or a mixture of conductive and non-conductive materials with metal substrates.
- Electrodes and the connector 170 at the proximal end of the catheter may be provided in some embodiments by means of conductive ink or adhesive applied over the polymer surface.
- conductor 324 of Figure 4 or conductor 342 of Figure 6 may be a line of conductive ink or adhesive over the outer surface of the tubular body 318 extending from electrode ring 314 to the proximal end of the catheter.
- Conductor 350 of Figure 7 may be a line of conductive ink or adhesive over the outer surface of non-conductive tubular body 318, with the outer layer 345 of non- conductive polymer laminated over the tubular body and conductor line 350.
Abstract
A radio frequency (RF) ablation catheter has a flexible distal end portion so that it can be deflected to position an antenna disposed in the distal end portion adjacent a tissue site to be treated. At least one electrical conductor is coupled to the antenna and extends through the catheter to the proximal end of the catheter to a connector at the proximal end of the catheter for connection to a power supply for the RF antenna. At least one electrode is disposed at the distal end portion of the catheter and electrically coupled to the proximal end connector for connection to a monitor. The electrode is of a flexible, electrically conductive material such as conductive polymer material. The electrode may be an electrocardiogram (ECG) electrode.
Description
ABLATION CATHETER APPARATUS WITH ONE OR MORE
ELECTRODES
Background
1. Field of the Invention
[01] The present invention generally relates to medical devices used for ablation of biological tissues, and more particularly to an ablation catheter apparatus incorporating one or more electrodes such as electrocardiogram (ECG) electrodes.
2. Related Art
[02] Ablation catheters apply energy to a biological tissue site which requires ablation. Such catheters may use various energy modes, such as radiofrequency, ultrasound, laser, cryogenic, and the like. Radio frequency ("RF") ablation catheters generally operate in the microwave frequency range and are used to destroy or ablate biological tissues for therapeutic purposes. In one application, microwave ablation catheters are used to ablate cardiac tissues that cause irregular heartbeats or arrhythmia, avoiding the need for more risky and invasive open heart surgery. In a microwave ablation procedure, the catheter- antenna is passed through the vein for access to the atrium. Within the atrium, the antenna is positioned at the desired location where ablation is required. An intracardiac electrogram is used to identify conductive pathways at the cardiac tissue site that needs to be ablated.
[03] Prior art ablation catheters have been equipped with two or more electrocardiogram ("ECG") electrode rings or buttons made of electrically conductive material to provide the necessary output signal for identification of the desired ablation site. Traditionally, all catheters used for this purpose are installed with metallic electrodes, regardless of energy mode (RF, ultrasound, laser, cryogenic, or the like). Installing metallic electrodes over a microwave antenna has special challenges. Naked metallic electrodes installed wrongly can absorb ablation energy and become hot. Hot electrodes can have adverse effects on the heart or other biological tissues or organs, such as blood clot formation, adherence to tissue, and tissue charring. Naked metallic electrodes can also impede efficient delivery of energy and hinder ablation efficiency. Additionally, metallic electrodes can separate from the catheter when it is bent, resulting in inaccurate or lost signals.
[04] Accordingly, what is needed is an efficient system and method for providing an ECG output signal from an ablation catheter device.
Summary
[05] The ablation catheter system of this invention comprises an elongate catheter adapted for insertion into a body vessel of a patient, the catheter having a distal end portion adapted for positioning adjacent a biological tissue site requiring treatment and a proximal end portion having a connector for connection to a control unit for controlling the ablation procedure, an antenna disposed at the distal end portion of the catheter for providing output energy for tissue ablation purposes, a pair of conductors extending through the catheter from the proximal end portion and connected to the antenna for providing power to the antenna from a power supply in the control unit, and at least one electrode formed of a flexible conductive material disposed at the distal end portion of the antenna and connected to the connector at the proximal end portion of the catheter for providing an output signal to the control unit. The flexible conductive material is at least substantially non-metallic.
[06] One or more electrodes may be disposed at the distal end portion of the catheter. In one embodiment, the electrode or electrodes are of conductive polymer material with hydrophilic characteristics for improved wetability. Two spaced electrode rings are mounted on or embedded in the outer surface of the cathode. Alternatively, one electrode ring may be provided and the other electrode may be a tip of conductive polymer material at the distal end of the catheter. In alternative embodiments, layers of conductive and nonconductive polymer material may be provided at specific positions at the distal end portion of the catheter to produce multiple working electrodes. In each case, the electrode output signal can be connected to a suitable electrode recording system inputs in the control unit or a separate electrocardiogram unit to provide intracardiac signal mapping. [07] This arrangement avoids the problems of metallic electrodes and also provides electrodes which are of a flexible polymer material which can bend readily with the distal end portion of the catheter as it is shaped or bent to negotiate a path through a body vessel. [08] Other features and advantages of the present invention will become more readily apparent to those of ordinary skill in the art after reviewing the following detailed description and accompanying drawings.
Brief Description of the Drawings
[09] The details of the present invention, both as to its structure and operation, may be gleaned in part by study of the accompanying drawings, in which like reference numerals refer to like parts, and in which:
[10] Figures IA and IB are side elevation views of a shapeable RF ablation catheter according to one embodiment in a straight and bent configuration, respectively;
[11] Figures 2A and 2B are side elevation views of a shapeable RF ablation catheter according to another embodiment with a different steering mechanism from Figure 1;
[12] Figures 3A and 3B are cross sectional views of the distal end portion of the tip of the catheter of Figure 1 or 2 in a straight configuration and a bent configuration, respectively;
[13] Figure 4 is a cross-sectional view of the tip or distal end portion of one embodiment of a shapeable or bendable RF ablation catheter incorporating electrodes;
[14] Figure 5 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter having a modified electrode arrangement according to another embodiment;
[15] Figure 6 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter with another electrode arrangement;
[16] Figure 7 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter with a modified electrode arrangement according to another embodiment; and
[17] Figure 8 is a cross-sectional view of the tip or distal end portion of a shapeable or bendable RF ablation catheter with modified electrodes according to another embodiment.
Detailed Description
[18] Certain embodiments as disclosed herein provide for systems and methods for ablation of biological tissues in body areas such as the heart, liver, and the like using a bendable radio-frequency (RF) catheter. The catheter is provided with electrodes of a flexible conductive material such as a conductive polymer at its distal end for providing an output signal such as an intracardiac electrocardiogram ("ECG") signal to a control unit to allow physicians to obtain tissue proximity and electrical conductivity information both before and after tissue ablation, as well as to provide other feedback during the ablation procedure.
[19] After reading this description, it will become apparent to one skilled in the art how to implement the invention in various alternative embodiments and alternative applications. However, although various embodiments of the present invention will be described herein, it is understood that these embodiments are presented by way of example only and not limitation. As such, this detailed description of various alternative embodiments should not be construed to limit the scope or breadth of the present invention as set forth in the appended claims.
[20] Figures IA and IB illustrate a radio-frequency ("RF") ablation catheter system 100 of one embodiment including a shapeable catheter device 100 adapted for insertion into a body vessel of a patient and incorporating an RF antenna for delivering electromagnetic energy to a treatment site, as described in more detail below.
[21] The catheter device 100 has a flexible, elongated tubular body 120 having a proximal portion 130 and a distal or tip portion 140. Located at the proximal portion of the body is a handle chassis 160 containing steering and positioning controls (not illustrated) for the body, activated by actuator 200. In the embodiment of Figures IA and IB, the tip portion of the catheter body is activated to bend between the straight configuration of Figure IA and the bent configuration of Figure IB by sliding the actuator back and forth in an axial direction. In the modified embodiment of Figures 2A and 2B, the tip portion is bent between the straight and bent configurations by rotating the actuator or collar 220. Suitable mechanisms for controlling bending of the tip portion of catheter body 120 are described in detail in U.S. Patent No. 7,004,938 of Ormsby et al., the contents of which are incorporated herein by reference. However, it will be understood that any suitable mechanism may be incorporated in the catheter device in order to control the bending or steering of the tip portion as it moves through a body vessel, organ, or cavity. [22] A coupling or electrical connector 170 is provided at the proximal end of the catheter device for connecting the catheter to a control unit or the like containing one or more electronic devices such as an RF generator and controller (not shown) for providing power to the antenna during an ablation procedure. Suitable signal control units are known in the ablation catheter field and are therefore not described in detail here. [23] The dimensions of the catheter body are adapted as required to suit the particular medical procedure, as is well known in the medical art. In one embodiment, the catheter is used to ablate cardiac tissue. However, the catheter may be used to ablate other types of body tissue in different organs, both internal and external to the body. The tubular body 120 of the catheter device may be generally constructed of a polymer material which is
bio-compatible with the body vessel environment. Examples of such materials include thermoplastic elastomer material such as Pebax® available from Autochem Germany, polyethylene, polyurethane, polyester, polyimide, polyamide, and the like, with varying degrees of radiopacity, hardness, and elasticity.
[24] The tubular body of the catheter may be formed with a plurality of segments using one or more of the aforementioned materials or equivalents, such that the catheter body 120 is progressively more flexible towards its distal end. The segments may be joined together by thermal bonding, butt joints, or adhesive bonding. Braiding reinforcement may be provided to the surface of the tubular body to attain a desirable level of stiffness and torsional strength for the catheter to advance and negotiate through the body vessel of the patient, while still allowing the distal end portion to be bent when needed. The distal end portion 140 may be of a softer polymer compound than the remainder of the body, with little or no braiding or reinforcement, to provide the desired flexibility for distal deflection and shaping of the apparatus.
[25] The structure of the catheter in one embodiment will now be described in more detail with reference to Figures 3A and 3B. As noted above, the catheter has a tubular body with a central bore 150 and a closed distal end or tip. The tip may be open in alternative embodiments. In the illustrated embodiment, deflection of the distal end portion of the catheter is accomplished by use of a pre-shaped deflection member 180 which is constrained in a straight orientation in the configuration of Figure 3 A and which adopts a bent shape when extended into the bent configuration of Figure 3B. However, it will be understood that other bending or shaping mechanisms may be used in alternative embodiments, as described, for example, in U.S. Patent No. 7,004,938 referenced above. The distal end portion 140 of the tubular body includes an RF antenna 250 comprising a flexible, helically coiled radiating antenna device 255 embedded in the flexible wall of the tubular body, as best illustrated in Figures 3A and 3B. The antenna device can therefore bend as the distal end portion is shaped to conform to a body vessel or the like, as illustrated in Figure 3B. Opposite ends of the antenna device are connected to electrical conductors or leads for connection to the proximal end connector 170 and thereby to a source of RF energy in the catheter control unit (not illustrated), as will be described in more detail below in connection with Figure 4. Other antenna devices may be provided in alternative embodiments, and the diameter, pitch and length of the coiled device 255, and the conductive material used for the device 255, may vary according to the particular procedure and flexibility requirements.
[26] The electrical conductors which connect the RF antenna to the connector 170 may be of a flexible mesh or braided wire construction 260 or of a thin-film electrically conductive material. In the embodiment illustrated in Figures 3A and 3B, the conductors are shown schematically as a mesh construction embedded in the walls of the tubular body 120 of the catheter. In alternative arrangements, separate conductors may be used to provide power to the antenna 250. Figure 4 illustrates the distal end portion 310 of a first embodiment of a modified catheter having integrated electrodes 312, 314. In one embodiment, the electrodes are ECG electrodes, although they may be other types of electrodes in other embodiments. Although two electrodes are illustrated in Figure 4, in other embodiments one electrode or more than two such electrodes may be provided. Some parts of the catheter of Figure 4 are identical to those in Figures 1 to 3 and like reference numerals have been used for like parts, as appropriate. In the embodiment of Figure 4, a pair of coaxial inner and outer tubular conductors 315, 316 extend along the length of the tubular body 318, with the outer conductor 316 connected to the proximal end of RF antenna 250 and the inner conductor 315 connected to the distal end of the RF antenna adjacent the tip of the catheter. The structure of the remainder of the tubular body 318 which is not shown in Figure 4 may be identical to that of tubular body 120 described above, and a similar connector 170 (not illustrated) may be provided at the proximal end of the catheter for connecting the conductors to a suitable RF source. The distal end portion illustrated in Figure 4 will be shapeable or bendable in a similar manner and using the same or similar control devices as were described above in connection with Figures 1 to 3.
[27] In the embodiment of Figure 4, the tubular body 318 is of dielectric material such as a non-conductive polymer and has a portion 320 of reduced outer diameter at its forward end. The first electrode 312 comprises a sleeve of flexible conductive material mounted over the reduced diameter end portion 320 of the tubular body and having an end portion or tip 322 extending over the open end of portion 320. The RF or microwave antenna 250 is embedded in the sleeve or electrode 312. The inner and outer conductors 315, 316 extend through the tubular body 318 as illustrated for connection to the opposite ends of the antenna coil 250. The second electrode 314 comprises a ring of flexible conductive material mounted over the tubular body 318 at a location spaced rearwardly from the rear end of conductive sleeve or electrode 312. The two electrodes may be secured over the inner tubular body 318 by adhesive, bonding, mechanical force, heat sealing or the like. The flexible conductive material forming the electrodes is at least
substantially non-metallic material and may be a conductive polymer material which is sufficiently bendable to allow bending of the distal end portion 310 between the positions illustrated in Figures IA and IB.
[28] In an alternative embodiment, the electrode ring 314 may be mounted flush in an annular recess or gap in the outer surface of the tubular body, or may be molded integrally with the tubular body, so that it does not project outwardly from the outer surface of the body 318. A conductor or connector 324 extends from electrode ring 314 to the connector 170 at the proximal end of the catheter, for suitable connection to an ECG monitor or the like in a control unit (not illustrated) for the catheter. Conductor 324 is shown spaced from the outer surface of body 318 in Figure 4 for clarity, but may be a line of conductive ink or adhesive over the outer surface of the tubular body, or may alternatively be embedded in the body 318 outside conductor 316, One of the conductors 315 or 316 will also be connected to the ECG or other monitor for suitable monitoring of the signal detected between the two electrodes 312, 314. In one embodiment, both electrodes are of a flexible, conductive polymer material, i.e. a polymer material loaded with conductive materials.
[29] Figure 5 illustrates the distal end portion 325 of a catheter with a modified electrode arrangement in which the electrode ring 314 of Figure 4 is replaced by an electrode end cap 330. Electrodes 312, 330 are of flexible conductive material such as a conductive polymer material as in Figure 4. In this embodiment, the conductive sleeve 312 in which the antenna is mounted has an outer cover layer 332 of non-conductive polymer material extending along at least part of its length and over its distal end, providing a non-conductive shield layer between the first and second electrodes 312, 330. A conductor or connector wire 334 extends from the connector at the proximal end of the catheter through the central lumen 150 of the tubular body 318 and into the electrode end cap 330 to provide a signal path between the electrode and the ECG monitor. The catheter of Figure 5 is otherwise identical to that of the previous embodiment and like reference numerals have been used as appropriate. Conductive sleeve 312, non-conductive layer 332, and end cap 330 may be laminated together over the tubular body 318 by any suitable means such as bonding, heat sealing, adhesive, or the like.
[30] Figure 6 illustrates the distal end portion 340 of a catheter having another modified electrode arrangement. Parts of the cathode of this embodiment are identical to those of Figures 4 and 5 and like reference numerals have been used for like parts as appropriate. Unlike the previous embodiments, the sleeve 335 in which the antenna coil 250 is
embedded does not comprise one of the two electrodes. As in the previous embodiment, sleeve 335 is mounted over the reduced diameter end portion 320 of the tubular body 318, which is of dielectric or non-conductive material, and the antenna coil 250 is connected at its opposite ends to the distal ends of the inner and outer conductors 315, 316. [31] In the embodiment of Figure 6, an outer layer 336 of non-conductive material, such as a non-conductive polymer material, extends over the conductive sleeve 335 and has an end cap portion 338 extending over the tip of the tubular body 318. The electrodes in this embodiment comprise a pair of conductive rings 339, 341 mounted at spaced intervals on the outer, non-conductive layer 336. The ring electrodes may be of conductive polymer material. The first ring 339 is positioned adjacent the non-conductive end cap portion 338 and the second ring 341 is positioned adjacent the rear end of the conductive layer 336. A central conductor or connector wire 342 extends through the hollow central bore or lumen of the tubular body 318, through the non-conductive end cap portion 338, and bends back to terminate in the first conductive ring electrode 339. In one embodiment, the part of connector wire 342 shown extending through lumen 150 may be a line of conductive ink or adhesive on the inner surface of tubular body 318. A second conductor or connector wire 343 extends along the outside of the tubular body 318 and is connected to the second conductive ring electrode 341. It will be understood that the connector wire 343 may comprise a line of conductive ink or adhesive on tubular body 318, or may alternatively be embedded in the tubular body 318 at location spaced outside the outer tubular conductor 316. The various conductive and non-conductive polymer layers of the distal end portion 340, including the electrode rings, are suitably laminated together by heat sealing, adhesive bonding, or the like.
[32] Also shown in Figure 6 is a pull wire 355 which extends through the lumen 150 to the tip 338 and is attached to suitable steering and positioning controls (not illustrated) at the proximal end of the catheter, for controlling bending of the distal end portion. Such a pull wire mechanism is described in U.S. Patent No. 7,004,938 referenced above, the contents of which are incorporated herein by reference. It may be understood that a similar position control mechanism will be provided in the embodiments of Figures 4 to 6, or the mechanism 180 of Figure 3 may be provided in any of these embodiments. [33] Figure 7 illustrates the distal end portion 400 of a catheter according to another embodiment. Again, some parts of the catheter illustrated in Figure 7 are identical to those of Figures 4 to 6 and like reference numerals have been used as appropriate. As in the previous embodiment, a tubular body 318 of flexible dielectric material extends the length
of the catheter and has a central through bore or lumen 150 and an end portion 320 of reduced outer diameter over which the sleeve 312 containing embedded RF antenna 250 is mounted. As in the previous embodiments, sleeve 312 is of conductive polymer material and the ends of the antenna are connected to the distal end connector 170 (Figure 1) of the catheter by means of inner and outer cylindrical conductors 315, 316 extending through the tubular body 318, in the manner described above in connection with Figure 1. Unlike the previous embodiments, an outer cover layer 345 of non-conductive polymer material extends along the entire length of the catheter, over the tubular body 318 and sleeve 312, and has a forward end or tip 344 covering the forward end of the sleeve and tubular body. A pair of contact rings 346,348 are mounted in the outer cover layer 345 in the distal end portion of the catheter, with the forward contact ring 346 located over the sleeve 312 and in electrical contact with the sleeve, and the rear contact ring 348 located slightly rearwardly from sleeve 312. Each ring is of a flexible conductive material such as conductive polymer material. Rings 346,348 and outer cover layer 345 are suitably bonded together and laminated over the tubular body 318 and conductive polymer sleeve 312. [34] The forward contact ring 346 is connected to the proximal end connector 170 via the conductive sleeve 312 and the outer conductor 316 which also provides power to the antenna 250. The rear contact ring 348 is connected to a conductive wire 350 which extends through the tubular body 318 to the proximal end connector 170 of the catheter. The conductors 316, 350 therefore provide the output for the ECG monitor in the control unit in this embodiment.
[35] The embodiment of Figure 7 also includes a temperature sensor 352 in the lumen 150 adjacent the tip of the catheter. In the illustrated embodiment, the temperature sensor 352 may be a thermistor, thermocouple, or the like and has a thermocouple junction or sensor end 352 and a pair of braided wires or conductors 354 extending from the sensor 352 through the tubular body to the connector 170 at the proximal end of the catheter, where they are connected to control circuitry for monitoring the temperature at the distal end of the catheter and controlling the antenna operation. A pull wire 355 is attached to the tip 344 of the catheter and extends through the central lumen 150 through the length of the catheter for attachment to a suitable steering and control mechanism (not illustrated), as in the previous embodiment.
[36] A system for monitoring and controlling operation of an RF ablation catheter incorporating a temperature sensor is described in co-pending application Serial No. 11/479,259 filed on June 30, 2006, the contents of which are incorporated herein by
reference. It will be understood that a similar control system may be provided for controlling operation of the microwave antenna in this embodiment or other embodiments described above, with suitable inclusion of a temperature sensor.
[37] Figure 8 illustrates a modification of the embodiment of Figure 5, and like reference numerals are used for like parts as appropriate. In this embodiment, as in the previous embodiments, a tubular body 318 of dielectric material having a central lumen 150 extends the entire length of the catheter, and has a reduced outer diameter portion 320 at the distal end portion 500 of the catheter. Conductive sleeve 312 is mounted over the portion 320 and the RF antenna 250 is embedded in sleeve 312. As in the embodiment of Figure 5, the electrodes comprise the conductive sleeve 312 and a conductive tip 330 mounted over the end of the catheter, with a layer 332 of non-conductive material such as non-conductive polymer between the electrodes 312 and 330. The various layers of conductive and non-conductive materials in the embodiment of Figure 8 will also be laminated together by any suitable means such as heat, adhesives and mechanical force. [38] In Figure 8, the conductive wire 334 which is connected to the conductive tip electrode 330 of Figure 5 is eliminated, and is replaced with double thermocouple wires 510 which extend through lumen 150 from the proximal end connector 170 of the catheter and into the conductive tip electrode 330, with a thermocouple junction 512 at the end of the double wires providing a temperature sensor. The thermocouple wires therefore have the dual function of providing a temperature sensor output as well as providing an ECG monitor output in combination with outer antenna conductor 316. The ECG output may be measured between conductor 316 and either one of the thermocouple wires 510. The temperature output may be used in monitoring and controlling operation of the RF antenna, as described above in connection with Figure 7.
[39] In each of the embodiments of Figures 4 to 8, electrodes are mounted at the distal end portion of a shapeable or bendable catheter to allow physicians to locate a tissue region causing problems and to obtain both optimum tissue proximity and electrical conductive activities before and after ablation, as well as to obtain feedback of their actions. Although two electrodes are provided in these embodiments, only one electrode or more than two electrodes may be provided in other embodiments. The electrode or electrodes in these embodiments may be ECG or other types of electrodes. Radio-opaque markers (not illustrated) at the distal end portion of the catheter may also be used to aid in positioning the tip of the catheter, as is known in the field. Where the electrodes are ECG electrodes, it will be understood that the conductor wires connected to the electrodes and
to the proximal end connector 170 of the catheter will communicate with an external ECG system and monitor (not illustrated) via a suitable connection cable which will transmit ECG signals between the electrodes and ECG system. The antenna conductors and thermocouple wires (if a temperature sensor is present) will be similarly connected to an appropriate antenna output control system.
[40] In each of the above embodiments, the RF antenna 250 is adapted to receive and radiate electromagnetic energy in order to treat a selected biological tissue site. An example of a suitable spectrum of radio frequency energy for use in the ablation catheter is that of the microwave frequency range above 300 MHz. The RF antenna is capable of applying substantially uniformly distributed electromagnetic field energy along the RF antenna in a direction substantially normal to the longitudinal axis of antenna 250. [41] The electrodes in the embodiments of Figures 4 to 8 are made of a suitable flexible conductive material, so that they can bend with the remainder of the distal end portion during steering. Such electrodes avoid or reduce the problems encountered with metallic electrodes, since they do not absorb microwave energy to any great extent and do not become excessively hot. The electrodes may be of an at least substantially non-metallic material, and in one embodiment they are made from a conductive polymer material such as nylon, polyethylene, polyolefϊn, polypropylene, polycarbonate, Pebax ®, TPE (thermoplastic elastomers) and blends, loaded with a selective conductive material. Other non-conductive parts of the catheter may be of the same polymer material or different polymer materials. The conductive material may be micro-carbon spheres, carbon particles, carbon nanotubes, nickel dust, or the like. The electrodes may be made entirely of conductive polymer material or may be a mixture of conductive and non-conductive polymer material, or a mixture of conductive and non-conductive materials with metal substrates. The composite polymer material is selected to have a relatively low resistance for reduced interference with the microwave radiation pattern, and to be hydrophilic for improved wetability on the outer surface of the catheter.
[42] Communication between the electrodes and the connector 170 at the proximal end of the catheter may be provided in some embodiments by means of conductive ink or adhesive applied over the polymer surface. For example, conductor 324 of Figure 4 or conductor 342 of Figure 6 may be a line of conductive ink or adhesive over the outer surface of the tubular body 318 extending from electrode ring 314 to the proximal end of the catheter. Conductor 350 of Figure 7 may be a line of conductive ink or adhesive over
the outer surface of non-conductive tubular body 318, with the outer layer 345 of non- conductive polymer laminated over the tubular body and conductor line 350. [43] Heat energy, adhesives, and/or mechanical force may be used to laminate the conductive and non-conductive polymer layers in the embodiments of Figures 4 to 8. Metallic substrates may also be laminated between the polymer layers, such as the inner and outer tubular conductors which provide power for operating RF antenna 250. [44] The above description of the disclosed embodiments is provided to enable any person skilled in the art to make or use the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles described herein can be applied to other embodiments without departing from the spirit or scope of the invention. Thus, it is to be understood that the description and drawings presented herein represent a presently preferred embodiment of the invention and are, therefore, representative of the subject matter which is broadly contemplated by the present invention. It is further understood that the scope of the present invention fully encompasses other embodiments that may become obvious to those skilled in the art and that the scope of the present invention is accordingly limited by nothing other than the appended claims.
Claims
1. An RF ablation catheter apparatus, comprising:
an elongate catheter adapted for insertion into a body vessel of a patient, the catheter having a proximal end and a distal end portion, at least the distal end portion of the catheter being flexible for allowing the distal end portion of the catheter to be deflected;
a radio-frequency ("RF") antenna disposed at the distal end portion of the catheter and adapted to receive input RF energy for the ablation of biological tissue;
an electrical connector at the proximal end of the catheter for connection to a power supply for the RF antenna; and
at least one electrode disposed at the distal end portion of the catheter and electrically coupled to the connector at the proximal end of the catheter for connection to a monitor;
the electrode being of a flexible, electrically conductive material.
2. The apparatus of claim 1, wherein the electrode is an electrocardiogram ("ECG") electrode.
3. The apparatus of claim 1, wherein the electrode material is an at least substantially non-metallic material.
4. The apparatus of claim 3, wherein the electrode material is a flexible conductive polymer material.
5. The apparatus of claim 1, wherein the electrically conductive material comprises a flexible polymer material loaded with a conductive material.
6. The apparatus of claim 5, wherein the polymer is selected from the group consisting of polyethylene, polyolefϊn, polypropylene, polycarbonate, nylon and thermoplastic elastomer material.
7. The apparatus of claim 5, wherein the conductive material is selected from the group consisting of micro-carbon spheres, carbon particles, carbon nanotubes, and nickel dust.
8. The apparatus of claim 1, further comprising at least one electrical conductor extending through the catheter and coupled at a first end to the antenna and to the proximal end connector at a second end.
9. The apparatus of claim 1 , wherein the catheter comprises a tubular body and the electrode comprises a ring mounted on said tubular body.
10. The apparatus of claim 1, wherein at least two spaced electrodes are disposed at the distal end portion of the catheter.
11. The apparatus of claim 10, wherein at least a portion of the tubular body at the distal end of the catheter is of non-conductive material and said electrodes comprise spaced rings on the non-conductive portion of said tubular body.
12. The apparatus of claim 1, wherein the electrode comprises an elongate sleeve at the distal end portion of said catheter.
13. The apparatus of claim 11, wherein the antenna comprises a helical coil embedded in said electrode sleeve, and at least one electrical conductor for connecting the antenna to an RF power source to provide an electrical connection from said electrode sleeve to said proximal end connector.
14. The apparatus as claimed in claim 13, wherein the electrical conductor is coupled to a first end of the helical coil and a second electrical conductor is coupled to a second end of the helical coil and extends through the catheter to the proximal end connector.
15. The apparatus as claimed in claim 11, further comprising a second electrode of flexible, electrically conductive material spaced from said conductive electrode sleeve.
16. The apparatus as claimed in claim 11, further comprising an outer layer of non- conductive material extending over at least part of the electrode sleeve, and a second electrode of flexible, electrically conductive material mounted on said outer layer.
17. The apparatus as claimed in claim 16, wherein the second electrode comprises an end cap extending over the distal end of the catheter and at least part of the said outer layer.
18. The apparatus as claimed in claim 17, further comprising an electrical conductor extending through said catheter and coupled to said end cap for electrically connecting the end cap to the proximal end connector of the catheter.
19. The apparatus as claimed in claim 1, further comprising a temperature sensor mounted in the distal end portion of the catheter and a pair of thermocouple wires connected to said temperature sensor and extending through the catheter to said proximal end connector.
20. The apparatus as claimed in claim 19, wherein said temperature sensor is coupled to the electrode and one of said thermocouple wires further comprises the electrical coupling from the second electrode to the proximal end connector.
21. The apparatus as claimed in claim 20, wherein the electrode comprises an end cap at the distal end of the catheter, and the temperature sensor is embedded in the end cap.
22. The apparatus as claimed in claim 1, wherein the catheter comprises a tubular body extending from the proximal end to the distal end of the catheter, the tubular body being of non-conductive material, and an outer sleeve of conductive material mounted over the distal end portion of the tubular body and containing the RF antenna, the electrode comprising a ring electrically isolated from the outer sleeve.
23. The apparatus as claimed in claim 22, wherein the electrode ring is mounted over the tubular body at a location spaced from the outer sleeve.
24. The apparatus as claimed in claim 23, wherein the outer sleeve comprises a second electrode electrically coupled to the proximal end connector.
25. The apparatus as claimed in claim 23, further comprising a layer of non-conductive material extending along at least part of the length of the outer sleeve, and a second electrode mounted on said layer of non-conductive material.
26. The apparatus as claimed in claim 1, further comprising a deflection member adapted to control deflection of the distal end portion of the catheter.
27. An RF ablation catheter apparatus, comprising: an elongate catheter adapted for insertion into a body vessel of a patient, the catheter having a proximal end and a distal end portion, at least the distal end portion of the catheter being flexible for allowing the distal end portion of the catheter to be deflected; a radio-frequency antenna disposed at the distal end portion of the catheter and adapted to receive input RF energy for ablation of biological tissue; an electrical connector at the proximal end of the catheter for connection to a power supply for the RF antenna; a pair of inner and outer coaxial electrical conductors extending through the cathode from said antenna to said electrical connector; and at least one electrode disposed at the distal end portion of the catheter and electrically coupled to the connector at the proximal end of the catheter for connection to a monitor, the electrode being of a flexible, electrically conductive material.
28. The apparatus of claim 27, wherein the antenna comprises a helical coil embedded in the distal end portion of the catheter, the coil having first and second ends, and the coaxial electrical conductors being coupled to the first and second ends of the coil, respectively.
29. The apparatus of claim 27, wherein the electrode comprises an elongate sleeve at the distal end portion of the catheter.
30. The apparatus of claim 29, further comprising a second electrode of flexible, electrically conductive material spaced from the conductive electrode sleeve.
31. The apparatus of claim 29, wherein the antenna is embedded in said electrode sleeve.
32. The apparatus of claim 27, wherein at least two spaced electrodes of flexible, electrically conductive material are disposed at the distal end portion of the catheter and coupled to the electrical connector for connection to a monitor.
33. The apparatus of claim 32, wherein the electrode material is a flexible conductive polymer material.
34. The apparatus of claim 32, wherein the electrodes comprise spaced electrode rings.
Priority Applications (3)
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ES07853876.6T ES2546754T3 (en) | 2006-10-19 | 2007-10-09 | Ablation catheter apparatus with one or more electrodes |
EP07853876.6A EP2073738B1 (en) | 2006-10-19 | 2007-10-09 | Ablation catheter apparatus with one or more electrodes |
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US11/551,162 US20070066972A1 (en) | 2001-11-29 | 2006-10-19 | Ablation catheter apparatus with one or more electrodes |
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Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2014064552A1 (en) * | 2012-10-26 | 2014-05-01 | Koninklijke Philips N.V. | System, catheter and planning method for hyperthermia-adjuvant brachytherapy |
GB2564942A (en) * | 2017-06-01 | 2019-01-30 | Creo Medical Ltd | Electrosurgical instrument for ablation and resection |
US11324408B2 (en) | 2011-08-26 | 2022-05-10 | Symap Medical (Suzhou), Ltd | Mapping sympathetic nerve distribution for renal ablation and catheters for same |
Families Citing this family (241)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US20070066972A1 (en) * | 2001-11-29 | 2007-03-22 | Medwaves, Inc. | Ablation catheter apparatus with one or more electrodes |
US6702811B2 (en) | 1999-04-05 | 2004-03-09 | Medtronic, Inc. | Ablation catheter assembly with radially decreasing helix and method of use |
WO2003047448A1 (en) * | 2001-11-29 | 2003-06-12 | Medwaves, Inc. | Radio-frequency-based catheter system with improved deflection and steering mechanisms |
US7087061B2 (en) * | 2002-03-12 | 2006-08-08 | Lithotech Medical Ltd | Method for intracorporeal lithotripsy fragmentation and apparatus for its implementation |
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 |
US20080213331A1 (en) | 2002-04-08 | 2008-09-04 | Ardian, Inc. | Methods and devices for renal nerve blocking |
US7620451B2 (en) | 2005-12-29 | 2009-11-17 | Ardian, Inc. | Methods and apparatus for pulsed electric field neuromodulation via an intra-to-extravascular approach |
US9308043B2 (en) | 2002-04-08 | 2016-04-12 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for monopolar renal neuromodulation |
US8131371B2 (en) * | 2002-04-08 | 2012-03-06 | Ardian, Inc. | Methods and apparatus for monopolar renal neuromodulation |
US6978174B2 (en) | 2002-04-08 | 2005-12-20 | Ardian, Inc. | Methods and devices for renal nerve blocking |
US8145317B2 (en) * | 2002-04-08 | 2012-03-27 | Ardian, Inc. | Methods for renal neuromodulation |
US8774922B2 (en) | 2002-04-08 | 2014-07-08 | Medtronic Ardian Luxembourg S.A.R.L. | Catheter apparatuses having expandable balloons for renal neuromodulation and associated systems and methods |
US8145316B2 (en) | 2002-04-08 | 2012-03-27 | Ardian, Inc. | Methods and apparatus for renal neuromodulation |
US8150520B2 (en) | 2002-04-08 | 2012-04-03 | Ardian, Inc. | Methods for catheter-based renal denervation |
US8150519B2 (en) | 2002-04-08 | 2012-04-03 | Ardian, Inc. | Methods and apparatus for bilateral renal neuromodulation |
US7617005B2 (en) | 2002-04-08 | 2009-11-10 | Ardian, Inc. | Methods and apparatus for thermally-induced renal neuromodulation |
US7162303B2 (en) | 2002-04-08 | 2007-01-09 | Ardian, Inc. | Renal nerve stimulation method and apparatus for treatment of patients |
US9308044B2 (en) | 2002-04-08 | 2016-04-12 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for therapeutic renal neuromodulation |
US20140018880A1 (en) | 2002-04-08 | 2014-01-16 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for monopolar renal neuromodulation |
US7756583B2 (en) | 2002-04-08 | 2010-07-13 | Ardian, Inc. | Methods and apparatus for intravascularly-induced neuromodulation |
US9636174B2 (en) | 2002-04-08 | 2017-05-02 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for therapeutic renal neuromodulation |
US7653438B2 (en) | 2002-04-08 | 2010-01-26 | Ardian, Inc. | Methods and apparatus for renal neuromodulation |
US20070135875A1 (en) * | 2002-04-08 | 2007-06-14 | Ardian, Inc. | Methods and apparatus for thermally-induced renal neuromodulation |
US8774913B2 (en) * | 2002-04-08 | 2014-07-08 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and apparatus for intravasculary-induced neuromodulation |
US7853333B2 (en) | 2002-04-08 | 2010-12-14 | Ardian, Inc. | Methods and apparatus for multi-vessel renal neuromodulation |
US20070129761A1 (en) | 2002-04-08 | 2007-06-07 | Ardian, Inc. | Methods for treating heart arrhythmia |
US20040082859A1 (en) | 2002-07-01 | 2004-04-29 | Alan Schaer | Method and apparatus employing ultrasound energy to treat body sphincters |
US7722601B2 (en) | 2003-05-01 | 2010-05-25 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
JP2007504910A (en) | 2003-09-12 | 2007-03-08 | ミノウ・メディカル・エルエルシイ | Selectable biased reshaping and / or excision of atherosclerotic material |
WO2005050151A1 (en) | 2003-10-23 | 2005-06-02 | Sherwood Services Ag | Thermocouple measurement circuit |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US9713730B2 (en) | 2004-09-10 | 2017-07-25 | Boston Scientific Scimed, Inc. | Apparatus and method for treatment of in-stent restenosis |
US8396548B2 (en) | 2008-11-14 | 2013-03-12 | Vessix Vascular, Inc. | Selective drug delivery in a lumen |
US7771411B2 (en) | 2004-09-24 | 2010-08-10 | Syntheon, Llc | Methods for operating a selective stiffening catheter |
US7947039B2 (en) * | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
CA2574934C (en) | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US9814372B2 (en) | 2007-06-27 | 2017-11-14 | Syntheon, Llc | Torque-transmitting, variably-flexible, locking insertion device and method for operating the insertion device |
US10123683B2 (en) | 2006-03-02 | 2018-11-13 | Syntheon, Llc | Variably flexible insertion device and method for variably flexing an insertion device |
WO2007112081A1 (en) | 2006-03-24 | 2007-10-04 | Micrablate | Transmission line with heat transfer ability |
JP4621621B2 (en) * | 2006-03-31 | 2011-01-26 | 株式会社東芝 | Charged beam lithography system |
US8019435B2 (en) | 2006-05-02 | 2011-09-13 | Boston Scientific Scimed, Inc. | Control of arterial smooth muscle tone |
US11389235B2 (en) | 2006-07-14 | 2022-07-19 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10376314B2 (en) | 2006-07-14 | 2019-08-13 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
AU2007310991B2 (en) | 2006-10-18 | 2013-06-20 | Boston Scientific Scimed, Inc. | System for inducing 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 |
WO2008049082A2 (en) | 2006-10-18 | 2008-04-24 | Minnow Medical, Inc. | Inducing desirable temperature effects on body tissue |
JP2008235464A (en) * | 2007-03-19 | 2008-10-02 | Toshiba Corp | Electron-beam drafting apparatus |
US7976537B2 (en) * | 2007-06-28 | 2011-07-12 | Biosense Webster, Inc. | Optical pyrometric catheter for tissue temperature monitoring during cardiac ablation |
US8123745B2 (en) * | 2007-06-29 | 2012-02-28 | Biosense Webster, Inc. | Ablation catheter with optically transparent, electrically conductive tip |
US20090082762A1 (en) * | 2007-09-20 | 2009-03-26 | Ormsby Theodore C | Radio frequency energy transmission device for the ablation of biological tissues |
US8118809B2 (en) * | 2007-12-21 | 2012-02-21 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Flexible conductive polymer electrode and method for ablation |
US8353907B2 (en) * | 2007-12-21 | 2013-01-15 | Atricure, Inc. | Ablation device with internally cooled electrodes |
US8175679B2 (en) * | 2007-12-26 | 2012-05-08 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Catheter electrode that can simultaneously emit electrical energy and facilitate visualization by magnetic resonance imaging |
US9675410B2 (en) * | 2007-12-28 | 2017-06-13 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Flexible polymer electrode for MRI-guided positioning and radio frequency ablation |
US8133222B2 (en) * | 2008-05-28 | 2012-03-13 | Medwaves, Inc. | Tissue ablation apparatus and method using ultrasonic imaging |
US8679106B2 (en) * | 2008-07-01 | 2014-03-25 | Medwaves, Inc. | Angioplasty and tissue ablation apparatus and method |
EP2813192A3 (en) * | 2008-10-21 | 2015-04-15 | Microcube, LLC | Methods and devices for applying energy to bodily tissues |
US11219484B2 (en) | 2008-10-21 | 2022-01-11 | Microcube, Llc | Methods and devices for delivering microwave energy |
US9980774B2 (en) | 2008-10-21 | 2018-05-29 | Microcube, Llc | Methods and devices for delivering microwave energy |
US11291503B2 (en) * | 2008-10-21 | 2022-04-05 | Microcube, Llc | Microwave treatment devices and methods |
CN102245119B (en) * | 2008-10-21 | 2017-06-06 | 微立方有限责任公司 | Energy is applied to the method and device of bodily tissue |
JP5406933B2 (en) * | 2008-11-10 | 2014-02-05 | マイクロキューブ, エルエルシー | Method and apparatus for applying energy to body tissue |
CN102271603A (en) | 2008-11-17 | 2011-12-07 | 明诺医学股份有限公司 | Selective accumulation of energy with or without knowledge of tissue topography |
US8652129B2 (en) | 2008-12-31 | 2014-02-18 | Medtronic Ardian Luxembourg S.A.R.L. | Apparatus, systems, and methods for achieving intravascular, thermally-induced renal neuromodulation |
US20100168739A1 (en) * | 2008-12-31 | 2010-07-01 | Ardian, Inc. | Apparatus, systems, and methods for achieving intravascular, thermally-induced renal neuromodulation |
EP2376011B1 (en) | 2009-01-09 | 2019-07-03 | ReCor Medical, Inc. | Apparatus for treatment of mitral valve insufficiency |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
US8934989B2 (en) * | 2009-04-15 | 2015-01-13 | Medwaves, Inc. | Radio frequency based ablation system and method with dielectric transformer |
US9326819B2 (en) * | 2009-04-15 | 2016-05-03 | Medwaves, Inc. | Electrically tunable tissue ablation system and method |
US8926605B2 (en) | 2012-02-07 | 2015-01-06 | Advanced Cardiac Therapeutics, Inc. | Systems and methods for radiometrically measuring temperature during tissue ablation |
US9226791B2 (en) | 2012-03-12 | 2016-01-05 | Advanced Cardiac Therapeutics, Inc. | Systems for temperature-controlled ablation using radiometric feedback |
US9277961B2 (en) | 2009-06-12 | 2016-03-08 | Advanced Cardiac Therapeutics, Inc. | Systems and methods of radiometrically determining a hot-spot temperature of tissue being treated |
US8954161B2 (en) | 2012-06-01 | 2015-02-10 | Advanced Cardiac Therapeutics, Inc. | Systems and methods for radiometrically measuring temperature and detecting tissue contact prior to and during tissue ablation |
WO2012116265A2 (en) * | 2011-02-24 | 2012-08-30 | MRI Interventions, Inc. | Mri-guided catheters |
EP3549544B1 (en) | 2009-07-28 | 2021-01-06 | Neuwave Medical, Inc. | Ablation system |
US9375273B2 (en) * | 2009-09-18 | 2016-06-28 | Covidien Lp | System and method for checking high power microwave ablation system status on startup |
CN102711648B (en) | 2009-11-30 | 2015-07-29 | 麦迪威公司 | There is the radio frequency ablation system of tracking transducer |
US9743980B2 (en) * | 2010-02-24 | 2017-08-29 | Safepass Vascular Ltd | Method and system for assisting a wire guide to cross occluded ducts |
US8777963B2 (en) | 2010-02-24 | 2014-07-15 | Lithotech Medical Ltd | Method and system for destroying of undesirable formations in mammalian body |
US20110213355A1 (en) * | 2010-03-01 | 2011-09-01 | Vivant Medical, Inc. | Sensors On Patient Side for a Microwave Generator |
EP2555699B1 (en) | 2010-04-09 | 2019-04-03 | 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 |
US8870863B2 (en) | 2010-04-26 | 2014-10-28 | Medtronic Ardian Luxembourg S.A.R.L. | Catheter apparatuses, systems, and methods for renal neuromodulation |
JP6153865B2 (en) | 2010-05-03 | 2017-06-28 | ニューウェーブ メディカル, インコーポレイテッドNeuwave Medical, Inc. | Energy delivery system |
US10799263B2 (en) * | 2010-05-07 | 2020-10-13 | Carefusion 2200, Inc. | Catheter design for use in treating pleural diseases |
US8473067B2 (en) | 2010-06-11 | 2013-06-25 | Boston Scientific Scimed, Inc. | Renal denervation and stimulation employing wireless vascular energy transfer arrangement |
US9358365B2 (en) | 2010-07-30 | 2016-06-07 | Boston Scientific Scimed, Inc. | Precision electrode movement control for renal nerve ablation |
US9463062B2 (en) | 2010-07-30 | 2016-10-11 | Boston Scientific Scimed, Inc. | Cooled conductive balloon RF 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 |
US9084609B2 (en) | 2010-07-30 | 2015-07-21 | Boston Scientific Scime, Inc. | Spiral balloon catheter 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 |
EP2632373B1 (en) | 2010-10-25 | 2018-07-18 | Medtronic Ardian Luxembourg S.à.r.l. | System for evaluation and feedback of neuromodulation treatment |
KR101912960B1 (en) | 2010-10-25 | 2018-10-29 | 메드트로닉 아르디언 룩셈부르크 에스에이알엘 | Catheter Appratuses having Multi-Electrode Arrays for Renal Neuromodulation and Associated Systems and Methods |
CN106377312B (en) | 2010-10-25 | 2019-12-10 | 美敦力Af卢森堡有限责任公司 | Microwave catheter apparatus, systems, and methods for renal neuromodulation |
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 |
US20120123326A1 (en) * | 2010-11-12 | 2012-05-17 | Christian Steven C | Catheter systems with distal end function, such as distal deflection, using remote actuation or low input force |
US9028485B2 (en) | 2010-11-15 | 2015-05-12 | Boston Scientific Scimed, Inc. | Self-expanding cooling electrode for renal nerve ablation |
US9668811B2 (en) | 2010-11-16 | 2017-06-06 | Boston Scientific Scimed, Inc. | Minimally invasive access 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 |
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 |
US9192435B2 (en) | 2010-11-22 | 2015-11-24 | Boston Scientific Scimed, Inc. | Renal denervation catheter with cooled RF electrode |
US9023034B2 (en) | 2010-11-22 | 2015-05-05 | Boston Scientific Scimed, Inc. | Renal ablation electrode with force-activatable conduction apparatus |
US20120157993A1 (en) | 2010-12-15 | 2012-06-21 | Jenson Mark L | Bipolar Off-Wall Electrode Device for Renal Nerve Ablation |
WO2012095873A1 (en) * | 2011-01-11 | 2012-07-19 | Quanta System S.P.A. | Laser surgery device |
US9220561B2 (en) | 2011-01-19 | 2015-12-29 | Boston Scientific Scimed, Inc. | Guide-compatible large-electrode catheter for renal nerve ablation with reduced arterial injury |
US8968297B2 (en) | 2011-07-19 | 2015-03-03 | Covidien Lp | Microwave and RF ablation system and related method for dynamic impedance matching |
US9028482B2 (en) | 2011-07-19 | 2015-05-12 | Covidien Lp | Microwave and RF ablation system and related method for dynamic impedance matching |
US9192422B2 (en) | 2011-07-19 | 2015-11-24 | Covidien Lp | System and method of matching impedances of an electrosurgical generator and/or a microwave generator |
AU2012283908B2 (en) | 2011-07-20 | 2017-02-16 | Boston Scientific Scimed, Inc. | Percutaneous devices and methods to visualize, target and ablate nerves |
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 |
US9014821B2 (en) | 2011-08-26 | 2015-04-21 | Symap Holding Limited | System and method for locating and identifying the functional nerves innervating the wall of arteries and catheters for same |
US9820811B2 (en) | 2011-08-26 | 2017-11-21 | Symap Medical (Suzhou), Ltd | System and method for mapping the functional nerves innervating the wall of arteries, 3-D mapping and catheters for same |
CN103271766B (en) * | 2012-08-24 | 2015-08-26 | 苏州信迈医疗器械有限公司 | A kind of for mapping and melt the device being positioned at the kidney nerve that renal artery distributes |
US8692992B2 (en) | 2011-09-22 | 2014-04-08 | Covidien Lp | Faraday shield integrated into sensor bandage |
US8726496B2 (en) | 2011-09-22 | 2014-05-20 | Covidien Lp | Technique for remanufacturing a medical sensor |
US9186210B2 (en) | 2011-10-10 | 2015-11-17 | Boston Scientific Scimed, Inc. | Medical devices including ablation electrodes |
US9420955B2 (en) | 2011-10-11 | 2016-08-23 | Boston Scientific Scimed, Inc. | Intravascular temperature monitoring system and method |
WO2013055815A1 (en) | 2011-10-11 | 2013-04-18 | Boston Scientific Scimed, Inc. | Off -wall electrode device for nerve modulation |
US9364284B2 (en) | 2011-10-12 | 2016-06-14 | Boston Scientific Scimed, Inc. | Method of making an off-wall spacer cage |
EP2768568B1 (en) | 2011-10-18 | 2020-05-06 | Boston Scientific Scimed, Inc. | Integrated crossing balloon catheter |
EP2768563B1 (en) | 2011-10-18 | 2016-11-09 | Boston Scientific Scimed, Inc. | Deflectable medical devices |
CN104023662B (en) | 2011-11-08 | 2018-02-09 | 波士顿科学西美德公司 | Hole portion renal nerve melts |
US9119600B2 (en) | 2011-11-15 | 2015-09-01 | 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 |
WO2013096803A2 (en) | 2011-12-21 | 2013-06-27 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US9265969B2 (en) | 2011-12-21 | 2016-02-23 | Cardiac Pacemakers, Inc. | Methods for modulating cell function |
EP3138521B1 (en) | 2011-12-23 | 2019-05-29 | Vessix Vascular, Inc. | 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 |
US10905494B2 (en) | 2011-12-29 | 2021-02-02 | St. Jude Medical, Atrial Fibrillation Division, Inc | Flexible conductive polymer based conformable device and method to create linear endocardial lesions |
US9050106B2 (en) | 2011-12-29 | 2015-06-09 | Boston Scientific Scimed, Inc. | Off-wall electrode device and methods for nerve modulation |
US9750568B2 (en) | 2012-03-08 | 2017-09-05 | Medtronic Ardian Luxembourg S.A.R.L. | Ovarian neuromodulation and associated systems and methods |
EP3348220A1 (en) | 2012-03-08 | 2018-07-18 | Medtronic Ardian Luxembourg S.à.r.l. | Biomarker sampling in the context of neuromodulation devices and associated systems |
US8968290B2 (en) | 2012-03-14 | 2015-03-03 | Covidien Lp | Microwave ablation generator control system |
US9190720B2 (en) * | 2012-03-23 | 2015-11-17 | Apple Inc. | Flexible printed circuit structures |
WO2013169927A1 (en) | 2012-05-08 | 2013-11-14 | Boston Scientific Scimed, Inc. | Renal nerve modulation devices |
CN104271063B (en) | 2012-05-11 | 2017-10-24 | 美敦力Af卢森堡有限责任公司 | Multiple electrode catheter component and associated system and method for renal regulation |
US9861802B2 (en) | 2012-08-09 | 2018-01-09 | University Of Iowa Research Foundation | Catheters, catheter systems, and methods for puncturing through a tissue structure |
WO2014032016A1 (en) | 2012-08-24 | 2014-02-27 | Boston Scientific Scimed, Inc. | Intravascular catheter with a balloon comprising separate microporous regions |
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 |
WO2014047411A1 (en) | 2012-09-21 | 2014-03-27 | Boston Scientific Scimed, Inc. | System for nerve modulation and innocuous thermal gradient nerve block |
WO2014047454A2 (en) | 2012-09-21 | 2014-03-27 | Boston Scientific Scimed, Inc. | Self-cooling ultrasound ablation catheter |
US10835305B2 (en) | 2012-10-10 | 2020-11-17 | Boston Scientific Scimed, Inc. | Renal nerve modulation devices and methods |
US20140110296A1 (en) | 2012-10-19 | 2014-04-24 | Medtronic Ardian Luxembourg S.A.R.L. | Packaging for Catheter Treatment Devices and Associated Devices, Systems, and Methods |
US9204921B2 (en) | 2012-12-13 | 2015-12-08 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9364277B2 (en) | 2012-12-13 | 2016-06-14 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
JP6453769B2 (en) * | 2013-02-07 | 2019-01-16 | 上▲海▼魅▲麗▼▲緯▼叶医▲療▼科技有限公司 | Induction cauterization method, system and induction cautery equipment |
US10076384B2 (en) | 2013-03-08 | 2018-09-18 | Symple Surgical, Inc. | Balloon catheter apparatus with microwave emitter |
WO2014163987A1 (en) | 2013-03-11 | 2014-10-09 | Boston Scientific Scimed, Inc. | Medical devices for modulating nerves |
US9693821B2 (en) | 2013-03-11 | 2017-07-04 | Boston Scientific Scimed, Inc. | Medical devices for modulating nerves |
US9808311B2 (en) | 2013-03-13 | 2017-11-07 | Boston Scientific Scimed, Inc. | Deflectable medical devices |
US10265122B2 (en) | 2013-03-15 | 2019-04-23 | Boston Scientific Scimed, Inc. | Nerve ablation devices and related methods of use |
JP6220044B2 (en) | 2013-03-15 | 2017-10-25 | 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 |
US9179974B2 (en) | 2013-03-15 | 2015-11-10 | Medtronic Ardian Luxembourg S.A.R.L. | Helical push wire electrode |
AU2014237950B2 (en) | 2013-03-15 | 2017-04-13 | Boston Scientific Scimed, Inc. | Control unit for use with electrode pads and a method for estimating an electrical leakage |
WO2014205388A1 (en) | 2013-06-21 | 2014-12-24 | Boston Scientific Scimed, Inc. | Renal denervation balloon catheter with ride along electrode support |
WO2014205399A1 (en) | 2013-06-21 | 2014-12-24 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation having rotatable shafts |
US9707036B2 (en) | 2013-06-25 | 2017-07-18 | Boston Scientific Scimed, Inc. | Devices and methods for nerve modulation using localized indifferent electrodes |
EP3016605B1 (en) | 2013-07-01 | 2019-06-05 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation |
CN105377170A (en) | 2013-07-11 | 2016-03-02 | 波士顿科学国际有限公司 | Medical device with stretchable electrode assemblies |
US10660698B2 (en) | 2013-07-11 | 2020-05-26 | Boston Scientific Scimed, Inc. | Devices and methods for nerve modulation |
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 |
WO2015013301A1 (en) | 2013-07-22 | 2015-01-29 | Boston Scientific Scimed, Inc. | Renal nerve ablation catheter having twist balloon |
WO2015013205A1 (en) | 2013-07-22 | 2015-01-29 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
EP4049605A1 (en) | 2013-08-22 | 2022-08-31 | Boston Scientific Scimed Inc. | Flexible circuit having improved adhesion to a renal nerve modulation balloon |
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 |
US20150073515A1 (en) | 2013-09-09 | 2015-03-12 | Medtronic Ardian Luxembourg S.a.r.I. | Neuromodulation Catheter Devices and Systems Having Energy Delivering Thermocouple Assemblies and Associated Methods |
CN105530885B (en) | 2013-09-13 | 2020-09-22 | 波士顿科学国际有限公司 | Ablation balloon with vapor deposited covering |
WO2015042173A1 (en) * | 2013-09-20 | 2015-03-26 | Advanced Cardiac Therapeutics, Inc. | Temperature sensing and tissue ablation using a plurality of electrodes |
US9687166B2 (en) | 2013-10-14 | 2017-06-27 | Boston Scientific Scimed, Inc. | High resolution cardiac mapping electrode array catheter |
US11246654B2 (en) | 2013-10-14 | 2022-02-15 | Boston Scientific Scimed, Inc. | Flexible renal nerve ablation devices and related methods of use and manufacture |
US9770606B2 (en) | 2013-10-15 | 2017-09-26 | Boston Scientific Scimed, Inc. | Ultrasound ablation catheter with cooling infusion and centering basket |
CN105636537B (en) | 2013-10-15 | 2018-08-17 | 波士顿科学国际有限公司 | Medical instrument sacculus |
EP3057521B1 (en) | 2013-10-18 | 2020-03-25 | Boston Scientific Scimed, Inc. | Balloon catheters with flexible conducting wires |
US10271898B2 (en) | 2013-10-25 | 2019-04-30 | Boston Scientific Scimed, Inc. | Embedded thermocouple in denervation flex circuit |
WO2015103574A1 (en) | 2014-01-06 | 2015-07-09 | Iowa Approach Inc. | Apparatus and methods for renal denervation ablation |
CN105899157B (en) | 2014-01-06 | 2019-08-09 | 波士顿科学国际有限公司 | Tear-proof flexible circuit assembly |
US11000679B2 (en) | 2014-02-04 | 2021-05-11 | Boston Scientific Scimed, Inc. | Balloon protection and rewrapping devices and related methods of use |
CN106572881B (en) | 2014-02-04 | 2019-07-26 | 波士顿科学国际有限公司 | Substitution of the heat sensor on bipolar electrode is placed |
US9622811B2 (en) | 2014-02-21 | 2017-04-18 | Warsaw Orthopedic, Inc. | Surgical instrument and method |
US10194979B1 (en) | 2014-03-28 | 2019-02-05 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for catheter-based renal neuromodulation |
US9980766B1 (en) | 2014-03-28 | 2018-05-29 | Medtronic Ardian Luxembourg S.A.R.L. | Methods and systems for renal neuromodulation |
US10194980B1 (en) | 2014-03-28 | 2019-02-05 | Medtronic Ardian Luxembourg S.A.R.L. | Methods for catheter-based renal neuromodulation |
WO2015164280A1 (en) | 2014-04-24 | 2015-10-29 | Medtronic Ardian Luxembourg S.A.R.L. | Neuromodulation catheters having braided shafts and associated systems and methods |
EP3495018B1 (en) | 2014-05-07 | 2023-09-06 | Farapulse, Inc. | Apparatus for selective tissue ablation |
US10016234B2 (en) * | 2014-06-05 | 2018-07-10 | St. Jude Medical, Cardiology Division, Inc. | Flex tip fluid lumen assembly with thermal sensor |
WO2015192018A1 (en) | 2014-06-12 | 2015-12-17 | Iowa Approach Inc. | Method and apparatus for rapid and selective tissue ablation with cooling |
EP3154463B1 (en) | 2014-06-12 | 2019-03-27 | Farapulse, Inc. | Apparatus for rapid and selective transurethral tissue ablation |
WO2016060983A1 (en) | 2014-10-14 | 2016-04-21 | Iowa Approach Inc. | Method and apparatus for rapid and safe pulmonary vein cardiac ablation |
GB201418486D0 (en) * | 2014-10-17 | 2014-12-03 | Creo Medical Ltd | Cable for conveying radiofrequency and/or microwave frequency energy to an electrosurgical instrument |
GB201418474D0 (en) * | 2014-10-17 | 2014-12-03 | Creo Medical Ltd | Electrosurgical apparatus |
EP3220841B1 (en) | 2014-11-19 | 2023-01-25 | EPiX Therapeutics, Inc. | High-resolution mapping of tissue with pacing |
EP3808298B1 (en) | 2014-11-19 | 2023-07-05 | EPiX Therapeutics, Inc. | Systems for high-resolution mapping of tissue |
CA2967824A1 (en) | 2014-11-19 | 2016-05-26 | Advanced Cardiac Therapeutics, Inc. | Ablation devices, systems and methods of using a high-resolution electrode assembly |
US9636164B2 (en) | 2015-03-25 | 2017-05-02 | Advanced Cardiac Therapeutics, Inc. | Contact sensing systems and methods |
CN107666859A (en) | 2015-06-03 | 2018-02-06 | 圣犹达医疗用品国际控股有限公司 | Active magnetic position sensor |
WO2017075067A1 (en) | 2015-10-26 | 2017-05-04 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
US10751123B2 (en) | 2015-10-30 | 2020-08-25 | Washington University | Thermoablation probe |
US10130423B1 (en) | 2017-07-06 | 2018-11-20 | Farapulse, Inc. | Systems, devices, and methods for focal ablation |
US20170189097A1 (en) | 2016-01-05 | 2017-07-06 | Iowa Approach Inc. | Systems, apparatuses and methods for delivery of ablative energy to tissue |
US10660702B2 (en) | 2016-01-05 | 2020-05-26 | Farapulse, Inc. | Systems, devices, and methods for focal ablation |
US10172673B2 (en) | 2016-01-05 | 2019-01-08 | Farapulse, Inc. | Systems devices, and methods for delivery of pulsed electric field ablative energy to endocardial tissue |
EP3429462B1 (en) | 2016-03-15 | 2022-08-03 | EPiX Therapeutics, Inc. | Improved devices and systems for irrigated ablation |
ES2581127B2 (en) * | 2016-04-13 | 2017-05-04 | Universidad Complutense De Madrid | Label, system and method for long-distance object detection |
ES2854935T3 (en) | 2016-04-15 | 2021-09-23 | Neuwave Medical Inc | Power delivery system |
GB2550414A (en) * | 2016-05-20 | 2017-11-22 | Creo Medical Ltd | Antenna structure |
WO2017218734A1 (en) | 2016-06-16 | 2017-12-21 | Iowa Approach, Inc. | Systems, apparatuses, and methods for guide wire delivery |
GB2552166B (en) * | 2016-07-11 | 2021-02-10 | Gyrus Medical Ltd | System and method for monitoring tissue temperature |
GB2552165B (en) * | 2016-07-11 | 2019-11-06 | Gyrus Medical Ltd | System for monitoring a microwave tissue ablation process |
GB2559604A (en) * | 2017-02-13 | 2018-08-15 | Creo Medical Ltd | Microwave energy transfer component for electrosurgical apparatus |
AU2018228880B2 (en) * | 2017-03-01 | 2023-03-30 | I.C. Medical, Inc. | Ultrapolar telescopic and non-telescopic electrosurgery pencils with argon beam capability and ultrapolar electrosurgery blade assembly |
EP3606457A4 (en) * | 2017-04-03 | 2021-04-21 | Broncus Medical Inc. | Electrosurgical access sheath |
US10751507B2 (en) * | 2017-04-10 | 2020-08-25 | Syn Variflex, Llc | Thermally controlled variable-flexibility catheters and methods of manufacturing same |
US9987081B1 (en) | 2017-04-27 | 2018-06-05 | Iowa Approach, Inc. | Systems, devices, and methods for signal generation |
WO2018200865A1 (en) | 2017-04-27 | 2018-11-01 | Epix Therapeutics, Inc. | Determining nature of contact between catheter tip and tissue |
US10617867B2 (en) | 2017-04-28 | 2020-04-14 | Farapulse, Inc. | Systems, devices, and methods for delivery of pulsed electric field ablative energy to esophageal tissue |
GB2563386A (en) * | 2017-06-08 | 2018-12-19 | Creo Medical Ltd | Electrosurgical instrument |
CN107349010A (en) * | 2017-07-07 | 2017-11-17 | 昆山雷盛医疗科技有限公司 | Radio frequency ablation probe and preparation method thereof |
CN109464186B (en) | 2017-09-08 | 2023-12-22 | 泽丹医疗股份有限公司 | Device and method for treating lung tumors |
JP2020533050A (en) | 2017-09-12 | 2020-11-19 | ファラパルス,インコーポレイテッド | Systems, devices, and methods for ventricular focal ablation |
WO2019094090A1 (en) * | 2017-11-13 | 2019-05-16 | Cryterion Medical, Inc. | Operator preference storage system for intravascular catheter system |
US11672596B2 (en) | 2018-02-26 | 2023-06-13 | Neuwave Medical, Inc. | Energy delivery devices with flexible and adjustable tips |
CN112087980B (en) | 2018-05-07 | 2023-01-10 | 波士顿科学医学有限公司 | Systems, devices, and methods for delivering ablation energy to tissue |
JP7379377B2 (en) | 2018-05-07 | 2023-11-14 | ファラパルス,インコーポレイテッド | Systems, devices, and methods for filtering high voltage noise induced by pulsed electric field ablation |
WO2019217300A1 (en) | 2018-05-07 | 2019-11-14 | Farapulse, Inc. | Epicardial ablation catheter |
JP7280897B2 (en) * | 2018-06-21 | 2023-05-24 | ショックウェーブ メディカル, インコーポレイテッド | System for treating an obstruction within a body lumen |
CN112638304A (en) * | 2018-08-13 | 2021-04-09 | 悉尼大学 | Catheter ablation device with temperature monitoring |
US10687892B2 (en) | 2018-09-20 | 2020-06-23 | Farapulse, Inc. | Systems, apparatuses, and methods for delivery of pulsed electric field ablative energy to endocardial tissue |
WO2020070727A2 (en) | 2018-10-06 | 2020-04-09 | Symap Medical (Suzhou), Limited | System and method for mapping the functional nerves innervating the wall of arteries, 3-d mapping and catheters for same |
US11832879B2 (en) | 2019-03-08 | 2023-12-05 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
US10625080B1 (en) | 2019-09-17 | 2020-04-21 | Farapulse, Inc. | Systems, apparatuses, and methods for detecting ectopic electrocardiogram signals during pulsed electric field ablation |
US20210128231A1 (en) * | 2019-11-04 | 2021-05-06 | Medwaves, Inc. | Energy transmitting therapeutic medical device |
US11065047B2 (en) | 2019-11-20 | 2021-07-20 | Farapulse, Inc. | Systems, apparatuses, and methods for protecting electronic components from high power noise induced by high voltage pulses |
US11497541B2 (en) | 2019-11-20 | 2022-11-15 | Boston Scientific Scimed, Inc. | Systems, apparatuses, and methods for protecting electronic components from high power noise induced by high voltage pulses |
US10842572B1 (en) | 2019-11-25 | 2020-11-24 | Farapulse, Inc. | Methods, systems, and apparatuses for tracking ablation devices and generating lesion lines |
AU2020391498B2 (en) * | 2019-11-27 | 2023-08-17 | Blossom Innovations, LLC | Devices, systems and methods for tissue analysis, location determination and tissue ablation |
CN110870791B (en) * | 2019-12-04 | 2021-09-03 | 上海微创电生理医疗科技股份有限公司 | Medical intervention needle assembly and medical intervention catheter |
Family Cites Families (112)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US595796A (en) | 1897-12-21 | Wrench | ||
US2847990A (en) | 1956-03-20 | 1958-08-19 | Ayre James Ernest | Instrument for obtaining cells for cytodiagnosis |
US3058473A (en) | 1959-11-27 | 1962-10-16 | Alfred E Whitchead | Remotely directing catheters and tools |
US3309455A (en) * | 1964-09-21 | 1967-03-14 | Dow Chemical Co | Coaxial cable with insulating conductor supporting layers bonded to the conductors |
US3552384A (en) | 1967-07-03 | 1971-01-05 | American Hospital Supply Corp | Controllable tip guide body and catheter |
US3521620A (en) | 1967-10-30 | 1970-07-28 | William A Cook | Vascular coil spring guide with bendable tip |
US4204549A (en) * | 1977-12-12 | 1980-05-27 | Rca Corporation | Coaxial applicator for microwave hyperthermia |
US4271848A (en) * | 1979-01-11 | 1981-06-09 | Bio Systems Design, Corp. | Apparatus for electromagnetic radiation of living tissue and the like |
US4408089A (en) * | 1979-11-16 | 1983-10-04 | Nixon Charles E | Extremely low-attenuation, extremely low radiation loss flexible coaxial cable for microwave energy in the gigaHertz frequency range |
US5370675A (en) * | 1992-08-12 | 1994-12-06 | Vidamed, Inc. | Medical probe device and method |
US4583556A (en) * | 1982-12-13 | 1986-04-22 | M/A-Com, Inc. | Microwave applicator/receiver apparatus |
US4700716A (en) * | 1986-02-27 | 1987-10-20 | Kasevich Associates, Inc. | Collinear antenna array applicator |
US4723936A (en) | 1986-07-22 | 1988-02-09 | Versaflex Delivery Systems Inc. | Steerable catheter |
US4906230A (en) | 1987-06-30 | 1990-03-06 | Baxter Travenol Laboratories, Inc. | Steerable catheter tip |
US5129396A (en) * | 1988-11-10 | 1992-07-14 | Arye Rosen | Microwave aided balloon angioplasty with lumen measurement |
US4960134A (en) | 1988-11-18 | 1990-10-02 | Webster Wilton W Jr | Steerable catheter |
US4945912A (en) * | 1988-11-25 | 1990-08-07 | Sensor Electronics, Inc. | Catheter with radiofrequency heating applicator |
AU664157B2 (en) | 1990-09-14 | 1995-11-09 | American Medical Systems, Inc. | Combined hyperthermia and dilation catheter |
US5327905A (en) * | 1992-02-14 | 1994-07-12 | Boaz Avitall | Biplanar deflectable catheter for arrhythmogenic tissue ablation |
US5370677A (en) * | 1992-03-06 | 1994-12-06 | Urologix, Inc. | Gamma matched, helical dipole microwave antenna with tubular-shaped capacitor |
US5413588A (en) | 1992-03-06 | 1995-05-09 | Urologix, Inc. | Device and method for asymmetrical thermal therapy with helical dipole microwave antenna |
US5540681A (en) * | 1992-04-10 | 1996-07-30 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of tissue |
US5275597A (en) * | 1992-05-18 | 1994-01-04 | Baxter International Inc. | Percutaneous transluminal catheter and transmitter therefor |
WO1994002077A2 (en) * | 1992-07-15 | 1994-02-03 | Angelase, Inc. | Ablation catheter system |
JP2586174Y2 (en) * | 1992-07-30 | 1998-12-02 | キム ジョン イル | Cigarette type gas lighter |
US5298682A (en) | 1992-08-20 | 1994-03-29 | Wireworld By David Salz, Inc. | Optimized symmetrical coaxial cable |
CA2109980A1 (en) * | 1992-12-01 | 1994-06-02 | Mir A. Imran | Steerable catheter with adjustable bend location and/or radius and method |
US6161543A (en) | 1993-02-22 | 2000-12-19 | Epicor, Inc. | Methods of epicardial ablation for creating a lesion around the pulmonary veins |
US5476495A (en) | 1993-03-16 | 1995-12-19 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5656796A (en) | 1993-04-26 | 1997-08-12 | Fmc Corp. | High energy flexible coaxial cable and connections |
US5693082A (en) * | 1993-05-14 | 1997-12-02 | Fidus Medical Technology Corporation | Tunable microwave ablation catheter system and method |
US5545193A (en) | 1993-10-15 | 1996-08-13 | Ep Technologies, Inc. | Helically wound radio-frequency emitting electrodes for creating lesions in body tissue |
US6071280A (en) * | 1993-11-08 | 2000-06-06 | Rita Medical Systems, Inc. | Multiple electrode ablation apparatus |
US5730127A (en) * | 1993-12-03 | 1998-03-24 | Avitall; Boaz | Mapping and ablation catheter system |
US5462545A (en) | 1994-01-31 | 1995-10-31 | New England Medical Center Hospitals, Inc. | Catheter electrodes |
US5882333A (en) * | 1994-05-13 | 1999-03-16 | Cardima, Inc. | Catheter with deflectable distal section |
US5617854A (en) * | 1994-06-22 | 1997-04-08 | Munsif; Anand | Shaped catheter device and method |
DE4425195C1 (en) * | 1994-07-16 | 1995-11-16 | Osypka Peter | Heart catheter with multiple electrode device |
US5885278A (en) | 1994-10-07 | 1999-03-23 | E.P. Technologies, Inc. | Structures for deploying movable electrode elements |
US5857997A (en) | 1994-11-14 | 1999-01-12 | Heart Rhythm Technologies, Inc. | Catheter for electrophysiological procedures |
US5683382A (en) * | 1995-05-15 | 1997-11-04 | Arrow International Investment Corp. | Microwave antenna catheter |
US5697958A (en) * | 1995-06-07 | 1997-12-16 | Intermedics, Inc. | Electromagnetic noise detector for implantable medical devices |
WO1996041654A1 (en) | 1995-06-12 | 1996-12-27 | Cordis Webster, Inc. | Catheter with an electromagnetic guidance sensor |
US5702433A (en) * | 1995-06-27 | 1997-12-30 | Arrow International Investment Corp. | Kink-resistant steerable catheter assembly for microwave ablation |
US5788692A (en) | 1995-06-30 | 1998-08-04 | Fidus Medical Technology Corporation | Mapping ablation catheter |
US5810717A (en) | 1995-09-22 | 1998-09-22 | Mitsubishi Cable Industries, Ltd. | Bending mechanism and stereoscope using same |
US5837001A (en) | 1995-12-08 | 1998-11-17 | C. R. Bard | Radio frequency energy delivery system for multipolar electrode catheters |
US6032077A (en) | 1996-03-06 | 2000-02-29 | Cardiac Pathways Corporation | Ablation catheter with electrical coupling via foam drenched with a conductive fluid |
US5800482A (en) | 1996-03-06 | 1998-09-01 | Cardiac Pathways Corporation | Apparatus and method for linear lesion ablation |
US5755760A (en) | 1996-03-11 | 1998-05-26 | Medtronic, Inc. | Deflectable catheter |
US5863291A (en) * | 1996-04-08 | 1999-01-26 | Cardima, Inc. | Linear ablation assembly |
US5904709A (en) * | 1996-04-17 | 1999-05-18 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Microwave treatment for cardiac arrhythmias |
EP0837716A1 (en) * | 1996-05-06 | 1998-04-29 | Thermal Therapeutics, Inc. | Transcervical intrauterine applicator for intrauterine hyperthermia |
US5776176A (en) * | 1996-06-17 | 1998-07-07 | Urologix Inc. | Microwave antenna for arterial for arterial microwave applicator |
US5752951A (en) | 1996-07-02 | 1998-05-19 | Yanik; Gary W. | Shielded monopolar electrosurgical apparatus |
US5800494A (en) | 1996-08-20 | 1998-09-01 | Fidus Medical Technology Corporation | Microwave ablation catheters having antennas with distal fire capabilities |
US5741249A (en) * | 1996-10-16 | 1998-04-21 | Fidus Medical Technology Corporation | Anchoring tip assembly for microwave ablation catheter |
US5893885A (en) | 1996-11-01 | 1999-04-13 | Cordis Webster, Inc. | Multi-electrode ablation catheter |
US5785706A (en) | 1996-11-18 | 1998-07-28 | Daig Corporation | Nonsurgical mapping and treatment of cardiac arrhythmia using a catheter contained within a guiding introducer containing openings |
US6508825B1 (en) * | 1997-02-28 | 2003-01-21 | Lumend, Inc. | Apparatus for treating vascular occlusions |
US5904667A (en) | 1997-03-17 | 1999-05-18 | C.R. Bard, Inc. | Rotatable control mechanism for steerable catheter |
US5876373A (en) | 1997-04-04 | 1999-03-02 | Eclipse Surgical Technologies, Inc. | Steerable catheter |
US5971983A (en) | 1997-05-09 | 1999-10-26 | The Regents Of The University Of California | Tissue ablation device and method of use |
US5849028A (en) * | 1997-05-16 | 1998-12-15 | Irvine Biomedical, Inc. | Catheter and method for radiofrequency ablation of cardiac tissue |
US6014579A (en) * | 1997-07-21 | 2000-01-11 | Cardiac Pathways Corp. | Endocardial mapping catheter with movable electrode |
US5897529A (en) | 1997-09-05 | 1999-04-27 | Cordis Webster, Inc. | Steerable deflectable catheter having improved flexibility |
US6123699A (en) | 1997-09-05 | 2000-09-26 | Cordis Webster, Inc. | Omni-directional steerable catheter |
US6183463B1 (en) | 1997-12-01 | 2001-02-06 | Cordis Webster, Inc. | Bidirectional steerable cathether with bidirectional control handle |
AU745659B2 (en) * | 1998-03-02 | 2002-03-28 | Atrionix, Inc. | Tissue ablation system and method for forming long linear lesion |
US6592581B2 (en) * | 1998-05-05 | 2003-07-15 | Cardiac Pacemakers, Inc. | Preformed steerable catheter with movable outer sleeve and method for use |
US6033403A (en) * | 1998-10-08 | 2000-03-07 | Irvine Biomedical, Inc. | Long electrode catheter system and methods thereof |
US6245062B1 (en) * | 1998-10-23 | 2001-06-12 | Afx, Inc. | Directional reflector shield assembly for a microwave ablation instrument |
US6123718A (en) * | 1998-11-02 | 2000-09-26 | Polymerex Medical Corp. | Balloon catheter |
US6067475A (en) | 1998-11-05 | 2000-05-23 | Urologix, Inc. | Microwave energy delivery system including high performance dual directional coupler for precisely measuring forward and reverse microwave power during thermal therapy |
US6319250B1 (en) * | 1998-11-23 | 2001-11-20 | C.R. Bard, Inc | Tricuspid annular grasp catheter |
US7070595B2 (en) * | 1998-12-14 | 2006-07-04 | Medwaves, Inc. | Radio-frequency based catheter system and method for ablating biological tissues |
US6190382B1 (en) * | 1998-12-14 | 2001-02-20 | Medwaves, Inc. | Radio-frequency based catheter system for ablation of body tissues |
US7594913B2 (en) * | 1998-12-14 | 2009-09-29 | Medwaves, Inc. | Radio-frequency based catheter system and method for ablating biological tissues |
US20070066972A1 (en) | 2001-11-29 | 2007-03-22 | Medwaves, Inc. | Ablation catheter apparatus with one or more electrodes |
US6267746B1 (en) | 1999-03-22 | 2001-07-31 | Biosense Webster, Inc. | Multi-directional steerable catheters and control handles |
EP1092449A1 (en) | 1999-04-30 | 2001-04-18 | Usaminanotechnology, Inc. | Catheter and guide wire |
US6277113B1 (en) | 1999-05-28 | 2001-08-21 | Afx, Inc. | Monopole tip for ablation catheter and methods for using same |
GB9912625D0 (en) | 1999-05-28 | 1999-07-28 | Gyrus Medical Ltd | An electrosurgical generator and system |
US20010007940A1 (en) | 1999-06-21 | 2001-07-12 | Hosheng Tu | Medical device having ultrasound imaging and therapeutic means |
US6254568B1 (en) | 1999-08-10 | 2001-07-03 | Biosense Webster, Inc. | Deflectable catheter with straightening element |
US6230060B1 (en) * | 1999-10-22 | 2001-05-08 | Daniel D. Mawhinney | Single integrated structural unit for catheter incorporating a microwave antenna |
US7033352B1 (en) | 2000-01-18 | 2006-04-25 | Afx, Inc. | Flexible ablation instrument |
US6663622B1 (en) | 2000-02-11 | 2003-12-16 | Iotek, Inc. | Surgical devices and methods for use in tissue ablation procedures |
US6673068B1 (en) | 2000-04-12 | 2004-01-06 | Afx, Inc. | Electrode arrangement for use in a medical instrument |
US6582536B2 (en) | 2000-04-24 | 2003-06-24 | Biotran Corporation Inc. | Process for producing steerable sheath catheters |
US6475214B1 (en) | 2000-05-01 | 2002-11-05 | Biosense Webster, Inc. | Catheter with enhanced ablation electrode |
DE60029752T2 (en) | 2000-05-03 | 2007-08-09 | Friedmann, Joshua, Dr., Danbury | Method and heating device for preheating dental materials |
JP3521253B2 (en) | 2000-05-18 | 2004-04-19 | 株式会社東北テクノアーチ | Shape memory alloy for living body |
US6669692B1 (en) * | 2000-08-21 | 2003-12-30 | Biosense Webster, Inc. | Ablation catheter with cooled linear electrode |
US6893155B2 (en) | 2000-09-30 | 2005-05-17 | Dolores C. Kaiser | Cooking thermometer with audible alarm |
US20020087151A1 (en) * | 2000-12-29 | 2002-07-04 | Afx, Inc. | Tissue ablation apparatus with a sliding ablation instrument and method |
US6610058B2 (en) * | 2001-05-02 | 2003-08-26 | Cardiac Pacemakers, Inc. | Dual-profile steerable catheter |
US6878147B2 (en) | 2001-11-02 | 2005-04-12 | Vivant Medical, Inc. | High-strength microwave antenna assemblies |
US7194297B2 (en) | 2001-11-13 | 2007-03-20 | Boston Scientific Scimed, Inc. | Impedance-matching apparatus and construction for intravascular device |
US6706040B2 (en) * | 2001-11-23 | 2004-03-16 | Medlennium Technologies, Inc. | Invasive therapeutic probe |
WO2003047448A1 (en) * | 2001-11-29 | 2003-06-12 | Medwaves, Inc. | Radio-frequency-based catheter system with improved deflection and steering mechanisms |
US7259640B2 (en) | 2001-12-03 | 2007-08-21 | Microfabrica | Miniature RF and microwave components and methods for fabricating such components |
US6907298B2 (en) | 2002-01-09 | 2005-06-14 | Medtronic, Inc. | Method and apparatus for imparting curves in implantable elongated medical instruments |
ITBS20020039U1 (en) * | 2002-03-20 | 2003-09-22 | Fogazzi Di Venturelli Andrea & | CATHETER WITH FLEXIBLE COOLED ELECTRODE |
EP1585572A4 (en) | 2002-09-20 | 2010-02-24 | Flowmedica Inc | Method and apparatus for intra aortic substance delivery to a branch vessel |
US7229450B1 (en) * | 2003-02-11 | 2007-06-12 | Pacesetter, Inc. | Kink resistant introducer with mapping capabilities |
US6941953B2 (en) * | 2003-02-20 | 2005-09-13 | Medwaves, Inc. | Preformed catheter set for use with a linear ablation system to produce ablation lines in the left and right atrium for treatment of atrial fibrillation |
US7104989B2 (en) * | 2003-09-05 | 2006-09-12 | Medtronic, Inc. | RF ablation catheter including a virtual electrode assembly |
US7736362B2 (en) | 2003-09-15 | 2010-06-15 | Boston Scientific Scimed, Inc. | Catheter balloons |
US8007495B2 (en) * | 2004-03-31 | 2011-08-30 | Biosense Webster, Inc. | Catheter for circumferential ablation at or near a pulmonary vein |
US7331959B2 (en) | 2004-05-27 | 2008-02-19 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Catheter electrode and rail system for cardiac ablation |
US20090082762A1 (en) * | 2007-09-20 | 2009-03-26 | Ormsby Theodore C | Radio frequency energy transmission device for the ablation of biological tissues |
-
2006
- 2006-10-19 US US11/551,162 patent/US20070066972A1/en not_active Abandoned
-
2007
- 2007-07-23 US US11/781,467 patent/US8308722B2/en not_active Expired - Fee Related
- 2007-10-09 WO PCT/US2007/080819 patent/WO2008051708A2/en active Application Filing
- 2007-10-09 ES ES07853876.6T patent/ES2546754T3/en active Active
- 2007-10-09 CN CN2007800389107A patent/CN101534737B/en active Active
- 2007-10-09 EP EP07853876.6A patent/EP2073738B1/en active Active
Non-Patent Citations (1)
Title |
---|
See references of EP2073738A4 * |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11324408B2 (en) | 2011-08-26 | 2022-05-10 | Symap Medical (Suzhou), Ltd | Mapping sympathetic nerve distribution for renal ablation and catheters for same |
WO2014064552A1 (en) * | 2012-10-26 | 2014-05-01 | Koninklijke Philips N.V. | System, catheter and planning method for hyperthermia-adjuvant brachytherapy |
GB2564942A (en) * | 2017-06-01 | 2019-01-30 | Creo Medical Ltd | Electrosurgical instrument for ablation and resection |
GB2564942B (en) * | 2017-06-01 | 2020-03-18 | Creo Medical Ltd | Electrosurgical instrument for ablation and resection |
Also Published As
Publication number | Publication date |
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US20080015570A1 (en) | 2008-01-17 |
EP2073738A2 (en) | 2009-07-01 |
EP2073738B1 (en) | 2015-06-10 |
US20070066972A1 (en) | 2007-03-22 |
WO2008051708A3 (en) | 2008-06-19 |
ES2546754T3 (en) | 2015-09-28 |
US8308722B2 (en) | 2012-11-13 |
EP2073738A4 (en) | 2011-06-15 |
CN101534737A (en) | 2009-09-16 |
CN101534737B (en) | 2011-07-06 |
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