CA2229874A1 - Electrosurgical generator power control circuit and method - Google Patents
Electrosurgical generator power control circuit and method Download PDFInfo
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- CA2229874A1 CA2229874A1 CA002229874A CA2229874A CA2229874A1 CA 2229874 A1 CA2229874 A1 CA 2229874A1 CA 002229874 A CA002229874 A CA 002229874A CA 2229874 A CA2229874 A CA 2229874A CA 2229874 A1 CA2229874 A1 CA 2229874A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
- A61B2018/00773—Sensed parameters
- A61B2018/00875—Resistance or impedance
Abstract
A constant power control circuit (107) for an electrosurgical generator (101) and a method for maintaining the electrical power output of an electrosurgical generator (101) at a generally constant value throughout a given tissue impedance range are disclosed. The constant power control circuit (107) and the method recognize and use the unique and simple linear characteristics associated with certain electrosurgical generator (101) designs to monitor and control the electrical power output without having to calculate or monitor the actual output power. The constant power control circuit (107) includes a current sampling circuit (115), a linear conversion circuit (117), and a feedback correction circuit (119). The constant power control circuit (107) may also include protection circuitry that prevents the electrosurgical generator (101) from being over-driven during high and/or low impedance loading (121), and reduces the severity of exit sparking by providing a quick response to high impedance indications while nonetheless maintaining increased power levels throughout a preset, nominal impedance range. The constant power control circuit (107) and method may be included as an integral part of the overall electrosurgical generator's (101) circuitry, or may be embodied as a separate unit that connects to, and controls, an electrosurgical generator (101). The constant power control circuit (107) and method may be embodied through a variety of analog and/or digital circuit components or arrangements, including software running on computational and memory circuitry.
Description
W O 97/11648 PCT~B96/00618 ELECTROSURGICAL GENERATOR POWER CONTROL CIRCUIT AND METHOD
1. Field of the Invention A constant power control circuit for an electrosurgical generator and a method for maintaining the electrical power output of an electrosurgical generator at a generally constant level throughout a given tissue impedance range.
1. Field of the Invention A constant power control circuit for an electrosurgical generator and a method for maintaining the electrical power output of an electrosurgical generator at a generally constant level throughout a given tissue impedance range.
2. Backaround of the t)isclosure An electrosurgical generator is used in surgical procedures to deliver electrical energy to the tissue of a patient. An electrosurgical generator often includes a radio frequency generator and its controls.
When an electrode is connected to the generator, the electrode can be used for cutting or coagulating the tissue of a patient with high frequency eiectrical energy.
During normal operation, alternating electrical current from the generator flowsbetween an active electrode and a return electrode by passing through the tissue and bodily fluids of a patient.
The electrical energy usually has its waveform shaped to enhance its ability to cut or coagulate tissue. Different waveforms correspond to different modes ofoperation of the generator, and each mode gives the surgeon various operating advantages. Modes may include cut, coagulate, a blend thereof, desiccate, or spray. A surgeon can easily select and change the different modes of operation as the surgical procedure progresses.
In each mode of operation, it is important to regulate the electrosurgical power delivered to the patient to achieve the desired surgical effect. Applying more electrosurgical power than necessary results in tissue destruction and prolongs healing. Applying less than the desired amount of electrosurgical power inhibits the surgical procedure. Thus, it is desirable to control the output energy from the electrosurgical generator for the type of tissue being treated.
Different types of tissues will be encountered as the surgical procedure progresses and each unique tissue requires more or less power as a function of frequently changing tissue impedance. Even the same tissue will present a different load impedance as the tissue is desiccated.
Two conventional types of power regulation are used in commercial electrosurgical generators. The most common type controls the DC power supply of the generator by limiting the amount of power provided from the AC mains to CA 02229874 l99X-02-18 W O 97/11648 PCT~B96/00618 which the generator is connected. A feedback control loop regulates output voltage by comparing a desired voltage with the output voltage supplied by the power supply. Another type of power regulation in commercial electrosurgical generators controls the gain of the high-frequency or radio frequency amplifier. A feedbackcontrol loop compares the output power supplied from the RF amplifier for adjustment to a desired power level. Generators that have feedback control are typically designed to hold a constant output voltage, and not to hold a constantoutput power.
U.S. Patents 3,964,487; 3,980,085; 4,188,927 and 4,092,986 have circuitry to reduce the output current in accordance with increasing load impedance.
In those patents, constant voltage output is maintained and the current is decreased with increasing load impedance.
U.S. Patent 4,126,137 controls the power amplifier of the electrosurgical unit in accord with a non linear compensation circuit applied to a feedback signal derived from a comparison of the power level reference signal and the mathematical product of two signals including sensed current and voltage in the unit.
U.S. Patent 4,658,819 has an electrosurgical generator which has a microprocessor controller based means for decreasing the output power as a function of changes in tissue impedance.
U.S. Patent 4,727,874 includes an electrosurgical generator with a high frequency pulse width modulated feedback power control wherein each cycle of thegenerator is regulated in power content by modulating the width of the driving energy pulses.
U.S. Patent 3,601,126 has an electrosurgical generator having a feedback circuit that attempts to msintain the output current at a constant amplitude over a wide range of tissue impedances.
None of the aforementioned U.S. Patents include a constant power control circuit that provides for a generally constant output power while also providing a linear adjustment to account for the unique waveform crest factors associated with different operational modes.
The preferred constant power control circuit and method provided herein allows for output power control by way of a unique and simple linear conversion circuit coupled with protection circuitry that prevents the electrosurgical generator W O 97/11648 PCT~B96/00618 from being over-driven during high and/or low impedance loading. The preferred constant power control circuit also reduces the severity of exit sparking by responding quickly to high impedance indications while nonetheless maintaining subst~ntially increased power levels throughout a predeler-~;ned patient tissue 5 impedance range.
SUMMARY OF THE INVENTION
A constant power control circuit for use with an electrosurgical generator.
The constant power control circuit and method may be included as an integral part 10 of the overall electrosurgical generator's circuitry, or may be designed as a separate unit that connects to, and controls, an electrosurgical generator. The constant power control circuit and method may be embodied through a variety of analog and/or digital circuit components or arrangements, including software running on computational and memory circuitry.
The constant power control circuit and method maintain the output power of the electrosurgical current at a generally constant level over a finite patient tissue impedance range. The preferred patient tissue impedance range is about 300 to 2500 ohms.
The constant power control circuit and method provide the capability to control the output power of the electrosurgical generator without having to actually monitor the amplitude of both the output current and output voltage. This allows for a simple constant power control circuit and method which operate to control the power output without having to calculate the actual power output of the electrosurgical generator.
While the constant power control circuit may be used to control electrosurgical generators of varying designs, it is preferred that the electrosurgical generator includes a power selection system wherein the user may initialize, set, monitor, and/or control the operation of the electrosurgical generator. It is also preferred that the power selection system produces a control voltage signal that acts to control a high voltage direct current supply which in turn acts to supply a high voltage signal to an output switching radio frequency stage~ Then output switching radio frequency stage creates an electrosurgical energy between two output electrodes. The preferred electrosurgical generator need not be limited to these three W O 97/11648 PCT~B96/00618 functional elements, for example the electrosurgical generator could also include additional safety, monitoring, signal modification/conditioning, and/or feedbackcircuitry or functional elements/processes. The actual electrosurgical generator's design may include the use of digital components and signaling and/or analogue 5 components and signaling, or may be embodied, completely or partially within a software process running on hardware components.
The constant power control circuit includes a current sampling circuit, a linearconversion circuit, and a feedback correction circuit. The current sampling circuit is coupled to one of the output electrodes, and functions so as to produce a sampled 10 current signal that is proportional to the average current fiowing through the output electrode.
The linear conversion circuit which is connected to the current sampling circuit internally generates one or more multiplier reference signals and one or more offset reference signals, each of which is used to modify the sampled current signal 15 in accord with the crest factor associated with the electrosurgical energy output by the electrosurgical generator; the modified signal being a linear converted signal.
The feedback correction circuit which is electrically connected to receive the linear converted signal from the linear conversion circuit and the control voltage signal from the power selection system functions to produce a feedback control 20 signal which it then supplies to the power selection system, within the electrosurgical generator, so as to cause the power selection system to control the amount of electrosurgical energy created. The feedback correction circuit functions so as to de~ermine the c3irrerence in amplitude between the control voltage signal and the linear converted signal and to then add this difference to the control voltage 25 signal to produce a feedback control signal. The feedback correction circuit may also be connected to the primary transformer winding within the output switching radio frequency stage, or its equivalent, thereby allowing the feedback correction circuit to detect high impedance loading between the output electrodes and to reduce theamplitude of the feedback control signal to protect the circuitry and/or the patient 30 from excessive current and/or voltage levels. A high impedance load is generally considered to be above 2500 ohms. The feedback correction circuit may also include circuitry or processes that substitute another signal for the feedback control signal when the impedance loading between the output electrodes is calculated as W O 97/11648 PCT~B96/00618 being low. A low impedance load is generally co--s;dered to be below 300 ohms.
Both high and low impedance limits may be adjusted to match the instruments processes and/or procedures as necessa- y.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 presents an electrosurgical generdlor interfaced to a con~L~nL power control circuit having a current sampling circuit linear conversion circuit and feedback correction circuit.
Figure 2 is the prerer.ed embodiment of the linear conversion circuit shown in Figure 1.
Figure 3 is the prefe. .ed embodiment of the feedback correction circuit shown in Figure 1.
DETAILED DESCRIPTION OF THE INVENTION
For an electrosurçlical generator 101 having a high voltage direct current (DC) supply 103 which is electrically connected to control an output switching radio frequency (RF) stage 105 a unique linear relationship exists between the controlvoltage s- ~pplied to the high voltage DC supply 103 and the root-mean-square (RMS) current generdL~d by the ele~L.osurgical generaLor 101. This unique linear relationship can be used to design a con:.LanL power control circuit 107 that functions as a feedback control loop to control the ele~ L-osurgical generaLor 101.
The following "~aLl,en,atical derivations define this unique linear relationship.
It can be shown that:
Vcontrol = Vdc / Kps;
where Vcontrol = a control voltage s~pFlied to the high voltage DC supply Vdc = the output voltage signal of the high voltage DC supply and Kps = a feedback ratio of the high voltage DC supply.
It can further be shown that:
Vdc2 x Ka = Pout;
where SUBSTIT~JTE SffEET ~lJLE 26) W O 97/11648 PCT~B96/00618 Pout = the output power of the electrosurgical generaLor 101, and Ka = a linear conalal-l (which can be empirically derived).
Therefore, the output power of the electrosurgical generaLor 101 is directly proportional to the square of the output voltage signal of the high voltage DC supply.
Thus, by substitution:
(Vcontrol x Kps)2 x Ka = Pout, or Vcontrol2 x Kg = Pout;
where, k~ = Kps2 x Ka.
Therefore, the output power of the electrosurgical genefdLor 101 is proportional to the square of the control voltaç~e s~pplied to the high voltage DC supply.
Examining the output of the çlenerator we have:
Pout = Vrms x Irms;
where, Vrms = output RMS voltage of the electrosurgical generaLor 101, and Irms = output RMS current of the electrosurgical generator 101.
Accordingly, at a given load i,-,pedance = R:
Vrms = Irms x R, and by substitution Pout = Irms2 x R.
By allowing R to equal a 'matched' load impedance we have Vcontrol2 x Kg = Irrr~s2 x R, and therefore Vcontrol2 = Irms2 x R / Kg.
Consequently, for a qiven impedance Kr = R / Kg the equation can be simplified to:
Vcontrol2 = Irms2 x Kr.
Therefore, the square of the control voltage supplied to the high voltage DC supply 103 is directly proportional to the square of the output RMS current of the SL~ JTE SHEET (RULE 26) W O 97/11648 PCT/nB96/00618 ele~,~,osurgical generdLor 101. It can also be shown by similar derivation that the square of the control voltage supplied to the high voltage DC supply 103 is directly proportional to the square of the output RMS voltage of the electrosurgical gene-dlor 101 .
Thus, the above derivation implies that if either the output RMS current or voltage is sampled properly (Isample & Vsample respectively) the control voltagesupplied to the high voltage DC supply 103 may be used as a reference value in afeedback control loop to keep either the output RMS current or output RMS voltage constant. When the linear relationship of Irms to Isample is 'mapped' into the linear relationship of Vcontrol to Irms then a linear relationship can be derived between Vcontrol and Isample. When the scaling is done properly for a given power setting, Vcontrol will equal Isample at the 'matched' load impedance. Tl-ererore, in a feedback circuit designed with the above mapping a feedback loop which keeps Isample equal to Vcontrol will by definition keep Irms consld~-L.
In accord with the above presenLed mathe.. ,dLical derivation, we have designed a con~L~. .L power control circuit 107 for the electrosurgical generator 101, shown in Figure 1, having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency sta~qe 105 thereby 20 creating an electrosurgical energy beL~rJccn two output electrodes 111. The prerer,ed electrosurgical ge,-tsraLor 101 has a plurality of operational modes selectable within the power selection system 109, and a primary L(dnsro. ~"er winding 1 13 within the output switching radio frequency stage 105, as shown in Figure 1.
The co,lsLd-)L power control circuit 107, shown in Figure 1, includes a current 25 sampling circuit 1 15, a linear conversion circuit 1 17 and a feedback correction circuit 1 1 9.
In the p(ere...3d embodiment, the current sampling circuit 115 is inductively coupled to one of the output electrodes 1 11, as shown in Figure 1. AlLt:~..dLively the current sampling circuit 115 could be actively coupled, in circuit, with the output 30 electrode.
The current sampling circuit 115 produces a sampled current signal that is proportional in amplitude to the average current flowing from the electrosurgical SU~S~ JTE SHEET (RULE 26) W O 97/11648 PCT~B96/00618 ge~.e-dlor 101 through the one output electrode, an impedance load 121, and returnin~ to the electrosurgical gene-dLor 101 through another output electrode.The prefe~tsd errt-~ ' ..e--L of ths current sampling circuit t15 includes an inductive coil element, similar in design and function to that of a secondary winding 5 of a current L-an:.ro-,ner. Additional circuit elements function to L-~llsror.~. the induced current into a proportional voltage signal and include a voltage drop res;~Lor, a calib.dli--y variable resistor, and elements that rectify and average the sampled current signal.
The current sampling circuit 115 s~Fp!;es the sampled current si~nal to the 10 linear conversion circuit 1 17. However, before the sampled current signal can be used as a feedback term, the mode crest factor for the selected electrosursaicalge.,eraLor 101 operational mode, needs to be compensated for. The linear conversion circuit 117, in Fi~aures 1 and 2, compensates for the linear relationship between the sampled current signal and a 'true' sampled RMS value, which is of the 15 form Irms = m x Isample + b, where Irms is a signal which is directly propo~ Lional to the RMS current, and m and b are given consLdnLs derived for a given crest factor.
While electrosurgical generaLo(s 101 have a wide variety of dirrere,.L output wave shapes with varying crest factors, it is prer~r-ad that the crest factor for a given mode be significantly cGn~;LanL over a finite patient tissue impedance range, such as 20 between 300 and 2500 ohms.
Accold;,-~ly, the linear conversion circuit 117 first multiples the sampled current si~qnal by the gain, m, and then adds the offset to it, b. When the values of m and b are chosen prciperly the resulting linear converted signal is directly proportional to the output RMS current of the slecL-osurgical geneidLor 101. The25 prefel.~d method for deter--.i;.-.a the proper values of m and b for a çlivenoperational mode and electrosurgical generator 101 includes collecting empirical data on the control voltage supplied to the high voltage DC supply 103 and the resulting output RMS current of the electrosurgical generator 101 and solving the linear equation, for m and b, by substitution.
The linear conversion circuit 1 17, shown in Figures 1 and 2, is electrically connected to the current sampling circuit 1 15. In the prefer,ed embodiment, thelinear conversion circuit 1 17 is also ele~,-L,ically connected to the power selection system 109 such that the operational mode of the electrosurgical generaLor 101 can S~S 111 ~JTE SHEET (RULE 26) W O 97/11648 PCT~B96/00618 be determined based on this connection. The linear conversion circuit 117 generates a linear converted signal and supplies this signal to the feedback correction circuit 119.
The preferred embodiment includes a linear multiplier generating means 201 within the linear conversion circuit 117, see Figure 2. The linear multiplier generating means 201 generates a plurality of unique multiplier reference signals ~i.e., a factor 'm'). There is preferably one, unique, multiplier reference signal for each operational mode. The preferred embodiment, of the linear multiplier generating means 201 includes several resistive components connected to voltage sources, across whicha predetermined voltage is maintained.
The preferled embodiment includes a linear offset generating means 203 within the linear conversion circuit 117, see Figure 2. The linear offset generating means 203 generates a plurality of unique offset reference signals ~i.e., a factor 'b').
There is preferably one, unique, offset reference signal for each operational mode.
The preferred embodiment of the linear offset generating means 203 includes several resistive components connected to voltage sources, across which a predetermined voltage is maintained.
The preferred embodiment also includes a plurality of multipliers 205, within the linear conversion circuit 117, see Figure 2. There is preferably one, corresponding, multiplier 205 for each operational mode. Each multiplier 205 is electricallyconnected to receive the sampled current signal and one unique multiplier reference signal from the linear multiplier generating means 201. Each multiplier 205 multiplies the sampled current signal and the unique multiplier reference signalassociated with one operational mode to produce a unique multiplied signal for that operational mode. The preferred embodiment of the multiplier 205 includes a plurality of operational amplifiers.
The preferred embodiment includes a plurality of summers 207, within the linear conversion circuit 117, see Figure 2. There is preferably one, corresponding, summer 207 for each operational mode. Each summer 207 is electrically connected to receive a unique multiplied signal and one unique offset reference signal from the linear offset generating means 203. Each summer 207 sums the offset reference signal associated with one operational mode and the unique multiplied signal associated with that operational mode to produce a unique linear converted signal for that operational mode. The preferred embodiment of the surrimer 207 includesconfiguring the plurality of operational amplifiers used as multipliers 205 to also function as summers 207.
The preferred embodiment includes a mode monitor 209, within the linear conversion circuit 1 17, see Figure 2. The mode monitor 209 is electrically connected to the power selection system 109, for identifying the operational mode of the electrosurgical generator 101 and producing an identified operational mode signal therefrom.
Closely associated with the mode monitor 209, is a signal selector 211 that is also within the linear conversion circuit 1 17, see Figure 2. The signal selector 21 1 is electrically connected to receive the identified operational mode signal and the unique linear converted signal from each of the summers 207. The signal selector2 11 selects the unique linear converted signal associated with the identified operational mode, and causes that linear converted signal to be supplied to the feedback correction circuit 1 19. In the preferred embodiment the mode monitor 209 and signal selector 211 are embodied within a circuit including a digital processing component that activates and/or deactivates a plurality of electronic switching elements.
The feedback correction circuit 119, shown in Figures 1 and 3, is electrically connected to receive the linear converted signal from the linear conversion circuit 117, the control voltage signal from the power selection system 109, and the voltage signal across the primary transformer winding 1 13. The feedback correction circuit 119 produces a feedback control signal and supplies the feedback controlsignal to the power selection system 109 so as to control the amount of electrosurgical energy created by the electrosurgical generator 101.
The feedback correction circuit 1 19 includes a subtractor 301, see Figure 3.
The subtractor 301 is electrically connected to receive the linear converted signal from the linear conversion circuit 1 17 and the control voltags signal which is generated by the power selection system 109 and supplied to the high voltage DC
supply, see Figures 1 and 3. The subtractor 301 determines the difference in amplitude between the control voltage signal and the linear converted signal, and produces a delta signal proportional to the ditt,arel-ce. The preferred embodiment of the subtractor 301 includes an operational amplifier component.
CA 02229874 l998-02-l8 W O 97/11648 PCT~B96/00618 Also included in the feedback correction circuit 119 is an adder 303, see Figure 3. The adder 303 is electrically connected to receive the delta signal and the control voltage signal. The adder 303 adds the delta si9nal to the control voltage signal to produce the feedback control signal. The prefel,dd embodiment includes5 an operational amplifier component.
Since holding the output RMS current constant for all impedances would be a physical impossibility based on the design limitations of the high voltage DC supply 103 and the output switching RF stage 105, it is preferred that the feedback control signal to the high voltage DC supply 103 be limited as a function of the impedance load 121 betweentheoutputelectrodes111.
In the prefer.ed embodiment, the feedback correction circuit 119 includes a maximum control voltage reference generator 305 for generating a maximum controlvoltage reference signal, see Figure 3. The preferred embodiment uses an operational amplifier component connected to the control voltage signal to establish a maximum control voltage reference signal based thereon.
The maximum control voltage reference signal is supplied to a switcher 307 within the preferred feedback correction circuit 119, see Figure 3. The switcher 307 is also electrically connected to receive the feedback control signal from the adder 303. The switcher 307 substitutes the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltage reference signal, thereby limiting the electrosurgical generator's 101 output current through the output electrodes 111when the impedance load 121 is at a low impedance level. The preferred embodiment of the switcher 307 includes an AND circuit created with diodes that passes the lower of the two signals as the feedback control signal.
When the impedance load 121 between the output electrodes 111 is high, the preferred constant power control circuit 107 should limit the output voltage of the electrosurgical generator 101 so as protect the electrosurgical generator 101, and reduce leakage currents and exit sparking.
In the preferred embodiment, the feedback correction circuit 119 shown in Figure 3, includes a high impedance reference generator 309 for generating a high impedance refere,1ce signal. The high impedance reference generator 309 is electrically connected to receive the control voltage signal. The preferred high W O 97/11648 PCT~B96/00618 impedance reference generator 309 establishes the high impedance reference signal by linearly converting the control voltage signal with an operational amplifier.In the preferred embodiment a connector 311 is used for electrically connecting a comparator 313, within the feedback correction circuit 119, to the primary transformer winding 113, see Figures 1 and 3. The connector 311 providesthe comparator 313 with the voltage across the primary transformer winding 113.
The comparator 313 is also electrically connected to receive the high impedance reference signal. The comparator 313 compares the amplitude of the high impedance reference signal to the voltage across the primary transformer winding113 and produces a high impedance detection signal that indicates the results of this comparison. In the preferred embodiment the comparator 313 includes an operational amplifier component.
The high impedance detection signal is received by a reducer 315, shown in Figure 3 of the preferred embodiment, which is electrically connected to the comparator 313 and to the switcher 307. The reducer 315 reduces, to an internally generated preset reduced voltage level signal, the amplitude of the feedback control signal from the switcher 307 when the voltage across the primary trsnsformer winding 113 is greater than the high impedance reference signal as indicated by the high impedance detection signal. In the preferred embodiment, the reducer 315 includes a logic driven switched circuit and an adiuct~hlQ resistor providing a reduced voltage level signal. The reducer 315 supplies the resulting feedback control signal to the power selection system 109.
Associated with the constant power control circuit 107 is a method for maintaining a generally cons~ant output power from an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111.
The method includes the steps of inductively coupling to one output electrode, sensing the current flowing through the output electrode 111 and producing a sampled current signal proportional to the average current flowing through the output electrode. The method then continues with the steps of generaLing a multiplier reference signal, generating an offset reference signal, multiplying the sampled current signal and the multiplier reference signal, and then summing the offset reference signal to the product to producing a linear converted signal.
The method continues with the steps of connecting to the control voltage 5 signal from the power selection system 109, detel-nil,i"s the dirrerence in amplitude between the control voltage signal and the linear converted signal, adding the difference determined by the subtraction means to the control voltage signal to produce a feedback control signal, and then supplying the feedback control signal to the power selection system 109 to control the amount of electrosurgical energy 1 0 created.
To protect the electrosurgical generator 101 and the patient when the impedance load 121 is high, the method can include the steps of generating a high impedance reference signal, connecting to the primary transformer winding 113, comparing the amplitude of the high impedance reference signal to the voltage 15 across the primary transformer winding 113, and reducing the amplitude of thefeedback control signal when the voltage across the primary transformer winding 1 13 is greater than the high impedance It,ference signal.
To protect the electrosurgical generator 101 and patient when the impedance load 121 is low, the method can include the steps of generating a maximum control 20 voltage reference signal and substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltage reference signal.
For electrosurgical generators 101 having a plurality of operational modes, the method can be modified to include the steps of generating a plurality of unique linear 25 multiplier reference signals, one for each operational mode, and generating a plurality of unique linear offset reference signals, one for each operational mode. The method would then include the steps of multiplying the sampled current signal, separately and concurrently, with each of the unique multiplier reference signals to produce a plurality of unique multiplied signals, one for each operational mode, and then 30 summing each of the unique multiplied signals with the offset reference signal associated with the same operational mode to produce a plurality of unique linear converted signals, one for each operational mode. The method would continue withthe steps of connecting to the power selection system 109 to identify the W O 97/11648 PCT~B96/00618 operational mode selected, selecting the unique linear converted signal that matches the identified operational mode, and then causing that linear converted signal to be supplied to the feedback correction circuit 119.
When an electrode is connected to the generator, the electrode can be used for cutting or coagulating the tissue of a patient with high frequency eiectrical energy.
During normal operation, alternating electrical current from the generator flowsbetween an active electrode and a return electrode by passing through the tissue and bodily fluids of a patient.
The electrical energy usually has its waveform shaped to enhance its ability to cut or coagulate tissue. Different waveforms correspond to different modes ofoperation of the generator, and each mode gives the surgeon various operating advantages. Modes may include cut, coagulate, a blend thereof, desiccate, or spray. A surgeon can easily select and change the different modes of operation as the surgical procedure progresses.
In each mode of operation, it is important to regulate the electrosurgical power delivered to the patient to achieve the desired surgical effect. Applying more electrosurgical power than necessary results in tissue destruction and prolongs healing. Applying less than the desired amount of electrosurgical power inhibits the surgical procedure. Thus, it is desirable to control the output energy from the electrosurgical generator for the type of tissue being treated.
Different types of tissues will be encountered as the surgical procedure progresses and each unique tissue requires more or less power as a function of frequently changing tissue impedance. Even the same tissue will present a different load impedance as the tissue is desiccated.
Two conventional types of power regulation are used in commercial electrosurgical generators. The most common type controls the DC power supply of the generator by limiting the amount of power provided from the AC mains to CA 02229874 l99X-02-18 W O 97/11648 PCT~B96/00618 which the generator is connected. A feedback control loop regulates output voltage by comparing a desired voltage with the output voltage supplied by the power supply. Another type of power regulation in commercial electrosurgical generators controls the gain of the high-frequency or radio frequency amplifier. A feedbackcontrol loop compares the output power supplied from the RF amplifier for adjustment to a desired power level. Generators that have feedback control are typically designed to hold a constant output voltage, and not to hold a constantoutput power.
U.S. Patents 3,964,487; 3,980,085; 4,188,927 and 4,092,986 have circuitry to reduce the output current in accordance with increasing load impedance.
In those patents, constant voltage output is maintained and the current is decreased with increasing load impedance.
U.S. Patent 4,126,137 controls the power amplifier of the electrosurgical unit in accord with a non linear compensation circuit applied to a feedback signal derived from a comparison of the power level reference signal and the mathematical product of two signals including sensed current and voltage in the unit.
U.S. Patent 4,658,819 has an electrosurgical generator which has a microprocessor controller based means for decreasing the output power as a function of changes in tissue impedance.
U.S. Patent 4,727,874 includes an electrosurgical generator with a high frequency pulse width modulated feedback power control wherein each cycle of thegenerator is regulated in power content by modulating the width of the driving energy pulses.
U.S. Patent 3,601,126 has an electrosurgical generator having a feedback circuit that attempts to msintain the output current at a constant amplitude over a wide range of tissue impedances.
None of the aforementioned U.S. Patents include a constant power control circuit that provides for a generally constant output power while also providing a linear adjustment to account for the unique waveform crest factors associated with different operational modes.
The preferred constant power control circuit and method provided herein allows for output power control by way of a unique and simple linear conversion circuit coupled with protection circuitry that prevents the electrosurgical generator W O 97/11648 PCT~B96/00618 from being over-driven during high and/or low impedance loading. The preferred constant power control circuit also reduces the severity of exit sparking by responding quickly to high impedance indications while nonetheless maintaining subst~ntially increased power levels throughout a predeler-~;ned patient tissue 5 impedance range.
SUMMARY OF THE INVENTION
A constant power control circuit for use with an electrosurgical generator.
The constant power control circuit and method may be included as an integral part 10 of the overall electrosurgical generator's circuitry, or may be designed as a separate unit that connects to, and controls, an electrosurgical generator. The constant power control circuit and method may be embodied through a variety of analog and/or digital circuit components or arrangements, including software running on computational and memory circuitry.
The constant power control circuit and method maintain the output power of the electrosurgical current at a generally constant level over a finite patient tissue impedance range. The preferred patient tissue impedance range is about 300 to 2500 ohms.
The constant power control circuit and method provide the capability to control the output power of the electrosurgical generator without having to actually monitor the amplitude of both the output current and output voltage. This allows for a simple constant power control circuit and method which operate to control the power output without having to calculate the actual power output of the electrosurgical generator.
While the constant power control circuit may be used to control electrosurgical generators of varying designs, it is preferred that the electrosurgical generator includes a power selection system wherein the user may initialize, set, monitor, and/or control the operation of the electrosurgical generator. It is also preferred that the power selection system produces a control voltage signal that acts to control a high voltage direct current supply which in turn acts to supply a high voltage signal to an output switching radio frequency stage~ Then output switching radio frequency stage creates an electrosurgical energy between two output electrodes. The preferred electrosurgical generator need not be limited to these three W O 97/11648 PCT~B96/00618 functional elements, for example the electrosurgical generator could also include additional safety, monitoring, signal modification/conditioning, and/or feedbackcircuitry or functional elements/processes. The actual electrosurgical generator's design may include the use of digital components and signaling and/or analogue 5 components and signaling, or may be embodied, completely or partially within a software process running on hardware components.
The constant power control circuit includes a current sampling circuit, a linearconversion circuit, and a feedback correction circuit. The current sampling circuit is coupled to one of the output electrodes, and functions so as to produce a sampled 10 current signal that is proportional to the average current fiowing through the output electrode.
The linear conversion circuit which is connected to the current sampling circuit internally generates one or more multiplier reference signals and one or more offset reference signals, each of which is used to modify the sampled current signal 15 in accord with the crest factor associated with the electrosurgical energy output by the electrosurgical generator; the modified signal being a linear converted signal.
The feedback correction circuit which is electrically connected to receive the linear converted signal from the linear conversion circuit and the control voltage signal from the power selection system functions to produce a feedback control 20 signal which it then supplies to the power selection system, within the electrosurgical generator, so as to cause the power selection system to control the amount of electrosurgical energy created. The feedback correction circuit functions so as to de~ermine the c3irrerence in amplitude between the control voltage signal and the linear converted signal and to then add this difference to the control voltage 25 signal to produce a feedback control signal. The feedback correction circuit may also be connected to the primary transformer winding within the output switching radio frequency stage, or its equivalent, thereby allowing the feedback correction circuit to detect high impedance loading between the output electrodes and to reduce theamplitude of the feedback control signal to protect the circuitry and/or the patient 30 from excessive current and/or voltage levels. A high impedance load is generally considered to be above 2500 ohms. The feedback correction circuit may also include circuitry or processes that substitute another signal for the feedback control signal when the impedance loading between the output electrodes is calculated as W O 97/11648 PCT~B96/00618 being low. A low impedance load is generally co--s;dered to be below 300 ohms.
Both high and low impedance limits may be adjusted to match the instruments processes and/or procedures as necessa- y.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 presents an electrosurgical generdlor interfaced to a con~L~nL power control circuit having a current sampling circuit linear conversion circuit and feedback correction circuit.
Figure 2 is the prerer.ed embodiment of the linear conversion circuit shown in Figure 1.
Figure 3 is the prefe. .ed embodiment of the feedback correction circuit shown in Figure 1.
DETAILED DESCRIPTION OF THE INVENTION
For an electrosurçlical generator 101 having a high voltage direct current (DC) supply 103 which is electrically connected to control an output switching radio frequency (RF) stage 105 a unique linear relationship exists between the controlvoltage s- ~pplied to the high voltage DC supply 103 and the root-mean-square (RMS) current generdL~d by the ele~L.osurgical generaLor 101. This unique linear relationship can be used to design a con:.LanL power control circuit 107 that functions as a feedback control loop to control the ele~ L-osurgical generaLor 101.
The following "~aLl,en,atical derivations define this unique linear relationship.
It can be shown that:
Vcontrol = Vdc / Kps;
where Vcontrol = a control voltage s~pFlied to the high voltage DC supply Vdc = the output voltage signal of the high voltage DC supply and Kps = a feedback ratio of the high voltage DC supply.
It can further be shown that:
Vdc2 x Ka = Pout;
where SUBSTIT~JTE SffEET ~lJLE 26) W O 97/11648 PCT~B96/00618 Pout = the output power of the electrosurgical generaLor 101, and Ka = a linear conalal-l (which can be empirically derived).
Therefore, the output power of the electrosurgical generaLor 101 is directly proportional to the square of the output voltage signal of the high voltage DC supply.
Thus, by substitution:
(Vcontrol x Kps)2 x Ka = Pout, or Vcontrol2 x Kg = Pout;
where, k~ = Kps2 x Ka.
Therefore, the output power of the electrosurgical genefdLor 101 is proportional to the square of the control voltaç~e s~pplied to the high voltage DC supply.
Examining the output of the çlenerator we have:
Pout = Vrms x Irms;
where, Vrms = output RMS voltage of the electrosurgical generaLor 101, and Irms = output RMS current of the electrosurgical generator 101.
Accordingly, at a given load i,-,pedance = R:
Vrms = Irms x R, and by substitution Pout = Irms2 x R.
By allowing R to equal a 'matched' load impedance we have Vcontrol2 x Kg = Irrr~s2 x R, and therefore Vcontrol2 = Irms2 x R / Kg.
Consequently, for a qiven impedance Kr = R / Kg the equation can be simplified to:
Vcontrol2 = Irms2 x Kr.
Therefore, the square of the control voltage supplied to the high voltage DC supply 103 is directly proportional to the square of the output RMS current of the SL~ JTE SHEET (RULE 26) W O 97/11648 PCT/nB96/00618 ele~,~,osurgical generdLor 101. It can also be shown by similar derivation that the square of the control voltage supplied to the high voltage DC supply 103 is directly proportional to the square of the output RMS voltage of the electrosurgical gene-dlor 101 .
Thus, the above derivation implies that if either the output RMS current or voltage is sampled properly (Isample & Vsample respectively) the control voltagesupplied to the high voltage DC supply 103 may be used as a reference value in afeedback control loop to keep either the output RMS current or output RMS voltage constant. When the linear relationship of Irms to Isample is 'mapped' into the linear relationship of Vcontrol to Irms then a linear relationship can be derived between Vcontrol and Isample. When the scaling is done properly for a given power setting, Vcontrol will equal Isample at the 'matched' load impedance. Tl-ererore, in a feedback circuit designed with the above mapping a feedback loop which keeps Isample equal to Vcontrol will by definition keep Irms consld~-L.
In accord with the above presenLed mathe.. ,dLical derivation, we have designed a con~L~. .L power control circuit 107 for the electrosurgical generator 101, shown in Figure 1, having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency sta~qe 105 thereby 20 creating an electrosurgical energy beL~rJccn two output electrodes 111. The prerer,ed electrosurgical ge,-tsraLor 101 has a plurality of operational modes selectable within the power selection system 109, and a primary L(dnsro. ~"er winding 1 13 within the output switching radio frequency stage 105, as shown in Figure 1.
The co,lsLd-)L power control circuit 107, shown in Figure 1, includes a current 25 sampling circuit 1 15, a linear conversion circuit 1 17 and a feedback correction circuit 1 1 9.
In the p(ere...3d embodiment, the current sampling circuit 115 is inductively coupled to one of the output electrodes 1 11, as shown in Figure 1. AlLt:~..dLively the current sampling circuit 115 could be actively coupled, in circuit, with the output 30 electrode.
The current sampling circuit 115 produces a sampled current signal that is proportional in amplitude to the average current flowing from the electrosurgical SU~S~ JTE SHEET (RULE 26) W O 97/11648 PCT~B96/00618 ge~.e-dlor 101 through the one output electrode, an impedance load 121, and returnin~ to the electrosurgical gene-dLor 101 through another output electrode.The prefe~tsd errt-~ ' ..e--L of ths current sampling circuit t15 includes an inductive coil element, similar in design and function to that of a secondary winding 5 of a current L-an:.ro-,ner. Additional circuit elements function to L-~llsror.~. the induced current into a proportional voltage signal and include a voltage drop res;~Lor, a calib.dli--y variable resistor, and elements that rectify and average the sampled current signal.
The current sampling circuit 115 s~Fp!;es the sampled current si~nal to the 10 linear conversion circuit 1 17. However, before the sampled current signal can be used as a feedback term, the mode crest factor for the selected electrosursaicalge.,eraLor 101 operational mode, needs to be compensated for. The linear conversion circuit 117, in Fi~aures 1 and 2, compensates for the linear relationship between the sampled current signal and a 'true' sampled RMS value, which is of the 15 form Irms = m x Isample + b, where Irms is a signal which is directly propo~ Lional to the RMS current, and m and b are given consLdnLs derived for a given crest factor.
While electrosurgical generaLo(s 101 have a wide variety of dirrere,.L output wave shapes with varying crest factors, it is prer~r-ad that the crest factor for a given mode be significantly cGn~;LanL over a finite patient tissue impedance range, such as 20 between 300 and 2500 ohms.
Accold;,-~ly, the linear conversion circuit 117 first multiples the sampled current si~qnal by the gain, m, and then adds the offset to it, b. When the values of m and b are chosen prciperly the resulting linear converted signal is directly proportional to the output RMS current of the slecL-osurgical geneidLor 101. The25 prefel.~d method for deter--.i;.-.a the proper values of m and b for a çlivenoperational mode and electrosurgical generator 101 includes collecting empirical data on the control voltage supplied to the high voltage DC supply 103 and the resulting output RMS current of the electrosurgical generator 101 and solving the linear equation, for m and b, by substitution.
The linear conversion circuit 1 17, shown in Figures 1 and 2, is electrically connected to the current sampling circuit 1 15. In the prefer,ed embodiment, thelinear conversion circuit 1 17 is also ele~,-L,ically connected to the power selection system 109 such that the operational mode of the electrosurgical generaLor 101 can S~S 111 ~JTE SHEET (RULE 26) W O 97/11648 PCT~B96/00618 be determined based on this connection. The linear conversion circuit 117 generates a linear converted signal and supplies this signal to the feedback correction circuit 119.
The preferred embodiment includes a linear multiplier generating means 201 within the linear conversion circuit 117, see Figure 2. The linear multiplier generating means 201 generates a plurality of unique multiplier reference signals ~i.e., a factor 'm'). There is preferably one, unique, multiplier reference signal for each operational mode. The preferred embodiment, of the linear multiplier generating means 201 includes several resistive components connected to voltage sources, across whicha predetermined voltage is maintained.
The preferled embodiment includes a linear offset generating means 203 within the linear conversion circuit 117, see Figure 2. The linear offset generating means 203 generates a plurality of unique offset reference signals ~i.e., a factor 'b').
There is preferably one, unique, offset reference signal for each operational mode.
The preferred embodiment of the linear offset generating means 203 includes several resistive components connected to voltage sources, across which a predetermined voltage is maintained.
The preferred embodiment also includes a plurality of multipliers 205, within the linear conversion circuit 117, see Figure 2. There is preferably one, corresponding, multiplier 205 for each operational mode. Each multiplier 205 is electricallyconnected to receive the sampled current signal and one unique multiplier reference signal from the linear multiplier generating means 201. Each multiplier 205 multiplies the sampled current signal and the unique multiplier reference signalassociated with one operational mode to produce a unique multiplied signal for that operational mode. The preferred embodiment of the multiplier 205 includes a plurality of operational amplifiers.
The preferred embodiment includes a plurality of summers 207, within the linear conversion circuit 117, see Figure 2. There is preferably one, corresponding, summer 207 for each operational mode. Each summer 207 is electrically connected to receive a unique multiplied signal and one unique offset reference signal from the linear offset generating means 203. Each summer 207 sums the offset reference signal associated with one operational mode and the unique multiplied signal associated with that operational mode to produce a unique linear converted signal for that operational mode. The preferred embodiment of the surrimer 207 includesconfiguring the plurality of operational amplifiers used as multipliers 205 to also function as summers 207.
The preferred embodiment includes a mode monitor 209, within the linear conversion circuit 1 17, see Figure 2. The mode monitor 209 is electrically connected to the power selection system 109, for identifying the operational mode of the electrosurgical generator 101 and producing an identified operational mode signal therefrom.
Closely associated with the mode monitor 209, is a signal selector 211 that is also within the linear conversion circuit 1 17, see Figure 2. The signal selector 21 1 is electrically connected to receive the identified operational mode signal and the unique linear converted signal from each of the summers 207. The signal selector2 11 selects the unique linear converted signal associated with the identified operational mode, and causes that linear converted signal to be supplied to the feedback correction circuit 1 19. In the preferred embodiment the mode monitor 209 and signal selector 211 are embodied within a circuit including a digital processing component that activates and/or deactivates a plurality of electronic switching elements.
The feedback correction circuit 119, shown in Figures 1 and 3, is electrically connected to receive the linear converted signal from the linear conversion circuit 117, the control voltage signal from the power selection system 109, and the voltage signal across the primary transformer winding 1 13. The feedback correction circuit 119 produces a feedback control signal and supplies the feedback controlsignal to the power selection system 109 so as to control the amount of electrosurgical energy created by the electrosurgical generator 101.
The feedback correction circuit 1 19 includes a subtractor 301, see Figure 3.
The subtractor 301 is electrically connected to receive the linear converted signal from the linear conversion circuit 1 17 and the control voltags signal which is generated by the power selection system 109 and supplied to the high voltage DC
supply, see Figures 1 and 3. The subtractor 301 determines the difference in amplitude between the control voltage signal and the linear converted signal, and produces a delta signal proportional to the ditt,arel-ce. The preferred embodiment of the subtractor 301 includes an operational amplifier component.
CA 02229874 l998-02-l8 W O 97/11648 PCT~B96/00618 Also included in the feedback correction circuit 119 is an adder 303, see Figure 3. The adder 303 is electrically connected to receive the delta signal and the control voltage signal. The adder 303 adds the delta si9nal to the control voltage signal to produce the feedback control signal. The prefel,dd embodiment includes5 an operational amplifier component.
Since holding the output RMS current constant for all impedances would be a physical impossibility based on the design limitations of the high voltage DC supply 103 and the output switching RF stage 105, it is preferred that the feedback control signal to the high voltage DC supply 103 be limited as a function of the impedance load 121 betweentheoutputelectrodes111.
In the prefer.ed embodiment, the feedback correction circuit 119 includes a maximum control voltage reference generator 305 for generating a maximum controlvoltage reference signal, see Figure 3. The preferred embodiment uses an operational amplifier component connected to the control voltage signal to establish a maximum control voltage reference signal based thereon.
The maximum control voltage reference signal is supplied to a switcher 307 within the preferred feedback correction circuit 119, see Figure 3. The switcher 307 is also electrically connected to receive the feedback control signal from the adder 303. The switcher 307 substitutes the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltage reference signal, thereby limiting the electrosurgical generator's 101 output current through the output electrodes 111when the impedance load 121 is at a low impedance level. The preferred embodiment of the switcher 307 includes an AND circuit created with diodes that passes the lower of the two signals as the feedback control signal.
When the impedance load 121 between the output electrodes 111 is high, the preferred constant power control circuit 107 should limit the output voltage of the electrosurgical generator 101 so as protect the electrosurgical generator 101, and reduce leakage currents and exit sparking.
In the preferred embodiment, the feedback correction circuit 119 shown in Figure 3, includes a high impedance reference generator 309 for generating a high impedance refere,1ce signal. The high impedance reference generator 309 is electrically connected to receive the control voltage signal. The preferred high W O 97/11648 PCT~B96/00618 impedance reference generator 309 establishes the high impedance reference signal by linearly converting the control voltage signal with an operational amplifier.In the preferred embodiment a connector 311 is used for electrically connecting a comparator 313, within the feedback correction circuit 119, to the primary transformer winding 113, see Figures 1 and 3. The connector 311 providesthe comparator 313 with the voltage across the primary transformer winding 113.
The comparator 313 is also electrically connected to receive the high impedance reference signal. The comparator 313 compares the amplitude of the high impedance reference signal to the voltage across the primary transformer winding113 and produces a high impedance detection signal that indicates the results of this comparison. In the preferred embodiment the comparator 313 includes an operational amplifier component.
The high impedance detection signal is received by a reducer 315, shown in Figure 3 of the preferred embodiment, which is electrically connected to the comparator 313 and to the switcher 307. The reducer 315 reduces, to an internally generated preset reduced voltage level signal, the amplitude of the feedback control signal from the switcher 307 when the voltage across the primary trsnsformer winding 113 is greater than the high impedance reference signal as indicated by the high impedance detection signal. In the preferred embodiment, the reducer 315 includes a logic driven switched circuit and an adiuct~hlQ resistor providing a reduced voltage level signal. The reducer 315 supplies the resulting feedback control signal to the power selection system 109.
Associated with the constant power control circuit 107 is a method for maintaining a generally cons~ant output power from an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111.
The method includes the steps of inductively coupling to one output electrode, sensing the current flowing through the output electrode 111 and producing a sampled current signal proportional to the average current flowing through the output electrode. The method then continues with the steps of generaLing a multiplier reference signal, generating an offset reference signal, multiplying the sampled current signal and the multiplier reference signal, and then summing the offset reference signal to the product to producing a linear converted signal.
The method continues with the steps of connecting to the control voltage 5 signal from the power selection system 109, detel-nil,i"s the dirrerence in amplitude between the control voltage signal and the linear converted signal, adding the difference determined by the subtraction means to the control voltage signal to produce a feedback control signal, and then supplying the feedback control signal to the power selection system 109 to control the amount of electrosurgical energy 1 0 created.
To protect the electrosurgical generator 101 and the patient when the impedance load 121 is high, the method can include the steps of generating a high impedance reference signal, connecting to the primary transformer winding 113, comparing the amplitude of the high impedance reference signal to the voltage 15 across the primary transformer winding 113, and reducing the amplitude of thefeedback control signal when the voltage across the primary transformer winding 1 13 is greater than the high impedance It,ference signal.
To protect the electrosurgical generator 101 and patient when the impedance load 121 is low, the method can include the steps of generating a maximum control 20 voltage reference signal and substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltage reference signal.
For electrosurgical generators 101 having a plurality of operational modes, the method can be modified to include the steps of generating a plurality of unique linear 25 multiplier reference signals, one for each operational mode, and generating a plurality of unique linear offset reference signals, one for each operational mode. The method would then include the steps of multiplying the sampled current signal, separately and concurrently, with each of the unique multiplier reference signals to produce a plurality of unique multiplied signals, one for each operational mode, and then 30 summing each of the unique multiplied signals with the offset reference signal associated with the same operational mode to produce a plurality of unique linear converted signals, one for each operational mode. The method would continue withthe steps of connecting to the power selection system 109 to identify the W O 97/11648 PCT~B96/00618 operational mode selected, selecting the unique linear converted signal that matches the identified operational mode, and then causing that linear converted signal to be supplied to the feedback correction circuit 119.
Claims (9)
1. A constant power control circuit 107 for an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 1 1 1, the constant power control circuit 107 comprising:
a current sampling circuit 115 inductively coupled to one output electrode, the current sampling circuit 115 producing a sampled current signal proportional to the average current flowing through the output electrode;
a linear conversion circuit 117 electrically connected to the current sampling circuit 115 for generating a linear converted signal, wherein the linear conversion circuit 117 includes;
a linear multiplier generating means 201 for generating a multiplier reference signal;
a linear offset generating means 203 for generating an offset reference signal;
a multiplier, electrically connected to the linear multiplier generating means 201, for multiplying the sampled current signal and the multiplier reference signal to produce a multiplied signal; and a summer, electrically connected to the linear offset generating means 203, for summing the offset reference signal and the multiplied signal to produce the linear converted signal; and a feedback correction circuit 119 electrically connected to receive the linear converted signal from the linear conversion circuit 117 and the control voltage signal from the power selection system 109 for producing a feedback control signal which is supplied to the power selection system 109 to control the amount of electrosurgical energy created, wherein the feedback correction circuit 119 includes:
a subtractor 301, electrically connected to receive the linear converted signal and the control voltage signal, for determining a difference in amplitudebetween the control voltage signal and the linear converted signal and producing a delta signal proportional to the difference; and an adder 303, electrically connected to receive the delta signal and the control voltage signal, for adding the delta signal to the control voltage signal and producing the feedback control signal.
a current sampling circuit 115 inductively coupled to one output electrode, the current sampling circuit 115 producing a sampled current signal proportional to the average current flowing through the output electrode;
a linear conversion circuit 117 electrically connected to the current sampling circuit 115 for generating a linear converted signal, wherein the linear conversion circuit 117 includes;
a linear multiplier generating means 201 for generating a multiplier reference signal;
a linear offset generating means 203 for generating an offset reference signal;
a multiplier, electrically connected to the linear multiplier generating means 201, for multiplying the sampled current signal and the multiplier reference signal to produce a multiplied signal; and a summer, electrically connected to the linear offset generating means 203, for summing the offset reference signal and the multiplied signal to produce the linear converted signal; and a feedback correction circuit 119 electrically connected to receive the linear converted signal from the linear conversion circuit 117 and the control voltage signal from the power selection system 109 for producing a feedback control signal which is supplied to the power selection system 109 to control the amount of electrosurgical energy created, wherein the feedback correction circuit 119 includes:
a subtractor 301, electrically connected to receive the linear converted signal and the control voltage signal, for determining a difference in amplitudebetween the control voltage signal and the linear converted signal and producing a delta signal proportional to the difference; and an adder 303, electrically connected to receive the delta signal and the control voltage signal, for adding the delta signal to the control voltage signal and producing the feedback control signal.
2. The constant power control circuit 107 for an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111 of Claim 1, wherein the output switching radio frequency stage 105 has a primary transformer winding 113, and wherein thefeedback correction circuit 119 further includes:
a high impedance reference generator 309, electrically connected to receive the control voltage signal, for generating a high impedance reference signal;
a connector 311 for electrically connecting the feedback correction circuit 119 to the primary transformer winding 113;
a comparator 313, electrically connected to the connector 311 and to receive the high impedance signal, for comparing the amplitude of the high impedance reference signal to the voltage across the primary transformer winding113 and producing a high impedance detection signal; and a reducer 315, electrically connected to receive the high impedance detection signal and the feedback control signal, for reducing the amplitude of the feedback control signal when the high impedance detection signal indicates that the voltage across the primary transformer winding 113 is greater than the high impedance reference signal.
a high impedance reference generator 309, electrically connected to receive the control voltage signal, for generating a high impedance reference signal;
a connector 311 for electrically connecting the feedback correction circuit 119 to the primary transformer winding 113;
a comparator 313, electrically connected to the connector 311 and to receive the high impedance signal, for comparing the amplitude of the high impedance reference signal to the voltage across the primary transformer winding113 and producing a high impedance detection signal; and a reducer 315, electrically connected to receive the high impedance detection signal and the feedback control signal, for reducing the amplitude of the feedback control signal when the high impedance detection signal indicates that the voltage across the primary transformer winding 113 is greater than the high impedance reference signal.
3. The constant power control circuit 107 for an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111 of Claim 1, wherein the feedback correction circuit 119 further includes:
a maximum control voltage reference generator 305, electrically connected to receive the control voltage signal, for generating a maximum control voltage reference signal; and a switcher 307, electrically connected to receive the maximum control voltage reference signal and the feedback control signal, for substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltagereference signal.
a maximum control voltage reference generator 305, electrically connected to receive the control voltage signal, for generating a maximum control voltage reference signal; and a switcher 307, electrically connected to receive the maximum control voltage reference signal and the feedback control signal, for substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltagereference signal.
4. The constant power control circuit 107 for an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111 of Claim 1, wherein the power selectionsystem 109 has a plurality of operational modes and wherein the linear multiplier generating means 201 generates a unique multiplier reference signal for each operational mode, and the linear offset generating means 203 generates a unique offset reference signal for each operational mode, and wherein the linear conversion circuit 117 further includes:
a plurality of multipliers 205, wherein there is one multiplier for each operational mode and each multiplier multiplies the sampled current signal and the unique multiplier reference signal associated with one operational mode to produce a unique multiplied signal for that operational mode;
a plurality of summers 207, wherein there is one summer for each operational mode and each summer sums the offset reference signal associated with one operational mode and the unique multiplied signal associated with that operational mode to produce a unique linear converted signal for that operational mode;
a mode monitor 209, electrically connected to the power selection system 109, for identifying the operational mode and producing an identified operational mode signal;
a signal selector 211, electrically connected to receive the identified operational mode signal and the unique linear converted signal from each of the summers, for selecting the unique linear converted signal associated with the identified operational mode, and causing that linear converted signal to be supplied to the feedback correction circuit 119.
a plurality of multipliers 205, wherein there is one multiplier for each operational mode and each multiplier multiplies the sampled current signal and the unique multiplier reference signal associated with one operational mode to produce a unique multiplied signal for that operational mode;
a plurality of summers 207, wherein there is one summer for each operational mode and each summer sums the offset reference signal associated with one operational mode and the unique multiplied signal associated with that operational mode to produce a unique linear converted signal for that operational mode;
a mode monitor 209, electrically connected to the power selection system 109, for identifying the operational mode and producing an identified operational mode signal;
a signal selector 211, electrically connected to receive the identified operational mode signal and the unique linear converted signal from each of the summers, for selecting the unique linear converted signal associated with the identified operational mode, and causing that linear converted signal to be supplied to the feedback correction circuit 119.
5. A constant power control circuit 107 for an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111, wherein the power selection system 109 has a plurality of operational modes and the output switching radio frequency stage 105 has a primary transformer winding 113, and wherein the constant power control circuit 107 comprises:
a current sampling circuit 115 inductively coupled to one output electrode, the current sampling circuit 115 producing a sampled current signal proportional to the average current flowing through the output electrode;
a linear conversion circuit 117 electrically connected to the current sampling circuit 115 for generating a linear converted signal, wherein the linear conversion circuit 117 includes;
a linear multiplier generating means 201 for generating a plurality of unique multiplier reference signals, wherein there is one multiplier reference signal for each operational mode;
a linear offset generating means 203 for generating a plurality of unique offset reference signals, wherein there is one offset reference signal for each operational mode;
a plurality of multipliers 205, electrically connected to the linear multiplier generating means 201 and to receive the sampled current signal, wherein there is one multiplier for each operational mode and each multiplier multiplies the sampled current signal and the unique multiplier reference signal associated with one operational mode to produce a unique multiplied signal for that operational mode;
a plurality of summers 207, electrically connected to the linear offset generating means 203 and to each multiplier, wherein there is one summer for each operational mode and each summer sums the offset reference signal associated with one operational mode and the unique multiplied signal associated with that operational mode to produce a unique linear converted signal for that operational mode;
a mode monitor 209, electrically connected to the power selection system 109, for identifying the operational mode and producing an identified operational mode signal;
a signal selector 211, electrically connected to receive the identified operational mode signal and the unique linear converted signal from each of the summers, for selecting the unique linear converted signal associated with the identified operational mode, and causing that linear converted signal to be supplied to the feedback correction circuit 119; and a feedback correction circuit 119 electrically connected to receive the linear converted signal from the linear conversion circuit 1 17 and the control voltage signal from the power selection system 109 for producing a feedback control signal which is supplied to the power selection system 109 to control the amount of electrosurgical energy created, wherein the feedback correction circuit 1 19 includes:
a subtractor 301, electrically connected to receive the linear converted signal and the control voltage signal, for determining a difference in amplitudebetween the control voltage signal and the linear converted signal and producing a delta signal proportional to the difference;
an adder 303, electrically connected to receive the delta signal and the control voltage signal, for adding the delta signal to the control voltage signal and producing the feedback control signal;
a maximum control voltage reference generator 305, electrically connected to receive the control voltage signal, for generating a maximum control voltage reference signal;
a switcher 307, electrically connected to receive the maximum control voltage reference signal and the feedback control signal, for substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltagereference signal a high impedance reference generator 309, electrically connected to receive the control voltage signal, for generating a high impedance reference signal;
a connector 311 for electrically connecting the feedback correction circuit 119 to the primary transformer winding 113;
a comparator 313, electrically connected to the connector 311 and to receive the high impedance signal, for comparing the amplitude of the high impedance reference signal to the voltage across the primary transformer winding113 and producing a high impedance detection signal; and a reducer 315, electrically connected to receive the high impedance detection signal and the feedback control signal, for reducing the amplitude of the feedback control signal when the high impedance detection signal indicates that the voltage across the primary transformer winding 113 is greater than the high impedance reference signal.
a current sampling circuit 115 inductively coupled to one output electrode, the current sampling circuit 115 producing a sampled current signal proportional to the average current flowing through the output electrode;
a linear conversion circuit 117 electrically connected to the current sampling circuit 115 for generating a linear converted signal, wherein the linear conversion circuit 117 includes;
a linear multiplier generating means 201 for generating a plurality of unique multiplier reference signals, wherein there is one multiplier reference signal for each operational mode;
a linear offset generating means 203 for generating a plurality of unique offset reference signals, wherein there is one offset reference signal for each operational mode;
a plurality of multipliers 205, electrically connected to the linear multiplier generating means 201 and to receive the sampled current signal, wherein there is one multiplier for each operational mode and each multiplier multiplies the sampled current signal and the unique multiplier reference signal associated with one operational mode to produce a unique multiplied signal for that operational mode;
a plurality of summers 207, electrically connected to the linear offset generating means 203 and to each multiplier, wherein there is one summer for each operational mode and each summer sums the offset reference signal associated with one operational mode and the unique multiplied signal associated with that operational mode to produce a unique linear converted signal for that operational mode;
a mode monitor 209, electrically connected to the power selection system 109, for identifying the operational mode and producing an identified operational mode signal;
a signal selector 211, electrically connected to receive the identified operational mode signal and the unique linear converted signal from each of the summers, for selecting the unique linear converted signal associated with the identified operational mode, and causing that linear converted signal to be supplied to the feedback correction circuit 119; and a feedback correction circuit 119 electrically connected to receive the linear converted signal from the linear conversion circuit 1 17 and the control voltage signal from the power selection system 109 for producing a feedback control signal which is supplied to the power selection system 109 to control the amount of electrosurgical energy created, wherein the feedback correction circuit 1 19 includes:
a subtractor 301, electrically connected to receive the linear converted signal and the control voltage signal, for determining a difference in amplitudebetween the control voltage signal and the linear converted signal and producing a delta signal proportional to the difference;
an adder 303, electrically connected to receive the delta signal and the control voltage signal, for adding the delta signal to the control voltage signal and producing the feedback control signal;
a maximum control voltage reference generator 305, electrically connected to receive the control voltage signal, for generating a maximum control voltage reference signal;
a switcher 307, electrically connected to receive the maximum control voltage reference signal and the feedback control signal, for substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltagereference signal a high impedance reference generator 309, electrically connected to receive the control voltage signal, for generating a high impedance reference signal;
a connector 311 for electrically connecting the feedback correction circuit 119 to the primary transformer winding 113;
a comparator 313, electrically connected to the connector 311 and to receive the high impedance signal, for comparing the amplitude of the high impedance reference signal to the voltage across the primary transformer winding113 and producing a high impedance detection signal; and a reducer 315, electrically connected to receive the high impedance detection signal and the feedback control signal, for reducing the amplitude of the feedback control signal when the high impedance detection signal indicates that the voltage across the primary transformer winding 113 is greater than the high impedance reference signal.
6. A method for maintaining a generally constant output power from an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111, the method including the steps of:
inductively coupling to one output electrode;
sensing the current flowing through the output electrode;
producing a sampled current signal proportional to the average current flowing through the output electrode;
generating a multiplier reference signal;
generating an offset reference signal;
multiplying the sampled current signal and the multiplier reference signal; then summing the offset reference signal to the product to producing a linear converted signal;
connecting to the control voltage signal from the power selection system 109;
determining the difference in amplitude between the control voltage signal and the linear converted signal;
adding the difference determined by the subtraction means to the control voltage signal to produce a feedback control signal.
supplying the feedback control signal to the power selection system 109 to control the amount of electrosurgical energy created.
inductively coupling to one output electrode;
sensing the current flowing through the output electrode;
producing a sampled current signal proportional to the average current flowing through the output electrode;
generating a multiplier reference signal;
generating an offset reference signal;
multiplying the sampled current signal and the multiplier reference signal; then summing the offset reference signal to the product to producing a linear converted signal;
connecting to the control voltage signal from the power selection system 109;
determining the difference in amplitude between the control voltage signal and the linear converted signal;
adding the difference determined by the subtraction means to the control voltage signal to produce a feedback control signal.
supplying the feedback control signal to the power selection system 109 to control the amount of electrosurgical energy created.
7. The method for maintaining a generally constant output power from an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111 of Claim 6, wherein the output switching radio frequency stage 105 has a primary transformer winding 113, and wherein the method further includes the steps of:
generating a high impedance reference signal;
connecting to the primary transformer winding 113;
comparing the amplitude of the high impedance reference signal to the voltage across the primary transformer winding 113; and reducing the amplitude of the feedback control signal when the voltage across the primary transformer winding 113 is greater than the high impedance reference signal.
generating a high impedance reference signal;
connecting to the primary transformer winding 113;
comparing the amplitude of the high impedance reference signal to the voltage across the primary transformer winding 113; and reducing the amplitude of the feedback control signal when the voltage across the primary transformer winding 113 is greater than the high impedance reference signal.
8. The method for maintaining a generally constant output power from an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111 of Claim 6, the method further including the steps of:
generating a maximum control voltage reference signal; and substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltage reference signal.
generating a maximum control voltage reference signal; and substituting the maximum control voltage reference signal for the feedback control signal when the feedback control signal is greater in amplitude than the maximum control voltage reference signal.
9. The method for maintaining a generally constant output power from an electrosurgical generator 101 having a power selection system 109 that produces a control voltage signal to control a high voltage direct current supply 103 which supplies a high voltage signal to an output switching radio frequency stage 105 thereby creating an electrosurgical energy between two output electrodes 111 of Claim 6, wherein the power selection system 109 has a plurality of operational modes and wherein the method further includes the steps of:
generating a plurality of unique linear multiplier reference signals, one for each operational mode;
generating a plurality of unique linear offset reference signals, one for each operational mode;
multiplying the sampled current signal, separately and concurrently, with each of the unique multiplier reference signals to produce a plurality of unique multiplied signals, one for each operational mode;
summing each of the unique multiplied signals with the offset reference signal associated with the same operational mode to produce a plurality of unique linear converted signals, one for each operational mode;
connecting to the power selection system 109 to identify the operational mode selected;
selecting the unique linear converted signal that matches the identified operational mode; and then causing that linear converted signal to be supplied to the feedback correction circuit 119.
generating a plurality of unique linear multiplier reference signals, one for each operational mode;
generating a plurality of unique linear offset reference signals, one for each operational mode;
multiplying the sampled current signal, separately and concurrently, with each of the unique multiplier reference signals to produce a plurality of unique multiplied signals, one for each operational mode;
summing each of the unique multiplied signals with the offset reference signal associated with the same operational mode to produce a plurality of unique linear converted signals, one for each operational mode;
connecting to the power selection system 109 to identify the operational mode selected;
selecting the unique linear converted signal that matches the identified operational mode; and then causing that linear converted signal to be supplied to the feedback correction circuit 119.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/533,891 US5772659A (en) | 1995-09-26 | 1995-09-26 | Electrosurgical generator power control circuit and method |
| US08/533,891 | 1995-09-26 | ||
| PCT/IB1996/000618 WO1997011648A2 (en) | 1995-09-26 | 1996-06-28 | Electrosurgical generator power control circuit and method |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2229874A1 true CA2229874A1 (en) | 1997-04-03 |
Family
ID=24127859
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002229874A Abandoned CA2229874A1 (en) | 1995-09-26 | 1996-06-28 | Electrosurgical generator power control circuit and method |
Country Status (6)
| Country | Link |
|---|---|
| US (2) | US5772659A (en) |
| EP (1) | EP0852479A2 (en) |
| JP (1) | JPH10510461A (en) |
| AU (1) | AU699351B2 (en) |
| CA (1) | CA2229874A1 (en) |
| WO (1) | WO1997011648A2 (en) |
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| CN114391941A (en) * | 2021-12-21 | 2022-04-26 | 杭州堃博生物科技有限公司 | Control method, device, equipment and storage medium of radio frequency ablation circuit |
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| US3913583A (en) * | 1974-06-03 | 1975-10-21 | Sybron Corp | Control circuit for electrosurgical units |
| JPS5710740B2 (en) * | 1974-06-17 | 1982-02-27 | ||
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| US4092986A (en) * | 1976-06-14 | 1978-06-06 | Ipco Hospital Supply Corporation (Whaledent International Division) | Constant output electrosurgical unit |
| US4126137A (en) * | 1977-01-21 | 1978-11-21 | Minnesota Mining And Manufacturing Company | Electrosurgical unit |
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-
1995
- 1995-09-26 US US08/533,891 patent/US5772659A/en not_active Expired - Lifetime
-
1996
- 1996-06-28 WO PCT/IB1996/000618 patent/WO1997011648A2/en not_active Application Discontinuation
- 1996-06-28 JP JP9513240A patent/JPH10510461A/en active Pending
- 1996-06-28 CA CA002229874A patent/CA2229874A1/en not_active Abandoned
- 1996-06-28 AU AU60134/96A patent/AU699351B2/en not_active Ceased
- 1996-06-28 EP EP96917617A patent/EP0852479A2/en not_active Withdrawn
-
1998
- 1998-05-21 US US09/082,557 patent/US6251106B1/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| AU6013496A (en) | 1997-04-17 |
| JPH10510461A (en) | 1998-10-13 |
| AU699351B2 (en) | 1998-12-03 |
| EP0852479A2 (en) | 1998-07-15 |
| US5772659A (en) | 1998-06-30 |
| WO1997011648A2 (en) | 1997-04-03 |
| US6251106B1 (en) | 2001-06-26 |
| WO1997011648A3 (en) | 1997-06-12 |
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| EEER | Examination request | ||
| FZDE | Dead |