WO1999058070A2 - A radio-frequency generator for an ablation device - Google Patents
A radio-frequency generator for an ablation device Download PDFInfo
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- WO1999058070A2 WO1999058070A2 PCT/US1999/009904 US9909904W WO9958070A2 WO 1999058070 A2 WO1999058070 A2 WO 1999058070A2 US 9909904 W US9909904 W US 9909904W WO 9958070 A2 WO9958070 A2 WO 9958070A2
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- impedance
- ablation device
- power
- ablation
- signal
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—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
- A61B18/1485—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
- A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
-
- 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
- A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
- A61B2018/00559—Female reproductive organs
-
- 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
- A61B2018/00684—Sensing and controlling the application of energy using lookup tables
-
- 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
-
- 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
- A61B2018/00779—Power or energy
-
- 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
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- 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
- A61B2018/124—Generators therefor switching the output to different electrodes, e.g. sequentially
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/06—Measuring instruments not otherwise provided for
- A61B2090/064—Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2218/00—Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2218/001—Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body having means for irrigation and/or aspiration of substances to and/or from the surgical site
- A61B2218/007—Aspiration
Definitions
- the present invention relates generally to the ablation of tissue and more specifically to an apparatus and method for providing radio-frequency power to an ablation device.
- Ablation of the interior lining of a body organ is a procedure which involves heating the organ lining to temperatures which destroy the cells of the lining or coagulate tissue proteins for hemostasis. Such a procedure may be performed as a treatment to one of many conditions, such as chronic bleeding of the endometrial layer of the uterus or abnormalities of the mucosal layer of the gallbladder.
- Existing methods for effecting ablation include circulation of heated fluid inside the organ (either directly or inside a balloon) , laser treatment of the organ lining, and resistive heating using application of radio-frequency (RF) energy to the tissue to be ablated.
- RF radio-frequency
- Techniques using RF energy provide an RF electrical signal to one or more electrodes in contact with the subject organ tissue. Electrical current flows from the electrodes and into the organ tissue. The current flow resistively heats the surrounding tissue. Eventually, the heating process destroys the cells surrounding the electrodes and thereby effectuates ablation.
- blood and saline solution may surround the electrodes. As the cells surrounding the electrodes are destroyed, additional blood and saline solution will surround the electrodes. These conductive liquids act to decrease the electrode impedance. These liquids may be suctioned away during the ablation process. Absent these conductive liquids, the electrode impedance will increase with the destruction of the surrounding cells. Depending upon the specific electrode configuration, the impedance characteristics may change from as little as a fraction of an ohm to well over 200 ohms during the course of an ablation procedure.
- the RF ablation technique must be performed using great care to prevent over-ablation. Monitoring of tissue surface temperature is normally carried out during these ablation procedures to ensure the temperature does not exceed 100° C. If the temperature exceeds 100° C, the fluid within the tissue begins to boil and to thereby produce steam. Because ablation is carried out within a closed cavity within the body, the steam cannot escape and may instead force itself deeply into the tissue, or it may pass into areas adjacent to the area intended to be ablated, causing embolism or unintended burning of adjacent tissues. An RF ablation device must accurately determine the appropriate level of power. This power level must provide sufficient heating to effectuate ablation. At the same time, the power level must be controlled to prevent over-ablation.
- an RF generator must be controlled to respond dynamically to changes in the impedance of the subject tissue.
- Existing RF ablation devices generally apply power to electrodes having a relatively small surface area (e.g. forcept electrodes). Such electrodes ablate a relatively small surface area at a relatively high impedance. Accordingly, the required RF power is relatively low and simple to deliver (typically 80 Watts at approximately 100 Ohms) . During an ablation procedure, the impedance characteristics of such electrodes may change.
- many generators are suitable for providing the relatively low power level over a range of high impedances .
- the power level must not result in over-ablation.
- An apparatus and method for use in performing ablation of organs and other tissues includes an RF generator configured to provide an RF signal to ablation electrodes.
- the power level of the RF signal is determined based on the subject area and depth of the volumetric ablation.
- the RF signal is coupled with the ablation electrode through a transformation circuit.
- the transformation circuit includes a low impedance and a high impedance transformation circuit.
- the low impedance and high impedance transformation circuits are selected based on the impedance of the ablation electrode in contact with the subject tissue. Vacuum level, impedance level, resistance level, and time are measured during ablation. If these parameters exceed determinable limits the ablation procedure is terminated.
- Fig. 1A is a side elevation view of an RF generator according to the invention and an ablation device suitable for use with the RF generator.
- Fig. IB is a top view of the distal end of the ablation device of Fig. 1A, shown with an applicator head in an extended position.
- Fig. IC is a perspective view of the applicator head in the extended position of Fig. IB.
- Fig. IC is a front elevational view of the applicator head in the extended position of Fig. IB.
- Fig. 2 is a circuit block diagram of the RF generator of Fig. 1.
- Fig. 3 is a circuit block diagram of the controller of Fig. 2, including additional circuit elements connected with the controller.
- Fig. 4 is a circuit block diagram of the auto- switch circuit of Fig. 2, including additional circuit elements connected with the auto-switch circuit .
- Fig. 5 is a circuit block diagram of the display board of Fig. 2, including additional circuit elements connected with the display board.
- Fig. 6 is a circuit diagram of one preferred embodiment of the transformer circuit of Fig. 5 connected with a regulator and a filter network.
- Fig. 7 is a circuit diagram of another embodiment of the transformer circuit of Fig. 5.
- Fig. 8 is a flow chart showing the operation of an RF generator according to the invention.
- Fig. 9 is a flow chart showing the operation of an the auto-switch circuit according to the invention.
- an intrauterine ablation device 100 suitable for use with an RF generator 116 according to the present invention is comprised generally of three major components: an RF applicator head 103, a sheath 105, and a handle 106.
- the applicator head 103 is slidably disposed within the sheath 105 (Fig. 1A) during insertion of the device into the uterine cavity, and the handle 106 is subsequently manipulated as indicated by arrow Al to cause the applicator head 103 to extend from the distal end of the sheath 105 (Fig. IB) .
- applicator head 103 extends from the distal end of a length of tubing 108 which is slidably disposed within the sheath 105.
- Applicator 103 includes an external electrode array 103a and an internal deflecting mechanism 103b used to expand the array for positioning into contact with the tissue.
- the RF electrode array 103a is formed of a stretchable metallized fabric mesh which is preferably knitted from a nylon and spandex knit plated with gold or other conductive material.
- Insulating regions 140 (Figs. IC, ID) are formed on the applicator head to divide the mesh into electrode regions.
- the insulated regions 140 are preferably formed using etching techniques to remove the conductive metal from the mesh, although alternate methods may also be used, such as by knitting conductive and non-conductive materials together to form the array.
- the array may be divided by the insulated regions 140 into a variety of electrode configurations.
- the insulating regions 140 divide the applicator head into four electrodes 142a - 142d by creating two electrodes on each of the broad faces 134.
- insulating regions 140 are placed longitudinally along each of the broad faces 134 as well as along the length of each of the faces 136, 138.
- the electrodes 142a-142d are used for ablation and, if desired, to measure tissue impedance during use .
- Deflecting mechanism 103b and its deployment structure is enclosed within electrode array 103a.
- external hypotube 109 extends from tubing 108 and an internal hypotube 110 is slidably and co-axially disposed within hypotube 109.
- Flexures 112 extend from the tubing 108 on opposite sides of hypotube 109.
- a plurality of longitudinally spaced apertures may be formed in each flexure 112. During use, these apertures allow moisture to pass through the flexures and to be drawn into exposed distal end of hypotube 109 using a vacuum source 140 fluidly coupled to hypotube 109 at vacuum port 138.
- Internal flexures 116 extend laterally and longitudinally from the exterior surface of hypotube 110 and are each connected to a corresponding one of the flexures 112.
- a transverse ribbon 118 extends between the distal portions of the internal flexures 116.
- Transverse ribbon 118 is preferably pre-shaped such that when in the relaxed condition the ribbon assumes the corrugated configuration shown in Fig. IB and such that when in a compressed condition it is folded along the plurality of creases 120 that extend along its length.
- the deflecting mechanism 103b formed by the flexures 112, 116, and ribbon 118 shapes the array 103a into the substantially triangular shape shown in Fig. IB, which is particularly adaptable to most uterine shapes.
- distal and proximal grips 144, 146 forming handle 106 are squeezed towards one another to deploy the array. This action results in relative rearward motion of the hypotube 109 and relative forward motion of the hypotube 110.
- the relative motion between the hypotubes causes deflection in flexures 112, 116 which deploys and tensions the electrode array 103a.
- Flexures 112, 116 and ribbon are preferably made from an insulated spring material such as heat treated 17-7 PH stainless steel.
- Each flexure 112 preferably includes conductive regions that are electrically coupled to the array for delivery of RF energy to the body tissue.
- Strands of thread 145 (which may be nylon) are preferably sewn through the array 103 and around the flexures 112 in order to prevent the conductive regions 132 from slipping out of alignment with the electrodes 142a - 142d.
- the RF generator system utilizes an ablation power that is selected based on the surface area of the target ablation tissue.
- the RF power is calculated using the measured length and width of the uterus . These measurements may be made using conventional intrauterine measurement devices.
- the ablation device 100 itself may be used to measure the uterine width by transducing the separation of flexures using a mechanical or electrical transducing means.
- the ablation device 100 includes non-conductive (e.g. nylon) suturing threads 122 that extend between the hypotube 110 and the distal portion of the deflecting mechanism (Fig. IB) .
- Threads 122 are connected to an elongate wire (not shown) which extends through the tubing and is coupled to a mechanical transducer such as a rotatable bobbin (not shown) or an electrical transducer such as a strain gauge electrically coupled to an A/D converter to electrically transduce the separation distance of the flexures 112 and to electronically transmit the uterine width to a visual display and/or directly to the RF generator.
- a mechanical transducer such as a rotatable bobbin (not shown) or an electrical transducer such as a strain gauge electrically coupled to an A/D converter to electrically transduce the separation distance of the flexures 112 and to electronically transmit the uterine width to a visual display and/or directly to the RF generator.
- the circuit includes a power supply 200.
- the power supply 200 accepts an AC signal and generates a 36 volt DC signal at up to 10 amps.
- the power supply 200 connects to converters 202, 204, 206, and 208.
- the converters 202, 204, 206, and 208 generate +5, +12, - 12, and +24 volt electric potentials, respectively.
- the converters 202, 204, 206, and 208 provide the electric potentials to various circuit components hereinafter described.
- a display board 212 generally provides a user interface. This interface allows a user to input selection data and provides feedback information.
- the display board 212 provides a digital signal indicating a desired power setting to digital-to- analog (D/A) converter 214.
- the D/A converter 214 converts the incoming digital signal into a voltage potential.
- This voltage potential (PSET) representing the desired power setting, is provided to an error amplifier 216.
- the error amplifier 216 also receives a voltage potential representing the actual power (PACT) currently delivered to an ablation device.
- the error amplifier compares the set power signal to the actual power signal to determine whether output power should be increased or decreased. If the set power signal is greater than the actual power signal, the error amplifier 216 provides a positive signal to the regulator 210. In response, the regulator 210 increases the output power. If the set power signal is less than the actual power signal, the error amplifier 216 provides a negative signal to the regulator 210. In response, the regulator 210 decreases the output power.
- the regulator 210 receives DC power from the power supply 200 and provides a RF signal to FET switch 211.
- the signal from the error amplifier 216 controls the pulse width modulation of the regulator 210. Pulse width increases effect an increase in power; pulse width decreases effect a decrease in power .
- the FET switch 211 receives the RF signal from the regulator 210.
- the FET switch also receives a control signal from the controller 218.
- the control signal turns on the FET switch 211 so that the RF signal is provided to auto-switch circuit 230.
- the control signal turns off the FET switch 211 so that any signal provided by the regulator 210 is disconnected from the auto-switch circuit 230.
- the auto-switch circuit 230 also receives control signals from the controller 218, and an impedance signal from the divider 222. Based on the control and impedance signals, the auto-switch circuit 230 selects between a low impedance and a high impedance transformation circuits 440 (Fig. 4) . The output of the selected transformer circuit is provided to the filter network 232.
- the filter network 232 acts as a bandpass filter having a preferred center frequency of approximately 482 KHz.
- the filter network 232 reduces any higher-order harmonic signals on the RF signal.
- the filter network 232 decouples any DC components from the regulator 210.
- Current detector 234 measures the current provided through the filter network 232.
- the voltage detector 236 measures the voltage provided across the output of the filter network 232. These measured signals are provided to the divider 222 through RMS convertors 221 and 222. The measured signals are also provided to the multiplier 220.
- the divider 222 divides the voltage signal by the current signal to produce a signal representing the effective impedance of an ablation device.
- the multiplier 220 multiplies the voltage signal by the current signal to produce a signal representing the actual power provided to an ablation device. As described above, the actual power signal is used by the error amplifier 216 to control the regulator 210.
- the effective impedance signal is used by the auto-switch circuit 230 to select between the low impedance and high impedance transformation circuit.
- the actual power signal (PACT) from multiplier 220 and the effective impedance signal from divider 222 are both provided to the controller 218.
- the controller 218 also connects to the set power signal input of the error amplifier 116.
- the controller 218 is configured to measure the power set signal and to generate a set power signal.
- the RF generator also includes a DC resistance detector 238 connected across output relays 240.
- the DC resistance detector 238 measures the DC resistance of an external ablation device.
- the DC resistance detector 238 provides a signal related to this resistance to the controller 218. The controller uses this signal to detect a short circuit in an attached ablation device.
- the output relays 240 receive the filtered RF signal from the filter network 232.
- the output relays 240 are configured to provide this signal to the output terminals 242 in response to a control signal from the controller 218.
- the output relays 240 When energized, the output relays 240 connect the RF generator circuit to an ablation device through output terminals 242.
- the output relays 240 isolate the RF generator circuit from an ablation device.
- a fault and steering control block 302 of the controller 218 provides control signals to the display board 212, the FET switch 211, the auto- switch circuit 230, and the output relays 240.
- the controller 218 provides the impedance signal from divider 222 (Fig. 2) to both an audio circuit 310 and a data I/O translator 306.
- the audio circuit 310 produces a frequency signal related to the impedance signal . Low impedances are transduced into higher frequency signals; high impedances are transduced into a lower frequency signals.
- the frequency signal lies within the range of audible frequencies and is used to drive a speaker 312. During the process of ablation, the measured impedance will increase. Accordingly, the frequency of the sound signal produced by the speaker 312 will decrease. This provides audible feedback of the ablation process to an operator.
- the audio circuit 310 may also be configured to provide signals that increase in frequency with increased impedance.
- the controller 218 also provides the actual and set power signals and the vacuum signal to the data
- the data I/O translator converts these signals and the impedance signal into a related digital signal, which is provided over an RS232 connection 308.
- Vacuum pump AC switch 314 is controlled by the controller 218. When activated, the pump AC switch connects AC power to a vacuum pump 316, which draws moisture from the ablation device and surrounding tissue. When deactivated, pump AC switch disconnects AC power from the vacuum pump 316.
- the vacuum pump 316 When activated, the pump AC switch connects AC power to a vacuum pump 316, which draws moisture from the ablation device and surrounding tissue. When deactivated, pump AC switch disconnects AC power from the vacuum pump 316.
- the 316 also includes a pressure transducer 318.
- the pressure transducer 318 is configured to measure the pressure induced within an ablation device.
- the pressure transducer 318 provides a signal representing this pressure to the controller 218, which monitors whether suction applied by the vacuum pump 316 is within determined limits.
- the auto-switch circuit includes a control sequence PAL 400.
- the PAL 400 receives timer, impedance, and ready signals from controller 218. When activated, the timer signal indicates that the duration of the ablation has exceeded 120 seconds; the impedance signal indicates that the impedance of the ablation device exceeds 50 ohms; and the ready signal indicates that an operator has engaged an RF enable switch.
- the impedance signal from the divider 222 (Fig. 2) is also provided to a comparator 420 via controller 218. If the impedance is greater than 10 ohms, the comparator 420 activates a signal to delay 430. If the impedance is less than 6 ohms, the comparator 420 activates a signal to delay 432.
- the delays 430 and 432 also receive a clock signal from controller 218. If either of the delays 430 or 432 continue to receive a signal from the comparators for more than five seconds, the respective delay activates a signal to the PAL 400.
- the PAL 400 When the impedance is greater than 10 ohms for longer than five seconds, the PAL 400 provides a switch taps (SWTAPS) signal to the transformer circuit 440 selecting a high impedance transformation circuit. When the impedance is less than 6 ohms for longer than 5 seconds, the PAL selects a low impedance transformation circuit.
- SWTAPS switch taps
- the controller 218 also provides an RF power on
- timer 436 receives a clear timer (CLRTMS) signal from the PAL 400.
- CLRTMS clear timer
- the CLRTMS signal is activated upon a change of state in the SWTAPS signal and indicates that the transformer circuit has changed to match the impedance of the ablation device.
- the timer 436 Upon receiving either the RFON or the SWTAPS signal, the timer 436 resets a short and a long timer. After expiration of the short timer, the timer 436 activates the short timer signal, which is provided to the PAL 400. After expiration of the long timer, the timer 436 activates the long timer, which is also provided to PAL 400.
- condition signals are used in conjunction with fault signals to determine whether to terminate an ablation procedure.
- the transformation circuit 440 is connected between the FET switch 211 and the output filter network 232 (Fig. 2) .
- the transformation circuit 440 operates to match the impedance of the regulator 210 to that of an ablation device. Again, the impedance of an ablation electrode in contact with the subject tissue may change significantly during the course of an ablation. By matching the impedance of regulator 210 to that of the electrode, the regulator 210 is able to deliver a relatively constant power level. This in turn allows accurate and uniform ablation. Alternatively, if the impedance of a regulator were matched to a low electrode impedance then the regulator's power delivery will decline as the electrode impedance increases. If the impedance of the regulator were instead matched to a high electrode impedance then at a low initial electrode impedance the regulator will bear a high current load. This load may cause damage or heating to regulator components .
- the transformation circuit 440 include a low impedance transformation circuit and a high impedance transformation circuit.
- a preferred low impedance transformation circuit matches the impedance of the regulator 210 to a three ohm load.
- a preferred high impedance transformation circuit matches the impedance of the regulator 210 to a twenty- five ohm load.
- the PAL 400 provides condition signals to the controller 218. Specifically, the PAL 400 generates a GENFAULT, an IGVAC, an ILPF and a PTEST signal .
- the GENFAULT signal indicates that the PAL has detected a fault condition and that the ablation should be terminated.
- the IGVAC signal indicates that the vacuum circuit has just been energized. Accordingly, any vacuum faults should be ignored for 2 seconds while the vacuum pump establishes the appropriate pressure.
- the IPLF signal indicates that any low priority faults should be ignored. The IPLF signal is activated during start up so that non- critical transient faults do not terminate the ablation procedure.
- the PTEST indicates that a low- level RF signal is currently being applied to the transformation circuit. The low-level RF signal is used to measure RF impedance before applying full power.
- the display board 212 of Fig. 2 and additional related components connects to length and width selection switches 502. After determining the length and width of a subject uterine cavity, an operator enters the appropriate settings using switches 502. The length and width selections are shown on displays 508 and 510, respectively. To increase the width, an operator engages the up arrow switch 550. To decreases the width, an operator engages the down arrow switch 552. To increase the length, an operator engages the up arrow switch 560. To decrease the length, an operator engages the down arrow switch 562. A signal indicating the length and width are provided to the EPROM 516. The EPROM 516 converts the length and width to a set power level according to the following relationship:
- P is the power level in Watts
- L is the length in centimeters
- W is the width in centimeters
- 5.5 is a constant having units of Watts per square centimeter.
- the display board 212 also provides a signal to a set power display 506. This signal is determined based on the length and width selections so that the set power display 506 shows the current power setting.
- the ready switch 504 provides a signal to the display board 212, which is in turn provided to the controller 218.
- the ready switch 504 indicates that the operator is ready to begin an ablation procedure.
- the operator may then depress foot pedal 512.
- the foot pedal 512 connects to foot switch 514 to provide a signal to the display board 212, which is also provided to the controller 218. This signal indicates that the RF generator should apply RF power to an ablation device.
- the display board 212 also connects to status LED's including a READY 320, RF OFF 322, HIGH Z 324, LOW Z 326, HIGH VAC 328, LOW VAC 340, and RF ON 342.
- the display board 212 controls these LED's based on signals received from the controller 218 and from the user inputs.
- the READY LED 520 indicates that the RF generator is in a ready condition, and that activation of the foot switch 514 would activate RF power.
- the RF OFF LED 522 indicates that a DC short condition exists with the ablation device currently connected to the RF generator and that the RF generator is not currently providing power to an ablation device.
- the HIGH Z LED 524 indicates that the impedance exceeds a determined level . When this condition occurs, the controller automatically terminates ablation.
- the LOW Z LED 526 indicates that the impedance falls below a determined level. When this condition occurs, an RF short condition exists.
- the HIGH VAC LED 528 indicates that the vacuum pump 140 is currently exceeding determined acceptable vacuum levels.
- this condition may be generated by an operator standing on the suction tubes connecting the vacuum pump 140 to port 138.
- the LOW VAC LED 540 indicates that the vacuum pump 140 is currently below an acceptable vacuum level. For example, this condition may be generated if the vacuum pump 140 were not properly attached to port 138.
- the RF ON LED 542 indicates that the RF generator is currently providing power to an ablation device.
- the transformation circuit 440 includes a transformer 605 having a power winding 610 and a load winding 620.
- the power winding 610 connects to FET switch 211 for receiving RF power from the regulator 210.
- the load winding 620 is electromagnetically coupled with power winding 610. Accordingly, electric power provided to the power winding 610 is transferred to the load winding 620.
- the load winding 620 includes a center tap 626 which divides the load winding into a first portion 622 and a second portion 624.
- Switch 630 selects between the center tap 626 and an exterior tap 627. Selection of the center tap 626 provides a circuit matched to a lower impedance. Selection of the exterior tap 627 provides a circuit matched to a higher impedance. Alternatively stated, the switch 630 selects the transformation ratio between the power winding 610 and the output terminals 642.
- the output terminals 642 connect to an output filter network 232 having the above described bandpass characteristics.
- the transformation circuit 740 includes a first transformer 705 having a power winding 710 and a load winding 720.
- the transformer switch circuit also includes a second transformer 706 having a power winding 712 and a load winding 722.
- the transformation ratio of the first transformer 705 is matched to a low impedance.
- the transformation ratio of the second transformer 706 is matched to a high impedance .
- Switch 730 is connected to select between the first transformer 705 and the second transformer 706. As shown, the switch 730 selects the first transformer 705 to electrically couple input terminals 740 to output terminals 742. The switch may also select the second transformer 706 to electrically couple input terminals 740 to output terminals 742.
- Fig. 8 a flow chart showing the preferred operation of an RF generator used to power an ablation device is illustrated.
- an operator selects a length and width related to the size of the subject uterus and activates a ready switch.
- the RF generator measures DC resistance through the ablation device. A measured resistance below 200 ohms indicates a short circuit. If a short circuit is detected, the RF generator will provide an indication to the operator and terminate the procedure. A measured resistance greater than
- 200 ohms indicates acceptable contact of the ablation device with the subject uterus.
- the operator may then activate a foot-switch to apply power to an RF regulator.
- the RF generator applies power to a vacuum pump. After a few seconds, the pressure within the subject uterus will drop.
- the RF generator applies a low- level RF signal (e.g. between 5 and 10 Watts) to the ablation device.
- the RF generator tests for faults which indicate that the procedure should be terminated. Specifically, the RF generator continues to test the DC resistance. The RF generator also tests whether the RF impedance falls within acceptable limits (e.g. 0.5 - 50 ohms), and whether the vacuum level falls within acceptable limits. During the first few seconds (e.g. 2 seconds) these faults may be ignored, as the transient characteristics may exceed fault tolerances.
- the RF generator applies full power to the ablation device.
- the power level may be gradually increased to the full power setting.
- the RF generator tests whether the impedance of the subject uterus has exceeded fifty ohms or if the duration of the ablation has exceeded 120 seconds. If ether of these events occur, the ablation is complete and the procedure is terminated at block 824. Otherwise, the RF generator continues to test for faults at block 820. Upon detection of a fault the procedure is similarly terminated and power to the ablation device is disabled.
- a flow chart showing the preferred operation of the application of power through a transformation circuit is illustrated.
- the transformation circuit is used to couple power supplied by the RF generator to an ablation device.
- a preferred transformation circuit includes a low impedance transformation circuit and a high impedance transformation circuit.
- the operation of the transformation circuit begins at block 910, where the low impedance transformation circuit is selected.
- a low level RF signal is applied to the transformation circuit.
- the impedance of an ablation device is measured. If the impedance has not exceeded 10 ohms for 5 seconds the process returns to block 911.
- the pulse width of the RF signal will increase until it reaches the selected power level. Upon reaching the selected level, the pulse width is controlled according to changes in the electrode impedance to maintain a constant power level .
- the process again returns to block 912 where the impedance of the ablation device is again measured.
- the process proceeds to block 913.
- the pulse width of the RF signal must be decreased so that the transformation circuit may switch from the low impedance transformation circuit to the high impedance transformation circuit.
- the switch changes states to select the high impedance transformation circuit.
- power is then ramped back up to the selected level . This reduction in power and gradual increase reduces transient spikes which might result from the switching between the low impedance transformation circuit and the high impedance transformation circuit .
- the impedance of the ablation device is measured. If the impedance has not dropped below 6 ohms for 5 seconds, the process returns to block 915.
- the pulse width is controlled to deliver the selected power level.
- the process again returns to block 916 where the impedance of the ablation device is again measured.
- the process proceeds to block 917.
- the pulse width of the RF signal must be decreased so that the transformation circuit may switch from the high impedance transformation circuit to the low impedance transformation circuit at block 910.
Abstract
Description
Claims
Priority Applications (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU39730/99A AU3973099A (en) | 1998-05-08 | 1999-05-07 | A radio-frequency generator for an ablation device |
EP99922822A EP1076516B1 (en) | 1998-05-08 | 1999-05-07 | A radio-frequency generator for an ablation device |
JP2000547924A JP2003526385A (en) | 1998-05-08 | 1999-05-07 | Radio frequency generator for ablation device |
CA002331321A CA2331321A1 (en) | 1998-05-08 | 1999-05-07 | A radio-frequency generator for an ablation device |
DE69940599T DE69940599D1 (en) | 1998-05-08 | 1999-05-07 | RADIO FREQUENCY GENERATOR FOR AN ABLATION REQUIREMENT |
NO20005623A NO20005623L (en) | 1998-05-08 | 2000-11-07 | Radio frequency generator for an ablation device |
HK01105168.4A HK1034655A1 (en) | 1998-05-08 | 2001-07-24 | A radio-frequency generator for an ablation device |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US8471298P | 1998-05-08 | 1998-05-08 | |
US60/084,712 | 1998-05-08 |
Publications (2)
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WO1999058070A2 true WO1999058070A2 (en) | 1999-11-18 |
WO1999058070A3 WO1999058070A3 (en) | 2000-02-17 |
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Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1999/009904 WO1999058070A2 (en) | 1998-05-08 | 1999-05-07 | A radio-frequency generator for an ablation device |
Country Status (10)
Country | Link |
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US (5) | US6508815B1 (en) |
EP (1) | EP1076516B1 (en) |
JP (1) | JP2003526385A (en) |
CN (1) | CN1308510A (en) |
AT (1) | ATE425702T1 (en) |
AU (1) | AU3973099A (en) |
CA (1) | CA2331321A1 (en) |
HK (1) | HK1034655A1 (en) |
NO (1) | NO20005623L (en) |
WO (1) | WO1999058070A2 (en) |
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---|---|---|---|---|
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US7811282B2 (en) | 2000-03-06 | 2010-10-12 | Salient Surgical Technologies, Inc. | Fluid-assisted electrosurgical devices, electrosurgical unit with pump and methods of use thereof |
US7815634B2 (en) | 2000-03-06 | 2010-10-19 | Salient Surgical Technologies, Inc. | Fluid delivery system and controller for electrosurgical devices |
US7871410B2 (en) | 2002-10-29 | 2011-01-18 | Cathrx Ltd | System for, and method of, heating a biological site in a patient's body |
US7998140B2 (en) | 2002-02-12 | 2011-08-16 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
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US10045810B2 (en) | 2009-03-11 | 2018-08-14 | Erbe Elektromedizin Gmbh | High frequency surgical generator comprising an additional transformer |
Families Citing this family (387)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7604633B2 (en) | 1996-04-12 | 2009-10-20 | Cytyc Corporation | Moisture transport system for contact electrocoagulation |
US6726686B2 (en) | 1997-11-12 | 2004-04-27 | Sherwood Services Ag | Bipolar electrosurgical instrument for sealing vessels |
US6352536B1 (en) * | 2000-02-11 | 2002-03-05 | Sherwood Services Ag | Bipolar electrosurgical instrument for sealing vessels |
US7435249B2 (en) * | 1997-11-12 | 2008-10-14 | Covidien Ag | Electrosurgical instruments which reduces collateral damage to adjacent tissue |
US6228083B1 (en) | 1997-11-14 | 2001-05-08 | Sherwood Services Ag | Laparoscopic bipolar electrosurgical instrument |
US8551082B2 (en) | 1998-05-08 | 2013-10-08 | Cytyc Surgical Products | Radio-frequency generator for powering an ablation device |
US7582087B2 (en) * | 1998-10-23 | 2009-09-01 | Covidien Ag | Vessel sealing instrument |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US20040249374A1 (en) * | 1998-10-23 | 2004-12-09 | Tetzlaff Philip M. | Vessel sealing instrument |
US7118570B2 (en) * | 2001-04-06 | 2006-10-10 | Sherwood Services Ag | Vessel sealing forceps with disposable electrodes |
US7137980B2 (en) * | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US20040167508A1 (en) * | 2002-02-11 | 2004-08-26 | Robert Wham | Vessel sealing system |
US7267677B2 (en) | 1998-10-23 | 2007-09-11 | Sherwood Services Ag | Vessel sealing instrument |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US20100042093A9 (en) * | 1998-10-23 | 2010-02-18 | Wham Robert H | System and method for terminating treatment in impedance feedback algorithm |
US20030109875A1 (en) * | 1999-10-22 | 2003-06-12 | Tetzlaff Philip M. | Open vessel sealing forceps with disposable electrodes |
US6558385B1 (en) * | 2000-09-22 | 2003-05-06 | Tissuelink Medical, Inc. | Fluid-assisted medical device |
US6689131B2 (en) | 2001-03-08 | 2004-02-10 | Tissuelink Medical, Inc. | Electrosurgical device having a tissue reduction sensor |
US10849681B2 (en) | 2001-04-06 | 2020-12-01 | Covidien Ag | Vessel sealer and divider |
DE60121229T2 (en) | 2001-04-06 | 2007-05-24 | Sherwood Services Ag | DEVICE FOR SEALING AND SHARING A VESSEL WITH NON-LASTING END STOP |
CA2442852C (en) * | 2001-04-06 | 2011-07-26 | Sherwood Services Ag | Molded insulating hinge for bipolar instruments |
US7101372B2 (en) * | 2001-04-06 | 2006-09-05 | Sherwood Sevices Ag | Vessel sealer and divider |
EP1527747B1 (en) * | 2001-04-06 | 2015-09-30 | Covidien AG | Electrosurgical instrument which reduces collateral damage to adjacent tissue |
US7959626B2 (en) | 2001-04-26 | 2011-06-14 | Medtronic, Inc. | Transmural ablation systems and methods |
US6989010B2 (en) * | 2001-04-26 | 2006-01-24 | Medtronic, Inc. | Ablation system and method of use |
EP1435867B1 (en) * | 2001-09-05 | 2010-11-17 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices and systems |
AU2002359576A1 (en) * | 2001-12-03 | 2003-06-17 | Ekos Corporation | Catheter with multiple ultrasound radiating members |
AU2002357166A1 (en) * | 2001-12-12 | 2003-06-23 | Tissuelink Medical, Inc. | Fluid-assisted medical devices, systems and methods |
WO2003092520A1 (en) | 2002-05-06 | 2003-11-13 | Sherwood Services Ag | Blood detector for controlling anesu and method therefor |
US7276068B2 (en) | 2002-10-04 | 2007-10-02 | Sherwood Services Ag | Vessel sealing instrument with electrical cutting mechanism |
US7931649B2 (en) | 2002-10-04 | 2011-04-26 | Tyco Healthcare Group Lp | Vessel sealing instrument with electrical cutting mechanism |
US7270664B2 (en) | 2002-10-04 | 2007-09-18 | Sherwood Services Ag | Vessel sealing instrument with electrical cutting mechanism |
US8475455B2 (en) | 2002-10-29 | 2013-07-02 | Medtronic Advanced Energy Llc | Fluid-assisted electrosurgical scissors and methods |
US7799026B2 (en) * | 2002-11-14 | 2010-09-21 | Covidien Ag | Compressible jaw configuration with bipolar RF output electrodes for soft tissue fusion |
US7044948B2 (en) * | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
US7776036B2 (en) | 2003-03-13 | 2010-08-17 | Covidien Ag | Bipolar concentric electrode assembly for soft tissue fusion |
CA2523675C (en) * | 2003-05-01 | 2016-04-26 | Sherwood Services Ag | Electrosurgical instrument which reduces thermal damage to adjacent tissue |
US7722601B2 (en) | 2003-05-01 | 2010-05-25 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US7160299B2 (en) * | 2003-05-01 | 2007-01-09 | Sherwood Services Ag | Method of fusing biomaterials with radiofrequency energy |
AU2004241092B2 (en) * | 2003-05-15 | 2009-06-04 | Covidien Ag | Tissue sealer with non-conductive variable stop members and method of sealing tissue |
US20050021020A1 (en) * | 2003-05-15 | 2005-01-27 | Blaha Derek M. | System for activating an electrosurgical instrument |
USD956973S1 (en) | 2003-06-13 | 2022-07-05 | Covidien Ag | Movable handle for endoscopic vessel sealer and divider |
US7156846B2 (en) | 2003-06-13 | 2007-01-02 | Sherwood Services Ag | Vessel sealer and divider for use with small trocars and cannulas |
US7150749B2 (en) * | 2003-06-13 | 2006-12-19 | Sherwood Services Ag | Vessel sealer and divider having elongated knife stroke and safety cutting mechanism |
US7857812B2 (en) | 2003-06-13 | 2010-12-28 | Covidien Ag | Vessel sealer and divider having elongated knife stroke and safety for cutting mechanism |
US7294125B2 (en) * | 2003-08-22 | 2007-11-13 | Scimed Life Systems, Inc. | Methods of delivering energy to body portions to produce a therapeutic response |
AU2004285412A1 (en) | 2003-09-12 | 2005-05-12 | Minnow Medical, Llc | Selectable eccentric remodeling and/or ablation of atherosclerotic material |
US8579892B2 (en) | 2003-10-07 | 2013-11-12 | Tsunami Medtech, Llc | Medical system and method of use |
AU2003284929B2 (en) | 2003-10-23 | 2010-07-22 | Covidien Ag | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
US8104956B2 (en) | 2003-10-23 | 2012-01-31 | Covidien Ag | Thermocouple measurement circuit |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US9848938B2 (en) | 2003-11-13 | 2017-12-26 | Covidien Ag | Compressible jaw configuration with bipolar RF output electrodes for soft tissue fusion |
US7232440B2 (en) * | 2003-11-17 | 2007-06-19 | Sherwood Services Ag | Bipolar forceps having monopolar extension |
US7367976B2 (en) | 2003-11-17 | 2008-05-06 | Sherwood Services Ag | Bipolar forceps having monopolar extension |
US7252667B2 (en) * | 2003-11-19 | 2007-08-07 | Sherwood Services Ag | Open vessel sealing instrument with cutting mechanism and distal lockout |
US7811283B2 (en) | 2003-11-19 | 2010-10-12 | Covidien Ag | Open vessel sealing instrument with hourglass cutting mechanism and over-ratchet safety |
US7500975B2 (en) * | 2003-11-19 | 2009-03-10 | Covidien Ag | Spring loaded reciprocating tissue cutting mechanism in a forceps-style electrosurgical instrument |
US7131970B2 (en) * | 2003-11-19 | 2006-11-07 | Sherwood Services Ag | Open vessel sealing instrument with cutting mechanism |
US7442193B2 (en) | 2003-11-20 | 2008-10-28 | Covidien Ag | Electrically conductive/insulative over-shoe for tissue fusion |
US7131860B2 (en) * | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US7300435B2 (en) * | 2003-11-21 | 2007-11-27 | Sherwood Services Ag | Automatic control system for an electrosurgical generator |
US7727232B1 (en) * | 2004-02-04 | 2010-06-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices and methods |
US7766905B2 (en) | 2004-02-12 | 2010-08-03 | Covidien Ag | Method and system for continuity testing of medical electrodes |
US7780662B2 (en) | 2004-03-02 | 2010-08-24 | Covidien Ag | Vessel sealing system using capacitive RF dielectric heating |
US8167874B2 (en) * | 2004-07-19 | 2012-05-01 | Mayo Foundation For Medical Education | Assembly and kit for marking tubal ostia |
CN1305445C (en) * | 2004-07-22 | 2007-03-21 | 上海交通大学 | Power generating and monitoring circuit of radio frequency melting therapeutic system |
US7506790B2 (en) * | 2004-07-28 | 2009-03-24 | Ethicon Endo-Surgery, Inc. | Surgical instrument incorporating an electrically actuated articulation mechanism |
US7410086B2 (en) * | 2004-07-28 | 2008-08-12 | Ethicon Endo-Surgery, Inc. | Electroactive polymer-based actuation mechanism for circular stapler |
US7857183B2 (en) | 2004-07-28 | 2010-12-28 | Ethicon Endo-Surgery, Inc. | Surgical instrument incorporating an electrically actuated articulation mechanism |
US7879070B2 (en) * | 2004-07-28 | 2011-02-01 | Ethicon Endo-Surgery, Inc. | Electroactive polymer-based actuation mechanism for grasper |
US7513408B2 (en) * | 2004-07-28 | 2009-04-07 | Ethicon Endo-Surgery, Inc. | Multiple firing stroke surgical instrument incorporating electroactive polymer anti-backup mechanism |
US7487899B2 (en) * | 2004-07-28 | 2009-02-10 | Ethicon Endo-Surgery, Inc. | Surgical instrument incorporating EAP complete firing system lockout mechanism |
US8057508B2 (en) | 2004-07-28 | 2011-11-15 | Ethicon Endo-Surgery, Inc. | Surgical instrument incorporating an electrically actuated articulation locking mechanism |
US7914551B2 (en) | 2004-07-28 | 2011-03-29 | Ethicon Endo-Surgery, Inc. | Electroactive polymer-based articulation mechanism for multi-fire surgical fastening instrument |
US8905977B2 (en) | 2004-07-28 | 2014-12-09 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument having an electroactive polymer actuated medical substance dispenser |
US7195631B2 (en) | 2004-09-09 | 2007-03-27 | Sherwood Services Ag | Forceps with spring loaded end effector assembly |
US8396548B2 (en) | 2008-11-14 | 2013-03-12 | Vessix Vascular, Inc. | Selective drug delivery in a lumen |
US9713730B2 (en) | 2004-09-10 | 2017-07-25 | Boston Scientific Scimed, Inc. | Apparatus and method for treatment of in-stent restenosis |
US9277955B2 (en) | 2010-04-09 | 2016-03-08 | Vessix Vascular, Inc. | Power generating and control apparatus for the treatment of tissue |
US7540872B2 (en) | 2004-09-21 | 2009-06-02 | Covidien Ag | Articulating bipolar electrosurgical instrument |
US20060079872A1 (en) * | 2004-10-08 | 2006-04-13 | Eggleston Jeffrey L | Devices for detecting heating under a patient return electrode |
US7955332B2 (en) * | 2004-10-08 | 2011-06-07 | Covidien Ag | Mechanism for dividing tissue in a hemostat-style instrument |
US7628786B2 (en) * | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
WO2006063199A2 (en) | 2004-12-09 | 2006-06-15 | The Foundry, Inc. | Aortic valve repair |
US7731712B2 (en) | 2004-12-20 | 2010-06-08 | Cytyc Corporation | Method and system for transcervical tubal occlusion |
US20060161148A1 (en) * | 2005-01-13 | 2006-07-20 | Robert Behnke | Circuit and method for controlling an electrosurgical generator using a full bridge topology |
US7686804B2 (en) | 2005-01-14 | 2010-03-30 | Covidien Ag | Vessel sealer and divider with rotating sealer and cutter |
US7909823B2 (en) | 2005-01-14 | 2011-03-22 | Covidien Ag | Open vessel sealing instrument |
US7918795B2 (en) | 2005-02-02 | 2011-04-05 | Gynesonics, Inc. | Method and device for uterine fibroid treatment |
US7784663B2 (en) * | 2005-03-17 | 2010-08-31 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument having load sensing control circuitry |
US7491202B2 (en) * | 2005-03-31 | 2009-02-17 | Covidien Ag | Electrosurgical forceps with slow closure sealing plates and method of sealing tissue |
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 |
US7674260B2 (en) | 2005-04-28 | 2010-03-09 | Cytyc Corporation | Emergency hemostasis device utilizing energy |
WO2007014063A2 (en) * | 2005-07-21 | 2007-02-01 | Vnus Medical Technologies, Inc. | Systems and methods for treating a hollow anatomical structure |
US7846161B2 (en) | 2005-09-30 | 2010-12-07 | Covidien Ag | Insulating boot for electrosurgical forceps |
US7879035B2 (en) | 2005-09-30 | 2011-02-01 | Covidien Ag | Insulating boot for electrosurgical forceps |
US7789878B2 (en) * | 2005-09-30 | 2010-09-07 | Covidien Ag | In-line vessel sealer and divider |
US7722607B2 (en) | 2005-09-30 | 2010-05-25 | Covidien Ag | In-line vessel sealer and divider |
US7922953B2 (en) | 2005-09-30 | 2011-04-12 | Covidien Ag | Method for manufacturing an end effector assembly |
CA2561034C (en) | 2005-09-30 | 2014-12-09 | Sherwood Services Ag | Flexible endoscopic catheter with an end effector for coagulating and transfecting tissue |
US8734438B2 (en) | 2005-10-21 | 2014-05-27 | Covidien Ag | Circuit and method for reducing stored energy in an electrosurgical generator |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
DE102005061148A1 (en) * | 2005-12-21 | 2007-06-28 | Robert Bosch Gmbh | Micromechanical structure comprising a substrate and a thermocouple, temperature and / or radiation sensor and method for producing a micromechanical structure |
US7874986B2 (en) * | 2006-04-20 | 2011-01-25 | Gynesonics, Inc. | Methods and devices for visualization and ablation of tissue |
US10058342B2 (en) | 2006-01-12 | 2018-08-28 | Gynesonics, Inc. | Devices and methods for treatment of tissue |
US20070161905A1 (en) * | 2006-01-12 | 2007-07-12 | Gynesonics, Inc. | Intrauterine ultrasound and method for use |
US7815571B2 (en) * | 2006-04-20 | 2010-10-19 | Gynesonics, Inc. | Rigid delivery systems having inclined ultrasound and needle |
US9357977B2 (en) * | 2006-01-12 | 2016-06-07 | Gynesonics, Inc. | Interventional deployment and imaging system |
US11259825B2 (en) | 2006-01-12 | 2022-03-01 | Gynesonics, Inc. | Devices and methods for treatment of tissue |
US7887534B2 (en) * | 2006-01-18 | 2011-02-15 | Stryker Corporation | Electrosurgical system |
CA2574934C (en) | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US8882766B2 (en) | 2006-01-24 | 2014-11-11 | Covidien Ag | Method and system for controlling delivery of energy to divide tissue |
US8298232B2 (en) | 2006-01-24 | 2012-10-30 | Tyco Healthcare Group Lp | Endoscopic vessel sealer and divider for large tissue structures |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US8147485B2 (en) | 2006-01-24 | 2012-04-03 | Covidien Ag | System and method for tissue sealing |
US20070173813A1 (en) * | 2006-01-24 | 2007-07-26 | Sherwood Services Ag | System and method for tissue sealing |
US20070173802A1 (en) * | 2006-01-24 | 2007-07-26 | Keppel David S | Method and system for transmitting data across patient isolation barrier |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
CA2574935A1 (en) | 2006-01-24 | 2007-07-24 | Sherwood Services Ag | A method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
US8241282B2 (en) * | 2006-01-24 | 2012-08-14 | Tyco Healthcare Group Lp | Vessel sealing cutting assemblies |
US8734443B2 (en) | 2006-01-24 | 2014-05-27 | Covidien Lp | Vessel sealer and divider for large tissue structures |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
CA2575392C (en) | 2006-01-24 | 2015-07-07 | Sherwood Services Ag | System and method for tissue sealing |
US7651493B2 (en) * | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US7648499B2 (en) * | 2006-03-21 | 2010-01-19 | Covidien Ag | System and method for generating radio frequency energy |
US20100056926A1 (en) * | 2008-08-26 | 2010-03-04 | Gynesonics, Inc. | Ablation device with articulated imaging transducer |
US8206300B2 (en) | 2008-08-26 | 2012-06-26 | Gynesonics, Inc. | Ablation device with articulated imaging transducer |
US10595819B2 (en) | 2006-04-20 | 2020-03-24 | Gynesonics, Inc. | Ablation device with articulated imaging transducer |
US7651492B2 (en) * | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US8019435B2 (en) | 2006-05-02 | 2011-09-13 | Boston Scientific Scimed, Inc. | Control of arterial smooth muscle tone |
US20070260238A1 (en) * | 2006-05-05 | 2007-11-08 | Sherwood Services Ag | Combined energy level button |
US8753334B2 (en) * | 2006-05-10 | 2014-06-17 | Covidien Ag | System and method for reducing leakage current in an electrosurgical generator |
US20070282320A1 (en) * | 2006-05-30 | 2007-12-06 | Sherwood Services Ag | System and method for controlling tissue heating rate prior to cellular vaporization |
EP2092957B2 (en) | 2006-06-28 | 2019-11-20 | Medtronic Ardian Luxembourg S.à.r.l. | Systems for thermally-induced renal neuromodulation |
US7776037B2 (en) * | 2006-07-07 | 2010-08-17 | Covidien Ag | System and method for controlling electrode gap during tissue sealing |
US8034049B2 (en) | 2006-08-08 | 2011-10-11 | Covidien Ag | System and method for measuring initial tissue impedance |
US7731717B2 (en) | 2006-08-08 | 2010-06-08 | Covidien Ag | System and method for controlling RF output during tissue sealing |
US8597297B2 (en) * | 2006-08-29 | 2013-12-03 | Covidien Ag | Vessel sealing instrument with multiple electrode configurations |
US8486060B2 (en) * | 2006-09-18 | 2013-07-16 | Cytyc Corporation | Power ramping during RF ablation |
US20080071269A1 (en) * | 2006-09-18 | 2008-03-20 | Cytyc Corporation | Curved Endoscopic Medical Device |
US7637907B2 (en) * | 2006-09-19 | 2009-12-29 | Covidien Ag | System and method for return electrode monitoring |
US7794457B2 (en) * | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US8070746B2 (en) | 2006-10-03 | 2011-12-06 | Tyco Healthcare Group Lp | Radiofrequency fusion of cardiac tissue |
EP2455034B1 (en) | 2006-10-18 | 2017-07-19 | Vessix Vascular, Inc. | System for inducing desirable temperature effects on body tissue |
JP5479901B2 (en) | 2006-10-18 | 2014-04-23 | べシックス・バスキュラー・インコーポレイテッド | Induction of desired temperature effects on body tissue |
CA2666661C (en) | 2006-10-18 | 2015-01-20 | Minnow Medical, Inc. | Tuned rf energy and electrical tissue characterization for selective treatment of target tissues |
US7846160B2 (en) | 2006-12-21 | 2010-12-07 | Cytyc Corporation | Method and apparatus for sterilization |
USD649249S1 (en) | 2007-02-15 | 2011-11-22 | Tyco Healthcare Group Lp | End effectors of an elongated dissecting and dividing instrument |
US20080249523A1 (en) * | 2007-04-03 | 2008-10-09 | Tyco Healthcare Group Lp | Controller for flexible tissue ablation procedures |
US8267935B2 (en) * | 2007-04-04 | 2012-09-18 | Tyco Healthcare Group Lp | Electrosurgical instrument reducing current densities at an insulator conductor junction |
US8777941B2 (en) * | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
US8216217B2 (en) | 2007-08-23 | 2012-07-10 | Aegea Medical, Inc. | Uterine therapy device and method |
CN101686834A (en) * | 2007-07-13 | 2010-03-31 | 波士顿科学医学有限公司 | Hybrid and portable power supplies for electrolytically detaching implantable medical devices |
US7834484B2 (en) | 2007-07-16 | 2010-11-16 | Tyco Healthcare Group Lp | Connection cable and method for activating a voltage-controlled generator |
US8216220B2 (en) | 2007-09-07 | 2012-07-10 | Tyco Healthcare Group Lp | System and method for transmission of combined data stream |
US7877853B2 (en) | 2007-09-20 | 2011-02-01 | Tyco Healthcare Group Lp | Method of manufacturing end effector assembly for sealing tissue |
US7877852B2 (en) | 2007-09-20 | 2011-02-01 | Tyco Healthcare Group Lp | Method of manufacturing an end effector assembly for sealing tissue |
US20090082766A1 (en) * | 2007-09-20 | 2009-03-26 | Tyco Healthcare Group Lp | Tissue Sealer and End Effector Assembly and Method of Manufacturing Same |
US8512332B2 (en) | 2007-09-21 | 2013-08-20 | Covidien Lp | Real-time arc control in electrosurgical generators |
US8267936B2 (en) * | 2007-09-28 | 2012-09-18 | Tyco Healthcare Group Lp | Insulating mechanically-interfaced adhesive for electrosurgical forceps |
US8235992B2 (en) * | 2007-09-28 | 2012-08-07 | Tyco Healthcare Group Lp | Insulating boot with mechanical reinforcement for electrosurgical forceps |
US8221416B2 (en) * | 2007-09-28 | 2012-07-17 | Tyco Healthcare Group Lp | Insulating boot for electrosurgical forceps with thermoplastic clevis |
US8235993B2 (en) * | 2007-09-28 | 2012-08-07 | Tyco Healthcare Group Lp | Insulating boot for electrosurgical forceps with exohinged structure |
US20090088748A1 (en) * | 2007-09-28 | 2009-04-02 | Tyco Healthcare Group Lp | Insulating Mesh-like Boot for Electrosurgical Forceps |
US8236025B2 (en) * | 2007-09-28 | 2012-08-07 | Tyco Healthcare Group Lp | Silicone insulated electrosurgical forceps |
US8241283B2 (en) | 2007-09-28 | 2012-08-14 | Tyco Healthcare Group Lp | Dual durometer insulating boot for electrosurgical forceps |
US20090088750A1 (en) * | 2007-09-28 | 2009-04-02 | Tyco Healthcare Group Lp | Insulating Boot with Silicone Overmold for Electrosurgical Forceps |
US9023043B2 (en) * | 2007-09-28 | 2015-05-05 | Covidien Lp | Insulating mechanically-interfaced boot and jaws for electrosurgical forceps |
US8251996B2 (en) * | 2007-09-28 | 2012-08-28 | Tyco Healthcare Group Lp | Insulating sheath for electrosurgical forceps |
US20090088745A1 (en) * | 2007-09-28 | 2009-04-02 | Tyco Healthcare Group Lp | Tapered Insulating Boot for Electrosurgical Forceps |
US8088072B2 (en) | 2007-10-12 | 2012-01-03 | Gynesonics, Inc. | Methods and systems for controlled deployment of needles in tissue |
US8280525B2 (en) | 2007-11-16 | 2012-10-02 | Vivant Medical, Inc. | Dynamically matched microwave antenna for tissue ablation |
WO2009086448A1 (en) * | 2007-12-28 | 2009-07-09 | Salient Surgical Technologies, Inc. | Fluid-assisted electrosurgical devices, methods and systems |
US8192444B2 (en) | 2008-01-16 | 2012-06-05 | Tyco Healthcare Group Lp | Uterine sealer |
US8682425B2 (en) * | 2008-01-30 | 2014-03-25 | Miridia Technology Inc. | Electroacupuncture system |
US8764748B2 (en) * | 2008-02-06 | 2014-07-01 | Covidien Lp | End effector assembly for electrosurgical device and method for making the same |
US8623276B2 (en) * | 2008-02-15 | 2014-01-07 | Covidien Lp | Method and system for sterilizing an electrosurgical instrument |
US20090287081A1 (en) * | 2008-04-29 | 2009-11-19 | Gynesonics , Inc | Submucosal fibroid ablation for the treatment of menorrhagia |
US8226639B2 (en) * | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
WO2010008834A2 (en) * | 2008-06-23 | 2010-01-21 | Angiodynamics, Inc. | Treatment devices and methods |
US8469956B2 (en) * | 2008-07-21 | 2013-06-25 | Covidien Lp | Variable resistor jaw |
US8162973B2 (en) * | 2008-08-15 | 2012-04-24 | Tyco Healthcare Group Lp | Method of transferring pressure in an articulating surgical instrument |
US20100042143A1 (en) * | 2008-08-15 | 2010-02-18 | Cunningham James S | Method of Transferring Pressure in an Articulating Surgical Instrument |
US8257387B2 (en) * | 2008-08-15 | 2012-09-04 | Tyco Healthcare Group Lp | Method of transferring pressure in an articulating surgical instrument |
US9603652B2 (en) * | 2008-08-21 | 2017-03-28 | Covidien Lp | Electrosurgical instrument including a sensor |
US8784417B2 (en) * | 2008-08-28 | 2014-07-22 | Covidien Lp | Tissue fusion jaw angle improvement |
US8795274B2 (en) * | 2008-08-28 | 2014-08-05 | Covidien Lp | Tissue fusion jaw angle improvement |
US8317787B2 (en) * | 2008-08-28 | 2012-11-27 | Covidien Lp | Tissue fusion jaw angle improvement |
US20100057081A1 (en) * | 2008-08-28 | 2010-03-04 | Tyco Healthcare Group Lp | Tissue Fusion Jaw Angle Improvement |
US20100063500A1 (en) * | 2008-09-05 | 2010-03-11 | Tyco Healthcare Group Lp | Apparatus, System and Method for Performing an Electrosurgical Procedure |
CN102149346B (en) * | 2008-09-08 | 2013-12-04 | 爱尔博电子医疗仪器股份有限公司 | Soft generator |
US8303582B2 (en) * | 2008-09-15 | 2012-11-06 | Tyco Healthcare Group Lp | Electrosurgical instrument having a coated electrode utilizing an atomic layer deposition technique |
US20100069953A1 (en) * | 2008-09-16 | 2010-03-18 | Tyco Healthcare Group Lp | Method of Transferring Force Using Flexible Fluid-Filled Tubing in an Articulating Surgical Instrument |
US20100069903A1 (en) * | 2008-09-18 | 2010-03-18 | Tyco Healthcare Group Lp | Vessel Sealing Instrument With Cutting Mechanism |
US20100076430A1 (en) * | 2008-09-24 | 2010-03-25 | Tyco Healthcare Group Lp | Electrosurgical Instrument Having a Thumb Lever and Related System and Method of Use |
US8535312B2 (en) * | 2008-09-25 | 2013-09-17 | Covidien Lp | Apparatus, system and method for performing an electrosurgical procedure |
US8968314B2 (en) * | 2008-09-25 | 2015-03-03 | Covidien Lp | Apparatus, system and method for performing an electrosurgical procedure |
US9375254B2 (en) * | 2008-09-25 | 2016-06-28 | Covidien Lp | Seal and separate algorithm |
US8142473B2 (en) * | 2008-10-03 | 2012-03-27 | Tyco Healthcare Group Lp | Method of transferring rotational motion in an articulating surgical instrument |
US8469957B2 (en) * | 2008-10-07 | 2013-06-25 | Covidien Lp | Apparatus, system, and method for performing an electrosurgical procedure |
US8636761B2 (en) | 2008-10-09 | 2014-01-28 | Covidien Lp | Apparatus, system, and method for performing an endoscopic electrosurgical procedure |
US8016827B2 (en) * | 2008-10-09 | 2011-09-13 | Tyco Healthcare Group Lp | Apparatus, system, and method for performing an electrosurgical procedure |
US20100094075A1 (en) * | 2008-10-10 | 2010-04-15 | Hologic Inc. | Expandable medical devices with reinforced elastomeric members and methods employing the same |
US8486107B2 (en) * | 2008-10-20 | 2013-07-16 | Covidien Lp | Method of sealing tissue using radiofrequency energy |
US8500732B2 (en) * | 2008-10-21 | 2013-08-06 | Hermes Innovations Llc | Endometrial ablation devices and systems |
US8382753B2 (en) | 2008-10-21 | 2013-02-26 | Hermes Innovations, LLC | Tissue ablation methods |
US8821486B2 (en) | 2009-11-13 | 2014-09-02 | Hermes Innovations, LLC | Tissue ablation systems and methods |
US8197476B2 (en) | 2008-10-21 | 2012-06-12 | Hermes Innovations Llc | Tissue ablation systems |
US9662163B2 (en) | 2008-10-21 | 2017-05-30 | Hermes Innovations Llc | Endometrial ablation devices and systems |
US8197477B2 (en) | 2008-10-21 | 2012-06-12 | Hermes Innovations Llc | Tissue ablation methods |
US8540708B2 (en) | 2008-10-21 | 2013-09-24 | Hermes Innovations Llc | Endometrial ablation method |
CN102271603A (en) | 2008-11-17 | 2011-12-07 | 明诺医学股份有限公司 | Selective accumulation of energy with or without knowledge of tissue topography |
US8197479B2 (en) * | 2008-12-10 | 2012-06-12 | Tyco Healthcare Group Lp | Vessel sealer and divider |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
US8114122B2 (en) | 2009-01-13 | 2012-02-14 | Tyco Healthcare Group Lp | Apparatus, system, and method for performing an electrosurgical procedure |
US9254168B2 (en) * | 2009-02-02 | 2016-02-09 | Medtronic Advanced Energy Llc | Electro-thermotherapy of tissue using penetrating microelectrode array |
JP5592409B2 (en) * | 2009-02-23 | 2014-09-17 | サリエント・サージカル・テクノロジーズ・インコーポレーテッド | Fluid-assisted electrosurgical device and method of use thereof |
US8262574B2 (en) | 2009-02-27 | 2012-09-11 | Gynesonics, Inc. | Needle and tine deployment mechanism |
US9326819B2 (en) * | 2009-04-15 | 2016-05-03 | Medwaves, Inc. | Electrically tunable tissue ablation system and method |
US8187273B2 (en) | 2009-05-07 | 2012-05-29 | Tyco Healthcare Group Lp | Apparatus, system, and method for performing an electrosurgical procedure |
US8246618B2 (en) | 2009-07-08 | 2012-08-21 | Tyco Healthcare Group Lp | Electrosurgical jaws with offset knife |
US7956620B2 (en) * | 2009-08-12 | 2011-06-07 | Tyco Healthcare Group Lp | System and method for augmented impedance sensing |
JP2013503723A (en) | 2009-09-08 | 2013-02-04 | サリエント・サージカル・テクノロジーズ・インコーポレーテッド | Cartridge assembly for electrosurgical devices, electrosurgical units, and methods of use thereof |
US8133254B2 (en) | 2009-09-18 | 2012-03-13 | Tyco Healthcare Group Lp | In vivo attachable and detachable end effector assembly and laparoscopic surgical instrument and methods therefor |
US8685015B2 (en) * | 2009-09-24 | 2014-04-01 | Covidien Lp | System and method for multi-pole phase-shifted radio frequency application |
US8112871B2 (en) * | 2009-09-28 | 2012-02-14 | Tyco Healthcare Group Lp | Method for manufacturing electrosurgical seal plates |
US8266783B2 (en) | 2009-09-28 | 2012-09-18 | Tyco Healthcare Group Lp | Method and system for manufacturing electrosurgical seal plates |
US9636251B2 (en) * | 2009-10-09 | 2017-05-02 | Bayer Healthcare Llc | Method and apparatus for endometrial ablation in combination with intrafallopian contraceptive devices |
US9168054B2 (en) * | 2009-10-09 | 2015-10-27 | Ethicon Endo-Surgery, Inc. | Surgical generator for ultrasonic and electrosurgical devices |
US10660697B2 (en) | 2009-11-10 | 2020-05-26 | Cardea Medsystems (Tianjin) Co., Ltd. | Hollow body cavity ablation apparatus |
WO2011059487A2 (en) * | 2009-11-10 | 2011-05-19 | Cardea MedSystems, Inc. | Hollow body cavity ablation apparatus |
US8715278B2 (en) * | 2009-11-11 | 2014-05-06 | Minerva Surgical, Inc. | System for endometrial ablation utilizing radio frequency |
US8529562B2 (en) | 2009-11-13 | 2013-09-10 | Minerva Surgical, Inc | Systems and methods for endometrial ablation |
US11896282B2 (en) | 2009-11-13 | 2024-02-13 | Hermes Innovations Llc | Tissue ablation systems and method |
US9289257B2 (en) | 2009-11-13 | 2016-03-22 | Minerva Surgical, Inc. | Methods and systems for endometrial ablation utilizing radio frequency |
US8882759B2 (en) | 2009-12-18 | 2014-11-11 | Covidien Lp | Microwave ablation system with dielectric temperature probe |
US8879995B2 (en) * | 2009-12-23 | 2014-11-04 | Viconics Electronics Inc. | Wireless power transmission using phased array antennae |
US8568404B2 (en) | 2010-02-19 | 2013-10-29 | Covidien Lp | Bipolar electrode probe for ablation monitoring |
WO2011112991A1 (en) | 2010-03-11 | 2011-09-15 | Salient Surgical Technologies, Inc. | Bipolar electrosurgical cutter with position insensitive return electrode contact |
US9192790B2 (en) | 2010-04-14 | 2015-11-24 | Boston Scientific Scimed, Inc. | Focused ultrasonic renal denervation |
US20110295249A1 (en) * | 2010-05-28 | 2011-12-01 | Salient Surgical Technologies, Inc. | Fluid-Assisted Electrosurgical Devices, and Methods of Manufacture Thereof |
US8473067B2 (en) | 2010-06-11 | 2013-06-25 | Boston Scientific Scimed, Inc. | Renal denervation and stimulation employing wireless vascular energy transfer arrangement |
US9138289B2 (en) | 2010-06-28 | 2015-09-22 | Medtronic Advanced Energy Llc | Electrode sheath for electrosurgical device |
US8906012B2 (en) | 2010-06-30 | 2014-12-09 | Medtronic Advanced Energy Llc | Electrosurgical devices with wire electrode |
US8920417B2 (en) | 2010-06-30 | 2014-12-30 | Medtronic Advanced Energy Llc | Electrosurgical devices and methods of use thereof |
US8956348B2 (en) | 2010-07-21 | 2015-02-17 | Minerva Surgical, Inc. | Methods and systems for endometrial ablation |
US9155589B2 (en) | 2010-07-30 | 2015-10-13 | Boston Scientific Scimed, Inc. | Sequential activation RF electrode set for renal nerve ablation |
US9084609B2 (en) | 2010-07-30 | 2015-07-21 | Boston Scientific Scime, Inc. | Spiral balloon catheter for renal nerve ablation |
US9463062B2 (en) | 2010-07-30 | 2016-10-11 | Boston Scientific Scimed, Inc. | Cooled conductive balloon RF catheter for renal nerve ablation |
US9358365B2 (en) | 2010-07-30 | 2016-06-07 | Boston Scientific Scimed, Inc. | Precision electrode movement control for renal nerve ablation |
US9408661B2 (en) | 2010-07-30 | 2016-08-09 | Patrick A. Haverkost | RF electrodes on multiple flexible wires for renal nerve ablation |
EP3449856B1 (en) | 2010-10-25 | 2023-06-28 | Medtronic Ardian Luxembourg S.à.r.l. | Device for evaluation and feedback of neuromodulation treatment |
US8974451B2 (en) | 2010-10-25 | 2015-03-10 | Boston Scientific Scimed, Inc. | Renal nerve ablation using conductive fluid jet and RF energy |
US9023040B2 (en) | 2010-10-26 | 2015-05-05 | Medtronic Advanced Energy Llc | Electrosurgical cutting devices |
US9220558B2 (en) | 2010-10-27 | 2015-12-29 | Boston Scientific Scimed, Inc. | RF renal denervation catheter with multiple independent electrodes |
US9510897B2 (en) | 2010-11-05 | 2016-12-06 | Hermes Innovations Llc | RF-electrode surface and method of fabrication |
US9144453B2 (en) * | 2010-11-08 | 2015-09-29 | Bovie Medical Corporation | Multi-mode electrosurgical apparatus |
US9060765B2 (en) | 2010-11-08 | 2015-06-23 | Bovie Medical Corporation | Electrosurgical apparatus with retractable blade |
WO2012064864A1 (en) | 2010-11-09 | 2012-05-18 | Aegea Medical Inc. | Positioning method and apparatus for delivering vapor to the uterus |
US9028485B2 (en) | 2010-11-15 | 2015-05-12 | Boston Scientific Scimed, Inc. | Self-expanding cooling electrode for renal nerve ablation |
US9089350B2 (en) | 2010-11-16 | 2015-07-28 | Boston Scientific Scimed, Inc. | Renal denervation catheter with RF electrode and integral contrast dye injection arrangement |
US9668811B2 (en) | 2010-11-16 | 2017-06-06 | Boston Scientific Scimed, Inc. | Minimally invasive access for renal nerve ablation |
US9326751B2 (en) | 2010-11-17 | 2016-05-03 | Boston Scientific Scimed, Inc. | Catheter guidance of external energy for renal denervation |
US9060761B2 (en) | 2010-11-18 | 2015-06-23 | Boston Scientific Scime, Inc. | Catheter-focused magnetic field induced renal nerve ablation |
US9023034B2 (en) | 2010-11-22 | 2015-05-05 | Boston Scientific Scimed, Inc. | Renal ablation electrode with force-activatable conduction apparatus |
US9192435B2 (en) | 2010-11-22 | 2015-11-24 | Boston Scientific Scimed, Inc. | Renal denervation catheter with cooled RF electrode |
US20120157993A1 (en) | 2010-12-15 | 2012-06-21 | Jenson Mark L | Bipolar Off-Wall Electrode Device for Renal Nerve Ablation |
US9113940B2 (en) | 2011-01-14 | 2015-08-25 | Covidien Lp | Trigger lockout and kickback mechanism for surgical instruments |
US9220561B2 (en) | 2011-01-19 | 2015-12-29 | Boston Scientific Scimed, Inc. | Guide-compatible large-electrode catheter for renal nerve ablation with reduced arterial injury |
US9427281B2 (en) | 2011-03-11 | 2016-08-30 | Medtronic Advanced Energy Llc | Bronchoscope-compatible catheter provided with electrosurgical device |
US8968293B2 (en) | 2011-04-12 | 2015-03-03 | Covidien Lp | Systems and methods for calibrating power measurements in an electrosurgical generator |
AU2012283908B2 (en) | 2011-07-20 | 2017-02-16 | Boston Scientific Scimed, Inc. | Percutaneous devices and methods to visualize, target and ablate nerves |
WO2013016203A1 (en) | 2011-07-22 | 2013-01-31 | Boston Scientific Scimed, Inc. | Nerve modulation system with a nerve modulation element positionable in a helical guide |
US9750565B2 (en) | 2011-09-30 | 2017-09-05 | Medtronic Advanced Energy Llc | Electrosurgical balloons |
US9662060B2 (en) | 2011-10-07 | 2017-05-30 | Aegea Medical Inc. | Integrity testing method and apparatus for delivering vapor to the uterus |
EP2765942B1 (en) | 2011-10-10 | 2016-02-24 | Boston Scientific Scimed, Inc. | Medical devices including ablation electrodes |
US9420955B2 (en) | 2011-10-11 | 2016-08-23 | Boston Scientific Scimed, Inc. | Intravascular temperature monitoring system and method |
US10085799B2 (en) | 2011-10-11 | 2018-10-02 | Boston Scientific Scimed, Inc. | Off-wall electrode device and methods for nerve modulation |
US9364284B2 (en) | 2011-10-12 | 2016-06-14 | Boston Scientific Scimed, Inc. | Method of making an off-wall spacer cage |
EP2768563B1 (en) | 2011-10-18 | 2016-11-09 | Boston Scientific Scimed, Inc. | Deflectable medical devices |
US9079000B2 (en) | 2011-10-18 | 2015-07-14 | Boston Scientific Scimed, Inc. | Integrated crossing balloon catheter |
US8870864B2 (en) | 2011-10-28 | 2014-10-28 | Medtronic Advanced Energy Llc | Single instrument electrosurgery apparatus and its method of use |
EP2775948B1 (en) | 2011-11-08 | 2018-04-04 | Boston Scientific Scimed, Inc. | Ostial renal nerve ablation |
EP2779929A1 (en) | 2011-11-15 | 2014-09-24 | Boston Scientific Scimed, Inc. | Device and methods for renal nerve modulation monitoring |
US9119632B2 (en) | 2011-11-21 | 2015-09-01 | Boston Scientific Scimed, Inc. | Deflectable renal nerve ablation catheter |
US9265969B2 (en) | 2011-12-21 | 2016-02-23 | Cardiac Pacemakers, Inc. | Methods for modulating cell function |
WO2013096913A2 (en) | 2011-12-23 | 2013-06-27 | Vessix Vascular, Inc. | Methods and apparatuses for remodeling tissue of or adjacent to a body passage |
WO2013101452A1 (en) | 2011-12-28 | 2013-07-04 | Boston Scientific Scimed, Inc. | Device and methods for nerve modulation using a novel ablation catheter with polymeric ablative elements |
US9050106B2 (en) | 2011-12-29 | 2015-06-09 | Boston Scientific Scimed, Inc. | Off-wall electrode device and methods for nerve modulation |
USD680220S1 (en) | 2012-01-12 | 2013-04-16 | Coviden IP | Slider handle for laparoscopic device |
US10064651B2 (en) | 2012-03-15 | 2018-09-04 | Inpress Technologies, Inc. | Uterine hemorrhage controlling system and method |
US9375250B2 (en) | 2012-04-09 | 2016-06-28 | Covidien Lp | Method for employing single fault safe redundant signals |
US10660703B2 (en) | 2012-05-08 | 2020-05-26 | Boston Scientific Scimed, Inc. | Renal nerve modulation devices |
GB2502981B (en) * | 2012-06-12 | 2018-11-07 | Gyrus Medical Ltd | Electrosurgical instrument & system |
US10321946B2 (en) | 2012-08-24 | 2019-06-18 | Boston Scientific Scimed, Inc. | Renal nerve modulation devices with weeping RF ablation balloons |
EP2895095A2 (en) | 2012-09-17 | 2015-07-22 | Boston Scientific Scimed, Inc. | Self-positioning electrode system and method for renal nerve modulation |
US10549127B2 (en) | 2012-09-21 | 2020-02-04 | Boston Scientific Scimed, Inc. | Self-cooling ultrasound ablation catheter |
US10398464B2 (en) | 2012-09-21 | 2019-09-03 | Boston Scientific Scimed, Inc. | System for nerve modulation and innocuous thermal gradient nerve block |
JP6074051B2 (en) | 2012-10-10 | 2017-02-01 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Intravascular neuromodulation system and medical device |
US9364277B2 (en) | 2012-12-13 | 2016-06-14 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9204921B2 (en) | 2012-12-13 | 2015-12-08 | Cook Medical Technologies Llc | RF energy controller and method for electrosurgical medical devices |
US9956033B2 (en) | 2013-03-11 | 2018-05-01 | Boston Scientific Scimed, Inc. | Medical devices for modulating nerves |
WO2014143571A1 (en) | 2013-03-11 | 2014-09-18 | Boston Scientific Scimed, Inc. | Medical devices for modulating nerves |
US9808311B2 (en) | 2013-03-13 | 2017-11-07 | Boston Scientific Scimed, Inc. | Deflectable medical devices |
JP6220044B2 (en) | 2013-03-15 | 2017-10-25 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Medical device for renal nerve ablation |
CN105228546B (en) | 2013-03-15 | 2017-11-14 | 波士顿科学国际有限公司 | Utilize the impedance-compensated medicine equipment and method that are used to treat hypertension |
US10265122B2 (en) | 2013-03-15 | 2019-04-23 | Boston Scientific Scimed, Inc. | Nerve ablation devices and related methods of use |
US9901394B2 (en) | 2013-04-04 | 2018-02-27 | Hermes Innovations Llc | Medical ablation system and method of making |
JP2016524949A (en) | 2013-06-21 | 2016-08-22 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Medical device for renal nerve ablation having a rotatable shaft |
US9943365B2 (en) | 2013-06-21 | 2018-04-17 | Boston Scientific Scimed, Inc. | Renal denervation balloon catheter with ride along electrode support |
US9707036B2 (en) | 2013-06-25 | 2017-07-18 | Boston Scientific Scimed, Inc. | Devices and methods for nerve modulation using localized indifferent electrodes |
WO2015002787A1 (en) | 2013-07-01 | 2015-01-08 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation |
EP3019106A1 (en) | 2013-07-11 | 2016-05-18 | Boston Scientific Scimed, Inc. | Medical device with stretchable electrode assemblies |
US10660698B2 (en) | 2013-07-11 | 2020-05-26 | Boston Scientific Scimed, Inc. | Devices and methods for nerve modulation |
EP3049007B1 (en) | 2013-07-19 | 2019-06-12 | Boston Scientific Scimed, Inc. | Spiral bipolar electrode renal denervation balloon |
US10695124B2 (en) | 2013-07-22 | 2020-06-30 | Boston Scientific Scimed, Inc. | Renal nerve ablation catheter having twist balloon |
WO2015013205A1 (en) | 2013-07-22 | 2015-01-29 | Boston Scientific Scimed, Inc. | Medical devices for renal nerve ablation |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
US10646267B2 (en) | 2013-08-07 | 2020-05-12 | Covidien LLP | Surgical forceps |
JP6159888B2 (en) | 2013-08-22 | 2017-07-05 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Flexible circuit with improved adhesion to renal neuromodulation balloon |
US9895194B2 (en) | 2013-09-04 | 2018-02-20 | Boston Scientific Scimed, Inc. | Radio frequency (RF) balloon catheter having flushing and cooling capability |
CN105530885B (en) | 2013-09-13 | 2020-09-22 | 波士顿科学国际有限公司 | Ablation balloon with vapor deposited covering |
US10631914B2 (en) | 2013-09-30 | 2020-04-28 | Covidien Lp | Bipolar electrosurgical instrument with movable electrode and related systems and methods |
WO2015054684A1 (en) * | 2013-10-11 | 2015-04-16 | The Trustees Of Columbia University In The City Of New York | System, method and computer-accessible medium for characterization of tissue |
WO2015057521A1 (en) | 2013-10-14 | 2015-04-23 | Boston Scientific Scimed, Inc. | High resolution cardiac mapping electrode array catheter |
US11246654B2 (en) | 2013-10-14 | 2022-02-15 | Boston Scientific Scimed, Inc. | Flexible renal nerve ablation devices and related methods of use and manufacture |
EP3057520A1 (en) | 2013-10-15 | 2016-08-24 | Boston Scientific Scimed, Inc. | Medical device balloon |
US9770606B2 (en) | 2013-10-15 | 2017-09-26 | Boston Scientific Scimed, Inc. | Ultrasound ablation catheter with cooling infusion and centering basket |
US9649125B2 (en) | 2013-10-15 | 2017-05-16 | Hermes Innovations Llc | Laparoscopic device |
JP6259099B2 (en) | 2013-10-18 | 2018-01-10 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Balloon catheter comprising a conductive wire with flexibility, and related uses and manufacturing methods |
US10433902B2 (en) * | 2013-10-23 | 2019-10-08 | Medtronic Ardian Luxembourg S.A.R.L. | Current control methods and systems |
CN105658163B (en) | 2013-10-25 | 2020-08-18 | 波士顿科学国际有限公司 | Embedded thermocouple in denervation flexible circuit |
ES2875967T3 (en) * | 2013-12-18 | 2021-11-11 | Novoxel Ltd | Devices for tissue vaporization |
US10004553B2 (en) | 2013-12-23 | 2018-06-26 | Hologic, Inc. | Power modulated endometrial lining tissue ablation |
WO2015103617A1 (en) | 2014-01-06 | 2015-07-09 | Boston Scientific Scimed, Inc. | Tear resistant flex circuit assembly |
US11000679B2 (en) | 2014-02-04 | 2021-05-11 | Boston Scientific Scimed, Inc. | Balloon protection and rewrapping devices and related methods of use |
EP3102136B1 (en) | 2014-02-04 | 2018-06-27 | Boston Scientific Scimed, Inc. | Alternative placement of thermal sensors on bipolar electrode |
US9579149B2 (en) | 2014-03-13 | 2017-02-28 | Medtronic Ardian Luxembourg S.A.R.L. | Low profile catheter assemblies and associated systems and methods |
US10610292B2 (en) | 2014-04-25 | 2020-04-07 | Medtronic Ardian Luxembourg S.A.R.L. | Devices, systems, and methods for monitoring and/or controlling deployment of a neuromodulation element within a body lumen and related technology |
US10179019B2 (en) | 2014-05-22 | 2019-01-15 | Aegea Medical Inc. | Integrity testing method and apparatus for delivering vapor to the uterus |
US9974599B2 (en) | 2014-08-15 | 2018-05-22 | Medtronic Ps Medical, Inc. | Multipurpose electrosurgical device |
US10231777B2 (en) | 2014-08-26 | 2019-03-19 | Covidien Lp | Methods of manufacturing jaw members of an end-effector assembly for a surgical instrument |
EP3203922B1 (en) | 2014-10-07 | 2018-04-18 | Hologic, Inc. | Endometrial lining tissue treatment device |
US9956029B2 (en) | 2014-10-31 | 2018-05-01 | Medtronic Advanced Energy Llc | Telescoping device with saline irrigation line |
WO2016070013A1 (en) | 2014-10-31 | 2016-05-06 | Medtronic Advanced Energy Llc | Fingerswitch circuitry to reduce rf leakage current |
EP3220844B1 (en) | 2014-11-19 | 2020-11-11 | EPiX Therapeutics, Inc. | Systems for high-resolution mapping of tissue |
SG11201703943VA (en) | 2014-11-19 | 2017-06-29 | Advanced Cardiac Therapeutics Inc | Ablation devices, systems and methods of using a high-resolution electrode assembly |
JP6673598B2 (en) | 2014-11-19 | 2020-03-25 | エピックス セラピューティクス,インコーポレイテッド | High resolution mapping of tissue with pacing |
US10492856B2 (en) | 2015-01-26 | 2019-12-03 | Hermes Innovations Llc | Surgical fluid management system and method of use |
WO2016123147A1 (en) | 2015-01-28 | 2016-08-04 | Bovie Medical Corporation | Cold plasma electrosurgical apparatus with bent tip applicator |
US9636164B2 (en) | 2015-03-25 | 2017-05-02 | Advanced Cardiac Therapeutics, Inc. | Contact sensing systems and methods |
US10342611B2 (en) | 2015-04-29 | 2019-07-09 | Innoblative Designs, Inc. | Cavitary tissue ablation |
EP3288477A4 (en) | 2015-04-29 | 2018-12-19 | Cirrus Technologies Ltd. | Medical ablation device and method of use |
US11389227B2 (en) | 2015-08-20 | 2022-07-19 | Medtronic Advanced Energy Llc | Electrosurgical device with multivariate control |
US11051875B2 (en) | 2015-08-24 | 2021-07-06 | Medtronic Advanced Energy Llc | Multipurpose electrosurgical device |
WO2017031712A1 (en) | 2015-08-26 | 2017-03-02 | Covidien Lp | Electrosurgical end effector assemblies and electrosurgical forceps configured to reduce thermal spread |
KR101782693B1 (en) * | 2015-09-04 | 2017-09-28 | 한국과학기술원 | Integrated Circuit for Renal Denervation using multi electrode |
US10559893B1 (en) * | 2015-09-10 | 2020-02-11 | Cpg Technologies, Llc | Pulse protection circuits to deter theft |
EP3367945B1 (en) | 2015-10-29 | 2020-02-26 | Innoblative Designs, Inc. | Screen sphere tissue ablation devices |
US10213250B2 (en) | 2015-11-05 | 2019-02-26 | Covidien Lp | Deployment and safety mechanisms for surgical instruments |
US10716612B2 (en) | 2015-12-18 | 2020-07-21 | Medtronic Advanced Energy Llc | Electrosurgical device with multiple monopolar electrode assembly |
US10052149B2 (en) | 2016-01-20 | 2018-08-21 | RELIGN Corporation | Arthroscopic devices and methods |
WO2017136261A1 (en) | 2016-02-02 | 2017-08-10 | Innoblative Designs, Inc. | Cavitary tissue ablation system |
EP3416551B1 (en) | 2016-02-19 | 2022-10-12 | Aegea Medical Inc. | Apparatus for determining the integrity of a bodily cavity |
WO2017151431A1 (en) | 2016-03-01 | 2017-09-08 | Innoblative Designs, Inc. | Resecting and coagulating tissue |
CA3017269A1 (en) | 2016-03-15 | 2017-09-21 | Epix Therapeutics, Inc. | Improved devices, systems and methods for irrigated ablation |
EP3445258A4 (en) | 2016-04-22 | 2019-12-04 | Relign Corporation | Arthroscopic devices and methods |
US20180000534A1 (en) | 2016-07-01 | 2018-01-04 | RELIGN Corporation | Arthroscopic devices and methods |
US11517336B2 (en) | 2016-08-24 | 2022-12-06 | Alydia Health, Inc. | Uterine hemorrhage controlling system and method |
WO2018075389A1 (en) | 2016-10-17 | 2018-04-26 | Innoblative Designs, Inc. | Treatment devices and methods |
JP6875757B2 (en) | 2016-11-08 | 2021-05-26 | イノブレイティブ デザインズ, インコーポレイテッド | Electrosurgical tissue and vascular seal device |
JP7237829B2 (en) | 2016-11-11 | 2023-03-13 | ガイネソニックス, インコーポレイテッド | Dynamic interaction of tissue controlled treatment with tissue and/or treatment data and their comparison |
US11147618B2 (en) | 2017-01-11 | 2021-10-19 | Medtronic Advanced Energy Llc | Electrosurgical unit and system |
EP3573560A4 (en) | 2017-01-27 | 2020-10-21 | Minerva Surgical, Inc. | Systems and methods for evaluating the integrity of a uterine cavity |
US10213151B2 (en) | 2017-01-27 | 2019-02-26 | Minerva Surgical, Inc. | Systems and methods for evaluating the integrity of a uterine cavity |
US11020045B2 (en) | 2017-03-17 | 2021-06-01 | Minerva Surgical, Inc. | Systems and methods for evaluating the integrity of a uterine cavity |
AU2018212000B2 (en) | 2017-01-30 | 2023-06-29 | Apyx Medical Corporation | Electrosurgical apparatus with flexible shaft |
CN110809448B (en) | 2017-04-27 | 2022-11-25 | Epix疗法公司 | Determining properties of contact between catheter tip and tissue |
DE102017109638A1 (en) | 2017-05-04 | 2018-11-08 | Olympus Winter & Ibe Gmbh | Generator for the delivery of high-frequency alternating current to a medical instrument |
US11166759B2 (en) | 2017-05-16 | 2021-11-09 | Covidien Lp | Surgical forceps |
WO2018222562A1 (en) | 2017-05-30 | 2018-12-06 | Bovie Medical Corporation | Electrosurgical apparatus with robotic tip |
CN117503320A (en) | 2017-06-20 | 2024-02-06 | 埃杰亚医疗公司 | Inductive coil assembly and method for uterine ablation |
EP3658053B1 (en) | 2017-07-26 | 2023-09-13 | Innoblative Designs, Inc. | Minimally invasive articulating assembly having ablation capabilities |
WO2020146483A1 (en) | 2019-01-09 | 2020-07-16 | Covidien Lp | Electrosurgical fallopian tube sealing devices with suction and methods of use thereof |
US11554214B2 (en) | 2019-06-26 | 2023-01-17 | Meditrina, Inc. | Fluid management system |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4739759A (en) * | 1985-02-26 | 1988-04-26 | Concept, Inc. | Microprocessor controlled electrosurgical generator |
US5558672A (en) * | 1994-06-24 | 1996-09-24 | Vidacare, Inc. | Thin layer ablation apparatus |
WO1997041785A2 (en) * | 1996-05-03 | 1997-11-13 | Somnus Medical Technologies, Inc. | Apparatus for cosmetically remodeling a body structure |
GB2317566A (en) * | 1996-09-27 | 1998-04-01 | Smiths Industries Plc | Electrosurgery apparatus waveform generator |
WO1998038932A1 (en) * | 1997-03-07 | 1998-09-11 | Advanced Closure Systems, Inc. | Resectoscope electrode assembly with simultaneous cutting and coagulation |
Family Cites Families (42)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4094320A (en) * | 1976-09-09 | 1978-06-13 | Valleylab, Inc. | Electrosurgical safety circuit and method of using same |
EP0097112B1 (en) * | 1982-06-04 | 1987-03-18 | BBC Aktiengesellschaft Brown, Boveri & Cie. | Hf adaptation transformer |
US5385544A (en) | 1992-08-12 | 1995-01-31 | Vidamed, Inc. | BPH ablation method and apparatus |
US4807620A (en) | 1987-05-22 | 1989-02-28 | Advanced Interventional Systems, Inc. | Apparatus for thermal angioplasty |
FR2660543B1 (en) * | 1990-04-06 | 1998-02-13 | Technomed Int Sa | METHOD FOR AUTOMATICALLY MEASURING THE VOLUME OF A TUMOR, IN PARTICULAR A PROSTATE TUMOR, MEASURING DEVICE, METHOD AND APPARATUS COMPRISING THE SAME. |
US5620481A (en) | 1991-07-05 | 1997-04-15 | Desai; Jawahar M. | Device for multi-phase radio-frequency ablation |
US5562703A (en) | 1994-06-14 | 1996-10-08 | Desai; Ashvin H. | Endoscopic surgical instrument |
AU3128593A (en) * | 1991-11-08 | 1993-06-07 | Ep Technologies Inc | Radiofrequency ablation with phase sensitive power detection |
US5498261A (en) | 1991-12-20 | 1996-03-12 | Advanced Cardiovascular Systems, Inc. | Thermal angioplasty system |
GB9204217D0 (en) * | 1992-02-27 | 1992-04-08 | Goble Nigel M | Cauterising apparatus |
US5540681A (en) | 1992-04-10 | 1996-07-30 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of tissue |
US5573533A (en) | 1992-04-10 | 1996-11-12 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5443470A (en) * | 1992-05-01 | 1995-08-22 | Vesta Medical, Inc. | Method and apparatus for endometrial ablation |
US5484400A (en) | 1992-08-12 | 1996-01-16 | Vidamed, Inc. | Dual channel RF delivery system |
US5542916A (en) | 1992-08-12 | 1996-08-06 | Vidamed, Inc. | Dual-channel RF power delivery system |
US5357956A (en) | 1992-11-13 | 1994-10-25 | American Cardiac Ablation Co., Inc. | Apparatus and method for monitoring endocardial signal during ablation |
US5599345A (en) | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment apparatus |
US5575788A (en) | 1994-06-24 | 1996-11-19 | Stuart D. Edwards | Thin layer ablation apparatus |
US5599788A (en) * | 1994-07-01 | 1997-02-04 | Advanced Tissue Sciences | Method for accelerating skin wound healing with H3 protein |
US6197025B1 (en) * | 1994-09-30 | 2001-03-06 | Circon Corporation | Grooved slider electrode for a resectoscope |
JPH08308851A (en) * | 1995-05-16 | 1996-11-26 | Olympus Optical Co Ltd | Electrosurgical device |
US6293942B1 (en) * | 1995-06-23 | 2001-09-25 | Gyrus Medical Limited | Electrosurgical generator method |
GB9526627D0 (en) * | 1995-12-29 | 1996-02-28 | Gyrus Medical Ltd | An electrosurgical instrument and an electrosurgical electrode assembly |
US5658316A (en) | 1995-07-03 | 1997-08-19 | Automatic Defibrillator, Inc. | Portable defibrillator with disposable power pack |
US6475213B1 (en) * | 1996-01-19 | 2002-11-05 | Ep Technologies, Inc. | Method of ablating body tissue |
US5891136A (en) * | 1996-01-19 | 1999-04-06 | Ep Technologies, Inc. | Expandable-collapsible mesh electrode structures |
US5846238A (en) * | 1996-01-19 | 1998-12-08 | Ep Technologies, Inc. | Expandable-collapsible electrode structures with distal end steering or manipulation |
US5769880A (en) * | 1996-04-12 | 1998-06-23 | Novacept | Moisture transport system for contact electrocoagulation |
US5891134A (en) * | 1996-09-24 | 1999-04-06 | Goble; Colin | System and method for applying thermal energy to tissue |
ES2353846T3 (en) * | 1997-04-11 | 2011-03-07 | United States Surgical Corporation | APPLIANCE FOR RF ABLATION AND CONTROLLER OF THE SAME. |
US6490474B1 (en) * | 1997-08-01 | 2002-12-03 | Cardiac Pathways Corporation | System and method for electrode localization using ultrasound |
US5954717A (en) * | 1997-09-25 | 1999-09-21 | Radiotherapeutics Corporation | Method and system for heating solid tissue |
WO1999017672A1 (en) | 1997-10-06 | 1999-04-15 | Somnus Medical Technologies, Inc. | Electro-surgical instrument with a graphical user interface |
DE19757720A1 (en) * | 1997-12-23 | 1999-06-24 | Sulzer Osypka Gmbh | Method for operating a high-frequency ablation device and device for high-frequency tissue ablation |
US6047700A (en) * | 1998-03-30 | 2000-04-11 | Arthrocare Corporation | Systems and methods for electrosurgical removal of calcified deposits |
US6171305B1 (en) * | 1998-05-05 | 2001-01-09 | Cardiac Pacemakers, Inc. | RF ablation apparatus and method having high output impedance drivers |
US5997534A (en) * | 1998-06-08 | 1999-12-07 | Tu; Hosheng | Medical ablation device and methods thereof |
US6112123A (en) | 1998-07-28 | 2000-08-29 | Endonetics, Inc. | Device and method for ablation of tissue |
US6245065B1 (en) * | 1998-09-10 | 2001-06-12 | Scimed Life Systems, Inc. | Systems and methods for controlling power in an electrosurgical probe |
US6123702A (en) * | 1998-09-10 | 2000-09-26 | Scimed Life Systems, Inc. | Systems and methods for controlling power in an electrosurgical probe |
US6451015B1 (en) * | 1998-11-18 | 2002-09-17 | Sherwood Services Ag | Method and system for menu-driven two-dimensional display lesion generator |
US6258085B1 (en) * | 1999-05-11 | 2001-07-10 | Sherwood Services Ag | Electrosurgical return electrode monitor |
-
1999
- 1999-05-06 US US09/306,480 patent/US6508815B1/en not_active Expired - Lifetime
- 1999-05-07 WO PCT/US1999/009904 patent/WO1999058070A2/en active Application Filing
- 1999-05-07 CA CA002331321A patent/CA2331321A1/en not_active Abandoned
- 1999-05-07 AU AU39730/99A patent/AU3973099A/en not_active Abandoned
- 1999-05-07 JP JP2000547924A patent/JP2003526385A/en active Pending
- 1999-05-07 AT AT99922822T patent/ATE425702T1/en not_active IP Right Cessation
- 1999-05-07 CN CN99808369A patent/CN1308510A/en active Pending
- 1999-05-07 EP EP99922822A patent/EP1076516B1/en not_active Expired - Lifetime
-
2000
- 2000-11-07 NO NO20005623A patent/NO20005623L/en not_active Application Discontinuation
-
2001
- 2001-07-24 HK HK01105168.4A patent/HK1034655A1/en not_active IP Right Cessation
-
2002
- 2002-12-23 US US10/328,447 patent/US7074217B2/en not_active Expired - Fee Related
-
2005
- 2005-07-05 US US11/175,128 patent/US7407502B2/en not_active Expired - Fee Related
- 2005-08-24 US US11/211,016 patent/US7717909B2/en not_active Expired - Fee Related
-
2010
- 2010-05-07 US US12/775,752 patent/US20100217256A1/en not_active Abandoned
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4739759A (en) * | 1985-02-26 | 1988-04-26 | Concept, Inc. | Microprocessor controlled electrosurgical generator |
US5558672A (en) * | 1994-06-24 | 1996-09-24 | Vidacare, Inc. | Thin layer ablation apparatus |
WO1997041785A2 (en) * | 1996-05-03 | 1997-11-13 | Somnus Medical Technologies, Inc. | Apparatus for cosmetically remodeling a body structure |
GB2317566A (en) * | 1996-09-27 | 1998-04-01 | Smiths Industries Plc | Electrosurgery apparatus waveform generator |
WO1998038932A1 (en) * | 1997-03-07 | 1998-09-11 | Advanced Closure Systems, Inc. | Resectoscope electrode assembly with simultaneous cutting and coagulation |
Cited By (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8038670B2 (en) | 2000-03-06 | 2011-10-18 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
US7811282B2 (en) | 2000-03-06 | 2010-10-12 | Salient Surgical Technologies, Inc. | Fluid-assisted electrosurgical devices, electrosurgical unit with pump and methods of use thereof |
US8361068B2 (en) | 2000-03-06 | 2013-01-29 | Medtronic Advanced Energy Llc | Fluid-assisted electrosurgical devices, electrosurgical unit with pump and methods of use thereof |
US8048070B2 (en) | 2000-03-06 | 2011-11-01 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
US7815634B2 (en) | 2000-03-06 | 2010-10-19 | Salient Surgical Technologies, Inc. | Fluid delivery system and controller for electrosurgical devices |
US7294126B2 (en) | 2001-01-16 | 2007-11-13 | Cytyc Corporation | Apparatus and method for treating venous reflux |
WO2002056772A3 (en) * | 2001-01-16 | 2002-10-24 | Novacept | Apparatus and method for treating venous reflux |
US7087052B2 (en) | 2001-01-16 | 2006-08-08 | Cytyc Surgical Products | Apparatus and method for treating venous reflux |
WO2002056772A2 (en) * | 2001-01-16 | 2002-07-25 | Novacept | Apparatus and method for treating venous reflux |
US6712815B2 (en) | 2001-01-16 | 2004-03-30 | Novacept, Inc. | Apparatus and method for treating venous reflux |
US7998140B2 (en) | 2002-02-12 | 2011-08-16 | Salient Surgical Technologies, Inc. | Fluid-assisted medical devices, systems and methods |
US7871410B2 (en) | 2002-10-29 | 2011-01-18 | Cathrx Ltd | System for, and method of, heating a biological site in a patient's body |
US10045810B2 (en) | 2009-03-11 | 2018-08-14 | Erbe Elektromedizin Gmbh | High frequency surgical generator comprising an additional transformer |
CN104473691A (en) * | 2014-12-30 | 2015-04-01 | 北京天助畅运医疗技术股份有限公司 | Power control system and power control method for radio frequency treatment equipment |
Also Published As
Publication number | Publication date |
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WO1999058070A3 (en) | 2000-02-17 |
US7717909B2 (en) | 2010-05-18 |
AU3973099A (en) | 1999-11-29 |
ATE425702T1 (en) | 2009-04-15 |
US20050245921A1 (en) | 2005-11-03 |
US20100217256A1 (en) | 2010-08-26 |
CA2331321A1 (en) | 1999-11-18 |
US20060025758A1 (en) | 2006-02-02 |
JP2003526385A (en) | 2003-09-09 |
US20030093070A1 (en) | 2003-05-15 |
EP1076516B1 (en) | 2009-03-18 |
CN1308510A (en) | 2001-08-15 |
US7407502B2 (en) | 2008-08-05 |
US6508815B1 (en) | 2003-01-21 |
NO20005623D0 (en) | 2000-11-07 |
NO20005623L (en) | 2001-01-05 |
HK1034655A1 (en) | 2001-11-02 |
US7074217B2 (en) | 2006-07-11 |
EP1076516A2 (en) | 2001-02-21 |
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