Bimodal tissue ablation device

Abstract

The application relates to a dual-mode tissue ablation device, which comprises a first pulse circuit configured to generate and output a first pulse signal; a second pulse circuit configured to generate and output a second pulse signal; a waveform conversion circuit connected with the second pulse circuit and configured to output a high-frequency resonance signal based on the second pulse signal; a signal switching circuit connected with the first pulse circuit and the waveform conversion circuit and configured to select the first pulse signal or the high-frequency resonance signal for output; and an output electrode configured to apply the signal output by the signal switching circuit to target tissue. By switching between the first pulse signal and the high-frequency resonance signal through the signal switching circuit and outputting the signal to the target tissue through the output electrode, switching between irreversible perforation ablation and radio frequency ablation can be realized, the two ablation modes can be synergized, and the influence of the heat sink effect on tissue ablation can be reduced.

Description

Technical Field

[0001] This application belongs to the field of medical device technology, and in particular relates to a dual-modal tissue ablation device. Background Technology

[0002] Currently, electrotherapy is widely used in many acute and chronic diseases and rehabilitation treatments. Because biological tissues possess certain electrical conductivity, the passage of current produces corresponding biological effects. These electrobiological effects vary significantly depending on the frequency. When high-frequency electrical energy is applied to biological tissues, the electrothermal effect can achieve tissue cutting, coagulation, and tissue ablation. High-frequency electrical energy applied to tissue ablation can be further divided into radiofrequency ablation and microwave ablation. Radiofrequency ablation uses high-frequency current to cause the polar molecules in the tissue to rotate at high speed, generating heat. When the heat generation temperature reaches a certain level, proteins denature and coagulative necrosis occurs. Microwave ablation uses voltage changes to create an alternating electric field, similar to the heating principle of a microwave oven, causing the tissue to heat up and die. Because both radiofrequency and microwave ablation utilize the electrothermal effect of biological tissues, the control of the ablation range depends on tissue heat conduction and diffusion, and is affected by the heat sink effect. In particular, blood in blood vessels carries away heat, making it difficult for the tissue near the blood vessels to reach the required ablation temperature, resulting in incomplete ablation at that location. Summary of the Invention

[0003] The purpose of this application is to provide a dual-modal tissue ablation device, which aims to solve the problem of heat sink effect in traditional radiofrequency ablation of tissue.

[0004] A first aspect of this application provides a dual-modal tissue ablation device, comprising: a first pulse circuit configured to generate and output a first pulse signal; a second pulse circuit configured to generate and output a second pulse signal; a waveform conversion circuit connected to the second pulse circuit and configured to output a high-frequency resonant signal based on the second pulse signal; a signal switching circuit connected to the first pulse circuit and the waveform conversion circuit and configured to receive the first pulse signal and the high-frequency resonant signal, and select one of the first pulse signal and the high-frequency resonant signal for output; and an output electrode connected to the signal switching circuit and configured to apply the signal output by the signal switching circuit to a target tissue for irreversible perforation ablation or radiofrequency ablation of the target tissue.

[0005] In one embodiment, the waveform conversion circuit includes a first inductor, a second inductor, and a filter capacitor. The first end of the first inductor is connected to the first output terminal of the second pulse circuit, the first end of the second inductor is connected to the second output terminal of the second pulse circuit, and the two ends of the filter capacitor are respectively connected to the second ends of the first inductor and the second inductor. Both ends of the filter capacitor are connected to the signal switching circuit for outputting the high-frequency resonant signal.

[0006] In one embodiment, the output electrode includes a first electrode needle and a second electrode needle. The first electrode needle is connected to a first output terminal of the signal switching circuit, and the second electrode needle is connected to a second output terminal of the signal switching circuit. The first electrode needle and the second electrode needle are used to contact the target tissue and apply the first pulse signal and the high-frequency resonant signal to the target tissue.

[0007] In one embodiment, the first electrode needle is a claw-shaped electrode needle.

[0008] In one embodiment, the first electrode needle includes an insulating sleeve, a fixed needle tip, and a plurality of bent elastic needle tips; one end of the insulating sleeve has an opening, and the other end of the insulating sleeve has an electrode connection end, which is used to connect to the signal switching circuit; the first end of the fixed needle tip and the first end of each elastic needle tip are electrically connected to the electrode connection end; the first end of the fixed needle tip is fixed inside the insulating sleeve; the second end of the fixed needle tip extends a certain length from the opening of the insulating sleeve along the axial direction of the insulating sleeve; the first end of each elastic needle tip is installed inside the insulating sleeve through a corresponding sliding structure, which is used to control the extension and retraction of the second end of the corresponding elastic needle tip at the opening of the insulating sleeve.

[0009] In one embodiment, the sliding structure includes a plurality of sliding grooves disposed on the side wall of the insulating sleeve and parallel to the axial direction of the sleeve, and a plurality of insulating push buttons corresponding to each of the sliding grooves. Each insulating push button is installed in a corresponding sliding groove and is connected to a corresponding elastic needle tip, so as to control the insulating push button to slide in the corresponding sliding groove, thereby causing the corresponding elastic needle tip to extend and retract at the opening of the insulating sleeve.

[0010] In one embodiment, a main control circuit is further included. The main control circuit is connected to the first pulse circuit and the second pulse circuit respectively. The main control circuit is configured to control the first pulse circuit and the second pulse circuit to operate, so as to generate and output the first pulse signal and the second pulse signal respectively.

[0011] In one embodiment, the first pulse circuit includes a plurality of power switches for generating and outputting the first pulse signal based on a driving voltage by controlling the on / off state of each of the power switches; the second pulse circuit has the same circuit structure as the first pulse circuit.

[0012] In one embodiment, an output detection circuit is further included. The output detection circuit is disposed between the signal switching circuit and the output electrode and connected to the main control circuit. It is configured to acquire the voltage applied to the target tissue through the output electrode and the current flowing through the output electrode, generate and output a corresponding digital feedback signal to the main control circuit. The main control circuit is further configured to obtain the electrochemical impedance parameters of the target tissue based on the digital feedback signal.

[0013] In one embodiment, a temperature detection circuit is further included. The temperature detection circuit is connected to the output electrode and the main control circuit respectively. The temperature detection circuit is configured to detect the temperature of the output electrode and output a corresponding temperature detection signal to the main control circuit. The main control circuit is further configured to obtain the temperature of the output electrode based on the temperature detection signal.

[0014] The beneficial effects of this application embodiment compared with the prior art are: by switching between the first pulse signal and the high-frequency resonant signal through the signal switching circuit, and outputting the signal to the target tissue through the output electrode, it is possible to switch between irreversible perforation ablation and radiofrequency ablation, and the two ablation modes can be used synergistically to reduce the impact of heat sink effect on tissue ablation. Attached Figure Description

[0015] Figure 1 This is a schematic diagram of the principle of a dual-modal tissue ablation device provided in an embodiment of this application;

[0016] Figure 2 This is a schematic diagram of the principle of a dual-modal tissue ablation device provided in another embodiment of this application;

[0017] Figure 3 This is a schematic diagram of the structure of the first electrode needle provided in an embodiment of this application;

[0018] Figure 4 A schematic diagram of the first pulse circuit provided in an embodiment of this application;

[0019] Figure 5 A schematic diagram of the first pulse switch circuit provided in an embodiment of this application;

[0020] Figure 6 A schematic diagram of the opto-isolation driving circuit provided in an embodiment of this application;

[0021] Figure 7 A schematic diagram of the opto-isolated driving circuit provided in another embodiment of this application;

[0022] Figure 8 A schematic diagram of a magnetically isolated power supply circuit provided in an embodiment of this application;

[0023] Figure 9 A schematic diagram illustrating the specific connection relationship between the magnetically isolated power supply circuit and the opto-isolated drive circuit provided in an embodiment of this application;

[0024] Figure 10 A schematic diagram of a first pulse switch circuit provided in another embodiment of this application;

[0025] Figure 11 A circuit diagram of a voltage equalization unit provided in an embodiment of this application;

[0026] Figure 12 A schematic diagram of the waveform conversion circuit provided in one embodiment of this application;

[0027] Figure 13 A schematic diagram of the output detection circuit provided in one embodiment of this application;

[0028] Figure 14 This is a schematic diagram of a temperature detection circuit provided in one embodiment of this application.

[0029] The above figures illustrate the following: 100, First pulse circuit; 110, Opto-isolated drive circuit; 111, Optocoupler unit; 112, Drive unit; 113, Delay unit; 120, Magnetic isolation power supply circuit; 121, Transformer; 122, Rectifier unit; 123, Voltage regulation unit; 130, First pulse switch circuit; 131, First switch branch; 132, Second switch branch; 140, Second pulse switch circuit; 150, Power switch; 160, Voltage equalization unit; 200, Second pulse circuit; 300, Waveform conversion circuit; 400, Signal switching circuit; 500, Output electrode; 510, First electrode needle; 511, Insulating sleeve. 512. Fixed needle tip; 513. Elastic needle tip; 514. Slide groove; 515. Insulated push button; 516. Discharge section; 520. Second electrode needle; 600. Main control circuit; 710. High voltage power supply circuit; 720. Working power supply circuit; 810. Output detection circuit; 811. Faraday current detection module; 812. Differential sampling module; 813. Voltage processing module; 814. High frequency sampling module; 820. Temperature detection circuit; 821. First temperature detection module; 822. Second temperature detection module; 823. First isolation communication module; 824. Second isolation communication module; 825. First thermocouple; 826. Second thermocouple. Detailed Implementation

[0030] To make the technical problems, technical solutions, and beneficial effects to be solved by this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and are not intended to limit the scope of this application.

[0031] It should be noted that when a component is referred to as being "fixed to" or "set on" another component, it can be directly on or indirectly on that other component. When a component is referred to as being "connected to" another component, it can be directly connected to or indirectly connected to that other component.

[0032] It should be understood that the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0033] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means two or more, unless otherwise explicitly specified.

[0034] Figure 1 A schematic diagram of the dual-modal tissue ablation device provided in one embodiment of this application is shown. For ease of explanation, only the parts relevant to this embodiment are shown, and are described in detail below:

[0035] A dual-modal tissue ablation device includes: a first pulse circuit 100, a second pulse circuit 200, a waveform conversion circuit 300, a signal switching circuit 400, and an output electrode 500.

[0036] The system includes a first pulse circuit 100 configured to generate and output a first pulse signal. A second pulse circuit 200 configured to generate and output a second pulse signal. A waveform conversion circuit 300 connected to the second pulse circuit 200 is configured to output a high-frequency resonant signal based on the second pulse signal. A signal switching circuit 400 connected to the first pulse circuit 100 and the waveform conversion circuit 300 is configured to receive the first pulse signal and the high-frequency resonant signal, and select to output either the first pulse signal or the high-frequency resonant signal. An output electrode 500 connected to the signal switching circuit 400 is configured to apply the signal output by the signal switching circuit 400 to a target tissue. The target tissue can be biological tissue. Both the first and second pulse signals can be bipolar high-frequency high-voltage pulse signals, and the high-frequency resonant signal can be a bipolar high-frequency high-voltage resonant signal.

[0037] When the first pulse signal is applied to the target tissue through the output electrode 500, the dual-mode tissue ablation device can perform irreversible perforation ablation on the target tissue. When the high-frequency resonant signal is applied to the target tissue, the dual-mode tissue ablation device can perform radiofrequency ablation on the target tissue. Therefore, the dual-mode tissue ablation device can switch the output signal through the signal switching circuit 400, thereby changing the tissue ablation mode and realizing dual-mode tissue ablation.

[0038] It should be noted that irreversible perforation ablation reduces the bioelectrical impedance of the target tissue. Switching to radiofrequency ablation in this situation can improve its efficiency. Furthermore, radiofrequency ablation can be used to supplement the ablation when irreversible perforation ablation has not completely removed the target tissue. Because irreversible perforation ablation offers high precision, while radiofrequency ablation has a wider ablation range, they complement each other, allowing for the selection of the appropriate ablation method based on specific needs.

[0039] like Figure 2 As shown, in this embodiment, the dual-modal tissue ablation device further includes a main control circuit 600, which is connected to the first pulse circuit 100 and the second pulse circuit 200 respectively. The main control circuit 600 is configured to control the operation of the first pulse circuit 100 and the second pulse circuit 200 to generate and output the first pulse signal and the second pulse signal respectively. The main control circuit 600 includes an industrial control computer, a single-chip microcomputer, or a microcontroller.

[0040] like Figure 2 As shown, in this embodiment, the output electrode 500 includes a first electrode needle 510 and a second electrode needle 520. The first electrode needle 510 is connected to the first output terminal of the signal switching circuit 400, and the second electrode needle 520 is connected to the second output terminal of the signal switching circuit 400. The first electrode needle 510 and the second electrode needle 520 are used to contact the target tissue and apply the first pulse signal and the high-frequency resonant signal to the target tissue.

[0041] It should be noted that radiofrequency ablation can be achieved with only one electrode needle, but irreversible perforation ablation requires two electrode needles. Therefore, the second electrode needle 520 of the first electrode needle 510 can simultaneously satisfy both ablation methods.

[0042] In this embodiment, the first electrode needle 510 can be a claw-shaped electrode needle. The claw-shaped electrode needle can expand the effective range of radiofrequency ablation.

[0043] The second electrode needle 520 can be either a claw-type electrode needle or a traditional single-needle electrode needle. This embodiment does not limit the type of the second electrode needle 520.

[0044] In another embodiment, the first electrode needle 510 and the second electrode needle 520 are both conventional single-needle electrode needles.

[0045] In this embodiment, the first electrode needle 510 can specifically be a single-layer claw-type electrode needle, such as... Figure 3 As shown, the first electrode needle 510 includes an insulating sleeve 511, a fixed needle tip 512, and several bent elastic needle tips 513. One end of the insulating sleeve 511 has an opening, and the other end has an electrode connection end for connecting to the signal switching circuit 400 via an insulated wire. The fixed needle tip 512 and the several bent elastic needle tips 513 are all installed at the opening of the insulating sleeve 511. The first end of the fixed needle tip 512 and the first end of each elastic needle tip 513 are electrically connected to the electrode connection end via an insulated wire. Specifically, the first end of the fixed needle tip 512 is fixed inside the insulating sleeve 511, and the second end of the fixed needle tip 512 extends a certain length along the axial direction of the insulating sleeve 511 from the opening of the insulating sleeve 511. The first end of each elastic needle tip 513 is mounted inside the insulating sleeve 511 via a corresponding sliding structure. The sliding structure controls the corresponding elastic needle tip 513 to slide along the axial direction of the insulating sleeve 511, so that the second end of the corresponding elastic needle tip 513 extends and retracts at the opening of the insulating sleeve 511. The number of elastic needle tips 513 can be set according to actual needs. In one example, there are a total of 4 elastic needle tips 513.

[0046] Specifically, the fixed needle tip 512 and each of the elastic needle tips 513 have a discharge portion 516 of 1 cm to 3 cm in length at their second ends. The surfaces of the fixed needle tip 512 and the elastic needle tips 513, except for the discharge portion 516, are covered with an insulating coating. In one example, the fixed needle tip 512 and each of the elastic needle tips 513 have a discharge portion 516 of 2 cm in length at their second ends. The surface of the insulating sleeve 511 is also covered with an insulating coating. The insulating coating can be a polyimide coating or a pyrene coating. The insulating coating prevents short circuits between the needle tips, and especially isolates the elastic needle tips 513 from the fixed needle tip 512.

[0047] When radiofrequency ablation is required, the corresponding elastic needle tip 513 can be controlled by a sliding structure to extend from the opening of the insulating sleeve 511. After extending from the insulating sleeve 511, the elastic needle tip 513 will return to its bent state, thus forming a claw-shaped electrode needle. When irreversible perforation ablation is required, the sliding structure can be controlled to retract each elastic needle tip 513 from the opening of the insulating sleeve 511, and irreversible perforation ablation can be performed only by fixing the needle tip 512. In the single-layer claw-shaped electrode needle, the potential of each elastic needle tip 513 and the fixed needle tip 512 is the same.

[0048] In this embodiment, the sliding structure includes several grooves 514 disposed on the sidewall of the insulating sleeve 511 and parallel to the axial direction of the insulating sleeve 511, and several insulating push buttons 515 corresponding one-to-one with each groove 514. Each insulating push button 515 is respectively installed in the corresponding groove 514 and fixed to the first end of the corresponding elastic needle tip 513, so as to control the sliding of the insulating push button 515 in the corresponding groove 514, thereby causing the corresponding elastic needle tip 513 to slide in the insulating sleeve 511, thereby controlling the extension and retraction of the second end of the elastic needle tip 513 at the opening of the insulating sleeve 511. The length of the groove 514 corresponds to the length that the second end of the elastic needle tip 513 can extend from the opening of the insulating sleeve 511. In one example, such as Figure 3 As shown, there are four elastic needle tips 513, four slide grooves 514, and four insulating push buttons 515 respectively installed in the four slide grooves 514. The four insulating push buttons 515 are respectively fixed to the first end of the corresponding elastic needle tip 513.

[0049] By controlling the sliding of the insulating push button 515 in the slide groove 514, the corresponding elastic needle tip 513 can be controlled to extend and retract. Each elastic needle tip 513 can be controlled individually to control the specific range of radiofrequency ablation according to the actual situation.

[0050] In another embodiment, unlike the above embodiment, the first electrode needle 510 can specifically be a double-layer claw-shaped electrode needle. The electrode connection ends of the first electrode needle 510 include a first connection end and a second connection end that are isolated from each other. The first connection end is electrically connected to the fixed needle tip 512 of the first electrode needle 510 and the first output end of the signal switching circuit 400 via insulated wires, respectively. The second connection end is electrically connected to each elastic needle tip 513 of the first electrode needle 510 and the second output end of the signal switching circuit 400 via insulated wires, respectively. The second electrode needle 520 is connected to the second output end of the signal switching circuit 400. In the double-layer claw-shaped electrode needle, the potential of each elastic needle tip 513 is the same, but the potentials of the elastic needle tip 513 and the fixed needle tip 512 may be different. Because the elastic needle tips 513 and the fixed needle tip 512 are isolated from each other, the first electrode needle 510 can not only achieve radiofrequency ablation but also irreversible perforation ablation. For example, the first electrode needle 510 can extend only one elastic needle tip 513. By cooperating with the fixed needle tip 512, irreversible perforation ablation can be achieved.

[0051] like Figure 4 As shown, specifically, the dual-modal tissue ablation device also includes a high-voltage power supply circuit 710 and a working power supply circuit 720. The high-voltage power supply circuit 710 provides the driving voltage, and the working power supply circuit 720 is used to provide the driving AC power.

[0052] In this embodiment, the second pulse circuit 200 has the same circuit structure as the first pulse circuit 100. As shown in Figure 4, taking the first pulse circuit 100 as an example, the first pulse circuit 100 includes several opto-isolated driving circuits 110, several magnetically isolated power supply circuits 120, a first pulse switch circuit 130, and a second pulse switch circuit 140. Both the first pulse switch circuit 130 and the second pulse switch circuit 140 include several power switches 150 connected in series between the high-voltage power supply circuit 710 and ground. The first pulse switch circuit 130 and the second pulse switch circuit 140 are configured to generate and output high-frequency high-voltage pulse signals V1 and V2 respectively by turning on or off the power switches 150, based on the driving voltage provided by the high-voltage power supply circuit 710 and under the control of the main control circuit 600. The high-frequency high-voltage pulse signals V1 and V2 can be phase-interleaved. By outputting the high-frequency high-voltage pulse signal V1 from the first pulse switch circuit 130 and the high-frequency high-voltage pulse signal V2 from the second pulse switch circuit 140 from two output terminals respectively, a bipolar high-frequency high-voltage pulse signal can be obtained. This bipolar high-frequency high-voltage pulse signal is the first pulse signal. The generation process of the second pulse signal in the second pulse circuit 200 is similar to that of the first pulse signal.

[0053] The number of opto-isolated drive circuits 110 is equal to and corresponds one-to-one with the power switches 150 in this embodiment. Each opto-isolated drive circuit 110 is connected between the corresponding power switch 150 and the main control circuit 600. The opto-isolated drive circuit 110 is configured to control the corresponding power switch 150 to turn on or off according to the switch control signal output by the main control circuit 600. The opto-isolated drive circuit 110 can isolate the first pulse circuit 100, the second pulse circuit 200 and the main control circuit 600 from each other. The number of magnetically isolated power supply circuits 120 is equal to and corresponds one-to-one with the opto-isolated drive circuits 110. Each magnetically isolated power supply circuit 120 corresponding to the same pulse switch circuit is connected in series between the working power supply circuit 720 and the ground terminal. The magnetically isolated power supply circuit 120 is configured to supply power to the corresponding opto-isolated drive circuit 110 based on the driving AC power provided by the working power supply circuit 720.

[0054] This embodiment achieves isolation between the power switch 150, the high-voltage power supply circuit 710, the working power supply circuit 720, and the main control circuit 600 through the aforementioned opto-isolation drive circuit 110 and magnetic isolation power supply circuit 120. In particular, it isolates the high-voltage power supply circuit 710 from other circuits, allowing each power switch 150 to be controlled independently, unaffected by the high-voltage power supply circuit 710. Simultaneously, the opto-isolation drive circuit 110 has a fast response speed. By controlling the power switches 150 according to the switch control signals, it achieves electrical isolation while improving the synchronization rate between the various power switches 150.

[0055] Specifically, the second pulse switching circuit 140 has the same circuit structure as the first pulse switching circuit 130. For example... Figure 5As shown, taking the first pulse switch circuit 130 as an example, among the power switches 150 in the first pulse switch circuit 130, X power switches 150 are connected in series to form a first switch branch 131, and the remaining Y power switches 150 are connected in series to form a second switch branch 132. The first end of the first switch branch 131 is connected to the high-voltage power supply circuit 710, the second end of the first switch branch 131 is connected to the first end of the second switch branch 132, and the second end of the second switch branch 132 is connected to ground. The main control circuit 600 can synchronously control each power switch 150 in the first switch branch 131 to be turned on or off, and can synchronously control each power switch 150 in the second switch branch 132 to be turned on or off. For example, by controlling each power switch 150 in the first switch branch 131 to be continuously and simultaneously turned on or off, and controlling each power switch 150 in the second switch branch 132 to be simultaneously turned off when the first switch branch 131 is turned on, and controlling each power switch 150 in the second switch branch 132 to be simultaneously turned on when the first switch branch 131 is turned off, a corresponding high-frequency high-voltage pulse signal V1 is generated at the second end of the first switch branch 131. Here, X and Y are both natural numbers greater than 0, and the specific values ​​of X and Y can be determined according to the actual situation. X and Y can also be equal. In one embodiment, X and Y are both 3. The power switch 150 can be a metal-oxide-semiconductor field-effect transistor (MOSFET) or an insulated-gate bipolar transistor (IGBT). For example, in this embodiment, an NMOS transistor can be used. Figure 1 As shown, one of the power switches 150 is an NMOS transistor Q1. The first conducting terminal of the power switch 150 corresponds to the drain of the NMOS transistor, the second conducting terminal of the power switch 150 corresponds to the source of the NMOS transistor, and the control terminal of the power switch 150 corresponds to the source of the NMOS transistor.

[0056] like Figure 6 As shown, in this embodiment, each opto-isolated driving circuit 110 includes an opto-coupler unit 111. The number of opto-coupler units 111 is equal to that of the power switches 150 and they correspond one-to-one. The input terminal of each opto-coupler unit 111 can be connected to the main control circuit 600, and the output terminal of each opto-coupler unit 111 can be connected to the corresponding power switch 150. The opto-coupler unit 111 is used to transmit the switch control signal unidirectionally to the corresponding power switch 150 through photoelectric conversion.

[0057] Specifically, in this embodiment, the first pulse switch circuit 130 includes X+Y opto-isolated drive circuits 110 and X+Y opto-coupler units 111. Each opto-coupler unit 111 can be an optocoupler. Upon receiving a switch control signal and performing photoelectric conversion, the opto-coupler unit 111 transmits the switch control signal to the corresponding power switch 150 to control the power switch 150's on or off state. While achieving synchronous control of the power switch 150, the opto-coupler unit 111 also isolates the main control circuit 600 and the power switch 150, preventing the drive voltage from being transmitted to the main control circuit 600 and affecting the normal operation of both the main control circuit 600 and the power switch 150.

[0058] like Figure 7 As shown, in another embodiment, each opto-isolated driving circuit 110 further includes a driving unit 112. The number of driving units 112 is equal to that of optocoupler units 111 and they correspond one-to-one. Each driving unit 112 is connected between the output terminal of the corresponding optocoupler unit 111 (i.e., the optocoupler unit 111 in the same opto-isolated driving circuit 110) and the corresponding power switch 150. The driving unit 112 is configured to output a corresponding level to the corresponding power switch 150 according to the switch control signal output by the optocoupler unit 111, so as to control the power switch 150 to be turned on or off.

[0059] It should be noted that because the output power of the main control circuit 600 is relatively low, the output power of the optocoupler unit 111 is also relatively low, which may be insufficient to control the power switch 150 to turn on or off. Therefore, the drive unit 112 can output a corresponding level according to the control switch signal to control the power switch 150 to turn on or off. The drive unit 112 can be a MOSFET driver chip, which can output a corresponding level according to the switch control signal output by the optocoupler unit 111 to drive the power switch 150.

[0060] like Figure 7 As shown, in another embodiment, each opto-isolated driving circuit 110 further includes a delay unit 113. The number of delay units 113 is equal to that of optocoupler units 111, and they correspond one-to-one. Each delay unit 113 is connected between the input terminal of the corresponding optocoupler unit 111 (i.e., the optocoupler unit 111 in the same opto-isolated driving circuit 110) and the main control circuit 600, so as to adjust the time for the switch control signal to be transmitted to the optocoupler unit 111. Specifically, the delay unit 113 can be an RC delay circuit.

[0061] It should be noted that the main control circuit 600 is connected to each opto-isolated drive circuit 110 via transmission lines. However, due to differences in the length of the transmission lines or the different timing of the switch control signals output from different interfaces of the main control circuit 600, the transmission time of the switch control signals from the main control circuit 600 to each opto-isolated drive circuit 110 varies, which can easily lead to the power switches 150 not being able to turn on or off synchronously. By configuring corresponding delay units 113 to adjust the transmission time of the switch control signals to the optocouplers 111, synchronous control of the power switches 150 can be achieved. For example, the shorter the transmission line between the opto-isolated drive circuit 110 and the main control circuit 600, the longer the delay time of the delay unit 113 of the opto-isolated drive circuit 110, ultimately ensuring that the transmission time of the switch control signals to each optocoupler 111 is the same.

[0062] like Figure 4 , Figure 8 As shown, in this embodiment, each magnetically isolated power supply circuit 120 includes a transformer 121 and a rectifier unit 122. The number of transformers 121 and rectifier units 122 is equal to the number of optocoupler units 111, and they correspond one-to-one. The primary winding of the transformer 121 of each magnetically isolated power supply circuit 120 corresponding to the same pulse switching circuit is connected in series between the working power supply circuit 720 and the ground terminal. The secondary winding of each transformer 121 is connected to the corresponding rectifier unit 122 (i.e., the rectifier unit 122 in the same magnetically isolated power supply circuit 120). Each rectifier unit 122 is connected to the corresponding opto-isolated drive circuit 110 to provide the corresponding working voltage to the corresponding opto-isolated drive circuit 110 based on the driving AC power provided by the working power supply circuit 720.

[0063] Transformer 121 and rectifier unit 122 are only used to provide operating voltage for the corresponding opto-isolated drive circuit 110. Even if transformer 121 has a low consistency problem, as long as the opto-isolated drive circuit 110 can work normally, it will not affect the normal turn-off of power switch 150. At the same time, powering the opto-isolated drive circuit 110 through magnetic isolation power supply circuit 120 can isolate the opto-isolated drive circuits 110 of different power switches 150 from each other.

[0064] Specifically, one of the rectifier units 122 includes a first diode D1, a second diode D2, a third diode D3, and a fourth diode D4. The anode of the first diode D1 is connected to the first terminal of the secondary winding of the transformer 121, and the cathode of the first diode D1 is connected to the operating voltage terminal. The anode of the second diode D2 serves as ground and is connected to the corresponding opto-isolated drive circuit 110, and the cathode of the second diode D2 is connected to the first terminal of the secondary winding. The anode of the third diode D3 is connected to the anode of the second diode D2, and the cathode of the third diode D3 is connected to the second terminal of the secondary winding of the transformer 121. The anode of the fourth diode D4 is connected to the second terminal of the secondary winding of the transformer 121, and the cathode of the fourth diode D4 is connected to the operating voltage terminal. The operating voltage terminal is used to connect to the corresponding opto-isolated drive circuit 110 to provide operating voltage to the corresponding opto-isolated drive circuit 110. While the rectifier unit 122 performs rectification, the ground terminals of each rectifier unit 122 are independent of each other, so that the magnetic isolation power supply circuits 120 are not connected to the same reference ground and remain isolated from each other. At the same time, the opto-isolated drive circuits 110 of different power switches 150 are in a floating isolation state, and the power switches 150 do not interfere with each other.

[0065] A voltage regulating unit 123 is also provided between the operating voltage terminal and the rectifier unit 122. The voltage regulating unit 123 is used to regulate the voltage output to the opto-isolated drive circuit 110. The voltage regulating unit 123 may include a voltage regulating resistor, such as... Figure 8 As shown, specifically, one of the voltage regulating units 123 includes a voltage regulating resistor R1, which is connected in series between the rectifier unit 122 and the corresponding operating voltage terminal.

[0066] In one example, such as Figure 9 As shown, the magnetically isolated power supply circuit 120 can be connected to the optocoupler unit 111 and the drive unit 112 in the corresponding optocoupler drive circuit 110 to supply power to the optocoupler unit 111 and the drive unit 112.

[0067] like Figure 10 As shown, in another embodiment, the first pulse switch circuit 130 further includes a plurality of voltage equalization units 160. The number of voltage equalization units 160 is equal to that of the power switches 150 and they correspond one-to-one. Each voltage equalization unit 160 is connected in parallel with the corresponding power switch 150 to adjust the voltage across each power switch 150.

[0068] In this embodiment, the voltage equalization unit 160 includes static voltage equalization resistors; the first end of the static voltage equalization resistor is connected to the first conducting end of the corresponding power switch 150, and the second end of the static voltage equalization resistor is connected to the second conducting end of the corresponding power switch 150. When all power switches 150 are turned off, the voltages across each power switch 150 are made equal through the static voltage equalization resistors. Specifically, as shown... Figure 11 As shown, one of the voltage equalization units 160 includes a resistor R4, which is a static voltage equalization resistor. The first end of the resistor R4 is connected to the first conducting end of the power switch 150, and the second end of the resistor R4 is connected to the second conducting end of the power switch 150.

[0069] In this embodiment, the voltage equalization unit 160 further includes a dynamic voltage equalization resistor and a dynamic voltage equalization capacitor; the first end of the dynamic voltage equalization resistor is connected to the first conducting end of the corresponding power switch 150, the second end of the dynamic voltage equalization resistor is connected to the first end of the dynamic voltage equalization capacitor, and the second end of the dynamic voltage equalization capacitor is connected to the second conducting end of the corresponding power switch 150. When the first pulse switching circuit 130 generates a corresponding high-frequency high-voltage pulse signal, the voltage on each power switch 150 in the same switching branch can be kept equal through the dynamic voltage equalization resistors and dynamic voltage equalization capacitors. Specifically, as shown... Figure 11 As shown, one of the voltage equalization units 160 includes a resistor R5 and a capacitor C1. The resistor R5 is a dynamic voltage equalization resistor, and the capacitor C1 is a dynamic voltage equalization capacitor. The first end of the resistor R5 is connected to the first conducting end of the power switch 150, the second end of the resistor R5 is connected to the first end of the capacitor C1, and the second end of the capacitor C1 is connected to the second conducting end of the power switch 150.

[0070] It should be noted that during the operation of the first pulse switching circuit 130, since several power switches 150 are connected in series, factors such as the parasitic parameters of the power switches 150 may cause uneven voltage distribution and uneven heating on each power switch 150, which may lead to thermal breakdown of some power switches 150. By controlling the voltage across each power switch 150 through the voltage equalization unit 160, the failure rate of the power switches 150 can be reduced and their service life can be improved.

[0071] In this embodiment, as Figure 12 As shown, specifically, the waveform conversion circuit 300 can be an LC resonant circuit. The waveform conversion circuit 300 includes a first inductor L1, a second inductor L2, and a filter capacitor C2. The first end of the first inductor L1 is connected to the first output terminal of the second pulse circuit 200, the first end of the second inductor L2 is connected to the second output terminal of the second pulse circuit 200, and the two ends of the filter capacitor C2 are respectively connected to the second ends of the first inductor L1 and the second end of the second inductor L2. Both ends of the filter capacitor C2 are connected to the signal switching circuit 400 for outputting a high-frequency resonant signal.

[0072] It should be noted that the circuit structure of the second pulse circuit 200 is the same as that of the first pulse circuit 100. The second pulse circuit 200 includes a third pulse switch circuit and a fourth pulse switch circuit. The circuit structures of the second pulse switch circuit 140, the third pulse switch circuit, and the fourth pulse switch circuit are all the same as those of the first pulse switch circuit 130. The output terminal of the third pulse switch circuit is the first output terminal of the second pulse circuit 200, and the output terminal of the fourth pulse switch circuit is the second output terminal of the second pulse circuit 200. Under the control of the main control circuit 600, the third pulse switch circuit and the fourth pulse switch circuit can output high-frequency high-voltage pulse signals V3 and V4 respectively. Combining the high-frequency high-voltage pulse signals V3 and V4 yields the second pulse signal. The waveform conversion circuit 300 can then generate and output a high-frequency resonant signal to the signal switching circuit 400 based on the second pulse signal for use in radio frequency ablation.

[0073] In this embodiment, as Figure 2 As shown, the dual-modal tissue ablation device also includes an output detection circuit 810. The output detection circuit 810 is disposed between the signal switching circuit 400 and the output electrode 500 and connected to the main control circuit 600. It is configured to collect the voltage applied to the target tissue through the output electrode 500 and the current flowing through the output electrode 500, generate and output a corresponding digital feedback signal to the main control circuit 600. The main control circuit 600 is also configured to obtain the electrochemical impedance parameters of the target tissue based on the digital feedback signal.

[0074] Specifically, such as Figure 13 As shown, the output detection circuit 810 includes a Faraday current detection module 811, a differential sampling module 812, a voltage processing module 813, and a high-frequency sampling module 814.

[0075] The Faraday current detection module 811 is located between the signal switching circuit 400 and the output electrode 500. It is configured to generate a corresponding sampling signal based on the current difference flowing through the first electrode needle 510 and the second electrode needle 520. The current difference corresponds to the Faraday current involved in the electrochemical reaction of the target tissue. The differential sampling module 812 is connected to the first and second output terminals of the signal switching circuit 400 and is configured to generate and output a first feedback voltage and a second feedback voltage based on the voltage changes at the first and second output terminals, respectively. The voltage processing module 813 is connected to the differential sampling module 812 and is configured to generate and output a voltage feedback signal based on the first and second feedback voltages. The voltage feedback signal corresponds to the voltage difference between the first and second output terminals. The high-frequency sampling module 814 is connected to both the voltage processing module 813 and the Faraday current detection module 811 and is configured to generate and output a corresponding digital feedback signal based on the voltage feedback signal and the sampling signal. The main control circuit 600 is connected to the signal switching circuit 400 and the high-frequency sampling module 814, respectively. It is configured to obtain the Faraday current and the voltage difference between the first and second output terminals based on the received digital feedback signal. Furthermore, it obtains the electrochemical impedance parameters of the target tissue based on the Faraday current, the voltage difference between the first and second output terminals, and a preset electrochemical impedance fitting function. These parameters are used to generate corresponding switching control signals to control the first pulse circuit 100 and the second pulse circuit 200. The electrochemical impedance fitting function can be obtained by fitting electrical parameters obtained during a pulsed electric field ablation simulation experiment based on an equivalent circuit model of the target tissue.

[0076] When the electrochemical impedance parameters of the target tissue obtained by the main control circuit 600 are abnormal, the main control circuit 600 can control the first pulse circuit 100 and the second pulse circuit 200, or control the signal switching circuit 400 to stop outputting signals, so as to stop tissue ablation and improve the safety of the dual-mode tissue ablation device.

[0077] In another embodiment, such as Figure 2 As shown, the dual-modal tissue ablation device also includes a temperature detection circuit 820, which is connected to the output electrode 500 and the main control circuit 600 respectively. The temperature detection circuit 820 is configured to detect the temperature of the output electrode 500 and output a corresponding temperature detection signal to the main control circuit 600.

[0078] Specifically, such as Figure 14As shown, the temperature detection circuit 820 includes a first temperature detection module 821, a second temperature detection module 822, a first isolation communication module 823, a second isolation communication module 824, a first thermocouple 825, and a second thermocouple 826. The first temperature detection module 821 is connected to the first thermocouple 825 in the first electrode needle 510 and is connected to the main control circuit 600 through the first isolation communication module 823. The second temperature detection module 822 is connected to the second thermocouple 826 in the second electrode needle 520 and is connected to the main control circuit 600 through the second isolation communication module 824. The first temperature detection module 821 is used to detect the temperature of the first electrode needle 510 through the first thermocouple 825 in the first electrode needle 510 and generate a corresponding temperature detection signal, and transmit the temperature detection signal to the main control circuit 600 through the first isolation communication module 823. The second temperature detection module 822 is used to detect the temperature of the second electrode needle 520 through the second thermocouple 826 in the second electrode needle 520 and generate a corresponding temperature detection signal, and transmit the temperature detection signal to the main control circuit 600 through the second isolation communication module 824.

[0079] The main control circuit 600 can determine the temperatures of the first electrode needle 510 and the second electrode needle 520 based on the received temperature detection signal. When the temperature of the first electrode needle 510 and the second electrode needle 520 is detected to be too high, the main control circuit 600 can control the first pulse circuit 100 and the second pulse circuit 200, or control the signal switching circuit 400 to stop outputting signals, thereby stopping tissue ablation and improving the safety of the dual-modal tissue ablation device. The main control circuit 600 can also control corresponding cooling equipment, such as controlling a peristaltic pump to water-cool the first electrode needle 510 and the second electrode needle 520 to reduce their temperatures.

[0080] Because the voltage values ​​of the first pulse signal and the high-frequency resonant signal are high, the first temperature detection module 821 and the second temperature detection module 822, which are isolated from each other, can prevent other circuits from being damaged by the high-voltage signal when a thermocouple is short-circuited and connected to a high-voltage signal.

[0081] It should be noted that the number of electrode pins in the output electrode 500 can be configured according to actual needs, and the output electrode 500 may include multiple electrode pins. The number of temperature detection modules in the temperature detection circuit 820 corresponds to the number of electrode pins. For example, in one example, the output electrode 500 has a total of 32 electrode pins, and correspondingly, the temperature detection circuit 820 has a total of 32 temperature detection modules and 32 isolation communication modules.

[0082] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional units and modules is merely an example. In practical applications, the above functions can be assigned to different functional units and modules as needed, that is, the internal structure of the device can be divided into different functional units or modules to complete all or part of the functions described above. The functional units and modules in the embodiments can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit. Furthermore, the specific names of the functional units and modules are only for easy differentiation and are not intended to limit the scope of protection of this application. The specific working process of the units and modules in the above system can be referred to the corresponding process in the foregoing method embodiments, and will not be repeated here.

[0083] In the above embodiments, the descriptions of each embodiment have different focuses. For parts that are not described in detail or recorded in a certain embodiment, please refer to the relevant descriptions of other embodiments.

[0084] The above-described embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application, and should all be included within the protection scope of this application.

Claims

1. A dual modality tissue ablation device, characterized by, include: The first pulse circuit is configured to generate and output a first pulse signal; The second pulse circuit is configured to generate and output a second pulse signal; A waveform conversion circuit, connected to the second pulse circuit, is configured to output a high-frequency resonant signal based on the second pulse signal; A signal switching circuit, connected to the first pulse circuit and the waveform conversion circuit, is configured to receive the first pulse signal and the high-frequency resonant signal, and select one of the first pulse signal and the high-frequency resonant signal to output. The output electrode, connected to the signal switching circuit, is configured to apply the signal output by the signal switching circuit to the target tissue to perform irreversible perforation ablation or radiofrequency ablation of the target tissue. The first pulse circuit includes multiple power switches and several voltage equalization units, for generating and outputting the first pulse signal based on the driving voltage by controlling the on and off states of each power switch. The number of voltage equalizing units is equal to the number of power switches and they correspond one-to-one. Each voltage equalizing unit is connected in parallel with the corresponding power switch to adjust the voltage across each power switch so that the voltage across each power switch is equal.

2. The dual-modal tissue ablation device as described in claim 1, characterized in that, The waveform conversion circuit includes a first inductor, a second inductor, and a filter capacitor. The first end of the first inductor is connected to the first output terminal of the second pulse circuit, and the first end of the second inductor is connected to the second output terminal of the second pulse circuit. The two ends of the filter capacitor are respectively connected to the second ends of the first inductor and the second inductor. Both ends of the filter capacitor are connected to the signal switching circuit for outputting the high-frequency resonant signal.

3. The dual-modal tissue ablation device as described in claim 1 or 2, characterized in that, The output electrode includes a first electrode needle and a second electrode needle. The first electrode needle is connected to the first output terminal of the signal switching circuit, and the second electrode needle is connected to the second output terminal of the signal switching circuit. The first electrode needle and the second electrode needle are used to contact the target tissue and apply the first pulse signal and the high-frequency resonant signal to the target tissue.

4. The dual-modal tissue ablation device as described in claim 3, characterized in that, The first electrode needle is a claw-shaped electrode needle.

5. The dual-modal tissue ablation device as described in claim 4, characterized in that, The first electrode needle includes an insulating sleeve, a fixed needle tip, and several curved elastic needle tips; One end of the insulating sleeve has an opening, and the other end of the insulating sleeve has an electrode connection end, which is used to connect to the signal switching circuit. The first end of the fixed needle tip and the first end of each elastic needle tip are electrically connected to the electrode connection end. The first end of the fixed needle tip is fixed inside the insulating sleeve, and the second end of the fixed needle tip extends a certain length from the opening of the insulating sleeve along the axial direction of the insulating sleeve. The first end of each elastic needle tip is installed inside the insulating sleeve through a corresponding sliding structure. The sliding structure is used to control the extension and retraction of the second end of the corresponding elastic needle tip at the opening of the insulating sleeve.

6. The dual-modal tissue ablation device as described in claim 5, characterized in that, The sliding structure includes a plurality of grooves disposed on the side wall of the insulating sleeve and parallel to the axial direction of the insulating sleeve, and a plurality of insulating push buttons corresponding to each groove. Each insulating push button is installed in the corresponding groove and fixed to the first end of the corresponding elastic needle tip, so as to control the sliding of the insulating push button in the corresponding groove, thereby causing the second end of the corresponding elastic needle tip to extend or retract at the opening of the insulating sleeve.

7. The dual-modal tissue ablation device as described in claim 1 or 2, characterized in that, It also includes a main control circuit, which is connected to the first pulse circuit and the second pulse circuit respectively. The main control circuit is configured to control the first pulse circuit and the second pulse circuit to generate and output the first pulse signal and the second pulse signal respectively.

8. The dual-modal tissue ablation device as described in claim 7, characterized in that, The second pulse circuit has the same circuit structure as the first pulse circuit.

9. The dual-modal tissue ablation device as described in claim 7, characterized in that, It also includes an output detection circuit, which is disposed between the signal switching circuit and the output electrode and connected to the main control circuit. The output detection circuit is configured to collect the voltage applied to the target tissue through the output electrode and the current flowing through the output electrode, generate and output a corresponding digital feedback signal to the main control circuit. The main control circuit is also configured to obtain the electrochemical impedance parameters of the target tissue based on the digital feedback signal.

10. The dual-modal tissue ablation device as described in claim 9, characterized in that, It also includes a temperature detection circuit, which is connected to the output electrode and the main control circuit respectively. The temperature detection circuit is configured to detect the temperature of the output electrode and output a corresponding temperature detection signal to the main control circuit. The main control circuit is also configured to obtain the temperature of the output electrode based on the temperature detection signal.

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