US3601126A - High frequency electrosurgical apparatus - Google Patents
High frequency electrosurgical apparatus Download PDFInfo
- Publication number
- US3601126A US3601126A US789716A US3601126DA US3601126A US 3601126 A US3601126 A US 3601126A US 789716 A US789716 A US 789716A US 3601126D A US3601126D A US 3601126DA US 3601126 A US3601126 A US 3601126A
- Authority
- US
- United States
- Prior art keywords
- tissue
- electrode
- generating means
- amplitude
- high frequency
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 239000000853 adhesive Substances 0.000 claims description 6
- 230000001070 adhesive effect Effects 0.000 claims description 6
- 239000011148 porous material Substances 0.000 claims description 4
- 238000009877 rendering Methods 0.000 claims description 4
- 239000000463 material Substances 0.000 claims description 3
- 230000001105 regulatory effect Effects 0.000 abstract description 2
- 239000003792 electrolyte Substances 0.000 description 11
- 239000003990 capacitor Substances 0.000 description 9
- 238000000034 method Methods 0.000 description 7
- 238000004804 winding Methods 0.000 description 7
- 238000005520 cutting process Methods 0.000 description 6
- 230000001112 coagulating effect Effects 0.000 description 5
- 230000001276 controlling effect Effects 0.000 description 5
- 238000012546 transfer Methods 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
- 239000012530 fluid Substances 0.000 description 4
- 238000001228 spectrum Methods 0.000 description 3
- 230000007423 decrease Effects 0.000 description 2
- 229920001821 foam rubber Polymers 0.000 description 2
- 238000012544 monitoring process Methods 0.000 description 2
- 229920006395 saturated elastomer Polymers 0.000 description 2
- 229910001220 stainless steel Inorganic materials 0.000 description 2
- 239000010935 stainless steel Substances 0.000 description 2
- 208000032544 Cicatrix Diseases 0.000 description 1
- 239000001828 Gelatine Substances 0.000 description 1
- 239000004677 Nylon Substances 0.000 description 1
- 235000014676 Phragmites communis Nutrition 0.000 description 1
- 229920005830 Polyurethane Foam Polymers 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical class [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- 239000002390 adhesive tape Substances 0.000 description 1
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 238000000151 deposition Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000001035 drying Methods 0.000 description 1
- 238000001704 evaporation Methods 0.000 description 1
- 230000008020 evaporation Effects 0.000 description 1
- 229920000159 gelatin Polymers 0.000 description 1
- 235000019322 gelatine Nutrition 0.000 description 1
- 230000012010 growth Effects 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 239000004816 latex Substances 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 229910052754 neon Inorganic materials 0.000 description 1
- GKAOGPIIYCISHV-UHFFFAOYSA-N neon atom Chemical compound [Ne] GKAOGPIIYCISHV-UHFFFAOYSA-N 0.000 description 1
- 231100000252 nontoxic Toxicity 0.000 description 1
- 230000003000 nontoxic effect Effects 0.000 description 1
- 229920001778 nylon Polymers 0.000 description 1
- 238000011017 operating method Methods 0.000 description 1
- 230000010355 oscillation Effects 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 239000002985 plastic film Substances 0.000 description 1
- 229920006255 plastic film Polymers 0.000 description 1
- 239000011496 polyurethane foam Substances 0.000 description 1
- 239000004800 polyvinyl chloride Substances 0.000 description 1
- 230000001681 protective effect Effects 0.000 description 1
- 239000005060 rubber Substances 0.000 description 1
- 239000000523 sample Substances 0.000 description 1
- 231100000241 scar Toxicity 0.000 description 1
- 230000037390 scarring Effects 0.000 description 1
- 230000037387 scars Effects 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 230000001954 sterilising effect Effects 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/16—Indifferent or passive electrodes for grounding
-
- G—PHYSICS
- G05—CONTROLLING; REGULATING
- G05F—SYSTEMS FOR REGULATING ELECTRIC OR MAGNETIC VARIABLES
- G05F1/00—Automatic systems in which deviations of an electric quantity from one or more predetermined values are detected at the output of the system and fed back to a device within the system to restore the detected quantity to its predetermined value or values, i.e. retroactive systems
- G05F1/10—Regulating voltage or current
- G05F1/12—Regulating voltage or current wherein the variable actually regulated by the final control device is ac
Definitions
- Electrosurgical apparatus including electrodes powered by high frequency electric current, wherein the amplitude of the current flowing through the circuit is monitored and compared with a reference amplitude so that the current source can be regulated to transmit power of a desired amplitude. Further, the waveform of the current can be selectively switched from a sinusoidal waveform to a pulsed waveform. Also, there is provided an indifferent or return electrode whose conductivity controls the operation of the power source.
- Known electrosurgical apparatus generates a high frequency electric current which is fed to an active electrode.
- An indifferent electrode is placed in contact with the patient to supply a return path for the current.
- the active electrode When the active electrode is applied to tissue of the patient at the operating site, a circuit is closed and the high frequency power emitted by the active electrode generates heat at the site. The resultant heat implements the desired operative procedure.
- the amplitude of the current flowing between the electrodes is a function of the electrical resistance of the tissue current path between the electrodes. If the current generator is set to transmit a current of a given amplitude, such amplitude will be effectively related to a given load resistance. If the resistance decreases, the current amplitude increases; and vice versa.
- Another object of this invention is to provide in apparatus of the character described, means for monitoring the am plitude of the power flow to the electrodes of the apparatus and controlling the output of the high frequency generator to maintain a desired or selected power amplitude.
- the electrosurgical apparatus of the instant invention comprises a pair of electrodes applicable to biological tissue; the electrodes being powered from a high frequency generator operative to controllably vary the power amplitude.
- the apparatus further includes reference means to establish a desired power amplitude in respect to the operating current passing through the biological tissue; together with means for sensing the amplitude of the power passing through the tissue and control means for comparing the amplitudes of the desired and actual power; the control means being responsive to such amplitude comparison to regulate the operation of the generator so that the generator will transmit power having an amplitude substantially equal to the desired power amplitude.
- a cutting operation calls for a continuous wave or sinusoidal radio frequency oscillation of the current; whereas a coagulating procedure requires an oscillating current of the type pro vided by a spark gap oscillator.
- a spark gap oscillator generates a spectrum of frequencies between 0.5 mHz. and 1.5 ml-lz. This noise spectrum is distinguished by high voltage spikes with low average power values.
- Such a signal when impressed by way of the electrode on tissue, has a drying effeet which leads to a coagulating action in respect to such tissue, with very little tissue separation or cutting.
- the instant invention comprises a high frequency current generator which can be selectively controlled to operate in a continuous wave mode or a pulsed wave mode with the amplitudes of the signals being held at predetermined values.
- the input current is applied to the tissue by way of an active electrode of very small cross section so as to obtain high current densities at the operation site.
- the return or indifferent electrode must be in contact over a substantial area of the tissue so that the return current has a low density, which prevents burning or scarring of the tissue in contact with the indifferent electrode.
- the indifferent electrode or its connection to the current source is broken or faulty, the low current density is not achieved and the tissue at the situs where the high frequency currents leave, will be burned or scarred.
- the conductive state of the indifferent electrode and its connection to the current generator is monitored and the generator made inoperative when the conductive state falls below a given value.
- the indifferent electrode takes the form of a stainless steel plate which is placed under the patient and a conductive fluid is spread thereover to increase the contact area.
- a conductive fluid is spread thereover to increase the contact area.
- Such an electrode must be sterilized before each use thereof and must be prewet with conductive fluid. This procedure may lead to omissions and inexact applications of fluid.
- an inexpensive, prepackaged disposable indifferent electrode which is presterilized and prewet with conductive fluid. Such an electrode facilitates monitoring its conductive state and thus avoids tissue burns or scars.
- FIG. 1 is a circuit diagram for electrosurgical apparatus embodying the invention
- FIG. 2 is a top plan view of the indifferent electrode, forming part of the apparatus
- FIG. 3 is a sectional view taken on the line 3-3 of FIG. 2;
- FIG. 4 is an enlarged, partial sectional view of a portion of said electrode
- FIG. 5 is a top plan view showing a connector for the electrode of FIG. 2;
- FIG. 6 is a sectional view taken on the line 645 of FIG. 5.
- electrosurgical apparatus embodying the invention is indicated at 10, for operative application to selected tissue portions of a patient indicated at 12.
- the apparatus 10 comprises a high frequency current generating system including an RF. oscillator 14 which drives a gain controlled power amplifier 16.
- the power amplifier 16 is coupled via step-up transformer 18 and coupling capacitors 20, 22 to active electrode 24 and an indifferent electrode 100, respectively.
- the power output in the form of the square of the amplitude of the alternating current must be set at a selected, desired level and maintained at such level for the desired operating procedure. Such desired levels are attained by adjusting one of the two calibrated power level setting potentiometers 32, 34. The operation of the respective potentiometers 32, 34 will be hereinafter described.
- Difference amplifier 38 compares the DC voltage on line 40 with the DC voltage on line 36 and transmits a signal on line 48 to gain control amplifier 50 which amplifies the signal and transmits the same by lead 52 to a gain control terminal of power amplifier 16.
- amplifier 16 and the elements connected to its output comprise a servo system with the current sensor, square law detector, difference amplifier and gain control amplifier being the feedback loop; the signal on line 52 being the error signal and the signal on line 36 being the reference signal.
- cutting switch 54 When the indicated surgical procedure involves a cutting operation, cutting switch 54 is closed to energize relay 56 which causes transfer contact 56A to connect potentiometer 32 to lead 36, and transfer contact 56B to connect with fixed contact 56C.
- oscillator 14 transmits a continuous wave of AC signal, as will be hereinafter described, and lead 36 transmits a DC voltage related to the desired amplitude of the alternating current for the cutting operation.
- switch 58 When a coagulating action is desired, switch 58 is closed, switch 54 being open, to energize relay 60 causing its transfer contact 60A to connect with fixed contact 608; transfer contact 56A of relay 56 now connects lead 36 to potentiometer 34. in this case, oscillator 14 emits packets of alternating current, as later described, and lead 36 transmits a DC voltage related to the desired amplitude of the alternating current for a coagulating operation.
- the indifferent electrode 100 requires an electrolyte to pro vide good conductive contact with patient 12.
- the electrolyte is monitored as to quantity and the oscillator 14 is rendered inoperative when the quantity falls below a given value.
- relay 66 is not energized and oscillator 14 is made inoperative, while bulb 68 is energized to direct attention to the insufficiency of electrolyte in electrode 100.
- the R.F. oscillator 14 comprises transistor T1 and transformer 70 whose primary winding is connected between the collector of the transistor and ground.
- the output winding of the transformer is connected to a voltage source V and the input of power amplifier 16.
- the feedback winding of the transformer has one end connected to the base of the transistor, the other end being connected to transfer contact 56B, and a center tap being connected to relay contact 60A.
- the emitter of the transistor T1 is connected via contact set 66A to operating voltage source V.
- a timing capacitor 72 connects the emitter to junction 74 which is connected to fixed contact 56C.
- Resistor 76 connects junction 74 to ground while resistor 78 connects junction 74 to contact 608.
- the feedback winding of transformer 70 is connected to the emitter of the transistor via capacitor 72 and the oscillator 14 operates in the continuous wave mode with a frequency determined by the constants of the transformer, the capacitor 72 and the load on the transformer.
- the frequency may thus be set at l mHz.
- relay 60 when relay 60 is energized the center tap of transformer 70 is connected to junction 74.
- capacitor 72 charges via resistor 76, the oscillator is turned ofi until the base-emitter junction of the transistor is forward biased. At that time the oscillator oscillates at 1 mHz. for a period of time determined by the time required for capacitor 72 to discharge via resistor 78 to a value which again back biases the base-emitter junction.
- resistor 78 it is possible to cause the oscillator to block at a kHz. rate.
- the power amplifier 16 is conventional in form and whose gain is controlled by shifting its operating voltage which is supplied by line 52.
- Gain control amplifier 50, difference amplifier 38 and square-law detector 42 are known devices.
- Active electrode 24 takes the form of known electrosurgical probes regularly used in the art.
- the indifferent electrode 100 is shown in detail in FIGS. 2 4; the same comprising a conductive base member which may take the form of a sheet of plastic such as polyvinyl chloride (PVC) whose top surface is metallized as by depositing aluminum or the like thereon by known techniques.
- Tabs 112, 114 are affixed to the bottom surface of member 110 at the opposite ends thereof, in the form of adhesive tapes, for affixing the electrode to patient 12.
- a porous sheet 116 of flexible spongy material such as sponge rubber, latex or polyurethane foam, or the like, is fixed to the top metallized surface of member 110 by an appropriate adhesive.
- the porous sheet 116 is impregnated with nontoxic electrolyte such as a saturated saline solution.
- the solution is preferably rendered somewhat viscous by adding gelatine thereto, to thereby reduce the evaporation of the same.
- a protective plastic film bag 118 encloses the electrode 100 including the saturated sheet 116 and the exposed adhesive surfaces of tabs 112, 114. Bag 118 provides a leakproof container for the electrolyte contained in sheet 116, while the same is in storage. When electrode 100 is to be used, no additional electrolyte need be added to sheet 116. Also, bag 118 serves as a germproof shield for its contents and need be sterilized but once when the same is filled. The bag protects the adhesive areas of the tabs 112, 114 until ready for use in applying the electrode in place.
- the bag 1 18 is opened to expose sheet 116 and tabs 112, 114.
- the top of sheet 116 is placed against the patient and held in place by adhesive tabs- 112, l 14.
- a terminal connector is clipped to the electrode.
- Connector 120 comprises a pair of plates 122, 124 which are hingedly interconnected by ear portions extending toward each other at the side edges thereof, as at 126, 128. Plates 122, 124 are formed of Nylon or the like to be resistant to sterilizing temperatures. A spring biases the forward jawlike portions of plates 122, 124 toward each other.
- a pair of stainless steel terminal blocks 102, 104 are suitably affixed to the underside of top plate 122 and signal leads 62, 64 are respectively connected to said blocks.
- the rear portions of plates 122, 124 are pinched together to open the jaw portions to receive the edge portion of electrode 100 therebetween.
- the terminal blocks 102, 104 will then embed themselves in the porous sheet 116 to make good contact therewith.
- Terminal blocks 102, 104 are electrically interconnected only when sheet 116 is saturated with electrolyte and a measurement of the conductivity between the terminal blocks will determine the presence or absence of electrolyte.
- the on/off switch 28 may be of the conventional foot pedal operated type. Alternatively such switch may be finger operated and mounted on the active electrode 24. Also the switch may be of the reed type which has a magnet to operate the same. Obviously, the foot operated and finger operated switches may be connected in parallel to afford a maximum of convenience in operation.
- said generating means includes means for selectively operating said generating means to operate in a first mode to generate a continuous alternating current, or in a second mode to generate timespaced packets of alternating current.
- said reference means comprises means for establishing a first desired amplitude for electric current related to said continuous alternating current generated by said generating means and a second desired amplitude for electric current related to said time-spaced packets of alternating current generated by said generating means, and
- selection means for simultaneously controlling the mode of operation of said generating means and controlling which desired amplitude of electric current is received by said control means for controlling said generating means.
- said first electrode is an active electrode and said second electrode is an indifferent electrode, and means for rendering said generating means inoperative when an open circuit exists in the electrical circuit including the tissue, said indifferent electrode and said generating means.
- High frequency electrosurgical apparatus for operating on electrically conductive tissue comprising: a controllably operable generating means for generating a high frequency electric current; an active electrode adapted to be applied to tissue at the situs of the operation; an indifferent electrode for contact with tissue at the situs of the operation, said indifferent electrode comprising a sheet of porous material, adhesive means connected to said sheet of material for removably affixing said indifferent electrode to tissue, and a pair of spaced electrical terminals in contact with said porous material; circuit means for connecting said active electrode and said terminals of said indifferent electrode to said generating means; and control means for rendering said generating means inoperative when the conductivity in a circuit including the tissue, said indifferent electrode and said circuit means connecting said indifferent electrode to said generating means is less than a given value.
Landscapes
- Engineering & Computer Science (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Physics & Mathematics (AREA)
- Surgery (AREA)
- Otolaryngology (AREA)
- Heart & Thoracic Surgery (AREA)
- Plasma & Fusion (AREA)
- Radar, Positioning & Navigation (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- General Physics & Mathematics (AREA)
- Electromagnetism (AREA)
- Power Engineering (AREA)
- Biomedical Technology (AREA)
- Automation & Control Theory (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Surgical Instruments (AREA)
Abstract
Electrosurgical apparatus including electrodes powered by high frequency electric current, wherein the amplitude of the current flowing through the circuit is monitored and compared with a reference amplitude so that the current source can be regulated to transmit power of a desired amplitude. Further, the waveform of the current can be selectively switched from a sinusoidal waveform to a pulsed waveform. Also, there is provided an indifferent or return electrode whose conductivity controls the operation of the power source.
Description
United States Patent [72] Inventor Jerry R. Estes Boulder, Colo. 2: Appl. No. 789,716 [22] Filed Jan. 8, 1969 [45] Patented Aug. 24, 1971 [73] Assignee Elects-o Medical Systems, Inc.
Englewood, Colo.
[54] HIGH FREQUENCY ELECTROSURGICAL APPARATUS 5 Claims, 6 Drawing Figs.
[52] US. Cl 128/301, 128/417 [51] lnL Cl. A6111 17/36 [50] Field of Search CUTTl N6 SWlTCH a ELECTRO SURGICA L [56] References Cited UNITED STATES PATENTS 3,478,744 11/1969 Leiter 123/303. 14
FOREIGN PATENTS 1,178,528 9/1964 Germany l28/303.l7 1,139,927 11/1962 Germany l28/303.l3
Primary ExaminerL W. Trapp Attomey Philip G. Hilbert ABSTRACT: Electrosurgical apparatus including electrodes powered by high frequency electric current, wherein the amplitude of the current flowing through the circuit is monitored and compared with a reference amplitude so that the current source can be regulated to transmit power of a desired amplitude. Further, the waveform of the current can be selectively switched from a sinusoidal waveform to a pulsed waveform. Also, there is provided an indifferent or return electrode whose conductivity controls the operation of the power source.
DEVICE g INDIFFERENT ELECTRODE COAGULATlNG SWITCH I 5a -ON/OFF l b I SWITCH 2 6 l T 668} l GAIN CONTROL AMF'LlFlER g9 SQUARE LAW DETECTOR DIFFERENCE AMPLIFIER g s HIGH FREQUENCY ELECTROSURGICAL APPARATUS BACKGROUND OF THE INVENTION This invention pertains to electrosurgical apparatus and more particularly, to such apparatus which is powered by high frequency current for cutting tissue, coagulating blood vessels and fulguration of growths.
Known electrosurgical apparatus generates a high frequency electric current which is fed to an active electrode. An indifferent electrode is placed in contact with the patient to supply a return path for the current. When the active electrode is applied to tissue of the patient at the operating site, a circuit is closed and the high frequency power emitted by the active electrode generates heat at the site. The resultant heat implements the desired operative procedure.
The amplitude of the current flowing between the electrodes is a function of the electrical resistance of the tissue current path between the electrodes. If the current generator is set to transmit a current of a given amplitude, such amplitude will be effectively related to a given load resistance. If the resistance decreases, the current amplitude increases; and vice versa.
During an operation, the impedance of the tissue changes as the active electrode moves through different types of tissue. Accordingly, a selected initial setting of the current generator at the start of an operation may not produce the desired current conditions as the operation proceeds.
It is a general object of this invention to provide electrosurgical apparatus wherein the power delivered to the active electrode as the same engages the tissue, is maintained at a constant desired level during the entire operational procedure.
Another object of this invention is to provide in apparatus of the character described, means for monitoring the am plitude of the power flow to the electrodes of the apparatus and controlling the output of the high frequency generator to maintain a desired or selected power amplitude.
Essentially, the electrosurgical apparatus of the instant invention comprises a pair of electrodes applicable to biological tissue; the electrodes being powered from a high frequency generator operative to controllably vary the power amplitude. The apparatus further includes reference means to establish a desired power amplitude in respect to the operating current passing through the biological tissue; together with means for sensing the amplitude of the power passing through the tissue and control means for comparing the amplitudes of the desired and actual power; the control means being responsive to such amplitude comparison to regulate the operation of the generator so that the generator will transmit power having an amplitude substantially equal to the desired power amplitude.
It is known in the art that different operative procedures require differing high frequency current waveforms. Thus, a cutting operation calls for a continuous wave or sinusoidal radio frequency oscillation of the current; whereas a coagulating procedure requires an oscillating current of the type pro vided by a spark gap oscillator. Such a spark gap oscillator generates a spectrum of frequencies between 0.5 mHz. and 1.5 ml-lz. This noise spectrum is distinguished by high voltage spikes with low average power values. Such a signal when impressed by way of the electrode on tissue, has a drying effeet which leads to a coagulating action in respect to such tissue, with very little tissue separation or cutting.
It is believed that any waveform which spreads the signal over a reasonable frequency spectrum, will produce the same effect.
Accordingly, the instant invention comprises a high frequency current generator which can be selectively controlled to operate in a continuous wave mode or a pulsed wave mode with the amplitudes of the signals being held at predetermined values.
In electrosurgical procedures the input current is applied to the tissue by way of an active electrode of very small cross section so as to obtain high current densities at the operation site.
These high current densities provide the desired heating effects. However the return or indifferent electrode must be in contact over a substantial area of the tissue so that the return current has a low density, which prevents burning or scarring of the tissue in contact with the indifferent electrode.
If for any reason, the indifferent electrode or its connection to the current source is broken or faulty, the low current density is not achieved and the tissue at the situs where the high frequency currents leave, will be burned or scarred.
With the apparatus of the instant invention, the conductive state of the indifferent electrode and its connection to the current generator is monitored and the generator made inoperative when the conductive state falls below a given value. I
In known electrosurgical apparatus, the indifferent electrode takes the form of a stainless steel plate which is placed under the patient and a conductive fluid is spread thereover to increase the contact area. Such an electrode must be sterilized before each use thereof and must be prewet with conductive fluid. This procedure may lead to omissions and inexact applications of fluid.
In the apparatus of the instant invention there is provided an inexpensive, prepackaged disposable indifferent electrode which is presterilized and prewet with conductive fluid. Such an electrode facilitates monitoring its conductive state and thus avoids tissue burns or scars.
Other objects of this invention will in part be obvious and in part hereinafter pointed out.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a circuit diagram for electrosurgical apparatus embodying the invention;
FIG. 2 is a top plan view of the indifferent electrode, forming part of the apparatus;
FIG. 3 is a sectional view taken on the line 3-3 of FIG. 2;
FIG. 4 is an enlarged, partial sectional view of a portion of said electrode;
FIG. 5 is a top plan view showing a connector for the electrode of FIG. 2;
FIG. 6 is a sectional view taken on the line 645 of FIG. 5.
DESCRIPTION OF THE PREFERRED EMBODIMENT As shown in the drawings, and particularly FIG. 1, electrosurgical apparatus embodying the invention is indicated at 10, for operative application to selected tissue portions of a patient indicated at 12. The apparatus 10 comprises a high frequency current generating system including an RF. oscillator 14 which drives a gain controlled power amplifier 16. The power amplifier 16 is coupled via step-up transformer 18 and coupling capacitors 20, 22 to active electrode 24 and an indifferent electrode 100, respectively.
During normal operation, when on/off switch 28 is in its closed position, the output of oscillator 14 is amplified by power amplifier 16 and transformer 18 to provide a alternating current which flows via capacitor 20 and active electrode 24 to the selected tissue area in contact therewith. The current passes through the body of patient 12 to the indifferent electrode where it is returned via lead 30 and capacitor 22 to transformer 18.
The power output in the form of the square of the amplitude of the alternating current must be set at a selected, desired level and maintained at such level for the desired operating procedure. Such desired levels are attained by adjusting one of the two calibrated power level setting potentiometers 32, 34. The operation of the respective potentiometers 32, 34 will be hereinafter described.
It is assumed that a voltage indicating the desired square law power amplitude level is present on lead 36 which feeds one input of difference amplifier 38. The other input of difference amplifier 38 is a voltage on lead 40 from square-law detector 42. The inputs of detector 42 are connected to a winding 44 of a magnetic core toroid 46 through which passes lead 30 connecting indifferent electrode 100 to capacitor 22. The combination of lead 30, toroid 46 and winding 44 provides in effect a transformer acting as a current sensor.
As the alternating current flows through lead 30, it will induce an alternating current in winding 44 which is detected in detector 42 to thereby generate a DC voltage having an amplitude proportional to the square of the AC current in lead 30. Difference amplifier 38 compares the DC voltage on line 40 with the DC voltage on line 36 and transmits a signal on line 48 to gain control amplifier 50 which amplifies the signal and transmits the same by lead 52 to a gain control terminal of power amplifier 16.
The relationship of the signals is such that if the amplitude of the current in lead 30 is greater than the desired amplitude as represented by the DC voltage on line 36, the signal on line 52 has a value to decrease the gain of amplifier 16. A similar effect occurs in the opposite direction when the actual current amplitude is less than the desired amplitude. Thus, amplifier 16 and the elements connected to its output comprise a servo system with the current sensor, square law detector, difference amplifier and gain control amplifier being the feedback loop; the signal on line 52 being the error signal and the signal on line 36 being the reference signal.
When the indicated surgical procedure involves a cutting operation, cutting switch 54 is closed to energize relay 56 which causes transfer contact 56A to connect potentiometer 32 to lead 36, and transfer contact 56B to connect with fixed contact 56C. In this case, oscillator 14 transmits a continuous wave of AC signal, as will be hereinafter described, and lead 36 transmits a DC voltage related to the desired amplitude of the alternating current for the cutting operation.
When a coagulating action is desired, switch 58 is closed, switch 54 being open, to energize relay 60 causing its transfer contact 60A to connect with fixed contact 608; transfer contact 56A of relay 56 now connects lead 36 to potentiometer 34. in this case, oscillator 14 emits packets of alternating current, as later described, and lead 36 transmits a DC voltage related to the desired amplitude of the alternating current for a coagulating operation.
The indifferent electrode 100 requires an electrolyte to pro vide good conductive contact with patient 12. When the quantity of electrolyte falls below a certain level, poor contact results and the patient may sufier from burns. Accordingly, the electrolyte is monitored as to quantity and the oscillator 14 is rendered inoperative when the quantity falls below a given value.
To this end, a series circuit is established between voltage source V, lead 62, a terminal 102 of electrode 100, the electrolyte in the electrode, another terminal 104 of the electrode lead 64, switch 28, the coil of relay 66 and ground. If sufficient dectrolyte is present when switch 28 is closed, relay 66 is energized, closing contact set 66A which supplies operating pow .1" o oscillator 14, and opening contact set 66B which breaks the series circuit from voltage source V via contact set 668 and neon bulb 68 and ground to deenergize bulb 68.
If the electrolyte is insufficient, relay 66 is not energized and oscillator 14 is made inoperative, while bulb 68 is energized to direct attention to the insufficiency of electrolyte in electrode 100.
The R.F. oscillator 14 comprises transistor T1 and transformer 70 whose primary winding is connected between the collector of the transistor and ground. The output winding of the transformer is connected to a voltage source V and the input of power amplifier 16. The feedback winding of the transformer has one end connected to the base of the transistor, the other end being connected to transfer contact 56B, and a center tap being connected to relay contact 60A. The emitter of the transistor T1 is connected via contact set 66A to operating voltage source V. A timing capacitor 72 connects the emitter to junction 74 which is connected to fixed contact 56C. Resistor 76 connects junction 74 to ground while resistor 78 connects junction 74 to contact 608.
When relay 66 is energized, an operating voltage is applied to the transistor T1 by virtue of the closing of contact set 66A.
Now, if relay 56 is energized, the feedback winding of transformer 70 is connected to the emitter of the transistor via capacitor 72 and the oscillator 14 operates in the continuous wave mode with a frequency determined by the constants of the transformer, the capacitor 72 and the load on the transformer. The frequency may thus be set at l mHz. However, when relay 60 is energized the center tap of transformer 70 is connected to junction 74. Now, as capacitor 72 charges via resistor 76, the oscillator is turned ofi until the base-emitter junction of the transistor is forward biased. At that time the oscillator oscillates at 1 mHz. for a period of time determined by the time required for capacitor 72 to discharge via resistor 78 to a value which again back biases the base-emitter junction. By a suitable choice of values for resistor 78 it is possible to cause the oscillator to block at a kHz. rate.
The power amplifier 16 is conventional in form and whose gain is controlled by shifting its operating voltage which is supplied by line 52. Gain control amplifier 50, difference amplifier 38 and square-law detector 42 are known devices. Active electrode 24 takes the form of known electrosurgical probes regularly used in the art.
The indifferent electrode 100 is shown in detail in FIGS. 2 4; the same comprising a conductive base member which may take the form of a sheet of plastic such as polyvinyl chloride (PVC) whose top surface is metallized as by depositing aluminum or the like thereon by known techniques. Tabs 112, 114 are affixed to the bottom surface of member 110 at the opposite ends thereof, in the form of adhesive tapes, for affixing the electrode to patient 12.
A porous sheet 116 of flexible spongy material such as sponge rubber, latex or polyurethane foam, or the like, is fixed to the top metallized surface of member 110 by an appropriate adhesive. The porous sheet 116 is impregnated with nontoxic electrolyte such as a saturated saline solution. The solution is preferably rendered somewhat viscous by adding gelatine thereto, to thereby reduce the evaporation of the same.
A protective plastic film bag 118 encloses the electrode 100 including the saturated sheet 116 and the exposed adhesive surfaces of tabs 112, 114. Bag 118 provides a leakproof container for the electrolyte contained in sheet 116, while the same is in storage. When electrode 100 is to be used, no additional electrolyte need be added to sheet 116. Also, bag 118 serves as a germproof shield for its contents and need be sterilized but once when the same is filled. The bag protects the adhesive areas of the tabs 112, 114 until ready for use in applying the electrode in place.
At the time of use of electrode 100, the bag 1 18 is opened to expose sheet 116 and tabs 112, 114. The top of sheet 116 is placed against the patient and held in place by adhesive tabs- 112, l 14. A terminal connector is clipped to the electrode.
A terminal connector 120 for attachment to electrode 100, is shown in FIGS. 5, 6. Connector 120 comprises a pair of plates 122, 124 which are hingedly interconnected by ear portions extending toward each other at the side edges thereof, as at 126, 128. Plates 122, 124 are formed of Nylon or the like to be resistant to sterilizing temperatures. A spring biases the forward jawlike portions of plates 122, 124 toward each other.
A pair of stainless steel terminal blocks 102, 104 are suitably affixed to the underside of top plate 122 and signal leads 62, 64 are respectively connected to said blocks. To clip the connector 120 to electrode 100, the rear portions of plates 122, 124 are pinched together to open the jaw portions to receive the edge portion of electrode 100 therebetween. The terminal blocks 102, 104 will then embed themselves in the porous sheet 116 to make good contact therewith. Terminal blocks 102, 104 are electrically interconnected only when sheet 116 is saturated with electrolyte and a measurement of the conductivity between the terminal blocks will determine the presence or absence of electrolyte.
The on/off switch 28 may be of the conventional foot pedal operated type. Alternatively such switch may be finger operated and mounted on the active electrode 24. Also the switch may be of the reed type which has a magnet to operate the same. Obviously, the foot operated and finger operated switches may be connected in parallel to afford a maximum of convenience in operation.
I claim:
1. High frequency electrosurgical apparatus for operating on electrically conductive tissue comprising first and second electrodes, each of said electrodes being adapted for electrically contacting tissue whereby an electric current path is established between said electrodes via said tissue, means for generating a high frequency electric current having a controllably varying amplitude, means for connecting said generating means to said electrodes, reference means for establishing a desired amplitude for the current passing through the tissue, sensing means for sensing the amplitude of the actual current passing through the tissue, and control means responsive to said reference means and said sensing means for controlling said generating means to generate a high frequency electric current having an amplitude substantially equal to said desired amplitude.
2. Apparatus as in claim 1 wherein said generating means includes means for selectively operating said generating means to operate in a first mode to generate a continuous alternating current, or in a second mode to generate timespaced packets of alternating current.
3. Apparatus as in claim 2 wherein said reference means comprises means for establishing a first desired amplitude for electric current related to said continuous alternating current generated by said generating means and a second desired amplitude for electric current related to said time-spaced packets of alternating current generated by said generating means, and
LII
further comprising selection means for simultaneously controlling the mode of operation of said generating means and controlling which desired amplitude of electric current is received by said control means for controlling said generating means.
4. The apparatus of claim 1 wherein said first electrode is an active electrode and said second electrode is an indifferent electrode, and means for rendering said generating means inoperative when an open circuit exists in the electrical circuit including the tissue, said indifferent electrode and said generating means.
5. High frequency electrosurgical apparatus for operating on electrically conductive tissue comprising: a controllably operable generating means for generating a high frequency electric current; an active electrode adapted to be applied to tissue at the situs of the operation; an indifferent electrode for contact with tissue at the situs of the operation, said indifferent electrode comprising a sheet of porous material, adhesive means connected to said sheet of material for removably affixing said indifferent electrode to tissue, and a pair of spaced electrical terminals in contact with said porous material; circuit means for connecting said active electrode and said terminals of said indifferent electrode to said generating means; and control means for rendering said generating means inoperative when the conductivity in a circuit including the tissue, said indifferent electrode and said circuit means connecting said indifferent electrode to said generating means is less than a given value.
Claims (5)
1. High frequency electrosurgical apparatus for operating on electrically conductive tissue comprising first and second electrodes, each of said electrodes being adapted for electrically contacting tissue whereby an electric current path is established between said electrodes via said tissue, means for generating a high frequency electric current having a controllably varying amplitude, means for connecting said generating means to said electrodes, reference means for establishing a desired amplitude for the current passing through the tissue, sensing means for sensing the amplitude of the actual current passing through the tissue, and control means responsive to said reference means and said sensing means for controlling said generating means to generate a high frequency electric current having an amplitude substantially equal to said desired amplitude.
2. Apparatus as in claim 1 wherein said generating means includes means for selectively operating said generating means to operate in a first mode to generate a continuous alternating current, or in a second mode to generate time-spaced packets of alternating current.
3. Apparatus as in claim 2 wherein said reference means comprises means for establishing a first desired amplitude for electric current related to said continuous alternating current generated by said generating means and a second desired amplitude for electric current related to said time-spaced packets of alternating current generated by said generating means, and further comprising selection means for simultaneously controlling the mode of operation of said generating means and controlling which desired amplitude of electric current is received by said control means for controlling said generating means.
4. The apparatus of claim 1 wherein said first electrode is an active electrode and said second electrode is an indifferent electrode, and means for rendering said generating means inoperative when an open circuit exists in the electrical circuit including the tissue, said indifferent electrode and said generating means.
5. High frequency electrosurgical apparatus for operating on electrically conductive tissue comprising: a controllably operable generating means for generating a high frequency electric current; an active electrode adapted to be applied to tissue at the situs of the operation; an indifferent electrode for contact with tissue at the situs of the operation, said indifferent electrode comprising a sheet of porous material, adhesive means connected to said sheet of material for removably affixing said indifferent electrode to tissue, and a pair of spaced electrical terminals in contact with said porous material; circuit means for connecting said active electrode and said terminals of said indifferent electrode to said generating means; and control means for rendering said generating means inoperative when the conductivity in a circuit including the tissue, said indifferent electrode and said circuit means connecting said indifferent electrode to said generating means is less than a given value.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US78971669A | 1969-01-08 | 1969-01-08 |
Publications (1)
Publication Number | Publication Date |
---|---|
US3601126A true US3601126A (en) | 1971-08-24 |
Family
ID=25148473
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US789716A Expired - Lifetime US3601126A (en) | 1969-01-08 | 1969-01-08 | High frequency electrosurgical apparatus |
Country Status (1)
Country | Link |
---|---|
US (1) | US3601126A (en) |
Cited By (171)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2170227A1 (en) * | 1972-02-03 | 1973-09-14 | Ndm Corp | |
US3804096A (en) * | 1972-11-30 | 1974-04-16 | Dentsply Int Inc | Electrosurgical device |
US3826245A (en) * | 1973-02-09 | 1974-07-30 | Statham Instrument Inc | Electrodes employing disposable electropods for cardiac instruments |
US3885569A (en) * | 1972-11-21 | 1975-05-27 | Birtcher Corp | Electrosurgical unit |
US3897787A (en) * | 1972-12-29 | 1975-08-05 | Olympus Optical Co | Power source device for an electric surgical knife |
US3913583A (en) * | 1974-06-03 | 1975-10-21 | Sybron Corp | Control circuit for electrosurgical units |
US3923063A (en) * | 1974-07-15 | 1975-12-02 | Sybron Corp | Pulse control circuit for electrosurgical units |
US3946738A (en) * | 1974-10-24 | 1976-03-30 | Newton David W | Leakage current cancelling circuit for use with electrosurgical instrument |
US3961623A (en) * | 1975-01-17 | 1976-06-08 | Medical Research Laboratories, Inc. | Method of using a disposable electrode pad |
US3963030A (en) * | 1973-04-16 | 1976-06-15 | Valleylab, Inc. | Signal generating device and method for producing coagulation electrosurgical current |
US3964487A (en) * | 1974-12-09 | 1976-06-22 | The Birtcher Corporation | Uncomplicated load-adapting electrosurgical cutting generator |
DE2602517A1 (en) * | 1975-01-23 | 1976-07-29 | Dentsply Int Inc | ELECTROSURGICAL DEVICE |
US3987796A (en) * | 1974-04-18 | 1976-10-26 | Dentsply Research & Development Corporation | Electrosurgical device |
US4016882A (en) * | 1975-03-05 | 1977-04-12 | Cavitron Corporation | Neurosonic aspirator and method |
US4051855A (en) * | 1976-02-06 | 1977-10-04 | Ipco Hospital Supply Corporation, Whaledent International Division | Electrosurgical unit |
US4102341A (en) * | 1975-12-20 | 1978-07-25 | Olympus Optical Co., Ltd. | Electric knife device |
US4114623A (en) * | 1975-02-01 | 1978-09-19 | Karl Storz Endoscopy-America, Inc. | Cutting and coagulation apparatus for surgery |
US4114622A (en) * | 1975-07-02 | 1978-09-19 | Dentsply Research And Development Corporation | Electrosurgical device |
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 |
US4122854A (en) * | 1973-08-23 | 1978-10-31 | Matburn (Holdings) Limited | Electrosurgical apparatus |
US4126137A (en) * | 1977-01-21 | 1978-11-21 | Minnesota Mining And Manufacturing Company | Electrosurgical unit |
US4164214A (en) * | 1977-07-25 | 1979-08-14 | The Regents Of The University Of California | Method and apparatus for measuring the sensitivity of teeth |
US4184492A (en) * | 1975-08-07 | 1980-01-22 | Karl Storz Endoscopy-America, Inc. | Safety circuitry for high frequency cutting and coagulating devices |
US4188927A (en) * | 1978-01-12 | 1980-02-19 | Valleylab, Inc. | Multiple source electrosurgical generator |
EP0013613A1 (en) * | 1979-01-08 | 1980-07-23 | Johnson & Johnson Products Inc. | Electrosurgical grounding pad |
US4303073A (en) * | 1980-01-17 | 1981-12-01 | Medical Plastics, Inc. | Electrosurgery safety monitor |
US4343308A (en) * | 1980-06-09 | 1982-08-10 | Gross Robert D | Surgical ground detector |
DE3225221A1 (en) * | 1981-09-03 | 1983-03-24 | Bard Inc C R | ELECTROSURGICAL GENERATOR |
US4494541A (en) * | 1980-01-17 | 1985-01-22 | Medical Plastics, Inc. | Electrosurgery safety monitor |
US4651280A (en) * | 1983-05-24 | 1987-03-17 | Chang Sien S | Electrosurgical control system using tissue conductivity |
US4658819A (en) * | 1983-09-13 | 1987-04-21 | Valleylab, Inc. | Electrosurgical generator |
US4687004A (en) * | 1976-12-27 | 1987-08-18 | Zenex Corporation | Dual element electrical connector |
US4722761A (en) * | 1986-03-28 | 1988-02-02 | Baxter Travenol Laboratories, Inc. | Method of making a medical electrode |
US4727874A (en) * | 1984-09-10 | 1988-03-01 | C. R. Bard, Inc. | Electrosurgical generator with high-frequency pulse width modulated feedback power control |
US4769519A (en) * | 1985-06-28 | 1988-09-06 | Metcal, Inc. | Ferromagnetic element with temperature regulation |
US4818954A (en) * | 1986-02-15 | 1989-04-04 | Karl Storz Endoscopy-America, Inc. | High-frequency generator with automatic power-control for high-frequency surgery |
US4969885A (en) * | 1987-11-17 | 1990-11-13 | Erbe Elektromedizin Gmbh | High frequency surgery device for cutting and/or coagulating biologic tissue |
USRE33644E (en) * | 1985-06-28 | 1991-07-23 | Metcal, Inc. | Ferromagnetic element with temperature regulation |
US5160317A (en) * | 1991-01-03 | 1992-11-03 | Costin John A | Computer controlled smart phacoemulsification method and apparatus |
WO1993013718A1 (en) * | 1992-01-21 | 1993-07-22 | Valleylab, Inc. | Electrosurgical control for a trocar |
US5279547A (en) * | 1991-01-03 | 1994-01-18 | Alcon Surgical Inc. | Computer controlled smart phacoemulsification method and apparatus |
WO1994024951A1 (en) * | 1993-04-30 | 1994-11-10 | Medical Scientific, Inc. | Impedance feedback electrosurgical system |
US5417687A (en) * | 1993-04-30 | 1995-05-23 | Medical Scientific, Inc. | Bipolar electrosurgical trocar |
US5422567A (en) * | 1993-12-27 | 1995-06-06 | Valleylab Inc. | High frequency power measurement |
US5437662A (en) * | 1992-11-13 | 1995-08-01 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical cauterization system |
US5484434A (en) * | 1993-12-06 | 1996-01-16 | New Dimensions In Medicine, Inc. | Electrosurgical scalpel |
US5498261A (en) * | 1991-12-20 | 1996-03-12 | Advanced Cardiovascular Systems, Inc. | Thermal angioplasty system |
US5540681A (en) * | 1992-04-10 | 1996-07-30 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of tissue |
US5573533A (en) * | 1992-04-10 | 1996-11-12 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5584830A (en) * | 1994-03-30 | 1996-12-17 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5688269A (en) * | 1991-07-10 | 1997-11-18 | Electroscope, Inc. | Electrosurgical apparatus for laparoscopic and like procedures |
US5713896A (en) * | 1991-11-01 | 1998-02-03 | Medical Scientific, Inc. | Impedance feedback electrosurgical system |
US5769841A (en) * | 1995-06-13 | 1998-06-23 | Electroscope, Inc. | Electrosurgical apparatus for laparoscopic and like procedures |
US5772659A (en) * | 1995-09-26 | 1998-06-30 | Valleylab Inc. | Electrosurgical generator power control circuit and method |
US5944715A (en) * | 1996-06-20 | 1999-08-31 | Gyrus Medical Limited | Electrosurgical instrument |
US5976128A (en) * | 1996-06-14 | 1999-11-02 | Gebrueder Berchtold Gmbh & Co. | Electrosurgical high frequency generator |
US6004319A (en) * | 1995-06-23 | 1999-12-21 | Gyrus Medical Limited | Electrosurgical instrument |
US6007532A (en) * | 1997-08-29 | 1999-12-28 | 3M Innovative Properties Company | Method and apparatus for detecting loss of contact of biomedical electrodes with patient skin |
US6013076A (en) * | 1996-01-09 | 2000-01-11 | Gyrus Medical Limited | Electrosurgical instrument |
US6015406A (en) * | 1996-01-09 | 2000-01-18 | Gyrus Medical Limited | Electrosurgical instrument |
US6027501A (en) * | 1995-06-23 | 2000-02-22 | Gyrus Medical Limited | Electrosurgical instrument |
US6090106A (en) * | 1996-01-09 | 2000-07-18 | Gyrus Medical Limited | Electrosurgical instrument |
US6093186A (en) * | 1996-12-20 | 2000-07-25 | Gyrus Medical Limited | Electrosurgical generator and system |
US6210405B1 (en) | 1996-06-20 | 2001-04-03 | Gyrus Medical Limited | Under water treatment |
US6261286B1 (en) | 1995-06-23 | 2001-07-17 | Gyrus Medical Limited | Electrosurgical generator and system |
US6277114B1 (en) | 1998-04-03 | 2001-08-21 | Gyrus Medical Limited | Electrode assembly for an electrosurical instrument |
WO2002094090A3 (en) * | 2001-05-23 | 2003-03-06 | Osypka Medical Gmbh | Transformer-isolated alternating current power supply |
US6565561B1 (en) | 1996-06-20 | 2003-05-20 | Cyrus Medical Limited | Electrosurgical instrument |
US20030163058A1 (en) * | 2001-10-11 | 2003-08-28 | Osypka Markus J. | Method and apparatus for determining the left-ventricular ejection time TLVE of a heart of a subject |
WO2003092520A1 (en) | 2002-05-06 | 2003-11-13 | Sherwood Services Ag | Blood detector for controlling anesu and method therefor |
US20040116918A1 (en) * | 2002-12-17 | 2004-06-17 | Konesky Gregory A. | Electrosurgical device to generate a plasma stream |
US6780180B1 (en) | 1995-06-23 | 2004-08-24 | Gyrus Medical Limited | Electrosurgical instrument |
US6790206B2 (en) * | 2002-01-31 | 2004-09-14 | Scimed Life Systems, Inc. | Compensation for power variation along patient cables |
US20050012414A1 (en) * | 2003-07-18 | 2005-01-20 | Osypka Medical Gmbh | Method and apparatus for isolated transformation of a first voltage into a second voltage for measurement of electrical bioimpedances or bioconductances |
US20050113817A1 (en) * | 2003-11-21 | 2005-05-26 | Isaacson James D. | Tuned return electrode with matching inductor |
US20050209560A1 (en) * | 2004-03-22 | 2005-09-22 | Alcon, Inc. | Method of controlling a surgical system based on a rate of change of an operating parameter |
US20050209561A1 (en) * | 2004-03-22 | 2005-09-22 | Raphael Gordon | Method of detecting surgical events |
US20050228425A1 (en) * | 2004-03-22 | 2005-10-13 | Alcon, Inc. | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US20050267504A1 (en) * | 2004-03-22 | 2005-12-01 | Alcon, Inc. | Method of controlling a surgical system based on irrigation flow |
US20050273091A1 (en) * | 2002-10-29 | 2005-12-08 | Cathrxptyltd | System for, and method of, heating a biological site in a patient's body |
US20050277869A1 (en) * | 2004-03-22 | 2005-12-15 | Alcon, Inc. | Method of operating an ultrasound handpiece |
US20060036180A1 (en) * | 2004-08-12 | 2006-02-16 | Mikhail Boukhny | Ultrasonic handpiece |
US20060041253A1 (en) * | 2004-08-17 | 2006-02-23 | Newton David W | System and method for performing an electrosurgical procedure |
US20060041220A1 (en) * | 2004-08-12 | 2006-02-23 | Alcon, Inc. | Ultrasound handpiece |
US20060041252A1 (en) * | 2004-08-17 | 2006-02-23 | Odell Roger C | System and method for monitoring electrosurgical instruments |
US20060041251A1 (en) * | 2004-08-17 | 2006-02-23 | Odell Roger C | Electrosurgical system and method |
US7044948B2 (en) | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
US7131860B2 (en) | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US20070043303A1 (en) * | 2005-08-17 | 2007-02-22 | Osypka Markus J | Method and apparatus for digital demodulation and further processing of signals obtained in the measurement of electrical bioimpedance or bioadmittance in an object |
US7255694B2 (en) | 2002-12-10 | 2007-08-14 | Sherwood Services Ag | Variable output crest factor electrosurgical generator |
US20070255271A1 (en) * | 2000-12-28 | 2007-11-01 | Senorx, Inc. | High frequency power source |
US7300435B2 (en) | 2003-11-21 | 2007-11-27 | Sherwood Services Ag | Automatic control system for an electrosurgical generator |
US7303557B2 (en) | 1998-10-23 | 2007-12-04 | Sherwood Services Ag | Vessel sealing system |
US20080009855A1 (en) * | 2004-10-29 | 2008-01-10 | Jacques Hamou | Device For Resection And/Or Ablation Of Organic Tissue By Means Of High-Frequency Current |
US20080030206A1 (en) * | 2006-07-14 | 2008-02-07 | Sherwood Services Ag | Surgical testing instrument and system |
US20080071263A1 (en) * | 2006-09-19 | 2008-03-20 | Sherwood Services Ag | System and method for return electrode monitoring |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
USRE40388E1 (en) | 1997-04-09 | 2008-06-17 | Covidien Ag | Electrosurgical generator with adaptive power control |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US20080172076A1 (en) * | 2006-11-01 | 2008-07-17 | Alcon, Inc. | Ultrasound apparatus and method of use |
US20080281253A1 (en) * | 2007-05-10 | 2008-11-13 | Injev Valentine P | Method of Operating an Ultrasound Handpiece |
US20090030405A1 (en) * | 2003-06-03 | 2009-01-29 | Senorx, Inc. | Universal medical device control console |
US20090076493A1 (en) * | 2000-12-28 | 2009-03-19 | Senorx, Inc. | Electrosurgical medical system and method |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US20090112204A1 (en) * | 2007-10-26 | 2009-04-30 | Encision, Inc. | Multiple Parameter Fault Detection in Electrosurgical Instrument Shields |
US7628786B2 (en) | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
US7648499B2 (en) | 2006-03-21 | 2010-01-19 | Covidien Ag | System and method for generating radio frequency energy |
US7651493B2 (en) | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US7651492B2 (en) | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US20100036256A1 (en) * | 2008-08-08 | 2010-02-11 | Mikhail Boukhny | Offset ultrasonic hand piece |
US20100036464A1 (en) * | 2008-08-05 | 2010-02-11 | Tony Picciano | Electronic stimulation device |
US20100094321A1 (en) * | 2008-10-10 | 2010-04-15 | Takayuki Akahoshi | Ultrasound Handpiece |
US7722601B2 (en) | 2003-05-01 | 2010-05-25 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US7731717B2 (en) | 2006-08-08 | 2010-06-08 | Covidien Ag | System and method for controlling RF output during tissue sealing |
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 |
US20100217260A1 (en) * | 2009-02-26 | 2010-08-26 | Megadyne Medical Products, Inc. | Self-limiting electrosurgical return electrode with pressure sore reduction and heating capabilities |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US20100241023A1 (en) * | 2009-03-19 | 2010-09-23 | Tyco Healthcare Group Lp | System and Method for Return Electrode Monitoring |
US7834484B2 (en) | 2007-07-16 | 2010-11-16 | Tyco Healthcare Group Lp | Connection cable and method for activating a voltage-controlled generator |
US20100324581A1 (en) * | 2006-12-08 | 2010-12-23 | Alcon, Inc. | Torsional Ultrasound Hand Piece That Eliminates Chatter |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US20110071517A1 (en) * | 2009-09-23 | 2011-03-24 | Bovie Medical Corporation | Electrosurgical system to generate a pulsed plasma stream and method thereof |
US7927328B2 (en) | 2006-01-24 | 2011-04-19 | Covidien Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US20110137232A1 (en) * | 2009-12-09 | 2011-06-09 | Alcon Research, Ltd. | Thermal Management Algorithm For Phacoemulsification System |
US7972328B2 (en) | 2006-01-24 | 2011-07-05 | Covidien Ag | System and method for tissue sealing |
US8007494B1 (en) | 2006-04-27 | 2011-08-30 | Encision, Inc. | Device and method to prevent surgical burns |
US8034049B2 (en) | 2006-08-08 | 2011-10-11 | Covidien Ag | System and method for measuring initial tissue impedance |
US8104956B2 (en) | 2003-10-23 | 2012-01-31 | Covidien Ag | Thermocouple measurement circuit |
US8147485B2 (en) | 2006-01-24 | 2012-04-03 | Covidien Ag | System and method for tissue sealing |
US8216220B2 (en) | 2007-09-07 | 2012-07-10 | Tyco Healthcare Group Lp | System and method for transmission of combined data stream |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
US8226639B2 (en) | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
US8251989B1 (en) | 2006-06-13 | 2012-08-28 | Encision, Inc. | Combined bipolar and monopolar electrosurgical instrument and method |
US8409190B2 (en) | 2002-12-17 | 2013-04-02 | Bovie Medical Corporation | Electrosurgical device to generate a plasma stream |
US8414605B2 (en) | 2011-07-08 | 2013-04-09 | Alcon Research, Ltd. | Vacuum level control of power for phacoemulsification hand piece |
US8486061B2 (en) | 2009-01-12 | 2013-07-16 | Covidien Lp | Imaginary impedance process monitoring and intelligent shut-off |
US8512332B2 (en) | 2007-09-21 | 2013-08-20 | Covidien Lp | Real-time arc control in electrosurgical generators |
US8623040B2 (en) | 2009-07-01 | 2014-01-07 | Alcon Research, Ltd. | Phacoemulsification hook tip |
US8663214B2 (en) | 2006-01-24 | 2014-03-04 | Covidien Ag | Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
US20140114303A1 (en) * | 2010-06-25 | 2014-04-24 | Covidien Lp | Current-fed push-pull converter with passive voltage clamp |
US8734438B2 (en) | 2005-10-21 | 2014-05-27 | Covidien Ag | Circuit and method for reducing stored energy in an electrosurgical generator |
US8753334B2 (en) | 2006-05-10 | 2014-06-17 | Covidien Ag | System and method for reducing leakage current in an electrosurgical generator |
US8777941B2 (en) | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
US8784357B2 (en) | 2010-09-15 | 2014-07-22 | Alcon Research, Ltd. | Phacoemulsification hand piece with two independent transducers |
US8808161B2 (en) | 2003-10-23 | 2014-08-19 | Covidien Ag | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
US9116179B2 (en) | 2012-12-17 | 2015-08-25 | Covidien Lp | System and method for voltage and current sensing |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
US9192424B2 (en) | 2012-05-31 | 2015-11-24 | Covidien Lp | AC active load |
US9314294B2 (en) | 2008-08-18 | 2016-04-19 | Encision, Inc. | Enhanced control systems including flexible shielding and support systems for electrosurgical applications |
US9387269B2 (en) | 2011-01-28 | 2016-07-12 | Bovie Medical Corporation | Cold plasma jet hand sanitizer |
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 |
US9504516B2 (en) | 2013-05-31 | 2016-11-29 | Covidien LLP | Gain compensation for a full bridge inverter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
US9681907B2 (en) | 2010-01-28 | 2017-06-20 | Bovie Medical Corporation | Electrosurgical apparatus to generate a dual plasma stream and method thereof |
US9833281B2 (en) | 2008-08-18 | 2017-12-05 | Encision Inc. | Enhanced control systems including flexible shielding and support systems for electrosurgical applications |
US9863983B2 (en) | 2012-12-17 | 2018-01-09 | Covidien Lp | System and method for voltage and current sensing |
US9867650B2 (en) | 2013-12-26 | 2018-01-16 | Megadyne Medical Products, Inc. | Universal self-limiting electrosurgical return electrode |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US10085791B2 (en) | 2013-12-26 | 2018-10-02 | Megadyne Medical Products, Inc. | Universal self-limiting electrosurgical return electrode |
US10258505B2 (en) | 2010-09-17 | 2019-04-16 | Alcon Research, Ltd. | Balanced phacoemulsification tip |
US10281496B2 (en) | 2014-12-02 | 2019-05-07 | Covidien Lp | Electrosurgical generators and sensors |
US10278764B2 (en) | 2014-12-02 | 2019-05-07 | Covidien Lp | Electrosurgical generators and sensors |
US10292753B2 (en) | 2014-12-02 | 2019-05-21 | Covidien Lp | Electrosurgical generators and sensors |
US10908187B2 (en) | 2016-05-02 | 2021-02-02 | Covidien Lp | Current sensor with reduced voltage coupling |
US10918433B2 (en) | 2016-09-27 | 2021-02-16 | Apyx Medical Corporation | Devices, systems and methods for enhancing physiological effectiveness of medical cold plasma discharges |
US11129665B2 (en) | 2015-12-02 | 2021-09-28 | Apyx Medical Corporation | Mixing cold plasma beam jets with atmopshere |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE1139927B (en) * | 1961-01-03 | 1962-11-22 | Friedrich Laber | High-frequency surgical device |
DE1178528B (en) * | 1962-11-22 | 1964-09-24 | Parisienne D Expl Des Etabliss | Electrosurgical device for diathermic coagulation |
US3478744A (en) * | 1964-12-30 | 1969-11-18 | Harry Leiter | Surgical apparatus |
-
1969
- 1969-01-08 US US789716A patent/US3601126A/en not_active Expired - Lifetime
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE1139927B (en) * | 1961-01-03 | 1962-11-22 | Friedrich Laber | High-frequency surgical device |
DE1178528B (en) * | 1962-11-22 | 1964-09-24 | Parisienne D Expl Des Etabliss | Electrosurgical device for diathermic coagulation |
US3478744A (en) * | 1964-12-30 | 1969-11-18 | Harry Leiter | Surgical apparatus |
Cited By (310)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2170227A1 (en) * | 1972-02-03 | 1973-09-14 | Ndm Corp | |
US3848600A (en) * | 1972-02-03 | 1974-11-19 | Ndm Corp | Indifferent electrode in electrosurgical procedures and method of use |
US3885569A (en) * | 1972-11-21 | 1975-05-27 | Birtcher Corp | Electrosurgical unit |
US3804096A (en) * | 1972-11-30 | 1974-04-16 | Dentsply Int Inc | Electrosurgical device |
US3897787A (en) * | 1972-12-29 | 1975-08-05 | Olympus Optical Co | Power source device for an electric surgical knife |
US3826245A (en) * | 1973-02-09 | 1974-07-30 | Statham Instrument Inc | Electrodes employing disposable electropods for cardiac instruments |
US3963030A (en) * | 1973-04-16 | 1976-06-15 | Valleylab, Inc. | Signal generating device and method for producing coagulation electrosurgical current |
US4122854A (en) * | 1973-08-23 | 1978-10-31 | Matburn (Holdings) Limited | Electrosurgical apparatus |
US3987796A (en) * | 1974-04-18 | 1976-10-26 | Dentsply Research & Development Corporation | Electrosurgical device |
US3913583A (en) * | 1974-06-03 | 1975-10-21 | Sybron Corp | Control circuit for electrosurgical units |
US3923063A (en) * | 1974-07-15 | 1975-12-02 | Sybron Corp | Pulse control circuit for electrosurgical units |
US3946738A (en) * | 1974-10-24 | 1976-03-30 | Newton David W | Leakage current cancelling circuit for use with electrosurgical instrument |
US3964487A (en) * | 1974-12-09 | 1976-06-22 | The Birtcher Corporation | Uncomplicated load-adapting electrosurgical cutting generator |
US3961623A (en) * | 1975-01-17 | 1976-06-08 | Medical Research Laboratories, Inc. | Method of using a disposable electrode pad |
DE2602517A1 (en) * | 1975-01-23 | 1976-07-29 | Dentsply Int Inc | ELECTROSURGICAL DEVICE |
FR2298342A1 (en) * | 1975-01-23 | 1976-08-20 | Dentsply Int Inc | HIGH FREQUENCY ELECTROSURGICAL DEVICE |
US4114623A (en) * | 1975-02-01 | 1978-09-19 | Karl Storz Endoscopy-America, Inc. | Cutting and coagulation apparatus for surgery |
US4209018A (en) * | 1975-02-01 | 1980-06-24 | Karl Fastenmeier | Tissue coagulation apparatus and method |
US4016882A (en) * | 1975-03-05 | 1977-04-12 | Cavitron Corporation | Neurosonic aspirator and method |
US4114622A (en) * | 1975-07-02 | 1978-09-19 | Dentsply Research And Development Corporation | Electrosurgical device |
US4184492A (en) * | 1975-08-07 | 1980-01-22 | Karl Storz Endoscopy-America, Inc. | Safety circuitry for high frequency cutting and coagulating devices |
US4102341A (en) * | 1975-12-20 | 1978-07-25 | Olympus Optical Co., Ltd. | Electric knife device |
US4051855A (en) * | 1976-02-06 | 1977-10-04 | Ipco Hospital Supply Corporation, Whaledent International Division | Electrosurgical unit |
US4687004A (en) * | 1976-12-27 | 1987-08-18 | Zenex Corporation | Dual element electrical connector |
US4126137A (en) * | 1977-01-21 | 1978-11-21 | Minnesota Mining And Manufacturing Company | Electrosurgical unit |
US4123673A (en) * | 1977-03-14 | 1978-10-31 | Dentsply Research And Development Corporation | Control circuit for an electrical device |
US4121590A (en) * | 1977-03-14 | 1978-10-24 | Dentsply Research And Development Corporation | System for monitoring integrity of a patient return circuit |
US4164214A (en) * | 1977-07-25 | 1979-08-14 | The Regents Of The University Of California | Method and apparatus for measuring the sensitivity of teeth |
US4188927A (en) * | 1978-01-12 | 1980-02-19 | Valleylab, Inc. | Multiple source electrosurgical generator |
EP0013613A1 (en) * | 1979-01-08 | 1980-07-23 | Johnson & Johnson Products Inc. | Electrosurgical grounding pad |
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 |
US4343308A (en) * | 1980-06-09 | 1982-08-10 | Gross Robert D | Surgical ground detector |
DE3225221A1 (en) * | 1981-09-03 | 1983-03-24 | Bard Inc C R | ELECTROSURGICAL GENERATOR |
US4651280A (en) * | 1983-05-24 | 1987-03-17 | Chang Sien S | Electrosurgical control system using tissue conductivity |
US4658819A (en) * | 1983-09-13 | 1987-04-21 | Valleylab, Inc. | Electrosurgical generator |
US4727874A (en) * | 1984-09-10 | 1988-03-01 | C. R. Bard, Inc. | Electrosurgical generator with high-frequency pulse width modulated feedback power control |
USRE33644E (en) * | 1985-06-28 | 1991-07-23 | Metcal, Inc. | Ferromagnetic element with temperature regulation |
US4769519A (en) * | 1985-06-28 | 1988-09-06 | Metcal, Inc. | Ferromagnetic element with temperature regulation |
US4818954A (en) * | 1986-02-15 | 1989-04-04 | Karl Storz Endoscopy-America, Inc. | High-frequency generator with automatic power-control for high-frequency surgery |
US4722761A (en) * | 1986-03-28 | 1988-02-02 | Baxter Travenol Laboratories, Inc. | Method of making a medical electrode |
US4969885A (en) * | 1987-11-17 | 1990-11-13 | Erbe Elektromedizin Gmbh | High frequency surgery device for cutting and/or coagulating biologic tissue |
US5160317A (en) * | 1991-01-03 | 1992-11-03 | Costin John A | Computer controlled smart phacoemulsification method and apparatus |
US5279547A (en) * | 1991-01-03 | 1994-01-18 | Alcon Surgical Inc. | Computer controlled smart phacoemulsification method and apparatus |
US5520633A (en) * | 1991-01-03 | 1996-05-28 | Costin; John A. | Computer controlled smart phacoemulsification method and apparatus |
US5688269A (en) * | 1991-07-10 | 1997-11-18 | Electroscope, Inc. | Electrosurgical apparatus for laparoscopic and like procedures |
US5713896A (en) * | 1991-11-01 | 1998-02-03 | Medical Scientific, Inc. | Impedance feedback electrosurgical system |
US5498261A (en) * | 1991-12-20 | 1996-03-12 | Advanced Cardiovascular Systems, Inc. | Thermal angioplasty system |
WO1993013718A1 (en) * | 1992-01-21 | 1993-07-22 | Valleylab, Inc. | Electrosurgical control for a trocar |
US5423809A (en) * | 1992-01-21 | 1995-06-13 | Valleylab Inc. | Electrosurgical control for a trocar |
US5540681A (en) * | 1992-04-10 | 1996-07-30 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of tissue |
US5573533A (en) * | 1992-04-10 | 1996-11-12 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5437662A (en) * | 1992-11-13 | 1995-08-01 | American Cardiac Ablation Co., Inc. | Fluid cooled electrosurgical cauterization system |
US5417687A (en) * | 1993-04-30 | 1995-05-23 | Medical Scientific, Inc. | Bipolar electrosurgical trocar |
US5658279A (en) * | 1993-04-30 | 1997-08-19 | Medical Scientific, Inc. | Bipolar electrosurgical trocar |
WO1994024949A1 (en) * | 1993-04-30 | 1994-11-10 | Medical Scientific, Inc. | Impedance feedback electrosurgical system |
WO1994024951A1 (en) * | 1993-04-30 | 1994-11-10 | Medical Scientific, Inc. | Impedance feedback electrosurgical system |
US5484434A (en) * | 1993-12-06 | 1996-01-16 | New Dimensions In Medicine, Inc. | Electrosurgical scalpel |
US5422567A (en) * | 1993-12-27 | 1995-06-06 | Valleylab Inc. | High frequency power measurement |
US5584830A (en) * | 1994-03-30 | 1996-12-17 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of cardiac tissue |
US5769841A (en) * | 1995-06-13 | 1998-06-23 | Electroscope, Inc. | Electrosurgical apparatus for laparoscopic and like procedures |
US6364877B1 (en) | 1995-06-23 | 2002-04-02 | Gyrus Medical Limited | Electrosurgical generator and system |
US6780180B1 (en) | 1995-06-23 | 2004-08-24 | Gyrus Medical Limited | Electrosurgical instrument |
US6004319A (en) * | 1995-06-23 | 1999-12-21 | Gyrus Medical Limited | Electrosurgical instrument |
US6416509B1 (en) | 1995-06-23 | 2002-07-09 | Gyrus Medical Limited | Electrosurgical generator and system |
US6306134B1 (en) | 1995-06-23 | 2001-10-23 | Gyrus Medical Limited | Electrosurgical generator and system |
US6293942B1 (en) | 1995-06-23 | 2001-09-25 | Gyrus Medical Limited | Electrosurgical generator method |
US6027501A (en) * | 1995-06-23 | 2000-02-22 | Gyrus Medical Limited | Electrosurgical instrument |
US6056746A (en) * | 1995-06-23 | 2000-05-02 | Gyrus Medical Limited | Electrosurgical instrument |
US6261286B1 (en) | 1995-06-23 | 2001-07-17 | Gyrus Medical Limited | Electrosurgical generator and system |
US6174308B1 (en) | 1995-06-23 | 2001-01-16 | Gyrus Medical Limited | Electrosurgical instrument |
US5772659A (en) * | 1995-09-26 | 1998-06-30 | Valleylab Inc. | Electrosurgical generator power control circuit and method |
US6251106B1 (en) | 1995-09-26 | 2001-06-26 | Sherwood Services Ag | Electrosurgical generator power control circuit and method |
US6234178B1 (en) | 1996-01-09 | 2001-05-22 | Gyrus Medical Limited | Electrosurgical instrument |
US6090106A (en) * | 1996-01-09 | 2000-07-18 | Gyrus Medical Limited | Electrosurgical instrument |
US6015406A (en) * | 1996-01-09 | 2000-01-18 | Gyrus Medical Limited | Electrosurgical instrument |
US6013076A (en) * | 1996-01-09 | 2000-01-11 | Gyrus Medical Limited | Electrosurgical instrument |
US5976128A (en) * | 1996-06-14 | 1999-11-02 | Gebrueder Berchtold Gmbh & Co. | Electrosurgical high frequency generator |
US6210405B1 (en) | 1996-06-20 | 2001-04-03 | Gyrus Medical Limited | Under water treatment |
US6482202B1 (en) | 1996-06-20 | 2002-11-19 | Gyrus Medical Limited | Under water treatment |
US5944715A (en) * | 1996-06-20 | 1999-08-31 | Gyrus Medical Limited | Electrosurgical instrument |
US6565561B1 (en) | 1996-06-20 | 2003-05-20 | Cyrus Medical Limited | Electrosurgical instrument |
US6093186A (en) * | 1996-12-20 | 2000-07-25 | Gyrus Medical Limited | Electrosurgical generator and system |
USRE40388E1 (en) | 1997-04-09 | 2008-06-17 | Covidien Ag | Electrosurgical generator with adaptive power control |
US6007532A (en) * | 1997-08-29 | 1999-12-28 | 3M Innovative Properties Company | Method and apparatus for detecting loss of contact of biomedical electrodes with patient skin |
US6277114B1 (en) | 1998-04-03 | 2001-08-21 | Gyrus Medical Limited | Electrode assembly for an electrosurical instrument |
US8105323B2 (en) | 1998-10-23 | 2012-01-31 | Covidien Ag | Method and system for controlling output of RF medical generator |
US7303557B2 (en) | 1998-10-23 | 2007-12-04 | 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 |
US8287528B2 (en) | 1998-10-23 | 2012-10-16 | Covidien Ag | Vessel sealing system |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US9113900B2 (en) | 1998-10-23 | 2015-08-25 | Covidien Ag | Method and system for controlling output of RF medical generator |
US9168089B2 (en) | 1998-10-23 | 2015-10-27 | Covidien Ag | Method and system for controlling output of RF medical generator |
US20090088737A1 (en) * | 2000-12-28 | 2009-04-02 | Senorx, Inc. | Electrosurgical medical system and method |
US9517104B2 (en) | 2000-12-28 | 2016-12-13 | Senorx, Inc. | Electrosurgical medical system and method |
US10278763B2 (en) | 2000-12-28 | 2019-05-07 | Senorx, Inc. | Electrosurgical medical system and method |
US10172664B2 (en) | 2000-12-28 | 2019-01-08 | Senorx, Inc. | Electrosurgical medical system and method |
US8231615B2 (en) | 2000-12-28 | 2012-07-31 | Senorx, Inc. | Electrosurgical medical system and method |
US9750558B2 (en) | 2000-12-28 | 2017-09-05 | Senorx, Inc. | Electrosurgical medical system and method |
US20070282322A1 (en) * | 2000-12-28 | 2007-12-06 | Senorx, Inc. | High frequency power source |
US9750557B2 (en) * | 2000-12-28 | 2017-09-05 | Senorx, Inc. | High frequency power source |
US8882760B2 (en) | 2000-12-28 | 2014-11-11 | Senorx, Inc. | Electrosurgical medical system and method |
US10517663B2 (en) | 2000-12-28 | 2019-12-31 | Senorx, Inc. | Electrosurgical medical system and method |
US9408664B2 (en) | 2000-12-28 | 2016-08-09 | Senorx, Inc. | Electrosurgical medical system and method |
US8764741B2 (en) | 2000-12-28 | 2014-07-01 | Senorx, Inc. | High frequency power source |
US20090076493A1 (en) * | 2000-12-28 | 2009-03-19 | Senorx, Inc. | Electrosurgical medical system and method |
US20090069799A1 (en) * | 2000-12-28 | 2009-03-12 | Senorx, Inc. | Electrosurgical medical system and method |
US8475446B2 (en) | 2000-12-28 | 2013-07-02 | Senorx, Inc. | Electrosurgical medical system and method |
US20070255271A1 (en) * | 2000-12-28 | 2007-11-01 | Senorx, Inc. | High frequency power source |
WO2002094090A3 (en) * | 2001-05-23 | 2003-03-06 | Osypka Medical Gmbh | Transformer-isolated alternating current power supply |
US20040152996A1 (en) * | 2001-05-23 | 2004-08-05 | Eberhard Gersing | Transformer-isolated alternating current power supply |
US7904141B2 (en) | 2001-10-11 | 2011-03-08 | Osypka Medical Gmbh | System and apparatus for determining the left-ventricular ejection time TLVE of a heart of a subject |
US20110190601A1 (en) * | 2001-10-11 | 2011-08-04 | Osypka Markus J | System for Determining the Left-Ventricular Ejection Time TLVE of a Heart of a Subject |
US20060167363A1 (en) * | 2001-10-11 | 2006-07-27 | Osypka Medical Gmbh | System and apparatus for determining the left-ventricular ejection time TLVE of a heart of a subject |
US7822470B2 (en) | 2001-10-11 | 2010-10-26 | Osypka Medical Gmbh | Method for determining the left-ventricular ejection time TLVE of a heart of a subject |
US8562538B2 (en) | 2001-10-11 | 2013-10-22 | Osypka Medical Gmbh | System for determining the left-ventricular ejection time TLVE of a heart of a subject |
US20030163058A1 (en) * | 2001-10-11 | 2003-08-28 | Osypka Markus J. | Method and apparatus for determining the left-ventricular ejection time TLVE of a heart of a subject |
US6790206B2 (en) * | 2002-01-31 | 2004-09-14 | Scimed Life Systems, Inc. | Compensation for power variation along patient cables |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
WO2003092520A1 (en) | 2002-05-06 | 2003-11-13 | Sherwood Services Ag | Blood detector for controlling anesu and method therefor |
US20060025760A1 (en) * | 2002-05-06 | 2006-02-02 | Podhajsky Ronald J | Blood detector for controlling anesu and method therefor |
US7749217B2 (en) | 2002-05-06 | 2010-07-06 | Covidien Ag | Method and system for optically detecting blood and controlling a generator during electrosurgery |
US7871410B2 (en) * | 2002-10-29 | 2011-01-18 | Cathrx Ltd | System for, and method of, heating a biological site in a patient's body |
US20050273091A1 (en) * | 2002-10-29 | 2005-12-08 | Cathrxptyltd | System for, and method of, heating a biological site in a patient's body |
US7824400B2 (en) | 2002-12-10 | 2010-11-02 | Covidien Ag | Circuit for controlling arc energy from an electrosurgical generator |
US7044948B2 (en) | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
US7255694B2 (en) | 2002-12-10 | 2007-08-14 | Sherwood Services Ag | Variable output crest factor electrosurgical generator |
US8523855B2 (en) | 2002-12-10 | 2013-09-03 | Covidien Ag | Circuit for controlling arc energy from an electrosurgical generator |
US8409190B2 (en) | 2002-12-17 | 2013-04-02 | Bovie Medical Corporation | Electrosurgical device to generate a plasma stream |
US7316682B2 (en) * | 2002-12-17 | 2008-01-08 | Aaron Medical Industries, Inc. | Electrosurgical device to generate a plasma stream |
US20040116918A1 (en) * | 2002-12-17 | 2004-06-17 | Konesky Gregory A. | Electrosurgical device to generate a plasma stream |
US7722601B2 (en) | 2003-05-01 | 2010-05-25 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US8080008B2 (en) | 2003-05-01 | 2011-12-20 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US8012150B2 (en) | 2003-05-01 | 2011-09-06 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US8267929B2 (en) | 2003-05-01 | 2012-09-18 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US8298223B2 (en) | 2003-05-01 | 2012-10-30 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US8303580B2 (en) | 2003-05-01 | 2012-11-06 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US20090030405A1 (en) * | 2003-06-03 | 2009-01-29 | Senorx, Inc. | Universal medical device control console |
US20100114335A1 (en) * | 2003-06-03 | 2010-05-06 | Senrx, Inc. | Universal medical device control consol |
US8696650B2 (en) | 2003-06-03 | 2014-04-15 | Senorx, Inc. | Universal medical device control console |
US10912541B2 (en) | 2003-06-03 | 2021-02-09 | Senorx, Inc. | Universal medical device control console |
US8652121B2 (en) | 2003-06-03 | 2014-02-18 | Senorx, Inc. | Universal medical device control console |
US20050012414A1 (en) * | 2003-07-18 | 2005-01-20 | Osypka Medical Gmbh | Method and apparatus for isolated transformation of a first voltage into a second voltage for measurement of electrical bioimpedances or bioconductances |
US8104956B2 (en) | 2003-10-23 | 2012-01-31 | Covidien Ag | Thermocouple measurement circuit |
US8808161B2 (en) | 2003-10-23 | 2014-08-19 | Covidien Ag | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
US8647340B2 (en) | 2003-10-23 | 2014-02-11 | Covidien Ag | Thermocouple measurement system |
US8096961B2 (en) | 2003-10-30 | 2012-01-17 | Covidien Ag | Switched resonant ultrasonic power amplifier system |
US8113057B2 (en) | 2003-10-30 | 2012-02-14 | Covidien Ag | Switched resonant ultrasonic power amplifier system |
US8966981B2 (en) | 2003-10-30 | 2015-03-03 | Covidien Ag | Switched resonant ultrasonic power amplifier system |
US9768373B2 (en) | 2003-10-30 | 2017-09-19 | Covidien Ag | Switched resonant ultrasonic power amplifier system |
US8485993B2 (en) | 2003-10-30 | 2013-07-16 | Covidien Ag | Switched resonant ultrasonic power amplifier system |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US7766693B2 (en) | 2003-11-20 | 2010-08-03 | Covidien Ag | Connector systems for electrosurgical generator |
US7131860B2 (en) | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US7416437B2 (en) | 2003-11-20 | 2008-08-26 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US20070049916A1 (en) * | 2003-11-21 | 2007-03-01 | Megadyne Medical Products, Inc. | Tuned return electrode with matching inductor |
US7837680B2 (en) | 2003-11-21 | 2010-11-23 | Megadyne Medical Products, Inc. | Tuned return electrode with matching inductor |
US20050113817A1 (en) * | 2003-11-21 | 2005-05-26 | Isaacson James D. | Tuned return electrode with matching inductor |
US7300435B2 (en) | 2003-11-21 | 2007-11-27 | Sherwood Services Ag | Automatic control system for an electrosurgical generator |
US7169145B2 (en) * | 2003-11-21 | 2007-01-30 | Megadyne Medical Products, Inc. | Tuned return electrode with matching inductor |
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 |
US20100036406A1 (en) * | 2004-03-22 | 2010-02-11 | Alcon, Inc. | Method of Controlling a Surgical System Based on a Load on the Cutting Tip of a Handpiece |
US8172786B2 (en) | 2004-03-22 | 2012-05-08 | Alcon Research, Ltd. | Method of operating an ultrasound handpiece |
US7625388B2 (en) | 2004-03-22 | 2009-12-01 | Alcon, Inc. | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US7727193B2 (en) | 2004-03-22 | 2010-06-01 | Alcon, Inc. | Method of controlling a surgical system based on a rate of change of an operating parameter |
US8403851B2 (en) | 2004-03-22 | 2013-03-26 | Novartis Ag | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US8257307B2 (en) | 2004-03-22 | 2012-09-04 | Alcon Research, Ltd. | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US20050209560A1 (en) * | 2004-03-22 | 2005-09-22 | Alcon, Inc. | Method of controlling a surgical system based on a rate of change of an operating parameter |
US20050209561A1 (en) * | 2004-03-22 | 2005-09-22 | Raphael Gordon | Method of detecting surgical events |
US8430838B2 (en) | 2004-03-22 | 2013-04-30 | Novartis Ag | Method of controlling a surgical system based on irrigation flow |
US7811255B2 (en) | 2004-03-22 | 2010-10-12 | Alcon, Inc. | Method of controlling a surgical system based on a rate of change of an operating parameter |
US20100130914A1 (en) * | 2004-03-22 | 2010-05-27 | Alcon, Inc. | Method Of Controlling A Surgical System Based On Irrigation Flow |
US7713202B2 (en) | 2004-03-22 | 2010-05-11 | Alcon, Inc. | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US20050228425A1 (en) * | 2004-03-22 | 2005-10-13 | Alcon, Inc. | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US20050261628A1 (en) * | 2004-03-22 | 2005-11-24 | Alcon, Inc. | Method of controlling a surgical system based on a rate of change of an operating parameter |
US20050261715A1 (en) * | 2004-03-22 | 2005-11-24 | Alcon, Inc. | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US20050267504A1 (en) * | 2004-03-22 | 2005-12-01 | Alcon, Inc. | Method of controlling a surgical system based on irrigation flow |
US20110015563A1 (en) * | 2004-03-22 | 2011-01-20 | Alcon, Inc. | Method Of Controlling A Surgical System Based On A Rate Of Change Of An Operating Parameter |
US20050277869A1 (en) * | 2004-03-22 | 2005-12-15 | Alcon, Inc. | Method of operating an ultrasound handpiece |
US20090306583A1 (en) * | 2004-03-22 | 2009-12-10 | Mikhail Boukhny | Method of Operating An Ultrasound Handpiece |
US8523812B2 (en) | 2004-03-22 | 2013-09-03 | Alcon Research, Ltd. | Method of controlling a surgical system based on a rate of change of an operating parameter |
US7572242B2 (en) | 2004-03-22 | 2009-08-11 | Alcon, Inc. | Method of operating an ultrasound handpiece |
US7758538B2 (en) | 2004-03-22 | 2010-07-20 | Alcon, Inc. | Method of controlling a surgical system based on irrigation flow |
US7645255B2 (en) | 2004-03-22 | 2010-01-12 | Alcon, Inc. | Method of controlling a surgical system based on irrigation flow |
US9282989B2 (en) | 2004-03-22 | 2016-03-15 | Novartis Ag | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US8048020B2 (en) | 2004-03-22 | 2011-11-01 | Alcon, Inc. | Method of controlling a surgical system based on irrigation flow |
US8974412B2 (en) | 2004-03-22 | 2015-03-10 | Novartis Ag | Method of controlling a surgical system based on a load on the cutting tip of a handpiece |
US7645256B2 (en) | 2004-08-12 | 2010-01-12 | Alcon, Inc. | Ultrasound handpiece |
US7651490B2 (en) | 2004-08-12 | 2010-01-26 | Alcon, Inc. | Ultrasonic handpiece |
US8771301B2 (en) | 2004-08-12 | 2014-07-08 | Alcon Research, Ltd. | Ultrasonic handpiece |
US20100004585A1 (en) * | 2004-08-12 | 2010-01-07 | Mikhail Boukhny | Ultrasonic Handpiece |
US20060041220A1 (en) * | 2004-08-12 | 2006-02-23 | Alcon, Inc. | Ultrasound handpiece |
US20060036180A1 (en) * | 2004-08-12 | 2006-02-16 | Mikhail Boukhny | Ultrasonic handpiece |
US8814894B2 (en) | 2004-08-12 | 2014-08-26 | Novartis Ag | Ultrasound handpiece |
US20060041253A1 (en) * | 2004-08-17 | 2006-02-23 | Newton David W | System and method for performing an electrosurgical procedure |
US20060041251A1 (en) * | 2004-08-17 | 2006-02-23 | Odell Roger C | Electrosurgical system and method |
US20060041252A1 (en) * | 2004-08-17 | 2006-02-23 | Odell Roger C | System and method for monitoring electrosurgical instruments |
US8758336B2 (en) | 2004-08-17 | 2014-06-24 | Encision, Inc. | System and method for monitoring electrosurgical systems |
US7465302B2 (en) | 2004-08-17 | 2008-12-16 | Encision, Inc. | System and method for performing an electrosurgical procedure |
US7422589B2 (en) | 2004-08-17 | 2008-09-09 | Encision, Inc. | System and method for performing an electrosurgical procedure |
US7628786B2 (en) | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
US8025660B2 (en) | 2004-10-13 | 2011-09-27 | Covidien Ag | Universal foot switch contact port |
US20080009855A1 (en) * | 2004-10-29 | 2008-01-10 | Jacques Hamou | Device For Resection And/Or Ablation Of Organic Tissue By Means Of High-Frequency Current |
US7789880B2 (en) * | 2004-10-29 | 2010-09-07 | Jacques Hamou | Device for resection and/or ablation of organic tissue by means of high-frequency current |
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 |
US11013548B2 (en) | 2005-03-31 | 2021-05-25 | Covidien Ag | Method and system for compensating for external impedance of energy carrying component when controlling electrosurgical generator |
US10470718B2 (en) | 2005-08-17 | 2019-11-12 | Osypka Medical Gmbh | Method for digital demodulation and further processing of signals obtained in the measurement of electrical bioimpedance or bioadmittance in a human subject |
US20070043303A1 (en) * | 2005-08-17 | 2007-02-22 | Osypka Markus J | Method and apparatus for digital demodulation and further processing of signals obtained in the measurement of electrical bioimpedance or bioadmittance in an object |
US11642088B2 (en) | 2005-08-17 | 2023-05-09 | Osypka Medical Gmbh | Method and apparatus for digital demodulation and further processing of signals obtained in the measurement of electrical bioimpedance or bioadmittance in an object |
US9522032B2 (en) | 2005-10-21 | 2016-12-20 | Covidien Ag | Circuit and method for reducing stored energy in an electrosurgical generator |
US8734438B2 (en) | 2005-10-21 | 2014-05-27 | Covidien Ag | Circuit and method for reducing stored energy in an electrosurgical generator |
US8241278B2 (en) | 2005-12-12 | 2012-08-14 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US8147485B2 (en) | 2006-01-24 | 2012-04-03 | Covidien Ag | System and method for tissue sealing |
US10582964B2 (en) | 2006-01-24 | 2020-03-10 | Covidien Lp | Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US8202271B2 (en) | 2006-01-24 | 2012-06-19 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US7972328B2 (en) | 2006-01-24 | 2011-07-05 | Covidien Ag | System and method for tissue sealing |
US9642665B2 (en) | 2006-01-24 | 2017-05-09 | Covidien Ag | Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
US8267928B2 (en) | 2006-01-24 | 2012-09-18 | Covidien Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US8187262B2 (en) | 2006-01-24 | 2012-05-29 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
US8663214B2 (en) | 2006-01-24 | 2014-03-04 | Covidien Ag | Method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
US8475447B2 (en) | 2006-01-24 | 2013-07-02 | Covidien Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
US7927328B2 (en) | 2006-01-24 | 2011-04-19 | Covidien 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 |
US7972332B2 (en) | 2006-03-03 | 2011-07-05 | 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 |
US8556890B2 (en) | 2006-04-24 | 2013-10-15 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US9119624B2 (en) | 2006-04-24 | 2015-09-01 | Covidien Ag | ARC based adaptive control system for an electrosurgical unit |
US8007494B1 (en) | 2006-04-27 | 2011-08-30 | Encision, Inc. | Device and method to prevent surgical burns |
US8753334B2 (en) | 2006-05-10 | 2014-06-17 | Covidien Ag | System and method for reducing leakage current in an electrosurgical generator |
US8251989B1 (en) | 2006-06-13 | 2012-08-28 | Encision, Inc. | Combined bipolar and monopolar electrosurgical instrument and method |
US7804308B2 (en) | 2006-07-14 | 2010-09-28 | Covidien Ag | Surgical testing instrument and system |
US20090039900A1 (en) * | 2006-07-14 | 2009-02-12 | Covidien Ag | Surgical Testing Instrument and System |
US20080030206A1 (en) * | 2006-07-14 | 2008-02-07 | Sherwood Services Ag | Surgical testing instrument and system |
US7443175B2 (en) | 2006-07-14 | 2008-10-28 | Covidien Ag | Surgical testing instrument and system |
US7731717B2 (en) | 2006-08-08 | 2010-06-08 | Covidien Ag | System and method for controlling RF output during tissue sealing |
US8034049B2 (en) | 2006-08-08 | 2011-10-11 | Covidien Ag | System and method for measuring initial tissue impedance |
US7637907B2 (en) | 2006-09-19 | 2009-12-29 | Covidien Ag | System and method for return electrode monitoring |
US20080071263A1 (en) * | 2006-09-19 | 2008-03-20 | Sherwood Services Ag | System and method for return electrode monitoring |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US8231616B2 (en) | 2006-09-28 | 2012-07-31 | Covidien Ag | Transformer for RF voltage sensing |
US20080172076A1 (en) * | 2006-11-01 | 2008-07-17 | Alcon, Inc. | Ultrasound apparatus and method of use |
US8579929B2 (en) | 2006-12-08 | 2013-11-12 | Alcon Research, Ltd. | Torsional ultrasound hand piece that eliminates chatter |
US20100324581A1 (en) * | 2006-12-08 | 2010-12-23 | Alcon, Inc. | Torsional Ultrasound Hand Piece That Eliminates Chatter |
US8777941B2 (en) | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
US8303530B2 (en) | 2007-05-10 | 2012-11-06 | Novartis Ag | Method of operating an ultrasound handpiece |
US20080281253A1 (en) * | 2007-05-10 | 2008-11-13 | Injev Valentine P | Method of Operating an Ultrasound Handpiece |
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 |
US8353905B2 (en) | 2007-09-07 | 2013-01-15 | Covidien 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 |
US9271790B2 (en) | 2007-09-21 | 2016-03-01 | Coviden Lp | Real-time arc control in electrosurgical generators |
US8460284B2 (en) | 2007-10-26 | 2013-06-11 | Encision, Inc. | Multiple parameter fault detection in electrosurgical instrument shields |
US9254165B2 (en) | 2007-10-26 | 2016-02-09 | Encision, Inc. | Multiple parameter fault detection in electrosurgical instrument shields |
US20090112204A1 (en) * | 2007-10-26 | 2009-04-30 | Encision, Inc. | Multiple Parameter Fault Detection in Electrosurgical Instrument Shields |
US9757183B2 (en) | 2007-10-26 | 2017-09-12 | Encision Inc. | Multiple parameter fault detection in electrosurgical instrument shields |
US8226639B2 (en) | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
US20100036464A1 (en) * | 2008-08-05 | 2010-02-11 | Tony Picciano | Electronic stimulation device |
US8340756B2 (en) | 2008-08-05 | 2012-12-25 | Tony Picciano | Electronic stimulation device |
US20100036256A1 (en) * | 2008-08-08 | 2010-02-11 | Mikhail Boukhny | Offset ultrasonic hand piece |
US9833281B2 (en) | 2008-08-18 | 2017-12-05 | Encision Inc. | Enhanced control systems including flexible shielding and support systems for electrosurgical applications |
US9314294B2 (en) | 2008-08-18 | 2016-04-19 | Encision, Inc. | Enhanced control systems including flexible shielding and support systems for electrosurgical applications |
US20100094321A1 (en) * | 2008-10-10 | 2010-04-15 | Takayuki Akahoshi | Ultrasound Handpiece |
US8486061B2 (en) | 2009-01-12 | 2013-07-16 | Covidien Lp | Imaginary impedance process monitoring and intelligent shut-off |
US20100217260A1 (en) * | 2009-02-26 | 2010-08-26 | Megadyne Medical Products, Inc. | Self-limiting electrosurgical return electrode with pressure sore reduction and heating capabilities |
US8876812B2 (en) | 2009-02-26 | 2014-11-04 | Megadyne Medical Products, Inc. | Self-limiting electrosurgical return electrode with pressure sore reduction and heating capabilities |
US20100241023A1 (en) * | 2009-03-19 | 2010-09-23 | Tyco Healthcare Group Lp | System and Method for Return Electrode Monitoring |
US8298225B2 (en) | 2009-03-19 | 2012-10-30 | Tyco Healthcare Group Lp | System and method for return electrode monitoring |
US9233021B2 (en) | 2009-07-01 | 2016-01-12 | Alcon Research, Ltd. | Phacoemulsification hook tip |
US8623040B2 (en) | 2009-07-01 | 2014-01-07 | Alcon Research, Ltd. | Phacoemulsification hook tip |
US9649143B2 (en) | 2009-09-23 | 2017-05-16 | Bovie Medical Corporation | Electrosurgical system to generate a pulsed plasma stream and method thereof |
US20110071517A1 (en) * | 2009-09-23 | 2011-03-24 | Bovie Medical Corporation | Electrosurgical system to generate a pulsed plasma stream and method thereof |
US8070711B2 (en) | 2009-12-09 | 2011-12-06 | Alcon Research, Ltd. | Thermal management algorithm for phacoemulsification system |
US20110137232A1 (en) * | 2009-12-09 | 2011-06-09 | Alcon Research, Ltd. | Thermal Management Algorithm For Phacoemulsification System |
US9681907B2 (en) | 2010-01-28 | 2017-06-20 | Bovie Medical Corporation | Electrosurgical apparatus to generate a dual plasma stream and method thereof |
US20140114303A1 (en) * | 2010-06-25 | 2014-04-24 | Covidien Lp | Current-fed push-pull converter with passive voltage clamp |
US9522041B2 (en) * | 2010-06-25 | 2016-12-20 | Covidien Lp | Current-fed push-pull converter with passive voltage clamp |
US8784357B2 (en) | 2010-09-15 | 2014-07-22 | Alcon Research, Ltd. | Phacoemulsification hand piece with two independent transducers |
US10258505B2 (en) | 2010-09-17 | 2019-04-16 | Alcon Research, Ltd. | Balanced phacoemulsification tip |
US9601317B2 (en) | 2011-01-28 | 2017-03-21 | Bovie Medical Corporation | Cold plasma sanitizing device |
US9387269B2 (en) | 2011-01-28 | 2016-07-12 | Bovie Medical Corporation | Cold plasma jet hand sanitizer |
US8414605B2 (en) | 2011-07-08 | 2013-04-09 | Alcon Research, Ltd. | Vacuum level control of power for phacoemulsification hand piece |
US9192424B2 (en) | 2012-05-31 | 2015-11-24 | Covidien Lp | AC active load |
US9116179B2 (en) | 2012-12-17 | 2015-08-25 | Covidien Lp | System and method for voltage and current sensing |
US9366703B2 (en) | 2012-12-17 | 2016-06-14 | Covidien Lp | System and method for voltage and current sensing |
US9863983B2 (en) | 2012-12-17 | 2018-01-09 | Covidien Lp | System and method for voltage and current sensing |
US10603098B2 (en) | 2013-05-31 | 2020-03-31 | Covidien Lp | Gain compensation for a full bridge inverter |
US9504516B2 (en) | 2013-05-31 | 2016-11-29 | Covidien LLP | Gain compensation for a full bridge inverter |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US11135001B2 (en) | 2013-07-24 | 2021-10-05 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
US9655670B2 (en) | 2013-07-29 | 2017-05-23 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
US9867650B2 (en) | 2013-12-26 | 2018-01-16 | Megadyne Medical Products, Inc. | Universal self-limiting electrosurgical return electrode |
US11464560B2 (en) | 2013-12-26 | 2022-10-11 | Megadyne Medical Products, Inc. | Universal self-limiting electrosurgical return electrode |
US10085791B2 (en) | 2013-12-26 | 2018-10-02 | Megadyne Medical Products, Inc. | Universal self-limiting electrosurgical return electrode |
US10278764B2 (en) | 2014-12-02 | 2019-05-07 | Covidien Lp | Electrosurgical generators and sensors |
US10987154B2 (en) | 2014-12-02 | 2021-04-27 | Covidien Lp | Electrosurgical generators and sensors |
US10292753B2 (en) | 2014-12-02 | 2019-05-21 | Covidien Lp | Electrosurgical generators and sensors |
US10281496B2 (en) | 2014-12-02 | 2019-05-07 | Covidien Lp | Electrosurgical generators and sensors |
US11129665B2 (en) | 2015-12-02 | 2021-09-28 | Apyx Medical Corporation | Mixing cold plasma beam jets with atmopshere |
US10908187B2 (en) | 2016-05-02 | 2021-02-02 | Covidien Lp | Current sensor with reduced voltage coupling |
US11703525B2 (en) | 2016-05-02 | 2023-07-18 | Covidien Lp | Current sensor with reduced voltage coupling |
US10918433B2 (en) | 2016-09-27 | 2021-02-16 | Apyx Medical Corporation | Devices, systems and methods for enhancing physiological effectiveness of medical cold plasma discharges |
US11696792B2 (en) | 2016-09-27 | 2023-07-11 | Apyx Medical Corporation | Devices, systems and methods for enhancing physiological effectiveness of medical cold plasma discharges |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US3601126A (en) | High frequency electrosurgical apparatus | |
US4531524A (en) | Circuit apparatus and method for electrothermal treatment of cancer eye | |
US4644955A (en) | Circuit apparatus and method for electrothermal treatment of cancer eye | |
EP0949886B1 (en) | Electrosurgical generator and system for underwater operation | |
US4196734A (en) | Combined electrosurgery/cautery system and method | |
US6309386B1 (en) | Linear power control with PSK regulation | |
US6508815B1 (en) | Radio-frequency generator for powering an ablation device | |
US4188927A (en) | Multiple source electrosurgical generator | |
US3885569A (en) | Electrosurgical unit | |
USRE41921E1 (en) | Electrosurgery system and method | |
US6210403B1 (en) | Automatic control for energy from an electrosurgical generator | |
US4658819A (en) | Electrosurgical generator | |
US5108391A (en) | High-frequency generator for tissue cutting and for coagulating in high-frequency surgery | |
US6039732A (en) | Electric operation apparatus | |
US9554853B2 (en) | Radio-frequency generator for powering an ablation device | |
EP0136855A2 (en) | Electrosurgical generator | |
AU655859B2 (en) | Iontophoresis system having features for reducing skin irritation | |
JP4162813B2 (en) | Iontophoresis device | |
JPH0761340B2 (en) | Radiofrequency surgical instrument for the thermal coagulation of biological tissue | |
CA2081464A1 (en) | Temperature controlled rf coagulation | |
JPH10500605A (en) | Electrosurgical return electrode circuit for monitoring electrosurgical current | |
JPS61124266A (en) | Surgical treatment electric-signal generator | |
NL8402177A (en) | ELECTROLYSIS MACHINE. | |
JP2683427B2 (en) | Microwave therapy device | |
EP0188413B1 (en) | Circuit apparatus for electrothermal treatment of cancer eye |