WO1997009938A2 - Hochfrequenz-chirurgiegerät und funktionsüberwachungsvorrichtung für ein hochfrequenz-chirurgiegerät - Google Patents
Hochfrequenz-chirurgiegerät und funktionsüberwachungsvorrichtung für ein hochfrequenz-chirurgiegerät Download PDFInfo
- Publication number
- WO1997009938A2 WO1997009938A2 PCT/DE1996/001738 DE9601738W WO9709938A2 WO 1997009938 A2 WO1997009938 A2 WO 1997009938A2 DE 9601738 W DE9601738 W DE 9601738W WO 9709938 A2 WO9709938 A2 WO 9709938A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- voltage
- relay
- relays
- frequency
- monitoring device
- Prior art date
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
- A61B18/1206—Generators 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
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/1206—Generators therefor
- A61B18/1233—Generators therefor with circuits for assuring patient safety
Definitions
- the invention relates to a high frequency (HF) surgical device according to the preamble of claim 1 and a function monitoring device of high voltage relays which are used in generic HF surgical devices and a method for monitoring the function of high voltage relays for surgical devices.
- HF high frequency
- HF surgery devices of this type are generally known. Reference is made only to the German laid-open documents 31 51 991, 39 11 416 or 39 42 998 by way of example only. Reference is expressly made to these publications for the explanation of all details, not described here in detail, or the other technical training of HF surgical devices.
- the known HF surgical devices - like other electromedical devices - have the following problem:
- electromedical devices require electrical isolation between the mains-side power supply and the patient user part.
- This galvanic separation takes place in the known generic HF surgical devices by means of an isolating transformer can either be a mains transformer directly connected to the mains AC voltage on the primary side or can be part of a primary switched switching power supply.
- Powerful high-frequency surgical devices now have an output power of 400 W, possibly even more. This means that - depending on the efficiency - about 600 W or more power must be provided on the input side.
- a mains transformer designed as an isolating transformer thus becomes very voluminous and correspondingly heavy.
- the transformer required becomes smaller, since frequencies between 50 and 100 kHz are generally used, but the cost of the transformer in comparison to the total costs is not a negligible variable. Furthermore, the volume of the device increases.
- a relay matrix with NO contacts is used as the work contact, so that the outputs are not connected to the generator electronics when the device is switched off or the outputs are switched off. It can be due to for example, material defects, connections between a switched-off output and the generator electronics have been switched, although this connection has been switched off by the user. This effect is caused, for example, by the contact of the relay sticking or sticking. The errors that the relay coil has an open or short circuit so that the contact can no longer close are less problematic.
- Relays have the property that they require a relatively large amount of power in order to attract the contact. This power must be made available by the internal supply, and as a rule, by an "auxiliary supply" for the electronic control part of the high-frequency surgical device, which is thereby comparatively heavily loaded. It is therefore desirable to reduce the power consumption of the relays.
- the invention is based on the object of specifying a high-frequency surgical device which meets the relevant standards for electromedical devices such as IEC 601 or VDE 0750 without the use of a mains isolating transformer for electrical isolation between the network and the user part. It is also an object of the present invention to make high-frequency surgical devices safer and to reduce the power consumption which must be applied by auxiliary supply devices.
- This high-frequency output transformer is not used in the known HF surgical devices for the galvanic separation between the network and the user part.
- the HF output transformer for the galvanic isolation between the (mains) supply voltage and the patient user part.
- the HF output transformer is designed in accordance with the required standards, in particular with regard to insulation voltage and air and creepage distances.
- a high-frequency transformer that meets FFIEC 601 or VDE 0750 can be used.
- the high-frequency output transformer is operated at very high frequencies, namely typically 0.3 to 1 MHz, the high-frequency output transformer can be designed to be small, light and therefore comparatively inexpensive in comparison with conventional mains isolating transformers or conventional isolating transformers in switched-mode power supplies .
- the design according to the invention therefore not only reduces the costs, but also the weight of the device and the overall size of the device.
- the controls of the control electronics that can be touched by the user are galvanically isolated from the power section.
- This electrical isolation can take place, for example, through the housing construction and the switches or keys used, or else through transmitters or optocouplers (claim 3).
- This measure enables a simple universal switching power supply to be used as the internal power supply.
- the measurement signals as well as the HF power can be separated from the mains by a larger insulation.
- This embodiment has the advantage that virtually no control signals have to be separated between the power section and the control electronics. However, more attention must be paid to the installation of the control modules in the housing, since a comparatively large creepage and clearance distance to the grounded housing is necessary.
- control electronics have a separate power supply unit (claim 4).
- the "power supply” has a universal rectifier and a controllable DC / DC converter.
- the DC / DC converter makes it possible to cover the entire mains voltage range of 100-240 V AC without switching.
- the DC / DC converter preferably has the property of drawing an almost sinusoidal current from the network. As a result, the voltage is less distorted and the RMS current load and thus the losses in the power lines are reduced in comparison to conventional rectifiers.
- the invention is also based on the finding that sticking a relay contact is the most dangerous type of control failure for the patient or the user. This type of failure can lead to the fact that the energy is emitted simultaneously to two outputs, for example.
- the switching status of the relay is safe for the person concerned when the relay is open.
- the function monitoring device checks whether the contacts of the relays are opened.
- the function monitoring device for high-voltage relays for surgical devices requires the following elements: a control logic for at least one relay, a controllable voltage source, an inductance measuring circuit, and a driver unit which has at least one relay driver.
- the relay coil excites a magnetic circuit, the properties of which change when the armature closes. For example, this changes the inductance.
- the connection inductance increases.
- reed relays are used as relays that can hold a sufficiently high voltage across the open contact and are of a small design. According to the invention, it has been recognized that one property of the reed relay, namely that the armature does not move a contact via a mechanical coupling, as is the case with conventional relays, but that the armature has the contact in itself forms, can advantageously be used.
- the connection inductance in reed contacts thus already changes in that the contact opens or closes.
- the relay driver is therefore preferably matched to reed relays (claim 7).
- the functional monitoring of the high-voltage relay advantageously takes place via the respective control circuit of the relay to be monitored. There are therefore no connections to the high-frequency outputs required (claim 9). This has a significant advantage for the implementation of the circuit, since, for example, no high-voltage components and also no high-frequency components have to be used.
- An alternating current is preferably superimposed on an output of the relay driver (claim 10). Due to this measure, it is easily possible to measure an inductance change in the relay.
- the method for monitoring the function of high-voltage relays for surgical devices is preferably carried out with the following method steps: applying the smallest possible DC voltage, in which all relays connected to high-frequency outputs attract, Superimposing the direct voltage with an alternating voltage (ACl),
- the measured AC component can preferably be stored.
- Fig. 1 is a block diagram of a high-frequency surgical device according to the invention.
- Fig. 2 is a block diagram of a function monitoring device according to the invention. Presentation of exemplary embodiments
- the power section (blocks in the upper row) is denoted by 1 and the control electronics (blocks in the lower row) by 2 (FIG. 1).
- the power section 1 has a universal rectifier 3, to which the AC mains voltage, which can be between 100 and 240 V depending on the national standard, is present.
- the output connection of the universal rectifier 3 is connected to a controllable DC / DC converter 4, which supplies an RF power amplifier 5 with power.
- the output connection of the power amplifier 5 is connected to a high-frequency output transformer 6, which represents the only galvanic isolation between the mains supply voltage and the patient user part (arrow 7).
- the control electronics 2 is constructed in the usual way.
- a unit 8 is provided, by means of which a measurement signal is coupled out of the RF output of the RF output transformer 6.
- the output signal of the unit 8 is applied to control electronics 9, which control both the controllable DC / DC converter 4 and the HF power amplifier 5.
- a galvanic isolation which typically fulfills 4 kV / 8 mm creepage distance, can be provided.
- the galvanic isolation can be implemented by means of suitable switches or in particular membrane switches or, for example, by means of optocouplers or transmitters.
- a second universal power supply unit 10 can also be provided, which for low power, such as 15 W is designed.
- the change in the inductance of the relay coil is measured.
- a small AC voltage is superimposed on the DC voltage that is required to set up the magnetic circuit and close the contact.
- the current which is caused by the AC voltage is used as a variable for determining the inductance, the absolute values not being of interest here. Only the change in inductance is considered. This makes it possible, for example, to use relays from different manufacturers.
- the circuit is freed from expensive components and from complex adjustments. To be It is important to ensure that this principle only works with reed relays.
- the change in inductance is determined in two phases. In this example, this process takes approx. 18 ms.
- 1st phase The smallest possible direct voltage is applied to the relay, at which all relays pick up, in this example 12V. A square wave voltage of 0.5V with 650Hz is superimposed on this voltage. For current measurement, the voltage drop is measured via a 1 ohm measuring resistor. The voltage resulting across the resistor is decoupled with a capacitor in order to evaluate only the AC voltage component. This AC signal is now amplified and rectified with a peak value rectifier; this voltage is stored with a holding amplifier (sample and hold).
- 2nd phase The greatest DC voltage is now applied to the relay, at which all relays drop out. In this example 2 V. The same AC voltage is superimposed as in the first phase. A new voltage is now set at the peak value rectifier, since the inductance of the open contact is smaller. This voltage is compared with the stored voltage using a comparator. If the new voltage increases by a predetermined minimum value, the contact has opened correctly. If the voltage changes too little, it must be assumed that the contact is stuck or another component is defective.
- the inductance measuring circuit 17 contains a high-pass filter, an amplifier, a peak value rectifier or a peak detector, a holding amplifier and a comparator.
- the alternating current is measured via a shunt resistor through which a current flows, which originates from the selected relay in the relay driver 16.
- the measurement accuracy is improved by restricting the DC voltage range to the minimum pull-in voltage and maximum drop voltage of the relay; these two relay parameters are monitored simultaneously.
- the circuit according to the invention can be used so that each relay is tested when it is switched off.
- the contact after the test is thus open and represents the safest state. This ensures that RF energy is never present at an output that has not been switched on.
- the circuit can of course also be used to test the relays when switched on.
- the circuit is constructed so that only one control and evaluation electronics 13 is required for any number of relays 15. The activation of the relays is carried out by an external controller 11.
- control and evaluation circuit has four circuit parts: - microcontroller
- the external controller 11 has an input connection and two output connections, so that three data lines are available for communication with it.
- the external controller tells the control circuit via one connection whether a relay is activated or whether a relay has to be tested.
- the other two connections serve for synchronization and the return of the test result.
- the data or control line 12 tells the relay driver 16 which relays are to be switched on.
- the circuit can control any number of relays, but in this example only test one at a time. In this example, it is the responsibility of the external controller to correctly interpret the data from the evaluation circuit and to select the desired relays.
- control circuit is constructed in such a way that every first error in the control circuit is recognized by a self-test and transmitted to the controller.
- the external controller controls the relay driver and the control circuit is informed that one or more relays are to be switched on.
- the supply voltage of the relays is increased by the adjustable voltage source 14 for 5 ms, so that the relays can pick up safely.
- the supply voltage reduced so that only a little more than the holding current flows in each relay coil.
- the supply voltage is reduced, for example, by clocking the DC voltage.
- the power is reduced by the pulse / pause ratio.
- a fault or defect in the control circuit could prevent a relay defect from being recognized. It is therefore necessary to carry out a self-test of the circuit.
- This self-test does not require any additional components and it is carried out autonomously by the control circuit. It is not activated from the outside and is also not detected. If an error is detected, the outputs of the microcontroller are blocked. In this way, the external controller can detect a circuit defect.
Abstract
Description
Claims
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/043,304 US6261285B1 (en) | 1995-09-14 | 1996-09-16 | High-frequency surgical device and operation monitoring device for a high-frequency surgical device |
EP96944551A EP0850025A2 (de) | 1995-09-14 | 1996-09-16 | Hochfrequenz-chirurgiegerät und funktionsüberwachungsvorrichtung für ein hochfrequenz-chirurgiegerät |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE19534151.1 | 1995-09-14 | ||
DE19534151A DE19534151A1 (de) | 1995-09-14 | 1995-09-14 | Hochfrequenz-Chirurgiegerät |
Publications (2)
Publication Number | Publication Date |
---|---|
WO1997009938A2 true WO1997009938A2 (de) | 1997-03-20 |
WO1997009938A3 WO1997009938A3 (de) | 1997-08-28 |
Family
ID=7772198
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/DE1996/001738 WO1997009938A2 (de) | 1995-09-14 | 1996-09-16 | Hochfrequenz-chirurgiegerät und funktionsüberwachungsvorrichtung für ein hochfrequenz-chirurgiegerät |
Country Status (4)
Country | Link |
---|---|
US (1) | US6261285B1 (de) |
EP (1) | EP0850025A2 (de) |
DE (1) | DE19534151A1 (de) |
WO (1) | WO1997009938A2 (de) |
Families Citing this family (45)
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US7364577B2 (en) | 2002-02-11 | 2008-04-29 | Sherwood Services Ag | Vessel sealing system |
US7137980B2 (en) | 1998-10-23 | 2006-11-21 | Sherwood Services Ag | Method and system for controlling output of RF medical generator |
US7901400B2 (en) | 1998-10-23 | 2011-03-08 | Covidien Ag | Method and system for controlling output of RF medical generator |
WO2003092520A1 (en) | 2002-05-06 | 2003-11-13 | Sherwood Services Ag | Blood detector for controlling anesu and method therefor |
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 |
EP1617776B1 (de) | 2003-05-01 | 2015-09-02 | Covidien AG | System zur programmierung und kontrolle eines elektrochirurgischen generatorsystems |
AU2003286644B2 (en) | 2003-10-23 | 2009-09-10 | 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 |
US7300435B2 (en) * | 2003-11-21 | 2007-11-27 | Sherwood Services Ag | Automatic control system for an electrosurgical generator |
US7766905B2 (en) | 2004-02-12 | 2010-08-03 | Covidien Ag | Method and system for continuity testing of medical electrodes |
US7780662B2 (en) | 2004-03-02 | 2010-08-24 | Covidien Ag | Vessel sealing system using capacitive RF dielectric heating |
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 |
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 |
CA2575392C (en) | 2006-01-24 | 2015-07-07 | Sherwood Services Ag | System and method for tissue sealing |
US9186200B2 (en) | 2006-01-24 | 2015-11-17 | Covidien Ag | System and method for tissue sealing |
CA2574935A1 (en) | 2006-01-24 | 2007-07-24 | Sherwood Services Ag | A method and system for controlling an output of a radio-frequency medical generator having an impedance based control algorithm |
US8147485B2 (en) | 2006-01-24 | 2012-04-03 | 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 |
US7513896B2 (en) | 2006-01-24 | 2009-04-07 | Covidien Ag | Dual synchro-resonant electrosurgical apparatus with bi-directional magnetic coupling |
US8216223B2 (en) | 2006-01-24 | 2012-07-10 | Covidien Ag | System and method for tissue sealing |
US8685016B2 (en) | 2006-01-24 | 2014-04-01 | Covidien Ag | System and method for tissue sealing |
DE102006010145A1 (de) * | 2006-01-27 | 2007-08-09 | Erbe Elektromedizin Gmbh | Optokopplervorrichtung und Verfahren zur Fertigung dessen |
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 |
US7731717B2 (en) | 2006-08-08 | 2010-06-08 | Covidien Ag | System and method for controlling RF output during tissue sealing |
US8034049B2 (en) | 2006-08-08 | 2011-10-11 | Covidien Ag | System and method for measuring initial tissue impedance |
US7637907B2 (en) * | 2006-09-19 | 2009-12-29 | Covidien Ag | System and method for return electrode monitoring |
US7794457B2 (en) | 2006-09-28 | 2010-09-14 | Covidien Ag | Transformer for RF voltage sensing |
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 |
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 |
US8226639B2 (en) | 2008-06-10 | 2012-07-24 | Tyco Healthcare Group Lp | System and method for output control of electrosurgical generator |
US8262652B2 (en) | 2009-01-12 | 2012-09-11 | Tyco Healthcare Group Lp | Imaginary impedance process monitoring and intelligent shut-off |
EA037357B1 (ru) * | 2013-06-25 | 2021-03-17 | Майкл Спирс | Система, способ и устройство для электрохирургии посредством использования излучения энергии |
US9872719B2 (en) | 2013-07-24 | 2018-01-23 | Covidien Lp | Systems and methods for generating electrosurgical energy using a multistage power converter |
US9655670B2 (en) | 2013-07-29 | 2017-05-23 | Covidien Lp | Systems and methods for measuring tissue impedance through an electrosurgical cable |
DE102017109638A1 (de) * | 2017-05-04 | 2018-11-08 | Olympus Winter & Ibe Gmbh | Generator für die Abgabe hochfrequenten Wechselstroms an ein Medizininstrument |
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US3699967A (en) * | 1971-04-30 | 1972-10-24 | Valleylab Inc | Electrosurgical generator |
EP0171967A2 (de) * | 1984-08-15 | 1986-02-19 | Valleylab, Inc. | Generator für die Elektrochirurgie |
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US3946738A (en) * | 1974-10-24 | 1976-03-30 | Newton David W | Leakage current cancelling circuit for use with electrosurgical instrument |
GB2090532B (en) * | 1981-01-02 | 1985-09-18 | Goof Sven Karl Lennart | An electrosurgical apparatus |
DE58906776D1 (de) * | 1989-05-19 | 1994-03-03 | Siemens Ag | Schaltungsanordnung zur Steuerung eines Elektro- Therapiegerätes, insbesondere HF-Chirurgiegerätes. |
US5540681A (en) * | 1992-04-10 | 1996-07-30 | Medtronic Cardiorhythm | Method and system for radiofrequency ablation of tissue |
US5318563A (en) * | 1992-06-04 | 1994-06-07 | Valley Forge Scientific Corporation | Bipolar RF generator |
-
1995
- 1995-09-14 DE DE19534151A patent/DE19534151A1/de not_active Withdrawn
-
1996
- 1996-09-16 EP EP96944551A patent/EP0850025A2/de not_active Ceased
- 1996-09-16 US US09/043,304 patent/US6261285B1/en not_active Expired - Fee Related
- 1996-09-16 WO PCT/DE1996/001738 patent/WO1997009938A2/de not_active Application Discontinuation
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3699967A (en) * | 1971-04-30 | 1972-10-24 | Valleylab Inc | Electrosurgical generator |
EP0171967A2 (de) * | 1984-08-15 | 1986-02-19 | Valleylab, Inc. | Generator für die Elektrochirurgie |
Also Published As
Publication number | Publication date |
---|---|
EP0850025A2 (de) | 1998-07-01 |
US6261285B1 (en) | 2001-07-17 |
DE19534151A1 (de) | 1997-03-20 |
WO1997009938A3 (de) | 1997-08-28 |
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