CA2243995A1 - Cordless bipolar electrocautery unit with automatic power control - Google Patents
Cordless bipolar electrocautery unit with automatic power control Download PDFInfo
- Publication number
- CA2243995A1 CA2243995A1 CA002243995A CA2243995A CA2243995A1 CA 2243995 A1 CA2243995 A1 CA 2243995A1 CA 002243995 A CA002243995 A CA 002243995A CA 2243995 A CA2243995 A CA 2243995A CA 2243995 A1 CA2243995 A1 CA 2243995A1
- Authority
- CA
- Canada
- Prior art keywords
- unit
- cautery
- output
- power
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00172—Connectors and adapters therefor
- A61B2018/00178—Electrical connectors
Abstract
A cordless electrocautery unit (5) for use in surgical procedures is described in which the unit is battery (10) operated and therefore cordless. The unit is microprocessor (14) controlled and provides for automatic feedback and control of the output power, in accordance with one of multiple power levels selected by the user.
Description
CA 0224399~ 1998-09-1~
DESCRIPTION
CO~DLESS BIPOLAR ELECTROCAUTERY UNIT WITH AUTOMATIC
POWER CONTRO~
TECHNICAL FI~LD
This invention related generally to an electrocautery unit and more particularly to a cordless bipolar electocautery unit with automatic power control.
~ACKGROUND ART
Electrocautery has been used in surgical procedures for many years for sealing openings in small veins and arteries, sealing certain other lumens such as in vasectomies procedures, and for cutting and removing tissue Electrocautery has become of particular importance with the increased popularity of laparoscopic surgery because of the difficulty in tying sutures and using scalpels through small trocar ports.
In a typical laparoscopic procedure, such as a laparoscopic cho}ecystectomy, a monopolar electrocautery unit is used to separate the gall bladder from the liver bed and to cauterize bleeders. Prior art monopolar 2 0 electrocautery units have a single internal electrode attached to the distal end of a long handle. The internal electrode is inserted into the abdominal cavity through a trocar. The handle is manipulated so that the e}ectrode is positioned proximate the bleeder or other tissue of concern. When the unit is activated by the surgeon, radio frequency (RF) energy is generated external to the patient and L~ led from the internal electrode as an RF current.
The current passes through the tissue to be cut or cauterized, traveling through the patients body, and re~ll...i..g to the cautery unit via a large flatexternal electrode in contact with the patients back Cutting is accomplished because the high current density proximate the small internal electrode causes the water content of the ~ rent tissue cells to evaporate, thereby bursting the cells. Cauterizing is accomplished by less power dissipation. Heating is localized near the internal electrode with little charring.
A number of problems can be associated with the use of monopolar cautery. If the patient's back does not make good contact with the external 3 5 electrode, the current density at the point where the charge exits the body can be high, producing severe burns to the patient. Bipolar electrocautery, in CA 0224399~ 1998-09-1~
which both electrodes are internal, solves this problem. The current density between the adjacent electrodes, both of which are put in contact with the tissue to be cut or cauterized, is readily controlled because the return path ofthe RF current is only from one electrode to another, usually spaced less than a millim~ter apart. U.S. patent nurnbers 4,034,762; 4,674,499; 4,805,616;
and 5,269,780 describe such bipolar probes for various surgical applications.
However, further problems arise from the use of prior art bipolar electrocautery devices, related to their portability and reliance on conventional AC power sources. Faulty components or poor electrical isolation can create a current leak from the AC power source to the cutting electrodes, causing severe injur,v or even death. Cosens, in U.~. Patent No.
DESCRIPTION
CO~DLESS BIPOLAR ELECTROCAUTERY UNIT WITH AUTOMATIC
POWER CONTRO~
TECHNICAL FI~LD
This invention related generally to an electrocautery unit and more particularly to a cordless bipolar electocautery unit with automatic power control.
~ACKGROUND ART
Electrocautery has been used in surgical procedures for many years for sealing openings in small veins and arteries, sealing certain other lumens such as in vasectomies procedures, and for cutting and removing tissue Electrocautery has become of particular importance with the increased popularity of laparoscopic surgery because of the difficulty in tying sutures and using scalpels through small trocar ports.
In a typical laparoscopic procedure, such as a laparoscopic cho}ecystectomy, a monopolar electrocautery unit is used to separate the gall bladder from the liver bed and to cauterize bleeders. Prior art monopolar 2 0 electrocautery units have a single internal electrode attached to the distal end of a long handle. The internal electrode is inserted into the abdominal cavity through a trocar. The handle is manipulated so that the e}ectrode is positioned proximate the bleeder or other tissue of concern. When the unit is activated by the surgeon, radio frequency (RF) energy is generated external to the patient and L~ led from the internal electrode as an RF current.
The current passes through the tissue to be cut or cauterized, traveling through the patients body, and re~ll...i..g to the cautery unit via a large flatexternal electrode in contact with the patients back Cutting is accomplished because the high current density proximate the small internal electrode causes the water content of the ~ rent tissue cells to evaporate, thereby bursting the cells. Cauterizing is accomplished by less power dissipation. Heating is localized near the internal electrode with little charring.
A number of problems can be associated with the use of monopolar cautery. If the patient's back does not make good contact with the external 3 5 electrode, the current density at the point where the charge exits the body can be high, producing severe burns to the patient. Bipolar electrocautery, in CA 0224399~ 1998-09-1~
which both electrodes are internal, solves this problem. The current density between the adjacent electrodes, both of which are put in contact with the tissue to be cut or cauterized, is readily controlled because the return path ofthe RF current is only from one electrode to another, usually spaced less than a millim~ter apart. U.S. patent nurnbers 4,034,762; 4,674,499; 4,805,616;
and 5,269,780 describe such bipolar probes for various surgical applications.
However, further problems arise from the use of prior art bipolar electrocautery devices, related to their portability and reliance on conventional AC power sources. Faulty components or poor electrical isolation can create a current leak from the AC power source to the cutting electrodes, causing severe injur,v or even death. Cosens, in U.~. Patent No.
4,034,762, describes a battery-operated bipolar electrocautery unit, designed for use in vasectomy procedures. The '762 device generates RF energy using a multi-vibrator and a step-up transformer. Although the '762 unit 1 5 solves the problems of portability and AC leakage, it is inefficient and requires a larger battery than could otherwise be used. Also, the '762 unit has no convenient means for adjusting the power delivered to the tissue and cannot control the amount of power delivered to the cutting area as the load resistance of the tissue changes during the cutting process.
What is needed, then, is an electrocautery unit which is portable, safe, usable in laparoscopic procedures, and which is capable of operating at autom:~ti-~lly controlled power levels selectable by the user, even as the load resi~t~n~e may change during use.
2 5 I~ISCLOSURE OF THE INVENTION
The electrocautery unit of this invention is cordless, as it relies on an integral, battery-powered regulated power supply. A microprocessor controls the operation of the electrocautery unit, and includes an input whereby the user of the unit can select one of multiple pre-det.ormined output power levels. An output on the ~ opfocessor provides a pulse-width-modulated ~PWM) drive signal to the input of a drive circuit. The output o~
the drive circuit is connected to the primary of a step-up transformer, with the secondary of the transforrner connPcted to a conventional bipolar cautery probe.
3 5 The output voltage across the cautery electrodes and the output current flowing through the electrodes are monitored in real time by a CA 0224399~ 1998-09-1~
WO 97/3~643 PCTIIB97/0~)346 feedback control circuit. Analog signals corresponding to the output voltage and current are ~iigiti7f~cl and used by the microprocessor to adjust the PWM
drive signal so that the power output is substantially m~int~in~ d at the predetermined level.
Preferably, the electrocautery unit of this invention will also include a battery pack having an encoder, with the microprocessor having a decoder.
In this embodiment, the microprocessor interrogates the battery encoder to verify that the battery installed in the unit is applo~l.ate for the application.
If not, operation of the unit is disabled.
The electrocautery unit of this invention also includes a digital display so that the user can visually confirrn the power level selected.
Fig. 1 is a block diagram of the cordless electrocautery unit of the present invention.
Figs. 2a and 2b are graphical representations of the signal levels and signal timing associated with the communication of control signals from the battery decoder to the battery pack encoder in a preferred embodirnent of the unit of Fig. 1, where tSyC represents the synchronization signal, tloW, represents the low logic signal for a write 1 tirne slot, t,owo represents the low logic signal for a write 0 time slot, and tSIot represents the duration of a single write time slot.
Figs. 3a and 3b are graphical representations of the signal levels and signal timing associated with col"""l"ic~tit)n of battery identifie:~ti--n data from the battery pack encoder to the cautery unit decoder, where tS~c represents the synchlo~ tion signal, TSU represents the read data setup 2 5 signal, tRDV represents the read data valid signal, and tSIot represents the duration of a single read time slot.
Fig. 4 is a table showing the sequence of states which are assumed by the battery encoder used in a ~3l er~ ed embodiment of the cautery unit.
Fig. S represents the sequence and logic levels during generation of a 3 0; reset pulse signal by the decoder and generation of presence detect signal by the battery encoder.
Fig. 6 is a block diagrarn of the decoder/controller section of the electrocautery unit of the present invention, as implemented in the microprocessor shown in Figs. 1 and 7.
Fig. 7 is a schem~ti~ diagrarn of the cordless electrocautery unit of Fig. l.
CA 0224399~ 1998-09-1~
WO 97/30643 PCT/lB97tO0346 BEST MODE FOR CARRYING OUT THE INVENTION
The general arrangement and a preferred embodiment of the electronic portion of a cordless electrocautery unit S are shown in Figs. 1 and 7. The purpose of the unit is to generate a cautery output signal including an output voltage VOU' at the secondary of a step-up transformer 11. The cautery output signal Vout represents an AC signal at a typical frequency of 400 kHz, and with typical peak voltages of 1200 volts, which is delivered to a conventional bipolar cautery probe (not shown), such as that described in U.S. Patent No. 5,269,780. Application of V,,ut across the electrodes of the probe creates a heat generating RF current (IoU,) through tissue located between the electrodes.
The cautery unit 5 is portable and cordless, being powered by an internal battery 10. A single-cell 3 volt lithium sulfur dioxide battery can be used, having a sufficiently low internal impedance to deliver a cauterizing output power re~uired by the needs of the surgeon, preferably variable up to 50 watts. The raw battery voltage Vb is boosted in a switching regulator circuit 15, based on a switching regulator chip ICl, such as a type LT1304 from Linear Technology. Chokes I,1 and L2, along with capacitors Cl and C2, and Zener diode Zl, smooth the output from I~1 to provide a 6.5 VDC
regulated operating voltage Vc~ for the active components of the cautery unit ~;, inrhl-ling a microprocessor 14, a drive circuit 13, a current sense amplifier 18, and a display decoder 32.
The cordless electrocautery unit 5 is improved over the battery-2 5 operated prior art because of its user selectable power output level . In accordance with this feature, an input switch 31 transmits a power level select signal to a power select input P0,0, preferably a memory register, in microprocessor 14. Preferably, the power level select signal will comprise one or more digital data pulses, with the number of pulses corresponding to discrete, user selected power levels. For example, the user may choose to use maximum (10~%) power and upon making that selection by using input switch 31 (such as by depressing switch 31 ten times), ten pulses will be generated and stored for use in a temporary memory location in microprocessor 14. Or, if switch 31 is depressed only one time, one pulse will be generated and stored if only 10% power is selected. The power level selected will be displayed on a two digit LCD display 35. The display 35 is CA 0224399~ lsss-os-l~
driven by a type MC14499 display decoder 32 through a bank of current Timiting resistors R~.
The power level of the cautery output signal Vout is varied using pulse width modulation (PWM). Accordingly, microprocessor 14 generates a PWM digital signal at output PMW to the input of a driver circuit 13.
Software resident in microprocessor 14 controls an internal data processor which causes the duty cycle (pulse width) of the drive signal to the input of drive circuit 13 to vary in proportion to the power level select signal previously stored in memory.
The drive circuit 13, shown in Fig. 7 as a pair of transistor Q1 and Q2 eleckically connected in a "totem pole" configuration to switch a field effect transistor (FET) stage 12 (transistors 12a and 12b on Fig. 7), acts as a switch in series with the prirnary of output transformer 11. Thus, the battery voltage Vb is switched on and off across the primary of transformer 11 at a rate and duty cycle detPrmin~d by microprocessor 14, discharging the bank of capacitors Cb (Fig. 7). Preferably, the switching frequency is approximately 400 kE~z. The duty cycle is varied as described above, in accordance with the user determined power level select signal. The FET 12 is protected from transient voltages, and the peak voltage applied to the 2 0 primary of transformer 11, by a one or more capacitors 26 and zener diodes 27.
The Ll~r~ er 11 steps up the primary voltage to approximately 1200 volts peak. Con~eql~ently, the duty cycle of the PWM output of microprocessor 14 defines the power available to the primary of transformer 11, and hence to the transformer secondary and cautery probe (not shown) for delivery to the tissue. The power available at the probe is roughly proportional to the square root of the duty cycle.
The cautery unit 5 is activated when switch 28 is closed, which provides a power-on signal to an input of microprocessor 14, through resistor Rl. However, in a preferred embodiment of the cautery unit, an encoder circuit 1~, based on a digital serial number encoder IC2, is associated with ~ battery 10. Encoder IC2, which preferably is integral to the package which includes battery 1(~, stores battery i~ ntif~c~tion data and commnnir~t~s that ~ battery ifiPnti~lc~tion data on command to an input of microprocessor 14. A
pull-up resistor R2 electrically connects encoder IC2 to the battery voltage Vb .
CA 0224399~ 1998-09-1~
WO 97~30643 PCT/IB97/00346 ~n a ~lt;r~ d embodiment of the cautery unit 5, the encoder chip IC2 can be a Model DS2401 Silicon Serial Nurnber integrated circuit m~m7f~ct-lred by Dallas Serniconductor. In such an embodiment, all data c. )" ., . ,u"i~:ltions between encoder IC2 and microprocessor 14 is accomplished by a single interface line. Battery identific~tion data stored in encoder IC2 can then include an eight-bit digitally encoded model or type number and a forty-eight bit battery identification code. Encoder IC2 in this embodiment can further include an eight-bit check value which can be used, as described below, to confirm that battery if lPnrifif ~tion data from encoder IC2 has been correctly received by the system.
The data stored in encoder IC2 is ~cessed during read and write time slots, as shown on Figs. 2a, 2b, 3a, and 3b.
To fully implement in the electrocautery unit of the present invention - all the features available ~rom encoder IC2 as described above, a decoderlcontrol unit 30 is illustrated in more detail in Fig. 6. Preferably, thedecoder/control unit 30 is integral to microprocessor 14. A type 83C752 microprocessor from Phillips Electronics can be used in this application. A
tirner circuit 41 provides the various timing and logic signals in a conventional marmer to other functional modules of decoder 30.
A reset pulse generator 43 is used to provide a control signal in the form of reset pulses to encoder IC2, as shown on Fig. 5. This allows encoder IC2 to progress in an olg~li:Ged se(luence from an initial reset condition to a condition where it can receive control signals from decoder 30 and then comm-lniczlt~ battery identification data, including the type number, the battery i-lt?ntific~ti~-n code, and the check value, such states of encoder IC2 being illustrated on Fig. 4. A command word generator 36 is also inclllrlecl in decoder 30 to generate other necessary control signals to encoderIC2.
When switch 28 is closed, a type number decoder/comparator module 37 receives the type number from encoder IC2 and makes the necessary comparisons to a pre-programmed type number stored in module 37 (non-volatile memory in microprocessor 14), which in the pre~llcd embodiment is the hexadecimal number 01. Battery identification code comparator module 39, also part of decoder 30, receives the battery identification code ~rom encoder IC2 and makes a comparison OlC the battery identification code to a unit identific~tion code stored in unit code memory module 38. Code co~ aldlor module 39 also provides a comparison signal to interrupt signal ,--CA 0224399~ lsss-os-l~
~1VO 97/30643 PCT/~B97/00346 generator 40 to imiir.~t~ whether there has been a proper match of the battery identifi~tit~n code with the unit identification code. If the comparison signal from code co~ aldLor module 39 in~ t~s a code mi~m~trh, interrupt signal ~ ~enerator 40 then generates an i~ llu~t signal, disabling operation of the electrocautery unit 5.
Thus, if the battery identific~tion data from encoder I~2 is outside the allowable value, the rnicroprocessor interrupts its PWM signal to the input of driver circuit 13, so that no cauterization signal VOU~ is available at the probe.
Under this Ull~llU~l condition, the battery 10 must be replaced before the unit 5 can be reset. Preferably, encoder circuit 16 will be integral to battery 10.
To further insure proper operation of the unit 5, an A/D input (AD0) of rnicroprocessor 14 monitors the raw battery voltage Vb and will shut the unit ~ down if the battery voltage goes too low.
In the irnproved electrocautery unit 5 of this invention, the power supplied to the cautery probe is monitored and controlled i~ulo~ lly by an alllulllalic cautery power feedback and control circuit. The RF current IoU, which passes through the tissue being cauL~ ed flows through a current sensing resistor 17. The value of current IoUt depends on the load (tissue) 2~ re~i.ct:~nl-e as well as the amplitude of Vo,~t, and is measured as a voltage drop across resistor 17. The voltage across resistor 17 is amplified by current sense di~r~ llial amplifier 18 then rectified and filtered in a first rectifier/filter stage 33, which on Fig. 7 comprises diodes D1 and D2, capacitor C3, resistor R3, and Zener diode Z2. The output of rectifier/filter stage 33 is now an analog DC signal which is proportional to the m~nit~-d~
of the current I~ flowing through the tissue. This signal is l1igiti7e~ by an A/D converter integral to a analog input AD2 on microprocessor 14. The cautery output voltage V0ut is also rectified and filtered in a second rectifier/filter stage 34 (diodes D3 and D4, capacitor C4, resistor R4, and Zener diode Z3 on Fig. 7) and ~1igiti7.~l1 at A/D converter input AD3 in microprocessor 14.
Thus, the product of the signals at inputs AD2 and AD3 is Lional to the cautery output power being supplied to the tissue. As the tissue irnpedance changes during the ~lul~ lg or cutting process, a software sub-routine resident in microprocessor 14 adJusts the duty cycle of the PWM output signal to driver circuit 13, to m~int~in the selected power level pre-selected by the user. This output power feedback and control CA 02243995 lsss-os-15 Wo 97130643 pcTlls97loo346 circuit also helps prevent injury or darnage if the probe is inadvertently touched to other tools placed inside the body cavity.
Thus, although a particular embodiment of a new cordless electrocautery unit has been described7 it is not intended that such descriptionbe construed as limiting the scope of this invention except as set forth in the following claims. Further, although certain components and operating parameters are described as being associated with the plc~rell~d embodiment, it is not intended that such be construed as limitations upon the scope of this invention except as set forth in the following claims.
What is needed, then, is an electrocautery unit which is portable, safe, usable in laparoscopic procedures, and which is capable of operating at autom:~ti-~lly controlled power levels selectable by the user, even as the load resi~t~n~e may change during use.
2 5 I~ISCLOSURE OF THE INVENTION
The electrocautery unit of this invention is cordless, as it relies on an integral, battery-powered regulated power supply. A microprocessor controls the operation of the electrocautery unit, and includes an input whereby the user of the unit can select one of multiple pre-det.ormined output power levels. An output on the ~ opfocessor provides a pulse-width-modulated ~PWM) drive signal to the input of a drive circuit. The output o~
the drive circuit is connected to the primary of a step-up transformer, with the secondary of the transforrner connPcted to a conventional bipolar cautery probe.
3 5 The output voltage across the cautery electrodes and the output current flowing through the electrodes are monitored in real time by a CA 0224399~ 1998-09-1~
WO 97/3~643 PCTIIB97/0~)346 feedback control circuit. Analog signals corresponding to the output voltage and current are ~iigiti7f~cl and used by the microprocessor to adjust the PWM
drive signal so that the power output is substantially m~int~in~ d at the predetermined level.
Preferably, the electrocautery unit of this invention will also include a battery pack having an encoder, with the microprocessor having a decoder.
In this embodiment, the microprocessor interrogates the battery encoder to verify that the battery installed in the unit is applo~l.ate for the application.
If not, operation of the unit is disabled.
The electrocautery unit of this invention also includes a digital display so that the user can visually confirrn the power level selected.
Fig. 1 is a block diagram of the cordless electrocautery unit of the present invention.
Figs. 2a and 2b are graphical representations of the signal levels and signal timing associated with the communication of control signals from the battery decoder to the battery pack encoder in a preferred embodirnent of the unit of Fig. 1, where tSyC represents the synchronization signal, tloW, represents the low logic signal for a write 1 tirne slot, t,owo represents the low logic signal for a write 0 time slot, and tSIot represents the duration of a single write time slot.
Figs. 3a and 3b are graphical representations of the signal levels and signal timing associated with col"""l"ic~tit)n of battery identifie:~ti--n data from the battery pack encoder to the cautery unit decoder, where tS~c represents the synchlo~ tion signal, TSU represents the read data setup 2 5 signal, tRDV represents the read data valid signal, and tSIot represents the duration of a single read time slot.
Fig. 4 is a table showing the sequence of states which are assumed by the battery encoder used in a ~3l er~ ed embodiment of the cautery unit.
Fig. S represents the sequence and logic levels during generation of a 3 0; reset pulse signal by the decoder and generation of presence detect signal by the battery encoder.
Fig. 6 is a block diagrarn of the decoder/controller section of the electrocautery unit of the present invention, as implemented in the microprocessor shown in Figs. 1 and 7.
Fig. 7 is a schem~ti~ diagrarn of the cordless electrocautery unit of Fig. l.
CA 0224399~ 1998-09-1~
WO 97/30643 PCT/lB97tO0346 BEST MODE FOR CARRYING OUT THE INVENTION
The general arrangement and a preferred embodiment of the electronic portion of a cordless electrocautery unit S are shown in Figs. 1 and 7. The purpose of the unit is to generate a cautery output signal including an output voltage VOU' at the secondary of a step-up transformer 11. The cautery output signal Vout represents an AC signal at a typical frequency of 400 kHz, and with typical peak voltages of 1200 volts, which is delivered to a conventional bipolar cautery probe (not shown), such as that described in U.S. Patent No. 5,269,780. Application of V,,ut across the electrodes of the probe creates a heat generating RF current (IoU,) through tissue located between the electrodes.
The cautery unit 5 is portable and cordless, being powered by an internal battery 10. A single-cell 3 volt lithium sulfur dioxide battery can be used, having a sufficiently low internal impedance to deliver a cauterizing output power re~uired by the needs of the surgeon, preferably variable up to 50 watts. The raw battery voltage Vb is boosted in a switching regulator circuit 15, based on a switching regulator chip ICl, such as a type LT1304 from Linear Technology. Chokes I,1 and L2, along with capacitors Cl and C2, and Zener diode Zl, smooth the output from I~1 to provide a 6.5 VDC
regulated operating voltage Vc~ for the active components of the cautery unit ~;, inrhl-ling a microprocessor 14, a drive circuit 13, a current sense amplifier 18, and a display decoder 32.
The cordless electrocautery unit 5 is improved over the battery-2 5 operated prior art because of its user selectable power output level . In accordance with this feature, an input switch 31 transmits a power level select signal to a power select input P0,0, preferably a memory register, in microprocessor 14. Preferably, the power level select signal will comprise one or more digital data pulses, with the number of pulses corresponding to discrete, user selected power levels. For example, the user may choose to use maximum (10~%) power and upon making that selection by using input switch 31 (such as by depressing switch 31 ten times), ten pulses will be generated and stored for use in a temporary memory location in microprocessor 14. Or, if switch 31 is depressed only one time, one pulse will be generated and stored if only 10% power is selected. The power level selected will be displayed on a two digit LCD display 35. The display 35 is CA 0224399~ lsss-os-l~
driven by a type MC14499 display decoder 32 through a bank of current Timiting resistors R~.
The power level of the cautery output signal Vout is varied using pulse width modulation (PWM). Accordingly, microprocessor 14 generates a PWM digital signal at output PMW to the input of a driver circuit 13.
Software resident in microprocessor 14 controls an internal data processor which causes the duty cycle (pulse width) of the drive signal to the input of drive circuit 13 to vary in proportion to the power level select signal previously stored in memory.
The drive circuit 13, shown in Fig. 7 as a pair of transistor Q1 and Q2 eleckically connected in a "totem pole" configuration to switch a field effect transistor (FET) stage 12 (transistors 12a and 12b on Fig. 7), acts as a switch in series with the prirnary of output transformer 11. Thus, the battery voltage Vb is switched on and off across the primary of transformer 11 at a rate and duty cycle detPrmin~d by microprocessor 14, discharging the bank of capacitors Cb (Fig. 7). Preferably, the switching frequency is approximately 400 kE~z. The duty cycle is varied as described above, in accordance with the user determined power level select signal. The FET 12 is protected from transient voltages, and the peak voltage applied to the 2 0 primary of transformer 11, by a one or more capacitors 26 and zener diodes 27.
The Ll~r~ er 11 steps up the primary voltage to approximately 1200 volts peak. Con~eql~ently, the duty cycle of the PWM output of microprocessor 14 defines the power available to the primary of transformer 11, and hence to the transformer secondary and cautery probe (not shown) for delivery to the tissue. The power available at the probe is roughly proportional to the square root of the duty cycle.
The cautery unit 5 is activated when switch 28 is closed, which provides a power-on signal to an input of microprocessor 14, through resistor Rl. However, in a preferred embodiment of the cautery unit, an encoder circuit 1~, based on a digital serial number encoder IC2, is associated with ~ battery 10. Encoder IC2, which preferably is integral to the package which includes battery 1(~, stores battery i~ ntif~c~tion data and commnnir~t~s that ~ battery ifiPnti~lc~tion data on command to an input of microprocessor 14. A
pull-up resistor R2 electrically connects encoder IC2 to the battery voltage Vb .
CA 0224399~ 1998-09-1~
WO 97~30643 PCT/IB97/00346 ~n a ~lt;r~ d embodiment of the cautery unit 5, the encoder chip IC2 can be a Model DS2401 Silicon Serial Nurnber integrated circuit m~m7f~ct-lred by Dallas Serniconductor. In such an embodiment, all data c. )" ., . ,u"i~:ltions between encoder IC2 and microprocessor 14 is accomplished by a single interface line. Battery identific~tion data stored in encoder IC2 can then include an eight-bit digitally encoded model or type number and a forty-eight bit battery identification code. Encoder IC2 in this embodiment can further include an eight-bit check value which can be used, as described below, to confirm that battery if lPnrifif ~tion data from encoder IC2 has been correctly received by the system.
The data stored in encoder IC2 is ~cessed during read and write time slots, as shown on Figs. 2a, 2b, 3a, and 3b.
To fully implement in the electrocautery unit of the present invention - all the features available ~rom encoder IC2 as described above, a decoderlcontrol unit 30 is illustrated in more detail in Fig. 6. Preferably, thedecoder/control unit 30 is integral to microprocessor 14. A type 83C752 microprocessor from Phillips Electronics can be used in this application. A
tirner circuit 41 provides the various timing and logic signals in a conventional marmer to other functional modules of decoder 30.
A reset pulse generator 43 is used to provide a control signal in the form of reset pulses to encoder IC2, as shown on Fig. 5. This allows encoder IC2 to progress in an olg~li:Ged se(luence from an initial reset condition to a condition where it can receive control signals from decoder 30 and then comm-lniczlt~ battery identification data, including the type number, the battery i-lt?ntific~ti~-n code, and the check value, such states of encoder IC2 being illustrated on Fig. 4. A command word generator 36 is also inclllrlecl in decoder 30 to generate other necessary control signals to encoderIC2.
When switch 28 is closed, a type number decoder/comparator module 37 receives the type number from encoder IC2 and makes the necessary comparisons to a pre-programmed type number stored in module 37 (non-volatile memory in microprocessor 14), which in the pre~llcd embodiment is the hexadecimal number 01. Battery identification code comparator module 39, also part of decoder 30, receives the battery identification code ~rom encoder IC2 and makes a comparison OlC the battery identification code to a unit identific~tion code stored in unit code memory module 38. Code co~ aldlor module 39 also provides a comparison signal to interrupt signal ,--CA 0224399~ lsss-os-l~
~1VO 97/30643 PCT/~B97/00346 generator 40 to imiir.~t~ whether there has been a proper match of the battery identifi~tit~n code with the unit identification code. If the comparison signal from code co~ aldLor module 39 in~ t~s a code mi~m~trh, interrupt signal ~ ~enerator 40 then generates an i~ llu~t signal, disabling operation of the electrocautery unit 5.
Thus, if the battery identific~tion data from encoder I~2 is outside the allowable value, the rnicroprocessor interrupts its PWM signal to the input of driver circuit 13, so that no cauterization signal VOU~ is available at the probe.
Under this Ull~llU~l condition, the battery 10 must be replaced before the unit 5 can be reset. Preferably, encoder circuit 16 will be integral to battery 10.
To further insure proper operation of the unit 5, an A/D input (AD0) of rnicroprocessor 14 monitors the raw battery voltage Vb and will shut the unit ~ down if the battery voltage goes too low.
In the irnproved electrocautery unit 5 of this invention, the power supplied to the cautery probe is monitored and controlled i~ulo~ lly by an alllulllalic cautery power feedback and control circuit. The RF current IoU, which passes through the tissue being cauL~ ed flows through a current sensing resistor 17. The value of current IoUt depends on the load (tissue) 2~ re~i.ct:~nl-e as well as the amplitude of Vo,~t, and is measured as a voltage drop across resistor 17. The voltage across resistor 17 is amplified by current sense di~r~ llial amplifier 18 then rectified and filtered in a first rectifier/filter stage 33, which on Fig. 7 comprises diodes D1 and D2, capacitor C3, resistor R3, and Zener diode Z2. The output of rectifier/filter stage 33 is now an analog DC signal which is proportional to the m~nit~-d~
of the current I~ flowing through the tissue. This signal is l1igiti7e~ by an A/D converter integral to a analog input AD2 on microprocessor 14. The cautery output voltage V0ut is also rectified and filtered in a second rectifier/filter stage 34 (diodes D3 and D4, capacitor C4, resistor R4, and Zener diode Z3 on Fig. 7) and ~1igiti7.~l1 at A/D converter input AD3 in microprocessor 14.
Thus, the product of the signals at inputs AD2 and AD3 is Lional to the cautery output power being supplied to the tissue. As the tissue irnpedance changes during the ~lul~ lg or cutting process, a software sub-routine resident in microprocessor 14 adJusts the duty cycle of the PWM output signal to driver circuit 13, to m~int~in the selected power level pre-selected by the user. This output power feedback and control CA 02243995 lsss-os-15 Wo 97130643 pcTlls97loo346 circuit also helps prevent injury or darnage if the probe is inadvertently touched to other tools placed inside the body cavity.
Thus, although a particular embodiment of a new cordless electrocautery unit has been described7 it is not intended that such descriptionbe construed as limiting the scope of this invention except as set forth in the following claims. Further, although certain components and operating parameters are described as being associated with the plc~rell~d embodiment, it is not intended that such be construed as limitations upon the scope of this invention except as set forth in the following claims.
Claims (10)
1. An electrocautery unit, including a cautery probe having bipolar electrodes, comprising:
a. cautery signal generator means to generate a cautery output signal at a pre-determined cautery power output such that an RF current is caused to flow between the electrodes through tissue proximate the probe;
b. power selection means to vary the pre-determined cautery power output in response to a power level selection made by a user of the unit such that the unit can be operated at multiple pre-determined cautery power output levels; and c. a power supply, including a battery, integral to the unit and which is electrically connected to the cautery signal generator means such that the unit can be operated without an external power supply cord.
a. cautery signal generator means to generate a cautery output signal at a pre-determined cautery power output such that an RF current is caused to flow between the electrodes through tissue proximate the probe;
b. power selection means to vary the pre-determined cautery power output in response to a power level selection made by a user of the unit such that the unit can be operated at multiple pre-determined cautery power output levels; and c. a power supply, including a battery, integral to the unit and which is electrically connected to the cautery signal generator means such that the unit can be operated without an external power supply cord.
2. The electrocautery unit of Claim 1 further comprising cautery power output feedback and control means to monitor the actual cautery power output during operation of the unit and to adjust the cautery output signal such that the pre-determined cautery power output selected by the user is automatically maintained during operation of the unit.
3. The electrocautery unit of Claim 2 wherein the battery includes an encoder containing electronic battery identification data, and the unit further comprising:
a. means to electronically store unit identification data;
b. means to compare the battery identification data to the unit identification data; and c. interrupt means to interrupt operation of the unit if the battery identification data does not match the unit identification data.
a. means to electronically store unit identification data;
b. means to compare the battery identification data to the unit identification data; and c. interrupt means to interrupt operation of the unit if the battery identification data does not match the unit identification data.
4. The electrocautery unit of Claim 2 wherein the cautery signal generator includes means to vary the cautery output signal by pulse width modulation in response to the power level selection means and in response to the cautery power output feedback and control means.
5. The electrocautery unit of Claim 4 wherein the cautery power output feedback and control means comprises:
a. means to produce a first digital signal proportional to the magnitude of the RF current;
b. means to produce a second digital signal proportional to the magnitude of the cautery output voltage; and c. means to calculate the actual cautery power output from the first and second digital signals.
a. means to produce a first digital signal proportional to the magnitude of the RF current;
b. means to produce a second digital signal proportional to the magnitude of the cautery output voltage; and c. means to calculate the actual cautery power output from the first and second digital signals.
6. An electrocautery unit for cutting and heating tissue in conjunction with a bipolar cautery probe comprising:
a. signal generator means to generate and supply a cautery output signal to the probe;
b. power output control means to control the cautery output signal such that the power dissipated in the tissue during use of the unit is controlled to a pre-determined power output level; and c. a battery integral to the unit and operatively connected to the signal generator means and to the power output control means to provide for cordless operation of the unit.
a. signal generator means to generate and supply a cautery output signal to the probe;
b. power output control means to control the cautery output signal such that the power dissipated in the tissue during use of the unit is controlled to a pre-determined power output level; and c. a battery integral to the unit and operatively connected to the signal generator means and to the power output control means to provide for cordless operation of the unit.
7. The electrocautery unit of Claim 6 further comprising power output selection means to adjust the pre-determined power output level of the unit in response to a user selection.
8. The electrocautery unit of Claim 7 further comprising means to display the pre-determined power output level selected by the user.
9. An electrocautery unit for use with a bipolar cautery probe comprising:
a. a microprocessor, including a signal generator connected to a cautery drive signal output, a first A/D converter input, and a second A/D
converter input;
b. an output transformer having a primary winding and a secondary winding;
c. a drive circuit having a drive circuit input and a drive circuit output, the drive circuit input connected to the cautery drive signal output andthe drive circuit output operatively connected to the primary winding of the output transformer;
d. an output current feedback circuit which provides an output current signal to the first A/D converter input of the microprocessor, the output current feedback signal corresponding to a magnitude of output current from the unit;
e. an output voltage feedback circuit electrically connecting the secondary winding of the output transformer and which provides an output voltage feedback signal to the second A/D converter input of the microprocessor corresponding a magnitude of the output voltage; and f. an integral battery connected to a regulated power supply for the unit.
a. a microprocessor, including a signal generator connected to a cautery drive signal output, a first A/D converter input, and a second A/D
converter input;
b. an output transformer having a primary winding and a secondary winding;
c. a drive circuit having a drive circuit input and a drive circuit output, the drive circuit input connected to the cautery drive signal output andthe drive circuit output operatively connected to the primary winding of the output transformer;
d. an output current feedback circuit which provides an output current signal to the first A/D converter input of the microprocessor, the output current feedback signal corresponding to a magnitude of output current from the unit;
e. an output voltage feedback circuit electrically connecting the secondary winding of the output transformer and which provides an output voltage feedback signal to the second A/D converter input of the microprocessor corresponding a magnitude of the output voltage; and f. an integral battery connected to a regulated power supply for the unit.
10. The electrocautery unit of Claim 9 in which the microprocessor further comprises:
a power select input including a memory register for receiving and storing power level data corresponding to a pre-determined power output level for the unit selected by the user; and a data processor, operatively connected to the power select input, to the first and second A/D converter inputs, and to the signal generator, the data processor including modulator means for changing a cautery output drive signal at the cautery drive signal output in response to changes in the power output level data and in response to changes in actual power output current and voltage signals.
a power select input including a memory register for receiving and storing power level data corresponding to a pre-determined power output level for the unit selected by the user; and a data processor, operatively connected to the power select input, to the first and second A/D converter inputs, and to the signal generator, the data processor including modulator means for changing a cautery output drive signal at the cautery drive signal output in response to changes in the power output level data and in response to changes in actual power output current and voltage signals.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/604,850 | 1996-02-22 | ||
US08/604,850 US5792138A (en) | 1996-02-22 | 1996-02-22 | Cordless bipolar electrocautery unit with automatic power control |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2243995A1 true CA2243995A1 (en) | 1997-08-28 |
Family
ID=24421309
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002243995A Abandoned CA2243995A1 (en) | 1996-02-22 | 1997-02-18 | Cordless bipolar electrocautery unit with automatic power control |
Country Status (6)
Country | Link |
---|---|
US (1) | US5792138A (en) |
EP (1) | EP0955923A1 (en) |
JP (1) | JP2000504616A (en) |
AU (1) | AU730413B2 (en) |
CA (1) | CA2243995A1 (en) |
WO (1) | WO1997030643A1 (en) |
Families Citing this family (293)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5772659A (en) * | 1995-09-26 | 1998-06-30 | Valleylab Inc. | Electrosurgical generator power control circuit and method |
US7267675B2 (en) * | 1996-01-05 | 2007-09-11 | Thermage, Inc. | RF device with thermo-electric cooler |
US7229436B2 (en) | 1996-01-05 | 2007-06-12 | Thermage, Inc. | Method and kit for treatment of tissue |
US20030212393A1 (en) * | 1996-01-05 | 2003-11-13 | Knowlton Edward W. | Handpiece with RF electrode and non-volatile memory |
US7473251B2 (en) * | 1996-01-05 | 2009-01-06 | Thermage, Inc. | Methods for creating tissue effect utilizing electromagnetic energy and a reverse thermal gradient |
US7115123B2 (en) * | 1996-01-05 | 2006-10-03 | Thermage, Inc. | Handpiece with electrode and non-volatile memory |
US6171305B1 (en) * | 1998-05-05 | 2001-01-09 | Cardiac Pacemakers, Inc. | RF ablation apparatus and method having high output impedance drivers |
JP4142173B2 (en) * | 1998-10-09 | 2008-08-27 | アルフレッサファーマ株式会社 | Disposable medical device and medical device incorporating the same |
US20040167508A1 (en) * | 2002-02-11 | 2004-08-26 | Robert Wham | Vessel sealing system |
US6796981B2 (en) | 1999-09-30 | 2004-09-28 | Sherwood Services Ag | Vessel sealing system |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
US6398779B1 (en) | 1998-10-23 | 2002-06-04 | Sherwood Services Ag | Vessel sealing system |
US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US6235027B1 (en) * | 1999-01-21 | 2001-05-22 | Garrett D. Herzon | Thermal cautery surgical forceps |
US6809649B1 (en) * | 1999-01-26 | 2004-10-26 | Telefonaktiebolaget Lm Ericsson(Publ) | Method and apparatus for communication between an electronic device and a connected battery |
AU7362400A (en) | 1999-09-10 | 2001-04-10 | Transurgical, Inc. | Occlusion of tubular anatomical structures by energy application |
JP4346826B2 (en) * | 2001-02-28 | 2009-10-21 | 瑞穂医科工業株式会社 | Portable electrosurgical device, portable electrosurgical device system including the same, and control method for portable electrosurgical device |
US6551312B2 (en) | 2001-03-09 | 2003-04-22 | Quantum Cor, Inc. | Wireless electrosurgical device and methods thereof |
US11229472B2 (en) | 2001-06-12 | 2022-01-25 | Cilag Gmbh International | Modular battery powered handheld surgical instrument with multiple magnetic position sensors |
US6630139B2 (en) * | 2001-08-24 | 2003-10-07 | Academia Sinica | Fibrinogenolytic proteases with thrombolytic and antihypertensive activities: medical application and novel process of expression and production |
US6796980B2 (en) * | 2001-11-21 | 2004-09-28 | Cardiac Pacemakers, Inc. | System and method for validating and troubleshooting ablation system set-up |
US6695837B2 (en) | 2002-03-13 | 2004-02-24 | Starion Instruments Corporation | Power supply for identification and control of electrical surgical tools |
WO2003092520A1 (en) | 2002-05-06 | 2003-11-13 | Sherwood Services Ag | Blood detector for controlling anesu and method therefor |
EP1601666A2 (en) | 2002-07-02 | 2005-12-07 | Schering Corporation | New neuropeptide y y5 receptor antagonists |
US6939347B2 (en) * | 2002-11-19 | 2005-09-06 | Conmed Corporation | Electrosurgical generator and method with voltage and frequency regulated high-voltage current mode power supply |
US7044948B2 (en) | 2002-12-10 | 2006-05-16 | Sherwood Services Ag | Circuit for controlling arc energy from an electrosurgical generator |
US8542717B2 (en) | 2003-03-03 | 2013-09-24 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US8063760B2 (en) | 2003-03-03 | 2011-11-22 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US7411506B2 (en) | 2003-03-03 | 2008-08-12 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US7019650B2 (en) | 2003-03-03 | 2006-03-28 | Caducys, L.L.C. | Interrogator and interrogation system employing the same |
US7893840B2 (en) | 2003-03-03 | 2011-02-22 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US8174366B2 (en) | 2003-03-03 | 2012-05-08 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US7671744B2 (en) * | 2003-03-03 | 2010-03-02 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US7764178B2 (en) | 2003-03-03 | 2010-07-27 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US7541933B2 (en) | 2003-03-03 | 2009-06-02 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US7128741B1 (en) * | 2003-04-04 | 2006-10-31 | Megadyne Medical Products, Inc. | Methods, systems, and devices for performing electrosurgical procedures |
US7722601B2 (en) | 2003-05-01 | 2010-05-25 | Covidien Ag | Method and system for programming and controlling an electrosurgical generator system |
US8104956B2 (en) | 2003-10-23 | 2012-01-31 | Covidien Ag | Thermocouple measurement circuit |
AU2003284929B2 (en) | 2003-10-23 | 2010-07-22 | Covidien Ag | Redundant temperature monitoring in electrosurgical systems for safety mitigation |
US7396336B2 (en) | 2003-10-30 | 2008-07-08 | Sherwood Services Ag | Switched resonant ultrasonic power amplifier system |
US7131860B2 (en) | 2003-11-20 | 2006-11-07 | Sherwood Services Ag | Connector systems for electrosurgical generator |
US7766905B2 (en) | 2004-02-12 | 2010-08-03 | Covidien Ag | Method and system for continuity testing of medical electrodes |
US8182501B2 (en) | 2004-02-27 | 2012-05-22 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical shears and method for sealing a blood vessel using same |
US7780662B2 (en) | 2004-03-02 | 2010-08-24 | Covidien Ag | Vessel sealing system using capacitive RF dielectric heating |
CA2558312A1 (en) | 2004-03-03 | 2005-09-15 | Caducys, L.L.C. | Interrogator and interrogation system employing the same |
US7088256B2 (en) * | 2004-07-30 | 2006-08-08 | Motorola, Inc. | Portable electronic device and method of operation therefore |
US7501948B2 (en) | 2004-09-29 | 2009-03-10 | Lone Star Ip Holdings, Lp | Interrogation system employing prior knowledge about an object to discern an identity thereof |
JP5009159B2 (en) | 2004-10-08 | 2012-08-22 | エシコン・エンド−サージェリィ・インコーポレイテッド | Ultrasonic surgical instrument |
US7628786B2 (en) | 2004-10-13 | 2009-12-08 | Covidien Ag | Universal foot switch contact port |
US9474564B2 (en) | 2005-03-31 | 2016-10-25 | Covidien Ag | Method and system for compensating for external impedance of an energy carrying component when controlling an electrosurgical generator |
US20070035383A1 (en) * | 2005-08-09 | 2007-02-15 | Roemerman Steven D | Radio frequency identification interrogation systems and methods of operating the same |
US20070191713A1 (en) | 2005-10-14 | 2007-08-16 | Eichmann Stephen E | Ultrasonic device for cutting and coagulating |
US8734438B2 (en) | 2005-10-21 | 2014-05-27 | Covidien Ag | Circuit and method for reducing stored energy in an electrosurgical generator |
US7947039B2 (en) | 2005-12-12 | 2011-05-24 | Covidien Ag | Laparoscopic apparatus for performing electrosurgical procedures |
US7621930B2 (en) | 2006-01-20 | 2009-11-24 | Ethicon Endo-Surgery, Inc. | Ultrasound medical instrument having a medical ultrasonic blade |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
CA2575392C (en) | 2006-01-24 | 2015-07-07 | Sherwood Services Ag | System and method for tissue sealing |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
US8147485B2 (en) | 2006-01-24 | 2012-04-03 | Covidien Ag | System and method for tissue sealing |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
CA2574934C (en) | 2006-01-24 | 2015-12-29 | Sherwood Services Ag | System and method for closed loop monitoring of monopolar electrosurgical apparatus |
CA2574935A1 (en) | 2006-01-24 | 2007-07-24 | Sherwood Services Ag | A method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US7651493B2 (en) | 2006-03-03 | 2010-01-26 | Covidien Ag | System and method for controlling electrosurgical snares |
US7648499B2 (en) | 2006-03-21 | 2010-01-19 | Covidien Ag | System and method for generating radio frequency energy |
US7651492B2 (en) | 2006-04-24 | 2010-01-26 | Covidien Ag | Arc based adaptive control system for an electrosurgical unit |
US8753334B2 (en) | 2006-05-10 | 2014-06-17 | Covidien Ag | System and method for reducing leakage current in an electrosurgical generator |
JP2009537226A (en) * | 2006-05-18 | 2009-10-29 | エヌディーアイ メディカル, エルエルシー | Portable assembly, system, and method for providing functional or therapeutic neural stimulation |
US8034049B2 (en) | 2006-08-08 | 2011-10-11 | Covidien Ag | System and method for measuring initial tissue impedance |
US7731717B2 (en) | 2006-08-08 | 2010-06-08 | Covidien Ag | System and method for controlling RF output during tissue sealing |
US7637907B2 (en) * | 2006-09-19 | 2009-12-29 | Covidien Ag | System and method for return electrode monitoring |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
US8142461B2 (en) | 2007-03-22 | 2012-03-27 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8911460B2 (en) | 2007-03-22 | 2014-12-16 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US8226675B2 (en) | 2007-03-22 | 2012-07-24 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8057498B2 (en) | 2007-11-30 | 2011-11-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instrument blades |
US8777941B2 (en) | 2007-05-10 | 2014-07-15 | Covidien Lp | Adjustable impedance electrosurgical electrodes |
US7834484B2 (en) | 2007-07-16 | 2010-11-16 | Tyco Healthcare Group Lp | Connection cable and method for activating a voltage-controlled generator |
US8523889B2 (en) | 2007-07-27 | 2013-09-03 | Ethicon Endo-Surgery, Inc. | Ultrasonic end effectors with increased active length |
US8808319B2 (en) | 2007-07-27 | 2014-08-19 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US8882791B2 (en) | 2007-07-27 | 2014-11-11 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US9044261B2 (en) | 2007-07-31 | 2015-06-02 | Ethicon Endo-Surgery, Inc. | Temperature controlled ultrasonic surgical instruments |
US8430898B2 (en) | 2007-07-31 | 2013-04-30 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US8512365B2 (en) | 2007-07-31 | 2013-08-20 | Ethicon Endo-Surgery, Inc. | Surgical instruments |
US7755491B2 (en) | 2007-08-13 | 2010-07-13 | Veroscan, Inc. | Interrogator and interrogation system employing the same |
US8216220B2 (en) | 2007-09-07 | 2012-07-10 | Tyco Healthcare Group Lp | System and method for transmission of combined data stream |
US8512332B2 (en) | 2007-09-21 | 2013-08-20 | Covidien Lp | Real-time arc control in electrosurgical generators |
US8623027B2 (en) | 2007-10-05 | 2014-01-07 | Ethicon Endo-Surgery, Inc. | Ergonomic surgical instruments |
US8758342B2 (en) * | 2007-11-28 | 2014-06-24 | Covidien Ag | Cordless power-assisted medical cauterization and cutting device |
US8377059B2 (en) * | 2007-11-28 | 2013-02-19 | Covidien Ag | Cordless medical cauterization and cutting device |
US9050098B2 (en) * | 2007-11-28 | 2015-06-09 | Covidien Ag | Cordless medical cauterization and cutting device |
US10010339B2 (en) | 2007-11-30 | 2018-07-03 | Ethicon Llc | Ultrasonic surgical blades |
US8338726B2 (en) | 2009-08-26 | 2012-12-25 | Covidien Ag | Two-stage switch for cordless hand-held ultrasonic cautery cutting device |
US9017355B2 (en) | 2007-12-03 | 2015-04-28 | Covidien Ag | Battery-powered hand-held ultrasonic surgical cautery cutting device |
US8663262B2 (en) | 2007-12-03 | 2014-03-04 | Covidien Ag | Battery assembly for battery-powered surgical instruments |
US8061014B2 (en) | 2007-12-03 | 2011-11-22 | Covidien Ag | Method of assembling a cordless hand-held ultrasonic cautery cutting device |
US9314261B2 (en) | 2007-12-03 | 2016-04-19 | Covidien Ag | Battery-powered hand-held ultrasonic surgical cautery cutting device |
US8435257B2 (en) * | 2007-12-03 | 2013-05-07 | Covidien Ag | Cordless hand-held ultrasonic cautery cutting device and method |
US8419757B2 (en) * | 2007-12-03 | 2013-04-16 | Covidien Ag | Cordless hand-held ultrasonic cautery cutting device |
US9107690B2 (en) | 2007-12-03 | 2015-08-18 | Covidien Ag | Battery-powered hand-held ultrasonic surgical cautery cutting device |
US8328802B2 (en) * | 2008-03-19 | 2012-12-11 | Covidien Ag | Cordless medical cauterization and cutting device |
US8491581B2 (en) * | 2008-03-19 | 2013-07-23 | Covidien Ag | Method for powering a surgical instrument |
US8226639B2 (en) | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
US9089360B2 (en) | 2008-08-06 | 2015-07-28 | Ethicon Endo-Surgery, Inc. | Devices and techniques for cutting and coagulating tissue |
US8058771B2 (en) | 2008-08-06 | 2011-11-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic device for cutting and coagulating with stepped output |
US9782217B2 (en) | 2008-11-13 | 2017-10-10 | Covidien Ag | Radio frequency generator and method for a cordless medical cauterization and cutting device |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
US8486058B1 (en) * | 2009-01-30 | 2013-07-16 | Chest Innovations, Inc. | Minigenerator |
US10045819B2 (en) | 2009-04-14 | 2018-08-14 | Covidien Lp | Frequency identification for microwave ablation probes |
US9700339B2 (en) | 2009-05-20 | 2017-07-11 | Ethicon Endo-Surgery, Inc. | Coupling arrangements and methods for attaching tools to ultrasonic surgical instruments |
US8344596B2 (en) | 2009-06-24 | 2013-01-01 | Ethicon Endo-Surgery, Inc. | Transducer arrangements for ultrasonic surgical instruments |
US8663220B2 (en) | 2009-07-15 | 2014-03-04 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments |
US10383629B2 (en) * | 2009-08-10 | 2019-08-20 | Covidien Lp | System and method for preventing reprocessing of a powered surgical instrument |
USRE47996E1 (en) | 2009-10-09 | 2020-05-19 | Ethicon Llc | Surgical generator for ultrasonic and electrosurgical devices |
US10172669B2 (en) | 2009-10-09 | 2019-01-08 | Ethicon Llc | Surgical instrument comprising an energy trigger lockout |
US11090104B2 (en) | 2009-10-09 | 2021-08-17 | Cilag Gmbh International | Surgical generator for ultrasonic and electrosurgical devices |
US10441345B2 (en) | 2009-10-09 | 2019-10-15 | Ethicon Llc | Surgical generator for ultrasonic and electrosurgical devices |
US9168054B2 (en) | 2009-10-09 | 2015-10-27 | Ethicon Endo-Surgery, Inc. | Surgical generator for ultrasonic and electrosurgical devices |
US8986302B2 (en) * | 2009-10-09 | 2015-03-24 | Ethicon Endo-Surgery, Inc. | Surgical generator for ultrasonic and electrosurgical devices |
US9198712B1 (en) * | 2010-01-29 | 2015-12-01 | Chest Innovations | Minigenerator |
US8951272B2 (en) | 2010-02-11 | 2015-02-10 | Ethicon Endo-Surgery, Inc. | Seal arrangements for ultrasonically powered surgical instruments |
US8486096B2 (en) | 2010-02-11 | 2013-07-16 | Ethicon Endo-Surgery, Inc. | Dual purpose surgical instrument for cutting and coagulating tissue |
US8961547B2 (en) | 2010-02-11 | 2015-02-24 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with moving cutting implement |
US8579928B2 (en) | 2010-02-11 | 2013-11-12 | Ethicon Endo-Surgery, Inc. | Outer sheath and blade arrangements for ultrasonic surgical instruments |
US8469981B2 (en) | 2010-02-11 | 2013-06-25 | Ethicon Endo-Surgery, Inc. | Rotatable cutting implement arrangements for ultrasonic surgical instruments |
US8834518B2 (en) | 2010-04-12 | 2014-09-16 | Ethicon Endo-Surgery, Inc. | Electrosurgical cutting and sealing instruments with cam-actuated jaws |
US8709035B2 (en) | 2010-04-12 | 2014-04-29 | Ethicon Endo-Surgery, Inc. | Electrosurgical cutting and sealing instruments with jaws having a parallel closure motion |
US8685020B2 (en) | 2010-05-17 | 2014-04-01 | Ethicon Endo-Surgery, Inc. | Surgical instruments and end effectors therefor |
GB2480498A (en) | 2010-05-21 | 2011-11-23 | Ethicon Endo Surgery Inc | Medical device comprising RF circuitry |
US9005199B2 (en) | 2010-06-10 | 2015-04-14 | Ethicon Endo-Surgery, Inc. | Heat management configurations for controlling heat dissipation from electrosurgical instruments |
US8795327B2 (en) | 2010-07-22 | 2014-08-05 | Ethicon Endo-Surgery, Inc. | Electrosurgical instrument with separate closure and cutting members |
US8663270B2 (en) | 2010-07-23 | 2014-03-04 | Conmed Corporation | Jaw movement mechanism and method for a surgical tool |
US9192431B2 (en) | 2010-07-23 | 2015-11-24 | Ethicon Endo-Surgery, Inc. | Electrosurgical cutting and sealing instrument |
US8840609B2 (en) | 2010-07-23 | 2014-09-23 | Conmed Corporation | Tissue fusion system and method of performing a functional verification test |
US8979890B2 (en) | 2010-10-01 | 2015-03-17 | Ethicon Endo-Surgery, Inc. | Surgical instrument with jaw member |
US9035774B2 (en) | 2011-04-11 | 2015-05-19 | Lone Star Ip Holdings, Lp | Interrogator and system employing the same |
CA2774751C (en) * | 2011-04-15 | 2018-11-06 | Covidien Ag | Battery powered hand-held ultrasonic surgical cautery cutting device |
US9636167B2 (en) | 2011-05-31 | 2017-05-02 | Covidien Lp | Surgical device with DC power connection |
US9844384B2 (en) * | 2011-07-11 | 2017-12-19 | Covidien Lp | Stand alone energy-based tissue clips |
US9259265B2 (en) | 2011-07-22 | 2016-02-16 | Ethicon Endo-Surgery, Llc | Surgical instruments for tensioning tissue |
US9044243B2 (en) | 2011-08-30 | 2015-06-02 | Ethcon Endo-Surgery, Inc. | Surgical cutting and fastening device with descendible second trigger arrangement |
US9033973B2 (en) | 2011-08-30 | 2015-05-19 | Covidien Lp | System and method for DC tissue impedance sensing |
US9314292B2 (en) | 2011-10-24 | 2016-04-19 | Ethicon Endo-Surgery, Llc | Trigger lockout mechanism |
EP2811932B1 (en) | 2012-02-10 | 2019-06-26 | Ethicon LLC | Robotically controlled surgical instrument |
US9724118B2 (en) | 2012-04-09 | 2017-08-08 | Ethicon Endo-Surgery, Llc | Techniques for cutting and coagulating tissue for ultrasonic surgical instruments |
US9226766B2 (en) | 2012-04-09 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Serial communication protocol for medical device |
US9241731B2 (en) | 2012-04-09 | 2016-01-26 | Ethicon Endo-Surgery, Inc. | Rotatable electrical connection for ultrasonic surgical instruments |
US9439668B2 (en) | 2012-04-09 | 2016-09-13 | Ethicon Endo-Surgery, Llc | Switch arrangements for ultrasonic surgical instruments |
US9237921B2 (en) | 2012-04-09 | 2016-01-19 | Ethicon Endo-Surgery, Inc. | Devices and techniques for cutting and coagulating tissue |
US20140005640A1 (en) | 2012-06-28 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Surgical end effector jaw and electrode configurations |
US20140005705A1 (en) | 2012-06-29 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Surgical instruments with articulating shafts |
US20140005702A1 (en) | 2012-06-29 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Ultrasonic surgical instruments with distally positioned transducers |
US9351754B2 (en) | 2012-06-29 | 2016-05-31 | Ethicon Endo-Surgery, Llc | Ultrasonic surgical instruments with distally positioned jaw assemblies |
US9226767B2 (en) | 2012-06-29 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Closed feedback control for electrosurgical device |
US9820768B2 (en) | 2012-06-29 | 2017-11-21 | Ethicon Llc | Ultrasonic surgical instruments with control mechanisms |
US9283045B2 (en) | 2012-06-29 | 2016-03-15 | Ethicon Endo-Surgery, Llc | Surgical instruments with fluid management system |
US9326788B2 (en) | 2012-06-29 | 2016-05-03 | Ethicon Endo-Surgery, Llc | Lockout mechanism for use with robotic electrosurgical device |
US9408622B2 (en) | 2012-06-29 | 2016-08-09 | Ethicon Endo-Surgery, Llc | Surgical instruments with articulating shafts |
US9393037B2 (en) | 2012-06-29 | 2016-07-19 | Ethicon Endo-Surgery, Llc | Surgical instruments with articulating shafts |
US9198714B2 (en) | 2012-06-29 | 2015-12-01 | Ethicon Endo-Surgery, Inc. | Haptic feedback devices for surgical robot |
BR112015007010B1 (en) | 2012-09-28 | 2022-05-31 | Ethicon Endo-Surgery, Inc | end actuator |
US10201365B2 (en) | 2012-10-22 | 2019-02-12 | Ethicon Llc | Surgeon feedback sensing and display methods |
US9095367B2 (en) | 2012-10-22 | 2015-08-04 | Ethicon Endo-Surgery, Inc. | Flexible harmonic waveguides/blades for surgical instruments |
US20140135804A1 (en) | 2012-11-15 | 2014-05-15 | Ethicon Endo-Surgery, Inc. | Ultrasonic and electrosurgical devices |
US10226273B2 (en) | 2013-03-14 | 2019-03-12 | Ethicon Llc | Mechanical fasteners for use with surgical energy devices |
US9241728B2 (en) | 2013-03-15 | 2016-01-26 | Ethicon Endo-Surgery, Inc. | Surgical instrument with multiple clamping mechanisms |
US9283028B2 (en) | 2013-03-15 | 2016-03-15 | Covidien Lp | Crest-factor control of phase-shifted inverter |
US10729484B2 (en) | 2013-07-16 | 2020-08-04 | Covidien Lp | Electrosurgical generator with continuously and arbitrarily variable crest factor |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9636165B2 (en) | 2013-07-29 | 2017-05-02 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
US9295514B2 (en) | 2013-08-30 | 2016-03-29 | Ethicon Endo-Surgery, Llc | Surgical devices with close quarter articulation features |
US9814514B2 (en) | 2013-09-13 | 2017-11-14 | Ethicon Llc | Electrosurgical (RF) medical instruments for cutting and coagulating tissue |
US9861428B2 (en) | 2013-09-16 | 2018-01-09 | Ethicon Llc | Integrated systems for electrosurgical steam or smoke control |
US9839469B2 (en) * | 2013-09-24 | 2017-12-12 | Covidien Lp | Systems and methods for improving efficiency of electrosurgical generators |
CA2860197C (en) * | 2013-09-24 | 2021-12-07 | Covidien Lp | Systems and methods for improving efficiency of electrosurgical generators |
US9770283B2 (en) * | 2013-09-24 | 2017-09-26 | Covidien Lp | Systems and methods for improving efficiency of electrosurgical generators |
US9265926B2 (en) | 2013-11-08 | 2016-02-23 | Ethicon Endo-Surgery, Llc | Electrosurgical devices |
US9526565B2 (en) | 2013-11-08 | 2016-12-27 | Ethicon Endo-Surgery, Llc | Electrosurgical devices |
GB2521229A (en) | 2013-12-16 | 2015-06-17 | Ethicon Endo Surgery Inc | Medical device |
GB2521228A (en) | 2013-12-16 | 2015-06-17 | Ethicon Endo Surgery Inc | Medical device |
US9795436B2 (en) | 2014-01-07 | 2017-10-24 | Ethicon Llc | Harvesting energy from a surgical generator |
US9408660B2 (en) | 2014-01-17 | 2016-08-09 | Ethicon Endo-Surgery, Llc | Device trigger dampening mechanism |
WO2015116825A1 (en) * | 2014-01-30 | 2015-08-06 | Eighmy Eugene A | Surgical cutting device |
US9554854B2 (en) | 2014-03-18 | 2017-01-31 | Ethicon Endo-Surgery, Llc | Detecting short circuits in electrosurgical medical devices |
US10463421B2 (en) | 2014-03-27 | 2019-11-05 | Ethicon Llc | Two stage trigger, clamp and cut bipolar vessel sealer |
US10092310B2 (en) | 2014-03-27 | 2018-10-09 | Ethicon Llc | Electrosurgical devices |
US10524852B1 (en) | 2014-03-28 | 2020-01-07 | Ethicon Llc | Distal sealing end effector with spacers |
US9737355B2 (en) | 2014-03-31 | 2017-08-22 | Ethicon Llc | Controlling impedance rise in electrosurgical medical devices |
US9913680B2 (en) | 2014-04-15 | 2018-03-13 | Ethicon Llc | Software algorithms for electrosurgical instruments |
US9757186B2 (en) | 2014-04-17 | 2017-09-12 | Ethicon Llc | Device status feedback for bipolar tissue spacer |
US9700333B2 (en) | 2014-06-30 | 2017-07-11 | Ethicon Llc | Surgical instrument with variable tissue compression |
US10285724B2 (en) | 2014-07-31 | 2019-05-14 | Ethicon Llc | Actuation mechanisms and load adjustment assemblies for surgical instruments |
US9877776B2 (en) | 2014-08-25 | 2018-01-30 | Ethicon Llc | Simultaneous I-beam and spring driven cam jaw closure mechanism |
US10194976B2 (en) | 2014-08-25 | 2019-02-05 | Ethicon Llc | Lockout disabling mechanism |
US10194972B2 (en) | 2014-08-26 | 2019-02-05 | Ethicon Llc | Managing tissue treatment |
WO2016070013A1 (en) | 2014-10-31 | 2016-05-06 | Medtronic Advanced Energy Llc | Fingerswitch circuitry to reduce rf leakage current |
US10639092B2 (en) | 2014-12-08 | 2020-05-05 | Ethicon Llc | Electrode configurations for surgical instruments |
US10111699B2 (en) | 2014-12-22 | 2018-10-30 | Ethicon Llc | RF tissue sealer, shear grip, trigger lock mechanism and energy activation |
US10159524B2 (en) | 2014-12-22 | 2018-12-25 | Ethicon Llc | High power battery powered RF amplifier topology |
US9848937B2 (en) | 2014-12-22 | 2017-12-26 | Ethicon Llc | End effector with detectable configurations |
US10092348B2 (en) | 2014-12-22 | 2018-10-09 | Ethicon Llc | RF tissue sealer, shear grip, trigger lock mechanism and energy activation |
US10245095B2 (en) | 2015-02-06 | 2019-04-02 | Ethicon Llc | Electrosurgical instrument with rotation and articulation mechanisms |
US10321950B2 (en) | 2015-03-17 | 2019-06-18 | Ethicon Llc | Managing tissue treatment |
US10342602B2 (en) | 2015-03-17 | 2019-07-09 | Ethicon Llc | Managing tissue treatment |
US10595929B2 (en) | 2015-03-24 | 2020-03-24 | Ethicon Llc | Surgical instruments with firing system overload protection mechanisms |
US10314638B2 (en) | 2015-04-07 | 2019-06-11 | Ethicon Llc | Articulating radio frequency (RF) tissue seal with articulating state sensing |
US10117702B2 (en) | 2015-04-10 | 2018-11-06 | Ethicon Llc | Surgical generator systems and related methods |
US10130410B2 (en) | 2015-04-17 | 2018-11-20 | Ethicon Llc | Electrosurgical instrument including a cutting member decouplable from a cutting member trigger |
US9872725B2 (en) | 2015-04-29 | 2018-01-23 | Ethicon Llc | RF tissue sealer with mode selection |
US10034684B2 (en) | 2015-06-15 | 2018-07-31 | Ethicon Llc | Apparatus and method for dissecting and coagulating tissue |
US11020140B2 (en) | 2015-06-17 | 2021-06-01 | Cilag Gmbh International | Ultrasonic surgical blade for use with ultrasonic surgical instruments |
US10898256B2 (en) | 2015-06-30 | 2021-01-26 | Ethicon Llc | Surgical system with user adaptable techniques based on tissue impedance |
US11141213B2 (en) | 2015-06-30 | 2021-10-12 | Cilag Gmbh International | Surgical instrument with user adaptable techniques |
US11051873B2 (en) | 2015-06-30 | 2021-07-06 | Cilag Gmbh International | Surgical system with user adaptable techniques employing multiple energy modalities based on tissue parameters |
US11129669B2 (en) | 2015-06-30 | 2021-09-28 | Cilag Gmbh International | Surgical system with user adaptable techniques based on tissue type |
US10034704B2 (en) | 2015-06-30 | 2018-07-31 | Ethicon Llc | Surgical instrument with user adaptable algorithms |
US10357303B2 (en) | 2015-06-30 | 2019-07-23 | Ethicon Llc | Translatable outer tube for sealing using shielded lap chole dissector |
US10154852B2 (en) | 2015-07-01 | 2018-12-18 | Ethicon Llc | Ultrasonic surgical blade with improved cutting and coagulation features |
US11446078B2 (en) * | 2015-07-20 | 2022-09-20 | Megadyne Medical Products, Inc. | Electrosurgical wave generator |
US11033322B2 (en) | 2015-09-30 | 2021-06-15 | Ethicon Llc | Circuit topologies for combined generator |
US10595930B2 (en) | 2015-10-16 | 2020-03-24 | Ethicon Llc | Electrode wiping surgical device |
US10959771B2 (en) | 2015-10-16 | 2021-03-30 | Ethicon Llc | Suction and irrigation sealing grasper |
US9901393B2 (en) * | 2015-11-09 | 2018-02-27 | First Pass, Llc | Cautery device |
EP3182552B1 (en) | 2015-12-18 | 2018-11-14 | Oxis Energy Limited | Lithium-sulfur battery management system |
US10959806B2 (en) | 2015-12-30 | 2021-03-30 | Ethicon Llc | Energized medical device with reusable handle |
US10179022B2 (en) | 2015-12-30 | 2019-01-15 | Ethicon Llc | Jaw position impedance limiter for electrosurgical instrument |
US10575892B2 (en) | 2015-12-31 | 2020-03-03 | Ethicon Llc | Adapter for electrical surgical instruments |
US11129670B2 (en) | 2016-01-15 | 2021-09-28 | Cilag Gmbh International | Modular battery powered handheld surgical instrument with selective application of energy based on button displacement, intensity, or local tissue characterization |
US11051840B2 (en) | 2016-01-15 | 2021-07-06 | Ethicon Llc | Modular battery powered handheld surgical instrument with reusable asymmetric handle housing |
US11229471B2 (en) | 2016-01-15 | 2022-01-25 | Cilag Gmbh International | Modular battery powered handheld surgical instrument with selective application of energy based on tissue characterization |
US10716615B2 (en) | 2016-01-15 | 2020-07-21 | Ethicon Llc | Modular battery powered handheld surgical instrument with curved end effectors having asymmetric engagement between jaw and blade |
US10555769B2 (en) | 2016-02-22 | 2020-02-11 | Ethicon Llc | Flexible circuits for electrosurgical instrument |
US10485607B2 (en) | 2016-04-29 | 2019-11-26 | Ethicon Llc | Jaw structure with distal closure for electrosurgical instruments |
US10646269B2 (en) | 2016-04-29 | 2020-05-12 | Ethicon Llc | Non-linear jaw gap for electrosurgical instruments |
US10702329B2 (en) | 2016-04-29 | 2020-07-07 | Ethicon Llc | Jaw structure with distal post for electrosurgical instruments |
US10856934B2 (en) | 2016-04-29 | 2020-12-08 | Ethicon Llc | Electrosurgical instrument with electrically conductive gap setting and tissue engaging members |
US10987156B2 (en) | 2016-04-29 | 2021-04-27 | Ethicon Llc | Electrosurgical instrument with electrically conductive gap setting member and electrically insulative tissue engaging members |
US10456193B2 (en) | 2016-05-03 | 2019-10-29 | Ethicon Llc | Medical device with a bilateral jaw configuration for nerve stimulation |
US10368898B2 (en) | 2016-05-05 | 2019-08-06 | Covidien Lp | Ultrasonic surgical instrument |
US10245064B2 (en) | 2016-07-12 | 2019-04-02 | Ethicon Llc | Ultrasonic surgical instrument with piezoelectric central lumen transducer |
US10893883B2 (en) | 2016-07-13 | 2021-01-19 | Ethicon Llc | Ultrasonic assembly for use with ultrasonic surgical instruments |
US10842522B2 (en) | 2016-07-15 | 2020-11-24 | Ethicon Llc | Ultrasonic surgical instruments having offset blades |
US10376305B2 (en) | 2016-08-05 | 2019-08-13 | Ethicon Llc | Methods and systems for advanced harmonic energy |
US10285723B2 (en) | 2016-08-09 | 2019-05-14 | Ethicon Llc | Ultrasonic surgical blade with improved heel portion |
USD847990S1 (en) | 2016-08-16 | 2019-05-07 | Ethicon Llc | Surgical instrument |
US10828056B2 (en) | 2016-08-25 | 2020-11-10 | Ethicon Llc | Ultrasonic transducer to waveguide acoustic coupling, connections, and configurations |
US10952759B2 (en) | 2016-08-25 | 2021-03-23 | Ethicon Llc | Tissue loading of a surgical instrument |
US10751117B2 (en) | 2016-09-23 | 2020-08-25 | Ethicon Llc | Electrosurgical instrument with fluid diverter |
US10603064B2 (en) | 2016-11-28 | 2020-03-31 | Ethicon Llc | Ultrasonic transducer |
US11266430B2 (en) | 2016-11-29 | 2022-03-08 | Cilag Gmbh International | End effector control and calibration |
US11033325B2 (en) | 2017-02-16 | 2021-06-15 | Cilag Gmbh International | Electrosurgical instrument with telescoping suction port and debris cleaner |
US10799284B2 (en) | 2017-03-15 | 2020-10-13 | Ethicon Llc | Electrosurgical instrument with textured jaws |
US11497546B2 (en) | 2017-03-31 | 2022-11-15 | Cilag Gmbh International | Area ratios of patterned coatings on RF electrodes to reduce sticking |
US10571435B2 (en) | 2017-06-08 | 2020-02-25 | Covidien Lp | Systems and methods for digital control of ultrasonic devices |
US10603117B2 (en) | 2017-06-28 | 2020-03-31 | Ethicon Llc | Articulation state detection mechanisms |
US10820920B2 (en) | 2017-07-05 | 2020-11-03 | Ethicon Llc | Reusable ultrasonic medical devices and methods of their use |
US11033323B2 (en) | 2017-09-29 | 2021-06-15 | Cilag Gmbh International | Systems and methods for managing fluid and suction in electrosurgical systems |
US11490951B2 (en) | 2017-09-29 | 2022-11-08 | Cilag Gmbh International | Saline contact with electrodes |
US11484358B2 (en) | 2017-09-29 | 2022-11-01 | Cilag Gmbh International | Flexible electrosurgical instrument |
US20200188055A1 (en) * | 2017-10-01 | 2020-06-18 | James Keith Bleiler | Surgical Safety Devices and Methods |
US11246617B2 (en) | 2018-01-29 | 2022-02-15 | Covidien Lp | Compact ultrasonic transducer and ultrasonic surgical instrument including the same |
US11246621B2 (en) | 2018-01-29 | 2022-02-15 | Covidien Lp | Ultrasonic transducers and ultrasonic surgical instruments including the same |
US11259832B2 (en) | 2018-01-29 | 2022-03-01 | Covidien Lp | Ultrasonic horn for an ultrasonic surgical instrument, ultrasonic surgical instrument including the same, and method of manufacturing an ultrasonic horn |
US11229449B2 (en) | 2018-02-05 | 2022-01-25 | Covidien Lp | Ultrasonic horn, ultrasonic transducer assembly, and ultrasonic surgical instrument including the same |
TWI666814B (en) * | 2018-02-14 | 2019-07-21 | 車王電子股份有限公司 | Battery pack |
US10582944B2 (en) | 2018-02-23 | 2020-03-10 | Covidien Lp | Ultrasonic surgical instrument with torque assist feature |
US11607278B2 (en) | 2019-06-27 | 2023-03-21 | Cilag Gmbh International | Cooperative robotic surgical systems |
US11547468B2 (en) | 2019-06-27 | 2023-01-10 | Cilag Gmbh International | Robotic surgical system with safety and cooperative sensing control |
US11612445B2 (en) | 2019-06-27 | 2023-03-28 | Cilag Gmbh International | Cooperative operation of robotic arms |
US11413102B2 (en) | 2019-06-27 | 2022-08-16 | Cilag Gmbh International | Multi-access port for surgical robotic systems |
US11723729B2 (en) | 2019-06-27 | 2023-08-15 | Cilag Gmbh International | Robotic surgical assembly coupling safety mechanisms |
US11478268B2 (en) | 2019-08-16 | 2022-10-25 | Covidien Lp | Jaw members for surgical instruments and surgical instruments incorporating the same |
US11666357B2 (en) | 2019-09-16 | 2023-06-06 | Covidien Lp | Enclosure for electronics of a surgical instrument |
US11684412B2 (en) | 2019-12-30 | 2023-06-27 | Cilag Gmbh International | Surgical instrument with rotatable and articulatable surgical end effector |
US11786294B2 (en) | 2019-12-30 | 2023-10-17 | Cilag Gmbh International | Control program for modular combination energy device |
US11950797B2 (en) | 2019-12-30 | 2024-04-09 | Cilag Gmbh International | Deflectable electrode with higher distal bias relative to proximal bias |
US20210196361A1 (en) | 2019-12-30 | 2021-07-01 | Ethicon Llc | Electrosurgical instrument with monopolar and bipolar energy capabilities |
US11812957B2 (en) | 2019-12-30 | 2023-11-14 | Cilag Gmbh International | Surgical instrument comprising a signal interference resolution system |
US11786291B2 (en) | 2019-12-30 | 2023-10-17 | Cilag Gmbh International | Deflectable support of RF energy electrode with respect to opposing ultrasonic blade |
US11944366B2 (en) | 2019-12-30 | 2024-04-02 | Cilag Gmbh International | Asymmetric segmented ultrasonic support pad for cooperative engagement with a movable RF electrode |
US11744636B2 (en) | 2019-12-30 | 2023-09-05 | Cilag Gmbh International | Electrosurgical systems with integrated and external power sources |
US11911063B2 (en) | 2019-12-30 | 2024-02-27 | Cilag Gmbh International | Techniques for detecting ultrasonic blade to electrode contact and reducing power to ultrasonic blade |
US11696776B2 (en) | 2019-12-30 | 2023-07-11 | Cilag Gmbh International | Articulatable surgical instrument |
US11779387B2 (en) | 2019-12-30 | 2023-10-10 | Cilag Gmbh International | Clamp arm jaw to minimize tissue sticking and improve tissue control |
US11452525B2 (en) | 2019-12-30 | 2022-09-27 | Cilag Gmbh International | Surgical instrument comprising an adjustment system |
US11937863B2 (en) | 2019-12-30 | 2024-03-26 | Cilag Gmbh International | Deflectable electrode with variable compression bias along the length of the deflectable electrode |
US11779329B2 (en) | 2019-12-30 | 2023-10-10 | Cilag Gmbh International | Surgical instrument comprising a flex circuit including a sensor system |
US11660089B2 (en) | 2019-12-30 | 2023-05-30 | Cilag Gmbh International | Surgical instrument comprising a sensing system |
US11937866B2 (en) | 2019-12-30 | 2024-03-26 | Cilag Gmbh International | Method for an electrosurgical procedure |
US20220117623A1 (en) | 2020-10-15 | 2022-04-21 | Covidien Lp | Ultrasonic surgical instrument |
US11931026B2 (en) | 2021-06-30 | 2024-03-19 | Cilag Gmbh International | Staple cartridge replacement |
US11717312B2 (en) | 2021-10-01 | 2023-08-08 | Covidien Lp | Surgical system including blade visualization markings |
Family Cites Families (22)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2894512A (en) * | 1957-10-07 | 1959-07-14 | Tapper Robert | Epilation device |
US2994324A (en) * | 1959-03-04 | 1961-08-01 | Lemos Albano | Electrolysis epilator |
US3646931A (en) * | 1970-02-25 | 1972-03-07 | Jerry A Phelps | Portable battery-powered instrument for visualizing the peripheral pulse waveform and pulse rate |
US3807411A (en) * | 1971-08-16 | 1974-04-30 | Concept | External cardiac pacer with separable generating and power-probe units |
US3978312A (en) * | 1974-10-17 | 1976-08-31 | Concept, Inc. | Variable temperature electric cautery assembly |
US4034762A (en) * | 1975-08-04 | 1977-07-12 | Electro Medical Systems, Inc. | Vas cautery apparatus |
US4276883A (en) * | 1978-11-06 | 1981-07-07 | Medtronic, Inc. | Battery monitor for digital cardiac pacemaker |
US4357943A (en) * | 1978-11-06 | 1982-11-09 | Medtronic, Inc. | Demand cardiac pacemaker having reduced polarity disparity |
US4515159A (en) * | 1978-11-06 | 1985-05-07 | Medtronic, Inc. | Digital cardiac pacemaker with rate limit means |
US4805616A (en) * | 1980-12-08 | 1989-02-21 | Pao David S C | Bipolar probes for ophthalmic surgery and methods of performing anterior capsulotomy |
US4674499A (en) * | 1980-12-08 | 1987-06-23 | Pao David S C | Coaxial bipolar probe |
FR2536924A1 (en) * | 1982-11-25 | 1984-06-01 | Courtois Michele | ELECTRO-SURGERY DEVICE COMPRISING A GENERATOR OF VERY STRAIGHT FRONT RECTANGULAR SLOTS |
US4878493A (en) * | 1983-10-28 | 1989-11-07 | Ninetronix Venture I | Hand-held diathermy apparatus |
US4658818A (en) * | 1985-04-12 | 1987-04-21 | Miller Jr George E | Apparatus for tagging and detecting surgical implements |
US4827906A (en) * | 1987-08-31 | 1989-05-09 | Heineman Medical Research Center | Apparatus and method for activating a pump in response to optical signals from a pacemaker |
US5025811A (en) * | 1990-02-16 | 1991-06-25 | Dobrogowski Michael J | Method for focal destruction of eye tissue by electroablation |
DE4009819C2 (en) * | 1990-03-27 | 1994-10-06 | Siemens Ag | HF surgery device |
US5169398A (en) * | 1990-09-21 | 1992-12-08 | Glaros Nicholas G | Electronic hair remover |
DE4032471C2 (en) * | 1990-10-12 | 1997-02-06 | Delma Elektro Med App | Electrosurgical device |
US5368041A (en) * | 1992-10-15 | 1994-11-29 | Aspect Medical Systems, Inc. | Monitor and method for acquiring and processing electrical signals relating to bodily functions |
US5422567A (en) * | 1993-12-27 | 1995-06-06 | Valleylab Inc. | High frequency power measurement |
US5608306A (en) * | 1994-03-15 | 1997-03-04 | Ericsson Inc. | Rechargeable battery pack with identification circuit, real time clock and authentication capability |
-
1996
- 1996-02-22 US US08/604,850 patent/US5792138A/en not_active Expired - Lifetime
-
1997
- 1997-02-18 WO PCT/IB1997/000346 patent/WO1997030643A1/en not_active Application Discontinuation
- 1997-02-18 EP EP97908446A patent/EP0955923A1/en not_active Withdrawn
- 1997-02-18 AU AU20403/97A patent/AU730413B2/en not_active Ceased
- 1997-02-18 JP JP9529944A patent/JP2000504616A/en not_active Ceased
- 1997-02-18 CA CA002243995A patent/CA2243995A1/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
JP2000504616A (en) | 2000-04-18 |
EP0955923A4 (en) | 1999-12-01 |
US5792138A (en) | 1998-08-11 |
WO1997030643A1 (en) | 1997-08-28 |
AU730413B2 (en) | 2001-03-08 |
AU2040397A (en) | 1997-09-10 |
EP0955923A1 (en) | 1999-11-17 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
AU730413B2 (en) | Cordless bipolar electrocautery unit with automatic power control | |
US11864814B2 (en) | System and method for harmonic control of dual-output generators | |
US7094231B1 (en) | Dual-mode electrosurgical instrument | |
US9522032B2 (en) | Circuit and method for reducing stored energy in an electrosurgical generator | |
US9326810B2 (en) | Multi-button electrosurgical apparatus | |
JP6486009B2 (en) | Constant power inverter with crest factor control | |
EP1489982B1 (en) | Power supply for identification and control of electrical surgical tools | |
EP3281711A1 (en) | Ultrasonic and radiofrequency energy production and control from a single power converter | |
EP1681026B1 (en) | Electrosurgical generator using a full bridge topology | |
US11369429B2 (en) | Advanced simultaneous activation algorithm | |
AU2014203435B2 (en) | Electrosurgical generators | |
CN106308923A (en) | Electrosurgical generator for minimizing neuromuscular stimulation | |
CA2721024A1 (en) | Class resonant-h electrosurgical generators | |
US10869712B2 (en) | System and method for high frequency leakage reduction through selective harmonic elimination in electrosurgical generators | |
US20200100831A1 (en) | Ancillary circuit to induce zero voltage switching in a power converter | |
EP3257461B1 (en) | Variable active snubber circuit to induce zero-voltage-switching in a current-fed power converter | |
EP3243472A1 (en) | Electrosurgical generator with half-cycle power regulation | |
US10537378B2 (en) | Variable active clipper circuit to control crest factor in an AC power converter |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
FZDE | Discontinued |