HF generator for powering one or more medical instruments
By using a coupler with a high insulation voltage in the HF generator to form isolation between the output block and the oscillator block, the problem of complex and uneven isolation schemes in the prior art is solved, and structural simplification and safety improvement are achieved.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- AERBO ELECTRONIC MEDICAL INSTR CO LTD
- Filing Date
- 2025-12-01
- Publication Date
- 2026-06-05
AI Technical Summary
Existing HF generator isolation schemes are complex and uneven, which affects system safety, especially the insulation locations with the lowest dielectric strength, which become the system's weak points.
A first power and data coupler with a high insulation voltage is used to form a clear isolation between the output block and the oscillator block, reducing the number of insulation locations, and high dielectric strength insulation is achieved through a transformer and an optocoupler, simplifying the isolation scheme.
The structure of the HF generator has been simplified, the safety and reliability of the system have been improved, the number of insulation points has been reduced, and the protection against voltage breakdown has been enhanced.
Smart Images
Figure CN122159172A_ABST
Abstract
Description
Technical Field
[0001] The present invention relates to a high-frequency generator (HF generator) for powering at least one medical device, particularly at least one HF surgical instrument, which is configured, for example, for cutting, coagulating, and, as needed, achieving additional tissue effects on biological tissues of human or animal patients. Background Technology
[0002] HF generators used to power one or more medical devices are typically known from existing technology.
[0003] WO 2004 / 030552 A1 describes an electrosurgical generator for powering one or more medical devices. The medical devices should allow for the influence of a patient's biological tissue, such as cutting or coagulating tissue. For this purpose, the medical device is at least temporarily attached to or in contact with the patient. Therefore, it is particularly important to ensure that no uncontrolled current can flow from the medical device through the patient. The patient, capacitively coupled to the ground wire associated with the power grid, should remain isolated. To ensure this, WO 2004 / 030552 A1 includes multiple insulation locations, respectively, between the power grid, the control unit, and the generator's oscillator, which are configured with increased electrical strength. The measures used to achieve this increased electrical strength at each insulation location are structurally complex. Therefore, the diversity of such insulation locations results in a considerably high complexity of the system architecture. Furthermore, in the case of multiple insulation locations arranged in parallel, these insulation locations have unequal dielectric strengths due to manufacturing reasons; for example, the insulation location with the lowest dielectric strength is a weakness in the system architecture. Therefore, despite the considerable complexity of the system architecture, system safety can be considered in part critical. Summary of the Invention
[0004] Therefore, the object of the present invention is to provide an HF generator with an improved and simplified isolation scheme. In particular, in HF generators, fewer or at least fewer insulation locations with particularly high dielectric strength are required, which have at least equal or improved safety.
[0005] This objective is achieved by means of the HF generator according to claim 1: The HF generator according to the invention is used to power at least one medical device, particularly at least one HF surgical instrument. The HF generator according to the invention includes an output block, an oscillator block, a communication block, and a power grid block.
[0006] The output block is configured to supply HF current to one or more medical devices. Therefore, the HF current is an alternating current with a frequency higher than 100 kHz, preferably higher than 300 kHz (e.g., between 300 kHz and 4 MHz). The output block specifically includes a sensor unit configured to determine sensor data of the HF current, such as current values, voltage values, apparent power values, active power values and / or reactive power values, and values such as the complex impedance of the device or tissue, its changes, and / or the linearity of the complex impedance. The output block may additionally include a preprocessing unit configured to preferably preprocess the sensor data in real time.
[0007] The oscillator block is configured to supply HF current to the output block via a first power coupler. Furthermore, the oscillator block is connected to the output block via a first data coupler. The oscillator block specifically includes an HF control unit configured to receive desired parameters and sensor data of the HF current of the output block, and to control the HF current in a closed-loop manner based on the parameters and sensor data.
[0008] The communication block is connected to the output block via a second power coupler and to the oscillator block via a second data coupler. The power grid block is coupled to the oscillator block and is coupled to the communication block via a third power coupler for power supply.
[0009] The HF generator according to the invention is characterized in that the first power coupler includes an insulation voltage that is higher than that of the remaining power couplers, preferably all of the remaining power couplers. Preferably, the first data coupler also includes an insulation voltage that is higher than that of the remaining data couplers, preferably all of the remaining data couplers. The higher insulation voltage of the first power coupler and the first data coupler means that the latter has a higher dielectric strength in terms of the voltage peak and potential difference between the power grid, the HF generator, and the patient.
[0010] The insulation concept according to the invention provides clear isolation between the output block and the oscillator block in order to reduce the number of insulation locations, especially the number of insulation locations with high dielectric strength. The oscillator block is sparsely protected or not protected at all relative to the grid block, while the output block is strongly protected relative to the oscillator block, which means that the insulation locations between the output block and the oscillator block include high insulation voltages or insulation strengths.
[0011] In this way, the output block can be insulated using only two couplers (the first power coupler and the first data coupler) with high dielectric strength relative to the oscillator block, thus providing an enhanced degree of dielectric strength. This significantly simplifies the isolation scheme of the HF generator. The inputs and outputs of the first power coupler and the first data coupler are currently isolated from each other with high dielectric strength in each case. Therefore, the dielectric strength of the coupler is defined by the maximum insulation voltage or breakdown voltage that can be applied between its primary and secondary sides without causing voltage breakdown or current flow. For example, the first power coupler could be a transformer with separate windings insulated from each other, these windings being separated from each other both currently and spatially. The first power coupler includes particularly high electrical insulation strength between the primary and secondary sides. This can be achieved, for example, by arranging the primary and secondary windings in separate encapsulated insulating material chambers within the first power coupler. By reducing to only one power coupler, this increases the safety against voltage breakdown (increased insulation strength), thus reducing the technical effort required for the HF generator while providing equal or even increased safety.
[0012] Preferably, the isolation voltage of the first power coupler and the first data coupler, which are of a set size, is greater than the sum of twice the peak output voltage of the oscillator block and an additional voltage that may exist in the form of a maximum voltage peak on the operating voltage of the oscillator block. This maximum voltage peak is the sum of the operating DC voltage of the oscillator block and twice the peak grid voltage, wherein this sum is additionally multiplied by a safety factor. For example, the safety factor may be at least 1, 2, 3, 4, or greater. A relatively large safety factor reduces the risk that the AC current from the grid block could break down the output block and thus via medical devices connected to the patient and / or surgeon.
[0013] For all couplers, the following applies explicitly: a power coupler is configured to transfer power between two blocks that are electrically insulated from each other. A data coupler is configured to transfer data (i.e., information) between two blocks that are also electrically insulated from each other.
[0014] Specifically, a first insulating path may be formed between the output block and the oscillator block, wherein the first power coupler and the first data coupler are arranged in parallel with each other. The insulating path is an conceivable path, however, interrupted by one or more insulating barriers, along which current cannot and should not flow from one end to the other. For this purpose, the one or more barriers present in the insulating path each include a defined insulating voltage that defines the insulating voltage of the insulating path. The first power coupler and the first data coupler preferably include equal insulating voltages.
[0015] Preferably, a second insulation path is additionally formed between the output block and the oscillator block, wherein the second power coupler and the second data coupler are arranged in series such that the insulation voltages of the second power coupler and the second data coupler are added to each other along the second insulation path.
[0016] The first and second insulation paths are specifically arranged in parallel with each other. The insulation voltages of the first and second insulation paths are preferably equal.
[0017] Specifically, the insulation voltage of the first power coupler and the first data coupler is each higher than, preferably significantly higher than, the insulation voltage of the second power coupler and the second data coupler, for example, by 1.5 times, 2 times, or 2.5 times.
[0018] It is preferred if the total insulation voltage of the second power coupler and the second data coupler corresponds to, and preferably coincides with, the insulation voltage of the first power coupler. It is also preferred if the total insulation voltage of the second power coupler and the second data coupler corresponds to, and preferably coincides with, the insulation voltage of the first data coupler. This results in the first and second insulation paths having equal insulation voltages, and thus, due to the parallel arrangement of the first insulation path relative to the second insulation path, in the event of overvoltage, neither insulation path yields, but both insulation paths withstand voltage peaks without voltage breakdown.
[0019] The first and second data couplers are preferably configured as inductive or capacitive data couplers or optocouplers. However, in each case, the first, second, and third power couplers can be configured as transformers.
[0020] Preferably, the oscillator block includes an HF unit, an HF control unit, a power grid unit, and a second data unit. The HF control unit is specifically configured to control the HF unit, causing it to generate an HF current that is transmitted to the output block via a first power coupler. The HF current can have different varying HF characteristics, which can be modified using the HF control unit during HF generator operation. For example, the HF characteristics can therefore include different current values, voltage values, frequency values, waveforms, crest factors, clocks, etc., to define different operating modes.
[0021] The grid unit is specifically configured to supply grid power from the grid block to the HF unit. The grid unit may include a power factor correction unit to make the current drawn from the grid side approximately sinusoidal and reduce its harmonics. The HF unit may also be configured to pre-control the power factor correction unit of the grid unit as needed to ensure that sufficient power is always provided, especially in the event of sudden load changes.
[0022] The output block preferably includes a distribution unit. This unit is configured to distribute an HF voltage, amplified by a transformer and received via a first power coupler, to one or more medical devices. The HF voltage may have an amount greater than, for example, 2 kV, 3 kV, or 4 kV.
[0023] The distribution unit specifically includes at least one sensor unit configured to detect the HF current as sensor data in the output block. For example, the sensor data may include at least current values, voltage values, apparent power values, active power values, and / or reactive power values.
[0024] In addition, the output block may include a preprocessing unit communicatively coupled to the sensor unit. In its simplest case, the preprocessing unit may simply be an analog-to-digital converter (ADC) that converts analog sensor data into digital sensor data. However, the preprocessing unit may also be configured to perform more complex preprocessing steps, such as determining complex tissue impedance, determining changes in complex tissue impedance, and / or determining the linearity of complex tissue impedance. The preprocessing unit is preferably configured to process the sensor data in real time.
[0025] The output block may additionally include a first data unit configured to buffer (digital) sensor data and provide the sensor data to the oscillator block. The first data unit is specifically communicatively connected to a second data unit via a first data coupler, allowing sensor data to be exchanged between the first and second data units.
[0026] The communication block may include an operation control unit and communication interfaces connected to the control unit to multiple operation and instruction units. Through the operation and instruction units, the user of the HF generator (i.e., a surgeon, physician assistant, or surgical assistant) can set desired parameters for the HF control unit.
[0027] The operation control unit communicates with the second data unit via a second data coupler, allowing the second data unit to receive preset parameters from the HF control unit via a second data interface. Furthermore, the second data unit receives and buffers sensor data detected by the output block via a first data coupler. The preset parameters and the detected sensor data are forwarded to the HF control unit configured to control the HF unit, causing the HF current in the output block to be set with preset HF characteristics (parameters) and controlled in a feedback manner.
[0028] Preferably, the first power coupler and the first data coupler are designated as a first insulation class, wherein the couplers withstand (particularly) high voltages, such as 8 kV, 10 kV, 12 kV or higher. However, the remaining power and data couplers are designated as a second insulation class, wherein, by contrast, the couplers withstand only lower voltages (such as 4 kV, 5 kV, 6 kV or lower) without voltage breakdown between the primary and secondary sides.
[0029] The output block can be protected relative to the grid block via a second power coupler and a third power coupler.
[0030] Due to the innovative system architecture of the HF generator, the generator blocks are divided into different insulation zones relative to the grid block, such as high insulation zone, intermediate insulation zone, and low insulation zone. The high insulation zone is best protected against voltage breakdown caused by the sum of the grid voltage peak and the voltage generated by the HF generator. The output block is located in the high insulation zone, the communication block is located in the intermediate insulation zone, and the oscillator block is located in the low insulation zone. Attached Figure Description
[0031] Further details of preferred embodiments of the invention are derived from the dependent claims, drawings, or description. The drawings illustrate: Figure 1 An example of an HF generator according to the present invention is shown in schematic diagram; Figure 2 An insulation diagram illustrating the insulation concept of an HF generator according to the present invention is shown; Figure 3 Another insulation diagram illustrating the insulation concept of an HF generator according to the present invention is shown; Figure 4 Examples of a first data coupler and a first power coupler are shown; Figure 5 Another example of a first data coupler and a first power coupler is shown; Figure 6 An example of a power grid unit in an oscillator block is shown; and Figure 7 An example is shown of the HF unit together with the oscillator block and the connection to the output block. Detailed Implementation
[0032] Figure 1 An exemplary illustration of an HF generator 10 according to the present invention is shown. The HF generator 10 includes an output block 11, an oscillator block 12, a communication block 13, and a power grid block 14.
[0033] Output block 11 supplies the HF current generated in oscillator block 12 to the medical device. Grid voltage is supplied to oscillator block 12 via grid block 14. Communication block 13 serves as an interface for the operator of the HF generator 10, through which the operator can adjust the HF current generated in oscillator block 12.
[0034] Output block 11 includes a distribution unit 15 with sensor unit 16, a preprocessing unit 17, and a first data unit 18. Furthermore, Figure 1 The output block 11 shown in the figure includes a first instrument interface 19, a second instrument interface 20, and a neutral electrode interface 21.
[0035] The first device interface 19 and the second device interface 20 are configured to connect the first and second medical devices to the output block 11 of the HF generator 10. The neutral electrode interface 21 is configured to connect a neutral electrode that can be attached to a patient. The medical device may be a monopolar and / or bipolar HF surgical instrument. HF current is supplied to the device and neutral electrode interfaces 19, 20, and 21 by means of a distribution unit 15. The device and neutral electrode interfaces 19, 20, and 21 may be configured to determine whether a medical device is connected and transmit this information to a first data unit. The device and neutral electrode interfaces 19, 20, and 21 may additionally be configured to identify the connected device.
[0036] Sensor unit 16 is configured to detect sensor data of the generated HF current. For example, such sensor data may include current values, voltage values, power values, complex impedance, etc. Sensor unit 16 is connected to preprocessing unit 17.
[0037] In its simplest form, the preprocessing unit 17 can be an analog-to-digital converter that generates discrete data from the received analog sensor data. However, the preprocessing unit 17 can also be configured to perform more complex preprocessing steps, by which the sensor data can be preprocessed as in real time as possible. For example, a moving average filter can be used to smooth the progression of sensor values. Other preprocessing of the sensor data can also be performed, such as noise suppression, data normalization, filtering, etc. The preprocessing unit 17 is connected to the first data unit 18 and is configured to forward digital sensor data to the first data unit 18.
[0038] Alternatively, sensor unit 16 may also include an analog-to-digital converter. In this case, sensor unit 16 can be directly connected to the first data unit 18. Digital sensor data can be directly forwarded from sensor unit 16 to the first data unit 18.
[0039] The first data unit 18 is configured to buffer digital sensor data. The first data unit 18 is connected to the oscillator block 12 via a first data coupler 22. More specifically, the first data unit 18 is communicatively connected to the second data unit 23 of the oscillator block 12 via the first data coupler 22.
[0040] The oscillator block 12 includes a second data unit 23, an HF control unit 24, an HF unit 25, and a power grid unit 26.
[0041] Grid voltage is supplied from grid block 14 to grid unit 26. The grid voltage is a typical AC grid voltage, which, depending on the country where the HF generator 10 is operated, is, for example, a sinusoidal AC voltage with an RMS value of 230 V and a grid frequency of 50 Hz between the phase conductors and the neutral conductor. Grid unit 26 may include a power factor correction unit 27, which increases the power factor of oscillator block 12 and thereby reduces interference harmonics in the grid. Power factor correction unit 27 is controlled by means of HF control unit 24.
[0042] The grid unit 26 can be configured to rectify the grid voltage and forward the resulting DC voltage to the HF unit 25. The resulting DC voltage can be higher or lower than the grid voltage of the grid block. The grid unit 26 may have, for example, a boost converter (also referred to as a boost transformer) for converting the rectified grid voltage.
[0043] An oscillator circuit is provided in HF unit 25, using which a high-frequency voltage signal is generated from a rectified boosted DC voltage. An HF current is generated from the HF voltage signal (e.g., by means of a power amplifier preferably operating in switching mode), and this HF current is used to power the medical device. HF unit 25 is thus controlled by HF control unit 24.
[0044] The HF current generated by HF unit 25 is transmitted from oscillator block 12 to output block 11 via first power coupler 28. Therefore, first power coupler 28 can be used as part of a power amplifier for generating HF current.
[0045] According to the insulation concept of the HF generator 10 according to the present invention, the first power coupler 28 and the first data coupler 22 have insulation voltages that are much higher than those of the remaining data and power couplers of the HF generator 10, thereby defining the insulation strength of the components. This results in the output block 11 being effectively protected against voltage peaks from the grid block 14 breaking down to the output block 11 via the oscillator block 12. For example, the insulation voltage of the first data coupler and the first power coupler can be twice that of the remaining data and power couplers. Due to the increased insulation between the output block 11 and the oscillator block 12, the number of insulation locations between blocks can be reduced, thereby simplifying the overall architecture of the HF generator 10.
[0046] Communication block 13 includes a second power coupler 29 and a third power coupler 30. The second power coupler 29 and the third power coupler 30 have a lower insulation voltage than the first power coupler 28. For example, the sum of the insulation voltages of the second power coupler 29 and the third power coupler 30 corresponds to the insulation voltage of the first power coupler 28. The second power coupler 29 and the third power coupler 30 are used to supply operating voltage to the unit consisting of the connected blocks (i.e., communication block 13 and output block 11).
[0047] Communication block 13 includes an operation control unit 31 connected to communication interface 32. Communication block 13 includes multiple operation and indication interfaces 33a to 33g. Operation and indication interfaces 33a to 33g may include, for example, a speaker interface 33a, a pedal interface 33b, additional auxiliary input interfaces 33c, 33d, 33e, and 33f (e.g., Universal Serial Bus (USB) or other communication buses), and a display interface 33g. Operation and indication interfaces 33a to 33g allow the operator to input operating parameters of the HF generator 10, and output (current) sensor data, operating parameters, etc., for example, via an operation unit such as a touchscreen. This can be done via, for example, an indication unit 34 including a display. Control of communication block 13 is performed using operation control unit 31.
[0048] The operation control unit 31 is connected to the second data unit 23 via the second data coupler 35. Furthermore, the second data coupler 35 has a lower insulation voltage than the first data coupler 22. For example, the first data coupler 22 and the second data coupler 35 can be configured as optocouplers.
[0049] At least a fourth power coupler 36 may be additionally arranged between the oscillator block 12 and the grid block 14. The fourth power coupler 36 may have a much lower insulation voltage than the other power couplers 28, 29, and 30. During operation, there is no risk of contact between the patient, operator, or surgeon and the oscillator block 12, thereby allowing for significantly lower requirements on the dielectric strength between the grid block 14 and the oscillator block 12. If the fourth power coupler 36 is provided, it can be used to supply operating voltage to the units comprised of the oscillator block 12. Alternatively, the units of the oscillator block 12 may also be directly powered by the grid block 14.
[0050] Isolation paths are defined between the various blocks 11, 12, 13, and 14 of the HF generator 10 via the first power coupler 28, the second power coupler 29, the third power coupler 30, the fourth power coupler 36, the first data coupler 22, and the second data coupler 35. The following will be based on... Figure 2 and Figure 3 These paths will be explained in more detail.
[0051] Figure 2 and Figure 3 The diagram illustrates the insulation scheme of the HF generator 10 according to the present invention. Figure 2 and 3 In this context, the vertical distance between blocks (meaning in the height direction) represents the insulation voltage between the individual power and data couplers.
[0052] exist Figure 2 and Figure 3 In the two examples depicted, the insulation voltage of the first power coupler 28 and the first data coupler 22 is twice the insulation voltage of the second data coupler 35 and the second power coupler 29.
[0053] The HF generator 10 is divided into multiple insulation zones, namely the high insulation zone 37, the intermediate insulation zone 38, and the low insulation zone 39.
[0054] exist Figure 2 In the example shown, both oscillator block 12 and grid block 14 are arranged in low insulation region 39. This means that no or only negligible low insulation voltage is provided between the two blocks. Output block 11 is designated as high insulation region 37. Conversely, communication block 13 is designated as intermediate insulation region 38.
[0055] A first insulating path 40 is formed between the output block 11 and the oscillator block 12, wherein the first data coupler 22 and the first power coupler 28 are arranged in parallel with each other.
[0056] Between the output block 11 and the oscillator block 12, there is a second insulation path 41 via the second power coupler 29, the communication block 13, and the second data coupler 35 (in series). The first insulation path 40 and the second insulation path 41 are then arranged in parallel with each other. In addition, the communication block 13 is insulated from the power grid block 14 by means of the third power coupler 30.
[0057] Figure 3 The illustration shows another insulation scheme for the HF generator 10 according to the invention. Referring to the already introduced reference numerals, the above explanation applies accordingly. Figure 3 Examples and basis Figure 2 The difference in the example is that the fourth power coupler 36 is arranged between the power grid block 14 and the oscillator block 12.
[0058] Figure 4A detailed illustration shows an example of a first data coupler 22 and a first power coupler 28. In this example, the first data coupler 22 is configured as an optocoupler. In the illustrated example, the first power coupler 28 is configured as a transformer. The insulation voltage of a transformer describes its ability to withstand voltage breakdown between the primary and secondary windings. For example, the transformer is sized to have an insulation voltage of 12 kV. This means that the voltage difference between the primary and secondary sides of the transformer can be up to 12 kV without causing a short circuit between the primary and secondary sides. The primary and secondary sides are thus reliably electrically isolated from each other. On the secondary side, Figure 4 The illustrated example provides an autotransformer for implementing one or more connectors, from which a medical device can be powered.
[0059] Figure 5 Detailed illustrations of an alternative example of the first data coupler 22 and the first power coupler 28 are shown. In this example, the first data coupler 22 includes an oscillator block-side optical coupler 42 and an output block-side optical coupler 43 connected to each other via multiple optical connection lines 44.
[0060] exist Figure 4 In the example shown, the insulation voltage of the first data coupler 22 is generated by the sum of the insulation voltages of the oscillator block-side optocoupler 42 and the output block-side optocoupler 43. For example, the oscillator block-side optocoupler 42 may have an insulation voltage of 6 kV, and the output block-side optocoupler 43 may also have an insulation voltage of 6 kV. Therefore, the first data coupler 22 has a total insulation voltage of 12 kV.
[0061] The first power coupler 28 includes an oscillator block-side transformer 45 and an output block-side transformer 46. The secondary side of the oscillator block-side transformer 45 is connected to the primary side of the output block-side transformer 46 via a transmission line 47.
[0062] In this example, the dimensions of the oscillator block-side transformer 45 and the output block-side transformer 46 are set for the sum of the insulation voltages due to the series connection of the two transformers in each case. For example, the insulation voltages of the two transformers are 6 kV, so the first power coupler 28 includes a total insulation voltage of 12 kV. In this embodiment, it is advantageous if the two transmission transformers 45, 46 have parasitic capacitances that overlap with each other between their respective primary and secondary windings. Although the two transformers 45, 46 cannot be constructed identical by definition due to the required voltage transmission or reduction ratio, this is indeed the case. However, due to the overlapping parasitic capacitances, the voltage peaks between the primary side of transformer 45 and the secondary side of transformer 46 are split evenly across the two transformers 45, 46. This avoids series voltage breakdown through the power coupler 28. If necessary, one or more capacitors can be switched to be connected in parallel with the parasitic capacitances to produce the indicated voltage balance.
[0063] Figure 6 The diagram shows the power grid unit 26 of the oscillator block 12. Figure 6 In the example shown, grid unit 26 includes a rectifier 48 that converts the grid voltage on the input side into a DC voltage. Grid unit 26 additionally includes a boost converter 49 that boosts the generated DC voltage.
[0064] The boost converter 49 includes a switch 50, an inductor 54, a diode 55, and a capacitor 56. When switch 50 is open, current remains due to the inductance of inductor 54. The voltage at the output side therefore increases rapidly until it exceeds the voltage applied to capacitor 56, and thus diode 55 turns on. Therefore, in the first case, current continues to flow unmodified, and capacitor 56 is additionally charged. The magnetic field of the inductor thus decreases, and its energy is output as current is driven into capacitor 56 via diode 55. The capacitance of capacitor 56 is sized such that the output voltage remains approximately constant during the operating cycle.
[0065] Switch 50 is controlled by power factor correction unit 27. Power factor correction unit 27 receives the absolute value of the rectified grid voltage (input voltage Ue), the output voltage (Ua) of boost converter 49, and a reference voltage Uref from HF control unit 24. In power factor correction unit 27, the difference between the output voltage Ua and the reference voltage is multiplied by the absolute value of the input voltage Ue to calculate the desired current for controlling switch 50. Therefore, the power factor can be set to a value close to 1.
[0066] Figure 7A detailed diagram is shown of the HF unit 25 with a first power coupler 28 and the distribution unit 15 of the output block 11. The HF unit 25 includes an oscillator circuit comprising a capacitor 51, an inductor 52, and a switch 53. The switch 53 is controlled by the HF unit 24.
[0067] The inductor 52 of HF unit 25 may already be, for example, configured as one side of the first power coupler 28 of the transformer. Figure 7 In this circuit, inductor 52 is the primary winding of the transformer in the first power coupler 28. Distribution unit 15 is connected to the secondary side of the first power coupler 28. Therefore, the secondary winding of the transformer can also be used to tap different HF currents with different voltage levels. A sensor unit 16 is provided in distribution unit 15, by means of which current, voltage, complex resistance, etc., applied to the output side can be detected. Sensor unit 16 is connected to preprocessing unit 17, which preprocesses the sensor data and forwards the sensor data to control unit 24 via a first data unit through a first data coupler.
[0068] This invention relates to an HF generator 10 for powering at least one medical device, particularly at least one HF surgical instrument, configured for, for example, cutting, coagulating, and, as needed, achieving additional tissue effects on biological tissue in human or animal patients. The HF generator 10 according to the invention includes an output block 11, an oscillator block 12, a communication block 13, and a power grid block 14. The output block 11 is configured to supply HF current to one or more medical devices. The oscillator block 12 is configured to supply HF current to the output block 11 via a first power coupler 28. Furthermore, the oscillator block 12 is connected to the output block 11 via a first data coupler 22. The communication block 13 is connected to the output block 11 via a second power coupler 29 and to the oscillator block 12 via a second data coupler 35. The HF generator according to the invention is unique in that the first power coupler 28 and the first data coupler 22 have higher insulation voltages than the remaining power couplers 29, 30 and data coupler 35, so that the output block 11 is protected relative to the oscillator block 12 by means of only two couplers, which are provided with measures to increase their insulation voltages while providing similar functionality and equal dielectric strength.
[0069] List of reference numerals in the attached diagram: 10 HF generator 11 Output Block 12 Oscillator Blocks 13 Communication Block 14 power grid blocks 15 Distribution Units 16 sensor units 17 Preprocessing Unit 18 First Data Unit 19 First Instrument Interface 20 Second Instrument Interface 21 Neutral electrode interface 22 First Data Coupler 23 Second Data Unit 24 HF Control Unit 25 HF units 26 Power Grid Units 27 Power Factor Correction Unit 28 First power coupler 29 Second power coupler 30 Third power coupler 31 Operation Control Unit 32 Communication Interface 33a-33g Operation and Instruction Interface 34. Indicator Unit (Display) 35 Second Data Coupler 36 Fourth power coupler 37 High Insulation Zone 38 Intermediate Insulation Zone 39 Low insulation zone 40 First Insulation Path 41 Second Insulation Path 42 Oscillator Block Side Optical Coupler 43 Output Block Side Optical Coupler 44 Optical Connector 45 Oscillator Block-Side Transformer 46 Output Block Side Transformer 47 Transmission Line 48 Rectifier 49 Boost Converter 50 Boost converter switch 51. Capacitors in an oscillator circuit 52. Inductors in oscillator circuits 53. Switching on the oscillator circuit 54. Inductors of boost converters 55 Diodes in a boost converter 56. Capacitors in the boost converter Ue is the input voltage of the boost converter. Ua Boost converter output voltage Uref reference voltage
Claims
1. An HF generator (10) for powering one or more medical devices, particularly one or more HF surgical instruments, comprising: An output block (11) is configured to supply HF current to one or more medical devices; An oscillator block (12) is configured to supply the HF current to the output block (11) via a first power coupler (28), wherein the oscillator block (12) is connected to the output block (11) via a first data coupler (22); The communication block (13) is connected to the output block (11) via the second power coupler (29) and to the oscillator block (12) via the second data coupler (35); as well as The power grid block (14), which is connected to the oscillator block (12) and connected to the communication block (13) via a third power coupler (30), is powered in a manner. The first power coupler (28) has a higher insulation voltage than the other power couplers (29, 30).
2. The HF generator (10) according to claim 1, characterized in that, The first data coupler (22) has a higher insulation voltage than the second data coupler (35).
3. The HF generator (10) according to claim 1 or 2, characterized in that, A first insulating path (40) is formed between the output block (11) and the oscillator block (12), wherein the first power coupler (28) and the first data coupler (22) are arranged in parallel with each other.
4. The HF generator (10) according to any one of the preceding claims, characterized in that, A second insulating path (41) is formed between the output block (11) and the oscillator block (12), wherein the second power coupler (29) and the second data coupler (35) are arranged in series with each other.
5. The HF generator (10) according to any one of the preceding claims, characterized in that, The insulation strength of the first power coupler (28) and the first data coupler (22) is at least equal to or higher than the sum of the insulation strengths of the second power coupler (29) and the second data coupler, respectively.
6. The HF generator (10) according to any one of the preceding claims, characterized in that, The first data coupler (22) and the second data coupler (35) are configured as inductive or capacitive data couplers or optocouplers (42, 43).
7. The HF generator according to any one of the preceding claims, characterized in that, The oscillator block (12) includes an HF unit (25), an HF control unit (24), a power grid unit, and a second data unit (23), wherein the HF control unit (24) is configured to control the HF unit (25) so that the HF unit generates an HF current with different parameters, such as different current values, voltage values, waveforms, crest factors, clocks, modes, etc.
8. The HF generator (10) according to any one of the preceding claims, characterized in that, The power grid unit (26) includes a power factor correction unit (27), wherein the HF control unit (24) is configured to adjust the power factor by means of the power factor correction unit (27).
9. The HF generator (10) according to any one of the preceding claims, characterized in that, The output block (11) includes a distribution unit (15) configured to distribute the HF current received via the first power coupler (28) to the one or more devices.
10. The HF generator (10) according to any one of the preceding claims, characterized in that, The distribution unit (15) includes at least one sensor unit (16) configured to detect the HF current as sensor data in the output block (11), wherein the sensor data preferably includes at least current, voltage, apparent power, active power and / or reactive power measurements, and particularly preferably includes the complex impedance of the tissue, changes in the complex impedance of the tissue and / or the linearity of the complex impedance of the tissue.
11. The HF generator (10) according to any one of the preceding claims, characterized in that, The output block (11) includes a first data unit (18) which is communicatively connected to the sensor unit and configured to distribute and buffer the sensor data.
12. The HF generator (10) according to any one of the preceding claims, characterized in that, The first data unit (18) is communicatively connected to the second data unit (23) via the first data coupler (22).
13. The HF generator (10) according to any one of the preceding claims, characterized in that, The communication block (13) includes an operation control unit (31) and one or more operation and instruction interfaces (33a, ..., 33g), through which a user can input parameters for the HF control unit (24), and the operation and instruction interfaces are connected to the operation control unit (31).
14. The HF generator (10) according to any one of the preceding claims, characterized in that, The operation control unit (31) is communicatively connected to the second data unit (23) via the second data coupler (35).
15. The HF generator according to any one of the preceding claims, characterized in that, The blocks (11, 12, 13) are designated as different isolation zones relative to the grid block (14), wherein the isolation zones (37, 38, 39) have different isolation voltages, such as a high insulation zone (37), an intermediate insulation zone (38), and a low insulation zone (39).
16. The HF generator (10) according to any one of the preceding claims, characterized in that, The output block (11) is protected relative to the power grid block (14) by means of the second power coupler (29) and the third power coupler (30).