A pulsed ablation forceps, a pulsed ablation circuit, a pulsed ablation system and a control method thereof

Abstract

The application provides a kind of pulse ablation forceps, comprising: forceps body;Jaw part, it includes fixed jaw arm and movable jaw arm, two respectively have fixed surface and movable surface for clamping;Fixed jaw arm includes width direction interval setting, along the length direction of fixed jaw arm extending first electrode and second electrode, movable jaw arm includes width direction interval setting, along the length direction of movable jaw arm extending third electrode and fourth electrode;First electrode and second electrode and / or third electrode and fourth electrode are provided with insulating protrusion, and the height of protruding of insulating protrusion is greater than the protruding height of electrode;And electrode and insulating protrusion are at least partially protruding from fixed surface or movable surface, the cross section of the part of first electrode, second electrode, third electrode, fourth electrode relative to the protruding of fixed surface or movable surface is arc-shaped.The pulse ablation forceps of the application reduces the risk of arc generation in the ablation process, and improves the ablation effect.

Description

Technical Field

[0001] This invention relates to the fields of medical devices and cardiac ablation, and particularly to a pulse ablation clamp, a pulse ablation circuit, a pulse ablation system, and a control method for the pulse ablation system. Background Technology

[0002] Atrial fibrillation (AF) is the most common type of cardiac arrhythmia, characterized by irregular heartbeats. The prevalence of AF in the general population is 0.5% to 1.5%. There are approximately 33.5 million people with AF worldwide, including about 8 million in my country. AF patients have a very high risk of stroke. Stroke is a leading cause of death in China, and strokes caused by AF often present with more severe clinical manifestations, higher mortality rates, and a higher recurrence rate. Therefore, treatment for AF is urgent.

[0003] Currently, the main treatments for atrial fibrillation include tissue ablation, such as using ablation forceps to ablate myocardial tissue. During treatment, the jaws of the ablation forceps clamp the abnormal myocardial tissue, and cryo-energy, radiofrequency energy, or pulsed electric field energy are released into the myocardial tissue to ablate the tissue at a specific location. After ablation, the myocardial cells at the contact site die or undergo apoptosis, thus ceasing the generation or transmission of abnormal currents, and the onset of atrial fibrillation is suppressed.

[0004] Ablation based on cryo-energy and radiofrequency energy shares some similarities in principle: it destroys myocardial tissue cells at the contact site through freezing or burning, leading to cell death. As relatively mature ablation technologies, both offer advantages such as simple operation, adjustable energy, and wide applicability. However, both cryo-energy and radiofrequency energy cause indiscriminate damage to all cells within the myocardial tissue—including but not limited to cardiomyocytes, blood vessels, and nerves—and the extent of ablation damage is difficult to control.

[0005] To address the aforementioned drawbacks, the latest pulsed energy ablation technology exhibits its unique advantage in cell selectivity. During ablation, the ablation line is accurate, complete, and transmural. By releasing pulsed electric field energy into the clamped myocardial tissue, irreversible electroporation occurs on the cell membrane of the myocardial cells, thereby inducing spontaneous apoptosis. Pulsed electric field ablation overcomes the shortcomings of "thermal energy" ablation methods such as radiofrequency and cryotherapy, improving the safety of ablation in areas adjacent to blood vessels and nerves.

[0006] Currently, common pulse ablation forceps typically use sheet-shaped ablation electrodes, as shown in CN120227137A. During the discharge process, it was found that arcs often occur at the four corners and even the sides of the sheet-shaped electrodes of these pulse ablation forceps, posing a risk to the patient's treatment due to the problem of tip discharge.

[0007] Therefore, there is a need to provide a new pulse ablation clamp to address the safety issues during pulse ablation. Summary of the Invention

[0008] To overcome the aforementioned problems in the prior art, one aspect of the present invention provides a highly efficient and safe pulse ablation forceps, comprising: a forceps body; and a jaw portion, the jaw portion being mounted on the forceps body and consisting of a fixed forceps arm and a movable forceps arm parallel to the fixed forceps arm, the fixed forceps arm having a fixed surface for clamping, and the movable forceps arm having a movable surface opposite to the fixed surface for clamping, wherein the jaw portion clamps or releases the target ablated tissue by moving the movable forceps arm relative to the fixed forceps arm; characterized in that the fixed forceps arm includes a first electrode and a second electrode spaced apart in the width direction, the first electrode and the second electrode being parallel to the fixed forceps arm. The fixed clamp arm extends along its length, and the movable clamp arm includes a third electrode and a fourth electrode spaced apart along its width. The third electrode and the fourth electrode extend along the length of the movable clamp arm. An insulating protrusion is provided between the first electrode and the second electrode and / or between the third electrode and the fourth electrode. The height of the insulating protrusion is greater than the height of the electrode. Both the electrode and the insulating protrusion protrude at least partially from the fixed surface or the movable surface. The cross-section of the portion of the first electrode, the second electrode, the third electrode, and the fourth electrode protruding relative to the fixed surface or the movable surface is arc-shaped.

[0009] More preferably, in the pulse ablation clamp of the present invention, the cross-section of the portion of the insulating protrusion that protrudes relative to the fixed surface or the movable surface is arc-shaped.

[0010] More preferably, in the pulse ablation clamp of the present invention, the first electrode, the second electrode, the third electrode, and the fourth electrode are cylindrical electrodes.

[0011] More preferably, in the pulse ablation clamp of the present invention, the radius of curvature of the arcuate protrusions of the first electrode, the second electrode, the third electrode, and the fourth electrode is 0.5-6 mm.

[0012] More preferably, in the pulse ablation clamp of the present invention, the electrode ends of the first electrode and the second electrode extending along the length direction extend into the interior of the fixed clamp arm, and the electrode ends of the third electrode and the fourth electrode extending along the length direction extend into the interior of the movable clamp arm.

[0013] More preferably, in the pulse ablation forceps of the present invention, one or more insulating protrusions are provided on the same clamp arm, and one or more injection holes are provided along the length direction of the insulating protrusion in a direction perpendicular to the fixed surface and / or the movable surface, which are used to inject fluid into the clamped part.

[0014] More preferably, in the pulse ablation clamp of the present invention, the pulse ablation clamp further includes an infusion structure, which includes: an infusion line disposed in the clamp body, the infusion line being used to supply infusion liquid to the clamp jaws; and an infusion cavity disposed in the fixed clamp arm and / or the movable clamp arm, the infusion cavity being used to allow the infusion line to be in fluid communication with the infusion orifice.

[0015] More preferably, in the pulse ablation clamp of the present invention, the infusion structure further includes a stop valve spring and a stop valve core disposed in the infusion chamber, wherein the stop valve spring and the stop valve core are disposed in one or more sets corresponding to the infusion orifice, and at least a portion of the stop valve core protrudes from the insulating protrusion; wherein the stop valve core has one or more liquid outflow channels distributed around it; in the free state, the stop valve core is closed by the stop valve spring; in the state of being squeezed by the clamped target ablation tissue, the stop valve core moves and causes the infusion liquid to flow out of the infusion orifice through the liquid outflow channels.

[0016] More preferably, in the pulse ablation clamp of the present invention, the shut-off valve core includes: a base and a pin protruding relative to the base; wherein, the base includes an outer surface facing the infusion orifice, the outer surface being in contact with the inner surface of the infusion cavity in a free state to close the infusion orifice, and separating from the inner surface of the infusion cavity in a squeezed state; the pin passes through the infusion orifice and has one or more liquid outflow channels distributed on its outer periphery, the liquid outflow channels allowing the infusion liquid to flow out of the infusion orifice in the squeezed state of the shut-off valve core.

[0017] More preferably, in the pulse ablation clamp of the present invention, the outer surface of the insulating protrusion is formed with a microchannel that is recessed toward the interior of the insulating protrusion. Under the condition of being squeezed, the infusion liquid flows out from the infusion cavity through the infusion hole and flows along the microchannel.

[0018] More preferably, in the pulse ablation clamp of the present invention, the microchannel includes: a first microchannel extending along the length direction; and one or more second microchannels extending from the first microchannel to the outer surface of the electrode along the width direction; wherein the first microchannel is in fluid communication with the infusion orifice.

[0019] Another aspect of the present invention provides a pulse ablation system, comprising: a pulse ablation clamp as described above and a pulse ablation device electrically connected to the pulse ablation clamp.

[0020] More preferably, the pulse ablation system of the present invention includes the pulse ablation clamp as described above, and a pulse ablation device; the pulse ablation device includes: a perfusion pump for supplying perfusion fluid; an ablation device discharge module for controlling the delayed discharge of electrodes on the fixed clamp arm and / or the movable clamp arm; a pressure monitoring module for monitoring pressure changes in the perfusion line and outputting a monitored pressure signal based on the pressure changes; and an ablation device control unit for controlling the opening and closing of the perfusion pump and the ablation device discharge module; wherein the ablation device control unit controls the opening of the perfusion pump and the ablation device discharge module based on a received signal indicating a decrease in pressure in the perfusion line; and controls the closing of the perfusion pump and the ablation device discharge module based on a received signal indicating an increase in pressure in the perfusion line.

[0021] Another aspect of the present invention provides a control method for the aforementioned pulse ablation system, the method comprising: S1) monitoring of pressure reduction in the perfusion line: when the target ablation tissue is clamped between the fixed clamp arm and the movable clamp arm, the valve core of the shut-off valve is subjected to force, the perfusion orifice is opened, the pressure monitoring module detects the pressure reduction in the perfusion line, and outputs a pressure signal characterizing the pressure reduction; S2) starting the perfusion pump: based on the received pressure signal characterizing the pressure reduction, the ablation device control unit controls the perfusion pump to start, supplying perfusion fluid; S3) discharging the ablation electrode: based on the received... The pressure signal controls the ablation device discharge module to start, and the ablation device discharge module sends a delayed pulse signal to the electrodes on the fixed clamp arm and / or the movable clamp arm to initiate ablation of the target ablation tissue after a delay; S4) Monitoring of pressure rise in the infusion line: When the target ablation tissue is removed, the valve core of the shut-off valve loses its force, the infusion orifice closes, the pressure monitoring module detects the pressure rise in the infusion line, and outputs a pressure signal characterizing the pressure rise; S5) Shutting down the infusion pump: Based on the received pressure signal characterizing the pressure rise, the ablation device control unit controls the infusion pump to shut down, stopping the supply of infusion fluid.

[0022] Another aspect of the present invention provides a pulse ablation circuit, comprising: a pulse generating circuit including four insulated-gate bipolar transistors (IGBTs) arranged in a full-bridge configuration, the four IGBTs being electrically connected between a power supply terminal and a ground terminal; and a relay matrix electrically connected to the pulse generating circuit for switching ablation channels; wherein the emitter of the first IGBT and the collector of the third IGBT are connected to form terminal A, the emitter of the second IGBT and the collector of the fourth IGBT are connected to form terminal B, and the relay matrix is ​​electrically connected between terminal A and terminal B; the pulse ablation circuit further includes a residual voltage discharge circuit for discharging residual electrical energy in the pulse generating circuit after the IGBTs arranged in the full-bridge configuration are turned off.

[0023] The pulse ablation clamp of the present invention has the following technical effects: 1) The pulse ablation forceps of this invention employs an electrode with an arc-shaped cross-section at the contact surface with the target ablation tissue, including but not limited to cylindrical electrodes. Based on this, the surface of the working electrode that contacts the target ablation tissue always transitions smoothly, without any contact points where the curvature increases or decreases abruptly. During discharge, the charge is uniformly distributed on the surface of the working electrode. Thus, this invention effectively reduces the risk of arcing at the tip of the working electrode during ablation through hardware design. Even with relatively high ablation voltages, the pulse ablation forceps of this invention can ensure the safety of the ablation procedure.

[0024] 2) The pulse ablation clamp of the present invention has an arc-shaped insulating protrusion between the ablation electrodes to increase the creepage distance between the ablation electrodes without increasing the size of the ablation clamp. Ablation of target tissues, especially myocardial tissue, often requires the ablation clamp to be in a high-humidity environment. In this situation, a water film can easily form on the air or other physical insulating surfaces between the working electrodes, leading to unintended partial discharges or even insulation failure. The insulating protrusion of the present invention effectively isolates the air path between two adjacent working electrodes while increasing the path length between the two electrodes relative to the insulating surface of the clamp arm, effectively improving the safety of pulse ablation.

[0025] 3) The pulse ablation forceps of the present invention are equipped with a liquid infusion structure. An infusion conduit is disposed within the forceps body, supplying infusion liquid, typically saline, to the infusion chamber of the forceps jaws. When the target ablation tissue is clamped in the forceps jaws, air gaps easily form at the contact points between the tissue and the forceps arms. In this case, the infusion structure of the present invention can open the infusion port under tissue pressure, filling the air gaps between the target ablation tissue and the ablation electrode and insulating protrusions with the infusion liquid. This solves the problem of uneven electric field distribution on the ablation electrode caused by the aforementioned gaps, resulting in a high risk of arcing. Attached Figure Description

[0026] Figure 1 This is a schematic diagram of the overall structure of the pulse ablation forceps of the present invention; Figure 2 for Figure 1 Exploded view of the pulse ablation clamp in the image; Figure 3 for Figure 1 A partial enlarged view of the clamp arm structure of the pulse ablation forceps; Figure 4 This is a diagram showing the equipotential lines of the electric field intensity during electrode discharge for sheet-shaped electrodes and arc-shaped electrodes. Figure 5 This is a cross-sectional view of the clamp arm structure of a pulse ablation clamp according to one embodiment of the present invention; Figure 6 This is a cross-sectional view of the clamp arm structure of a pulse ablation clamp with insulating protrusions, according to another embodiment of the present invention. Figure 7 for Figure 6 A schematic diagram of the cross-sectional shape of the arc-shaped electrode of the pulse ablation clamp shown; Figure 8 for Figure 6 A schematic diagram of the cross-sectional shape of another arc-shaped electrode of the pulse ablation clamp shown; Figure 9 This is a schematic diagram of the closed-section of the infusion structure of the pulse ablation forceps in another embodiment of the present invention; Figure 10 for Figure 9 A schematic diagram of the open cross-section of the infusion structure of the pulse ablation clamp shown; Figure 11 for Figure 9 The shown is a cross-sectional view of the clamp arm structure along the long side of the pulse ablation clamp; Figure 12 This is a schematic diagram of the pulse ablation forceps arm of the present invention clamping myocardial tissue; Figure 13 for Figure 9 The diagram shows the equipotential lines of the electric field intensity during discharge of the same-side clamp arm electrode of the pulse ablation clamp. Figure 14 for Figure 9 The diagram shows the equipotential lines of the electric field intensity when the pulse ablation clamp is discharged at an angle to the electrode on the opposite side. Figure 15 for Figure 9 The diagram shows the equipotential lines of the electric field intensity when the opposite clamp arm of the pulse ablation clamp discharges to the electrode. Figure 16 for Figure 9 The isometric view of the microchannel on the insulating protrusion of the pulse ablation clamp shown. Figure 17 for Figure 16 The diagram shows the structure of the microchannel on the insulating protrusion. Figure 18 This is a flowchart of the ablation control method of the pulse ablation clamp of the present invention; Figure 19 This is a circuit simulation diagram of the core module of the pulse ablation device in one embodiment of the present invention; Figure 20 This is a simulation diagram of a residual voltage discharge circuit using a direct delay method; Figure 21 The discharge curve of the capacitor in the circuit when the residual voltage is directly discharged; Figure 22 The discharge curve of the capacitor when the residual voltage of the circuit is discharged through the PCB insulation resistor; Figure 23 This is a simulation diagram of a residual voltage discharge circuit that uses a fast discharge method; Figure 24 for Figure 23 The residual voltage discharge curve of the circuit shown is when the initial voltage is 500V. Figure 25 for Figure 23 The residual voltage discharge curve of the circuit shown is when the initial voltage is 1000V. Figure 26 for Figure 23 The residual voltage discharge curve of the circuit shown is when the initial voltage is 1500V. Figure 27 This is a simulation diagram of a residual voltage discharge circuit that uses a fast discharge method; Figure 28 This is a circuit simulation diagram with load voltage monitoring function. Detailed Implementation

[0027] definition Distal side: In this specification, when the term "distal side" is used to describe the device of the present invention, it refers to the side relatively away from the user. For the jaw portion of the present invention, "distal side" refers to the side away from the slide groove.

[0028] Proximal side: In this specification, when the term "proximal side" is used to describe the device of the present invention, it refers to the side relatively closer to the user. For the jaw portion of the present invention, "proximal side" refers to the side closer to the slide groove.

[0029] Distant end: In this specification, when the term "distant end" is used to describe the system or apparatus of the present invention, it generally refers to the end that is relatively far from the user. For the jaw portion of the present invention, "distant end" refers to the end that is far from the slide groove.

[0030] Proximal end: In this specification, when the term "proximal end" is used to describe the system or apparatus of the present invention, it generally refers to the end that is relatively closer to the user. For the jaw portion of the present invention, "proximal end" refers to the end closer to the slide groove.

[0031] Length direction: In this specification, when describing the jaw portion or related structures of the present invention, "length direction" refers to the direction extending along the end near the slide groove and the end away from the slide groove.

[0032] Width direction: In this specification, when describing the jaw portion or related structures of the present invention, "width direction" refers to the direction perpendicular to the aforementioned length direction in a plane perpendicular to the jaw body.

[0033] The terms "installation," "connection," "linking," and "fixing" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise explicitly defined. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0034] The term "electroporation" refers to applying an electric field to a cell membrane to alter its permeability to the extracellular environment. As used herein, the term "irreversible electroporation" refers to applying an electric field to a cell membrane to permanently alter its permeability to the extracellular environment. For example, cells subjected to irreversible electroporation may exhibit the formation of one or more pores in their cell membranes, which remain even after the electric field is removed.

[0035] Preferred embodiments of the present invention are described below with reference to the accompanying drawings. Those skilled in the art should understand that the embodiments or examples described below with reference to the drawings are only for illustrating the best ways to implement the present invention, and are not intended to limit the scope of the present invention to these embodiments. Various improvements and variations can be made to the present invention based on the following embodiments. All such improvements and variations are included within the scope of the present invention.

[0036] Figure 1 and Figure 2 This invention illustrates a pulse ablation forceps according to one embodiment of the present invention. It is a parallel push-pull type ablation forceps that uses pulse energy for ablation. It includes a forceps body and a jaw portion mounted on the forceps body, consisting of a fixed forceps arm 1 and a movable forceps arm 2 parallel to the fixed forceps arm 1. The jaw portion can clamp or release the target ablated tissue by moving the movable forceps arm 2 relative to the fixed forceps arm 1. The forceps body includes a groove, with the fixed forceps arm 1 fixedly connected to the distal end of the groove. The movable forceps arm 2 can slide up and down along the groove when the handle is gripped, moving closer to or further away from the fixed forceps arm 1. Compared to scissor-type clamp arms, the clamp arms of this invention can more easily hold the target ablated tissue between the two clamp arms. The fixed clamp arm 1 is located at a more distal end than the movable clamp arm 2. The target ablated tissue is controlled between the fixed clamp arm 1 and the movable clamp arm 2 and is supported by the fixed clamp arm 2. When the movable clamp arm 2 is pushed to clamp the target ablated tissue, the change in the target ablated tissue is mainly controlled at the relatively proximal end (the end closer to the movable clamp arm 2), which can be more easily observed by the operator, thereby visually perceiving whether the tissue is clamped.

[0037] The structure that moves the movable jaw 2 closer to or further away from the fixed jaw 1 along the slide groove is known and easily implemented by those skilled in the art. For example, CN102198012A and CN120227137A both disclose that the movable jaw is moved closer to or further away from the fixed jaw by a push rod. This invention does not limit this.

[0038] As an example only, the present invention provides the following structure: the pulse ablation forceps of the present invention includes a fixed forceps arm 1, a movable forceps arm 2, a support tube 3, and a handle 4. After the pulse ablation forceps are assembled, the support tube 3 is connected to the handle 4 and extends distally, and the support tube 3 is provided with a sliding groove. The handle 4 includes a handle housing, a push rod 5, a button 6, a cable 7, a button spring 8, and a push rod spring 9. The handle 4 is provided with a grip portion, which may be provided with anti-slip texture to increase friction for easy gripping. The grip portion is configured to cooperate with the handle housing, push rod 5, and push rod spring 9 for the operator's use. During use, the operator's palm contacts the grip portion, and the fingers press the handle housing. The palm force pushes the push rod 5, thereby moving the movable forceps arm 2 and locking the pulse ablation forceps. The push rod 5 is partially exposed outside the handle housing and passes through the handle housing to connect with the support tube 3. Pushing the push rod 5 will cause the inner tube of the support tube 3 (not shown in the figure) to move, thereby moving the movable forceps arm 2 relative to the fixed forceps arm 1. The push rod 5 includes a push handle (not shown in the figure) for moving the movable clamp arm 2 and a return spring (not shown in the figure). During the movement of the movable clamp arm 2 from the proximal side to the distal side, i.e., during the pushing process of the movable clamp arm 2 from away from the fixed clamp arm 1 to near the fixed clamp arm 1, the push rod spring 9 is compressed, while the return spring is stretched. In one embodiment of the invention, the handle housing is also provided with a button 6, which includes a fixed-position limiting post structure, and a corresponding limiting part and a release part (not shown in the figure) are provided on the push rod 5. From the time the movable clamp arm 2 of the pulse ablation forceps is in a free state until the push rod 5 is pushed to the preset position, the button 6 is always in the corresponding hole in the handle housing and cannot pop out of the handle housing. When the push rod 5 is pushed to the preset position, the limiting post structure of the button 6 slides past the limiting part to reach the release part. At this time, the button 6 is ejected from the handle housing by the elastic force of the button spring 8, thereby forming a limiting position. At this time, the pulse ablation forceps becomes a limited and fixed state and is locked. In the above embodiment, the return spring of the push rod 5 is connected to the handle housing and the inner tube of the support tube 3, providing the elastic force required for the inner tube to rebound. The push rod spring 9 abuts against the end of the handle 4 away from the support tube 3, and can still provide a constant rebound force within a certain range after the button 6 provides the limit, thereby solving the problem of clamping and ablation of cardiac tissue of different thicknesses. The operator does not need to worry about the surgical difficulties caused by the difference in the thickness of the heart wall of each patient, effectively reducing the difficulty of the operation and protecting the tissue to be ablated of different thicknesses from damage by the clamping force. At the same time, it can form a surface that effectively adheres to the tissue to be ablated. After the ablation is completed, the operator presses the button 6, and the movable clamp arm 2 automatically pushes back the support tube 3 under the action of the double spring structure, returning to the initial position, so that the ablation of the next position can be performed. After the button 6 locks into the handle 4 to form an automatic limit, under the action of the double spring structure, the thickness of the clamping object between the fixed clamp arm 1 and the movable clamp arm 2 can be between 0 and 20 mm. In this invention, the clamping force between the movable clamp arm 2 and the fixed clamp arm 1 is provided by the elastic force of the push rod spring 9 and the return spring.Furthermore, in other embodiments of this application, button 6 is a starting device. In this embodiment, handle 4 may also include a rotating device disposed within the handle housing. This rotating device is an electric device activated by button 6. After being activated by pressing button 6, the electric device pushes the movable clamp arm 2 to move until the reaction pressure from the push rod spring 9 and the return spring on the movable clamp arm 2 reaches a preset value. After ablation is completed, pressing button 6 again will cause the rotating device to move in the opposite direction, driving the movable clamp arm 2 away from the fixed clamp arm 1. In addition, handle 4 includes a connecting cable for connecting an external ablation device to achieve electrical connection.

[0039] The support tube 3 extends the length of the ablation forceps, facilitating insertion of the forceps arms into the human body for operation. It includes an inner tube, an outer tube, and a sliding groove. The outer tube is fixedly connected to the handle housing, and the sliding groove is fixed to the distal end of the outer tube. The sliding groove is an open component consisting of two side walls and an inner wall connecting the two side walls. One side of the fixed forceps arm 1 and the movable forceps arm 2 enters through the opening and connects to the sliding groove. Perpendicular to the outer tube, there is a certain distance from the opening of the sliding groove to its inner wall, giving the sliding groove depth to accommodate the fixed forceps 1 and the movable forceps 2. Along the direction of extension of the outer tube, the sliding groove has a certain length to accommodate the sliding of the inner tube and the movable forceps arm 2. The fixed forceps arm 1 is fixedly connected to the distal end of the sliding groove, the outer tube is sleeved over the inner tube, and the inner tube can move relative to the outer tube. The movable forceps arm 2 is fixed to the distal end of the inner tube. The inner tube is connected to a push rod 5 and can move relative to the outer tube under the action of the push rod 5. The movement of the inner tube relative to the outer tube causes the movable clamp arm 2 to slide in the groove, and the movable clamp arm 2 moves parallel to the fixed clamp arm 1. Furthermore, the inner and outer tubes can be made of metal-shaped flexible tubing, and the doctor can manually adjust the bending shape according to the specific tissue structure location to adapt to various surgical conditions.

[0040] like Figure 2 and Figure 3 As shown, the fixed clamp arm 1 and the movable clamp arm 2 can be configured as straight lines of the same length. Besides the shape described above, any suitable shape can be used according to actual needs, as long as the fixed clamp arm 1 and the movable clamp arm 2 are parallel and capable of clamping the target tissue for ablation. In one embodiment, the length of the fixed clamp arm 1 and the movable clamp arm 2 along the length direction of the jaws can be 5-10 cm. Furthermore, the fixed clamp arm 1 and the movable clamp arm 2 have the same angle relative to the plane of the handle housing, which can be 90-120°.

[0041] The following is for reference Figure 3 The structure of the fixed clamp arm 1 and the movable clamp arm 2 of the present invention will be explained. For example... Figure 3As shown, the pulse ablation forceps of the present invention includes a fixed forceps arm 1 and a movable forceps arm 2 disposed opposite to each other. In the following description, the direction of the opposing surfaces of the fixed forceps arm 1 and the movable forceps arm 2 is the inside of the jaw portion, and vice versa. The opposing surfaces of the fixed forceps arm 1 and the movable forceps arm 2 are the fixed surface and the movable surface, respectively. The fixed forceps arm 1 includes a fixed forceps arm main body portion 11 located opposite to the outside and a fixed forceps arm insulating portion 12 located opposite to the inside. The fixed forceps arm main body portion 11 has a groove (such as... Figure 5 As shown), the insulating portion 12 of the fixed clamp arm is at least partially disposed within the groove, thereby fixing it to the fixed clamp arm body 11. The movable clamp arm 2 includes a movable clamp arm body 21 located on the outside and a movable clamp arm insulating portion 22 located on the inside. The movable clamp arm body 21 also has a groove (as shown). Figure 5 As shown, the insulating part 22 of the movable clamp arm is at least partially disposed within the groove, thereby fixing it to the movable clamp arm body 21. There are no strict restrictions on whether the fixed clamp arm body 11 and the movable clamp arm body 21 are made of insulating material. The insulating parts 12 and 22 should be made of insulating material, and their opposing surfaces respectively cover the inner surfaces of the fixed clamp arm body 11 and the movable clamp arm body 21. That is, when the jaws are closed, the target ablation tissue is clamped between the fixed clamp arm 1 and the movable clamp arm 2, and the fixed clamp arm body 11 and the movable clamp arm body 21 do not contact the target ablation tissue.

[0042] Existing pulse ablation clamps often use sheet-shaped or strip-shaped electrodes, and the electric field intensity is not uniformly distributed during the discharge process. Figure 4 The diagram shows the equipotential line distribution of the electric field intensity during electrode discharge for a sheet electrode in the prior art and an arc-shaped electrode of the present invention. Figure 4 In the diagram, the boundary lines of different colored regions are contour lines of electric field intensity. The electric field intensity is equal along the same line, and the variation in the spacing between different lines reflects the change in electric field intensity. For example... Figure 4 Distribution in Figure I As shown, due to the abrupt curvature edges of the sheet-like or strip-shaped electrodes (13', 14'), the charge distribution density is greater at these edges than at other edges, causing the electric field intensity equipotential lines to narrow sharply at the edges, i.e., as the distribution... Figure I As shown at point P, the equipotential lines of the electric field intensity are significantly denser. In contrast, this problem does not exist for the arc-shaped or cylindrical electrodes. Under the same conditions, the distribution of the electric field intensity equipotential lines for the arc-shaped or cylindrical electrodes (13, 14) is shown below. Figure 4 Distribution in Figure IIAs shown, since there are no boundary lines with abrupt increases or decreases in curvature, the charge distribution is relatively uniform, the changes in the equipotential lines of the electric field intensity always tend to be gradual, and the distribution of the electric field intensity is always relatively dispersed. During pulse ablation, the tip discharge of the ablation electrode poses the following risks: 1. According to J=σE (where σ is the conductivity and E is the electric field strength), the current density J increases synchronously at the narrowing region P of the line. The high current density region may generate significant Joule heating, leading to local overheating or carbonization of the ablated tissue. 2. Local overheating during ablation can cause tissue dehydration and further carbonization. Carbon is a semiconductor with a conductivity much lower than that of biological tissue. The increased resistance in the carbonized area forces the current to concentrate in the surrounding uncarbonized tissue, further increasing the current density in these areas and forming a thermo-electric positive feedback. The carbonized area continues to expand, losing the advantage of pulsed electric field ablation (tissue selectivity) and indiscriminately ablating the tissue near the electrode. 3. When the water in the tissue is heated, it vaporizes to form steam and microbubbles. The rupture of the microbubbles causes the electrode to separate from the tissue, creating an air gap. The air gap is equivalent to a low dielectric constant medium, and the electric field strength at the interface will increase dramatically. When the electric field strength is greater than the breakdown threshold of the air gap, the air gap will be ionized to form a plasma channel (electric arc). 4. After carbonization, the electrical conductivity of the tissue decreases, and the charge cannot diffuse in time, forming a local high electric field. If it exceeds a certain threshold, there is a risk of generating an electric arc.

[0043] Based on the above problems, the present invention improves the design by setting a pulse ablation electrode with an arc-shaped cross-section. Figure 5-6 It shows along Figure 3 Section a shows a cross-sectional view of the pulse ablation clamp of the present invention. Figure 5 As shown, from a relative positional perspective, the fixed clamp arm 1 is located on the lower side, and the movable clamp arm 2 is located on the upper side. The insulating portion 12 of the fixed clamp arm and the insulating portion 22 of the movable clamp arm are respectively disposed within the grooves of the main body portion 11 of the fixed clamp arm and the main body portion 21 of the movable clamp arm. A first groove and a second groove are formed on the insulating portion 12 of the fixed clamp arm. A first electrode 13 is disposed in the first groove, and a second electrode 14 is disposed in the second groove. A third groove and a fourth groove are formed on the insulating portion 22 of the movable clamp arm. A third electrode 23 is disposed in the third groove, and a fourth electrode 24 is disposed in the fourth groove. The aforementioned first electrode 13, second electrode 14, third electrode 23, and fourth electrode 24 are all spaced apart from each other along the width direction.

[0044] exist Figure 5-6In the illustrated embodiment, the first electrode 13, second electrode 14, third electrode 23, and fourth electrode 24 of the present invention are all cylindrical electrodes, and all four have the same length and size. In this case, viewed from the cross-sectional angle of the first groove, second groove, third groove, and fourth groove, all four are arc-shaped grooves matching the shape of the electrodes, and all have the same length and size. Setting the electrodes and grooves to have the same shape, length, and size ensures that the area available for energy release by the four electrodes is equal, resulting in more uniform energy release, improved stability and safety, and convenient monitoring and optimization of energy release. However, it should be understood that the above setting of equal shape, length, and size of the electrodes and grooves is only for design convenience and can be different in other embodiments to suit target tissues or special cases with different shapes and locations. For example, in another embodiment of this application, the overall length of the first electrode 13, second electrode 14, third electrode 23, and fourth electrode 24 can be different, as long as the length exposed outside the fixed clamp arm 1 and / or the movable clamp arm 2—that is, the portion used for energy release (preferably pulse energy)—is set to be the same. The length and size of the first, second, third, and fourth grooves are set according to the size of the corresponding electrodes.

[0045] exist Figure 5-6 In the illustrated embodiment, the cylindrical electrodes are partially embedded in their respective grooves. The portion protruding from the fixed and movable surfaces has a semi-circular arc-shaped cross-section along the length of the fixed clamp arm 1 or the movable clamp arm 2. The cross-sections of the first, second, third, and fourth grooves corresponding to the first electrode 13, second electrode 14, third electrode 23, and fourth electrode 24, respectively, are also semi-circular arc-shaped. However, in other embodiments of the present invention, the first electrode 13, second electrode 14, third electrode 23, and fourth electrode 24 can be embedded in their respective grooves at any depth, and the groove depth and shape can be adjusted accordingly based on the portion protruding from the fixed and movable surfaces. Furthermore, the radius of curvature of the arc-shaped protruding portion of the electrodes of the present invention can be selected from 0.5 to 6 mm according to actual needs. Preferably, this radius of curvature can be set to 1.5 mm.

[0046] The ablation electrode of the present invention can also be in a non-cylindrical shape. See below for reference. Figure 7-8 Another embodiment of the present invention will be described in comparison. Figure 7 The first electrode 13a, the second electrode 14a, the third electrode 23a, and the fourth electrode 24a all use cylindrical electrodes. Figure 8 The first electrode 13b, second electrode 14b, third electrode 23b, and fourth electrode 24b shown have an arc-shaped cross-section on one side of their internal ablation clamp protruding from the fixing surface and the opposite surface. The shape of the portion embedded in the first, second, third, and fourth grooves on the external side is not particularly limited; for example, it can be selected as follows: Figure 8The rectangle shown. The first, second, third, and fourth grooves on the insulating part can be designed as grooves that match the shape of the electrode. That is, for the pulse ablation forceps of the present invention, the surface used to contact the target ablation tissue should be a smoothly transitioned surface, while the other side can be selected by those skilled in the art according to factors such as technical purpose and processing conditions.

[0047] Furthermore, since the first electrode 13 and the second electrode 14 extend along the length direction of the fixed clamp arm 1, and the third electrode 23 and the fourth electrode 24 extend along the length direction of the movable clamp arm 2, in order to ensure that the edges of the electrodes do not contact the target ablated tissue, both ends of the electrodes extend into the interior of the fixed clamp arm 1 and the movable clamp arm 2 in the length direction (e.g., Figure 3 As shown, the clamp arm is covered by an electrically insulating shell for electrical insulation. That is, regardless of whether a cylindrical electrode is used ( Figure 5-7 The embodiment shown is still an irregularly shaped arc electrode. Figure 8 In the embodiment shown, the boundary lines at both ends of the electrode extending along its length are not exposed in the jaws and do not contact the target ablated tissue.

[0048] Based on the aforementioned technical solution of the present invention, during the discharge process, the protruding / sharp parts of the exposed structure of the ablation electrode are completely eliminated at the structural level, thereby effectively avoiding the generation of tip discharge during the ablation process. Furthermore, since the pulse ablation electrode of the present invention does not contain sheet-like or strip-like structures, and has no sharp parts in contact with the target ablated tissue, the charge distribution on the electrode surface is uniform. Even under relatively large voltages (e.g., 1500V and above), tip discharge is less likely to occur as the voltage increases. Additionally, since "curvature" is a relative concept, the side edges at both ends of a cylindrical electrode in the length direction are more prone to tip discharge compared to smooth side surfaces. Based on this, the pulse ablation clamp of the present invention designs the two ends of the electrode to be covered by an electrically insulating shell consisting of a fixed clamp arm and a movable clamp arm. The side edges at both ends of the electrode are not exposed and do not serve as discharge parts, reducing the probability of tip discharge and improving safety.

[0049] like Figure 5-6 In the pulse ablation clamp, when the target ablation tissue is clamped between the fixed clamp arm 1 and the movable clamp arm 2, the electrode surfaces do not have 'points' with abrupt increases or decreases in curvature within the area in contact with the tissue, effectively reducing the risk of tip discharge. However, at this time, because the first electrode 13, the second electrode 14, the third electrode 23, and the fourth electrode 24 protrude from the fixed surface and the movable surface respectively, a gap caused by the hardware structure will be generated between the clamped target ablation tissue and the first electrode 13 and the second electrode 14. This gap also exists between the clamped target ablation tissue and the third electrode 23 and the fourth electrode 24. Figure 5 As shown in region W, during the ablation process, fluids such as blood and tissue fluid are generated and accumulate here. Generally, the impedance of blood and tissue fluid is lower than that of myocardial tissue. The fluid accumulated in region W easily forms a low-resistance parallel path with the adjacent electrode relative to the target ablated tissue. During discharge, current flows through the relatively lower impedance blood or tissue fluid, which can result in insufficient electric field strength in the target ablated tissue, leading to incomplete ablation. Furthermore, a large current flowing through the blood can easily cause it to coagulate due to heat, potentially forming a thrombus.

[0050] To solve the above-mentioned technical problems, in another embodiment of the present invention, the fixed clamp arm 1 and the movable clamp arm 2 further include an insulating protrusion. See below for reference. Figure 6 Describe the structure of the insulating protrusion. For example... Figure 6 As shown, at least one insulating protrusion 121 extending along the length of the fixed clamp arm 1 is provided between the first electrode 13 and the second electrode 14, which are spaced apart along the width direction on the fixed clamp arm 1. At least one insulating protrusion 221 extending along the length of the movable clamp arm 2 is provided between the third electrode 23 and the fourth electrode 24, which are spaced apart along the width direction on the movable clamp arm 2. The insulating protrusion 121 is formed by the fixed clamp arm insulating portion 12 between the first electrode 13 and the second electrode 14, and the insulating protrusion 221 is formed by the movable clamp arm insulating portion 22 between the third electrode 23 and the fourth electrode 24. The cross-section of the insulating protrusion 121 and the insulating protrusion 221 in the clamp arm length direction is arc-shaped. When the target ablation tissue is clamped between the fixed clamp arm 1 and the movable clamp arm 2, the insulating protrusion 121 and the insulating protrusion 221 can lift up the target ablation tissue that was originally suspended and laid flat between the first electrode 13 and the second electrode 14, and between the third electrode 23 and the fourth electrode 24. In addition, such as Figure 6 In the illustrated embodiment, the heights of the first electrode 13 and the second electrode 14 protruding from the fixed surface, and the heights of the third electrode 23 and the fourth electrode 24 protruding from the movable surface, are both h. The heights of the insulating protrusion 121 protruding from the fixed surface and the insulating protrusion 221 protruding from the movable surface are both H. It should be understood that the value of the height H of the insulating protrusion is greater than the value of the height h of the electrode. Preferably, the difference between the value of the height H of the insulating protrusion and the value of the height h of the electrode is less than 1 mm.

[0051] The aforementioned insulating protrusions 121 and 221 are both made of electrically insulating material. Their arrangement significantly increases the creepage distance between adjacent working electrodes on the same clamp arm. Specifically, creepage distance refers to the shortest path measured along the insulating surface between two conductive parts or between a conductive part and the equipment's protective interface. In high-humidity environments, even normally electrically insulating surfaces such as air or other physical structures between the working electrodes can form a water film. As the voltage of the working electrodes increases, the formation of this water film can easily lead to unintended partial discharges or even insulation failure. Figure 5 In the illustrated embodiment, no insulating protrusions are provided between the first electrode 13 and the second electrode 14, or between the third electrode 23 and the fourth electrode 24. In this case, the straight-line distance L (shortest distance) between the insulating portions of adjacent electrodes on the same side of the clamp arm is the creepage distance. Due to limitations such as the application scenario and the target ablation location, this creepage distance cannot be increased by increasing the width of the clamp arm. However, in… Figure 6 In the illustrated embodiment, the creepage distance between adjacent electrodes on the same side clamp arm is increased from the straight-line distance L between the electrodes to the arc length ⁀L of the upper surface of the insulating protrusion. The original distance L could not achieve electrical conduction due to the presence of the insulating protrusion; therefore, the new shortest distance between them must pass through the outer edge of the insulating protrusion. In this case, without increasing the clamp arm width, the added insulating protrusion effectively increases the creepage distance between the ablation electrodes. Compared to... Figure 5 In the embodiment shown, all other things being equal, the jaws with the insulating protrusions have significantly higher security.

[0052] To better prevent the formation of a water film on the surface of the insulating structure, in another embodiment of the invention, the insulating protrusion is further provided with a hydrophobic coating, which covers the arc-shaped upper surface of the insulating protrusion, such as... Figure 6 The hydrophobic coating 15 on the insulating protrusion 121 and the hydrophobic coating 25 on the insulating protrusion 221 are shown. The coating material of this hydrophobic coating can be a fluorinated polymer, etc., which can further reduce the surface energy of the insulating protrusion. Due to the arc-shaped structure design of the insulating protrusion and the presence of the hydrophobic coating thereon, the blood, tissue fluid, and other liquids that originally accumulated or flowed in area W form a high contact angle on the arc-shaped surface of the insulating protrusion. During the contact with the working surface of the ablation forceps, the above-mentioned liquids form "water droplets" and are difficult to form a continuous electrically conductive liquid film (water film), further ensuring that the insulating area between the electrodes can maintain effective electrical insulation even in a humid environment.

[0053] To achieve a more uniform distribution of the ablation electric field, in another embodiment of the present invention, the pulse ablation clamp is provided with an infusion structure, as described below. Figure 9-11 The grouting structure is described.

[0054] like Figure 9 and 11 The pulse ablation clamp shown has one or more injection holes along its length on the arc-shaped protrusions of the insulating protrusions 121 and 221, and an injection cavity (e.g., [missing information]) extending along its length within the insulating protrusions 121 and 221. Figure 11 (The location of the saline solution N filling position is shown). The infusion port extends through the insulating protrusions 121 and 122 in a direction perpendicular to the fixed and movable surfaces of the clamp arm, and the internal infusion chamber is in fluid communication with the external space through the infusion port. The clamp body of the pulse ablation clamp includes a cable 7, within which are infusion lines 71 and 72, respectively in fluid communication with the infusion chamber in the insulating protrusion 121 and the infusion line 72, respectively in fluid communication with the infusion chamber in the insulating protrusion 221. The infusion lines 71 and 72 are respectively used to connect with the infusion pump installed in the pulse ablation device or other external devices, and to supply infusion fluid to the infusion chamber during the ablation process. The infusion fluid used is usually physiological saline. The purpose of the infusion chamber in the clamp arm is to accumulate infusion fluid and to achieve fluid communication between the infusion lines 71 and 72 and the infusion port and the space between the external clamp arm, and its form is not limited to the above-mentioned integral through-type form. In another embodiment of the present invention, through holes can be provided at corresponding positions of the insulating protrusions for each injection hole. By providing and extending injection pipelines, each injection hole and its corresponding injection pipeline are fluidly connected. Each injection pipeline is bundled into a cable in the sliding groove of the clamp body and is fluidly connected to the injection pump described later.

[0055] In addition to the aforementioned injection pipeline and injection chamber, the injection structure of the present invention also includes a stop valve core and a stop valve spring. Figures 9 to 11 The structure of the shut-off valve spool and shut-off valve spring is shown. (As...) Figures 9 to 11 As shown, the insulating protrusion 121 of the clamp arm 1 has a through-hole filling chamber. Along the length of the clamp arm, one or more sets of shut-off valve cores 16a and shut-off valve springs 17a are spaced apart within the filling chamber, their positions and numbers corresponding to one or more filling holes of the aforementioned insulating protrusion. (Reference) Figure 9 , 11The shut-off valve cores 16a and 16b include a pin 161 and a base 162, with the pin 161 protruding from the base 162. The base 162 has an upper side facing inward and a lower side facing outward; the upper side has an outer surface 1621, and the lower end has an inwardly recessed inner cavity 1622. The pin 161 has one or more liquid outflow channels 1611 along its outer circumference. One end of the shut-off valve spring 17a abuts against the bottom of the filling chamber within the insulating portion 12 of the fixing clamp arm, and the other end abuts against the inner cavity 1622 of the shut-off valve core. Under the elastic force of the shut-off valve spring 17a, the outer surface 1621 of the shut-off valve core 16a in its free state abuts against the inner surface 1211 on one side of the arc-shaped protrusion within the filling chamber, and the pin 161 and the base 162 cooperate to cover and seal the corresponding filling holes. The filling liquid (such as saline N) is sealed within the filling chamber. The filling structure, corresponding to the arc-shaped electrode and the insulating protrusion, can be selectively provided on the fixed clamp arm 1 and / or the movable clamp arm 2. When the movable clamp arm 2 is also provided with a filling structure, its overall structure is the same as that on the fixed clamp arm 1. The insulating protrusion 221 of the movable clamp arm 2 has a through filling cavity. Along the length of the clamp arm, one or more sets of shut-off valve cores 26a and shut-off valve springs 27a are spaced apart in the filling cavity, and their positions and numbers correspond to one or more filling holes of the aforementioned insulating protrusion. The structure of the shut-off valves 26a and 26b is the same as that of the shut-off valve cores 16a and 16b, and will not be described in detail here. One end of the shut-off valve spring 27a abuts against the bottom of the filling cavity in the insulating part 22 of the movable clamp arm, and the other end abuts against the shut-off valve core 26a. Under the action of the elastic force of the shut-off valve spring 27a, the shut-off valve core 26a in the free state abuts against the inner surface of the filling cavity, covering and sealing the corresponding filling hole. The infusion fluid (such as saline N) is sealed within the infusion chamber. One or more fluid outlet channels 2611 are also provided along the outer periphery of the valve cores 26a and 26b of the shut-off valve to allow the infusion fluid to flow out under the pressure of the clamped target ablation tissue.

[0056] The following explains the relative positions of the shut-off valve core and the shut-off valve spring under the state of compression of the ablation tissue of the clamped target. For example... Figure 10-11 As shown, when compressed by the target ablated tissue, the state of the shut-off valve spring after compression is as shown by shut-off valve springs 17b and 27b. The outer surface 1621 of the shut-off valve core 16b separates from the inner surface 1211 of the infusion chamber, and the infusion chamber is in fluid communication with the infusion orifice. At this time, the infusion fluid flows out from the infusion chamber through the liquid outflow channels 1611 and 2611 of the shut-off valve core, and flows out from the corresponding infusion orifice, filling the gap between the target ablated tissue and the clamp arm (e.g., Figure 10 (As shown). A comparison of the relative positions of the valve core and spring of the shut-off valve with the injection hole on the insulating protrusion in the free state and in the state of being squeezed by the target ablation tissue, as shown. Figure 11 The image shows a magnified portion of the view. Figure 11 In the clamping state, the distance between the movable clamp arm 2 and the fixed clamp arm 1 is T. Under the clamping force, the shut-off valve spring 17b within the tissue M coverage area is compressed, and the shut-off valve core 16b moves outward from the jaws, separating its outer surface 1621 from the inner surface 1211 of the infusion chamber. Conversely, in the free state, the shut-off valve spring 17a presses the outer surface 1621 of the shut-off valve core 16a against the inner surface 1211 of the infusion chamber, and the maximum distance t between the arc-shaped protrusion of the shut-off valve core and the insulating protrusion 121 is greater than 0.

[0057] Figure 12 A diagram illustrating the clamping of a pig's heart-shaped ear is shown. (For example...) Figure 12 As shown, the target ablation tissue does not necessarily cover the entire length of the clamp arm. The shut-off valve core and shut-off valve spring are spaced apart along the length of the clamp arm in one or more groups. When the target ablation tissue only covers a portion of the pulse ablation clamp's length, only the perfusion pathway within the covered area—that is, the flow path formed by the perfusion fluid flowing through the perfusion chamber, the fluid outlet of the shut-off valve core, and the corresponding perfusion orifice—is connected (e.g., Figure 11 The perfusion passage within the area in contact with tissue M remains closed due to the action of the shut-off valve core and shut-off valve spring (e.g., the perfusion passage within the area in contact with tissue M). Figure 11 (The perfusion pathway is within the area not in contact with tissue M). Furthermore, to ensure the perfusion fluid properly fills the gaps, the opening pressure threshold of the aforementioned shut-off valve core is set to less than 0.1 Newtons. Thus, the operator only needs to apply minimal force to spray the perfusion fluid onto the target tissue, thereby achieving cooling during the ablation process.

[0058] The following is for reference Figure 13-15 This paper describes the technical effects of the pulse ablation clamp of the present invention, which adopts the above technical solution, under several discharge modes.

[0059] like Figure 13 As shown, the pulse ablation clamp of the present invention can adopt a first discharge mode of discharging adjacent electrodes on the same side clamp arm according to actual needs. In this case, the first electrode 13 and the second electrode 14 on the fixed clamp arm 1, or the third electrode 23 and the fourth electrode 24 on the movable clamp arm 2, are selected to discharge as positive and negative electrodes respectively, and the target ablation tissue M is clamped within the ablation area between the fixed clamp arm 1 and the movable clamp arm 2. Figure 14As shown, the pulse ablation clamp of the present invention can adopt a second discharge method of discharging the opposing clamp arms at an angle to the electrodes, depending on actual needs. In this case, the first electrode 13 on the fixed clamp arm 1 and the fourth electrode 24 on the movable clamp arm 2, or the third electrode 23 on the movable clamp arm 2 and the second electrode 14 on the fixed clamp arm 1, are selected to discharge as positive and negative electrodes to each other, and the target ablation tissue M is clamped within the ablation area between the fixed clamp arm 1 and the movable clamp arm 2. Figure 15 As shown, the pulse ablation clamp of the present invention can adopt a third discharge mode, in which opposing clamp arms discharge to opposite electrodes, according to actual needs. In this case, the first electrode 13 on the fixed clamp arm 1 and the third electrode 23 on the movable clamp arm 2, or the fourth electrode 24 on the movable clamp arm 2 and the second electrode 14 on the fixed clamp arm 1, are selected to discharge to each other as positive and negative electrodes, and the target ablation tissue M is clamped within the ablation area between the fixed clamp arm 1 and the movable clamp arm 2. Among the above three discharge modes, according to... Figure 13 Distribution in Figure III , Figure 14 Distribution in Figure V , Figure 15 Distribution in Figure VII It can be seen that even with an arc-shaped electrode, the contact area between the electrode and the target ablation tissue is reduced when an insulating protrusion is provided, and a gap still exists between them. At position P, the equipotential lines of the electric field strength still narrow sharply, the current density increases, and there is a risk of arcing or ablation heat effects. According to... Figure 13 Distribution in Figure IV , Figure 14 Distribution in Figure VI , Figure 15 Distribution in Figure VIII As can be seen, when a perfusion structure is provided, the gap between the aforementioned electrode and the target ablated tissue is filled with a perfusion liquid—such as saline N. In this case, the perfusion liquid acts as a conductor, enabling conductivity between the electrode surface, which is not in direct contact with the target ablated tissue, and the target ablated tissue. Its presence makes the electric field distribution more uniform. Simultaneously, the perfusion liquid fills the surfaces of the electrode and the target ablated tissue, absorbing the heat generated during the ablation process and effectively reducing or avoiding thermal effects.

[0060] Furthermore, to improve the uniformity of the injected fluid flow, the pulse ablation clamp of the present invention also has a microchannel on the surface of the insulating protrusion that is in fluid communication with the injection hole. See below for reference. Figure 16-17 Taking one side of the fixed clamp arm 1 as an example, the structure of the microchannel is explained. Figure 16-17As shown, the outer surface of the insulating protrusion 121 has a microchannel 122 that is recessed towards the outside of the fixed clamp arm 1. This includes a first microchannel extending along the length direction and one or more second microchannels extending from the first microchannel to the outer surface of the electrodes 13 and 14 along the width direction. The first microchannel is fluidly connected to the liquid outlet channel 1611 of the shut-off valve core. Under the pressure of the clamped target ablation tissue, the infusion liquid flows out from the infusion hole through the liquid outlet channel 1611 of the shut-off valve core and flows along the first and second microchannels. The microchannels 122 are uniformly distributed on the outer surface of the insulating protrusion 121. The infusion liquid flowing out of the infusion hole is guided by the microchannels 122, flows, and is uniformly distributed throughout the clamp arm, thereby making the electric field distribution more uniform during the ablation process. Simultaneously, the arrangement of the microchannels 122 with their concave-convex structure also increases the clamping friction between the fixed clamp arm and the movable clamp arm on the target ablation tissue. However, it should be understood that… Figure 16-17 The example shown is only one example of the microchannel 122 configuration of the present invention. The purpose of the microchannel and the brine outlet channel of the shut-off valve core is to achieve smooth and uniform outflow of the injected liquid. Therefore, those skilled in the art can select an appropriate structure according to the actual situation to achieve the above-mentioned technical objectives. Figure 16-17 The structure shown should not be construed as a limitation on the structure of the microchannels and the brine outlet channel of the shut-off valve core. For example, those skilled in the art can adjust the number of microchannels and their relative positions around the shut-off valve core, or adjust the number of brine outlet channels of the shut-off valve core and their extension method on the surface of the insulating protrusion, according to the actual situation.

[0061] The following is for reference Figure 18 The pulse ablation system and its control method of the present invention are described below.

[0062] The pulse ablation system of the present invention includes a pulse ablation clamp as described above and a pulse ablation device electrically connected thereto. The pulse ablation device receives setting and operation instructions from the operator, monitors the working status of the pulse ablation clamp, and controls the pulse ablation clamp to complete the ablation operation. Specifically, the pulse ablation device includes a perfusion pump for supplying perfusion fluid, an ablation device discharge module for controlling the delayed discharge of electrodes on the fixed clamp arm and / or movable clamp arm, a pressure monitoring module for monitoring pressure changes in the perfusion line and outputting the monitored pressure signal based on the pressure changes, and an ablation device control unit for controlling the opening and closing of the perfusion pump and the ablation device discharge module. The ablation device control unit controls the opening of the perfusion pump and the ablation device discharge module based on a received signal indicating a decrease in pressure in the perfusion line; and controls the closing of the perfusion pump and the ablation device discharge module based on a received signal indicating an increase in pressure in the perfusion line.

[0063] Figure 18The control method of the pulse ablation system of the present invention is illustrated. Initially, the operator connects the aforementioned pulse ablation clamp to the pulse ablation device and operates both to complete system identification and initialization. After completion, the operator uses the pulse ablation clamp to clamp the myocardial tissue to be ablated. Once clamped, the valve core of the shut-off valve, protruding from the surface of the insulating protrusion on the clamp arm within the contact area with the myocardial tissue, is subjected to a force exerted by the myocardial tissue. Under this force, the shut-off valve spring is compressed, and the valve core and shut-off valve spring move as a whole outward from the clamp arm, opening the closed perfusion orifice, as shown in the diagram. Figure 10 As shown. At this time, the pressure monitoring module of the pulse ablation device detects a decrease in the pressure of the saline perfusion tubing and outputs a pressure signal indicating the pressure decrease. The control unit of the ablation device receives the pressure signal and controls the perfusion pump to start based on the pressure signal. At this time, the perfusion pump supplies perfusion fluid to the perfusion chambers in each clamp arm through the perfusion tubing in the cable. In addition, the control unit of the ablation device also controls the discharge module of the ablation device to start based on the received pressure signal. The discharge module of the ablation device emits a delayed pulse signal to the working electrode on the fixed clamp arm and / or the movable clamp arm, and initiates ablation of the clamped myocardial tissue after a delay. This delay is set to provide working time for the perfusion fluid to flow through the microchannel and fully fill the gap between the myocardial tissue and the working electrode. After the ablation is completed, the operator releases the myocardial tissue clamped by the pulse ablation clamp. At this time, as the force exerted by the tissue on the valve core of the shut-off valve disappears, under the action of the spring restoring force of the shut-off valve, the valve core of the shut-off valve re-abuts against the inner surface of the insulating protrusion, and the perfusion orifice is closed again. At this point, the pressure monitoring module detects an increase in pressure in the infusion line and outputs a pressure signal indicating this increase. Based on the received pressure signal, the ablation device control unit shuts down the infusion pump, stopping the supply of infusion fluid. It also stops the ablation device's discharge module from emitting pulse signals, thus halting the pulse ablation of the ablation clamp.

[0064] In addition to the above, this invention also improves the circuit design to address the problem of electric arc generation during pulse ablation clamping. See the appendix below. Figures 19 to 28 The pulse ablation circuit of the present invention will be described.

[0065] Figure 19 The circuit simulation diagram of the core module of the pulse ablation device of the present invention is shown. It employs four insulated-gate bipolar transistors (IGBTs) (Q34, Q35, Q36, Q37) arranged in a full-bridge structure to form a pulse generation circuit. The IGBTs switch rapidly and can withstand high voltage, thus enabling the generation of high-frequency pulses applied to the load, while also allowing for rapid and safe isolation and shutdown. Specifically, in terms of structure... Figure 19For example, the collectors of the first insulated-gate bipolar transistor (IGBT) Q34 and the second IGBT Q35 are electrically connected to the power supply terminal VCC, while the emitters of the third IGBT Q37 and the fourth IGBT Q36 are grounded. The emitter of the first IGBT Q34 and the collector of the third IGBT Q37 are connected to form AC output terminal A (i.e., the load terminal). The emitter of the second IGBT Q35 and the collector of the fourth IGBT Q36 are connected to form AC output terminal B (i.e., the load terminal). After the ablation circuit is turned on, a pulse voltage is applied between AC output terminals A and B.

[0066] In practical applications, pulse ablation devices often require switching ablation channels due to the need for targeted tissue ablation. For example, the working electrode is switched according to the type and / or shape of the tissue to be ablated, adaptively adjusting the position of the pulse electric field. Based on this, the pulse ablation circuit of this invention also connects a relay matrix between the full-bridge IGBT and the ablation electrode for channel switching. Figure 19 For example, a relay matrix can include multiple 6-pin double-pole double-throw (DPDT) relays. Each 6-pin relay includes two common terminals on the side connected to the ablation electrode, as shown by the two pins 102 in the figure; two normally open terminals on the side connected to AC output terminals A and B, as shown by the two pins 103 in the figure; and two normally closed terminals, as shown by the two pins 101 in the figure. When a relay is working, the relay is energized to the on state, and the common terminal 102 (pin 2) and the normally open terminal 103 (pin 3) are connected. The ablation voltage is applied to the load connected to the common terminal through the AC output terminal. When a relay is not working, the relay is not connected, the common terminal 2 is connected to the normally closed terminal 1 and disconnected from the normally open terminal 3, and the two ends of the load are in a short-circuit state.

[0067] The aforementioned channel switching process is essentially a relay switching process. However, during this process, switching channels via relays is highly susceptible to arcing, impacting the lifespan of the ablation instrument and the safety of the ablation operation. In practice, ablation channels cannot be switched when the full-bridge output is active. When the high-voltage circuit is connected, the contact / separation of the relay and contacts can easily cause arcing. Therefore, channel switching can only be performed after the full-bridge output is closed. However, even after the full-bridge is closed, the risk of arcing still exists when switching channels.

[0068] Specifically, parasitic and distributed capacitances naturally exist between circuit components and lines. During full-bridge output, both the distributed and parasitic capacitances in the entire circuit are "charged." This results in energy storage between the load terminals even after all IGBTs are turned off. At this time, because the IGBTs are in a high-impedance state after being turned off, the entire circuit is essentially an open circuit, and the energy stored in the aforementioned capacitors cannot be released in time. If the relay is switched immediately at this time, whether at the moment of separation between the relay and the preceding contact or at the moment of contact between the relay and the following contact, arcing may occur in the instrument due to a tiny air gap between the energized components.

[0069] Since the residual energy can naturally dissipate over time, one embodiment of the present invention avoids arcing by adding a direct delay to the control program design. Figure 20 An example of an ablation circuit using direct delay mode is shown. After clamping the target ablation tissue, the human body load is connected between terminals A and B of the circuit. When switching channels is required, the IGBTs (Q5, Q6, Q7, Q8) are turned off. At this time, because terminals A and B in the circuit and the ground point (GND) are respectively equipped with protection circuits for freewheeling, clamping, and RC absorption as shown in the figure, such as a circuit with Schottky diodes (D1, D2) in series, RC circuits with capacitors (C1) and resistors (R1), capacitors (C2) and resistors (R2) in series, and a circuit with the internal body diode of the IGBT in series, the above-mentioned IGBT protection buffers still have a certain amount of stored energy, equivalent to the aforementioned parasitic capacitance. This energy has no fast discharge path after the IGBT is turned off. Therefore, by adding an appropriate direct delay, it can be ensured that the relay operates and switches under low voltage, avoiding arcing.

[0070] Specifically, the direct delay is implemented by setting a preset delay time in the control program through the controller. After the full-bridge output is turned off, the relay can only be controlled to switch the execution channel after the delay time has elapsed. Figure 21 The diagram shows the natural voltage drop curve of the residual voltage under measured conditions with an initial voltage of 500V. In practice, the direct delay time can be determined based on the time constants of the IGBT leakage current discharge path and the PCB insulation resistance discharge path, preferably not less than 500ms. The following examples illustrate the calculation method of the direct delay time under the above two paths.

[0071] Path 1: Discharge through IGBT leakage current Assuming the preset switchable voltage is 50V, the residual voltage to be discharged is V=200V, and the IGBT leakage current is in the μA range. Therefore, the formula for calculating the delay time for natural discharge is: t = C × V / I in, C represents capacitance, with a value of 1 nanofarad (nF). V represents the residual voltage that needs to be discharged, which is 200 volts (V). I represents current, with a value of 1 microampere (µA). t represents the delay time used for discharge, calculated as in path 1 above, with a value of 200 milliseconds (ms).

[0072] Because IGBTs are not completely insulated, even when they are turned off, a microampere-level leakage current will still slowly seep in. If this leakage current is used to slowly and naturally discharge the residual voltage, it would take approximately 200 milliseconds for a 1 nanofarad capacitor to discharge a 200-volt residual voltage. Therefore, the minimum direct delay time set in the control program needs to be preset to be no less than 200 milliseconds.

[0073] Path 2: Discharge via PCB insulation resistor When the residual voltage is discharged through the PCB insulation resistor, the capacitor's discharge curve is as follows: Figure 22 As shown. At this point, the formula for calculating the time constant is: T=R × C in, C represents capacitance, with a value of 1 nF; R represents resistance, with a value of 150 megohms (MΩ). T represents the time constant, which is 150ms according to the calculation method of path 2 above.

[0074] like Figure 22 As shown, at time 1T, the residual voltage drops to 37% of the initial voltage Vs; at time 4T, the residual voltage in the circuit is basically discharged; and at time 5T, the residual voltage in the circuit is completely discharged.

[0075] Both of the above discharge paths exist in the circuit. By setting a preset delay time, the relay can be controlled to switch channels under low voltage conditions—such as a preset switchable safety voltage—thereby reducing the risk of arcing.

[0076] While the aforementioned direct delay design can address the residual pressure issue to some extent, considering that the ablation of the target tissue must be performed via open-chest surgery, the entire procedure should be completed as quickly as possible. Therefore, in one embodiment of the present invention, a low-resistance discharge circuit is added to the circuit to accelerate the residual pressure release process. For example... Figure 23 As shown, in this embodiment, a low-resistance discharge circuit is added between the load terminals (terminal A and terminal B) and the ground terminal. Figure 23In the illustrated circuit design example, the low-impedance discharge circuit includes a first discharge resistor R1 connected in series between terminal A and ground, and a second discharge resistor R2 connected in series between terminal B and ground. The resistance values ​​of discharge resistors R1 and R2 are determined based on the balance between the discharge time constant and the system's static power consumption, preferably ranging from 10kΩ to 100kΩ. When the IGBTs (Q30, Q31, Q32, Q33) in the circuit are turned off, the parasitic capacitances (C5, C7, C8, C9) and the residual voltage in the load, in addition to the portion directly discharged, can also be discharged through the added low-impedance discharge circuit. Thus, by adding a low-impedance discharge path as described above, the improved circuit can accelerate the discharge of residual voltage, effectively shortening the waiting time required for switching channels.

[0077] Appendix Figures 24 to 26 The paper compares the residual voltage discharge effect of the circuit with and without a low-resistance discharge circuit, for initial voltage values ​​of 500V, 1000V, and 1500V respectively. Figure 24 As shown, when the initial voltage is 500V, the initial residual voltage is approximately 250V. Without a low-impedance discharge circuit, it takes approximately 80ms for the capacitor's residual voltage to drop to 0V; however, with the addition of a low-impedance discharge circuit, it takes approximately only 0.2ms for the capacitor's residual voltage to drop to 0V. Figure 25 As shown, when the initial voltage is 1000V, the initial residual voltage is approximately 500V. At this point, without the addition of a low-impedance discharge circuit, it takes approximately 80ms for the capacitor residual voltage to drop to 0V; with the addition of the low-impedance discharge circuit, it takes approximately 0.2ms for the capacitor residual voltage to drop to 0V. Figure 26 As shown, when the initial voltage is 1500V, the initial residual voltage is approximately 750V. Without the added low-impedance discharge circuit, it still takes approximately 80ms for the capacitor residual voltage to drop to 0V; with the added low-impedance discharge circuit, it still takes approximately only 0.2ms. This demonstrates that the initial residual voltage in the circuit differs depending on the initial voltage value. However, by adding a low-impedance discharge circuit, the residual voltage in the circuit can be quickly discharged, and this method remains stable and effective regardless of the initial voltage.

[0078] Regarding rapid discharge, one embodiment of the present invention may also be as follows: Figure 27As shown, Q47 and Q46 are N-channel MOSFETs positioned between terminal A and ground, and between terminal B and ground, respectively. The drain of Q47 is connected to point A, its source is grounded, and its gate is connected to the controller; the drain of Q46 is connected to point B, its source is grounded, and its gate is connected to the controller. After the full-bridge output is turned off, the IGBTs (Q42, Q43, Q44, Q45) are turned off, and the controller outputs a high level to turn on Q46 and Q47. This allows the residual charge at load terminals A and B, stored in parasitic capacitances (C14, C15, C16, C17), to be quickly discharged through the turned-on MOSFETs (Q47, Q46). The delay time can be preset to 100μs via software. After the delay, the controller outputs a low level to the gate, turning off the turned-on MOSFETs (Q46, Q47), and then outputs a relay signal to switch channels.

[0079] like Figure 28 As shown, the ablation circuit of the present invention may further include a voltage detection circuit. In one embodiment of the present invention, during full-bridge output, the IGBTs (Q38, Q39, Q40, Q41) in the circuit are turned on, and the parasitic capacitances (C10, C11, C12, C13) are charged. After the full-bridge output is turned off, the residual voltage in the parasitic capacitances is discharged through the aforementioned natural discharge, rapid discharge, or similar methods. At this time, gating can be added between terminal A and ground, and between terminal B and ground, respectively, to set up a voltage monitoring circuit. For example... Figure 28 As shown, the voltage monitoring circuit may include a hysteresis comparator for monitoring the voltage at the load terminal, having a non-inverting input pin 1', an inverting input pin 3', an output pin 4', and a positive power supply pin 5' (i.e., Figure 28 The "v+" terminal and the negative power / ground pin 2' (i.e. Figure 28 (The "GND" end in the middle). Figure 28In the illustrated embodiment, the voltage monitoring circuit is designed such that: the load terminals (A and B terminals) are connected to the inverting input pin 3'; a Zener diode (D3, D4) is connected between the non-inverting input pin 1' and the ground terminal, providing a stable gate voltage for the comparator; the gate output pin 4' is connected to the controller (not shown in the figure). When the load terminal voltage drops below a preset threshold (i.e., the gate voltage), the output of the hysteresis comparator outputs an electrical signal allowing channel switching to the controller. At this time, the controller controls the relay to switch channels based on this signal. The preset allowable switching voltage threshold range can be selected as below 10V-50V. Since the residual voltage discharge curve of the circuit is not a smooth straight line, by setting this hysteresis comparator, false triggering and oscillation caused by voltage fluctuations can be effectively prevented. As long as the load terminal voltage is within a certain range, even if jitter occurs, the output signal will not arbitrarily flip, thereby stably controlling the channel switching.

[0080] The embodiments of the present invention have been described in detail above with reference to the accompanying drawings. However, the present invention is not limited to the above embodiments. The components of the present invention can be used in any combination. Within the knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of the present invention.

Claims

1. A pulse ablation clamp, comprising: clamp body; The jaws are mounted on the jaws body and consist of a fixed jaw arm and a movable jaw arm parallel to the fixed jaw arm. The fixed jaw arm has a fixed surface for clamping, and the movable jaw arm has a movable surface opposite to the fixed surface for clamping. The jaws clamp or release the target ablation tissue by moving the movable jaw arm relative to the fixed jaw arm. Its features are, The fixed clamp arm includes a first electrode and a second electrode spaced apart in the width direction, the first electrode and the second electrode extending along the length direction of the fixed clamp arm; the movable clamp arm includes a third electrode and a fourth electrode spaced apart in the width direction, the third electrode and the fourth electrode extending along the length direction of the movable clamp arm. An insulating protrusion is provided between the first electrode and the second electrode and / or between the third electrode and the fourth electrode, wherein the height of the insulating protrusion is greater than the height of the protrusion of the electrode. as well as Both the electrode and the insulating protrusion protrude at least partially from the fixed surface or the movable surface, and the cross-sections of the portions of the first electrode, the second electrode, the third electrode, and the fourth electrode protruding relative to the fixed surface or the movable surface are arc-shaped.

2. The pulse ablation clamp according to claim 1, characterized in that, The cross-section of the portion of the insulating protrusion that protrudes relative to the fixed surface or the movable surface is arc-shaped.

3. The pulse ablation clamp according to claim 1, characterized in that, The first electrode, the second electrode, the third electrode, and the fourth electrode are cylindrical electrodes.

4. The pulse ablation clamp according to claim 1, characterized in that, The radius of curvature of the arc-shaped protrusions of the first electrode, the second electrode, the third electrode, and the fourth electrode is 0.5-6 mm.

5. The pulse ablation clamp according to any one of claims 1 to 4, characterized in that, The ends of the first and second electrodes, which extend along the length direction, extend into the interior of the fixed clamp arm, and the ends of the third and fourth electrodes, which also extend along the length direction, extend into the interior of the movable clamp arm.

6. The pulse ablation clamp according to claim 2, characterized in that, The same clamp arm is provided with one or more insulating protrusions, and each insulating protrusion has one or more injection holes along its length that extend through the insulating protrusion in a direction perpendicular to the fixed surface and / or the movable surface, for injecting fluid into the clamped part.

7. The pulse ablation clamp according to claim 6, characterized in that, The pulse ablation clamp further includes an infusion structure, which comprises: An infusion line disposed within the clamp body is used to supply infusion liquid to the jaws. An injection cavity is provided within the fixed clamp arm and / or the movable clamp arm, the injection cavity being used to allow fluid communication between the injection pipeline and the injection hole.

8. The pulse ablation clamp according to claim 7, characterized in that, The injection structure also includes a stop valve spring and a stop valve core disposed in the injection cavity. The stop valve spring and the stop valve core are provided with one or more sets corresponding to the injection hole. At least a portion of the stop valve core protrudes from the insulating protrusion. in, The valve core of the shut-off valve has one or more liquid outflow channels distributed around it. In the free state, the valve core of the shut-off valve is closed by the shut-off valve spring; When the target ablation tissue is clamped and compressed, the valve core of the shut-off valve moves and the infusion fluid flows out of the infusion orifice through the fluid outlet channel.

9. The pulse ablation clamp according to claim 8, characterized in that, The shut-off valve core includes: a base and a pin protruding relative to the base; in, The base includes an outer surface facing the injection hole, which in a free state fits against the inner surface of the injection cavity to seal the injection hole, and in a valve core-pressed state separates from the inner surface of the injection cavity. The ejector pin passes through the injection hole and has one or more liquid outlet channels distributed around its outer periphery. The liquid outlet channels allow the injection liquid to flow out of the injection hole when the valve core of the shut-off valve is squeezed.

10. The pulse ablation clamp according to any one of claims 5 to 9, characterized in that, The outer surface of the insulating protrusion is formed with a microchannel that is recessed toward the interior of the insulating protrusion. Under the condition of being squeezed, the injection liquid flows out from the injection cavity through the injection hole and flows along the microchannel.

11. The pulse ablation clamp according to claim 10, characterized in that, The microchannels include: The first microchannel extending along the length direction; and One or more second microchannels extending along the width direction from the first microchannel to the outer surface of the electrode; The first microchannel is fluidly connected to the injection hole.

12. A pulse ablation system, comprising: The pulse ablation clamp and the pulse ablation device electrically connected to the pulse ablation clamp as described in any one of claims 1-11.

13. The pulse ablation system according to claim 12, characterized in that... Includes the pulse ablation clamp as described in claims 5-11, and the pulse ablation device; The pulse ablation device includes: A filling pump, used to supply filling liquid; The ablation device discharge module is used to control the delayed discharge of electrodes on the fixed clamp arm and / or the movable clamp arm; A pressure monitoring module is used to monitor pressure changes in the infusion pipeline and output the monitored pressure signal based on the pressure changes. The ablation device control unit is used to control the opening and closing of the infusion pump and the ablation device discharge module; The ablation device control unit controls the opening of the infusion pump and the ablation device discharge module based on a received signal indicating a decrease in pressure in the infusion line; and controls the closing of the infusion pump and the ablation device discharge module based on a received signal indicating an increase in pressure in the infusion line.

14. A control method for the pulse ablation system of claim 13, characterized in that, The method includes: S1) Monitoring of pressure reduction in the infusion line: When the target ablation tissue is clamped between the fixed clamp arm and the movable clamp arm, the valve core of the shut-off valve is subjected to force, the infusion orifice is opened, the pressure monitoring module detects the pressure reduction in the infusion line, and outputs a pressure signal characterizing the pressure reduction. S2) Start-up of the perfusion pump: The ablation device control unit controls the perfusion pump to start based on the received pressure signal indicating a decrease in pressure, so as to supply perfusion fluid; S3) Ablation electrode discharge: Based on the received pressure signal, the ablation device control unit controls the ablation device discharge module to turn on. The ablation device discharge module sends a delayed pulse signal to the electrodes on the fixed clamp arm and / or the movable clamp arm to initiate ablation of the target ablation tissue after a delay. S4) Monitoring of pressure rise in the infusion pipeline: When the target ablation tissue is removed, the valve core of the shut-off valve loses its force, the infusion orifice closes, the pressure monitoring module detects the pressure rise in the infusion pipeline, and outputs a pressure signal characterizing the pressure rise; S5) Shutdown of the perfusion pump: The ablation device control unit controls the perfusion pump to shut down and stop supplying perfusion fluid based on the received pressure signal indicating an increase in pressure.

15. A pulse ablation circuit, comprising: A pulse generating circuit includes four insulated-gate bipolar transistors arranged in a full-bridge structure, the four insulated-gate bipolar transistors being electrically connected between a power supply terminal and a ground terminal; as well as A relay matrix, electrically connected to the pulse generation circuit, is used to switch ablation channels; Wherein, the emitter of the first insulated gate bipolar transistor and the collector of the third insulated gate bipolar transistor are connected to form terminal A, the emitter of the second insulated gate bipolar transistor and the collector of the fourth insulated gate bipolar transistor are connected to form terminal B, and the relay matrix is ​​electrically connected between terminal A and terminal B. Its features are, The pulse ablation circuit further includes a residual voltage discharge circuit, which is used to discharge residual electrical energy in the pulse generation circuit after the insulated gate bipolar transistor arranged in a full-bridge structure is turned off.

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