EP1615572A2 - Systeme electrochirurgical - Google Patents

Systeme electrochirurgical

Info

Publication number
EP1615572A2
EP1615572A2 EP04717148A EP04717148A EP1615572A2 EP 1615572 A2 EP1615572 A2 EP 1615572A2 EP 04717148 A EP04717148 A EP 04717148A EP 04717148 A EP04717148 A EP 04717148A EP 1615572 A2 EP1615572 A2 EP 1615572A2
Authority
EP
European Patent Office
Prior art keywords
electrodes
power
output
electrode
source
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.)
Withdrawn
Application number
EP04717148A
Other languages
German (de)
English (en)
Inventor
Colin Charles Owen Goble
Scott T. Latterell
Douglas S. Wahnschaffe
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Gyrus Medical Ltd
Original Assignee
Gyrus Medical Ltd
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Priority claimed from GB0305022A external-priority patent/GB0305022D0/en
Priority claimed from US10/378,657 external-priority patent/US6929641B2/en
Application filed by Gyrus Medical Ltd filed Critical Gyrus Medical Ltd
Priority claimed from PCT/GB2004/000921 external-priority patent/WO2004078051A2/fr
Publication of EP1615572A2 publication Critical patent/EP1615572A2/fr
Withdrawn legal-status Critical Current

Links

Definitions

  • This invention relates to an electrosurgical system comprising an electrosurgical generator and a handpiece including electrosurgical electrodes.
  • electrosurgical generator and a handpiece including electrosurgical electrodes.
  • Such systems are commonly used for the cutting and/or coagulation of tissue in surgical intervention, most commonly in “keyhole” or minimally invasive surgery, but also in laparoscopic or “open” surgery.
  • electrosurgical generators which provide different radio frequency (RF) power signals for cutting and coagulation, and also to switch between two different instruments, e.g. bipolar and monopolar instruments.
  • RF radio frequency
  • electrosurgical instrument with a single electrode, and switching means on the instrument to connect the electrode alternately to either a cutting output or to a coagulating output from the generator. Examples of these types of instrument are to be seen in US 4,427,006, US 5,376,089 and US 5,573,424.
  • the invention provides an electrosurgical system including a generator for generating radio frequency power, and an electrosurgical instrument including at least three electrodes, the generator comprising at least one source of radio frequency (RF) power, and the instrument including a selection arrangement operable to vary the coupling between the at least one RF source and the at least three electrodes, the system further including a switching device operable to cause the selection arrangement to vary the electrode or electrodes to which RF power is supplied, the arrangement of the system being such that the RF power signal applied to at least one of the electrodes varies depending on the electrode or electrodes to which radio frequency power is supplied, and also such that one of the electrodes has no direct connection to the output stage of the generator and is connected via a capacitor to another of the electrodes.
  • RF radio frequency
  • the RF power source includes an RF output stage having at least a pair of RF output lines;
  • the generator includes a controller capable of varying the RF power signal supplied to the output lines;
  • the selection arrangement comprises a switching circuit having at least three output connections each in electrical connection with a respective one of the at least three electrodes, and is operable to vary the connections between the RF output lines and the output connections; and the switching device is operable to cause the RF power signal applied to at least one of the three or more output connections to vary depending on the electrode or electrodes to which radio frequency power is supplied.
  • the capacitor preferably has a value of between 1 and 10 nF. This arrangement can simplify the switching required, and/or free up additional switching capability for use in other circumstances.
  • the switching circuit is preferably located within the generator, although it is conceivable that the switching circuit alternatively be located within the handpiece of the electrosurgical instrument
  • the electrosurgical power signal employed can be optimised depending on the choice of electrodes, and similarly the electrodes can be designed specifically for the function they are chosen to perform.
  • the controller automatically adjusts the RF power supplied to at least one of the three or more output connections to limit the peak generator output voltage to at least a first value when a first combination of electrodes is selected by the switching circuit, and to at least a second value when a second combination of electrodes is selected by the switching circuit.
  • the generator supplies RF power to at least three electrodes simultaneously, the output voltage being limited to a first peak value between a first combination of electrodes, and to a second peak value between a second combination of electrodes.
  • the generator having first and second output stages adapted to produce RF power for the first and second combination of electrodes respectively.
  • at least three of the electrodes are connected to respective other electrodes by capacitors, such that the peak voltage delivered by a single output stage is different between the first and second combination of electrodes.
  • two of the three or more electrodes are in the form of jaws adapted to grasp tissue therebetween, and the third electrode is mounted on one of the jaws, separated therefrom by an insulating member.
  • the third electrode may be mounted on the internal or external face of one of the jaws, or even at the tip thereof.
  • the third electrode may be mounted on one of the jaws in a recess therein, such that only a part of the electrode protrudes from the jaw. This type of arrangement applies to forceps or scissors-type instruments, suitable for grasping and/or cutting tissue.
  • At least one and preferably at least three of the electrodes is in the form of a hook.
  • Hook and needle-type instruments are also common in Laparoscopic surgery, and may be employed in the present invention.
  • one of the hook electrodes extends distally beyond the other electrodes.
  • the electrode which extends distally beyond the other electrodes is positioned centrally between the other electrodes.
  • At least one of the electrodes is longitudinally movable such that it can be extended and retracted with respect to the other electrodes. In this way tissue can be held in the gap formed between the retractable electrode and the other electrodes.
  • the longitudinally movable electrode is preferably positioned centrally between the other electrodes.
  • the invention further resides in an electrosurgical system including a generator for generating radio frequency (RF) power, and an electrosurgical instrument including at least three electrodes, two of the at least three electrodes being in the form of jaws adapted to grasp tissue therebetween, and the third electrode being mounted on one of the jaws, separated therefrom by an insulating member, wherein the generator comprises at least one source of RF power, and the instrument also includes a selection circuit operable to vary the coupling between the at least one RF source and the at least three electrodes, the system further including a switching device operable to cause the selection circuit to vary the electrode or electrodes to which RF power is supplied, the arrangement being such that the RF signal applied to at least one of the electrodes varies depending on the electrode or electrodes to which RF power is supplied.
  • RF radio frequency
  • the invention further resides in an electrosurgical system including a generator for generating RF power, and an electrosurgical instrument including at least three electrodes, wherein the generator comprises:
  • the electrosurgical instrument includes a selection circuit having at least three output connections each in electrical connection with a respective one of the at least three electrodes, and operable to vary the connections between the RF output lines and the said output connections, the system further including a switching device operable to send a signal to the selection circuit in order to vary the electrode or electrodes to which RF power is supplied, the switching device also causing the RF power signal supplied to at least one of at least three output connections to vary depending on the electrode or electrodes to which RF power is supplied.
  • the invention resides in an electrosurgical system including a generator for generating radio frequency (RF) power, and an electrosurgical instrument including at least three electrodes, wherein the generator comprises an RF source having at least a pair of RF output lines, the RF source being operable to deliver RF power to said output lines at at least different first and second radio frequencies, wherein the system further includes a coupling stage for coupling RF power on said RF output lines to the electrodes, the coupling stage comprising: a first output circuit connected to a first pair of said electrodes and tuned to said first frequency, and a second output circuit connected to a second pair of said electrodes and tuned to said second frequency, and wherein the system includes means for varying the output frequency of said RF source to deliver RF power to the first and second output circuits at said first frequency or at said second frequency.
  • RF radio frequency
  • Figure 1 is a schematic diagram of an electrosurgical system
  • FIG. 2 is a block diagram of a generator forming part of the system of Figure 1,
  • Figure 3 is a schematic side view, shown partly in section, of a forceps-type instrument for use in the system of Figure 1,
  • Figure 3 A is a sectional side view showing an alternative jaw for the instrument of Figure 3
  • Figure 4 is a cross-section of a shaft of the instrument of Figure 3 ,
  • FIGS 5 A and 5B are schematic views of the switching circuitry of Figure 2, shown in first and second alternative conditions,
  • Figures 6 and 7 are side and plan views, respectively, of a part of an alternative instrument for use in the system of Figure 1
  • Figure 7A is a plan view of a variation on the instrument of Figures 6 and 7,
  • Figure 8 is a side view of a part of a further alternative instrument for use in the system of Figure 1, the instrument being shown in a retracted position,
  • Figure 9 is an end view of the instrument of Figure 8.
  • Figure 10 is a side view of the instrument of Figure 8, shown in an extended position
  • FIGS 11 A and 1 IB are schematic circuit diagrams showing an alternative switching arrangement
  • Figure 12 is a schematic diagram of an electrosurgical system in accordance with the present invention
  • Figure 13 is a schematic diagram of a furtl er electrosurgical system in accordance with the invention
  • Figures 14A and 14B are circuit diagrams of alternative RF output stages of yet further embodiments of the invention.
  • a generator 10 has an output socket 10S providing a radio frequency (RF) output for an instrument 12 via a connection cord 14. Activation of the generator may be performed from the instrument 12 via a connection in cord 14 or by means of a footswitch unit 16, as shown, connected to the rear of the generator by a footswitch connection cord 18.
  • footswitch unit 16 has two footswitches 16A and 16B for selecting a coagulation mode and a cutting mode of the generator respectively.
  • the generator front panel has push buttons 20 and 22 for respectively setting coagulation and cutting power levels, which are indicated in a display 24. Push buttons 26 are provided as an alternative means for selection between coagulation and cutting modes.
  • the generator comprises a radio frequency (RF) output stage in the form of a power oscillator 60 having a pair of output lines 60C for coupling via switching circuit 62 to the instrument 12.
  • Switching circuit 62 has three output connections 62A, 62B and 62C for connection to the electrodes of the instrument as will be described later.
  • a capacitor 69 is connected between output connections 62A and 62B as shown.
  • Power is supplied to the oscillator 60 by a switched mode power supply 66.
  • the RF oscillator 60 operates at about 400 kHz, with any frequency from 300 kHz upwards into the HF range being feasible.
  • the switched mode power supply typically operates at a frequency in the range of from 25 to 50 kHz.
  • a voltage threshold detector 68 having a first output 68 A coupled to the switched mode power supply 16 and a second output 68B coupled to an "on" time control circuit 70.
  • a micro-processor controller 72 coupled to the operator controls and display (shown in Figure 1) is connected to a control input 66A of the power supply 66 for adjusting the generator output power by supply voltage variation and to a threshold-set input 68C of the voltage threshold detector 68 for setting peak RF output voltage limits.
  • the microprocessor controller 72 causes power to be applied to the switched mode power supply 66 when electrosurgical power is demanded by the surgeon operating an activation switch arrangement which may be provided on a hand- piece or footswitch (see Figure 1).
  • a constant output voltage threshold is set independently of the supply voltage via input 68C according to control settings on the front panel of the generator (see Figure 1).
  • the threshold is set at a desiccation threshold value between 150 volts and 200 volts.
  • the threshold is set to a value in the range of from 250 or 300 volts to 600 volts.
  • These voltage values are peak values. Their being peak values means that for desiccation at least it is preferable to have an output RF waveform of low crest factor to give maximum power before the voltage is clamped at the values given. Typically a crest factor of 1.5 or less is achieved.
  • the status of the control input 601 of the RF oscillator 60 (which is connected to the "on" time control circuit 70) is "on", such that the power switching device which forms the oscillating element of the oscillator 60 is switched on for a maximum conduction period during each RF oscillation cycle.
  • the power delivered to the load 64 depends partly on the supply voltage applied to the RF oscillator 60 from the switched mode power supply 66 and partly on the load impedance 64.
  • the voltage threshold for a desiccation output is set to cause trigger signals to be sent to the "on" time control circuit 70 and to the switched mode power supply 66 when the voltage threshold is reached.
  • the "on" time control circuit 70 has the effect of virtually instantaneously reducing the "on” time of the RF oscillator-switching device. Simultaneously, the switched mode power supply is disabled so that the voltage supplied to oscillator 60 begins to fall.
  • the operation of the generator in this way is described in detail in our European Patent Application No. 0754437, the disclosure of which is hereby incorporated by way of reference.
  • FIG. 3 shows one type of instrument 12 which can be connected to the generator 10.
  • the device is a bipolar forceps shown generally at 110.
  • the forceps has an elongated tubular member or shaft 112 with a proximal end 114, distal end 116, and a lumen 118 which extends for the entire length of the shaft.
  • a scissors-type handle assembly 124 At the proximal end 114 of the shaft 112 is a scissors-type handle assembly 124 with a first handle 126 and a second handle 134.
  • the second handle 134 is pivotable with respect to the first, about pivot pin 152.
  • the second handle 134 has a pin 123 affixed to the top thereof, such that movement of the handle causes a corresponding movement of a sphere 129 supported in a U-shaped cradle 127.
  • a forceps jaw assembly 158 comprising a first jaw member 160 and a second jaw member 162, pivotally joined to each other by an insulated rivet 164.
  • Jaw member 162 is provided with a cutting electrode 220, isolated from jaw member 162 by a ceramic insulator 221.
  • three rigid electrically conductive rods 166, 184 and 222, each covered with a layer of electrical insulation, extend through the lumen 118 of the shaft 112.
  • the rods 166, 184 are pivotally connected to the respective jaw members 160, 162 by rigid links 168, whilst rod 222 is connected by means of a wire (not shown) to the electrode 220.
  • the proximal ends of the rods 166, 184 and 222 extend from the tubular member through the sphere 129 and terminate in a connector 320.
  • Output connections 62 A, 62B and 62C from the generator 10 are thereby electrically connected to the rods 166, 184 and 222 respectively, via lead 14 and connector 320.
  • the controller 72 sets the switching circuit to the position in Figure 5A, it also sends a signal via line 68C to the voltage threshold detector 68 to set the peak output voltage limit to a relatively high "cutting" level.
  • the control of this cutting signal is described in more detail in EP 0754437, referred to earlier.
  • the output from the generator is a relatively high voltage, with a consequent low current level, and the impedance offered by the capacitor 69 is small in comparison with the impedance provided between the cutting electrode and the tissue being treated.
  • footswitch 16B is depressed which causes the controller 72 to set the switching circuit 62 to its "coag" state, as illustrated in Figure 5B.
  • the power signals from the oscillator are connected between output connections 62A and 62B.
  • the controller sends a signal to the voltage threshold detector 68 to set the peak output voltage limit to a relatively lower "coagulating" level, again as more particularly described in EP 0754437.
  • the output from the generator is a relatively lower voltage, with a corresponding relatively higher current, and the impedance offered by the capacitor 69 is sufficient to maintain a potential difference between the output connections 62A and 62B.
  • the capacitor 69 therefore allows sufficient voltage differential between the coagulating electrodes (160 and 162) to permit the coagulation of tissue to be performed. It will be noted that in Figures 5 A and 5B, only one switching element is required, with the connection between the generator and output connection 62A being maintained for both cutting and coagulation. The use of the capacitor 69 therefore simplifies the switching required, and/or frees up additional switching capability within the generator for use in other circumstances. It will also be appreciated that, although the capacitor 69 is shown in Figures 5 A and 5B as being a part of the generator 10, it may alternatively be provided as a part of the instrument 12. In this way, different values of capacitor can be provided for different instruments, depending on their size and configuration.
  • the cutting electrode 220 may be located at the tip of the jaw member 162, or even on the inside jaw face as opposed to the outside jaw face illustrated in Figure 3.
  • the cutting electrode 220 and the ceramic insulator 221 may be mounted on the jaw member 162 in a recess 223 provided thereon. This is the arrangement illustrated in Figure 3 a. The operation of the instrument will be the same, and the location of the cutting electrode may merely depend on the type of procedure undertaken.
  • FIGS 6 and 7 show an alternative embodiment in which the jaw members of the device of Figure 3 are replaced by hook electrodes. These types of instrument are particularly suited to procedures such as Prostatectomy and Nephrectomy.
  • First and second outside hook electrodes 31 and 32 are connected to output connections 62A and 62B respectively, whilst a central cutting hook electrode 33 is connected to output connection 62C.
  • the cutting hook electrode protrudes slightly further forward than the outside electrodes 31 and 32, as shown in Figure 6.
  • the switching circuit 62 is set to the state shown in Figure 5A, and the cutting hook electrode 33 is energised with a cutting RF power signal, with one or both of the outside hook electrodes acting as the return electrode.
  • the switching circuit is set to the state shown in Figure 5B such that a coagulating RF power signal is supplied to both of the outside hook electrodes 31 and 32.
  • either the central cutting electrode or the outside electrodes can be made extendible and retractable, or the outside electrodes can be made jaw-like in order to spread or grasp tissue to be cut or coagulated.
  • Figure 7a shows a variation on the device of Figures 6 and 7 in which the central hook electrode 33 is movable longitudinally with respect to the outside electrodes 31 and 32. In Figure 7a the central electrode is shown retracted behind the outside electrodes, such as would be the case when coagulating using the outside electrodes or cutting by pulling the tissue towards the central cutting electrode 33.
  • a central extendible hook electrode 40 is provided between stationary outside electrodes 41 and 42.
  • the central electrode In its retracted position, shown in Figure 8, the central electrode protrudes only slightly beyond the outside electrodes 41 and 42.
  • the instrument may be used as a tissue cutter, with the central electrode being supplied with a cutting RF power signal from the generator 10, and one or both of the outside electrodes acting as return electrodes.
  • the central electrode may also be extended, as shown in Figure 10, and then retracted to hold tissue in the gap 43 created between the central hook electrode 40 and the outside electrodes 41 and 42.
  • the tissue held in the gap 43 can be coagulated or desiccated.
  • a cutting RF power signal is supplied to the central hook electrode 40 (the switching circuit connecting the oscillator 60 to the output connections 62A and 62C), and the electrode 40 is retracted in order to cut through the tissue in the gap 4.
  • this additional capacitor 73 is less than that for capacitor 69, typically 1.1 nF.
  • the effect of this additional capacitor is as follows.
  • the output stage of the generator is primarily connected between output connections 62A (and hence one of the coagulation electrodes) and 62C (and hence the cutting electrode).
  • the relatively high potential difference between the cutting electrode and one or both of the coagulating electrodes will be such that the cutting of tissue can occur.
  • the linking of the three electrodes by the capacitors 69 and 73 will have the effect that a relatively low potential difference will also be generated between output connections 62A and 62B (and hence the two coagulation electrodes).
  • FIG. 1 IB the switching circuit is arranged such that the output stage of the generator is primarily connected between output connections 62 A and 62B (and hence the two coagulation electrodes). This is the arrangement for the "coagulation only" setting of the device. The effect of the additional capacitor 73 will be that coagulation will occur between all three electrodes, with the cutting electrode becoming an additional coagulation electrode in the setting of Figure 11B.
  • Figure 12 shows a generator circuit for a system in accordance with the invention, the circuit being similar to that of Figure 2, with like components being designated with like reference numerals.
  • the major difference from the generator of Figure 2 is that the switching circuit 62 is not present within the generator 10, but is located within the electrosurgical instrument 12. Thus the generator 10 has only two output connections 60C to which the instrument 12 is connected.
  • the instrument 12 includes the switching circuit 62, which has output connections 62A, 62B and 62C as before, an instrument shaft 44, and electrodes 40, 41 and 42.
  • two RF power oscillators 60-1 and 60-2 are powered from a common power supply 62 and are controlled by a common controller 72 to produce on respective output lines 60C an RF power signal suitable for cutting and an RF power signal suitable for coagulation.
  • These signals may be fed to a switching circuit 63 for selecting the power signal from one oscillator 60-1 or the other oscillator 60-2 according to inputs from, for instance, foot switches, the selected power signal being transmitted on output connections 80, 81.
  • the switch is operated repeatedly at a predetermined rate to produce a blended output power signal across connections 80, 81.
  • the power oscillators 60-1, 60-2 are operated at different frequencies, and the respective cut and coagulation signals are fed to the required electrodes by feeding the power signal on output connections 80, 81 to tuned circuits 82-1 and 82-2 tuned to the different frequencies.
  • the outputs of the tuned circuits are coupled via electrode lines 48, 49 and 50 to the respective electrodes of the electrosurgical instrument. In this way, the cutting signal from oscillator 60-1 is fed to a cutting electrode 48 and a common electrode 49, whereas the coagulation signal from oscillator 60-2 is fed to a coagulation electrode 50 and the common electrode 49.
  • connection between the electrosurgical generator and the electrosurgical instrument is typically provided by output connections 80 and 81, but the apportionment of circuit blocks between the generator and the instrument may be varied.
  • FIGS 14A and 14B Further embodiments are shown in Figures 14A and 14B. These embodiments dispense with the need for a signal routing switch or switching circuit.
  • FIG 1 A there are provided two tuned circuits 82-1 and 82-
  • each tuned circuit has a series-resonant inductor- capacitor pair 84 and a parallel-resonant inductor-capacitor pair 86, the latter being transformer-coupled to electrode output connections 46 and 47 on the one hand and 46 5 and 47' on the other hand.
  • each tuned circuit has two inputs, one of which is connected to a generator output connection 80 and the other of which is connected to a generator output connection 81.
  • the generator has an output stage comprising RF switches arranged in two oppositely acting push-pull pairs 90A, 90B and 91 A, 9 IB. Typically these switches comprise power MOSFETS.
  • Each switch 90A, 90B, 91 A, 91B is connected to driver inputs 92, 93, as shown, which receive an RF drive signal which, for producing on the output connections 80, 81 an output having a cut waveform, is at one RF frequency, and, for producing a coagulation output on the output connections 80, 81, has a different RF frequency, these frequencies being, respectively, the resonant frequency of the resonant combinations 84, 86 of the first tuned circuit 82-1 and the resonant frequency of the corresponding resonant combinations of the other tuned circuit 82-2.
  • the RF switches 90 A, 90B, 91 A and 9 IB of the generator output stage may be driven according to, for instance, a footswitch control to produce a cut output or a coagulation output.
  • a blended output may be produced in which the RF frequency alternates constantly between the two resonant frequencies of the tuned output circuits.
  • FIG. 14B is a modification of that of Figure 14 A, in which the generator output stage has a single push-pull pair of RF switches 90A, 90B and in which the tuned circuits each have one input connected to the junction between the switches 90A, 90B and the other input connected to ground. More generally, it will be appreciated that other embodiments of generator and electrode, can be envisioned without departing from the scope of the present invention. By employing three or more electrodes and selecting their coupling to the source of the RF power, and also adjusting the RF power signal depending on which electrodes are being employed at any one time, the electrosurgical signal and the electrode configuration can be matched to optimum effect.

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  • Surgical Instruments (AREA)

Abstract

La présente invention se rapporte à un système électochirurgical, qui comprend un générateur destiné à générer une puissance radiofréquence (RF), et un instrument électrochirurgical possédant au moins trois électrodes. Le générateur comprend un étage de sortie RF possédant au moins une paire de lignes de sortie RF, un bloc d'alimentation couplé à l'étage de sortie pour fournir de la puissance à l'étage de sortie, et un contrôleur pouvant faire varier le signal de puissance RF fourni aux lignes de sortie. Le système selon l'invention comprend également un circuit de sélection possédant au moins trois connexions de sortie, chacune de ces dernières étant reliée par voie électrique respectivement à l'une desdites trois électrodes. Ledit circuit de sélection fait varier le couplage existant entre l'étage de sortie RF et lesdites trois connexions de sortie. A l'aide d'un dispositif de commutation, que l'utilisateur peut faire fonctionner, le circuit de sélection fait varier la ou les électrodes auxquelles de la puissance RF est fournie, et le signal de puissance RF fourni à au moins l'une desdites trois connexions varie en fonction de la ou les électrodes auxquelles la puissance RF est fournie. Dans un agencement du circuit de sélection, l'une des électrodes n'est pas reliée directement à l'étage de sortie du générateur, mais est reliée à une autre des électrodes par l'intermédiaire d'un condensateur.
EP04717148A 2003-03-05 2004-03-04 Systeme electrochirurgical Withdrawn EP1615572A2 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
GB0305022A GB0305022D0 (en) 2003-03-05 2003-03-05 Electrosurgical system
US10/378,657 US6929641B2 (en) 2001-08-27 2003-03-05 Electrosurgical system
PCT/GB2004/000921 WO2004078051A2 (fr) 2001-08-27 2004-03-04 Systeme electrochirurgical

Publications (1)

Publication Number Publication Date
EP1615572A2 true EP1615572A2 (fr) 2006-01-18

Family

ID=35466301

Family Applications (1)

Application Number Title Priority Date Filing Date
EP04717148A Withdrawn EP1615572A2 (fr) 2003-03-05 2004-03-04 Systeme electrochirurgical

Country Status (1)

Country Link
EP (1) EP1615572A2 (fr)

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2004078051A3 *

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