WO1999001074A1 - Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue - Google Patents
Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue Download PDFInfo
- Publication number
- WO1999001074A1 WO1999001074A1 PCT/US1998/013414 US9813414W WO9901074A1 WO 1999001074 A1 WO1999001074 A1 WO 1999001074A1 US 9813414 W US9813414 W US 9813414W WO 9901074 A1 WO9901074 A1 WO 9901074A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- energy applicator
- energy
- electrode
- tissue
- kit
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
- A61B5/0531—Measuring skin impedance
-
- 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
-
- 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
- A61B18/1402—Probes for open surgery
-
- 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
- A61B18/1477—Needle-like probes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/48—Other medical applications
- A61B5/4887—Locating particular structures in or on the body
- A61B5/4893—Nerves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B10/00—Other methods or instruments for diagnosis, e.g. instruments for taking a cell sample, for biopsy, for vaccination diagnosis; Sex determination; Ovulation-period determination; Throat striking implements
- A61B10/02—Instruments for taking cell samples or for biopsy
-
- 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
- A61B18/1206—Generators therefor
-
- 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
- A61B18/1482—Probes or electrodes therefor having a long rigid shaft for accessing the inner body transcutaneously in minimal invasive surgery, e.g. laparoscopy
-
- 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
- A61B18/1485—Probes or electrodes therefor having a short rigid shaft for accessing the inner body through natural openings
-
- 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
- A61B18/1487—Trocar-like, i.e. devices producing an enlarged transcutaneous opening
-
- 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
- A61B2018/0022—Balloons
-
- 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
- A61B2018/0022—Balloons
- A61B2018/0025—Multiple balloons
- A61B2018/00261—Multiple balloons arranged in a line
-
- 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
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00577—Ablation
-
- 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
- A61B2018/00666—Sensing and controlling the application of energy using a threshold value
-
- 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
- A61B2018/00666—Sensing and controlling the application of energy using a threshold value
- A61B2018/00678—Sensing and controlling the application of energy using a threshold value upper
-
- 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
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00702—Power or energy
- A61B2018/00708—Power or energy switching the power on or off
-
- 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
- A61B2018/00696—Controlled or regulated parameters
- A61B2018/00761—Duration
-
- 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
- A61B2018/00827—Current
-
- 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
- A61B2018/00875—Resistance or impedance
-
- 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
- A61B2018/00886—Duration
-
- 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
-
- 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
- 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
- A61B18/1206—Generators therefor
- A61B2018/1246—Generators therefor characterised by the output polarity
- A61B2018/126—Generators therefor characterised by the output polarity bipolar
-
- 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
- A61B18/1206—Generators therefor
- A61B2018/1273—Generators therefor including multiple generators in one 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
- 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
- A61B18/1206—Generators therefor
- A61B2018/128—Generators therefor generating two or more frequencies
-
- 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
- A61B2018/1405—Electrodes having a specific shape
- A61B2018/1425—Needle
-
- 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
- A61B18/16—Indifferent or passive electrodes for grounding
- A61B2018/162—Indifferent or passive electrodes for grounding located on the probe body
Definitions
- the present invention relates to apparatus and methods for in situ cauterization of biological tissue, and more particularly, for causing in situ necrosis of predetermined volumes of abnormal biological tissue, such as a malignant tumor.
- Apparatus and methods are known for inducing therapeutic hyperthermia in biological tissue by inductive, radiant, contact and joulean heating methods.
- Inductive methods such as described in U.S. Patent Nos. 5,251,645 and 4,679,561, heat a volume of tissue located within a body cavity by passing high frequency electromagnetic radiation through tissue positioned between two external electrodes located near or in contact with the patient's skin. Heating is achieved due to the interaction of the changing electromagnetic field within the tissue.
- a drawback of the foregoing devices is that this approach to therapeutic hyperthermia heats a relatively large volume of tissue to elevated temperatures for extended periods of time.
- tissue is heated to temperatures of 6 to 10 C above normal body temperature, with heating sources operating in a range from ultrasonic frequencies to microwave frequencies, for periods of 20 minutes or more to achieve a desired degree of necrosis.
- heating sources operating in a range from ultrasonic frequencies to microwave frequencies, for periods of 20 minutes or more to achieve a desired degree of necrosis.
- Such devices generally do not allow the volume of tissue to be well defined, resulting in either insufficient necrosis or excessive necrosis of surrounding healthy tissue. Consequently, diffuse and prolonged heating of tissue is often combined with chemotherapy or radiation therapy modalities.
- a single heating element could be inserted along a diameter of the sphere.
- the central regions must be raised to a higher temperature than the periphery to produce an adequate thermal gradient, as may be demonstrated using well-known thermal conduction equations .
- dispersed contact heating methods also have been developed.
- small spheres or wire segments of ferromagnetic alloys have been inserted into tumors in the brain and other tissue and heated to an auto-regulating temperature (i.e., the Curie temperature of the alloy) by an externally applied electromagnetic field.
- the resulting eddy current heating causes hyperthermia in the tissue immediately surrounding the small spheres or wire segments .
- Electrosurgery utilizes heating produced by the flow of electrical current through tissue, such as described in U.S. Patent Nos. 5,599,346, 5,599,345, 5,486,161, 5,472,441, 5,458,597, 5,536,267, 5,507,743, 4,846,196, 4,121,592, and 4,016,886.
- Electrosurgery generally employs either a monopolar or bipolar modality. In the monopolar mode, electric current is conducted between a relatively small active electrode and a large return electrode located at a distance from the active electrode. Because in the monopolar mode the current density in tissue decreases as the square of the distance from the active electrode, it is difficult to obtain necrosis of a predetermined volume of tissue.
- the bipolar mode of electrosurgical (joulean) heating involves passing current between tissue disposed between two electrodes of similar surface area.
- electrosurgical joulean
- the capability to heat tissue in a precise manner requires that the region of tissue to be exposed to therapeutic hyperthermia be accurately defined in terms of both location and dimensions .
- tissue temperature measurements may be influenced by the distance between the temperature sensor and the working surface of the device, often resulting in underestimation of temperatures for more distal regions of tissue.
- electrosurgical heating methods can lead to tissue heating effects which may be several or tens of millimeters from the working surface, well beyond the range of a temperature sensor mounted near the working surface .
- breast tumors or other abnormal tissue masses may be first identified by palpation, radiography, thermography and/or ultrasonography. Once a tumor is detected, a biopsy needle is used to extract a tissue sample (under the guidance of radiographs, ultrasound and/or palpation) , and the biopsy needle is withdrawn from the patient. If hyperthermic treatment is indicated, the patient is subsequently exposed to a separate procedure (often invasive) which may be hours, days, weeks or longer after the initial invasive needle biopsy procedure .
- a separate procedure often invasive
- an energy applicator could be tailored to the size and shape of the tumor, as quantified, for example, using tumor imaging techniques .
- the methods and apparatus of the present invention preferably enable treatment of a tumor of predetermined volume within a brief period of time (e.g., several seconds to tens of seconds) .
- devices constructed in accordance with the present invention may be designed to be compatible with previously known electrosurgical generators by accepting the available voltages and impedances of such generators, thereby eliminating the need for specialty generators .
- apparatus comprising two or more electrodes which are electrically isolated from one another, so that the only path for the flow of electrical current is through tissue contacting the electrodes.
- the apparatus permits selection of the electrode size and spacing, so that a predetermined volume of tissue may be heated to a temperature sufficient to cause irreversible necrosis.
- the two or more electrodes are disposed on either a rigid or flexible cannula or catheter.
- Apparatus constructed in accordance with the invention allows application of therapeutic heating to a target tissue site promptly after a tissue biopsy procedure.
- a battery-powered control device may be provided, which may also serve as a handle for the apparatus.
- the device could include controls for initiating therapy and control circuitry that interrupts application of power to an energy applicator after a preselected time duration and/or current reduction ratio has been attained.
- a specially designed radio- frequency power supply may be used (instead of a previously known electrosurgical generator) that incorporates controls for initiating therapy and circuitry for interrupting the application of power to the energy applicator after a predetermined time duration or when a predetermined current reduction ratio has been attained.
- the apparatus of the present invention further utilizes electrode geometry to predictably control the size and shape of the tissue mass cauterized. Accordingly, the clinician may adjust or select an energy applicator configuration appropriate for the predetermined size and shape of the tumor to be treated, so that tissue temperatures in the range of 70 degrees C (sufficient to cause cell death) , but preferably less than 100 degrees C, may be achieved within relatively brief periods, thus reducing risk of injury to adjacent healthy tissue.
- a further alternative embodiment of the present invention includes one or more expandable electrodes that may be expanded, once inserted in the tissue mass to be cauterized, to provide an increased electrode surface area during the energy application step, while reducing the diameter of the energy applicator during insertion.
- patient physical discomfort and mental stress are reduced by: (1) the use of a local anesthetic applied to the site of the intended cauterization and (2) the completion of the therapeutic cauterization of tissue soon after completion of the biopsy procedure.
- the costs associated with medical treatment are reduced since therapy can be completed within the same time frame previously required for a biopsy procedure alone.
- FIG. 1 is a perspective view of apparatus constructed in accordance with the present invention, including various energy applicators, together with a power source ;
- FIGS. 2A and 2B are side views of an illustrative energy applicator and associated control device constructed in accordance with the present invention
- FIG. 3 is a partial sectional view of the distal tip of the energy applicator of FIGS. 2, showing an illustrative electric field resulting from activation of the energy applicator;
- FIG. 4 is a partial sectional view of the distal tip of the energy applicator of FIGS. 2, showing a predetermined volume of cauterized tissue resulting from activation of the energy applicator;
- FIGS. 5A-5C are views showing the effect on the volume of tissue treated for different values of electrode parameters and also illustrating use of telescoping components in accordance with one family of embodiments of the present invention
- FIG. 6 is a graph illustrating the effect that varying electrode parameters has on the predetermined volume of the cauterization zone;
- FIG. 7 is a side view of an alternative energy applicator constructed in accordance with the present invention.
- FIGS. 8A and 8B are partial cross-sectional views of an alternative embodiment of the energy applicator of the present invention suitable for use in performing a biopsy procedure;
- FIGS. 9A and 9B are, respectively, sectional and side views of the working end of a further alternative embodiment of the energy applicator of the present invention.
- FIG. 10 is a sectional view of the distal tip of the energy applicator of FIGS. 9, showing an illustrative electric field and cauterization zone resulting from activation of the energy applicator;
- FIG. 11 is a view similar to that of FIG. 10 for an energy applicator having electrodes disposed over only a portion of the expandable members;
- FIG. 12 is a perspective view of yet another alternative embodiment of an energy applicator constructed in accordance with the present invention.
- apparatus 10 includes power source 11 and therapeutic cauterization device 20 comprising a plurality of energy applicators 21a-21d and control device 22 that accepts and activates a selected one of the energy applicators.
- Control device 22 is coupled to power source 11 by cable 23 using connectors 24.
- Energy applicator 21 is energized by activation of switch 25 on control device 22, in conjunction with foot pedal 12.
- Foot pedal 12 is coupled to power source 11 by cable 13.
- Power source 11 may be any one of a wide range of previously known and commercially available electrosurgical generators, such as the Valleylab Force 2 electrosurgical generator, sold by Valleylab Inc., Boulder, Colorado. Power source 11 includes at least power level (or voltage level) control 14 and power level (or voltage level) set point indicator 15, to allow a clinician to adjust the output of the power source to a set point level appropriate for the intended therapy. Alternatively, power source 11 may be a specially designed electrosurgical controller unit that incorporates the control and set point circuitry described in detail hereinafter with respect to FIGS. 2A and 2B.
- energy applicators 21 come in a range of sizes and styles designed for effecting cauterization of predetermined volumes of tissue.
- Energy applicators 21a-21c illustratively comprise two or more electrodes disposed on a rigid or bendable needle or cannula, and operable in a bipolar mode for cauterizing specified volumes of tissue when activated for specified durations at predefined power levels.
- energy applicator 21d also available with a range of electrode configurations (only one shown) , also includes two or more electrodes disposed on a flexible catheter for percutaneous use.
- Other embodiments may feature energy applicators employing flexible cannulas so that energy applicator 21 can be introduced to a treatment site through a tortuous body lumen or by using a previously known steerable catheter delivery system, thus permitting treatment of diseased tissue in the brain, prostate, uterus, bladder, lung, esophagus, liver, stomach and bowel.
- energy applicators 21a-d all may be employed with common control device 22 using a plug-in arrangement described hereinafter.
- energy applicator 21 comprises cannula 26 having distal region 27 carrying two or more electrodes operable in a bipolar mode.
- the length of cannula 26 is dependent on the depth at which a target tissue site is located, typically, several to tens of centimeters from the external surface of a patient's body.
- Energy applicator 21 connects to control device 22 (and is electrically coupled thereto) by insertion of plugs 32a and 32b extending from hub 33 into mating electrical receptacles 34a and 34b of control device 22. With respect to FIG. 3, distal region 27 of energy applicator 21 is described in greater detail.
- Cannula 26 comprises shaft 40 comprising an electrically conducting material (e.g. metal or alloy) having sharpened distal tip 41.
- Distal tip 41 serves as distal electrode 29, and has a length of L DE and diameter D DE .
- a thin layer of electrical insulation 42 is disposed on the external surface of shaft 40 up to (but not including) distal electrode 29.
- a layer of electrically conductive material 43 is disposed on the layer of electrical insulation 42 to form annular proximal electrode 28, having outer diameter D PB .
- a further layer of electrical insulation 44 is disposed on electrically conductive material 43 for the length of cannula 26 (except for the length L PE of electrically conductive material 43 exposed to form proximal electrode 28) .
- the layer of electrical insulating material 42 provides electrical insulation between distal electrode 29 and proximal electrode 28, the length between the proximal edge of distal electrode 29 and the distal edge of proximal electrode 28 defining interelectrode spacing L ES .
- Electrically conductive material 43 is illustratively shown as comprising a metal or alloy annular tubing that extends from the proximal end of energy applicator 21.
- proximal electrode 28 and distal electrode 29 may also comprise metal-filled films disposed only for the length of the respective electrodes. In this latter case, suitable conductive traces or wires must be provided to connect the electrodes to plugs 32a or 32b.
- Distal tip 41 of shaft 40 has a sharpened end forming an angle preferably in a range of about 20 to 40 degrees to facilitate insertion of energy applicator 21 into the tissue to be treated.
- Shaft 40 therefore preferably comprises a material capable of retaining a sharp tip, for example, Type 304 stainless steel.
- Energy applicator 21 preferably comprises biocompatible materials and preferably has an overall size of between about 2 to 20 French (i.e., diameter of about 1.4 to 6.7 mm). Electrically insulating materials 42 and 44 preferably have thicknesses of about 0.002 inches (0.05 mm) and are selected to minimize the overall diameter of energy applicator 21.
- proximal electrode 28 illustratively comprises a thin-walled metal tube, such as stainless steel hypodermic tubing, having a wall thickness of 0.002 inch to 0.010 inch, and preferably 0.005 inch (0.13 mm) and a gauge size of about 2 to 20 French depending on the size of the tumor being treated.
- Electrically insulating materials 42 and 44 may comprise shrink tubing or be formed of a deposited insulating coating, such as Parylene, available from Specialty Coating Systems, Inc. Indianapolis, Indiana.
- control device 22 which preferably serves as a reusable handle of the therapeutic cauterization device, is coupled to power supply 11 via cable 23.
- Control device 22 includes switch 25, lights 35a-35c, battery 36, current sensor 37 and limit circuit 38 coupled to control circuit 39.
- Wires 45a and 45b couple receptacles 34a and 34b to cable 23 via limit circuit 38, which may comprise, for example, a double pole switch.
- Switch 25, when depressed, causes lights 35a-35c to be individually illuminated, thereby indicating the status of the device, as described hereinbelow.
- a presterilized energy applicator is coupled to control device 22 by urging plugs 32a and 32b of the energy applicator into receptacles 34a and 34b of the control device. Operation of the therapeutic cauterization device of FIG. 2A is now described. First, a clinician selects a presterilized energy applicator 21 appropriate for the size and shape of the tumor to be treated, and connects it to control device 22. Power supply 11 is then turned on and adjusted to provide an appropriate output signal for that energy applicator. The clinician first depresses switch 25 to check the status of the apparatus.
- control circuit 39 If the voltage level of battery 36 is at an acceptable level and all other circuitry is in a "ready” state according to preprogrammed logic contained within control circuit 39, green light 35a flashes, indicating that therapeutic cauterization may be initiated by depressing footpedal 12. If the preprogrammed logic of control circuit 39 indicates that the device is in a "not ready” state (e.g., due to low battery), orange light 35b flashes, indicating that correction of the fault condition is required. If the green light flashes during the system check, the clinician may next administer a local anesthetic to the patient and insert distal region 27 of energy applicator 21 into the patient's tissue, for example, guided by ultrasound or radiographic images. For example, the imaging system described in commonly assigned U.S.
- patent application Serial No. 08/421,381 may be used to position distal region 27 of energy applicator 21 within the tissue at a target site.
- the clinician depresses footpedal 12 (or another switch controlling activation of power source 11) to initiate application of radio-frequency voltage between proximal and distal electrodes 28 and 29, thereby causing current to flow through the tissue which effects the joulean heating of, and thereby, thermal necrosis of the tissue within a volume defined by electrode parameters L DE , D DE , L PE , D PE and L ES of the energy applicator.
- control circuit 39 monitors the current flow in wire 45b using current sensor 37, which communicates a sensed voltage to control circuit 39.
- current sensor 37 which communicates a sensed voltage to control circuit 39.
- a predetermined level e.g., about one-fifth to one-tenth the initial current level
- control circuit 39 causes double-pole switch 38 to be opened, thereby interrupting further application of current from power source 11.
- control circuit 39 causes red light 35c to begin flashing, thus providing an indication to the clinician that treatment is complete.
- Control device 22 in addition may activate an audible indicator when red light 35c is illuminated.
- control circuit 39 may include timer logic that is used in addition to or instead of current sensor 37 to terminate application of power after a predetermined period (e.g., 5 to 10 seconds) . If both current and time of activation are monitored, control circuit 39 preferably is programmed to open limit circuit 38 (e.g., a double pole switch) and activate light 35c as soon as either limit is reached (i.e., current reduction or time duration). Preferably, no further activation of energy applicator 21 can occur until switch 25 is again depressed, thereby resetting the program logic of control circuit 39.
- open limit circuit 38 e.g., a double pole switch
- the power delivered to the electrodes is controlled so that the power density (watts/cm 2 ) at the electrode/tissue interface or the current density (amps/cm ) through the intervening tissue between electrodes does not exceed a predetermined limit. Below this limit, boiling of cellular liquids leading to the generation of steam, and rapid increase in tissue impedance due to desiccation, may be minimized. It has been found that rapid desiccation of tissue can be minimized during purposeful cauterization of tissue by maintaining the power density at the electrode/tissue interface below about 250 watts/cm or the current density to below about 5 am s/cm 2 .
- the exposed areas of the electrodes of energy applicator 21 preferably are designed to be of similar area, for example, differing by less than 25%.
- the exposed electrode areas for any particular energy applicator may vary over a wide range, depending on the size of the target tissue volume to be cauterized and the characteristics of the target tissue. Accordingly, each energy applicator 21 may be supplied with a recommended set of power or voltage settings with which that energy applicator may be used with selected commercially available power sources.
- power control circuitry that maintains the time-averaged power and/or current application below a limit value corresponding to the selected electrode parameters can be incorporated into control device 22.
- a limit value may be applied for each of the time-averaged power and current application.
- a predetermined limit value may be set within the power control device 22 based on "coding" or identifying circuit element 83 (e.g., a resistor or capacitor) contained within energy applicator 21.
- "coding" or identifying circuit element 83 is connected to plugs 32a and 32c via leads 84 and 85, respectively.
- energy applicator 21 is coupled to control device 22 by inserting plugs 32a, 32b and 32c into receptacles 34a, 34b and 34c, respectively.
- control circuit 86 measures a value of a parameter of circuit element 83 (e.g., resistance or capacitance) and sets an upper power and/or current limit value which is used during the period of power application to control maximum power and/or current delivery and, accordingly, maximum power density and/or current density applied to tissue.
- a parameter of circuit element 83 e.g., resistance or capacitance
- control circuit 86 interrupts current flow for brief periods using, for example, limit circuit 87, so that the average power and/or current level (for example, the current level integrated over 100 milliseconds) remains below the limit value.
- the energy applicator of FIG. 2B may be constructed with circuit element 83 disposed between lead wires 81 and 82 so that control circuit 86 measures a value of a parameter of circuit element 83 when electrodes 28 and 29 are open-circuited (i.e., not in contact with the tissue) .
- plug 32c would be unnecessary, and could be omitted.
- Other power and/or current control limit elements 87 can also be employed using designs well known to those skilled in the art.
- circuit element 83 may form part of a bridge circuit or other suitable analog circuit, known to those skilled in the art, which limits the maximum amount of power or current that can be applied according to the size and surface area of the electrodes of energy applicator 21.
- the output power again decreases monotonically, approaching a ten-fold lower output level at a 1000 ohm load impedance.
- the power output is insufficient to raise the tissue temperature in the cauterization zone around the electrodes to a level that will result in irreversible necrosis of the tissue .
- electrode parameters L DE , D DE , L PE , D PB and L ES may be selected to effect the therapeutic cauterization of a predetermined volume 111 when placed in biological tissue 100.
- the capability to predict the cauterized volume based on electrode parameters L DE , D DB , L PE , D PE and L ES enables power to be applied for a preset period of time sufficient to effect the cauterization of the entire volume of tissue.
- the duration of power application required depends on the electrode parameters and the electrical characteristics of the biological tissue. For example, fatty tissue has relatively higher electrical impedance than lean tissue, and requires a longer period of power application than more vascularized tissue (e.g., fascia) .
- spherical region 110 (represented by cross-hatching) is completely cauterized within about 2 seconds after the application of 50 watts of power through electrodes 28 and 29.
- Cauterization then progresses throughout cauterization zone 111 with continued application of power, until the self-limiting stage is attained in about 5-7 seconds.
- FIGS. 5A to 5C applicant has observed that as interelectrode spacing L ES increases, cauterization zone 111 becomes more elliptical. As the interelectrode spacing continues to increase, the cauterization zone develops into two lobes (with one lobe centered on each electrode) and a mid-region of incomplete cauterization between the two lobes.
- cauterization zone 111 tends to become more spherical as interelectrode spacing L ES decreases. As the interelectrode spacing decreases and the cauterization zone becomes more spherical, electrode parameters L PE , L DE , D PE and D DE increasingly dictate the size of the cauterization zone relative to the effect of interelectrode spacing.
- a plurality of energy applicators 21a-21d are provided, each having different electrode parameters L PE , L DE , D PE , D DE and L ES that are established at the time of manufacture to effect the complete cauterization of different predetermined volumes 111.
- each distal region 27 of the respective energy applicators 21a-21c is constructed to treat a specified predetermined volume 111.
- the clinician may select an energy applicator to treat a tumor having a size and shape that has been determined by the clinician using suitable tumor imaging techniques (e.g., using radiography and/or ultrasonography methods) .
- the energy applicator may be designed so that electrode parameters L PB , L DE and L ES may be adjusted by the clinician at the time of treatment.
- each of insulating layers 42 and 44 and electrically conducting material 43 may be designed to telescope with respect to one another (indicated by directional arrows A in FIGS. 5A-5C) , thereby allowing the components of the energy applicator to be slidingly displaced with respect to one another to individually vary the lengths of the proximal and distal electrodes and interelectrode spacing.
- a single energy applicator could be configured to provide any of the energy applicators 21a-21c depicted in FIGS. 5A-5C.
- a clinician using such an embodiment of the invention would, after determining the size and shape of a tumor, consult a table specifying the electrode parameters to which the energy applicator should be adjusted, together with the appropriate power settings for power source 11.
- Separate energy applicators may be supplied having varying diameters to affect larger or smaller cauterization zones.
- the cauterization zone thickness and length are affected by the interelectrode spacing and the duration of time that energy is applied to the site.
- the length of the cauterization zone is effected more by the interelectrode spacing and the time duration than is the thickness of the cauterization zone.
- the length of the cauterization zone is more sensitive to the interelectrode spacing, so that as the interelectrode spacing increases, up to the point at which two lobes develop, the cauterization zone becomes a more elongated ellipsoid.
- Energy applicator 50 includes distal electrode 51 and multiple proximal electrodes 52a, 52b and 52c disposed on cannula 53 with interposed insulating regions 54a, 54b and 54c.
- Electrodes 52a-52c may of the thin film type, so that a selected one of proximal electrodes 52a-52c may be energized in conjunction with distal electrode 51.
- the lengths of proximal electrodes 52a- 52c, as well as the lengths of insulating regions 54a-54c, may vary along the length of cannula 53, so that for each one of proximal electrodes 52a-52c energized in combination with distal electrode 51 for a specified time, a corresponding predetermined volume of tissue is cauterized.
- a clinician could consult a table similar to FIG. 6 that provides length and thickness of the cauterized zone as a function of the proximal electrode. The clinician then activates a desired proximal electrode, using a selector switch on the control device (not shown) , to cauterize the region of abnormal tissue. Alternatively, or in addition, more than one of proximal electrodes 52a-52c may be energized in combination with distal electrode 51. Referring now to FIGS. 8A and 8B, a yet further alternative embodiment is described in which energy applicator 60 includes tubular shaft 61 having lumen 62.
- Distal edge 63 of tubular shaft 61 preferably includes bevel 64 to facilitate introduction and advancement of the energy applicator into biological tissue 120, and includes an exposed region forming distal electrode 65.
- Energy applicator is otherwise similar in construction to energy applicators 21 of FIGS. 2, and includes proximal electrode 66 and insulation layers 67 and 68.
- the hub and control device used with energy applicator 60 are modified to allow the introduction and positioning of extraction device 70 (e.g., a biopsy needle) through lumen 62, as shown in FIG. 8B, for example, to permit aspiration of debris from the treatment site through lumen 62.
- extraction device 70 e.g., a biopsy needle
- biopsy needle 130 may be inserted through lumen 62 so that a portion of the tissue protrudes into cavity 131 formed in region 132 of the biopsy needle.
- bevel 64 of shaft 61 severs the tissue, thereby permitting sample of tissue 121 to be withdrawn for pathological examination prior to the initiation of therapeutic cauterization.
- the control device used with the energy applicator and biopsy needle of FIGS. 8 may advantageously include a mechanical, electromagnetic, or pneumatic advancement mechanism for actuating movement of shaft 61 to sever tissue sample 121. Accordingly, the embodiment of FIGS.
- working end 150 of energy applicator 21 comprises shaft 152 having trocar tip member 154.
- Trocar tip member 154 may be joined to shaft 152 using known methods, e.g., welding, brazing or adhesive bonding, as appropriate to the materials of construction.
- shaft 152 and trocar tip member 154 may be manufactured using biocompatible metals such as stainless steel, titanium or nickel-based alloys.
- Expandable members 160 and 170 are located at the distal and proximal ends, respectively, of working end 150, and may be formed from an elastomeric material such as polyurethane or polyethylene teraphthalate . A portion or all of the outer surfaces of distal and proximal expandable members 160 and 170 are covered with electrically conducting layers, such as films of stainless steel, silver, gold or other biocompatible metal or alloy, that form electrodes 162 and 172, respectively. In FIG. 9B, electrodes 162 and 172 illustratively cover only a portion of the circumference of expandable members 160 and 170.
- Locking collars 158a and 158b are positioned at the proximal and distal ends, respectively, of expandable member 160 to provide a fluid tight seal between expandable member 160 and shaft 152.
- locking collars 168a and 168b are positioned at the proximal and distal ends, respectively, of expandable member 170 to provide a fluid tight seal between expandable member 170 and shaft 152.
- Distal hole 178 and proximal hole 182 allow fluid communication between lumen 151 of shaft 152 and the annular spaces formed between shaft 152 and expandable members 160 and 170.
- Electrically insulated lead wires 180 and 184 are brought into electrical communication with the electrodes 162 and 172, respectively, and terminate at the proximal end of the energy applicator at plugs 32a and 32b (see FIG. 2A) .
- Electrically insulated lead wires 180 and 184 illustratively extend through holes 178 and 182, respectively and, in turn, are electrically attached to electrodes 162 and 172 using locking collars 158a and 168a, respectively.
- electrically insulating layer 166 The portion of shaft 152 between distal electrode 162 and proximal electrode 172 is covered with electrically insulating layer 166. Also, the portion of shaft 152 proximal of proximal electrode 172 is also covered with electrically insulating layer 176. Electrically insulating layers 166 and 176 may be formed using plastic sleeving (e.g., polyimide) , heat shrink tubing (e.g., Kynar, polyester or polyolefin tubing) or may be formed of a deposited insulating coating such as Parylene.
- plastic sleeving e.g., polyimide
- heat shrink tubing e.g., Kynar, polyester or polyolefin tubing
- Parylene Parylene
- the overall diameter, D SWE , of working end 150, prior to inflation of expandable members 160 and 170, is expected typically to be in a range of 0.7 mm to 6.7 mm.
- a target tissue e.g., tumor
- expandable members 160 and 170 are inflated, as shown in FIGS. 9B and 10.
- working end 150 of the energy applicator of FIGS. 9 is shown positioned so that target tissue 192 (e.g., tumor) is located between distal electrode 162 and proximal electrode 172, with expandable members 160 and 170 being inflated.
- Working end 150 is first positioned in tissue 100 with distal electrode 162 and proximal electrode 172 in the unexpanded (i.e., minimum diameter) configuration, so as to minimize trauma to healthy tissue during the insertion step.
- proximal and distal electrodes are positioned relative to target tissue 192, as confirmed, for example, by fluoroscopy, radiography, ultrasonography or vectoring of a device based on previous mapping of target tissue (e.g., using computer aided tomography, magnetic resonance imaging and/or ultrasonography)
- expandable members 160 and 170 are inflated using suitable pressurizing fluid 190, such as sterile water or isotonic saline, to achieve the enlarged electrode shapes depicted in FIG. 10.
- a high frequency voltage may be applied between plugs 32a and 32b at the proximal and of the energy applicator using the control device described hereinabove .
- leads 180 and 184 current flows through tissue 100 located between electrodes 162 and 172, illustrated by current flux lines 101.
- a predefined volume of tissue 111 is cauterized due to the attainment of a current density in volume 111 sufficient to cause heating to above about 60 to 70 °C, resulting in irreversible necrosis of tissue throughout volume 111, including target tissue 192.
- electrodes 162 and 172 cover the entire circumference of expandable members 160 and 170.
- the duration of energy application by the method and apparatus of the present invention is typically expected to be in a range from several seconds to tens of seconds, depending upon the volume of tissue to be cauterized.
- the dimensions of the expanded electrodes at working end 150 depend on the size and shape of the target tissue that requires cauterization.
- the diameter of the expanded electrodes, D EE ranges from 1 mm to 20 mm
- the lengths of the proximal and distal electrodes, L PE and L DE range from 2 mm to 50 mm.
- the thickness of electrically insulating layers 166 and 176 range from 0.02 to 0.2 mm.
- the frequency of the applied voltage is preferably in a range of from 20 kHz to 40 MHZ, and more preferably in the range from 200 kHz to 2 MHZ.
- the applied voltage may be in a range of from 5 volts (RMS) to 1000 volts (RMS) , depending on the size and interelectrode spacing of the electrodes as well as the operating frequency and electrical properties of the tissue being treated.
- the crest factor for the applied voltage is preferably in a range from 1 to 10, and more preferably, in the range from 1 to 2.
- target tissue 192 e.g., tumor
- This arrangement may be preferred in some treatment situations to avoid iatrogenic metastases that might otherwise occur when the vascular network within malignant tissue is disrupted (e.g., if the trocar tip pierced the tumor) .
- working end 150 is positioned adjacent to target tissue 192, the proximal and distal electrodes are expanded, and voltage is applied between the electrodes, thereby causing current to flow in the localized region defined by current flux lines 101.
- predefined volume of tissue 113 is cauterized due to the attainment of a current density in volume 113 sufficient to cause heating to above about 60° to 70° C, resulting in irreversible necrosis of tissue throughout volume 113 (including target tissue 192).
- FIGS. 9 utilize one or more expandable electrodes that provide increased electrode surface area during the energy application step, while providing a reduced diameter of the energy application during the tissue insertion and positioning step.
- the increased electrode surface area provided by the expandable members enables the level of current and power that can be applied during the treatment step to be increased, relative to a constant diameter energy applicator, while preventing unwanted desiccation and steam generation due to boiling of tissue/cellular liquids.
- the increased electrode surface area also enables the duration of the energy application period to be reduced.
- FIGS. 9 is that electrical contact between the electrode surface and the adjacent tissue is enhanced because the expandable member (and electrode) are pressed against the surface of the adjacent tissue.
- the resulting reduction in interfacial contact impedance reduces localized heating at the electrode/tissue interface, and further reduces the potential for excessive localized heating and associated desiccation, which may otherwise lead to significant electrical impedance at the electrode/tissue interface.
- the preferred use of water or isotonic saline as the pressurizing fluid serves to moderate temperatures at the electrode/tissue interface, thereby further reducing localized tissue desiccation and/or water vapor generation at the electrode/tissue interface.
- the diameter of the energy application may be maintained as small and atraumatic as possible, thereby allowing the use of the present invention in a wide range of applications, including office-based procedures, with little scarring and discomfort to the patient and reduced risk of iatrogenic injury to the patient.
- the shaft of energy applicator 21e is divided into three distinct regions.
- the distal-most region comprises working end 150 as described hereinabove with respect to FIGS. 9, and may incorporate rigid shaft member 152 (e.g., stainless steel Type 304) and electrodes 162 and 172 disposed on expandable members 160 and 170, respectively.
- Flexible segment 206 is positioned between working end 150 and rigid support shaft 208.
- Support shaft 208 is, in turn, affixed to hub 194, which couples to control device 22.
- Hub 194 preferably includes mechanical actuation slider 196, which may be advanced or retracted to change the angular position of working end 150.
- support shaft 208 may also be flexible, allowing its use within the channel provided in conventional flexible endoscopic devices.
- a pull wire between mechanical actuation slider 196 and the distal portion of the working end effects the controllable deflection of working end 150 relative to the axis of support shaft 208 through angle ⁇ .
- the dimensions of the various segments depend on the size, shape and location of the target tissue within the body.
- working end length, L WE is expected to range from 6 mm to 100 mm
- the length of the support member L RS is expected to range from 5 cm to 200 cm.
- the length of flexible segment 206, L FS should be sufficiently long that angle ⁇ of working end 150 may provide deflection through a range of from 0 to about 75°.
- Syringe 212 or other pressurization device may be used to inject pressurizing fluid 190 into expandable members 160 and 170 to effect their controlled dilation, once working end 150 is properly positioned relative to the target tissue.
- the target tissue is not limited to only tumors but also may include any tissue that a clinician may choose to treat, including, but not limited to, tissue in the prostate, uterus, esophagus, uvula, tonsils and adenoids. It will be understood that the foregoing is merely illustrative of the apparatus and methods of the present invention, and that various modifications can be made by those skilled in the art without departing from the scope and spirit of the claimed invention.
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Surgery (AREA)
- Engineering & Computer Science (AREA)
- Veterinary Medicine (AREA)
- General Health & Medical Sciences (AREA)
- Physics & Mathematics (AREA)
- Public Health (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Otolaryngology (AREA)
- Plasma & Fusion (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Dermatology (AREA)
- Radiology & Medical Imaging (AREA)
- Neurology (AREA)
- Surgical Instruments (AREA)
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE69827270T DE69827270T2 (en) | 1997-07-03 | 1998-06-30 | DEVICE FOR THE THERAPEUTIC COMBINATION OF PRE-SPECIFIED VOLUMES OF BIOLOGICAL TISSUE |
CA002294946A CA2294946A1 (en) | 1997-07-03 | 1998-06-30 | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
JP50726299A JP2002507924A (en) | 1997-07-03 | 1998-06-30 | Method and apparatus for therapeutic ablation of a volume of biological tissue |
EP98931678A EP1006903B1 (en) | 1997-07-03 | 1998-06-30 | Apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/888,063 | 1997-07-03 | ||
US08/888,063 US6106524A (en) | 1995-03-03 | 1997-07-03 | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999001074A1 true WO1999001074A1 (en) | 1999-01-14 |
Family
ID=25392448
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1998/013414 WO1999001074A1 (en) | 1997-07-03 | 1998-06-30 | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue |
Country Status (7)
Country | Link |
---|---|
US (1) | US6106524A (en) |
EP (2) | EP1006903B1 (en) |
JP (1) | JP2002507924A (en) |
CA (1) | CA2294946A1 (en) |
DE (2) | DE69830087T2 (en) |
ES (2) | ES2230703T3 (en) |
WO (1) | WO1999001074A1 (en) |
Cited By (53)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1059067A1 (en) * | 1999-06-11 | 2000-12-13 | Sherwood Services AG | Ablation treatment of bone metastases |
US6423081B1 (en) | 1998-09-03 | 2002-07-23 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
US6440147B1 (en) | 1998-09-03 | 2002-08-27 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
US6561998B1 (en) | 1998-04-07 | 2003-05-13 | Transvascular, Inc. | Transluminal devices, systems and methods for enlarging interstitial penetration tracts |
JP2004505663A (en) * | 2000-08-09 | 2004-02-26 | アースロケア コーポレイション | Device for treating spinal irregularities |
US6936014B2 (en) | 2002-10-16 | 2005-08-30 | Rubicor Medical, Inc. | Devices and methods for performing procedures on a breast |
US7029451B2 (en) | 2002-11-06 | 2006-04-18 | Rubicor Medical, Inc. | Excisional devices having selective cutting and atraumatic configurations and methods of using same |
US7044956B2 (en) | 2002-07-03 | 2006-05-16 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
US7122011B2 (en) | 2003-06-18 | 2006-10-17 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
US7198626B2 (en) | 2000-12-07 | 2007-04-03 | Rubicor Medical, Inc. | Methods and devices for radiofrequency electrosurgery |
EP1804676A2 (en) * | 2004-10-26 | 2007-07-11 | Poh Choo Mona Tan | Device for cauterising tissue and uses thereof |
GB2450679A (en) * | 2007-06-19 | 2009-01-07 | Gyrus Medical Ltd | Electrosurgical System with status indicators on instruments |
US7725155B2 (en) | 2001-04-13 | 2010-05-25 | Novian Health, Inc. | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
US8092449B2 (en) | 2003-07-11 | 2012-01-10 | Celon Ag | Surgical probe |
WO2013096632A1 (en) * | 2011-12-20 | 2013-06-27 | Applied Medical Resources Corporation | Advanced surgical simulation |
US8613743B2 (en) | 2007-05-14 | 2013-12-24 | Erbe Elektromedizin Gmbh | HF surgical testing device |
US8709010B2 (en) | 2007-06-19 | 2014-04-29 | Gyrus Medical Limited | Electrosurgical system |
US8764452B2 (en) | 2010-10-01 | 2014-07-01 | Applied Medical Resources Corporation | Portable laparoscopic trainer |
US8956350B2 (en) | 2007-01-31 | 2015-02-17 | Covidien Lp | Thermal feedback systems and methods of using the same |
US9113888B2 (en) | 2004-10-08 | 2015-08-25 | Covidien Ag | Electrosurgical system employing multiple electrodes and method thereof |
US9218753B2 (en) | 2011-10-21 | 2015-12-22 | Applied Medical Resources Corporation | Simulated tissue structure for surgical training |
US9375252B2 (en) | 2012-08-02 | 2016-06-28 | Covidien Lp | Adjustable length and/or exposure electrodes |
US9449532B2 (en) | 2013-05-15 | 2016-09-20 | Applied Medical Resources Corporation | Hernia model |
US9486269B2 (en) | 2007-06-22 | 2016-11-08 | Covidien Lp | Electrosurgical systems and cartridges for use therewith |
US9548002B2 (en) | 2013-07-24 | 2017-01-17 | Applied Medical Resources Corporation | First entry model |
US9820805B2 (en) | 2012-06-12 | 2017-11-21 | Gyrus Medical Limited | Electrosurgical instrument and system |
US9848932B2 (en) | 2006-07-28 | 2017-12-26 | Covidien Ag | Cool-tip thermocouple including two-piece hub |
US9877769B2 (en) | 2008-07-22 | 2018-01-30 | Covidien Lp | Electrosurgical devices, systems and methods of using the same |
US9898937B2 (en) | 2012-09-28 | 2018-02-20 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US9922579B2 (en) | 2013-06-18 | 2018-03-20 | Applied Medical Resources Corporation | Gallbladder model |
US9940849B2 (en) | 2013-03-01 | 2018-04-10 | Applied Medical Resources Corporation | Advanced surgical simulation constructions and methods |
US9959786B2 (en) | 2012-09-27 | 2018-05-01 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10081727B2 (en) | 2015-05-14 | 2018-09-25 | Applied Medical Resources Corporation | Synthetic tissue structures for electrosurgical training and simulation |
US10121391B2 (en) | 2012-09-27 | 2018-11-06 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10198965B2 (en) | 2012-08-03 | 2019-02-05 | Applied Medical Resources Corporation | Simulated stapling and energy based ligation for surgical training |
US10198966B2 (en) | 2013-07-24 | 2019-02-05 | Applied Medical Resources Corporation | Advanced first entry model for surgical simulation |
US10223936B2 (en) | 2015-06-09 | 2019-03-05 | Applied Medical Resources Corporation | Hysterectomy model |
US10332425B2 (en) | 2015-07-16 | 2019-06-25 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US10354556B2 (en) | 2015-02-19 | 2019-07-16 | Applied Medical Resources Corporation | Simulated tissue structures and methods |
US10395559B2 (en) | 2012-09-28 | 2019-08-27 | Applied Medical Resources Corporation | Surgical training model for transluminal laparoscopic procedures |
US10490105B2 (en) | 2015-07-22 | 2019-11-26 | Applied Medical Resources Corporation | Appendectomy model |
US10535281B2 (en) | 2012-09-26 | 2020-01-14 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10679520B2 (en) | 2012-09-27 | 2020-06-09 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10682170B2 (en) | 2010-01-29 | 2020-06-16 | Medtronic Cryocath Lp | Multifunctional ablation device |
US10706743B2 (en) | 2015-11-20 | 2020-07-07 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US10720084B2 (en) | 2015-10-02 | 2020-07-21 | Applied Medical Resources Corporation | Hysterectomy model |
US10796606B2 (en) | 2014-03-26 | 2020-10-06 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US10818201B2 (en) | 2014-11-13 | 2020-10-27 | Applied Medical Resources Corporation | Simulated tissue models and methods |
US10828100B2 (en) | 2009-08-25 | 2020-11-10 | Covidien Lp | Microwave ablation with tissue temperature monitoring |
US10847057B2 (en) | 2017-02-23 | 2020-11-24 | Applied Medical Resources Corporation | Synthetic tissue structures for electrosurgical training and simulation |
US11030922B2 (en) | 2017-02-14 | 2021-06-08 | Applied Medical Resources Corporation | Laparoscopic training system |
US11120708B2 (en) | 2016-06-27 | 2021-09-14 | Applied Medical Resources Corporation | Simulated abdominal wall |
US12004806B2 (en) | 2020-10-22 | 2024-06-11 | Covidien Lp | Microwave ablation with tissue temperature monitoring |
Families Citing this family (215)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7992572B2 (en) | 1998-06-10 | 2011-08-09 | Asthmatx, Inc. | Methods of evaluating individuals having reversible obstructive pulmonary disease |
US6634363B1 (en) | 1997-04-07 | 2003-10-21 | Broncus Technologies, Inc. | Methods of treating lungs having reversible obstructive pulmonary disease |
US7027869B2 (en) | 1998-01-07 | 2006-04-11 | Asthmatx, Inc. | Method for treating an asthma attack |
US6626903B2 (en) * | 1997-07-24 | 2003-09-30 | Rex Medical, L.P. | Surgical biopsy device |
CA2297118C (en) * | 1997-07-24 | 2008-12-09 | James F. Mcguckin, Jr. | Breast surgery method and apparatus |
US7921855B2 (en) | 1998-01-07 | 2011-04-12 | Asthmatx, Inc. | Method for treating an asthma attack |
US6331166B1 (en) * | 1998-03-03 | 2001-12-18 | Senorx, Inc. | Breast biopsy system and method |
US7198635B2 (en) | 2000-10-17 | 2007-04-03 | Asthmatx, Inc. | Modification of airways by application of energy |
US8181656B2 (en) | 1998-06-10 | 2012-05-22 | Asthmatx, Inc. | Methods for treating airways |
WO2000009209A1 (en) * | 1998-08-14 | 2000-02-24 | K.U. Leuven Research & Development | Expandable wet electrode |
US7329253B2 (en) * | 2003-12-09 | 2008-02-12 | Rubicor Medical, Inc. | Suction sleeve and interventional devices having such a suction sleeve |
US7517348B2 (en) * | 1998-09-03 | 2009-04-14 | Rubicor Medical, Inc. | Devices and methods for performing procedures on a breast |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US6221039B1 (en) * | 1998-10-26 | 2001-04-24 | Scimed Life Systems, Inc. | Multi-function surgical instrument |
US6962586B2 (en) | 1999-05-04 | 2005-11-08 | Afx, Inc. | Microwave ablation instrument with insertion probe |
US6306132B1 (en) | 1999-06-17 | 2001-10-23 | Vivant Medical | Modular biopsy and microwave ablation needle delivery apparatus adapted to in situ assembly and method of use |
US6607528B1 (en) * | 1999-06-22 | 2003-08-19 | Senorx, Inc. | Shapeable electrosurgical scalpel |
US6409726B1 (en) * | 1999-11-08 | 2002-06-25 | Alan G. Ellman | Electrosurgical instrument for ear surgery |
US6416512B1 (en) * | 1999-11-08 | 2002-07-09 | Health Care Technologies, Llc. | Electrosurgical instrument for ear surgery |
US6770070B1 (en) * | 2000-03-17 | 2004-08-03 | Rita Medical Systems, Inc. | Lung treatment apparatus and method |
US8251070B2 (en) | 2000-03-27 | 2012-08-28 | Asthmatx, Inc. | Methods for treating airways |
US20030083656A1 (en) * | 2000-11-07 | 2003-05-01 | George Morrison | Tissue separator assembly and method |
US7534242B2 (en) * | 2003-02-25 | 2009-05-19 | Artemis Medical, Inc. | Tissue separating catheter assembly and method |
US20030204188A1 (en) * | 2001-11-07 | 2003-10-30 | Artemis Medical, Inc. | Tissue separating and localizing catheter assembly |
US7458974B1 (en) * | 2000-07-25 | 2008-12-02 | Endovascular Technologies, Inc. | Apparatus and method for electrically induced thrombosis |
CA2416581A1 (en) * | 2000-07-25 | 2002-04-25 | Rita Medical Systems, Inc. | Apparatus for detecting and treating tumors using localized impedance measurement |
US7104987B2 (en) | 2000-10-17 | 2006-09-12 | Asthmatx, Inc. | Control system and process for application of energy to airway walls and other mediums |
CA2444568A1 (en) * | 2001-04-18 | 2002-10-31 | Richard S. Lansil | Electrosurgery systems |
US6709380B2 (en) | 2001-05-31 | 2004-03-23 | Neoseed Technology Llc | Brachytherapy needle with impedance measurement apparatus and methods of use |
DE10128701B4 (en) * | 2001-06-07 | 2005-06-23 | Celon Ag Medical Instruments | probe assembly |
US6994706B2 (en) | 2001-08-13 | 2006-02-07 | Minnesota Medical Physics, Llc | Apparatus and method for treatment of benign prostatic hyperplasia |
US20030093007A1 (en) * | 2001-10-17 | 2003-05-15 | The Government Of The U.S.A., As Represented By The Secretary, Department Of Health And Human Serv | Biopsy apparatus with radio frequency cauterization and methods for its use |
US6942662B2 (en) * | 2001-12-27 | 2005-09-13 | Gyrus Group Plc | Surgical Instrument |
WO2003055402A1 (en) * | 2001-12-27 | 2003-07-10 | Gyrus Group Plc | A surgical instrument |
US20060264929A1 (en) * | 2001-12-27 | 2006-11-23 | Gyrus Group Plc | Surgical system |
GB0130975D0 (en) | 2001-12-27 | 2002-02-13 | Gyrus Group Plc | A surgical instrument |
US6676660B2 (en) | 2002-01-23 | 2004-01-13 | Ethicon Endo-Surgery, Inc. | Feedback light apparatus and method for use with an electrosurgical instrument |
US7819869B2 (en) * | 2004-11-15 | 2010-10-26 | Kimberly-Clark Inc. | Methods of treating the sacroilac region of a patient's body |
US6752767B2 (en) | 2002-04-16 | 2004-06-22 | Vivant Medical, Inc. | Localization element with energized tip |
US7197363B2 (en) | 2002-04-16 | 2007-03-27 | Vivant Medical, Inc. | Microwave antenna having a curved configuration |
US20040030330A1 (en) * | 2002-04-18 | 2004-02-12 | Brassell James L. | Electrosurgery systems |
US20040006355A1 (en) * | 2002-07-03 | 2004-01-08 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
CA2505727A1 (en) * | 2002-11-13 | 2004-05-27 | Artemis Medical, Inc. | Devices and methods for controlling initial movement of an electrosurgical electrode |
US20050119646A1 (en) * | 2002-11-13 | 2005-06-02 | Artemis Medical, Inc. | Devices and methods for controlling movement of an electrosurgical electrode |
US7044948B2 (en) | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
US7247160B2 (en) * | 2002-12-30 | 2007-07-24 | Calypso Medical Technologies, Inc. | Apparatuses and methods for percutaneously implanting objects in patients |
US7195627B2 (en) * | 2003-01-09 | 2007-03-27 | Gyrus Medical Limited | Electrosurgical generator |
JP4463113B2 (en) * | 2003-01-09 | 2010-05-12 | ジャイラス メディカル リミテッド | Electrosurgical generator |
US20040220655A1 (en) * | 2003-03-03 | 2004-11-04 | Sinus Rhythm Technologies, Inc. | Electrical conduction block implant device |
US7481798B2 (en) * | 2003-03-20 | 2009-01-27 | Boston Scientific Scimed, Inc. | Devices and methods for delivering therapeutic or diagnostic agents |
US20050020965A1 (en) * | 2003-03-20 | 2005-01-27 | Scimed Life Systems, Inc. | Devices and methods for delivering agents to tissue region while preventing leakage |
US8512290B2 (en) * | 2003-03-20 | 2013-08-20 | Boston Scientific Scimed, Inc. | Devices and methods for delivering therapeutic or diagnostic agents |
JP4698128B2 (en) * | 2003-03-28 | 2011-06-08 | テルモ株式会社 | Catheter with puncture sensor |
JP2006525096A (en) | 2003-05-01 | 2006-11-09 | シャーウッド・サービシーズ・アクチェンゲゼルシャフト | Method and system for programming and controlling an electrosurgical generator system |
US20040226556A1 (en) | 2003-05-13 | 2004-11-18 | Deem Mark E. | Apparatus for treating asthma using neurotoxin |
US7842034B2 (en) * | 2003-06-10 | 2010-11-30 | Neomedix Corporation | Electrosurgical devices and methods for selective cutting of tissue |
GB2403148C2 (en) | 2003-06-23 | 2013-02-13 | Microsulis Ltd | Radiation applicator |
EP1676108B1 (en) | 2003-10-23 | 2017-05-24 | Covidien AG | Thermocouple measurement circuit |
WO2005039689A2 (en) * | 2003-10-24 | 2005-05-06 | Sinus Rhythm Technologies, Inc. | Methods and devices for creating cardiac electrical blocks |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
SE526861C2 (en) * | 2003-11-17 | 2005-11-15 | Syntach Ag | Tissue lesion creation device and a set of devices for the treatment of cardiac arrhythmia disorders |
EP1684655A2 (en) * | 2003-11-18 | 2006-08-02 | SciMed Life Systems, Inc. | System and method for tissue ablation |
WO2005067563A2 (en) * | 2004-01-12 | 2005-07-28 | Calypso Medical Technologies, Inc. | Instruments with location markers and methods for tracking instruments through anatomical passageways |
US7632266B2 (en) * | 2004-02-17 | 2009-12-15 | Boston Scientific Scimed, Inc. | Endoscopic devices and related methods of use |
US9398967B2 (en) | 2004-03-02 | 2016-07-26 | Syntach Ag | Electrical conduction block implant device |
US8414580B2 (en) | 2004-04-20 | 2013-04-09 | Boston Scientific Scimed, Inc. | Co-access bipolar ablation probe |
US7101369B2 (en) * | 2004-04-29 | 2006-09-05 | Wisconsin Alumni Research Foundation | Triaxial antenna for microwave tissue ablation |
US7467015B2 (en) | 2004-04-29 | 2008-12-16 | Neuwave Medical, Inc. | Segmented catheter for tissue ablation |
US20070016181A1 (en) | 2004-04-29 | 2007-01-18 | Van Der Weide Daniel W | Microwave tissue resection tool |
US7244254B2 (en) * | 2004-04-29 | 2007-07-17 | Micrablate | Air-core microwave ablation antennas |
GB2415630C2 (en) | 2004-07-02 | 2007-03-22 | Microsulis Ltd | Radiation applicator and method of radiating tissue |
US20090209804A1 (en) * | 2004-07-23 | 2009-08-20 | Calypso Medical Technologies, Inc. | Apparatuses and methods for percutaneously implanting objects in patients |
US7824408B2 (en) | 2004-08-05 | 2010-11-02 | Tyco Healthcare Group, Lp | Methods and apparatus for coagulating and/or constricting hollow anatomical structures |
US7553309B2 (en) | 2004-10-08 | 2009-06-30 | Covidien Ag | Electrosurgical system employing multiple electrodes and method thereof |
US7776035B2 (en) * | 2004-10-08 | 2010-08-17 | Covidien Ag | Cool-tip combined electrode introducer |
US20060167405A1 (en) * | 2004-12-13 | 2006-07-27 | Medex, Inc. | Bodily fluid space entry detection |
US7467075B2 (en) * | 2004-12-23 | 2008-12-16 | Covidien Ag | Three-dimensional finite-element code for electrosurgery and thermal ablation simulations |
GB2423020A (en) * | 2005-02-14 | 2006-08-16 | Algotec Ltd | Percutaneous electrical stimulation probe for pain relief |
US7625372B2 (en) | 2005-02-23 | 2009-12-01 | Vnus Medical Technologies, Inc. | Methods and apparatus for coagulating and/or constricting hollow anatomical structures |
US9474564B2 (en) * | 2005-03-31 | 2016-10-25 | Covidien Ag | Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator |
WO2006119245A2 (en) * | 2005-04-29 | 2006-11-09 | Stryker Corporation | Medical bipolar electrode assembly with cannula and removable supply electrode |
GB2434314B (en) | 2006-01-03 | 2011-06-15 | Microsulis Ltd | Microwave applicator with dipole antenna |
DE102005038864A1 (en) * | 2005-08-17 | 2007-03-01 | Stryker Leibinger Gmbh & Co. Kg | Surgical power tool and operating unit therefor |
US20070066971A1 (en) * | 2005-09-21 | 2007-03-22 | Podhajsky Ronald J | Method and system for treating pain during an electrosurgical procedure |
US7879031B2 (en) * | 2005-09-27 | 2011-02-01 | Covidien Ag | Cooled RF ablation needle |
US20070078454A1 (en) * | 2005-09-30 | 2007-04-05 | Mcpherson James W | System and method for creating lesions using bipolar electrodes |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US9844682B2 (en) | 2006-01-17 | 2017-12-19 | Endymed Medical Ltd. | Skin treatment devices and methods |
US9827437B2 (en) | 2006-01-17 | 2017-11-28 | Endymed Medical Ltd | Skin treatment devices and methods |
JP2009527262A (en) * | 2006-01-17 | 2009-07-30 | エンディメド メディカル リミテッド | Electrosurgical method and apparatus using phase controlled radio frequency energy |
CA2574934C (en) | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US7651493B2 (en) | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US8672932B2 (en) | 2006-03-24 | 2014-03-18 | Neuwave Medical, Inc. | Center fed dipole for use with tissue ablation systems, devices and methods |
WO2007112103A1 (en) * | 2006-03-24 | 2007-10-04 | Neuwave Medical, Inc. | Energy delivery system |
US10363092B2 (en) | 2006-03-24 | 2019-07-30 | Neuwave Medical, Inc. | Transmission line with heat transfer ability |
US8795270B2 (en) * | 2006-04-24 | 2014-08-05 | Covidien Ag | System and method for ablating tissue |
US20070258838A1 (en) * | 2006-05-03 | 2007-11-08 | Sherwood Services Ag | Peristaltic cooling pump system |
US20070260240A1 (en) | 2006-05-05 | 2007-11-08 | Sherwood Services Ag | Soft tissue RF transection and resection device |
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 |
US20080033422A1 (en) * | 2006-08-04 | 2008-02-07 | Turner Paul F | Microwave applicator with margin temperature sensing element |
US20080221650A1 (en) * | 2006-08-04 | 2008-09-11 | Turner Paul F | Microwave applicator with adjustable heating length |
IL177550A0 (en) | 2006-08-17 | 2006-12-31 | Sialo Technology Israel Ltd | All-in-one optical microscopic handle |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US8068921B2 (en) | 2006-09-29 | 2011-11-29 | Vivant Medical, Inc. | Microwave antenna assembly and method of using the same |
WO2008045869A2 (en) * | 2006-10-10 | 2008-04-17 | Biosense Webster, Inc. | Esophageal mapping catheter |
US8181995B2 (en) | 2007-09-07 | 2012-05-22 | Tyco Healthcare Group Lp | Cool tip junction |
US8292880B2 (en) | 2007-11-27 | 2012-10-23 | Vivant Medical, Inc. | Targeted cooling of deployable microwave antenna |
US9050098B2 (en) | 2007-11-28 | 2015-06-09 | Covidien Ag | Cordless medical cauterization and cutting device |
US8758342B2 (en) | 2007-11-28 | 2014-06-24 | Covidien Ag | Cordless power-assisted medical cauterization and cutting device |
US8377059B2 (en) | 2007-11-28 | 2013-02-19 | Covidien Ag | Cordless medical cauterization and cutting device |
DE102007060431B3 (en) | 2007-12-14 | 2009-07-23 | Erbe Elektromedizin Gmbh | Neutral electrode recognition |
US8483831B1 (en) | 2008-02-15 | 2013-07-09 | Holaira, Inc. | System and method for bronchial dilation |
US8328802B2 (en) * | 2008-03-19 | 2012-12-11 | Covidien Ag | Cordless medical cauterization and cutting device |
US8491581B2 (en) * | 2008-03-19 | 2013-07-23 | Covidien Ag | Method for powering a surgical instrument |
WO2009137609A2 (en) | 2008-05-06 | 2009-11-12 | Cellutions, Inc. | Apparatus and systems for treating a human tissue condition |
CN102014779B (en) | 2008-05-09 | 2014-10-22 | 赫莱拉公司 | Systems, assemblies, and methods for treating a bronchial tree |
JP5169551B2 (en) * | 2008-07-07 | 2013-03-27 | 日本ゼオン株式会社 | Electrode catheter |
US8758349B2 (en) | 2008-10-13 | 2014-06-24 | Dfine, Inc. | Systems for treating a vertebral body |
EP2364128A4 (en) * | 2008-09-30 | 2013-07-24 | Dfine Inc | System for use in treatment of vertebral fractures |
US9332973B2 (en) | 2008-10-01 | 2016-05-10 | Covidien Lp | Needle biopsy device with exchangeable needle and integrated needle protection |
US9782565B2 (en) | 2008-10-01 | 2017-10-10 | Covidien Lp | Endoscopic ultrasound-guided biliary access system |
US20110190662A1 (en) * | 2008-10-01 | 2011-08-04 | Beacon Endoscopic Corporation | Rapid exchange fna biopsy device with diagnostic and therapeutic capabilities |
US9186128B2 (en) | 2008-10-01 | 2015-11-17 | Covidien Lp | Needle biopsy device |
US11298113B2 (en) | 2008-10-01 | 2022-04-12 | Covidien Lp | Device for needle biopsy with integrated needle protection |
US8968210B2 (en) | 2008-10-01 | 2015-03-03 | Covidien LLP | Device for needle biopsy with integrated needle protection |
US9782217B2 (en) | 2008-11-13 | 2017-10-10 | Covidien Ag | Radio frequency generator and method for a cordless medical cauterization and cutting device |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
ES2405550T3 (en) * | 2009-02-04 | 2013-05-31 | Stryker Leibinger Gmbh & Co. Kg | Surgical power tool, operating procedure and corresponding drive construction group |
EP2215980B1 (en) * | 2009-02-04 | 2012-12-19 | Stryker Leibinger GmbH & Co. KG | Surgical electric tool and actuation components for same |
US20100298832A1 (en) | 2009-05-20 | 2010-11-25 | Osseon Therapeutics, Inc. | Steerable curvable vertebroplasty drill |
US8903488B2 (en) | 2009-05-28 | 2014-12-02 | Angiodynamics, Inc. | System and method for synchronizing energy delivery to the cardiac rhythm |
US9895189B2 (en) | 2009-06-19 | 2018-02-20 | Angiodynamics, Inc. | Methods of sterilization and treating infection using irreversible electroporation |
US9119649B2 (en) | 2009-07-28 | 2015-09-01 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
GB2474233A (en) | 2009-10-06 | 2011-04-13 | Uk Investments Associates Llc | Cooling pump comprising a detachable head portion |
US8568401B2 (en) * | 2009-10-27 | 2013-10-29 | Covidien Lp | System for monitoring ablation size |
CN107049479B (en) | 2009-10-27 | 2020-10-16 | 努瓦拉公司 | Delivery device with coolable energy emitting assembly |
US8430871B2 (en) * | 2009-10-28 | 2013-04-30 | Covidien Lp | System and method for monitoring ablation size |
US8911439B2 (en) | 2009-11-11 | 2014-12-16 | Holaira, Inc. | Non-invasive and minimally invasive denervation methods and systems for performing the same |
EP4111995A1 (en) | 2009-11-11 | 2023-01-04 | Nuvaira, Inc. | Device for treating tissue and controlling stenosis |
US8469953B2 (en) | 2009-11-16 | 2013-06-25 | Covidien Lp | Twin sealing chamber hub |
US8414570B2 (en) * | 2009-11-17 | 2013-04-09 | Bsd Medical Corporation | Microwave coagulation applicator and system |
US8551083B2 (en) | 2009-11-17 | 2013-10-08 | Bsd Medical Corporation | Microwave coagulation applicator and system |
US9993294B2 (en) * | 2009-11-17 | 2018-06-12 | Perseon Corporation | Microwave coagulation applicator and system with fluid injection |
US20110125148A1 (en) * | 2009-11-17 | 2011-05-26 | Turner Paul F | Multiple Frequency Energy Supply and Coagulation System |
US9616246B2 (en) * | 2010-01-04 | 2017-04-11 | Covidien Lp | Apparatus and methods for treating hollow anatomical structures |
US20110172659A1 (en) * | 2010-01-13 | 2011-07-14 | Vivant Medical, Inc. | Ablation Device With User Interface at Device Handle, System Including Same, and Method of Ablating Tissue Using Same |
US9078661B2 (en) * | 2010-02-11 | 2015-07-14 | Arthrex, Inc. | Ablator with improved cutting tip |
US10058336B2 (en) | 2010-04-08 | 2018-08-28 | Dfine, Inc. | System for use in treatment of vertebral fractures |
US9173700B2 (en) | 2010-04-26 | 2015-11-03 | 9234438 Canada Inc. | Electrosurgical device and methods |
US9526507B2 (en) | 2010-04-29 | 2016-12-27 | Dfine, Inc. | System for use in treatment of vertebral fractures |
BR112012027708B1 (en) | 2010-04-29 | 2021-03-09 | Dfine, Inc | medical device for ablation of tissue within a patient's bone |
BR112012027707A2 (en) | 2010-04-29 | 2018-05-08 | Dfine Inc | medical device to treat rigid tissue |
CA2800312C (en) | 2010-05-03 | 2021-01-19 | Neuwave Medical, Inc. | Energy delivery systems and uses thereof |
EP2627274B1 (en) | 2010-10-13 | 2022-12-14 | AngioDynamics, Inc. | System for electrically ablating tissue of a patient |
DK2642931T3 (en) | 2010-11-22 | 2017-06-06 | Dfine Inc | SYSTEM FOR USE IN TREATMENT OF VERTEBRA FRACTURES |
US10405920B2 (en) | 2016-01-25 | 2019-09-10 | Biosense Webster (Israel) Ltd. | Temperature controlled short duration ablation |
US10441354B2 (en) | 2016-01-25 | 2019-10-15 | Biosense Webster (Israel) Ltd. | Temperature controlled short duration ablation |
US10292763B2 (en) | 2016-01-25 | 2019-05-21 | Biosense Webster (Israel) Ltd. | Temperature controlled short duration ablation |
RU2457773C1 (en) * | 2011-01-24 | 2012-08-10 | Государственное бюджетное образовательное учреждение дополнительного профессионального образования "Новокузнецкий государственный институт усовершенствования врачей" Министерства здравоохранения и социального развития Российской Федерации (ГБОУ ДПО НГИУВ Минздравсоцразвития России) | Device for sampling of biological material from lacunae of palatine tonsils |
EP3095407A3 (en) | 2011-04-08 | 2017-03-08 | Covidien LP | Flexible microwave catheters for natural or artificial lumens |
US8706258B2 (en) * | 2011-08-08 | 2014-04-22 | Medamp Electronics, Llc | Method and apparatus for treating cancer |
US9078665B2 (en) | 2011-09-28 | 2015-07-14 | Angiodynamics, Inc. | Multiple treatment zone ablation probe |
EP2793726B1 (en) | 2011-12-21 | 2020-09-30 | Neuwave Medical, Inc. | Energy delivery systems |
WO2013147990A1 (en) | 2012-03-27 | 2013-10-03 | Dfine, Inc. | Methods and systems for use in controlling tissue ablation volume by temperature monitoring |
WO2013184319A1 (en) | 2012-06-04 | 2013-12-12 | Boston Scientific Scimed, Inc. | Systems and methods for treating tissue of a passageway within a body |
WO2013192553A1 (en) | 2012-06-22 | 2013-12-27 | Covidien Lp | Microwave thermometry for microwave ablation systems |
EP2877113B1 (en) | 2012-07-24 | 2018-07-25 | Boston Scientific Scimed, Inc. | Electrodes for tissue treatment |
US9247992B2 (en) | 2012-08-07 | 2016-02-02 | Covidien, LP | Microwave ablation catheter and method of utilizing the same |
US9272132B2 (en) | 2012-11-02 | 2016-03-01 | Boston Scientific Scimed, Inc. | Medical device for treating airways and related methods of use |
WO2014071372A1 (en) | 2012-11-05 | 2014-05-08 | Boston Scientific Scimed, Inc. | Devices for delivering energy to body lumens |
US9918766B2 (en) | 2012-12-12 | 2018-03-20 | Dfine, Inc. | Devices, methods and systems for affixing an access device to a vertebral body for the insertion of bone cement |
US9398933B2 (en) | 2012-12-27 | 2016-07-26 | Holaira, Inc. | Methods for improving drug efficacy including a combination of drug administration and nerve modulation |
US9717551B2 (en) | 2013-02-21 | 2017-08-01 | Carefusion 2200, Inc. | Intravertebral tissue ablation device and method |
US9877707B2 (en) | 2013-03-07 | 2018-01-30 | Kyphon SÀRL | Systems and methods for track coagulation |
WO2014160931A1 (en) | 2013-03-29 | 2014-10-02 | Covidien Lp | Step-down coaxial microwave ablation applicators and methods for manufacturing same |
EP2986229A4 (en) | 2013-04-16 | 2016-09-28 | Transmed7 Llc | Methods, devices and therapeutic platform for automated, selectable, soft tissue resection |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9655670B2 (en) | 2013-07-29 | 2017-05-23 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
CN110547865B (en) | 2013-08-09 | 2022-10-04 | 波士顿科学国际有限公司 | Expandable catheter and related methods of manufacture and use |
WO2015042900A1 (en) | 2013-09-29 | 2015-04-02 | Covidien Lp | Medical treatment devices having adjustable length and/or diameter |
WO2015042906A1 (en) | 2013-09-29 | 2015-04-02 | Covidien Lp | Medical treatment devices having adjustable length and/or diameter |
US9433460B2 (en) * | 2014-05-30 | 2016-09-06 | Bipad, Llc | Electrosurgery actuator |
EP3179944A4 (en) * | 2014-08-12 | 2018-04-04 | Invuity, Inc. | Illuminated electrosurgical system and method of use |
US10624697B2 (en) | 2014-08-26 | 2020-04-21 | Covidien Lp | Microwave ablation system |
US10813691B2 (en) | 2014-10-01 | 2020-10-27 | Covidien Lp | Miniaturized microwave ablation assembly |
US20160262731A1 (en) * | 2015-03-10 | 2016-09-15 | Michel Kliot | Nerve stimulation biopsy device |
WO2016177600A1 (en) * | 2015-05-06 | 2016-11-10 | Koninklijke Philips N.V. | Optical tissue feedback device for an electrosurgical device |
US9901392B2 (en) | 2015-05-11 | 2018-02-27 | Dfine, Inc. | System for use in treatment of vertebral fractures |
KR102601297B1 (en) | 2015-10-26 | 2023-11-14 | 뉴웨이브 메디컬, 인코포레이티드 | Energy transfer systems and their uses |
US9901393B2 (en) * | 2015-11-09 | 2018-02-27 | First Pass, Llc | Cautery device |
US10441339B2 (en) | 2015-11-17 | 2019-10-15 | Medtronic Holding Company Sárl | Spinal tissue ablation apparatus, system, and method |
US10307206B2 (en) | 2016-01-25 | 2019-06-04 | Biosense Webster (Israel) Ltd. | Temperature controlled short duration ablation |
US10813692B2 (en) | 2016-02-29 | 2020-10-27 | Covidien Lp | 90-degree interlocking geometry for introducer for facilitating deployment of microwave radiating catheter |
KR102368115B1 (en) | 2016-04-15 | 2022-03-03 | 뉴웨이브 메디컬, 인코포레이티드 | Systems for energy transfer |
US20200000516A1 (en) * | 2016-06-21 | 2020-01-02 | Daniel Igor Branovan | Sterile disposable bipolar ablation needle, associated system, and method of use |
US20170360501A1 (en) * | 2016-06-21 | 2017-12-21 | Daniel Igor Branovan | Disposable bipolar coaxial radio frequency ablation needle, system and method |
US11197715B2 (en) | 2016-08-02 | 2021-12-14 | Covidien Lp | Ablation cable assemblies and a method of manufacturing the same |
US11065053B2 (en) | 2016-08-02 | 2021-07-20 | Covidien Lp | Ablation cable assemblies and a method of manufacturing the same |
US10376309B2 (en) | 2016-08-02 | 2019-08-13 | Covidien Lp | Ablation cable assemblies and a method of manufacturing the same |
US10646268B2 (en) | 2016-08-26 | 2020-05-12 | Bipad, Inc. | Ergonomic actuator for electrosurgical tool |
US10478241B2 (en) | 2016-10-27 | 2019-11-19 | Merit Medical Systems, Inc. | Articulating osteotome with cement delivery channel |
US10905492B2 (en) | 2016-11-17 | 2021-02-02 | Angiodynamics, Inc. | Techniques for irreversible electroporation using a single-pole tine-style internal device communicating with an external surface electrode |
US11052237B2 (en) | 2016-11-22 | 2021-07-06 | Dfine, Inc. | Swivel hub |
KR20190082300A (en) | 2016-11-28 | 2019-07-09 | 디파인 인코포레이티드 | Tumor ablation device and related method |
US10470781B2 (en) | 2016-12-09 | 2019-11-12 | Dfine, Inc. | Medical devices for treating hard tissues and related methods |
EP3565486B1 (en) | 2017-01-06 | 2021-11-10 | Dfine, Inc. | Osteotome with a distal portion for simultaneous advancement and articulation |
TWI634868B (en) | 2017-12-22 | 2018-09-11 | 財團法人工業技術研究院 | Bipolar electrode probe |
US11672596B2 (en) | 2018-02-26 | 2023-06-13 | Neuwave Medical, Inc. | Energy delivery devices with flexible and adjustable tips |
US10576248B2 (en) | 2018-07-23 | 2020-03-03 | Crossbay Medical, Inc. | Apparatus and method for everting catheter for uterine access for biopsy and cytology |
EP3876856A4 (en) | 2018-11-08 | 2022-10-12 | Dfine, Inc. | Tumor ablation device and related systems and methods |
US11832879B2 (en) | 2019-03-08 | 2023-12-05 | Neuwave Medical, Inc. | Systems and methods for energy delivery |
EP4031040A4 (en) | 2019-09-18 | 2023-11-15 | Merit Medical Systems, Inc. | Osteotome with inflatable portion and multiwire articulation |
EP4349288A1 (en) | 2022-10-07 | 2024-04-10 | Erbe Elektromedizin GmbH | Ablation probe with internal cooling |
US11937869B1 (en) | 2023-01-20 | 2024-03-26 | Panacea Spine, LLC | Electrocautery rhizotomy using wanding of energized electrocautery probe |
Citations (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4658836A (en) | 1985-06-28 | 1987-04-21 | Bsd Medical Corporation | Body passage insertable applicator apparatus for electromagnetic |
US4679561A (en) | 1985-05-20 | 1987-07-14 | The United States Of America As Represented By The United States Department Of Energy | Implantable apparatus for localized heating of tissue |
US4737628A (en) | 1984-02-07 | 1988-04-12 | International Technical Associates | Method and system for controlled and selective removal of material |
US4860744A (en) | 1987-11-02 | 1989-08-29 | Raj K. Anand | Thermoelectrically controlled heat medical catheter |
US4872458A (en) | 1986-09-16 | 1989-10-10 | Olympus Optical Co., Ltd. | Thermotherapy apparatus |
US4898169A (en) * | 1987-05-08 | 1990-02-06 | Boston Scientific Corporation | Medical instrument for therapy of hemorrhoidal lesions |
US4979518A (en) | 1986-06-13 | 1990-12-25 | Olympus Optical Co., Ltd. | Body depth heating hyperthermal apparatus |
US5085659A (en) * | 1990-11-21 | 1992-02-04 | Everest Medical Corporation | Biopsy device with bipolar coagulation capability |
US5117828A (en) * | 1989-09-25 | 1992-06-02 | Arzco Medical Electronics, Inc. | Expandable esophageal catheter |
US5125928A (en) * | 1989-04-13 | 1992-06-30 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5251645A (en) | 1991-06-26 | 1993-10-12 | Massachusetts Institute Of Technology | Adaptive nulling hyperthermia array |
US5284144A (en) | 1989-11-22 | 1994-02-08 | The United States Of America As Represented By The Secretary Of The Dept. Of Health & Human Services | Apparatus for hyperthermia treatment of cancer |
US5330470A (en) * | 1991-07-04 | 1994-07-19 | Delma Elektro-Und Medizinische Apparatebau Gesellschaft Mbh | Electro-surgical treatment instrument |
US5383874A (en) * | 1991-11-08 | 1995-01-24 | Ep Technologies, Inc. | Systems for identifying catheters and monitoring their use |
US5429636A (en) * | 1993-10-08 | 1995-07-04 | United States Surgical Corporation | Conductive body tissue penetrating device |
US5514130A (en) * | 1994-10-11 | 1996-05-07 | Dorsal Med International | RF apparatus for controlled depth ablation of soft tissue |
US5599345A (en) * | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment apparatus |
Family Cites Families (25)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE257754C (en) * | ||||
US34421A (en) * | 1862-02-18 | Improvement in channeling-tools for harness-makers | ||
US4016886A (en) * | 1974-11-26 | 1977-04-12 | The United States Of America As Represented By The United States Energy Research And Development Administration | Method for localizing heating in tumor tissue |
US4121592A (en) * | 1975-08-04 | 1978-10-24 | Critical Systems, Inc. | Apparatus for heating tissue |
US4140109A (en) * | 1977-10-17 | 1979-02-20 | Savic Michael I | Impedance-based method and apparatus for monitoring cryodestruction in controlled cryosurgery |
US4458694A (en) * | 1977-11-02 | 1984-07-10 | Yeda Research & Development Co., Ltd. | Apparatus and method for detection of tumors in tissue |
IL53286A (en) * | 1977-11-02 | 1980-01-31 | Yeda Res & Dev | Apparatus and method for detection of tumors in tissue |
US4520249A (en) * | 1977-11-11 | 1985-05-28 | Submicron, Inc. | Method of and apparatus for selective localized differential hyperthermia of a medium |
US4776334A (en) * | 1985-03-22 | 1988-10-11 | Stanford University | Catheter for treatment of tumors |
FR2582947B1 (en) * | 1985-06-07 | 1988-05-13 | Cgr Mev | HYPERTHERMIA TREATMENT DEVICE |
SE455920B (en) * | 1986-01-29 | 1988-08-22 | Hans Wiksell | TUMOR HYPERTERMY TREATMENT DEVICE |
SE467196B (en) * | 1987-11-13 | 1992-06-15 | Bjoern Nordenstroem | DEVICE TO APPLY ELECTRICAL ENERGY TO BIOLOGICAL WEAVE TO SIMULATE THE PHYSIOLOGICAL HEALING PROCESS |
US4920978A (en) * | 1988-08-31 | 1990-05-01 | Triangle Research And Development Corporation | Method and apparatus for the endoscopic treatment of deep tumors using RF hyperthermia |
IL91193A (en) * | 1989-08-02 | 1996-01-19 | Yeda Res & Dev | Tumor detection system |
DE3930451C2 (en) * | 1989-09-12 | 2002-09-26 | Leibinger Gmbh | Device for high-frequency coagulation of biological tissue |
US5069223A (en) * | 1990-02-14 | 1991-12-03 | Georgetown University | Method of evaluating tissue changes resulting from therapeutic hyperthermia |
US5122137A (en) * | 1990-04-27 | 1992-06-16 | Boston Scientific Corporation | Temperature controlled rf coagulation |
US5470308A (en) * | 1992-08-12 | 1995-11-28 | Vidamed, Inc. | Medical probe with biopsy stylet |
US5486161A (en) * | 1993-02-02 | 1996-01-23 | Zomed International | Medical probe device and method |
US5458597A (en) * | 1993-11-08 | 1995-10-17 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5536267A (en) * | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5472441A (en) * | 1993-11-08 | 1995-12-05 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5507743A (en) * | 1993-11-08 | 1996-04-16 | Zomed International | Coiled RF electrode treatment apparatus |
US5578030A (en) * | 1994-11-04 | 1996-11-26 | Levin; John M. | Biopsy needle with cauterization feature |
DE19541566A1 (en) * | 1995-11-08 | 1997-05-15 | Laser & Med Tech Gmbh | Application system for HF surgery for interstitial thermotherapy in bipolar technology (HF-ITT) |
-
1997
- 1997-07-03 US US08/888,063 patent/US6106524A/en not_active Expired - Lifetime
-
1998
- 1998-06-30 JP JP50726299A patent/JP2002507924A/en not_active Ceased
- 1998-06-30 DE DE69830087T patent/DE69830087T2/en not_active Expired - Fee Related
- 1998-06-30 ES ES98931678T patent/ES2230703T3/en not_active Expired - Lifetime
- 1998-06-30 WO PCT/US1998/013414 patent/WO1999001074A1/en active IP Right Grant
- 1998-06-30 ES ES04008393T patent/ES2240954T3/en not_active Expired - Lifetime
- 1998-06-30 EP EP98931678A patent/EP1006903B1/en not_active Expired - Lifetime
- 1998-06-30 DE DE69827270T patent/DE69827270T2/en not_active Expired - Fee Related
- 1998-06-30 CA CA002294946A patent/CA2294946A1/en not_active Abandoned
- 1998-06-30 EP EP04008393A patent/EP1440665B1/en not_active Expired - Lifetime
Patent Citations (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4737628A (en) | 1984-02-07 | 1988-04-12 | International Technical Associates | Method and system for controlled and selective removal of material |
US4679561A (en) | 1985-05-20 | 1987-07-14 | The United States Of America As Represented By The United States Department Of Energy | Implantable apparatus for localized heating of tissue |
US4658836A (en) | 1985-06-28 | 1987-04-21 | Bsd Medical Corporation | Body passage insertable applicator apparatus for electromagnetic |
US4979518A (en) | 1986-06-13 | 1990-12-25 | Olympus Optical Co., Ltd. | Body depth heating hyperthermal apparatus |
US4872458A (en) | 1986-09-16 | 1989-10-10 | Olympus Optical Co., Ltd. | Thermotherapy apparatus |
US4898169A (en) * | 1987-05-08 | 1990-02-06 | Boston Scientific Corporation | Medical instrument for therapy of hemorrhoidal lesions |
US4860744A (en) | 1987-11-02 | 1989-08-29 | Raj K. Anand | Thermoelectrically controlled heat medical catheter |
US5125928A (en) * | 1989-04-13 | 1992-06-30 | Everest Medical Corporation | Ablation catheter with selectively deployable electrodes |
US5117828A (en) * | 1989-09-25 | 1992-06-02 | Arzco Medical Electronics, Inc. | Expandable esophageal catheter |
US5284144A (en) | 1989-11-22 | 1994-02-08 | The United States Of America As Represented By The Secretary Of The Dept. Of Health & Human Services | Apparatus for hyperthermia treatment of cancer |
US5085659A (en) * | 1990-11-21 | 1992-02-04 | Everest Medical Corporation | Biopsy device with bipolar coagulation capability |
US5251645A (en) | 1991-06-26 | 1993-10-12 | Massachusetts Institute Of Technology | Adaptive nulling hyperthermia array |
US5330470A (en) * | 1991-07-04 | 1994-07-19 | Delma Elektro-Und Medizinische Apparatebau Gesellschaft Mbh | Electro-surgical treatment instrument |
US5383874A (en) * | 1991-11-08 | 1995-01-24 | Ep Technologies, Inc. | Systems for identifying catheters and monitoring their use |
US5429636A (en) * | 1993-10-08 | 1995-07-04 | United States Surgical Corporation | Conductive body tissue penetrating device |
US5599345A (en) * | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment apparatus |
US5514130A (en) * | 1994-10-11 | 1996-05-07 | Dorsal Med International | RF apparatus for controlled depth ablation of soft tissue |
Non-Patent Citations (1)
Title |
---|
See also references of EP1006903A4 |
Cited By (96)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6561998B1 (en) | 1998-04-07 | 2003-05-13 | Transvascular, Inc. | Transluminal devices, systems and methods for enlarging interstitial penetration tracts |
US6849080B2 (en) | 1998-09-03 | 2005-02-01 | Rubicon Medical, Inc. | Excisional biopsy device and methods |
US6423081B1 (en) | 1998-09-03 | 2002-07-23 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
US6440147B1 (en) | 1998-09-03 | 2002-08-27 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
US7303531B2 (en) | 1998-09-03 | 2007-12-04 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
US6863676B2 (en) | 1998-09-03 | 2005-03-08 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
US6764495B2 (en) | 1998-09-03 | 2004-07-20 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
EP1059067A1 (en) * | 1999-06-11 | 2000-12-13 | Sherwood Services AG | Ablation treatment of bone metastases |
US6478793B1 (en) | 1999-06-11 | 2002-11-12 | Sherwood Services Ag | Ablation treatment of bone metastases |
US6881214B2 (en) | 1999-06-11 | 2005-04-19 | Sherwood Services Ag | Ablation treatment of bone metastases |
JP2004505663A (en) * | 2000-08-09 | 2004-02-26 | アースロケア コーポレイション | Device for treating spinal irregularities |
US7198626B2 (en) | 2000-12-07 | 2007-04-03 | Rubicor Medical, Inc. | Methods and devices for radiofrequency electrosurgery |
US7725155B2 (en) | 2001-04-13 | 2010-05-25 | Novian Health, Inc. | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
US10765342B2 (en) | 2001-04-13 | 2020-09-08 | Novian Health, Inc. | Apparatus and method for delivering ablative laser energy and determining the volume of tumor mass destroyed |
US8066727B2 (en) | 2002-07-03 | 2011-11-29 | Rubicor Medical Llc | Methods and devices for cutting and collecting soft tissue |
US7044956B2 (en) | 2002-07-03 | 2006-05-16 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
US7438693B2 (en) | 2002-10-16 | 2008-10-21 | Rubicor Medical, Inc. | Devices and methods for performing procedures on a breast |
US6936014B2 (en) | 2002-10-16 | 2005-08-30 | Rubicor Medical, Inc. | Devices and methods for performing procedures on a breast |
US7029451B2 (en) | 2002-11-06 | 2006-04-18 | Rubicor Medical, Inc. | Excisional devices having selective cutting and atraumatic configurations and methods of using same |
US7122011B2 (en) | 2003-06-18 | 2006-10-17 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
US7615013B2 (en) | 2003-06-18 | 2009-11-10 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
US8092449B2 (en) | 2003-07-11 | 2012-01-10 | Celon Ag | Surgical probe |
US9113888B2 (en) | 2004-10-08 | 2015-08-25 | Covidien Ag | Electrosurgical system employing multiple electrodes and method thereof |
EP1804676A2 (en) * | 2004-10-26 | 2007-07-11 | Poh Choo Mona Tan | Device for cauterising tissue and uses thereof |
EP1804676A4 (en) * | 2004-10-26 | 2012-09-05 | Jabez Hope Pte Ltd | Device for cauterising tissue and uses thereof |
US9848932B2 (en) | 2006-07-28 | 2017-12-26 | Covidien Ag | Cool-tip thermocouple including two-piece hub |
US9833287B2 (en) | 2007-01-31 | 2017-12-05 | Covidien Lp | Thermal feedback systems and methods of using the same |
US8956350B2 (en) | 2007-01-31 | 2015-02-17 | Covidien Lp | Thermal feedback systems and methods of using the same |
US8613743B2 (en) | 2007-05-14 | 2013-12-24 | Erbe Elektromedizin Gmbh | HF surgical testing device |
GB2450679A (en) * | 2007-06-19 | 2009-01-07 | Gyrus Medical Ltd | Electrosurgical System with status indicators on instruments |
US8709010B2 (en) | 2007-06-19 | 2014-04-29 | Gyrus Medical Limited | Electrosurgical system |
US9486269B2 (en) | 2007-06-22 | 2016-11-08 | Covidien Lp | Electrosurgical systems and cartridges for use therewith |
US10524850B2 (en) | 2008-07-22 | 2020-01-07 | Covidien Lp | Electrosurgical devices, systems and methods of using the same |
US9877769B2 (en) | 2008-07-22 | 2018-01-30 | Covidien Lp | Electrosurgical devices, systems and methods of using the same |
US10828100B2 (en) | 2009-08-25 | 2020-11-10 | Covidien Lp | Microwave ablation with tissue temperature monitoring |
US10682170B2 (en) | 2010-01-29 | 2020-06-16 | Medtronic Cryocath Lp | Multifunctional ablation device |
US11666369B2 (en) | 2010-01-29 | 2023-06-06 | Medtronic Cryocath Lp | Multifunctional ablation device |
US10854112B2 (en) | 2010-10-01 | 2020-12-01 | Applied Medical Resources Corporation | Portable laparoscopic trainer |
US8764452B2 (en) | 2010-10-01 | 2014-07-01 | Applied Medical Resources Corporation | Portable laparoscopic trainer |
US9472121B2 (en) | 2010-10-01 | 2016-10-18 | Applied Medical Resources Corporation | Portable laparoscopic trainer |
US9218753B2 (en) | 2011-10-21 | 2015-12-22 | Applied Medical Resources Corporation | Simulated tissue structure for surgical training |
US11158212B2 (en) | 2011-10-21 | 2021-10-26 | Applied Medical Resources Corporation | Simulated tissue structure for surgical training |
US8961190B2 (en) | 2011-12-20 | 2015-02-24 | Applied Medical Resources Corporation | Advanced surgical simulation |
AU2012358851B2 (en) * | 2011-12-20 | 2016-08-11 | Applied Medical Resources Corporation | Advanced surgical simulation |
AU2016238938B2 (en) * | 2011-12-20 | 2017-10-26 | Applied Medical Resources Corporation | Advanced Surgical Simulation |
WO2013096632A1 (en) * | 2011-12-20 | 2013-06-27 | Applied Medical Resources Corporation | Advanced surgical simulation |
US11403968B2 (en) | 2011-12-20 | 2022-08-02 | Applied Medical Resources Corporation | Advanced surgical simulation |
US9820805B2 (en) | 2012-06-12 | 2017-11-21 | Gyrus Medical Limited | Electrosurgical instrument and system |
EP2692306B1 (en) * | 2012-08-02 | 2016-10-05 | Covidien LP | Adjustable length and/or exposure electrodes |
US9375252B2 (en) | 2012-08-02 | 2016-06-28 | Covidien Lp | Adjustable length and/or exposure electrodes |
US10198965B2 (en) | 2012-08-03 | 2019-02-05 | Applied Medical Resources Corporation | Simulated stapling and energy based ligation for surgical training |
US10535281B2 (en) | 2012-09-26 | 2020-01-14 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US11514819B2 (en) | 2012-09-26 | 2022-11-29 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10121391B2 (en) | 2012-09-27 | 2018-11-06 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US11361679B2 (en) | 2012-09-27 | 2022-06-14 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US9959786B2 (en) | 2012-09-27 | 2018-05-01 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US11869378B2 (en) | 2012-09-27 | 2024-01-09 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US11990055B2 (en) | 2012-09-27 | 2024-05-21 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10679520B2 (en) | 2012-09-27 | 2020-06-09 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10395559B2 (en) | 2012-09-28 | 2019-08-27 | Applied Medical Resources Corporation | Surgical training model for transluminal laparoscopic procedures |
US9898937B2 (en) | 2012-09-28 | 2018-02-20 | Applied Medical Resources Corporation | Surgical training model for laparoscopic procedures |
US10991270B2 (en) | 2013-03-01 | 2021-04-27 | Applied Medical Resources Corporation | Advanced surgical simulation constructions and methods |
US9940849B2 (en) | 2013-03-01 | 2018-04-10 | Applied Medical Resources Corporation | Advanced surgical simulation constructions and methods |
US10140889B2 (en) | 2013-05-15 | 2018-11-27 | Applied Medical Resources Corporation | Hernia model |
US9449532B2 (en) | 2013-05-15 | 2016-09-20 | Applied Medical Resources Corporation | Hernia model |
US11735068B2 (en) | 2013-06-18 | 2023-08-22 | Applied Medical Resources Corporation | Gallbladder model |
US11049418B2 (en) | 2013-06-18 | 2021-06-29 | Applied Medical Resources Corporation | Gallbladder model |
US9922579B2 (en) | 2013-06-18 | 2018-03-20 | Applied Medical Resources Corporation | Gallbladder model |
US10657845B2 (en) | 2013-07-24 | 2020-05-19 | Applied Medical Resources Corporation | First entry model |
US11854425B2 (en) | 2013-07-24 | 2023-12-26 | Applied Medical Resources Corporation | First entry model |
US10198966B2 (en) | 2013-07-24 | 2019-02-05 | Applied Medical Resources Corporation | Advanced first entry model for surgical simulation |
US10026337B2 (en) | 2013-07-24 | 2018-07-17 | Applied Medical Resources Corporation | First entry model |
US11450236B2 (en) | 2013-07-24 | 2022-09-20 | Applied Medical Resources Corporation | Advanced first entry model for surgical simulation |
US9548002B2 (en) | 2013-07-24 | 2017-01-17 | Applied Medical Resources Corporation | First entry model |
US10796606B2 (en) | 2014-03-26 | 2020-10-06 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US10818201B2 (en) | 2014-11-13 | 2020-10-27 | Applied Medical Resources Corporation | Simulated tissue models and methods |
US11887504B2 (en) | 2014-11-13 | 2024-01-30 | Applied Medical Resources Corporation | Simulated tissue models and methods |
US10354556B2 (en) | 2015-02-19 | 2019-07-16 | Applied Medical Resources Corporation | Simulated tissue structures and methods |
US11100815B2 (en) | 2015-02-19 | 2021-08-24 | Applied Medical Resources Corporation | Simulated tissue structures and methods |
US10081727B2 (en) | 2015-05-14 | 2018-09-25 | Applied Medical Resources Corporation | Synthetic tissue structures for electrosurgical training and simulation |
US11034831B2 (en) | 2015-05-14 | 2021-06-15 | Applied Medical Resources Corporation | Synthetic tissue structures for electrosurgical training and simulation |
US11721240B2 (en) | 2015-06-09 | 2023-08-08 | Applied Medical Resources Corporation | Hysterectomy model |
US10223936B2 (en) | 2015-06-09 | 2019-03-05 | Applied Medical Resources Corporation | Hysterectomy model |
US10733908B2 (en) | 2015-06-09 | 2020-08-04 | Applied Medical Resources Corporation | Hysterectomy model |
US10755602B2 (en) | 2015-07-16 | 2020-08-25 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US11587466B2 (en) | 2015-07-16 | 2023-02-21 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US10332425B2 (en) | 2015-07-16 | 2019-06-25 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US10490105B2 (en) | 2015-07-22 | 2019-11-26 | Applied Medical Resources Corporation | Appendectomy model |
US11721242B2 (en) | 2015-10-02 | 2023-08-08 | Applied Medical Resources Corporation | Hysterectomy model |
US10720084B2 (en) | 2015-10-02 | 2020-07-21 | Applied Medical Resources Corporation | Hysterectomy model |
US10706743B2 (en) | 2015-11-20 | 2020-07-07 | Applied Medical Resources Corporation | Simulated dissectible tissue |
US11830378B2 (en) | 2016-06-27 | 2023-11-28 | Applied Medical Resources Corporation | Simulated abdominal wall |
US11120708B2 (en) | 2016-06-27 | 2021-09-14 | Applied Medical Resources Corporation | Simulated abdominal wall |
US11030922B2 (en) | 2017-02-14 | 2021-06-08 | Applied Medical Resources Corporation | Laparoscopic training system |
US10847057B2 (en) | 2017-02-23 | 2020-11-24 | Applied Medical Resources Corporation | Synthetic tissue structures for electrosurgical training and simulation |
US12004806B2 (en) | 2020-10-22 | 2024-06-11 | Covidien Lp | Microwave ablation with tissue temperature monitoring |
Also Published As
Publication number | Publication date |
---|---|
ES2230703T3 (en) | 2005-05-01 |
EP1006903B1 (en) | 2004-10-27 |
DE69827270T2 (en) | 2005-11-10 |
ES2240954T3 (en) | 2005-10-16 |
EP1440665A1 (en) | 2004-07-28 |
JP2002507924A (en) | 2002-03-12 |
EP1006903A1 (en) | 2000-06-14 |
US6106524A (en) | 2000-08-22 |
DE69830087D1 (en) | 2005-06-09 |
DE69830087T2 (en) | 2005-09-22 |
DE69827270D1 (en) | 2004-12-02 |
CA2294946A1 (en) | 1999-01-14 |
EP1006903A4 (en) | 2000-11-29 |
EP1440665B1 (en) | 2005-05-04 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP1440665B1 (en) | Apparatus for therapeutic cauterization of predetermined volumes of biological tissue | |
US5947964A (en) | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue | |
US6312428B1 (en) | Methods and apparatus for therapeutic cauterization of predetermined volumes of biological tissue | |
US6287304B1 (en) | Interstitial cauterization of tissue volumes with electrosurgically deployed electrodes | |
JP4414238B2 (en) | Positioning element having a tip that is energized | |
US5507743A (en) | Coiled RF electrode treatment apparatus | |
US5536267A (en) | Multiple electrode ablation apparatus | |
JP6130905B2 (en) | Method and system for use in controlling tissue ablation volume by temperature monitoring | |
JP4191897B2 (en) | Electrosurgical device for cell necrosis induction | |
US9078655B2 (en) | Heated balloon catheter | |
JP7481418B2 (en) | Transperitoneal vapor ablation system and method | |
KR101330755B1 (en) | Ablation instruments and related methods | |
US9265556B2 (en) | Thermally adjustable surgical tool, balloon catheters and sculpting of biologic materials | |
US20140249524A1 (en) | System and method for performing renal nerve modulation | |
US20070112342A1 (en) | Tissue ablation apparatus and method | |
JP5909054B2 (en) | Energy applicator temperature monitoring to assess ablation size | |
JP2019072522A (en) | Electrosurgical device having lumen | |
CN207384319U (en) | Biological tissue's burn treatment device | |
US20170296261A1 (en) | Ablation medical device |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): CA JP |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE |
|
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
ENP | Entry into the national phase |
Ref document number: 2294946 Country of ref document: CA Ref country code: CA Ref document number: 2294946 Kind code of ref document: A Format of ref document f/p: F |
|
WWE | Wipo information: entry into national phase |
Ref document number: 1998931678 Country of ref document: EP |
|
WWP | Wipo information: published in national office |
Ref document number: 1998931678 Country of ref document: EP |
|
WWG | Wipo information: grant in national office |
Ref document number: 1998931678 Country of ref document: EP |