CA2484875C - Method and system for optically detecting blood and controlling a generator during electrosurgery - Google Patents
Method and system for optically detecting blood and controlling a generator during electrosurgery Download PDFInfo
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1402—Probes for open surgery
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
- A61B2017/00057—Light
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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
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00642—Sensing and controlling the application of energy with feedback, i.e. closed loop control
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- A—HUMAN NECESSITIES
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
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- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
- A61B5/0086—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters using infrared radiation
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/02042—Determining blood loss or bleeding, e.g. during a surgical procedure
Abstract
A method and electrosurgical system for optically detecting blood and controlling an electrosurgical generator are provided. An optical blood detection system is used for optically detecting blood and may be included as an integral part of the overall electrosurgical system's circuitry, or may be designed as a separate unit that connects to, and controls, an electrosurgical generator. The optical blood detection system may be embodied through a variety of analog, digital and/or optical circuit components or arrangements, including software running on computational and memory circuitry. The optical blood detection system controls the output mode and energy of the electrosurgical generator in accordance with the amount of blood detected.
Description
METHOD AND SYSTEM FOR OPTICALLY DETECTING
BLOOD AND CONTROLLING A GENERATOR DURING
ELECTROSURGERY
BACKGROUND
1. Technical Field The disclosure relates to electrosurgey combined with optical detection of blood, and more particularly the automatic control of the level of electrosurgical energy to be delivered to tissue in accordance with the amount of blood optically detected.
BLOOD AND CONTROLLING A GENERATOR DURING
ELECTROSURGERY
BACKGROUND
1. Technical Field The disclosure relates to electrosurgey combined with optical detection of blood, and more particularly the automatic control of the level of electrosurgical energy to be delivered to tissue in accordance with the amount of blood optically detected.
2. Description of the Related Art Electrosurgery involves the application of radio frequency energy to achieve a tissue effect. An electrosurgical generator is used in surgical procedures to deliver electrical energy to the tissue of a patient. An electrosurgical generator often includes a radio frequency generator and its controls. When an electrode is connected to the generator, the electrode can be used for cutting or coagulating the tissue of a patient with high frequency electrical energy. During normal operation, alternating electrical current from the generator flows between an active electrode and a return electrode by passing through the tissue and bodily fluids of a patient.
The electrical energy usually has its waveform shaped to enhance its ability to cut or coagulate tissue. Different waveforms correspond to different modes of operation of the generator, and each mode gives the surgeon various operating advantages. Modes may include cut, coagulate, a blend thereof, or desiccate. A
surgeon can eas ily select and change the different modes of operation as the surgical procedure progresses.
In each mode of operation, it is important to regulate the electrosurgical energy delivered to the patient to achieve the desired surgical effect. This can be done, for example, by controlling the output energy from the electrosurgical generator for the type of tissue being treated.
Different types of tissues will be encountered as the surgical procedure progresses and each unique tissue requires more or less energy in terms of voltage, current or power as a function of frequently changing tissue impedance and other factors, such as the level of vascularization, i.e., blood flow within the tissue.
Therefore, the same tissue will present different load impedance as the tissue is desiccated.
Two conventional types of energy regulation are used in commercial electrosurgical generators. The most common type controls the DC power supply of the generator by limiting the amount of power provided from the AC mains to which the generator is connected. A feedback control loop regulates output voltage by comparing a desired voltage or current with the output voltage or current supplied by the power supply. Another type of power regulation in commercial electrosurgical generators controls the gain of the high-frequency or radio frequency amplifier. A
feedback control loop compares the output power supplied from the RF amplifier for adjustment to a desired power level.
U.S. Patent Nos. 3,964,487; 3,980,085; 4,188,927 and 4,092,986 have circuitry to reduce the output current in accordance with increasing load impedance. In those patents, constant voltage output is maintained and the current is decreased with increasing load impedance.
U.S. Patent No. 4,126,137 controls the power amplifier of the electrosurgical unit in accord with a non-linear compensation circuit applied to a feedback signal derived from a comparison of the power level reference signal and the mathematical product of two signals including sensed current and voltage in the unit.
U.S. Patent No. 4,658,819 has an electrosurgical generator which has a microprocessor controller based means for decreasing the output power as a function of changes in tissue impedance.
U.S. Patent No. 4,727,874 includes an electrosurgical generator with a high frequency pulse width modulated feedback power control wherein each cycle of the generator is regulated in power content by modulating the width of the driving energy pulses.
The electrical energy usually has its waveform shaped to enhance its ability to cut or coagulate tissue. Different waveforms correspond to different modes of operation of the generator, and each mode gives the surgeon various operating advantages. Modes may include cut, coagulate, a blend thereof, or desiccate. A
surgeon can eas ily select and change the different modes of operation as the surgical procedure progresses.
In each mode of operation, it is important to regulate the electrosurgical energy delivered to the patient to achieve the desired surgical effect. This can be done, for example, by controlling the output energy from the electrosurgical generator for the type of tissue being treated.
Different types of tissues will be encountered as the surgical procedure progresses and each unique tissue requires more or less energy in terms of voltage, current or power as a function of frequently changing tissue impedance and other factors, such as the level of vascularization, i.e., blood flow within the tissue.
Therefore, the same tissue will present different load impedance as the tissue is desiccated.
Two conventional types of energy regulation are used in commercial electrosurgical generators. The most common type controls the DC power supply of the generator by limiting the amount of power provided from the AC mains to which the generator is connected. A feedback control loop regulates output voltage by comparing a desired voltage or current with the output voltage or current supplied by the power supply. Another type of power regulation in commercial electrosurgical generators controls the gain of the high-frequency or radio frequency amplifier. A
feedback control loop compares the output power supplied from the RF amplifier for adjustment to a desired power level.
U.S. Patent Nos. 3,964,487; 3,980,085; 4,188,927 and 4,092,986 have circuitry to reduce the output current in accordance with increasing load impedance. In those patents, constant voltage output is maintained and the current is decreased with increasing load impedance.
U.S. Patent No. 4,126,137 controls the power amplifier of the electrosurgical unit in accord with a non-linear compensation circuit applied to a feedback signal derived from a comparison of the power level reference signal and the mathematical product of two signals including sensed current and voltage in the unit.
U.S. Patent No. 4,658,819 has an electrosurgical generator which has a microprocessor controller based means for decreasing the output power as a function of changes in tissue impedance.
U.S. Patent No. 4,727,874 includes an electrosurgical generator with a high frequency pulse width modulated feedback power control wherein each cycle of the generator is regulated in power content by modulating the width of the driving energy pulses.
U.S. Patent No. 3,601,126 has an electrosurgical generator having a feedback circuit that attempts to maintain the output current at constant amplitude over a wide range of tissue impedances.
None of the aforementioned U.S. patents include optical detection of blood for regulating or controlling the output energy or output waveforms of the electrosurgical generator during different operational modes over a finite patient tissue impedance range. Optical detection of blood during electrosurgery also allows surgeons with color blindness to effectively perform electrosurgery. In a study that was published in 1997, 18 of 40 physicians with color blindness reported difficulties in detecting blood in body products. Spalding, J. Anthony B., "Doctors with inherited colour vision deficiency:
their difficulties in clinical work," Cavonius CR, ed., Colour Vision Deficiencies, XII:
Proceeding of the International Research Group for Colour Vision Deficiencies, 1995, Norwell, Mass.: Kluwer Academic Publishers, pages 483-489, 1997.
Accordingly, there exists a need for a method and system for optically detecting blood during electrosurgery and controlling the output energy or output waveforms of an electrosurgical generator in accordance with the amount of blood optically detected.
SUMMARY
A method and electrosurgical system for optically detecting blood and controlling an electrosurgical generator are provided. An optical blood detection system is used for optically detecting blood and may be included as an integral part of the overall electrosurgical system's circuitry, or may be designed as a separate unit that connects to, and controls, an electrosurgical generator. The optical blood detection system may be embodied through a variety of analog, digital and/or optical circuit components or arrangements, including software running on computational and memory circuitry.
The optical blood detection system controls the output energy of the electrosurgical generator in accordance with the amount of blood detected.
This allows for a surgeon to perform electrosurgery without having to stop and observe the condition of the tissue to determine if additional electrosurgery is needed.
None of the aforementioned U.S. patents include optical detection of blood for regulating or controlling the output energy or output waveforms of the electrosurgical generator during different operational modes over a finite patient tissue impedance range. Optical detection of blood during electrosurgery also allows surgeons with color blindness to effectively perform electrosurgery. In a study that was published in 1997, 18 of 40 physicians with color blindness reported difficulties in detecting blood in body products. Spalding, J. Anthony B., "Doctors with inherited colour vision deficiency:
their difficulties in clinical work," Cavonius CR, ed., Colour Vision Deficiencies, XII:
Proceeding of the International Research Group for Colour Vision Deficiencies, 1995, Norwell, Mass.: Kluwer Academic Publishers, pages 483-489, 1997.
Accordingly, there exists a need for a method and system for optically detecting blood during electrosurgery and controlling the output energy or output waveforms of an electrosurgical generator in accordance with the amount of blood optically detected.
SUMMARY
A method and electrosurgical system for optically detecting blood and controlling an electrosurgical generator are provided. An optical blood detection system is used for optically detecting blood and may be included as an integral part of the overall electrosurgical system's circuitry, or may be designed as a separate unit that connects to, and controls, an electrosurgical generator. The optical blood detection system may be embodied through a variety of analog, digital and/or optical circuit components or arrangements, including software running on computational and memory circuitry.
The optical blood detection system controls the output energy of the electrosurgical generator in accordance with the amount of blood detected.
This allows for a surgeon to perform electrosurgery without having to stop and observe the condition of the tissue to determine if additional electrosurgery is needed.
More particularly, the optical blood detection system automatically controls the output waveform generated by the electrosurgical generator during electrosurgery using a feedback signal received from the optical blood detection system. For example, if coagulation of the tissue is desired, the optical blood detection system continuously analyzes the tissue for the presence of blood and controls the output waveform accordingly.
While the optical blood detection system may be used to control electrosurgical generators of varying designs, it is preferred that the electrosurgical generator includes a power selection system wherein the user may initialize, set, monitor, and/or control the operation of the electrosurgical generator. The preferred electrosurgical generator need not be limited to these four functional elements, for example the electrosurgical generator could also include additional safety, monitoring, signal modification/conditioning, and/or feedback circuitry or functional elements/processes.
The actual electrosurgical generator's design may include the use of digital components and signaling, analog components and signaling, and/or optical components and signaling, or may be embodied, completely or partially within a software process running on hardware components.
The optical blood detection system includes an optical light beam generating circuit having optical components for generating and focusing a light beam in close proximity to and/or on an electrode of an electrosurgical instrument; a circuit having optical components for capturing reflected light energy, such as a photosensitive detector; a blood detection circuit for analyzing the reflected light energy and/or other characteristics and determining the amount of blood present in proximity to and/or on the electrode; and a feedback correction circuit.
The feedback correction circuit which is electrically connected to receive a signal from the blood detection circuit functions to produce a feedback control signal which it then supplies to the power selection system, within the electrosurgical generator, so as to cause the power selection system to control the amount of electrosurgical energy created and/or the type of output waveform generated in accordance to the amount of blood present in proximity to and/or on the electrode. The system can also detect the presence of any blood vessels in proximity to the distal end of the electrode and control the electrosurgical generator accordingly or alert the surgeon to prevent, for example, the severing of major blood vessels.
Preferably, the optical light beam is focused in front of the distal end of the electrode to detect blood present on tissue which is being cut or coagulated by the 5 electrosurgical instrument. The optical light beam may have light energy within the visible, near-infrared and infrared light spectrum wavelengths.
It is provided that one or more of the above-mentioned circuits can be implemented by one or more sets of programmable instructions configured for being executed by at least one processor of the electrosurgical system or at least one processor remotely located from the electrosurgical system. For example, the data corresponding to the reflected light energy can be transmitted, either wirelessly or non-wirelessly, over a network, such as a LAN, WAN, or the Internet, to a remote server or control station for analyzing the data using a set of programmable instructions for determining the amount of blood present in proximity to and/or on the electrode.
In accordance with the analysis performed, the remote server or control station then generates using the same or another set of programmable instructions the feedback control signal and supplies the signal to the power selection system. It is contemplated that another form of electromagnetic energy can be used to detect for the presence of blood besides the optical beam of light.
In one embodiment of the present invention an electrosurgical system is provided which includes a handpiece having a proximal end and a distal end from which light energy is emitted therefrom; at least one electrosurgical electrode on the handpiece and extending from the distal end from which electrosurgical energy is emitted there from; a source of light energy for generating the light energy and transmitting the same to the distal end via at least one waveguide; a source of electrosurgical energy for generating the electrosurgical energy and transmitting the same by at least one electrically conductive element to the electrode; and means for analyzing light energy characteristics for determining the amount of blood present in proximity to the electrode and for controlling the source of electrosurgical energy accordingly.
While the optical blood detection system may be used to control electrosurgical generators of varying designs, it is preferred that the electrosurgical generator includes a power selection system wherein the user may initialize, set, monitor, and/or control the operation of the electrosurgical generator. The preferred electrosurgical generator need not be limited to these four functional elements, for example the electrosurgical generator could also include additional safety, monitoring, signal modification/conditioning, and/or feedback circuitry or functional elements/processes.
The actual electrosurgical generator's design may include the use of digital components and signaling, analog components and signaling, and/or optical components and signaling, or may be embodied, completely or partially within a software process running on hardware components.
The optical blood detection system includes an optical light beam generating circuit having optical components for generating and focusing a light beam in close proximity to and/or on an electrode of an electrosurgical instrument; a circuit having optical components for capturing reflected light energy, such as a photosensitive detector; a blood detection circuit for analyzing the reflected light energy and/or other characteristics and determining the amount of blood present in proximity to and/or on the electrode; and a feedback correction circuit.
The feedback correction circuit which is electrically connected to receive a signal from the blood detection circuit functions to produce a feedback control signal which it then supplies to the power selection system, within the electrosurgical generator, so as to cause the power selection system to control the amount of electrosurgical energy created and/or the type of output waveform generated in accordance to the amount of blood present in proximity to and/or on the electrode. The system can also detect the presence of any blood vessels in proximity to the distal end of the electrode and control the electrosurgical generator accordingly or alert the surgeon to prevent, for example, the severing of major blood vessels.
Preferably, the optical light beam is focused in front of the distal end of the electrode to detect blood present on tissue which is being cut or coagulated by the 5 electrosurgical instrument. The optical light beam may have light energy within the visible, near-infrared and infrared light spectrum wavelengths.
It is provided that one or more of the above-mentioned circuits can be implemented by one or more sets of programmable instructions configured for being executed by at least one processor of the electrosurgical system or at least one processor remotely located from the electrosurgical system. For example, the data corresponding to the reflected light energy can be transmitted, either wirelessly or non-wirelessly, over a network, such as a LAN, WAN, or the Internet, to a remote server or control station for analyzing the data using a set of programmable instructions for determining the amount of blood present in proximity to and/or on the electrode.
In accordance with the analysis performed, the remote server or control station then generates using the same or another set of programmable instructions the feedback control signal and supplies the signal to the power selection system. It is contemplated that another form of electromagnetic energy can be used to detect for the presence of blood besides the optical beam of light.
In one embodiment of the present invention an electrosurgical system is provided which includes a handpiece having a proximal end and a distal end from which light energy is emitted therefrom; at least one electrosurgical electrode on the handpiece and extending from the distal end from which electrosurgical energy is emitted there from; a source of light energy for generating the light energy and transmitting the same to the distal end via at least one waveguide; a source of electrosurgical energy for generating the electrosurgical energy and transmitting the same by at least one electrically conductive element to the electrode; and means for analyzing light energy characteristics for determining the amount of blood present in proximity to the electrode and for controlling the source of electrosurgical energy accordingly.
In another embodiment of the present invention an electrosurgical system is provided which includes means for generating and directing light energy on tissue;
means for generating electrosurgical energy and transmitting the same via an electrode to the tissue; and means for analyzing characteristics of the light energy for determining the amount of blood present in proximity to the electrode and for controlling the means for generating electrosurgical energy accordingly.
Further, in another embodiment of the present invention, a method is provided for performing electrosurgery. The method includes the steps of supplying light energy and electrosurgical energy to tissue via at least one instrument having a distal end; and analyzing characteristics of the light energy for determining the amount of blood present in proximity to the at least one instrument and for controlling the delivery of electrosurgical energy accordingly.
Finally, in another embodiment of the present invention, a surgical method is provided which includes the steps of providing a surgical instrument configured for insertion within a patient; providing a source of light energy for generating light energy and delivering the same via the surgical instrument; and analyzing light energy characteristics for determining the amount of blood present in proximity to the surgical instrument.
Further features of the disclosure will become more readily apparent to those skilled in the art from the following detailed description taken in conjunction with the drawings.
means for generating electrosurgical energy and transmitting the same via an electrode to the tissue; and means for analyzing characteristics of the light energy for determining the amount of blood present in proximity to the electrode and for controlling the means for generating electrosurgical energy accordingly.
Further, in another embodiment of the present invention, a method is provided for performing electrosurgery. The method includes the steps of supplying light energy and electrosurgical energy to tissue via at least one instrument having a distal end; and analyzing characteristics of the light energy for determining the amount of blood present in proximity to the at least one instrument and for controlling the delivery of electrosurgical energy accordingly.
Finally, in another embodiment of the present invention, a surgical method is provided which includes the steps of providing a surgical instrument configured for insertion within a patient; providing a source of light energy for generating light energy and delivering the same via the surgical instrument; and analyzing light energy characteristics for determining the amount of blood present in proximity to the surgical instrument.
Further features of the disclosure will become more readily apparent to those skilled in the art from the following detailed description taken in conjunction with the drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
Various embodiments will be described hereinbelow with reference to the drawings wherein:
FIG. 1 is a perspective diagram of one embodiment of the present electrosurgical system;
FIG. 2 is cut-away, schematic diagram of an electrosurgical handpiece instrument of the electrosurgical system of FIG. 1;
FIG. 3 is a block diagram of the optical blood detection system;
FIG. 4 is a flow chart showing the operation of the optical blood detection system according to a first method;
FIG. 5 is a flow chart showing the operation of the optical blood detection system according to a second method; and FIG. 6 is a cut-away, schematic diagram of another embodiment for the electrosurgical handpiece instrument.
DETAILED DESCRIPTION OF A PREFERRED EMBODIMENT
An electrosurgical system 10 is shown in perspective in FIG. 1 and allows a surgeon to provide cutting, coagulating, and/or a combination thereof on tissue of a patient 11. The electrosurgical system 10 has a handpiece 12 with a proximal end 13 to be held and controlled by the surgeon. A distal end 14 on the handpiece 12 has a port 15 from which an optical light beam is directed to the patient 11. An electrosurgical electrode 16 extends from the distal end 14 of the handpiece 12.
An optical blood detection system 17 for generating the optical light beam is connected to the proximal end 13 of the handpiece 12 via waveguide/wires 34.
The optical blood detection system 17 can be manually controlled by the surgeon or automatically controlled for delivering the optical light beam from the distal end 14 of the handpiece 12 toward the patient 11. An electrosurgical generator 18 for generating the electrosurgical energy is electrically connected to the proximal end 13 of the handpiece 12 and may be manually controlled by the surgeon or automatically controlled for transmitting electrosurgical energy from the electrosurgical electrode 16 toward the patient 11. The optical blood detection system 17 and the electrosurgical generator 18 are connected by a cable 38 for providing data communications there between and a feedback control signal from the optical blood detection system 17 to the generator 18 for controlling the generator 18.
While the optical blood detection system 17 may be used to control electrosurgical generator 18, it is preferred that the electrosurgical generator 18 includes a power selection system wherein the user may initialize, set, monitor, and/or control the operation of the electrosurgical generator 18. The preferred electrosurgical generator need not be limited to these four functional elements, for example the electrosurgical generator 18 could also include additional safety, monitoring, signal modification/conditioning, and/or feedback circuitry or functional elements/processes.
The actual electrosurgical generator's design may include the use of digital components and signaling, analog components and signaling, and/or optical components and signaling, or may be embodied, completely or partially within a software process running on hardware components.
A return path 19 is provided for the electrosurgical energy; the return path may be in a monopolar or bipolar circuit. FIG. 1 illustrates a monopolar circuit having a return pad 20, in lieu of a return electrode in the case of a bipolar circuit. The return path 19 is connected to receive at least a portion of the transmitted electrosurgical energy from the source of electrosurgical energy 18 and then the patient 11. A
return input 22 for the source of electrosurgical energy 18 is connected to the return path 19 for furnishing a complete circuit 23 between the electrosurgical electrode 16, the patient 11, and the electrosurgical generator 18.
A manually-actuated control button 24 is provided on the handpiece 12 for the selective control by the surgeon of the electrosurgical generator 18 for controlling the electrosurgical energy delivered from the distal end 14. The control button 24 may also be located at a foot pedal 26.
It is provided that the surgeon can utilize the optical beam emanating from port 15 to pinpoint the target tissue to be treated if the optical light beam has light energy within the visible spectrum. It is envisioned that the optical light beam may have light 3o energy within the visible, near-infrared and infrared light spectrum wavelengths.
Various embodiments will be described hereinbelow with reference to the drawings wherein:
FIG. 1 is a perspective diagram of one embodiment of the present electrosurgical system;
FIG. 2 is cut-away, schematic diagram of an electrosurgical handpiece instrument of the electrosurgical system of FIG. 1;
FIG. 3 is a block diagram of the optical blood detection system;
FIG. 4 is a flow chart showing the operation of the optical blood detection system according to a first method;
FIG. 5 is a flow chart showing the operation of the optical blood detection system according to a second method; and FIG. 6 is a cut-away, schematic diagram of another embodiment for the electrosurgical handpiece instrument.
DETAILED DESCRIPTION OF A PREFERRED EMBODIMENT
An electrosurgical system 10 is shown in perspective in FIG. 1 and allows a surgeon to provide cutting, coagulating, and/or a combination thereof on tissue of a patient 11. The electrosurgical system 10 has a handpiece 12 with a proximal end 13 to be held and controlled by the surgeon. A distal end 14 on the handpiece 12 has a port 15 from which an optical light beam is directed to the patient 11. An electrosurgical electrode 16 extends from the distal end 14 of the handpiece 12.
An optical blood detection system 17 for generating the optical light beam is connected to the proximal end 13 of the handpiece 12 via waveguide/wires 34.
The optical blood detection system 17 can be manually controlled by the surgeon or automatically controlled for delivering the optical light beam from the distal end 14 of the handpiece 12 toward the patient 11. An electrosurgical generator 18 for generating the electrosurgical energy is electrically connected to the proximal end 13 of the handpiece 12 and may be manually controlled by the surgeon or automatically controlled for transmitting electrosurgical energy from the electrosurgical electrode 16 toward the patient 11. The optical blood detection system 17 and the electrosurgical generator 18 are connected by a cable 38 for providing data communications there between and a feedback control signal from the optical blood detection system 17 to the generator 18 for controlling the generator 18.
While the optical blood detection system 17 may be used to control electrosurgical generator 18, it is preferred that the electrosurgical generator 18 includes a power selection system wherein the user may initialize, set, monitor, and/or control the operation of the electrosurgical generator 18. The preferred electrosurgical generator need not be limited to these four functional elements, for example the electrosurgical generator 18 could also include additional safety, monitoring, signal modification/conditioning, and/or feedback circuitry or functional elements/processes.
The actual electrosurgical generator's design may include the use of digital components and signaling, analog components and signaling, and/or optical components and signaling, or may be embodied, completely or partially within a software process running on hardware components.
A return path 19 is provided for the electrosurgical energy; the return path may be in a monopolar or bipolar circuit. FIG. 1 illustrates a monopolar circuit having a return pad 20, in lieu of a return electrode in the case of a bipolar circuit. The return path 19 is connected to receive at least a portion of the transmitted electrosurgical energy from the source of electrosurgical energy 18 and then the patient 11. A
return input 22 for the source of electrosurgical energy 18 is connected to the return path 19 for furnishing a complete circuit 23 between the electrosurgical electrode 16, the patient 11, and the electrosurgical generator 18.
A manually-actuated control button 24 is provided on the handpiece 12 for the selective control by the surgeon of the electrosurgical generator 18 for controlling the electrosurgical energy delivered from the distal end 14. The control button 24 may also be located at a foot pedal 26.
It is provided that the surgeon can utilize the optical beam emanating from port 15 to pinpoint the target tissue to be treated if the optical light beam has light energy within the visible spectrum. It is envisioned that the optical light beam may have light 3o energy within the visible, near-infrared and infrared light spectrum wavelengths.
With reference to FIG. 3, the optical blood detection system 17 includes an optical light beam generating circuit 52 having optical components for generating and focusing a light beam, such as a laser light beam, as known in the art, in close proximity to and/or on the electrode 16 of the handpiece 12. The wave guide 34, shown in FIG. 1, is used to deliver the light energy from the proximal end 13 to beyond the distal end 14.
The optical blood detection system 17 further includes at least one optical component 54 positioned at the distal end 14 of the handpiece 12, for capturing reflected light energy as known in the art. The at least one optical component 54 returns signals indicative of the reflected light energy to the system 17 via waveguide/wires 34 to at least one photosensitive detector.
The optical blood detection system 17 further includes a blood detection circuit 56 for analyzing the reflected light energy and determining the amount of blood present in proximity to and/or on the electrode 16; and a feedback correction circuit 58.
The reflected light energy preferably includes data corresponding to light reflections indicative of two different wavelengths, a first and a second wavelength.
First, a first optical light beam having the first wavelength is generated and emanated from the handpiece 12. The reflected light energy indicative of the first optical light beam is captured and analyzed by the optical blood detection system 17 for measuring various parameters, such as photon counts. Second, a second optical light beam having the second wavelength is generated and emanated from the handpiece 12. The reflected light energy indicative of the second optical light beam is captured and analyzed by the optical blood detection system 17 for measuring various parameters, such as photon counts.
Alternatively, a broadband optical light beam is generated and emanated from the handpiece 12. The reflected light energies indicative of two separate and distinct wavelengths are captured and analyzed by the optical blood detection system 17 for measuring various parameters, such as photon counts. Preferably, in either method, the first wavelength is in the range of 620-700 nanometers and the second wavelength is in the range of 540-610 nanometers or 950-1050 nanometers.
A ratio is then obtained using two measured values corresponding to a particular parameter; one measured value is indicative of the first optical light beam or wavelength and one measured value is indicative of the second optical light beam or wavelength. A look-up table or other data structure is then used by a processor or by an individual to correlate the ratio with a particular amount or level of blood present in proximity to the electrode 16.
5 The reflected light energy can also be analyzed for determining the amount of blood present using one of several known methods, such as Near Infrared Spectroscopy (LAIRS), Infrared Spectroscopy (IRS), Fluorescence Spectroscopy, Raman Spectroscopy, Photoacoustic Spectroscopy (where the system 10 is equipped with a microphone for measuring an acoustic pressure wave created by the optical beam rapidly heating the 10 tissue), laser Doppler flowmetry, light scatter change measurements, and polarization change measurements. These methods determine the light intensity level, light scattering effects, level of fluorescent energy, and other characteristics of the reflected light energy. The determined light intensity level, light scattering effects, level of fluorescent energy, and/or other characteristics of the reflected light energy are then used to compute using mathematical equations, algorithms, and/or programmable instructions executed by at least one processor the amount of blood present in proximity to the electrode 16.
By knowing the optical signal characteristics of the generated light beam and the determined light intensity level, light scattering effects, level of fluorescent energy, and other characteristics of the reflected light energy, the system 17 is able to determine using a look-up table or other data structure the amount of blood present in proximity to the electrode 16. If the analysis indicates that there is a high amount of blood present in proximity to the electrode 16, one can conclude that the tissue has not coagulated (in the case of a coagulation procedure) or has been cut (in the case of a cutting procedure).
If the analysis indicates that there is a low amount of blood present in proximity to the electrode 16, one can conclude that the tissue has coagulated (in the case of a coagulation procedure) or has not been adequately cut (in the case of a cutting procedure).
The system can also detect the presence of any blood vessels in proximity to the distal end of the electrode 16 and control the electrosurgical generator 18 accordingly or alert the surgeon to prevent, for example, the severing of major blood vessels.
The optical blood detection system 17 further includes at least one optical component 54 positioned at the distal end 14 of the handpiece 12, for capturing reflected light energy as known in the art. The at least one optical component 54 returns signals indicative of the reflected light energy to the system 17 via waveguide/wires 34 to at least one photosensitive detector.
The optical blood detection system 17 further includes a blood detection circuit 56 for analyzing the reflected light energy and determining the amount of blood present in proximity to and/or on the electrode 16; and a feedback correction circuit 58.
The reflected light energy preferably includes data corresponding to light reflections indicative of two different wavelengths, a first and a second wavelength.
First, a first optical light beam having the first wavelength is generated and emanated from the handpiece 12. The reflected light energy indicative of the first optical light beam is captured and analyzed by the optical blood detection system 17 for measuring various parameters, such as photon counts. Second, a second optical light beam having the second wavelength is generated and emanated from the handpiece 12. The reflected light energy indicative of the second optical light beam is captured and analyzed by the optical blood detection system 17 for measuring various parameters, such as photon counts.
Alternatively, a broadband optical light beam is generated and emanated from the handpiece 12. The reflected light energies indicative of two separate and distinct wavelengths are captured and analyzed by the optical blood detection system 17 for measuring various parameters, such as photon counts. Preferably, in either method, the first wavelength is in the range of 620-700 nanometers and the second wavelength is in the range of 540-610 nanometers or 950-1050 nanometers.
A ratio is then obtained using two measured values corresponding to a particular parameter; one measured value is indicative of the first optical light beam or wavelength and one measured value is indicative of the second optical light beam or wavelength. A look-up table or other data structure is then used by a processor or by an individual to correlate the ratio with a particular amount or level of blood present in proximity to the electrode 16.
5 The reflected light energy can also be analyzed for determining the amount of blood present using one of several known methods, such as Near Infrared Spectroscopy (LAIRS), Infrared Spectroscopy (IRS), Fluorescence Spectroscopy, Raman Spectroscopy, Photoacoustic Spectroscopy (where the system 10 is equipped with a microphone for measuring an acoustic pressure wave created by the optical beam rapidly heating the 10 tissue), laser Doppler flowmetry, light scatter change measurements, and polarization change measurements. These methods determine the light intensity level, light scattering effects, level of fluorescent energy, and other characteristics of the reflected light energy. The determined light intensity level, light scattering effects, level of fluorescent energy, and/or other characteristics of the reflected light energy are then used to compute using mathematical equations, algorithms, and/or programmable instructions executed by at least one processor the amount of blood present in proximity to the electrode 16.
By knowing the optical signal characteristics of the generated light beam and the determined light intensity level, light scattering effects, level of fluorescent energy, and other characteristics of the reflected light energy, the system 17 is able to determine using a look-up table or other data structure the amount of blood present in proximity to the electrode 16. If the analysis indicates that there is a high amount of blood present in proximity to the electrode 16, one can conclude that the tissue has not coagulated (in the case of a coagulation procedure) or has been cut (in the case of a cutting procedure).
If the analysis indicates that there is a low amount of blood present in proximity to the electrode 16, one can conclude that the tissue has coagulated (in the case of a coagulation procedure) or has not been adequately cut (in the case of a cutting procedure).
The system can also detect the presence of any blood vessels in proximity to the distal end of the electrode 16 and control the electrosurgical generator 18 accordingly or alert the surgeon to prevent, for example, the severing of major blood vessels.
The feedback correction circuit 58 which is electrically connected to receive a signal from the blood detection circuit 56 fiulctions to produce a feedback control signal which it then supplies to the power selection system, within the electrosurgical generator 18, via wire 3 8 so as to cause the power selection system to control the amount of electrosurgical energy created and/or the type of output waveform generated (coagulation or tissue division waveform) in accordance to the amount of blood present in proximity to and/or on the electrode 16.
FIG. 4 is a flow chart illustrating an exemplary method of operation of the optical blood detection system 17. In step 400, the optical light beam and electrosurgical energy are generated. The reflected light energy is captured in step 402 and analyzed in step 404 to determine the amount of blood present in proximity to the electrode 16 at step 406. In step 408 it is determined whether the sensed level of blood in proximity to the electrode 16 is above a predetermined threshold (the predetermined threshold value is dependent on the method being used to detect the amount of blood present). If the sensed level of blood is not above the predetermined threshold value, it is then determined at step 410 whether the procedure being performed is a coagulation procedure. If a coagulation procedure is not being performed, i.e., a cutting procedure is being performed, the cutting procedure is continued at step 412, and the process returns to step 408.
If at step 410, it is determined that a coagulation procedure is being performed, the process proceeds to step 414 where a signal is transmitted by the feedback correction circuit ' 58 to the electrosurgical generator 18 to control the amount of electrosurgical energy and/or the type of output waveform generated or to shut-off the electrosurgical generator 18, since the coagulation procedure has been adequately performed. If at step 408, it is determined that the sensed level of blood is above the predetermined threshold value, it is then determined at step 416 whether the procedure being performed is a cutting procedure. If a cutting procedure is not being performed, i.e., a coagulation procedure is being performed, the coagulation procedure is continued at step 418, and the process returns to step 408.
If at step 416, it is determined that a cutting procedure is being performed, the process proceeds to step 414 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 to control the amount of electrosurgical energy and/or the type of output waveform generated or to shut-off the electrosurgical generator 18, since the cutting procedure has been adequately performed.
FIG. 5 is a flow chart illustrating another exemplary method of operation of the optical blood detection system 17. In step 500, the optical light beam and electrosurgical energy are generated. The reflected light energy is captured in step 502 and analyzed in step 504 to determine the amount of blood present in proximity to the electrode 16 at step 506. Step 506 determines the amount of blood present by calculating the ratio value as determined by dividing the photon counts at wavelength 1 by the photon counts at wavelength 2. The ratio value is analyzed at step 508.
If the ratio value is low (lower than a predetermined ratio value)then the process proceeds to step 510 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 to control the mode of operation, namely, selecting a tissue division (cut) mode. Also, the amount of electrosurgical energy may be adjusted.
If at step 508, it is determined that the ratio value is high (greater than the predetermined ratio value), the process proceeds to step 512 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 selecting a hemostasis (coagulation) mode. The amount of electrosurgical energy may also be adjusted.
If at step 508, it is determined that the ratio value is at an intermediate value (approximately equal to the predetermined ratio value), the process proceeds to step 514 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 selecting a blended mode that is in proportion to the detected ratio value. Following either step 510, 512, or 514, the process returns to capture reflected light energy in step 502 in a continuous loop.
It is provided that depending on which of the above spectroscopy and other methods is used by the optical blood detection system 17 to determine the amount of blood present, the optical blood detection system 17 is controlled accordingly using known blood-related optical measurement parameters for each method, in order to generate and focus an optical light beam having characteristics suitable for the method.
The optical blood detection system 17 can change the wavelength of the optical light beam within the visible, near-infrared and infrared light spectrum wavelengths depending on which of the above methods is being used for determining the amount of blood present in proximity to the electrode 16. For example, if the LAIRS
method is used, the optical light beam needs to have a wavelength just above the visible spectrum.
The wavelength of the optical light beam can be manually selected using a control knob or other control means on the optical blood detection system 17.
If the wavelength of the optical light beam is in a particular range, the light energy of the optical light beam can be used to create an ionized conductive pathway along which the electrosurgical energy can be guided.
When the light energy is being used to create an ionized pathway, the light energy must be controlled using the control means in order to avoid undesired tissue effects. The duty cycle of the light beam should be kept in the range of 10-5 to 10-8.
Energy density delivered to any single area of tissue from the light beam should not exceed 26 J/cm2 for wavelengths between 1.06 and 10.6 microns, and 17 J/cm2 for wavelengths around and below 0.53 microns. For creating the ionized pathway, the wavelength of the optical beam should be in the range of 0.3 to 10.6 microns.
It is further provided that one or more of the above-mentioned circuits 52, 56 and 58 can be implemented by one or more sets of programmable instructions configured for being executed by at least one processor of the electrosurgical system 10 or at least one processor remotely located from the electrosurgical system 10.
For example, the data corresponding to the reflected light energy can be transmitted, either wirelessly or non-wirelessly, over a network, such as a LAN, WAN, or the Internet, to a remote server or control station for analyzing the data using a set of programmable instructions for determining the amount of blood present in proximity to and/or on the electrode 16 and/or the presence of blood vessels in proximity to the distal end of the electrode 16.
In accordance with the analysis performed, the remote server or control station then generates using the same or another set of programmable instructions the feedback control signal and supplies the signal to the power selection system. It is contemplated that another form of electromagnetic energy can be used to detect for the presence of blood besides the optical beam of light.
FIG. 4 is a flow chart illustrating an exemplary method of operation of the optical blood detection system 17. In step 400, the optical light beam and electrosurgical energy are generated. The reflected light energy is captured in step 402 and analyzed in step 404 to determine the amount of blood present in proximity to the electrode 16 at step 406. In step 408 it is determined whether the sensed level of blood in proximity to the electrode 16 is above a predetermined threshold (the predetermined threshold value is dependent on the method being used to detect the amount of blood present). If the sensed level of blood is not above the predetermined threshold value, it is then determined at step 410 whether the procedure being performed is a coagulation procedure. If a coagulation procedure is not being performed, i.e., a cutting procedure is being performed, the cutting procedure is continued at step 412, and the process returns to step 408.
If at step 410, it is determined that a coagulation procedure is being performed, the process proceeds to step 414 where a signal is transmitted by the feedback correction circuit ' 58 to the electrosurgical generator 18 to control the amount of electrosurgical energy and/or the type of output waveform generated or to shut-off the electrosurgical generator 18, since the coagulation procedure has been adequately performed. If at step 408, it is determined that the sensed level of blood is above the predetermined threshold value, it is then determined at step 416 whether the procedure being performed is a cutting procedure. If a cutting procedure is not being performed, i.e., a coagulation procedure is being performed, the coagulation procedure is continued at step 418, and the process returns to step 408.
If at step 416, it is determined that a cutting procedure is being performed, the process proceeds to step 414 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 to control the amount of electrosurgical energy and/or the type of output waveform generated or to shut-off the electrosurgical generator 18, since the cutting procedure has been adequately performed.
FIG. 5 is a flow chart illustrating another exemplary method of operation of the optical blood detection system 17. In step 500, the optical light beam and electrosurgical energy are generated. The reflected light energy is captured in step 502 and analyzed in step 504 to determine the amount of blood present in proximity to the electrode 16 at step 506. Step 506 determines the amount of blood present by calculating the ratio value as determined by dividing the photon counts at wavelength 1 by the photon counts at wavelength 2. The ratio value is analyzed at step 508.
If the ratio value is low (lower than a predetermined ratio value)then the process proceeds to step 510 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 to control the mode of operation, namely, selecting a tissue division (cut) mode. Also, the amount of electrosurgical energy may be adjusted.
If at step 508, it is determined that the ratio value is high (greater than the predetermined ratio value), the process proceeds to step 512 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 selecting a hemostasis (coagulation) mode. The amount of electrosurgical energy may also be adjusted.
If at step 508, it is determined that the ratio value is at an intermediate value (approximately equal to the predetermined ratio value), the process proceeds to step 514 where a signal is transmitted by the feedback correction circuit 58 to the electrosurgical generator 18 selecting a blended mode that is in proportion to the detected ratio value. Following either step 510, 512, or 514, the process returns to capture reflected light energy in step 502 in a continuous loop.
It is provided that depending on which of the above spectroscopy and other methods is used by the optical blood detection system 17 to determine the amount of blood present, the optical blood detection system 17 is controlled accordingly using known blood-related optical measurement parameters for each method, in order to generate and focus an optical light beam having characteristics suitable for the method.
The optical blood detection system 17 can change the wavelength of the optical light beam within the visible, near-infrared and infrared light spectrum wavelengths depending on which of the above methods is being used for determining the amount of blood present in proximity to the electrode 16. For example, if the LAIRS
method is used, the optical light beam needs to have a wavelength just above the visible spectrum.
The wavelength of the optical light beam can be manually selected using a control knob or other control means on the optical blood detection system 17.
If the wavelength of the optical light beam is in a particular range, the light energy of the optical light beam can be used to create an ionized conductive pathway along which the electrosurgical energy can be guided.
When the light energy is being used to create an ionized pathway, the light energy must be controlled using the control means in order to avoid undesired tissue effects. The duty cycle of the light beam should be kept in the range of 10-5 to 10-8.
Energy density delivered to any single area of tissue from the light beam should not exceed 26 J/cm2 for wavelengths between 1.06 and 10.6 microns, and 17 J/cm2 for wavelengths around and below 0.53 microns. For creating the ionized pathway, the wavelength of the optical beam should be in the range of 0.3 to 10.6 microns.
It is further provided that one or more of the above-mentioned circuits 52, 56 and 58 can be implemented by one or more sets of programmable instructions configured for being executed by at least one processor of the electrosurgical system 10 or at least one processor remotely located from the electrosurgical system 10.
For example, the data corresponding to the reflected light energy can be transmitted, either wirelessly or non-wirelessly, over a network, such as a LAN, WAN, or the Internet, to a remote server or control station for analyzing the data using a set of programmable instructions for determining the amount of blood present in proximity to and/or on the electrode 16 and/or the presence of blood vessels in proximity to the distal end of the electrode 16.
In accordance with the analysis performed, the remote server or control station then generates using the same or another set of programmable instructions the feedback control signal and supplies the signal to the power selection system. It is contemplated that another form of electromagnetic energy can be used to detect for the presence of blood besides the optical beam of light.
Another embodiment for a handpiece for the electrosurgical system 10 is depicted by FIG. 6 and designated generally by reference numeral 12A. The handpiece 12A includes a proximal end 13A which is held and controlled by the surgeon. A
distal end 14A on the handpiece 12A has a port 15A from which an optical light beam is directed to the patient 11. An electrosurgical electrode 16A extends from the distal end 14A of the handpiece 12A. The at least one optical component 54 at the distal end 14A
of the handpiece 12A returns signals indicative of the reflected light energy to the optical blood detection system 17 via waveguide/wires 34 to at least one photosensitive detector.
A manually-actuated variable control button 24A is provided on the handpiece 12A for the real-time, selective control by the surgeon of the intensity or level of the current, i.e., intensity of the output waveform, provided by the electrosurgical generator 18 in accordance with the amount of blood detected by the optical blood detection system 17. Accordingly, the handpiece 12A provides the surgeon with the ability to control the amount of tissue cutting, coagulating, etc. as the system 10 concurrently detects the amount of blood.
In another preferred embodiment with continued reference to FIG. 6, the optical detection of the presence of blood controls the mode of the electrosurgical generator output in real-time or on-the-fly. For illustrative purposes, if a large amount of blood is detected adjacent to the electrode 16A then the electrosurgical generator output mode is automatically set for a high-level "hemostasis" (coag) waveform. If no blood is detected, then a "tissue division" (cut) waveform is automatically selected for the electrosurgical generator output. If an intermediate amount of blood is detected, then a "blend" is selected in proportion to the amount of blood detected.
Simultaneously, the surgeon can use the manually-actuated variable control button 24A for real-time, selective control of the intensity or level of current.
The surgeon selects the intensity that provides an operational speed within his individual comfort zone. So the selection of the mode is automatically controlled by the blood detection circuit 56 and the surgeon controls the intensity of the output in real-time or on-the-fly. This embodiment greatly simplifies the surgeon-equipment interface by providing an automated mode select to assist the surgeon. As a result there is an improvement in the surgical outcome, because the appropriate mode is selected in real-time, thereby reducing thermal spread within the tissue. Additionally, since the surgeon maintains control of the intensity of the current, there is a built-in safety feature.
5 The above-described control scheme can be offered as a selectable feature or option. That is, a selectable switch would allow the surgeon to choose between operating the system of the present invention in a fully automatic mode or in a mode which enables the surgeon to control the intensity of the current.
It is contemplated that the control button 24A may also be located at the foot 10 pedal 26. It is further contemplated that the functions of the variable control button 24A can be automated, in order for the system 10 to automatically control the intensity of the current in accordance with the amount of blood detected by the optical blood detection system 17.
It is provided that the surgeon can utilize the optical beam emanating from port 15 15A to pinpoint the target tissue to be treated if the optical light beam has light energy within the visible spectrum. It is envisioned that the optical light beam may have light energy within the visible, near-infrared and infrared light spectrum wavelengths.
As shown by FIGS. 2 and 6, the electrosurgical system 10 is configured so the distal end 14, 14A and the electrosurgical electrode 16, 16A are preferably arranged geometrically relative to the handpiece 12, 12A to provide the light energy from the distal end 14, 14A. This geometry provides for the combined concurrent application of the light energy and the electrosurgical energy. The ionized pathway is formed by the light energy from the distal end 14, 14A to the patient 11 to direct the electrosurgical energy there along.
A method for providing cutting, coagulating, and/or a combination thereof on tissue of the patient 11 with the electrosurgical system 10 includes the following step of directing light energy and electrosurgical energy from the handpiece 12, 12A
with its proximal and distal ends, 13, 13A and 14, 14A, along a longitudinal axis of the handpiece 12, 12A by aiming the distal end 14, 14A thereof along the longitudinal axis from which light energy and electrosurgical energy may be at least in part concurrently directed.
distal end 14A on the handpiece 12A has a port 15A from which an optical light beam is directed to the patient 11. An electrosurgical electrode 16A extends from the distal end 14A of the handpiece 12A. The at least one optical component 54 at the distal end 14A
of the handpiece 12A returns signals indicative of the reflected light energy to the optical blood detection system 17 via waveguide/wires 34 to at least one photosensitive detector.
A manually-actuated variable control button 24A is provided on the handpiece 12A for the real-time, selective control by the surgeon of the intensity or level of the current, i.e., intensity of the output waveform, provided by the electrosurgical generator 18 in accordance with the amount of blood detected by the optical blood detection system 17. Accordingly, the handpiece 12A provides the surgeon with the ability to control the amount of tissue cutting, coagulating, etc. as the system 10 concurrently detects the amount of blood.
In another preferred embodiment with continued reference to FIG. 6, the optical detection of the presence of blood controls the mode of the electrosurgical generator output in real-time or on-the-fly. For illustrative purposes, if a large amount of blood is detected adjacent to the electrode 16A then the electrosurgical generator output mode is automatically set for a high-level "hemostasis" (coag) waveform. If no blood is detected, then a "tissue division" (cut) waveform is automatically selected for the electrosurgical generator output. If an intermediate amount of blood is detected, then a "blend" is selected in proportion to the amount of blood detected.
Simultaneously, the surgeon can use the manually-actuated variable control button 24A for real-time, selective control of the intensity or level of current.
The surgeon selects the intensity that provides an operational speed within his individual comfort zone. So the selection of the mode is automatically controlled by the blood detection circuit 56 and the surgeon controls the intensity of the output in real-time or on-the-fly. This embodiment greatly simplifies the surgeon-equipment interface by providing an automated mode select to assist the surgeon. As a result there is an improvement in the surgical outcome, because the appropriate mode is selected in real-time, thereby reducing thermal spread within the tissue. Additionally, since the surgeon maintains control of the intensity of the current, there is a built-in safety feature.
5 The above-described control scheme can be offered as a selectable feature or option. That is, a selectable switch would allow the surgeon to choose between operating the system of the present invention in a fully automatic mode or in a mode which enables the surgeon to control the intensity of the current.
It is contemplated that the control button 24A may also be located at the foot 10 pedal 26. It is further contemplated that the functions of the variable control button 24A can be automated, in order for the system 10 to automatically control the intensity of the current in accordance with the amount of blood detected by the optical blood detection system 17.
It is provided that the surgeon can utilize the optical beam emanating from port 15 15A to pinpoint the target tissue to be treated if the optical light beam has light energy within the visible spectrum. It is envisioned that the optical light beam may have light energy within the visible, near-infrared and infrared light spectrum wavelengths.
As shown by FIGS. 2 and 6, the electrosurgical system 10 is configured so the distal end 14, 14A and the electrosurgical electrode 16, 16A are preferably arranged geometrically relative to the handpiece 12, 12A to provide the light energy from the distal end 14, 14A. This geometry provides for the combined concurrent application of the light energy and the electrosurgical energy. The ionized pathway is formed by the light energy from the distal end 14, 14A to the patient 11 to direct the electrosurgical energy there along.
A method for providing cutting, coagulating, and/or a combination thereof on tissue of the patient 11 with the electrosurgical system 10 includes the following step of directing light energy and electrosurgical energy from the handpiece 12, 12A
with its proximal and distal ends, 13, 13A and 14, 14A, along a longitudinal axis of the handpiece 12, 12A by aiming the distal end 14, 14A thereof along the longitudinal axis from which light energy and electrosurgical energy may be at least in part concurrently directed.
Preferably, as shown by FIGS. 2 and 6, the optical light beam is focused in front of the distal end 14, 14A of the electrode 16, 16A to detect blood present on tissue which is being cut or coagulated by the handpiece 12, 12A. The light energy is emanated continuously from the distal end 14, 14A of the handpiece 12, 12A.
Or, alternatively, the surgeon activates the electrosurgical generator 18 using the control button 24, 24A on the handpiece 12, 12A or the footswitch 26. When activation is initiated, first, light energy is emitted from the distal end 14, 14A of the handpiece 12, 12A, then after a brief time delay in which the presence of blood is detected, the transmission of electrosurgical energy from the electrosurgical electrode 16, 16A at the distal end 14, l4Aof the handpiece 12, 12A is enabled.
In the case of encountering a bleeding vessel that has created a pool of blood, this method provides detection of the pool of blood and automatic select of a hemostatic (coagulation) waveform by the electrosurgical generator 18 in order to affect a "spot coag" procedure.
Likewise, if no blood is present, the detection system selects a tissue division (cut) waveform. In this way, the thermal damage to the tissue is reduced creating a superior tissue effect.
The method includes the additional step of guiding the electrosurgical energy by arranging the distal end 14, 14A and the electrosurgical electrode 16, 16A
geometrically relative to the handpiece 12, 12A for providing the optical light beam from the distal end 14, 14A for the combined concurrent application of the optical light beam and the electrosurgical energy. Then the added step of ionizing a conductive pathway with light energy from the distal end 14, 14A to the patient 11 to direct the flow of electrosurgical energy is performed.
The method also includes the additional step of providing an elongate electrosurgical electrode support for supporting the electrode 16, 16A for endoscopic or laparoscopic use where a cannula is placed through the patient's body wall.
The claims which follow seek to cover the described embodiments and their equivalents. The concept in its broadest scope covers the system and methods for optically detecting the presence of blood and/or determining the amount of blood detected during electrosurgery. It is to be understood that the concept is subject to many modifications without departing from the spirit and scope of the claims as recited herein.
Although the subject invention has been described with respect to preferred embodiments, it will be readily apparent to those having ordinary skill in the art to which it appertains that changes and modifications may be made thereto without departing from the spirit or scope of the subject apparatus as defined by the appended claims.
Or, alternatively, the surgeon activates the electrosurgical generator 18 using the control button 24, 24A on the handpiece 12, 12A or the footswitch 26. When activation is initiated, first, light energy is emitted from the distal end 14, 14A of the handpiece 12, 12A, then after a brief time delay in which the presence of blood is detected, the transmission of electrosurgical energy from the electrosurgical electrode 16, 16A at the distal end 14, l4Aof the handpiece 12, 12A is enabled.
In the case of encountering a bleeding vessel that has created a pool of blood, this method provides detection of the pool of blood and automatic select of a hemostatic (coagulation) waveform by the electrosurgical generator 18 in order to affect a "spot coag" procedure.
Likewise, if no blood is present, the detection system selects a tissue division (cut) waveform. In this way, the thermal damage to the tissue is reduced creating a superior tissue effect.
The method includes the additional step of guiding the electrosurgical energy by arranging the distal end 14, 14A and the electrosurgical electrode 16, 16A
geometrically relative to the handpiece 12, 12A for providing the optical light beam from the distal end 14, 14A for the combined concurrent application of the optical light beam and the electrosurgical energy. Then the added step of ionizing a conductive pathway with light energy from the distal end 14, 14A to the patient 11 to direct the flow of electrosurgical energy is performed.
The method also includes the additional step of providing an elongate electrosurgical electrode support for supporting the electrode 16, 16A for endoscopic or laparoscopic use where a cannula is placed through the patient's body wall.
The claims which follow seek to cover the described embodiments and their equivalents. The concept in its broadest scope covers the system and methods for optically detecting the presence of blood and/or determining the amount of blood detected during electrosurgery. It is to be understood that the concept is subject to many modifications without departing from the spirit and scope of the claims as recited herein.
Although the subject invention has been described with respect to preferred embodiments, it will be readily apparent to those having ordinary skill in the art to which it appertains that changes and modifications may be made thereto without departing from the spirit or scope of the subject apparatus as defined by the appended claims.
Claims (25)
1. An electrosurgical system comprising:
a handpiece having a proximal end and a distal end from which light energy is emitted therefrom;
at least one electrosurgical electrode on the handpiece and extending from the distal end from which electrosurgical energy is emitted therefrom;
a source of broadband light energy for generating a first light beam having a first wavelength and a second light beam having a second wavelength and transmitting the first and second wavelengths to the distal end via corresponding waveguides;
a source of electrosurgical energy for generating the electrosurgical energy and transmitting the same by at least one electrically conductive element to the electrode;
and an optical blood detector operatively coupled to the handpiece that captures and analyzes reflected light energy characteristics from the first and second wavelengths and utilizes a ratio value between the light energy characteristics of the first and second wavelengths to determine an amount of blood present in proximity to the electrode, wherein the optical blood detector operably communicates with a feedback correction circuit configured to compare the ratio value with a predetermined ratio value to control the amount of electrosurgical energy and to select at least one control mode of the source of electrosurgical energy accordingly, wherein the feedback correction circuit selects a first control mode when the ratio value is below the predetermined threshold value and a second control mode when the ratio value is above the predetermined threshold value.
a handpiece having a proximal end and a distal end from which light energy is emitted therefrom;
at least one electrosurgical electrode on the handpiece and extending from the distal end from which electrosurgical energy is emitted therefrom;
a source of broadband light energy for generating a first light beam having a first wavelength and a second light beam having a second wavelength and transmitting the first and second wavelengths to the distal end via corresponding waveguides;
a source of electrosurgical energy for generating the electrosurgical energy and transmitting the same by at least one electrically conductive element to the electrode;
and an optical blood detector operatively coupled to the handpiece that captures and analyzes reflected light energy characteristics from the first and second wavelengths and utilizes a ratio value between the light energy characteristics of the first and second wavelengths to determine an amount of blood present in proximity to the electrode, wherein the optical blood detector operably communicates with a feedback correction circuit configured to compare the ratio value with a predetermined ratio value to control the amount of electrosurgical energy and to select at least one control mode of the source of electrosurgical energy accordingly, wherein the feedback correction circuit selects a first control mode when the ratio value is below the predetermined threshold value and a second control mode when the ratio value is above the predetermined threshold value.
2. The electrosurgical system of Claim 1, wherein the source of broadband light energy generates light energy in at least one of the visible, near-infrared and infrared light spectrum wavelengths.
3. The electrosurgical system of Claim 1, wherein the source of electrosurgical energy generates electrosurgical energy having at least one of a tissue division and a coagulation output waveform.
4. The electrosurgical system of Claim 1, wherein the broadband light energy characteristics are selected from the group consisting of light intensity level, light scattering effects, and level of fluorescent energy.
5. The electrosurgical system of Claim 1, wherein the optical blood detector is remotely located from the source of broadband light energy and the source of electrosurgical energy.
6. The electrosurgical system of Claim 1, wherein the optical blood detector operatively communicates with the source of broadband light energy via a network.
7. The electrosurgical system of Claim 1, wherein the optical blood detector analyzes reflected light energy characteristics using a technique selected from the group consisting of Near Infrared Spectroscopy, Infrared Spectroscopy, Fluorescence Spectroscopy, Raman Spectroscopy, Photoacoustic Spectroscopy, laser Doppler flowmetry, measurement of light scatter changes, and measurement of polarization changes.
8. The electrosurgical system of Claim 1, wherein the broadband light energy has at least one wavelength suitable for creating an ionized pathway between the distal end and the tissue of a patient, and the electrode is positioned near the ionized pathway such that the electrosurgical energy is conducted along the ionized pathway.
9. The electrosurgical system of Claim 1, wherein the optical blood detector operatively detects the presence of at least one blood vessel in proximity to the distal end of the electrode.
10. The electrosurgical system of Claim 1, wherein the optical blood detector analyzes the broadband light energy characteristics to further determine the ratio value by dividing a first parameter obtained by emitting light energy from the handpiece having a first wavelength from a second parameter obtained by emitting light energy from the handpiece having a second wavelength.
11. The electrosurgical system of Claim 10, wherein the optical blood detector analyzes the broadband light energy characteristics to further determine whether the ratio value is at least one of lower than, approximately equal to, and greater than a predetermined ratio value and for controlling the electrosurgical generator accordingly.
12. The electrosurgical system of Claim 10, wherein the first wavelength is in the range of about 620 to about 700 nanometers and the second wavelength is in the range of about 950 to about 1050 nanometers.
13. The electrosurgical system of Claim 1, wherein the optical blood detector controls the source of electrosurgical energy to variably control the intensity of the current generated by the electrosurgical generator.
14. An electrosurgical system comprising:
means for generating and directing broadband light energy of two different wavelengths onto tissue;
means for generating electrosurgical energy and transmitting the same via an electrode to the tissue;
means for capturing and analyzing characteristics of reflected broadband light energy and utilizing a ratio therebetween to determine an amount of blood present in proximity to the electrode and for controlling the means for generating electrosurgical energy accordingly; and means for selecting a first control mode when the ratio value is below the predetermined threshold value and a second control mode when the ratio value is above a predetermined threshold value.
means for generating and directing broadband light energy of two different wavelengths onto tissue;
means for generating electrosurgical energy and transmitting the same via an electrode to the tissue;
means for capturing and analyzing characteristics of reflected broadband light energy and utilizing a ratio therebetween to determine an amount of blood present in proximity to the electrode and for controlling the means for generating electrosurgical energy accordingly; and means for selecting a first control mode when the ratio value is below the predetermined threshold value and a second control mode when the ratio value is above a predetermined threshold value.
15. The electrosurgical system of Claim 14, wherein the means for generating and directing broadband light energy of two different wavelengths generates light energy in at least one of the visible, near-infrared and infrared light spectrum wavelengths.
16. The electrosurgical system of Claim 14, wherein the means for generating electrosurgical energy generates electrosurgical energy having at least one of a tissue division and a coagulation output waveform.
17. The electrosurgical system of Claim 14, wherein the reflected broadband light energy characteristics are selected from the group consisting of light intensity level, light scattering effects, and level of fluorescent energy.
18. The electrosurgical system of Claim 14, wherein the means for capturing and analyzing is remotely located from the means for generating broadband light energy and the means for generating electrosurgical energy.
19. The electrosurgical system of Claim 14, wherein the means for capturing and analyzing analyzes reflected broadband light energy characteristics using a technique selected from the group consisting of Near Infrared Spectroscopy, Infrared Spectroscopy, Fluorescence Spectroscopy, Raman Spectroscopy, Photoacoustic Spectroscopy, laser Doppler flowmetry, measurement of light scatter changes, and measurement of polarization changes.
20. The electrosurgical system of Claim 14, wherein the broadband light energy has at least one wavelength suitable for creating an ionized pathway between a distal end of the electrode and the tissue, and the electrode is positioned near the ionized pathway such that the electrosurgical energy is conducted along the ionized pathway.
21. The electrosurgical system of Claim 14, wherein the means for capturing and analyzing includes means for detecting the presence of at least one blood vessel in proximity to a distal end of the electrode.
22. The electrosurgical system of Claim 14, wherein the means for capturing and analyzing reflected characteristics of the light energy includes means for determining the ratio value by dividing a first parameter obtained by directing light energy having a first wavelength from a second parameter obtained by directing light energy having a second wavelength.
23. The electrosurgical system of Claim 22, wherein the means for capturing and analyzing reflected characteristics of the light energy further includes means for determining whether the ratio value is at least one of lower than, approximately equal to, and greater than a predetermined ratio value and for controlling the means for generating electrosurgical energy accordingly.
24. The electrosurgical system of Claim 22, wherein the first wavelength is in the range of about 620 to about 700 nanometers and the second wavelength is in the range of about 540 to about 610 nanometers or about 950 to about 1050 nanometers.
25. The electrosurgical system of Claim 14, wherein the means for controlling the source of electrosurgical energy includes means for variably controlling the intensity of the current generated by the electrosurgical generator.
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PCT/US2003/014155 WO2003092520A1 (en) | 2002-05-06 | 2003-05-06 | Blood detector for controlling anesu and method therefor |
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Families Citing this family (186)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20080154257A1 (en) * | 2006-12-22 | 2008-06-26 | Shiva Sharareh | Real-time optoacoustic monitoring with electophysiologic catheters |
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 |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US7137980B2 (en) * | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US6300108B1 (en) * | 1999-07-21 | 2001-10-09 | The Regents Of The University Of California | Controlled electroporation and mass transfer across cell membranes |
US8251986B2 (en) | 2000-08-17 | 2012-08-28 | Angiodynamics, Inc. | Method of destroying tissue cells by eletroporation |
US6795728B2 (en) | 2001-08-17 | 2004-09-21 | Minnesota Medical Physics, Llc | Apparatus and method for reducing subcutaneous fat deposits by electroporation |
US6697670B2 (en) | 2001-08-17 | 2004-02-24 | Minnesota Medical Physics, Llc | Apparatus and method for reducing subcutaneous fat deposits by electroporation with improved comfort of patients |
US6892099B2 (en) * | 2001-02-08 | 2005-05-10 | Minnesota Medical Physics, Llc | Apparatus and method for reducing subcutaneous fat deposits, virtual face lift and body sculpturing by electroporation |
ES2364666T3 (en) | 2001-04-06 | 2011-09-12 | Covidien Ag | SHUTTER AND DIVIDER OF GLASSES WITH NON-CONDUCTIVE BUMPER MEMBERS. |
US6994706B2 (en) | 2001-08-13 | 2006-02-07 | Minnesota Medical Physics, Llc | Apparatus and method for treatment of benign prostatic hyperplasia |
US7130697B2 (en) * | 2002-08-13 | 2006-10-31 | Minnesota Medical Physics Llc | Apparatus and method for the treatment of benign prostatic hyperplasia |
USRE42016E1 (en) | 2001-08-13 | 2010-12-28 | Angiodynamics, Inc. | Apparatus and method for the treatment of benign prostatic hyperplasia |
ES2289307T3 (en) | 2002-05-06 | 2008-02-01 | Covidien Ag | BLOOD DETECTOR TO CONTROL AN ELECTROCHIRURGICAL UNIT. |
US7931649B2 (en) | 2002-10-04 | 2011-04-26 | Tyco Healthcare Group Lp | Vessel sealing instrument with electrical cutting mechanism |
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 |
US7753909B2 (en) | 2003-05-01 | 2010-07-13 | Covidien Ag | Electrosurgical instrument which reduces thermal damage to adjacent tissue |
AU2004235739B2 (en) | 2003-05-01 | 2010-06-17 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
EP1675499B1 (en) | 2003-10-23 | 2011-10-19 | Covidien AG | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
AU2003286644B2 (en) | 2003-10-23 | 2009-09-10 | 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 |
US7367976B2 (en) | 2003-11-17 | 2008-05-06 | Sherwood Services Ag | Bipolar forceps having monopolar extension |
US7131970B2 (en) | 2003-11-19 | 2006-11-07 | Sherwood Services Ag | Open vessel sealing instrument with cutting mechanism |
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 |
US8298222B2 (en) * | 2003-12-24 | 2012-10-30 | The Regents Of The University Of California | Electroporation to deliver chemotherapeutics and enhance tumor regression |
AU2004311842C1 (en) | 2003-12-24 | 2011-01-06 | The Regents Of The University Of California | Tissue ablation with irreversible electroporation |
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 |
JP4443278B2 (en) * | 2004-03-26 | 2010-03-31 | テルモ株式会社 | Catheter with expansion body |
US7628786B2 (en) * | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
JP5090176B2 (en) * | 2004-11-17 | 2012-12-05 | バイオセンス・ウエブスター・インコーポレーテツド | Real-time evaluation system for tissue ablation |
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 |
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 |
US8114070B2 (en) * | 2005-06-24 | 2012-02-14 | Angiodynamics, Inc. | Methods and systems for treating BPH using electroporation |
US20060293730A1 (en) | 2005-06-24 | 2006-12-28 | Boris Rubinsky | Methods and systems for treating restenosis sites using electroporation |
US20060293725A1 (en) * | 2005-06-24 | 2006-12-28 | Boris Rubinsky | Methods and systems for treating fatty tissue sites using electroporation |
US20060293731A1 (en) * | 2005-06-24 | 2006-12-28 | Boris Rubinsky | Methods and systems for treating tumors using electroporation |
WO2007004831A1 (en) * | 2005-06-30 | 2007-01-11 | Lg Electronics Inc. | Method and apparatus for encoding and decoding an audio signal |
US7879035B2 (en) | 2005-09-30 | 2011-02-01 | Covidien Ag | Insulating boot for electrosurgical forceps |
US7722607B2 (en) | 2005-09-30 | 2010-05-25 | Covidien Ag | In-line vessel sealer and divider |
US7846161B2 (en) | 2005-09-30 | 2010-12-07 | Covidien Ag | Insulating boot for electrosurgical forceps |
CA2561034C (en) | 2005-09-30 | 2014-12-09 | Sherwood Services Ag | Flexible endoscopic catheter with an end effector for coagulating and transfecting tissue |
US7922953B2 (en) | 2005-09-30 | 2011-04-12 | Covidien Ag | Method for manufacturing an end effector assembly |
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 |
US20070156135A1 (en) * | 2006-01-03 | 2007-07-05 | Boris Rubinsky | System and methods for treating atrial fibrillation using electroporation |
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 |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | 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 |
US20070173802A1 (en) * | 2006-01-24 | 2007-07-26 | Keppel David S | Method and system for transmitting data across patient isolation barrier |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
EP1810634B8 (en) | 2006-01-24 | 2015-06-10 | Covidien AG | System for tissue sealing |
CA2574934C (en) | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US7651493B2 (en) | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US7648499B2 (en) * | 2006-03-21 | 2010-01-19 | Covidien Ag | System and method for generating radio frequency energy |
US7651492B2 (en) * | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US8753334B2 (en) * | 2006-05-10 | 2014-06-17 | Covidien Ag | System and method for reducing leakage current in an electrosurgical generator |
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 |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
EP2076313A4 (en) * | 2006-10-16 | 2012-07-25 | Univ California | Gels with predetermined conductivity used in irreversible electroporation of tissue |
US20080132884A1 (en) * | 2006-12-01 | 2008-06-05 | Boris Rubinsky | Systems for treating tissue sites using electroporation |
US8690864B2 (en) * | 2007-03-09 | 2014-04-08 | Covidien Lp | System and method for controlling tissue treatment |
US20080249523A1 (en) * | 2007-04-03 | 2008-10-09 | Tyco Healthcare Group Lp | Controller for flexible tissue ablation procedures |
US8777941B2 (en) | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
AU2008271014B2 (en) * | 2007-06-29 | 2014-03-20 | Covidien Lp | Method and system for monitoring tissue during an electrosurgical procedure |
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 |
US8512332B2 (en) | 2007-09-21 | 2013-08-20 | Covidien Lp | Real-time arc control in electrosurgical generators |
CN101909516B (en) * | 2007-12-28 | 2012-07-04 | 皇家飞利浦电子股份有限公司 | Tissue ablation device with photoacoustic lesion formation feedback |
US20100004623A1 (en) * | 2008-03-27 | 2010-01-07 | Angiodynamics, Inc. | Method for Treatment of Complications Associated with Arteriovenous Grafts and Fistulas Using Electroporation |
US20090247933A1 (en) * | 2008-03-27 | 2009-10-01 | The Regents Of The University Of California; Angiodynamics, Inc. | Balloon catheter method for reducing restenosis via irreversible electroporation |
US8257349B2 (en) * | 2008-03-28 | 2012-09-04 | Tyco Healthcare Group Lp | Electrosurgical apparatus with predictive RF source control |
US9283051B2 (en) | 2008-04-29 | 2016-03-15 | Virginia Tech Intellectual Properties, Inc. | System and method for estimating a treatment volume for administering electrical-energy based therapies |
US11254926B2 (en) | 2008-04-29 | 2022-02-22 | Virginia Tech Intellectual Properties, Inc. | Devices and methods for high frequency electroporation |
US10702326B2 (en) | 2011-07-15 | 2020-07-07 | Virginia Tech Intellectual Properties, Inc. | Device and method for electroporation based treatment of stenosis of a tubular body part |
US10238447B2 (en) | 2008-04-29 | 2019-03-26 | Virginia Tech Intellectual Properties, Inc. | System and method for ablating a tissue site by electroporation with real-time monitoring of treatment progress |
US10117707B2 (en) | 2008-04-29 | 2018-11-06 | Virginia Tech Intellectual Properties, Inc. | System and method for estimating tissue heating of a target ablation zone for electrical-energy based therapies |
US10245098B2 (en) | 2008-04-29 | 2019-04-02 | Virginia Tech Intellectual Properties, Inc. | Acute blood-brain barrier disruption using electrical energy based therapy |
US10272178B2 (en) | 2008-04-29 | 2019-04-30 | Virginia Tech Intellectual Properties Inc. | Methods for blood-brain barrier disruption using electrical energy |
US9867652B2 (en) | 2008-04-29 | 2018-01-16 | Virginia Tech Intellectual Properties, Inc. | Irreversible electroporation using tissue vasculature to treat aberrant cell masses or create tissue scaffolds |
US8926606B2 (en) * | 2009-04-09 | 2015-01-06 | Virginia Tech Intellectual Properties, Inc. | Integration of very short electric pulses for minimally to noninvasive electroporation |
US9198733B2 (en) | 2008-04-29 | 2015-12-01 | Virginia Tech Intellectual Properties, Inc. | Treatment planning for electroporation-based therapies |
US8992517B2 (en) | 2008-04-29 | 2015-03-31 | Virginia Tech Intellectual Properties Inc. | Irreversible electroporation to treat aberrant cell masses |
CA2722296A1 (en) | 2008-04-29 | 2009-11-05 | Virginia Tech Intellectual Properties, Inc. | Irreversible electroporation to create tissue scaffolds |
US11272979B2 (en) | 2008-04-29 | 2022-03-15 | Virginia Tech Intellectual Properties, Inc. | System and method for estimating tissue heating of a target ablation zone for electrical-energy based therapies |
WO2009137800A2 (en) * | 2008-05-09 | 2009-11-12 | Angiodynamics, Inc. | Electroporation device and method |
CN104939806B (en) | 2008-05-20 | 2021-12-10 | 大学健康网络 | Apparatus and method for fluorescence-based imaging and monitoring |
US8226639B2 (en) | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
US9173704B2 (en) * | 2008-06-20 | 2015-11-03 | Angiodynamics, Inc. | Device and method for the ablation of fibrin sheath formation on a venous catheter |
US9681909B2 (en) * | 2008-06-23 | 2017-06-20 | Angiodynamics, Inc. | Treatment devices and methods |
US9603652B2 (en) * | 2008-08-21 | 2017-03-28 | Covidien Lp | Electrosurgical instrument including a sensor |
US8142473B2 (en) | 2008-10-03 | 2012-03-27 | Tyco Healthcare Group Lp | Method of transferring rotational motion in an articulating surgical instrument |
US8016827B2 (en) | 2008-10-09 | 2011-09-13 | Tyco Healthcare Group Lp | Apparatus, system, and method for performing an electrosurgical procedure |
US8690872B2 (en) * | 2008-11-14 | 2014-04-08 | Prash Jayaraj | Surgical pencil enabling suction |
US20100125172A1 (en) * | 2008-11-14 | 2010-05-20 | Prash Jayaraj | Surgical pencil providing an illuminated surgical site |
US9907621B2 (en) | 2008-11-14 | 2018-03-06 | Prash Jayaraj | Surgical pencil |
US20100152725A1 (en) * | 2008-12-12 | 2010-06-17 | Angiodynamics, Inc. | Method and system for tissue treatment utilizing irreversible electroporation and thermal track coagulation |
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 |
WO2010085765A2 (en) * | 2009-01-23 | 2010-07-29 | Moshe Meir H | Therapeutic energy delivery device with rotational mechanism |
US8231603B2 (en) * | 2009-02-10 | 2012-07-31 | Angiodynamics, Inc. | Irreversible electroporation and tissue regeneration |
US8319953B2 (en) * | 2009-03-10 | 2012-11-27 | Spectra Tracker LLC | Method and device for spectrally detecting presence of blood |
US11382681B2 (en) | 2009-04-09 | 2022-07-12 | Virginia Tech Intellectual Properties, Inc. | Device and methods for delivery of high frequency electrical pulses for non-thermal ablation |
US11638603B2 (en) | 2009-04-09 | 2023-05-02 | Virginia Tech Intellectual Properties, Inc. | Selective modulation of intracellular effects of cells using pulsed electric fields |
US8187273B2 (en) | 2009-05-07 | 2012-05-29 | Tyco Healthcare Group Lp | Apparatus, system, and method for performing an electrosurgical procedure |
USD630321S1 (en) | 2009-05-08 | 2011-01-04 | Angio Dynamics, Inc. | Probe handle |
WO2010138919A2 (en) | 2009-05-28 | 2010-12-02 | Angiodynamics, Inc. | System and method for synchronizing energy delivery to the cardiac rhythm |
US9895189B2 (en) | 2009-06-19 | 2018-02-20 | Angiodynamics, Inc. | Methods of sterilization and treating infection using irreversible electroporation |
US8246618B2 (en) | 2009-07-08 | 2012-08-21 | Tyco Healthcare Group Lp | Electrosurgical jaws with offset knife |
US8983567B1 (en) | 2009-08-01 | 2015-03-17 | Nuvasive, Inc. | Systems and methods for vessel avoidance during spine surgery |
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 |
US8112871B2 (en) | 2009-09-28 | 2012-02-14 | Tyco Healthcare Group Lp | Method for manufacturing electrosurgical seal plates |
US8652125B2 (en) | 2009-09-28 | 2014-02-18 | Covidien Lp | Electrosurgical generator user interface |
US20110118732A1 (en) | 2009-11-19 | 2011-05-19 | The Regents Of The University Of California | Controlled irreversible electroporation |
DE102010015899B4 (en) * | 2010-02-04 | 2022-07-28 | Erbe Elektromedizin Gmbh | Electrosurgical assembly and electrosurgical instrument |
US8961504B2 (en) | 2010-04-09 | 2015-02-24 | Covidien Lp | Optical hydrology arrays and system and method for monitoring water displacement during treatment of patient tissue |
US9700368B2 (en) | 2010-10-13 | 2017-07-11 | Angiodynamics, Inc. | System and method for electrically ablating tissue of a patient |
WO2012088149A2 (en) | 2010-12-20 | 2012-06-28 | Virginia Tech Intellectual Properties, Inc. | High-frequency electroporation for cancer therapy |
US9113940B2 (en) | 2011-01-14 | 2015-08-25 | Covidien Lp | Trigger lockout and kickback mechanism for surgical instruments |
US9646375B2 (en) | 2011-07-09 | 2017-05-09 | Gauss Surgical, Inc. | Method for setting a blood transfusion parameter |
US9870625B2 (en) | 2011-07-09 | 2018-01-16 | Gauss Surgical, Inc. | Method for estimating a quantity of a blood component in a fluid receiver and corresponding error |
US10426356B2 (en) | 2011-07-09 | 2019-10-01 | Gauss Surgical, Inc. | Method for estimating a quantity of a blood component in a fluid receiver and corresponding error |
US8792693B2 (en) | 2011-07-09 | 2014-07-29 | Gauss Surgical | System and method for estimating extracorporeal blood volume in a physical sample |
CN104066368B (en) | 2011-09-22 | 2017-02-22 | 乔治华盛顿大学 | Systems and methods for visualizing ablated tissue |
US9078665B2 (en) | 2011-09-28 | 2015-07-14 | Angiodynamics, Inc. | Multiple treatment zone ablation probe |
USD680220S1 (en) | 2012-01-12 | 2013-04-16 | Coviden IP | Slider handle for laparoscopic device |
US9861427B2 (en) | 2012-01-20 | 2018-01-09 | Koninklijke Philips N.V. | Electro-surgical system, an electro-surgical device, and a method for operating an electro-surgical system |
US9414881B2 (en) | 2012-02-08 | 2016-08-16 | Angiodynamics, Inc. | System and method for increasing a target zone for electrical ablation |
US11399898B2 (en) | 2012-03-06 | 2022-08-02 | Briteseed, Llc | User interface for a system used to determine tissue or artifact characteristics |
US9375249B2 (en) | 2012-05-11 | 2016-06-28 | Covidien Lp | System and method for directing energy to tissue |
EP3576018B1 (en) | 2012-05-14 | 2022-03-16 | Gauss Surgical, Inc. | System and methods for managing blood loss of a patient |
EP2850559B1 (en) | 2012-05-14 | 2021-02-24 | Gauss Surgical, Inc. | System and method for estimating a quantity of a blood component in a fluid canister |
US9529025B2 (en) | 2012-06-29 | 2016-12-27 | Covidien Lp | Systems and methods for measuring the frequency of signals generated by high frequency medical devices |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9655670B2 (en) | 2013-07-29 | 2017-05-23 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
JP6737705B2 (en) | 2013-11-14 | 2020-08-12 | ザ・ジョージ・ワシントン・ユニバーシティThe George Washingtonuniversity | Method of operating system for determining depth of injury site and system for generating images of heart tissue |
US20150141847A1 (en) | 2013-11-20 | 2015-05-21 | The George Washington University | Systems and methods for hyperspectral analysis of cardiac tissue |
US10166321B2 (en) | 2014-01-09 | 2019-01-01 | Angiodynamics, Inc. | High-flow port and infusion needle systems |
US10251600B2 (en) | 2014-03-25 | 2019-04-09 | Briteseed, Llc | Vessel detector and method of detection |
WO2015161003A1 (en) | 2014-04-15 | 2015-10-22 | Gauss Surgical, Inc. | Method for estimating a quantity of a blood component in a fluid canister |
US9824441B2 (en) | 2014-04-15 | 2017-11-21 | Gauss Surgical, Inc. | Method for estimating a quantity of a blood component in a fluid canister |
EP3143124A4 (en) | 2014-05-12 | 2018-01-17 | Virginia Tech Intellectual Properties, Inc. | Selective modulation of intracellular effects of cells using pulsed electric fields |
US10438356B2 (en) | 2014-07-24 | 2019-10-08 | University Health Network | Collection and analysis of data for diagnostic purposes |
KR102499045B1 (en) * | 2014-11-03 | 2023-02-10 | 더 조지 워싱턴 유니버시티 | Systems and methods for lesion assessment |
JP6771731B2 (en) * | 2014-11-03 | 2020-10-21 | 460メディカル・インコーポレイテッド460Medical, Inc. | Contact evaluation system and method |
WO2016100325A1 (en) | 2014-12-15 | 2016-06-23 | Virginia Tech Intellectual Properties, Inc. | Devices, systems, and methods for real-time monitoring of electrophysical effects during tissue treatment |
WO2016117106A1 (en) * | 2015-01-23 | 2016-07-28 | オリンパス株式会社 | Surgical treatment device |
EP4000509B1 (en) | 2015-02-19 | 2023-08-30 | Briteseed, LLC | Surgical system for determining vessel size |
WO2016134327A1 (en) | 2015-02-19 | 2016-08-25 | Briteseed Llc | System for determining vessel size using light absorption |
JP6758308B2 (en) | 2015-02-25 | 2020-09-23 | アウトセンス ダイアグノスティクス リミテッド | Analysis of human excrement |
WO2016151787A1 (en) | 2015-03-25 | 2016-09-29 | オリンパス株式会社 | Blood flow measuring method for blood vessel identification |
WO2016171238A1 (en) * | 2015-04-23 | 2016-10-27 | オリンパス株式会社 | Surgical treatment device |
US10555675B2 (en) | 2015-05-15 | 2020-02-11 | Gauss Surgical, Inc. | Method for projecting blood loss of a patient during a surgery |
WO2016187072A1 (en) | 2015-05-15 | 2016-11-24 | Gauss Surgical, Inc. | Methods and systems for characterizing fluids from a patient |
US11504037B2 (en) | 2015-05-15 | 2022-11-22 | Gauss Surgical, Inc. | Systems and methods for assessing fluids from a patient |
US10779904B2 (en) | 2015-07-19 | 2020-09-22 | 460Medical, Inc. | Systems and methods for lesion formation and assessment |
WO2017031712A1 (en) | 2015-08-26 | 2017-03-02 | Covidien Lp | Electrosurgical end effector assemblies and electrosurgical forceps configured to reduce thermal spread |
EP3359021B1 (en) | 2015-10-08 | 2019-07-31 | Briteseed, LLC | System for determining vessel size |
US10213250B2 (en) | 2015-11-05 | 2019-02-26 | Covidien Lp | Deployment and safety mechanisms for surgical instruments |
JP6968427B2 (en) | 2015-12-23 | 2021-11-17 | ガウス サージカル, インコーポレイテッドGauss Surgical, Inc. | Systems and methods for estimating the amount of blood components in a volume of fluid |
EP3394831A4 (en) | 2015-12-23 | 2019-08-07 | Gauss Surgical, Inc. | Method for estimating blood component quantities in surgical textiles |
EP4026489A1 (en) | 2016-08-30 | 2022-07-13 | Briteseed, LLC | System and method for determining vessel size with angular distortion compensation |
EP3506834B1 (en) | 2016-08-30 | 2021-08-04 | Outsense Diagnostics Ltd. | Bodily emission analysis |
US10905492B2 (en) | 2016-11-17 | 2021-02-02 | Angiodynamics, Inc. | Techniques for irreversible electroporation using a single-pole tine-style internal device communicating with an external surface electrode |
EP3563343A4 (en) | 2017-01-02 | 2020-08-19 | Gauss Surgical, Inc. | Tracking surgical items with prediction of duplicate imaging of items |
US11229368B2 (en) | 2017-01-13 | 2022-01-25 | Gauss Surgical, Inc. | Fluid loss estimation based on weight of medical items |
US20180317995A1 (en) * | 2017-05-02 | 2018-11-08 | C. R. Bard, Inc. | Systems And Methods Of An Electrohemostatic Renal Sheath |
EP3449815A1 (en) * | 2017-08-28 | 2019-03-06 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Monitoring of tissue coagulation by optical reflectance signals |
ES2898312T3 (en) | 2017-09-05 | 2022-03-07 | Briteseed Llc | System and method used to determine tissue and/or artifact characteristics |
US11607537B2 (en) | 2017-12-05 | 2023-03-21 | Virginia Tech Intellectual Properties, Inc. | Method for treating neurological disorders, including tumors, with electroporation |
US11696777B2 (en) | 2017-12-22 | 2023-07-11 | Briteseed, Llc | Compact system used to determine tissue or artifact characteristics |
US11311329B2 (en) | 2018-03-13 | 2022-04-26 | Virginia Tech Intellectual Properties, Inc. | Treatment planning for immunotherapy based treatments using non-thermal ablation techniques |
US11925405B2 (en) | 2018-03-13 | 2024-03-12 | Virginia Tech Intellectual Properties, Inc. | Treatment planning system for immunotherapy enhancement via non-thermal ablation |
US11950835B2 (en) | 2019-06-28 | 2024-04-09 | Virginia Tech Intellectual Properties, Inc. | Cycled pulsing to mitigate thermal damage for multi-electrode irreversible electroporation therapy |
US20210236189A1 (en) * | 2020-01-30 | 2021-08-05 | Kester Julian Batchelor | Adaptive blend of electrosurgical cutting and coagulation |
US11931098B2 (en) * | 2020-02-19 | 2024-03-19 | Boston Scientific Medical Device Limited | System and method for carrying out a medical procedure |
DE102021101410A1 (en) | 2021-01-22 | 2022-07-28 | Olympus Winter & Ibe Gmbh | Method and system for controlling a surgical RF generator and software program product |
Family Cites Families (581)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE179607C (en) | 1906-11-12 | |||
DE390937C (en) | 1922-10-13 | 1924-03-03 | Adolf Erb | Device for internal heating of furnace furnaces for hardening, tempering, annealing, quenching and melting |
US1841968A (en) | 1924-08-16 | 1932-01-19 | William J Cameron | Radio-surgical apparatus |
US1863118A (en) | 1927-10-31 | 1932-06-14 | Liebel Flarsheim Co | Surgeon's instrument |
US1813902A (en) | 1928-01-18 | 1931-07-14 | Liebel Flarsheim Co | Electrosurgical apparatus |
US1787709A (en) | 1928-06-11 | 1931-01-06 | Wappler Frederick Charles | High-frequency surgical cutting device |
US1945667A (en) | 1929-12-11 | 1934-02-06 | Gen Electric | Supervisory system |
GB607850A (en) | 1946-04-01 | 1948-09-06 | William George Curwain | Electric connectors |
US2849611A (en) | 1955-05-16 | 1958-08-26 | Honeywell Regulator Co | Electrical oscillator circuit |
US2827056A (en) | 1955-06-21 | 1958-03-18 | Thomas H Ballantine Jr | Electrode discharge control for surgical apparatus |
BE556940A (en) | 1956-04-26 | |||
GB855459A (en) | 1958-04-11 | 1960-11-30 | Keeler Optical Products Ltd | Improvements in or relating to electro-surgical apparatus |
US2982881A (en) | 1958-05-22 | 1961-05-02 | Robert W Reich | Portable light source |
DE1099658B (en) | 1959-04-29 | 1961-02-16 | Siemens Reiniger Werke Ag | Automatic switch-on device for high-frequency surgical devices |
GB902775A (en) | 1959-05-16 | 1962-08-09 | Kathleen Zilla Rumble | Improvements in or relating to electrical plugs |
US3089496A (en) | 1959-08-19 | 1963-05-14 | Code Inc | Control system for surgical apparatus |
US3163165A (en) | 1960-09-12 | 1964-12-29 | Islkawa Humio | Uterotube-closing instrument |
FR1275415A (en) | 1960-09-26 | 1961-11-10 | Device for detecting disturbances for electrical installations, in particular electrosurgery | |
DE1139927B (en) | 1961-01-03 | 1962-11-22 | Friedrich Laber | High-frequency surgical device |
DE1149832C2 (en) | 1961-02-25 | 1977-10-13 | Siemens AG, 1000 Berlin und 8000 München | HIGH FREQUENCY SURGICAL EQUIPMENT |
FR1347865A (en) | 1962-11-22 | 1964-01-04 | Improvements to diathermo-coagulation devices | |
US3252052A (en) | 1963-08-23 | 1966-05-17 | Jacuzzi Bros Inc | Leakage detection and control circuit |
DE1264513C2 (en) | 1963-11-29 | 1973-01-25 | Texas Instruments Inc | REFERENCE POTENTIAL FREE DC DIFFERENCE AMPLIFIER |
US3478744A (en) | 1964-12-30 | 1969-11-18 | Harry Leiter | Surgical apparatus |
US3486115A (en) | 1965-04-01 | 1969-12-23 | Donald J Anderson | Means for measuring the power in an electrical circuit |
US3439680A (en) | 1965-04-12 | 1969-04-22 | Univ Northwestern | Surgical instrument for cataract removal |
FR1494065A (en) | 1965-05-10 | 1967-09-08 | Const De Vaux Andigny Atel | Detector-amplifier for low level signals and devices with application |
US3495584A (en) | 1965-06-03 | 1970-02-17 | Gen Electric | Lead failure detection circuit for a cardiac monitor |
US3436563A (en) | 1965-12-27 | 1969-04-01 | Bell Telephone Labor Inc | Pulse driver with linear current rise |
US3471770A (en) | 1966-03-30 | 1969-10-07 | Ibm | Pulsed current generating circuits |
US3461874A (en) | 1966-08-10 | 1969-08-19 | Miguel Martinez | Electric cautery |
GB1169706A (en) | 1966-09-29 | 1969-11-05 | English Electric Co Ltd | An Electrical Fault Detector |
US3391351A (en) | 1966-11-21 | 1968-07-02 | Bell Telephone Labor Inc | Circuits using a transistor operated into second breakdown region |
US3439253A (en) | 1967-04-05 | 1969-04-15 | R I Phelon Inc | Alternator rectifier and voltage regulator |
NL145136C (en) | 1967-07-25 | 1900-01-01 | ||
US3513353A (en) | 1967-08-17 | 1970-05-19 | John L Lansch | Voltage monitoring circuit |
US3551786A (en) | 1967-12-05 | 1970-12-29 | Omark Industries Inc | Circuit for adjustably increasing or decreasing the charge on a capacitor |
US3562623A (en) | 1968-07-16 | 1971-02-09 | Hughes Aircraft Co | Circuit for reducing stray capacity effects in transformer windings |
US3514689A (en) | 1968-08-21 | 1970-05-26 | United Aircraft Corp | Three-phase ac-operated dc power supply |
US3642008A (en) * | 1968-09-25 | 1972-02-15 | Medical Plastics Inc | Ground electrode and test circuit |
US3601126A (en) * | 1969-01-08 | 1971-08-24 | Electro Medical Systems Inc | High frequency electrosurgical apparatus |
US3571644A (en) | 1969-01-27 | 1971-03-23 | Heurtey Sa | High frequency oscillator for inductive heating |
US3595221A (en) | 1969-03-04 | 1971-07-27 | Matburn Holdings Ltd | Endoscopic having illumination supply unit |
US3611053A (en) | 1969-10-10 | 1971-10-05 | Farmer Electric Products Co In | Intrinsically safe circuit |
US3662151A (en) | 1969-11-17 | 1972-05-09 | Codman & Shurtleff | Cautery |
US3675655A (en) | 1970-02-04 | 1972-07-11 | Electro Medical Systems Inc | Method and apparatus for high frequency electric surgery |
DE7023433U (en) | 1970-06-23 | 1974-07-11 | Siemens Ag | Handpiece for high frequency electrodes |
US3826263A (en) | 1970-08-13 | 1974-07-30 | R Shaw | Electrically heated surgical cutting instrument |
US3683923A (en) | 1970-09-25 | 1972-08-15 | Valleylab Inc | Electrosurgery safety circuit |
US3641422A (en) | 1970-10-01 | 1972-02-08 | Robert P Farnsworth | Wide band boost regulator power supply |
US3697808A (en) | 1970-11-23 | 1972-10-10 | Safety Co The | System for monitoring chassis potential and ground continuity |
US3693613A (en) | 1970-12-09 | 1972-09-26 | Cavitron Corp | Surgical handpiece and flow control system for use therewith |
FR2123896A5 (en) | 1971-02-04 | 1972-09-15 | Radiotechnique Compelec | |
US3699967A (en) | 1971-04-30 | 1972-10-24 | Valleylab Inc | Electrosurgical generator |
US3766434A (en) | 1971-08-09 | 1973-10-16 | S Sherman | Safety power distribution system |
US3784842A (en) | 1972-02-03 | 1974-01-08 | F Kremer | Body current activated circuit breaker |
US3848600A (en) | 1972-02-03 | 1974-11-19 | Ndm Corp | Indifferent electrode in electrosurgical procedures and method of use |
US3828768A (en) | 1972-07-13 | 1974-08-13 | Physiological Electronics Corp | Method and apparatus for detecting cardiac arrhythmias |
US3783340A (en) | 1972-09-07 | 1974-01-01 | Biotek Instr Inc | Ground safe system |
US3768482A (en) | 1972-10-10 | 1973-10-30 | R Shaw | Surgical cutting instrument having electrically heated cutting edge |
US3812858A (en) | 1972-10-24 | 1974-05-28 | Sybron Corp | Dental electrosurgical unit |
US3885569A (en) | 1972-11-21 | 1975-05-27 | Birtcher Corp | Electrosurgical unit |
US3801800A (en) | 1972-12-26 | 1974-04-02 | Valleylab Inc | Isolating switching circuit for an electrosurgical generator |
JPS5241593B2 (en) | 1972-12-29 | 1977-10-19 | ||
US3801766A (en) | 1973-01-22 | 1974-04-02 | Valleylab Inc | Switching means for an electro-surgical device including particular contact means and particular printed-circuit mounting means |
US3971365A (en) | 1973-02-12 | 1976-07-27 | Beckman Instruments, Inc. | Bioelectrical impedance measuring system |
US3815015A (en) | 1973-02-20 | 1974-06-04 | Gen Electric | Transformer-diode isolated circuits for high voltage power supplies |
US3963030A (en) | 1973-04-16 | 1976-06-15 | Valleylab, Inc. | Signal generating device and method for producing coagulation electrosurgical current |
GB1480736A (en) | 1973-08-23 | 1977-07-20 | Matburn Ltd | Electrodiathermy apparatus |
US3933157A (en) | 1973-10-23 | 1976-01-20 | Aktiebolaget Stille-Werner | Test and control device for electrosurgical apparatus |
US3875945A (en) | 1973-11-02 | 1975-04-08 | Demetron Corp | Electrosurgery instrument |
US3870047A (en) | 1973-11-12 | 1975-03-11 | Dentsply Res & Dev | Electrosurgical device |
DE2455174A1 (en) | 1973-11-21 | 1975-05-22 | Termiflex Corp | INPUT / OUTPUT DEVICE FOR DATA EXCHANGE WITH DATA PROCESSING DEVICES |
US3901216A (en) | 1973-12-20 | 1975-08-26 | Milton R Felger | Method for measuring endodontic working lengths |
US3897788A (en) | 1974-01-14 | 1975-08-05 | Valleylab Inc | Transformer coupled power transmitting and isolated switching circuit |
DE2407559C3 (en) | 1974-02-16 | 1982-01-21 | Dornier System Gmbh, 7990 Friedrichshafen | Heat probe |
US3905373A (en) | 1974-04-18 | 1975-09-16 | Dentsply Res & Dev | Electrosurgical device |
US3913583A (en) | 1974-06-03 | 1975-10-21 | Sybron Corp | Control circuit for electrosurgical units |
JPS5710740B2 (en) | 1974-06-17 | 1982-02-27 | ||
US3923063A (en) | 1974-07-15 | 1975-12-02 | Sybron Corp | Pulse control circuit for electrosurgical units |
US4024467A (en) | 1974-07-15 | 1977-05-17 | Sybron Corporation | Method for controlling power during electrosurgery |
US3952748A (en) | 1974-07-18 | 1976-04-27 | Minnesota Mining And Manufacturing Company | Electrosurgical system providing a fulguration current |
US3946738A (en) | 1974-10-24 | 1976-03-30 | Newton David W | Leakage current cancelling circuit for use with electrosurgical instrument |
US4231372A (en) | 1974-11-04 | 1980-11-04 | Valleylab, Inc. | Safety monitoring circuit for electrosurgical unit |
US3964487A (en) * | 1974-12-09 | 1976-06-22 | The Birtcher Corporation | Uncomplicated load-adapting electrosurgical cutting generator |
US4237887A (en) | 1975-01-23 | 1980-12-09 | Valleylab, Inc. | Electrosurgical device |
DE2504280C3 (en) | 1975-02-01 | 1980-08-28 | Hans Heinrich Prof. Dr. 8035 Gauting Meinke | Device for cutting and / or coagulating human tissue with high frequency current |
US3978393A (en) * | 1975-04-21 | 1976-08-31 | Burroughs Corporation | High efficiency switching regulator |
US4005714A (en) | 1975-05-03 | 1977-02-01 | Richard Wolf Gmbh | Bipolar coagulation forceps |
CA1064581A (en) | 1975-06-02 | 1979-10-16 | Stephen W. Andrews | Pulse control circuit and method for electrosurgical units |
US4074719A (en) | 1975-07-12 | 1978-02-21 | Kurt Semm | Method of and device for causing blood coagulation |
DE2540968C2 (en) | 1975-09-13 | 1982-12-30 | Erbe Elektromedizin GmbH, 7400 Tübingen | Device for switching on the coagulation current of a bipolar coagulation forceps |
SE399495B (en) * | 1975-11-03 | 1978-02-13 | Lindmark Magnus C W | SWITCHING POWER SUPPLY UNIT FOR CONVERTING DC DIRECTION TO AC VOLTAGE |
JPS5275882A (en) | 1975-12-20 | 1977-06-25 | Olympus Optical Co | High frequency electric knife |
US4051855A (en) | 1976-02-06 | 1977-10-04 | Ipco Hospital Supply Corporation, Whaledent International Division | Electrosurgical unit |
US4041952A (en) | 1976-03-04 | 1977-08-16 | Valleylab, Inc. | Electrosurgical forceps |
US4063557A (en) | 1976-04-01 | 1977-12-20 | Cavitron Corporation | Ultrasonic aspirator |
US4191188A (en) | 1976-05-07 | 1980-03-04 | Macan Engineering & Manufacturing Company, Inc. | Variable crest factor high frequency generator apparatus |
US4092986A (en) * | 1976-06-14 | 1978-06-06 | Ipco Hospital Supply Corporation (Whaledent International Division) | Constant output electrosurgical unit |
JPS5324173U (en) | 1976-08-09 | 1978-03-01 | ||
US4094320A (en) | 1976-09-09 | 1978-06-13 | Valleylab, Inc. | Electrosurgical safety circuit and method of using same |
US4171700A (en) | 1976-10-13 | 1979-10-23 | Erbe Elektromedizin Gmbh & Co. Kg | High-frequency surgical apparatus |
US4114604A (en) * | 1976-10-18 | 1978-09-19 | Shaw Robert F | Catheter oximeter apparatus and method |
US4126137A (en) | 1977-01-21 | 1978-11-21 | Minnesota Mining And Manufacturing Company | Electrosurgical unit |
US4121590A (en) | 1977-03-14 | 1978-10-24 | Dentsply Research And Development Corporation | System for monitoring integrity of a patient return circuit |
US4123673A (en) | 1977-03-14 | 1978-10-31 | Dentsply Research And Development Corporation | Control circuit for an electrical device |
FR2390968A1 (en) | 1977-05-16 | 1978-12-15 | Skovajsa Joseph | Local acupuncture treatment appts. - has oblong head with end aperture and contains laser diode unit (NL 20.11.78) |
FR2391588A1 (en) | 1977-05-18 | 1978-12-15 | Satelec Soc | HIGH FREQUENCY VOLTAGE GENERATOR |
SU727201A2 (en) | 1977-11-02 | 1980-04-15 | Киевский Научно-Исследовательский Институт Нейрохирургии | Electric surgical apparatus |
US4200104A (en) | 1977-11-17 | 1980-04-29 | Valleylab, Inc. | Contact area measurement apparatus for use in electrosurgery |
US4188927A (en) * | 1978-01-12 | 1980-02-19 | Valleylab, Inc. | Multiple source electrosurgical generator |
DE2803275C3 (en) | 1978-01-26 | 1980-09-25 | Aesculap-Werke Ag Vormals Jetter & Scheerer, 7200 Tuttlingen | Remote switching device for switching a monopolar HF surgical device |
US4196734A (en) | 1978-02-16 | 1980-04-08 | Valleylab, Inc. | Combined electrosurgery/cautery system and method |
US4237891A (en) | 1978-05-17 | 1980-12-09 | Agri-Bio Corporation | Apparatus for removing appendages from avian species by using electrodes to induce a current through the appendage |
US4200105A (en) | 1978-05-26 | 1980-04-29 | Dentsply Research & Development Corp. | Electrosurgical safety circuit |
DE2823291A1 (en) | 1978-05-27 | 1979-11-29 | Rainer Ing Grad Koch | Coagulation instrument automatic HF switching circuit - has first lead to potentiometer and second to transistor base |
US4232676A (en) | 1978-11-16 | 1980-11-11 | Corning Glass Works | Surgical cutting instrument |
US4311154A (en) | 1979-03-23 | 1982-01-19 | Rca Corporation | Nonsymmetrical bulb applicator for hyperthermic treatment of the body |
US4321926A (en) | 1979-04-16 | 1982-03-30 | Roge Ralph R | Insertion detecting probe and electrolysis system |
US4608977A (en) | 1979-08-29 | 1986-09-02 | Brown Russell A | System using computed tomography as for selective body treatment |
DE2946728A1 (en) | 1979-11-20 | 1981-05-27 | Erbe Elektromedizin GmbH & Co KG, 7400 Tübingen | HF surgical appts. for use with endoscope - provides cutting or coagulation current at preset intervals and of selected duration |
US4314559A (en) | 1979-12-12 | 1982-02-09 | Corning Glass Works | Nonstick conductive coating |
US4378801A (en) | 1979-12-17 | 1983-04-05 | Medical Research Associates Ltd. #2 | Electrosurgical generator |
US4287557A (en) | 1979-12-17 | 1981-09-01 | General Electric Company | Inverter with improved regulation |
US4303073A (en) | 1980-01-17 | 1981-12-01 | Medical Plastics, Inc. | Electrosurgery safety monitor |
US4494541A (en) | 1980-01-17 | 1985-01-22 | Medical Plastics, Inc. | Electrosurgery safety monitor |
US4334539A (en) | 1980-04-28 | 1982-06-15 | Cimarron Instruments, Inc. | Electrosurgical generator control apparatus |
EP0040658A3 (en) | 1980-05-28 | 1981-12-09 | Drg (Uk) Limited | Patient plate for diathermy apparatus, and diathermy apparatus fitted with it |
US4343308A (en) | 1980-06-09 | 1982-08-10 | Gross Robert D | Surgical ground detector |
US4372315A (en) | 1980-07-03 | 1983-02-08 | Hair Free Centers | Impedance sensing epilator |
US4565200A (en) | 1980-09-24 | 1986-01-21 | Cosman Eric R | Universal lesion and recording electrode system |
US4411266A (en) | 1980-09-24 | 1983-10-25 | Cosman Eric R | Thermocouple radio frequency lesion electrode |
JPS5764036A (en) | 1980-10-08 | 1982-04-17 | Olympus Optical Co | Endoscope apparatus |
JPS5778844A (en) | 1980-11-04 | 1982-05-17 | Kogyo Gijutsuin | Lasre knife |
US4376263A (en) | 1980-11-06 | 1983-03-08 | Braun Aktiengesellschaft | Battery charging circuit |
DE3045996A1 (en) | 1980-12-05 | 1982-07-08 | Medic Eschmann Handelsgesellschaft für medizinische Instrumente mbH, 2000 Hamburg | Electro-surgical scalpel instrument - has power supply remotely controlled by surgeon |
US4436091A (en) * | 1981-03-20 | 1984-03-13 | Surgical Design Corporation | Surgical cutting instrument with release mechanism |
FR2502935B1 (en) | 1981-03-31 | 1985-10-04 | Dolley Roger | METHOD AND DEVICE FOR CONTROLLING THE COAGULATION OF TISSUES USING A HIGH FREQUENCY CURRENT |
DE3120102A1 (en) | 1981-05-20 | 1982-12-09 | F.L. Fischer GmbH & Co, 7800 Freiburg | ARRANGEMENT FOR HIGH-FREQUENCY COAGULATION OF EGG WHITE FOR SURGICAL PURPOSES |
US4566454A (en) | 1981-06-16 | 1986-01-28 | Thomas L. Mehl | Selected frequency hair removal device and method |
US4429694A (en) * | 1981-07-06 | 1984-02-07 | C. R. Bard, Inc. | Electrosurgical generator |
US4582057A (en) | 1981-07-20 | 1986-04-15 | Regents Of The University Of Washington | Fast pulse thermal cautery probe |
US4559496A (en) | 1981-07-24 | 1985-12-17 | General Electric Company | LCD Hook-on digital ammeter |
US4397314A (en) | 1981-08-03 | 1983-08-09 | Clini-Therm Corporation | Method and apparatus for controlling and optimizing the heating pattern for a hyperthermia system |
US4559943A (en) | 1981-09-03 | 1985-12-24 | C. R. Bard, Inc. | Electrosurgical generator |
US4438766A (en) * | 1981-09-03 | 1984-03-27 | C. R. Bard, Inc. | Electrosurgical generator |
US4416277A (en) | 1981-11-03 | 1983-11-22 | Valleylab, Inc. | Return electrode monitoring system for use during electrosurgical activation |
US4416276A (en) | 1981-10-26 | 1983-11-22 | Valleylab, Inc. | Adaptive, return electrode monitoring system |
US4437464A (en) | 1981-11-09 | 1984-03-20 | C.R. Bard, Inc. | Electrosurgical generator safety apparatus |
US4452546A (en) | 1981-11-30 | 1984-06-05 | Richard Wolf Gmbh | Coupling member for coupling an optical system to an endoscope shaft |
FR2517953A1 (en) | 1981-12-10 | 1983-06-17 | Alvar Electronic | Diaphanometer for optical examination of breast tissue structure - measures tissue transparency using two plates and optical fibre bundle cooperating with photoelectric cells |
US4463759A (en) | 1982-01-13 | 1984-08-07 | Garito Jon C | Universal finger/foot switch adaptor for tube-type electrosurgical instrument |
DE3325612A1 (en) | 1982-07-15 | 1984-01-19 | Tokyo Shibaura Electric Co | OVERVOLTAGE SUPPRESSION DEVICE |
DE3228136C2 (en) | 1982-07-28 | 1985-05-30 | Erbe Elektromedizin GmbH, 7400 Tübingen | High-frequency surgical device |
US5370675A (en) | 1992-08-12 | 1994-12-06 | Vidamed, Inc. | Medical probe device and method |
US4492231A (en) | 1982-09-17 | 1985-01-08 | Auth David C | Non-sticking electrocautery system and forceps |
JPS5957650A (en) | 1982-09-27 | 1984-04-03 | 呉羽化学工業株式会社 | Probe for heating body cavity |
US4472661A (en) | 1982-09-30 | 1984-09-18 | Culver Clifford T | High voltage, low power transformer for efficiently firing a gas discharge luminous display |
US4514619A (en) | 1982-09-30 | 1985-04-30 | The B. F. Goodrich Company | Indirect current monitoring via voltage and impedance monitoring |
US4492832A (en) | 1982-12-23 | 1985-01-08 | Neomed, Incorporated | Hand-controllable switching device for electrosurgical instruments |
US4644955A (en) | 1982-12-27 | 1987-02-24 | Rdm International, Inc. | Circuit apparatus and method for electrothermal treatment of cancer eye |
US4576177A (en) | 1983-02-18 | 1986-03-18 | Webster Wilton W Jr | Catheter for removing arteriosclerotic plaque |
DE3306402C2 (en) | 1983-02-24 | 1985-03-07 | Werner Prof. Dr.-Ing. 6301 Wettenberg Irnich | Monitoring device for a high-frequency surgical device |
US4520818A (en) | 1983-02-28 | 1985-06-04 | Codman & Shurtleff, Inc. | High dielectric output circuit for electrosurgical power source |
US4630218A (en) | 1983-04-22 | 1986-12-16 | Cooper Industries, Inc. | Current measuring apparatus |
US4590934A (en) | 1983-05-18 | 1986-05-27 | Jerry L. Malis | Bipolar cutter/coagulator |
DE3378719D1 (en) | 1983-05-24 | 1989-01-26 | Chang Sien Shih | Electro-surgical unit control apparatus |
US4615330A (en) | 1983-09-05 | 1986-10-07 | Olympus Optical Co., Ltd. | Noise suppressor for electronic endoscope |
US4658819A (en) | 1983-09-13 | 1987-04-21 | Valleylab, Inc. | Electrosurgical generator |
US4586120A (en) * | 1983-12-30 | 1986-04-29 | At&T Bell Laboratories | Current limit shutdown circuit with time delay |
CA1257165A (en) | 1984-02-08 | 1989-07-11 | Paul Epstein | Infusion system having plural fluid input ports and at least one patient output port |
US4569345A (en) | 1984-02-29 | 1986-02-11 | Aspen Laboratories, Inc. | High output electrosurgical unit |
US5162217A (en) | 1984-08-27 | 1992-11-10 | Bio-Technology General Corp. | Plasmids for expression of human superoxide dismutase (SOD) analogs containing lambda PL promoter with engineered restriction site for substituting ribosomal binding sites and methods of use thereof |
US4651264A (en) | 1984-09-05 | 1987-03-17 | Trion, Inc. | Power supply with arcing control and automatic overload protection |
US4727874A (en) | 1984-09-10 | 1988-03-01 | C. R. Bard, Inc. | Electrosurgical generator with high-frequency pulse width modulated feedback power control |
USRE33420E (en) | 1984-09-17 | 1990-11-06 | Cordis Corporation | System for controlling an implanted neural stimulator |
US4735204A (en) | 1984-09-17 | 1988-04-05 | Cordis Corporation | System for controlling an implanted neural stimulator |
FR2573301B3 (en) | 1984-11-16 | 1987-04-30 | Lamidey Gilles | SURGICAL PLIERS AND ITS CONTROL AND CONTROL APPARATUS |
US4632109A (en) | 1984-12-11 | 1986-12-30 | Valleylab, Inc. | Circuitry for processing requests made from the sterile field of a surgical procedure to change the output power level of an electrosurgical generator |
US4827927A (en) | 1984-12-26 | 1989-05-09 | Valleylab, Inc. | Apparatus for changing the output power level of an electrosurgical generator while remaining in the sterile field of a surgical procedure |
US4658820A (en) | 1985-02-22 | 1987-04-21 | Valleylab, Inc. | Electrosurgical generator with improved circuitry for generating RF drive pulse trains |
US4739759A (en) | 1985-02-26 | 1988-04-26 | Concept, Inc. | Microprocessor controlled electrosurgical generator |
DE3510586A1 (en) | 1985-03-23 | 1986-10-02 | Erbe Elektromedizin GmbH, 7400 Tübingen | Control device for a high-frequency surgical instrument |
DE3516354A1 (en) | 1985-05-07 | 1986-11-13 | Werner Prof. Dr.-Ing. 6301 Wettenberg Irnich | MONITORING DEVICE FOR A HIGH-FREQUENCY SURGERY DEVICE |
DE3689698T2 (en) | 1985-05-20 | 1994-07-21 | Matsushita Electric Ind Co Ltd | Blood speed meter based on the ultrasound Doppler principle. |
US4712559A (en) | 1985-06-28 | 1987-12-15 | Bsd Medical Corporation | Local current capacitive field applicator for interstitial array |
US4750488A (en) * | 1986-05-19 | 1988-06-14 | Sonomed Technology, Inc. | Vibration apparatus preferably for endoscopic ultrasonic aspirator |
DE3544443C2 (en) | 1985-12-16 | 1994-02-17 | Siemens Ag | HF surgery device |
US4887199A (en) | 1986-02-07 | 1989-12-12 | Astec International Limited | Start circuit for generation of pulse width modulated switching pulses for switch mode power supplies |
DE3604823C2 (en) | 1986-02-15 | 1995-06-01 | Lindenmeier Heinz | High frequency generator with automatic power control for high frequency surgery |
US4827911A (en) | 1986-04-02 | 1989-05-09 | Cooper Lasersonics, Inc. | Method and apparatus for ultrasonic surgical fragmentation and removal of tissue |
US4901720A (en) | 1986-04-08 | 1990-02-20 | C. R. Bard, Inc. | Power control for beam-type electrosurgical unit |
US4691703A (en) | 1986-04-25 | 1987-09-08 | Board Of Regents, University Of Washington | Thermal cautery system |
FR2597744A1 (en) | 1986-04-29 | 1987-10-30 | Boussignac Georges | CARDIO-VASCULAR CATHETER FOR LASER SHOOTING |
DE3775281D1 (en) | 1986-06-16 | 1992-01-30 | Siemens Ag | DEVICE FOR CONTROLLING A HEART PACER BY MEANS OF IMPEDANCE ON BODY TISSUES. |
DE3689889D1 (en) | 1986-07-17 | 1994-07-07 | Erbe Elektromedizin | High-frequency surgical device for the thermal coagulation of biological tissues. |
US5157603A (en) | 1986-11-06 | 1992-10-20 | Storz Instrument Company | Control system for ophthalmic surgical instruments |
JPH0511882Y2 (en) | 1987-01-06 | 1993-03-25 | ||
US5024668A (en) * | 1987-01-20 | 1991-06-18 | Rocky Mountain Research, Inc. | Retrograde perfusion system, components and method |
DE3878477D1 (en) | 1987-04-10 | 1993-03-25 | Siemens Ag | MONITORING CIRCUIT FOR AN HF SURGERY DEVICE. |
US4788634A (en) | 1987-06-22 | 1988-11-29 | Massachusetts Institute Of Technology | Resonant forward converter |
JPS6410264A (en) | 1987-07-03 | 1989-01-13 | Fuji Xerox Co Ltd | Electrophotographic developer |
DE3728906A1 (en) | 1987-08-29 | 1989-03-09 | Asea Brown Boveri | METHOD FOR DETECTING A CURRENT FLOWS CURRENTLY FLOWING FROM THE HUMAN BODY AND CIRCUIT ARRANGEMENT FOR IMPLEMENTING THE METHOD |
US5015227A (en) | 1987-09-30 | 1991-05-14 | Valleylab Inc. | Apparatus for providing enhanced tissue fragmentation and/or hemostasis |
US4931047A (en) | 1987-09-30 | 1990-06-05 | Cavitron, Inc. | Method and apparatus for providing enhanced tissue fragmentation and/or hemostasis |
JPH0636834Y2 (en) | 1987-10-28 | 1994-09-28 | オリンパス光学工業株式会社 | High frequency dielectric heating electrode |
EP0653192B1 (en) | 1987-11-17 | 2000-04-12 | Erbe Elektromedizin GmbH | High frequence surgical device to cut and/or coagulate biological tissues |
GB8801177D0 (en) | 1988-01-20 | 1988-02-17 | Goble N M | Diathermy unit |
DE68925215D1 (en) * | 1988-01-20 | 1996-02-08 | G2 Design Ltd | Diathermy unit |
US4848335B1 (en) | 1988-02-16 | 1994-06-07 | Aspen Lab Inc | Return electrode contact monitor |
DE3805179A1 (en) | 1988-02-19 | 1989-08-31 | Wolf Gmbh Richard | DEVICE WITH A ROTATING DRIVEN SURGICAL INSTRUMENT |
US5588432A (en) | 1988-03-21 | 1996-12-31 | Boston Scientific Corporation | Catheters for imaging, sensing electrical potentials, and ablating tissue |
US4907589A (en) | 1988-04-29 | 1990-03-13 | Cosman Eric R | Automatic over-temperature control apparatus for a therapeutic heating device |
DE3815835A1 (en) | 1988-05-09 | 1989-11-23 | Flachenecker Gerhard | HIGH FREQUENCY GENERATOR FOR TISSUE CUTTING AND COAGULATION IN HIGH FREQUENCY SURGERY |
US4890610A (en) | 1988-05-15 | 1990-01-02 | Kirwan Sr Lawrence T | Bipolar forceps |
DE3824970C2 (en) | 1988-07-22 | 1999-04-01 | Lindenmeier Heinz | Feedback high frequency power oscillator |
US4903696A (en) | 1988-10-06 | 1990-02-27 | Everest Medical Corporation | Electrosurgical generator |
US4966597A (en) | 1988-11-04 | 1990-10-30 | Cosman Eric R | Thermometric cardiac tissue ablation electrode with ultra-sensitive temperature detection |
US4961047A (en) | 1988-11-10 | 1990-10-02 | Smiths Industries Public Limited Company | Electrical power control apparatus and methods |
US4959606A (en) | 1989-01-06 | 1990-09-25 | Uniphase Corporation | Current mode switching regulator with programmed offtime |
DE3904558C2 (en) | 1989-02-15 | 1997-09-18 | Lindenmeier Heinz | Automatically power-controlled high-frequency generator for high-frequency surgery |
US4938761A (en) | 1989-03-06 | 1990-07-03 | Mdt Corporation | Bipolar electrosurgical forceps |
EP0390937B1 (en) | 1989-04-01 | 1994-11-02 | Erbe Elektromedizin GmbH | Device for the surveillance of the adherence of neutral electrodes in high-frequency surgery |
DE3911416A1 (en) | 1989-04-07 | 1990-10-11 | Delma Elektro Med App | ELECTRO-SURGICAL HIGH-FREQUENCY DEVICE |
US5151085A (en) * | 1989-04-28 | 1992-09-29 | Olympus Optical Co., Ltd. | Apparatus for generating ultrasonic oscillation |
FR2647683B1 (en) | 1989-05-31 | 1993-02-12 | Kyocera Corp | BLOOD WATERPROOFING / COAGULATION DEVICE OUTSIDE BLOOD VESSELS |
US5029588A (en) | 1989-06-15 | 1991-07-09 | Cardiovascular Imaging Systems, Inc. | Laser catheter with imaging capability |
US4992719A (en) * | 1989-07-24 | 1991-02-12 | Hughes Aircraft Company | Stable high voltage pulse power supply |
US4931717A (en) | 1989-09-05 | 1990-06-05 | Motorola Inc. | Load response control and method |
DE58908704D1 (en) | 1989-09-07 | 1995-01-12 | Siemens Ag | Method and circuit arrangement for monitoring several electrode surfaces of the neutral electrode of an H.F. surgical device. |
US5531774A (en) | 1989-09-22 | 1996-07-02 | Alfred E. Mann Foundation For Scientific Research | Multichannel implantable cochlear stimulator having programmable bipolar, monopolar or multipolar electrode configurations |
US5249121A (en) | 1989-10-27 | 1993-09-28 | American Cyanamid Company | Remote control console for surgical control system |
DE3942998C2 (en) | 1989-12-27 | 1998-11-26 | Delma Elektro Med App | High frequency electrosurgical unit |
US5290283A (en) | 1990-01-31 | 1994-03-01 | Kabushiki Kaisha Toshiba | Power supply apparatus for electrosurgical unit including electrosurgical-current waveform data storage |
US5031618A (en) | 1990-03-07 | 1991-07-16 | Medtronic, Inc. | Position-responsive neuro stimulator |
US5019176A (en) | 1990-03-20 | 1991-05-28 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Thin solar cell and lightweight array |
US5122137A (en) | 1990-04-27 | 1992-06-16 | Boston Scientific Corporation | Temperature controlled rf coagulation |
US5108389A (en) | 1990-05-23 | 1992-04-28 | Ioan Cosmescu | Automatic smoke evacuator activator system for a surgical laser apparatus and method therefor |
US5233515A (en) | 1990-06-08 | 1993-08-03 | Cosman Eric R | Real-time graphic display of heat lesioning parameters in a clinical lesion generator system |
US5540677A (en) * | 1990-06-15 | 1996-07-30 | Rare Earth Medical, Inc. | Endoscopic systems for photoreactive suturing of biological materials |
US5103804A (en) | 1990-07-03 | 1992-04-14 | Boston Scientific Corporation | Expandable tip hemostatic probes and the like |
US5152762A (en) | 1990-11-16 | 1992-10-06 | Birtcher Medical Systems, Inc. | Current leakage control for electrosurgical generator |
DE9117217U1 (en) | 1991-01-16 | 1997-05-15 | Erbe Elektromedizin | High frequency surgical device |
US5167658A (en) | 1991-01-31 | 1992-12-01 | Mdt Corporation | Method and apparatus for electrosurgical measurement |
US5160334A (en) | 1991-04-30 | 1992-11-03 | Utah Medical Products, Inc. | Electrosurgical generator and suction apparatus |
FI93607C (en) | 1991-05-24 | 1995-05-10 | John Koivukangas | Cutting Remedy |
US5190517A (en) | 1991-06-06 | 1993-03-02 | Valleylab Inc. | Electrosurgical and ultrasonic surgical system |
US5472443A (en) | 1991-06-07 | 1995-12-05 | Hemostatic Surgery Corporation | Electrosurgical apparatus employing constant voltage and methods of use |
DE4121977C2 (en) | 1991-07-03 | 1994-10-27 | Wolf Gmbh Richard | Medical instrument with a contactless switch for controlling external devices |
US5383917A (en) | 1991-07-05 | 1995-01-24 | Jawahar M. Desai | Device and method for multi-phase radio-frequency ablation |
DE4126608A1 (en) | 1991-08-12 | 1993-02-18 | Fastenmeier Karl | ARRANGEMENT FOR CUTTING ORGANIC TISSUE WITH HIGH-FREQUENCY CURRENT |
WO1993003677A2 (en) | 1991-08-12 | 1993-03-04 | Karl Storz Gmbh & Co. | Surgical high-frequency generator for cutting tissues |
US5196009A (en) | 1991-09-11 | 1993-03-23 | Kirwan Jr Lawrence T | Non-sticking electrosurgical device having nickel tips |
CA2075319C (en) | 1991-09-26 | 1998-06-30 | Ernie Aranyi | Handle for surgical instruments |
US5713896A (en) | 1991-11-01 | 1998-02-03 | Medical Scientific, Inc. | Impedance feedback electrosurgical system |
US5207691A (en) | 1991-11-01 | 1993-05-04 | Medical Scientific, Inc. | Electrosurgical clip applicator |
US5323778A (en) | 1991-11-05 | 1994-06-28 | Brigham & Women's Hospital | Method and apparatus for magnetic resonance imaging and heating tissues |
ATE241938T1 (en) | 1991-11-08 | 2003-06-15 | Boston Scient Ltd | ABLATION ELECTRODE WITH INSULATED TEMPERATURE MEASUREMENT ELEMENT |
US5383874A (en) | 1991-11-08 | 1995-01-24 | Ep Technologies, Inc. | Systems for identifying catheters and monitoring their use |
CA2106409A1 (en) | 1991-11-08 | 1993-05-09 | Stuart D. Edwards | Radiofrequency ablation with phase sensitive power detection |
US5230623A (en) | 1991-12-10 | 1993-07-27 | Radionics, Inc. | Operating pointer with interactive computergraphics |
US6142992A (en) | 1993-05-10 | 2000-11-07 | Arthrocare Corporation | Power supply for limiting power in electrosurgery |
JP2547520B2 (en) | 1992-01-21 | 1996-10-23 | ヴァリーラブ・インコーポレーテッド | Electrosurgical controller for trocar |
US5267994A (en) | 1992-02-10 | 1993-12-07 | Conmed Corporation | Electrosurgical probe |
GB9204218D0 (en) | 1992-02-27 | 1992-04-08 | Goble Nigel M | A surgical cutting tool |
US5201900A (en) | 1992-02-27 | 1993-04-13 | Medical Scientific, Inc. | Bipolar surgical clip |
GB9204217D0 (en) | 1992-02-27 | 1992-04-08 | Goble Nigel M | Cauterising apparatus |
US5330518A (en) | 1992-03-06 | 1994-07-19 | Urologix, Inc. | Method for treating interstitial tissue associated with microwave thermal therapy |
US5300070A (en) | 1992-03-17 | 1994-04-05 | Conmed Corporation | Electrosurgical trocar assembly with bi-polar electrode |
US5254117A (en) | 1992-03-17 | 1993-10-19 | Alton Dean Medical | Multi-functional endoscopic probe apparatus |
US5432459A (en) | 1992-03-17 | 1995-07-11 | Conmed Corporation | Leakage capacitance compensating current sensor for current supplied to medical device loads with unconnected reference conductor |
US5436566A (en) | 1992-03-17 | 1995-07-25 | Conmed Corporation | Leakage capacitance compensating current sensor for current supplied to medical device loads |
US5573533A (en) | 1992-04-10 | 1996-11-12 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5540681A (en) | 1992-04-10 | 1996-07-30 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of tissue |
US5281213A (en) | 1992-04-16 | 1994-01-25 | Implemed, Inc. | Catheter for ice mapping and ablation |
US5300068A (en) | 1992-04-21 | 1994-04-05 | St. Jude Medical, Inc. | Electrosurgical apparatus |
US5443463A (en) | 1992-05-01 | 1995-08-22 | Vesta Medical, Inc. | Coagulating forceps |
US5445635A (en) | 1992-05-01 | 1995-08-29 | Hemostatic Surgery Corporation | Regulated-current power supply and methods for resistively-heated surgical instruments |
GB9209859D0 (en) | 1992-05-07 | 1992-06-24 | Smiths Industries Plc | Electrical apparatus |
US5318563A (en) | 1992-06-04 | 1994-06-07 | Valley Forge Scientific Corporation | Bipolar RF generator |
US5341807A (en) | 1992-06-30 | 1994-08-30 | American Cardiac Ablation Co., Inc. | Ablation catheter positioning system |
WO1994002077A2 (en) | 1992-07-15 | 1994-02-03 | Angelase, Inc. | Ablation catheter system |
US5762609A (en) * | 1992-09-14 | 1998-06-09 | Sextant Medical Corporation | Device and method for analysis of surgical tissue interventions |
US5478303A (en) | 1992-09-18 | 1995-12-26 | Foley-Nolan; Darragh | Electromagnetic apparatus for use in therapy |
US5414238A (en) * | 1992-10-02 | 1995-05-09 | Martin Marietta Corporation | Resonant power supply for an arcjet thruster |
US5370672A (en) | 1992-10-30 | 1994-12-06 | The Johns Hopkins University | Computer-controlled neurological stimulation system |
US5342357A (en) | 1992-11-13 | 1994-08-30 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical cauterization system |
US5334193A (en) | 1992-11-13 | 1994-08-02 | American Cardiac Ablation Co., Inc. | Fluid cooled ablation catheter |
AU5456494A (en) | 1992-11-13 | 1994-06-08 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical probe |
US5348554A (en) | 1992-12-01 | 1994-09-20 | Cardiac Pathways Corporation | Catheter for RF ablation with cooled electrode |
US5342356A (en) | 1992-12-02 | 1994-08-30 | Ellman Alan G | Electrical coupling unit for electrosurgery |
DE4240722C2 (en) | 1992-12-03 | 1996-08-29 | Siemens Ag | Device for the treatment of pathological tissue |
US5400267A (en) | 1992-12-08 | 1995-03-21 | Hemostatix Corporation | Local in-device memory feature for electrically powered medical equipment |
US5403312A (en) | 1993-07-22 | 1995-04-04 | Ethicon, Inc. | Electrosurgical hemostatic device |
US5558671A (en) | 1993-07-22 | 1996-09-24 | Yates; David C. | Impedance feedback monitor for electrosurgical instrument |
US5403276A (en) | 1993-02-16 | 1995-04-04 | Danek Medical, Inc. | Apparatus for minimally invasive tissue removal |
US5430434A (en) | 1993-02-24 | 1995-07-04 | Lederer; Gabor | Portable surgical early warning device |
US5403311A (en) | 1993-03-29 | 1995-04-04 | Boston Scientific Corporation | Electro-coagulation and ablation and other electrotherapeutic treatments of body tissue |
GB9306637D0 (en) | 1993-03-30 | 1993-05-26 | Smiths Industries Plc | Electrosurgery monitor and appartus |
US5370645A (en) | 1993-04-19 | 1994-12-06 | Valleylab Inc. | Electrosurgical processor and method of use |
US6235020B1 (en) | 1993-05-10 | 2001-05-22 | Arthrocare Corporation | Power supply and methods for fluid delivery in electrosurgery |
US5395368A (en) | 1993-05-20 | 1995-03-07 | Ellman; Alan G. | Multiple-wire electrosurgical electrodes |
US5396062A (en) | 1993-05-27 | 1995-03-07 | The Whitaker Corporation | Receptacle having an internal switch with an emitter and a receiver |
EP0703756B1 (en) | 1993-06-10 | 2004-12-15 | IMRAN, Mir, A. | Transurethral radio frequency ablation apparatus |
GB9314391D0 (en) | 1993-07-12 | 1993-08-25 | Gyrus Medical Ltd | A radio frequency oscillator and an electrosurgical generator incorporating such an oscillator |
US5817093A (en) | 1993-07-22 | 1998-10-06 | Ethicon Endo-Surgery, Inc. | Impedance feedback monitor with query electrode for electrosurgical instrument |
US5372596A (en) | 1993-07-27 | 1994-12-13 | Valleylab Inc. | Apparatus for leakage control and method for its use |
US5921982A (en) | 1993-07-30 | 1999-07-13 | Lesh; Michael D. | Systems and methods for ablating body tissue |
US5385148A (en) | 1993-07-30 | 1995-01-31 | The Regents Of The University Of California | Cardiac imaging and ablation catheter |
US5749871A (en) | 1993-08-23 | 1998-05-12 | Refractec Inc. | Method and apparatus for modifications of visual acuity by thermal means |
US5417719A (en) | 1993-08-25 | 1995-05-23 | Medtronic, Inc. | Method of using a spinal cord stimulation lead |
US5409000A (en) | 1993-09-14 | 1995-04-25 | Cardiac Pathways Corporation | Endocardial mapping and ablation system utilizing separately controlled steerable ablation catheter with ultrasonic imaging capabilities and method |
US5485312A (en) * | 1993-09-14 | 1996-01-16 | The United States Of America As Represented By The Secretary Of The Air Force | Optical pattern recognition system and method for verifying the authenticity of a person, product or thing |
US5423806A (en) | 1993-10-01 | 1995-06-13 | Medtronic, Inc. | Laser extractor for an implanted object |
US6210403B1 (en) | 1993-10-07 | 2001-04-03 | Sherwood Services Ag | Automatic control for energy from an electrosurgical generator |
US5496312A (en) | 1993-10-07 | 1996-03-05 | Valleylab Inc. | Impedance and temperature generator control |
US5433739A (en) | 1993-11-02 | 1995-07-18 | Sluijter; Menno E. | Method and apparatus for heating an intervertebral disc for relief of back pain |
US5571147A (en) | 1993-11-02 | 1996-11-05 | Sluijter; Menno E. | Thermal denervation of an intervertebral disc for relief of back pain |
JP3325098B2 (en) | 1993-11-08 | 2002-09-17 | オリンパス光学工業株式会社 | Induction cautery equipment |
US5536267A (en) | 1993-11-08 | 1996-07-16 | Zomed International | Multiple electrode ablation apparatus |
US5599345A (en) | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment apparatus |
US5472441A (en) | 1993-11-08 | 1995-12-05 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
US5458597A (en) | 1993-11-08 | 1995-10-17 | Zomed International | Device for treating cancer and non-malignant tumors and methods |
DE4339049C2 (en) | 1993-11-16 | 2001-06-28 | Erbe Elektromedizin | Surgical system configuration facility |
US5514129A (en) | 1993-12-03 | 1996-05-07 | Valleylab Inc. | Automatic bipolar control for an electrosurgical generator |
US6241725B1 (en) | 1993-12-15 | 2001-06-05 | Sherwood Services Ag | High frequency thermal ablation of cancerous tumors and functional targets with image data assistance |
US5645059A (en) | 1993-12-17 | 1997-07-08 | Nellcor Incorporated | Medical sensor with modulated encoding scheme |
US5462521A (en) | 1993-12-21 | 1995-10-31 | Angeion Corporation | Fluid cooled and perfused tip for a catheter |
US5422567A (en) | 1993-12-27 | 1995-06-06 | Valleylab Inc. | High frequency power measurement |
EP0740533A4 (en) | 1994-01-18 | 1998-01-14 | Endovascular Inc | Apparatus and method for venous ligation |
US5501703A (en) | 1994-01-24 | 1996-03-26 | Medtronic, Inc. | Multichannel apparatus for epidural spinal cord stimulator |
US5434398A (en) | 1994-02-22 | 1995-07-18 | Haim Labenski | Magnetic smartcard |
US5584830A (en) | 1994-03-30 | 1996-12-17 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5529235A (en) | 1994-04-28 | 1996-06-25 | Ethicon Endo-Surgery, Inc. | Identification device for surgical instrument |
US5458596A (en) | 1994-05-06 | 1995-10-17 | Dorsal Orthopedic Corporation | Method and apparatus for controlled contraction of soft tissue |
US5696441A (en) | 1994-05-13 | 1997-12-09 | Distribution Control Systems, Inc. | Linear alternating current interface for electronic meters |
US6464689B1 (en) | 1999-09-08 | 2002-10-15 | Curon Medical, Inc. | Graphical user interface for monitoring and controlling use of medical devices |
US6733495B1 (en) | 1999-09-08 | 2004-05-11 | Curon Medical, Inc. | Systems and methods for monitoring and controlling use of medical devices |
US6113591A (en) | 1994-06-27 | 2000-09-05 | Ep Technologies, Inc. | Systems and methods for sensing sub-surface temperatures in body tissue |
ES2216016T3 (en) | 1994-06-27 | 2004-10-16 | Boston Scientific Limited | NON-LINEAR CONTROL SYSTEMS ON HEATING OF BODY FABRIC AND ABLATION PROCEDURES. |
CA2194062C (en) | 1994-06-27 | 2005-06-28 | Dorin Panescu | System for controlling tissue ablation using temperature sensors |
GB9413070D0 (en) | 1994-06-29 | 1994-08-17 | Gyrus Medical Ltd | Electrosurgical apparatus |
US5594636A (en) | 1994-06-29 | 1997-01-14 | Northrop Grumman Corporation | Matrix converter circuit and commutating method |
US5846236A (en) | 1994-07-18 | 1998-12-08 | Karl Storz Gmbh & Co. | High frequency-surgical generator for adjusted cutting and coagulation |
US5625370A (en) | 1994-07-25 | 1997-04-29 | Texas Instruments Incorporated | Identification system antenna with impedance transformer |
US5540684A (en) | 1994-07-28 | 1996-07-30 | Hassler, Jr.; William L. | Method and apparatus for electrosurgically treating tissue |
US8025661B2 (en) * | 1994-09-09 | 2011-09-27 | Cardiofocus, Inc. | Coaxial catheter instruments for ablation with radiant energy |
US5496313A (en) | 1994-09-20 | 1996-03-05 | Conmed Corporation | System for detecting penetration of medical instruments |
US6142994A (en) | 1994-10-07 | 2000-11-07 | Ep Technologies, Inc. | Surgical method and apparatus for positioning a diagnostic a therapeutic element within the body |
US5605150A (en) | 1994-11-04 | 1997-02-25 | Physio-Control Corporation | Electrical interface for a portable electronic physiological instrument having separable components |
US5534018A (en) | 1994-11-30 | 1996-07-09 | Medtronic, Inc. | Automatic lead recognition for implantable medical device |
AU4252596A (en) | 1994-12-13 | 1996-07-03 | Torben Lorentzen | An electrosurgical instrument for tissue ablation, an apparatus, and a method for providing a lesion in damaged and diseased tissue from a mammal |
US5613966A (en) | 1994-12-21 | 1997-03-25 | Valleylab Inc | System and method for accessory rate control |
US5695494A (en) | 1994-12-22 | 1997-12-09 | Valleylab Inc | Rem output stage topology |
US5596466A (en) | 1995-01-13 | 1997-01-21 | Ixys Corporation | Intelligent, isolated half-bridge power module |
US5500616A (en) | 1995-01-13 | 1996-03-19 | Ixys Corporation | Overvoltage clamp and desaturation detection circuit |
US5712772A (en) * | 1995-02-03 | 1998-01-27 | Ericsson Raynet | Controller for high efficiency resonant switching converters |
US5694304A (en) | 1995-02-03 | 1997-12-02 | Ericsson Raynet Corporation | High efficiency resonant switching converters |
US5540724A (en) | 1995-02-03 | 1996-07-30 | Intermedics, Inc. | Cardiac cardioverter/defibrillator with in vivo impedance estimation |
US6409722B1 (en) * | 1998-07-07 | 2002-06-25 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
US5696351A (en) | 1995-03-10 | 1997-12-09 | Ericsson Raynet | Cable retention and sealing device |
US5647871A (en) | 1995-03-10 | 1997-07-15 | Microsurge, Inc. | Electrosurgery with cooled electrodes |
US5868740A (en) | 1995-03-24 | 1999-02-09 | Board Of Regents-Univ Of Nebraska | Method for volumetric tissue ablation |
US5707369A (en) | 1995-04-24 | 1998-01-13 | Ethicon Endo-Surgery, Inc. | Temperature feedback monitor for hemostatic surgical instrument |
US5626575A (en) | 1995-04-28 | 1997-05-06 | Conmed Corporation | Power level control apparatus for electrosurgical generators |
US5688267A (en) | 1995-05-01 | 1997-11-18 | Ep Technologies, Inc. | Systems and methods for sensing multiple temperature conditions during tissue ablation |
US6053912A (en) | 1995-05-01 | 2000-04-25 | Ep Techonologies, Inc. | Systems and methods for sensing sub-surface temperatures in body tissue during ablation with actively cooled electrodes |
WO1996034570A1 (en) | 1995-05-01 | 1996-11-07 | Ep Technologies, Inc. | Systems and methods for obtaining desired lesion characteristics while ablating body tissue |
CA2222617C (en) | 1995-05-02 | 2002-07-16 | Heart Rhythm Technologies, Inc. | System for controlling the energy delivered to a patient for ablation |
US6575969B1 (en) | 1995-05-04 | 2003-06-10 | Sherwood Services Ag | Cool-tip radiofrequency thermosurgery electrode system for tumor ablation |
ATE308930T1 (en) | 1995-05-04 | 2005-11-15 | Sherwood Serv Ag | THERMO-SURGERY SYSTEM WITH COLD ELECTRIC TIP |
US5613996A (en) | 1995-05-08 | 1997-03-25 | Plasma Processing Corporation | Process for treatment of reactive fines |
WO1996038094A1 (en) | 1995-05-31 | 1996-12-05 | Nuvotek Ltd. | Electrosurgical cutting and coagulation apparatus |
US5628745A (en) | 1995-06-06 | 1997-05-13 | Bek; Robin B. | Exit spark control for an electrosurgical generator |
US5599344A (en) | 1995-06-06 | 1997-02-04 | Valleylab Inc. | Control apparatus for electrosurgical generator power output |
US5720744A (en) | 1995-06-06 | 1998-02-24 | Valleylab Inc | Control system for neurosurgery |
US5868737A (en) | 1995-06-09 | 1999-02-09 | Engineering Research & Associates, Inc. | Apparatus and method for determining ablation |
AU710619B2 (en) | 1995-06-23 | 1999-09-23 | Gyrus Medical Limited | An electrosurgical instrument |
GB9526627D0 (en) | 1995-12-29 | 1996-02-28 | Gyrus Medical Ltd | An electrosurgical instrument and an electrosurgical electrode assembly |
US6293942B1 (en) | 1995-06-23 | 2001-09-25 | Gyrus Medical Limited | Electrosurgical generator method |
DE19534151A1 (en) | 1995-09-14 | 1997-03-20 | Storz Endoskop Gmbh | High frequency surgical device |
US5827271A (en) | 1995-09-19 | 1998-10-27 | Valleylab | Energy delivery system for vessel sealing |
US5766165A (en) | 1995-09-22 | 1998-06-16 | Gentelia; John S. | Return path monitoring system |
US5772659A (en) | 1995-09-26 | 1998-06-30 | Valleylab Inc. | Electrosurgical generator power control circuit and method |
US5658322A (en) | 1995-10-11 | 1997-08-19 | Regeneration Technology | Bio-active frequency generator and method |
BR9611166A (en) | 1995-10-11 | 1999-04-06 | Regeneration Tech | Bioactive frequency generator and process |
US5660567A (en) | 1995-11-14 | 1997-08-26 | Nellcor Puritan Bennett Incorporated | Medical sensor connector with removable encoding device |
US5718246A (en) * | 1996-01-03 | 1998-02-17 | Preferential, Inc. | Preferential induction of electrically mediated cell death from applied pulses |
US5792138A (en) | 1996-02-22 | 1998-08-11 | Apollo Camera, Llc | Cordless bipolar electrocautery unit with automatic power control |
US6458121B1 (en) | 1996-03-19 | 2002-10-01 | Diapulse Corporation Of America | Apparatus for athermapeutic medical treatments |
US5733281A (en) | 1996-03-19 | 1998-03-31 | American Ablation Co., Inc. | Ultrasound and impedance feedback system for use with electrosurgical instruments |
US5702429A (en) | 1996-04-04 | 1997-12-30 | Medtronic, Inc. | Neural stimulation techniques with feedback |
US5925070A (en) | 1996-04-04 | 1999-07-20 | Medtronic, Inc. | Techniques for adjusting the locus of excitation of electrically excitable tissue |
US5797902A (en) | 1996-05-10 | 1998-08-25 | Minnesota Mining And Manufacturing Company | Biomedical electrode providing early detection of accidental detachment |
US5938690A (en) | 1996-06-07 | 1999-08-17 | Advanced Neuromodulation Systems, Inc. | Pain management system and method |
DE19623840A1 (en) | 1996-06-14 | 1997-12-18 | Berchtold Gmbh & Co Geb | High frequency electrosurgical generator |
US6246912B1 (en) | 1996-06-27 | 2001-06-12 | Sherwood Services Ag | Modulated high frequency tissue modification |
US5983141A (en) | 1996-06-27 | 1999-11-09 | Radionics, Inc. | Method and apparatus for altering neural tissue function |
DE19628482A1 (en) | 1996-07-15 | 1998-01-22 | Berchtold Gmbh & Co Geb | Method for operating a high-frequency surgical device and high-frequency surgical device |
US5931836A (en) | 1996-07-29 | 1999-08-03 | Olympus Optical Co., Ltd. | Electrosurgery apparatus and medical apparatus combined with the same |
US5836943A (en) | 1996-08-23 | 1998-11-17 | Team Medical, L.L.C. | Electrosurgical generator |
US5836909A (en) | 1996-09-13 | 1998-11-17 | Cosmescu; Ioan | Automatic fluid control system for use in open and laparoscopic laser surgery and electrosurgery and method therefor |
US5820568A (en) | 1996-10-15 | 1998-10-13 | Cardiac Pathways Corporation | Apparatus and method for aiding in the positioning of a catheter |
KR100398923B1 (en) | 1996-10-16 | 2003-09-19 | 아이씨엔 파마슈티컬스, 인코포레이티드 | Monocyclic l-nucleosides, analogs and uses thereof |
US5830212A (en) | 1996-10-21 | 1998-11-03 | Ndm, Inc. | Electrosurgical generator and electrode |
US6053910A (en) | 1996-10-30 | 2000-04-25 | Megadyne Medical Products, Inc. | Capacitive reusable electrosurgical return electrode |
US5729448A (en) * | 1996-10-31 | 1998-03-17 | Hewlett-Packard Company | Low cost highly manufacturable DC-to-DC power converter |
US5954719A (en) | 1996-12-11 | 1999-09-21 | Irvine Biomedical, Inc. | System for operating a RF ablation generator |
GB9626512D0 (en) | 1996-12-20 | 1997-02-05 | Gyrus Medical Ltd | An improved electrosurgical generator and system |
US6113596A (en) | 1996-12-30 | 2000-09-05 | Enable Medical Corporation | Combination monopolar-bipolar electrosurgical instrument system, instrument and cable |
US6063078A (en) | 1997-03-12 | 2000-05-16 | Medtronic, Inc. | Method and apparatus for tissue ablation |
EP0971637A1 (en) * | 1997-04-04 | 2000-01-19 | Minnesota Mining And Manufacturing Company | Method and apparatus for controlling contact of biomedical electrodes with patient skin |
US6033399A (en) | 1997-04-09 | 2000-03-07 | Valleylab, Inc. | Electrosurgical generator with adaptive power control |
DE19714972C2 (en) | 1997-04-10 | 2001-12-06 | Storz Endoskop Gmbh Schaffhaus | Device for monitoring the application of a neutral electrode |
US5871481A (en) | 1997-04-11 | 1999-02-16 | Vidamed, Inc. | Tissue ablation apparatus and method |
GB9708268D0 (en) | 1997-04-24 | 1997-06-18 | Gyrus Medical Ltd | An electrosurgical instrument |
DE19717411A1 (en) | 1997-04-25 | 1998-11-05 | Aesculap Ag & Co Kg | Monitoring of thermal loading of patient tissue in contact region of neutral electrode of HF treatment unit |
US5948007A (en) | 1997-04-30 | 1999-09-07 | Medtronic, Inc. | Dual channel implantation neurostimulation techniques |
US5797802A (en) | 1997-05-12 | 1998-08-25 | Nowak Products, Inc. | Die head |
US5838558A (en) | 1997-05-19 | 1998-11-17 | Trw Inc. | Phase staggered full-bridge converter with soft-PWM switching |
JP3315623B2 (en) | 1997-06-19 | 2002-08-19 | オリンパス光学工業株式会社 | Return electrode peeling monitor of electrocautery device |
US5908444A (en) | 1997-06-19 | 1999-06-01 | Healing Machines, Inc. | Complex frequency pulsed electromagnetic generator and method of use |
DE19730456A1 (en) * | 1997-07-16 | 1999-01-21 | Berchtold Gmbh & Co Geb | Electrically powered medical device |
US5961344A (en) | 1997-08-26 | 1999-10-05 | Yazaki Corporation | Cam-actuated terminal connector |
US6055458A (en) * | 1997-08-28 | 2000-04-25 | Bausch & Lomb Surgical, Inc. | Modes/surgical functions |
DE19739699A1 (en) * | 1997-09-04 | 1999-03-11 | Laser & Med Tech Gmbh | Electrode arrangement for the electro-thermal treatment of the human or animal body |
US5836990A (en) | 1997-09-19 | 1998-11-17 | Medtronic, Inc. | Method and apparatus for determining electrode/tissue contact |
US5954717A (en) | 1997-09-25 | 1999-09-21 | Radiotherapeutics Corporation | Method and system for heating solid tissue |
US6358246B1 (en) | 1999-06-25 | 2002-03-19 | 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 |
US6176857B1 (en) * | 1997-10-22 | 2001-01-23 | Oratec Interventions, Inc. | Method and apparatus for applying thermal energy to tissue asymmetrically |
US6068627A (en) | 1997-12-10 | 2000-05-30 | Valleylab, Inc. | Smart recognition apparatus and method |
US6080149A (en) | 1998-01-09 | 2000-06-27 | Radiotherapeutics, Corporation | Method and apparatus for monitoring solid tissue heating |
US5954686A (en) | 1998-02-02 | 1999-09-21 | Garito; Jon C | Dual-frequency electrosurgical instrument |
US6562037B2 (en) | 1998-02-12 | 2003-05-13 | Boris E. Paton | Bonding of soft biological tissues by passing high frequency electric current therethrough |
US6132429A (en) | 1998-02-17 | 2000-10-17 | Baker; James A. | Radiofrequency medical instrument and methods for luminal welding |
US6273886B1 (en) | 1998-02-19 | 2001-08-14 | Curon Medical, Inc. | Integrated tissue heating and cooling apparatus |
US6358245B1 (en) | 1998-02-19 | 2002-03-19 | Curon Medical, Inc. | Graphical user interface for association with an electrode structure deployed in contact with a tissue region |
US6864686B2 (en) | 1998-03-12 | 2005-03-08 | Storz Endoskop Gmbh | High-frequency surgical device and operation monitoring device for a high-frequency surgical device |
US6014581A (en) | 1998-03-26 | 2000-01-11 | Ep Technologies, Inc. | Interface for performing a diagnostic or therapeutic procedure on heart tissue with an electrode structure |
DE19814681B4 (en) * | 1998-04-01 | 2008-11-13 | Infineon Technologies Ag | Current Mode Switching Regulators |
US6383183B1 (en) | 1998-04-09 | 2002-05-07 | Olympus Optical Co., Ltd. | High frequency treatment apparatus |
US6508815B1 (en) | 1998-05-08 | 2003-01-21 | Novacept | Radio-frequency generator for powering an ablation device |
US6188211B1 (en) * | 1998-05-13 | 2001-02-13 | Texas Instruments Incorporated | Current-efficient low-drop-out voltage regulator with improved load regulation and frequency response |
US6212433B1 (en) | 1998-07-28 | 2001-04-03 | Radiotherapeutics Corporation | Method for treating tumors near the surface of an organ |
US6123702A (en) | 1998-09-10 | 2000-09-26 | Scimed Life Systems, Inc. | Systems and methods for controlling power in an electrosurgical probe |
US6245065B1 (en) | 1998-09-10 | 2001-06-12 | Scimed Life Systems, Inc. | Systems and methods for controlling power in an electrosurgical probe |
US6402748B1 (en) * | 1998-09-23 | 2002-06-11 | Sherwood Services Ag | Electrosurgical device having a dielectrical seal |
JP4136118B2 (en) | 1998-09-30 | 2008-08-20 | オリンパス株式会社 | Electrosurgical equipment |
DE19848540A1 (en) | 1998-10-21 | 2000-05-25 | Reinhard Kalfhaus | Circuit layout and method for operating a single- or multiphase current inverter connects an AC voltage output to a primary winding and current and a working resistance to a transformer's secondary winding and current. |
US6796981B2 (en) | 1999-09-30 | 2004-09-28 | Sherwood Services Ag | Vessel sealing system |
US20100042093A9 (en) | 1998-10-23 | 2010-02-18 | Wham Robert H | System and method for terminating treatment in impedance feedback algorithm |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US6398779B1 (en) | 1998-10-23 | 2002-06-04 | Sherwood Services Ag | Vessel sealing system |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US20040167508A1 (en) | 2002-02-11 | 2004-08-26 | Robert Wham | Vessel sealing system |
US6102497A (en) * | 1998-11-03 | 2000-08-15 | Sherwood Services Ag | Universal cart |
US6155975A (en) | 1998-11-06 | 2000-12-05 | Urich; Alex | Phacoemulsification apparatus with personal computer |
US6451015B1 (en) | 1998-11-18 | 2002-09-17 | Sherwood Services Ag | Method and system for menu-driven two-dimensional display lesion generator |
US6436096B1 (en) | 1998-11-27 | 2002-08-20 | Olympus Optical Co., Ltd. | Electrosurgical apparatus with stable coagulation |
SE520276C2 (en) * | 1999-01-25 | 2003-06-17 | Elekta Ab | Device for controlled tissue destruction |
US6464696B1 (en) | 1999-02-26 | 2002-10-15 | Olympus Optical Co., Ltd. | Electrical surgical operating apparatus |
US6398781B1 (en) | 1999-03-05 | 2002-06-04 | Gyrus Medical Limited | Electrosurgery system |
US6582427B1 (en) | 1999-03-05 | 2003-06-24 | Gyrus Medical Limited | Electrosurgery system |
US6645198B1 (en) | 1999-03-17 | 2003-11-11 | Ntero Surgical, Inc. | Systems and methods for reducing post-surgical complications |
US6939346B2 (en) | 1999-04-21 | 2005-09-06 | Oratec Interventions, Inc. | Method and apparatus for controlling a temperature-controlled probe |
US6162217A (en) | 1999-04-21 | 2000-12-19 | Oratec Interventions, Inc. | Method and apparatus for controlling a temperature-controlled probe |
US6203541B1 (en) | 1999-04-23 | 2001-03-20 | Sherwood Services Ag | Automatic activation of electrosurgical generator bipolar output |
US6258085B1 (en) | 1999-05-11 | 2001-07-10 | Sherwood Services Ag | Electrosurgical return electrode monitor |
GB9911956D0 (en) | 1999-05-21 | 1999-07-21 | Gyrus Medical Ltd | Electrosurgery system and method |
US6547786B1 (en) | 1999-05-21 | 2003-04-15 | Gyrus Medical | Electrosurgery system and instrument |
US20030181898A1 (en) | 1999-05-28 | 2003-09-25 | Bowers William J. | RF filter for an electrosurgical generator |
US6391024B1 (en) * | 1999-06-17 | 2002-05-21 | Cardiac Pacemakers, Inc. | RF ablation apparatus and method having electrode/tissue contact assessment scheme and electrocardiogram filtering |
US6692489B1 (en) * | 1999-07-21 | 2004-02-17 | Team Medical, Llc | Electrosurgical mode conversion system |
US6666860B1 (en) | 1999-08-24 | 2003-12-23 | Olympus Optical Co., Ltd. | Electric treatment system |
WO2001017452A1 (en) | 1999-09-08 | 2001-03-15 | Curon Medical, Inc. | System for controlling a family of treatment devices |
US6238388B1 (en) | 1999-09-10 | 2001-05-29 | Alan G. Ellman | Low-voltage electrosurgical apparatus |
US6402741B1 (en) | 1999-10-08 | 2002-06-11 | Sherwood Services Ag | Current and status monitor |
US6517538B1 (en) * | 1999-10-15 | 2003-02-11 | Harold Jacob | Temperature-controlled snare |
US6442434B1 (en) * | 1999-10-19 | 2002-08-27 | Abiomed, Inc. | Methods and apparatus for providing a sufficiently stable power to a load in an energy transfer system |
US6635057B2 (en) | 1999-12-02 | 2003-10-21 | Olympus Optical Co. Ltd. | Electric operation apparatus |
GB0002607D0 (en) | 2000-02-05 | 2000-03-29 | Smiths Industries Plc | Cable testing |
US6758846B2 (en) * | 2000-02-08 | 2004-07-06 | Gyrus Medical Limited | Electrosurgical instrument and an electrosurgery system including such an instrument |
US6623423B2 (en) * | 2000-02-29 | 2003-09-23 | Olympus Optical Co., Ltd. | Surgical operation system |
US6689131B2 (en) * | 2001-03-08 | 2004-02-10 | Tissuelink Medical, Inc. | Electrosurgical device having a tissue reduction sensor |
US6663623B1 (en) | 2000-03-13 | 2003-12-16 | Olympus Optical Co., Ltd. | Electric surgical operation apparatus |
US6498466B1 (en) | 2000-05-23 | 2002-12-24 | Linear Technology Corp. | Cancellation of slope compensation effect on current limit |
US6558376B2 (en) | 2000-06-30 | 2003-05-06 | Gregory D. Bishop | Method of use of an ultrasonic clamp and coagulation apparatus with tissue support surface |
US6511478B1 (en) * | 2000-06-30 | 2003-01-28 | Scimed Life Systems, Inc. | Medical probe with reduced number of temperature sensor wires |
EP1307154B1 (en) * | 2000-08-08 | 2005-02-23 | Erbe Elektromedizin GmbH | High-frequency generator for performing high-frequency surgery having adjustable power limitation |
US6730080B2 (en) | 2000-08-23 | 2004-05-04 | Olympus Corporation | Electric operation apparatus |
US6693782B1 (en) * | 2000-09-20 | 2004-02-17 | Dell Products L.P. | Surge suppression for current limiting circuits |
US6338657B1 (en) | 2000-10-20 | 2002-01-15 | Ethicon Endo-Surgery | Hand piece connector |
US6893435B2 (en) * | 2000-10-31 | 2005-05-17 | Gyrus Medical Limited | Electrosurgical system |
US6843789B2 (en) | 2000-10-31 | 2005-01-18 | Gyrus Medical Limited | Electrosurgical system |
US20030139741A1 (en) | 2000-10-31 | 2003-07-24 | Gyrus Medical Limited | Surgical instrument |
US6560470B1 (en) * | 2000-11-15 | 2003-05-06 | Datex-Ohmeda, Inc. | Electrical lockout photoplethysmographic measurement system |
US6740085B2 (en) | 2000-11-16 | 2004-05-25 | Olympus Corporation | Heating treatment system |
DE10057585A1 (en) | 2000-11-21 | 2002-05-29 | Erbe Elektromedizin | Device and method for the automatic configuration of high-frequency system elements |
US6620157B1 (en) | 2000-12-28 | 2003-09-16 | Senorx, Inc. | High frequency power source |
US20020111624A1 (en) * | 2001-01-26 | 2002-08-15 | Witt David A. | Coagulating electrosurgical instrument with tissue dam |
US20020107517A1 (en) * | 2001-01-26 | 2002-08-08 | Witt David A. | Electrosurgical instrument for coagulation and cutting |
JP2002238919A (en) | 2001-02-20 | 2002-08-27 | Olympus Optical Co Ltd | Control apparatus for medical care system and medical care system |
US6682527B2 (en) | 2001-03-13 | 2004-01-27 | Perfect Surgical Techniques, Inc. | Method and system for heating tissue with a bipolar instrument |
DE60109328T2 (en) | 2001-04-06 | 2006-04-06 | Sherwood Services Ag | VESSEL SEALING DEVICE AND VACUUM CLEANER |
US6989010B2 (en) * | 2001-04-26 | 2006-01-24 | Medtronic, Inc. | Ablation system and method of use |
US6648883B2 (en) | 2001-04-26 | 2003-11-18 | Medtronic, Inc. | Ablation system and method of use |
US6642376B2 (en) | 2001-04-30 | 2003-11-04 | North Carolina State University | Rational synthesis of heteroleptic lanthanide sandwich coordination complexes |
JP4656755B2 (en) | 2001-05-07 | 2011-03-23 | オリンパス株式会社 | Electrosurgical equipment |
US20040015159A1 (en) * | 2001-07-03 | 2004-01-22 | Syntheon, Llc | Methods and apparatus for treating the wall of a blood vessel with electromagnetic energy |
US6740079B1 (en) | 2001-07-12 | 2004-05-25 | Neothermia Corporation | Electrosurgical generator |
US6923804B2 (en) | 2001-07-12 | 2005-08-02 | Neothermia Corporation | Electrosurgical generator |
US7282048B2 (en) | 2001-08-27 | 2007-10-16 | Gyrus Medical Limited | Electrosurgical generator and system |
US6966907B2 (en) | 2001-08-27 | 2005-11-22 | Gyrus Medical Limited | Electrosurgical generator and system |
US6929641B2 (en) | 2001-08-27 | 2005-08-16 | Gyrus Medical Limited | Electrosurgical system |
US6652514B2 (en) | 2001-09-13 | 2003-11-25 | Alan G. Ellman | Intelligent selection system for electrosurgical instrument |
US6685703B2 (en) * | 2001-10-19 | 2004-02-03 | Scimed Life Systems, Inc. | Generator and probe adapter |
US6790206B2 (en) | 2002-01-31 | 2004-09-14 | Scimed Life Systems, Inc. | Compensation for power variation along patient cables |
US6733498B2 (en) | 2002-02-19 | 2004-05-11 | Live Tissue Connect, Inc. | System and method for control of tissue welding |
US20040030330A1 (en) * | 2002-04-18 | 2004-02-12 | Brassell James L. | Electrosurgery systems |
DE10218895B4 (en) | 2002-04-26 | 2006-12-21 | Storz Endoskop Produktions Gmbh | High-frequency surgical generator |
ES2289307T3 (en) | 2002-05-06 | 2008-02-01 | Covidien Ag | BLOOD DETECTOR TO CONTROL AN ELECTROCHIRURGICAL UNIT. |
US20040015216A1 (en) * | 2002-05-30 | 2004-01-22 | Desisto Stephen R. | Self-evacuating electrocautery device |
US7004174B2 (en) * | 2002-05-31 | 2006-02-28 | Neothermia Corporation | Electrosurgery with infiltration anesthesia |
US7220260B2 (en) * | 2002-06-27 | 2007-05-22 | Gyrus Medical Limited | Electrosurgical system |
US6855141B2 (en) | 2002-07-22 | 2005-02-15 | Medtronic, Inc. | Method for monitoring impedance to control power and apparatus utilizing same |
US6824539B2 (en) | 2002-08-02 | 2004-11-30 | Storz Endoskop Produktions Gmbh | Touchscreen controlling medical equipment from multiple manufacturers |
GB0221707D0 (en) * | 2002-09-18 | 2002-10-30 | Gyrus Medical Ltd | Electrical system |
US6860881B2 (en) | 2002-09-25 | 2005-03-01 | Sherwood Services Ag | Multiple RF return pad contact detection system |
US7041096B2 (en) * | 2002-10-24 | 2006-05-09 | Synergetics Usa, Inc. | Electrosurgical generator apparatus |
CA2505727A1 (en) * | 2002-11-13 | 2004-05-27 | Artemis Medical, Inc. | Devices and methods for controlling initial movement of an electrosurgical electrode |
US7799026B2 (en) * | 2002-11-14 | 2010-09-21 | Covidien Ag | Compressible jaw configuration with bipolar RF output electrodes for soft tissue fusion |
US20040097912A1 (en) | 2002-11-18 | 2004-05-20 | Gonnering Wayne J. | Electrosurgical generator and method with removable front panel having replaceable electrical connection sockets and illuminated receptacles |
US6830569B2 (en) | 2002-11-19 | 2004-12-14 | Conmed Corporation | Electrosurgical generator and method for detecting output power delivery malfunction |
US6939347B2 (en) * | 2002-11-19 | 2005-09-06 | Conmed Corporation | Electrosurgical generator and method with voltage and frequency regulated high-voltage current mode power supply |
US6875210B2 (en) | 2002-11-19 | 2005-04-05 | Conmed Corporation | Electrosurgical generator and method for cross-checking mode functionality |
US6942660B2 (en) | 2002-11-19 | 2005-09-13 | Conmed Corporation | Electrosurgical generator and method with multiple semi-autonomously executable functions |
US6948503B2 (en) | 2002-11-19 | 2005-09-27 | Conmed Corporation | Electrosurgical generator and method for cross-checking output power |
US7255694B2 (en) | 2002-12-10 | 2007-08-14 | Sherwood Services Ag | Variable output crest factor electrosurgical generator |
US7044948B2 (en) | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
JP2004208922A (en) | 2002-12-27 | 2004-07-29 | Olympus Corp | Medical apparatus, medical manipulator and control process for medical apparatus |
ES2286487T3 (en) * | 2003-01-09 | 2007-12-01 | Gyrus Medical Limited | ELECTROCHIRURGICAL GENERATOR. |
US7753909B2 (en) | 2003-05-01 | 2010-07-13 | Covidien Ag | Electrosurgical instrument which reduces thermal damage to adjacent tissue |
AU2004235739B2 (en) | 2003-05-01 | 2010-06-17 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US20050021020A1 (en) | 2003-05-15 | 2005-01-27 | Blaha Derek M. | System for activating an electrosurgical instrument |
JP4231743B2 (en) | 2003-07-07 | 2009-03-04 | オリンパス株式会社 | Biological tissue resection device |
EP1675499B1 (en) | 2003-10-23 | 2011-10-19 | Covidien AG | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
AU2003286644B2 (en) * | 2003-10-23 | 2009-09-10 | Covidien Ag | Thermocouple measurement circuit |
US7396336B2 (en) * | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
EP1684654B1 (en) | 2003-10-30 | 2014-11-12 | Covidien AG | Automatic control system for an electrosurgical generator |
US7252667B2 (en) | 2003-11-19 | 2007-08-07 | Sherwood Services Ag | Open vessel sealing instrument with cutting mechanism and distal lockout |
US7131860B2 (en) | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
AU2003294390A1 (en) | 2003-11-20 | 2005-07-14 | Sherwood Services Ag | Electrosurgical pencil with plurality of controls |
US7300435B2 (en) | 2003-11-21 | 2007-11-27 | Sherwood Services Ag | Automatic control system for an electrosurgical generator |
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 |
US7250746B2 (en) * | 2004-03-31 | 2007-07-31 | Matsushita Electric Industrial Co., Ltd. | Current mode switching regulator with predetermined on time |
US20050251117A1 (en) * | 2004-05-07 | 2005-11-10 | Anderson Robert S | Apparatus and method for treating biological external tissue |
US7282049B2 (en) | 2004-10-08 | 2007-10-16 | Sherwood Services Ag | Electrosurgical system employing multiple electrodes and method thereof |
US7628786B2 (en) * | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
US20060161148A1 (en) * | 2005-01-13 | 2006-07-20 | Robert Behnke | Circuit and method for controlling an electrosurgical generator using a full bridge topology |
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 |
US7491202B2 (en) | 2005-03-31 | 2009-02-17 | Covidien Ag | Electrosurgical forceps with slow closure sealing plates and method of sealing 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 |
US7513896B2 (en) * | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
CA2574934C (en) * | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US20070173802A1 (en) * | 2006-01-24 | 2007-07-26 | Keppel David S | Method and system for transmitting data across patient isolation barrier |
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 |
US20070173813A1 (en) | 2006-01-24 | 2007-07-26 | Sherwood Services Ag | System and method for tissue sealing |
EP1810634B8 (en) * | 2006-01-24 | 2015-06-10 | Covidien AG | System 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 |
US7651492B2 (en) | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
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 |
US7662152B2 (en) * | 2006-06-13 | 2010-02-16 | Biosense Webster, Inc. | Catheter with multi port tip for optical lesion evaluation |
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 |
US7794457B2 (en) * | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
-
2003
- 2003-05-06 ES ES03741779T patent/ES2289307T3/en not_active Expired - Lifetime
- 2003-05-06 AU AU2003265331A patent/AU2003265331B2/en not_active Ceased
- 2003-05-06 JP JP2004500710A patent/JP4490807B2/en not_active Expired - Fee Related
- 2003-05-06 WO PCT/US2003/014155 patent/WO2003092520A1/en active IP Right Grant
- 2003-05-06 US US10/513,764 patent/US7749217B2/en not_active Expired - Fee Related
- 2003-05-06 EP EP03741779A patent/EP1501435B1/en not_active Expired - Lifetime
- 2003-05-06 CA CA2484875A patent/CA2484875C/en not_active Expired - Fee Related
- 2003-05-06 DE DE60315970T patent/DE60315970T2/en not_active Expired - Lifetime
- 2003-05-06 AT AT03741779T patent/ATE371413T1/en not_active IP Right Cessation
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2008
- 2008-06-20 AU AU2008202721A patent/AU2008202721B2/en not_active Ceased
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ATE371413T1 (en) | 2007-09-15 |
WO2003092520A1 (en) | 2003-11-13 |
JP2005524441A (en) | 2005-08-18 |
DE60315970T2 (en) | 2008-05-21 |
AU2003265331B2 (en) | 2008-03-20 |
US20060025760A1 (en) | 2006-02-02 |
JP4490807B2 (en) | 2010-06-30 |
AU2008202721A1 (en) | 2008-07-10 |
ES2289307T3 (en) | 2008-02-01 |
AU2008202721B2 (en) | 2011-04-14 |
AU2008202721A2 (en) | 2008-10-02 |
DE60315970D1 (en) | 2007-10-11 |
US7749217B2 (en) | 2010-07-06 |
EP1501435B1 (en) | 2007-08-29 |
CA2484875A1 (en) | 2003-11-13 |
EP1501435A1 (en) | 2005-02-02 |
AU2003265331A1 (en) | 2003-11-17 |
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