A pulse ablation clamp

Abstract

The present application relates to the field of cardiac ablation, and provides a pulse ablation forceps, the pulse ablation forceps include forceps body and be installed on the forceps body, the jaw part that is composed of fixed jaw arm and the movable jaw arm parallel to fixed jaw arm, the forceps body includes sliding slot, fixed jaw arm is fixedly connected at the distal end of sliding slot, the movable jaw arm is along sliding slot and is away from fixed jaw arm, along the direction of jaw part extension, from the distal end to the proximal end, n first electrodes are arranged on the movable jaw arm, n+1 second electrodes are arranged on the fixed jaw arm, n≥2;In the direction perpendicular to the extension of fixed jaw arm, the projection of each first electrode on fixed jaw arm is located between two second electrodes;All first electrodes are arranged outside the sliding slot, and at least a part of the n+1 second electrode is arranged in the sliding slot.The pulse ablation forceps of the present application avoids the situation of leakage ablation, and does not produce arc at the same time, improves the ablation effect.

Description

Technical Field

[0001] This invention relates to the field of cardiac ablation, and more specifically to a pulse ablation clamp. 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] For the treatment of atrial fibrillation, the common approach is intracardiac catheterization, which is minimally invasive, has a fast recovery time, and is highly safe. However, for some more severe cases, invasive surgical treatment is required. In cases involving open-chest surgery, commonly used equipment includes ablation forceps and ablation pens. There are also requirements for treatment effectiveness and treatment time, aiming to minimize the treatment time while ensuring therapeutic efficacy.

[0004] Most existing ablation clamps are radiofrequency ablation clamps, but the ablation damage area is difficult to control when using radiofrequency energy. The latest method uses pulsed energy for ablation, which produces accurate, complete, and transmural ablation lines, making it one of the effective methods for treating atrial fibrillation. Factors affecting the ablation effect of pulsed ablation include voltage, current, pulse width, and frequency. These are mostly emitted by the ablation instrument within its rated safety range. For the operator, the ablation is largely based on experience or preset values ​​of the equipment. Control of the process is limited to visually confirming whether the clamping of the target ablation tissue is tight and reliable, which has considerable uncertainty.

[0005] Meanwhile, in existing ablation forceps, due to the relative movement of the two forceps arms, there is a reserved gap. When actually clamping the target tissue for ablation, it has been found that some tissue enters the reserved gap, making it impossible to completely ablate the target tissue.

[0006] Furthermore, after pulsed energy ablation, cells undergo irreversible electroporation, but this irreversible electroporation cannot be immediately and directly observed, making it impossible to effectively determine the effect of pulsed ablation. Therefore, to reduce the possibility of surgical failure, it is necessary to improve the reliability of the ablation process as much as possible, while avoiding missed ablation. Current pulsed ablation forceps cannot meet the practical needs.

[0007] Therefore, a new pulse ablation forceps is needed for surgical pulse ablation. Summary of the Invention

[0008] In order to overcome the above-mentioned problems in the prior art, the present invention provides a highly efficient and safe pulse ablation clamp that can avoid missed ablation.

[0009] This invention provides a pulse ablation forceps, comprising a forceps body and a jaw portion mounted on the forceps body, consisting of a fixed forceps arm and a movable forceps arm parallel to the fixed forceps arm. The jaw portion clamps or releases target ablated tissue by moving the movable forceps arm relative to the fixed forceps arm. The forceps body includes a slide groove, the fixed forceps arm is fixedly connected to the distal end of the slide groove, and the movable forceps arm extends along the slide groove towards or away from the fixed forceps arm. Along the direction extending from the distal end to the proximal end of the jaw portion, n first electrodes are provided on the movable forceps arm, and n+1 second electrodes are provided on the fixed forceps arm, where n≥2. In a direction perpendicular to the extension of the fixed forceps arm, the projection of each first electrode on the fixed forceps arm is located between two second electrodes. All first electrodes are disposed outside the slide groove, and at least a portion of the (n+1)th second electrode is disposed within the slide groove.

[0010] More preferably, n is 5.

[0011] More preferably, adjacent first electrodes are arranged at equal intervals along the direction of extension of the jaw portion, and / or adjacent second electrodes are arranged at equal intervals.

[0012] More preferably, the spacing between the equally spaced elements is 1.5-4 mm.

[0013] Preferably, each of the first electrode and / or the second electrode has the same length and area; the length is the distance that each of the first electrode and the second electrode extends in the direction in which the jaws extend; the area is the cross-sectional area of ​​each of the first electrode and the second electrode with a plane parallel to the direction in which the jaws extend as a cross section.

[0014] Preferably, the fixed clamp arm and / or the movable clamp arm have insulating protrusions between adjacent first electrodes and / or between adjacent second electrodes.

[0015] Preferably, the (n+1)th second electrode extends into the groove by 1-4 mm, and the distance between the end of the (n+1)th second electrode near the groove and the inner wall of the groove is 2-4 mm.

[0016] Preferably, it also includes a pressure sensor.

[0017] Preferably, it also includes distance sensors correspondingly disposed on the fixed clamp arm and the movable clamp arm.

[0018] More preferably, it also includes an impedance detection module.

[0019] The technical effects achieved by the pulse ablation clamp of the present invention are as follows:

[0020] 1) The ablation forceps of this invention use pulsed energy for ablation. Compared to radiofrequency energy ablation, pulsed ablation has a clear boundary / range, and only when the voltage threshold is reached will irreversible electroporation occur in the target ablation tissue. It can selectively ablate myocardial tissue and is less likely to accidentally damage other organs like radiofrequency ablation. It does not affect tissues in non-ablation areas, greatly reducing the occurrence of complications. Using pulsed electric field energy for ablation results in a short action time, almost no thermal effect, no need for cold saline perfusion cooling, and faster recovery. Compared to cryoablation, the product structure is simpler.

[0021] 2) The pulse ablation forceps of the present invention employs two parallel push-pull clamping arms. Compared with scissor-type clamping arms, it is easier to hold the target ablation tissue between the two clamping arms. The fixed clamping arm is located at a more distal end than the movable clamping arm. The target ablation tissue is controlled between the fixed clamping arm and the movable clamping arm and is supported by the fixed clamping arm. When the movable clamping arm is pushed to clamp the target ablation tissue, the change of the target ablation tissue is mainly controlled at the relatively proximal end (the end closer to the movable clamping arm), which can be more easily observed by the operator, thereby visually perceiving whether the tissue is clamped.

[0022] 3) In practical applications, the inventors discovered that when the first and second electrodes are set in a one-to-one correspondence, i.e., when the projection of the first electrode coincides with the second electrode in the direction perpendicular to the extension of the fixed clamp arm, and the upper and lower electrodes are set as positive and negative poles respectively for low-voltage discharge (800-1200V), a gap in the ablation area easily appears between the movable clamp arm and the fixed clamp arm (e.g., Figure 6 (O in the original text). By setting the first electrode to be one less than the second electrode, and in the direction perpendicular to the extension of the fixed clamp arm, so that the projection of the first electrode is located between the two second electrodes, that is, the first electrode and the second electrode are arranged alternately, it is possible to control the ablation range more conveniently and efficiently by controlling the number and position of the discharge electrodes, avoiding the risk of arcing due to the first electrode and the second electrode being too close, and it is also beneficial to reduce or eliminate the above-mentioned gaps in the ablation area, so as to make the ablation more complete.

[0023] 4) The inventors discovered that although the surgeon tries to place the target ablation tissue in the center of the clamp arm during the procedure, due to the size of the target ablation tissue, pushing the movable clamp arm during clamping can cause the target ablation tissue to be compressed / squeezed to both sides along the fixed clamp arm. This can lead to the target ablation tissue entering the groove. On conventional ablation clamps, the electrodes are usually spaced from the groove and are not placed inside it, thus causing missed ablation. To solve this problem, the pulse ablation clamp of this invention has n+1 second electrodes on the fixed clamp arm, and the n+1th second electrode is at least partially placed inside the groove, thereby achieving ablation of the target ablation tissue that has entered the groove and preventing missed ablation. Furthermore, by placing the first electrode on the movable clamp arm outside the groove, the risk of arcing and short circuits caused by placing both the first and second electrodes inside the groove and being too close together is avoided.

[0024] 5) Furthermore, due to factors such as the distance between electrodes and pulse intensity, the pulsed electric field generated between the positive and negative electrodes during ablation may not cover all preset ablation areas, such as... Figure 10 , 12 As shown in Figures 17 and 23, there is an ablation gap M. This invention, by providing insulating protrusions between adjacent electrodes of the fixed clamp arm and / or the movable clamp arm, can support the tissue to be ablated at the gap location, allowing it to enter the range of the pulsed electric field, thereby compensating for the ablation gap and preventing incomplete ablation.

[0025] 6) When using the pulse ablation forceps of the present invention, the position and number of electrodes clamping the target ablation tissue can be determined by detecting the impedance between the first and second electrodes, thereby determining the working electrode and avoiding short circuits caused by discharge between electrodes that do not clamp the target ablation tissue. The working electrode is pre-checked by detecting the impedance between adjacent electrodes on the same side of the clamp arm to determine the adhesion between the working electrode and the target ablation tissue, thus avoiding short circuits caused by poor adhesion. Furthermore, the present invention can also set a pressure reminder to detect whether the pressure difference between the first and second electrodes is within a certain range, thus making a preliminary judgment on the clamping condition of the ablation forceps on the target ablation tissue. In addition, during discharge ablation, the present invention preferably uses the first and second electrodes to form an electrode pair for discharge, thereby reducing or eliminating the ablation gap between the first and second electrodes. The control method of the present invention also includes discharge protection control to avoid adverse consequences caused by excessively high pulse signals applied to the tissue. In summary, the control method of the present invention is safe, efficient, and can minimize the occurrence of short circuits and ablation gaps. Attached Figure Description

[0026] Figure 1This is a schematic diagram of a pulse ablation clamp according to one embodiment of the present invention;

[0027] Figure 2 An exploded view of a pulse ablation clamp according to one embodiment of the present invention;

[0028] Figure 3 This is a schematic diagram of the fixed clamp arm and the movable clamp arm of a pulse ablation forceps according to one embodiment of the present invention.

[0029] Figure 4 This is a schematic diagram of the fixed clamp arm and the movable clamp arm of a pulse ablation forceps according to another embodiment of the present invention;

[0030] Figure 5 A schematic diagram of ablation forceps clamping a pig's auricle using existing technology;

[0031] Figure 6 A simulation diagram of the ablation area of ​​the pulse ablation clamp in existing technology;

[0032] Figure 7 A simulation diagram of the ablation area of ​​the pulse ablation clamp according to one embodiment of the present invention;

[0033] Figure 8 This is a schematic diagram showing the configuration of the first and second electrodes in the fixed and movable clamp arms of a pulse ablation clamp according to one embodiment of the present invention.

[0034] Figure 9 for Figure 8 A schematic diagram of the electric field lines for one ablation method of the pulse ablation clamp;

[0035] Figure 10 for Figure 9 A schematic diagram of the ablation area produced by the ablation method shown;

[0036] Figure 11 for Figure 8 A schematic diagram of the electric field lines for another ablation method using pulse ablation clamps;

[0037] Figure 12 for Figure 11 A schematic diagram of the ablation area produced by the ablation method shown;

[0038] Figure 13 for Figure 8 A schematic diagram of the electric field lines for another ablation method using pulse ablation clamps;

[0039] Figure 14 for Figure 13 A schematic diagram of the ablation area produced by the ablation method shown;

[0040] Figure 15 for Figure 8A schematic diagram of the electric field lines for another ablation method using pulse ablation clamps;

[0041] Figure 16 for Figure 13 and Figure 15 A schematic diagram of the ablation area generated by the superposition of ablation methods shown;

[0042] Figure 17 This is a simulation result of ablation on a potato using a pulse ablation clamp according to one embodiment of the present invention;

[0043] Figure 18 A pulse ablation clamp according to one embodiment of the present invention, wherein the fixed clamp arm and the movable clamp arm have insulating protrusions;

[0044] Figure 19 for Figure 18 The diagram shows the electric field lines of one ablation method using pulse ablation clamp.

[0045] Figure 20 for Figure 19 A schematic diagram of the ablation area produced by the ablation method shown;

[0046] Figure 21 This is a schematic diagram showing the configuration of the first and second electrodes in the fixed and movable clamp arms of a pulse ablation clamp according to another embodiment of the present invention.

[0047] Figure 22 for Figure 21 The diagram shows the electric field lines of one ablation method using pulse ablation clamp.

[0048] Figure 23 for Figure 22 A schematic diagram of the ablation area produced by the ablation method shown;

[0049] Figure 24 for Figure 21 A schematic diagram of the electric field lines for another ablation method using pulse ablation clamps;

[0050] Figure 25 for Figure 24 A schematic diagram of the ablation area produced by the ablation method shown;

[0051] Figure 26 for Figure 21 A schematic diagram of the electric field for another ablation method using pulse ablation clamps;

[0052] Figure 27 for Figure 26 A schematic diagram of the ablation area produced by the ablation method shown;

[0053] Figure 28A pulse ablation clamp according to one embodiment of the present invention, wherein the clamp arm has insulating protrusions.

[0054] Figure 29 for Figure 28 The diagram shows the electric field lines of one ablation method using pulse ablation clamp.

[0055] Figure 30 for Figure 29 A schematic diagram of the ablation area produced by the ablation method shown;

[0056] Figure 31 This is a schematic diagram of a pulse ablation system according to one embodiment of the present invention;

[0057] Figure 32 A flowchart illustrating a control method according to one embodiment of the present invention;

[0058] Figure 33 This is a schematic diagram of the discharge protection circuit of the present invention;

[0059] Figure 34 This is a circuit diagram illustrating the real-time acquisition of pulse current and calculation of ablation energy according to the present invention. Detailed Implementation

[0060] definition

[0061] 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.

[0062] 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.

[0063] 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.

[0064] 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.

[0065] Several: In this specification, "several" means more than one, that is, two or more, such as two, three, four, five, six, seven, etc.

[0066] 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.

[0067] 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.

[0068] 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.

[0069] Figure 1 and Figure 2 A schematic diagram of a pulse ablation forceps 100 according to one embodiment of the present invention is shown. 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 3 and a movable forceps arm 4 parallel to the fixed forceps arm 3. The jaw portion can clamp or release the target ablated tissue by moving the movable forceps arm 4 relative to the fixed forceps arm 3. The forceps body includes a groove 23, and the fixed forceps arm 3 is fixedly connected to the distal end of the groove 23. The movable forceps arm 4 moves along the groove 23 towards or away from the fixed forceps arm 3. The pulse ablation forceps 100 of the present invention employs two parallel push-pull clamping arms 3 and 4. Compared with scissor-type clamping arms, it is easier to hold the target ablation tissue between the two clamping arms 3 and 4. The fixed clamping arm 3 is located at a more distal end than the movable clamping arm 4. The target ablation tissue is controlled between the fixed clamping arm 3 and the movable clamping arm 4 and is supported by the fixed clamping arm 3. When the movable clamping arm 4 is pushed to clamp the target ablation tissue, the change of the target ablation tissue is mainly controlled at the relatively proximal end (the end closer to the movable clamping arm 4), which can be more easily observed by the operator, thereby visually perceiving whether the tissue is clamped.

[0070] The structure that moves the movable jaw 4 closer to or further away from the fixed jaw 3 along the slide groove 23 is known and easily implemented by those skilled in the art. For example, CN102198012A discloses a method of driving the movable jaw closer to or further away from the fixed jaw by a push rod. This invention does not limit this method.

[0071] As an example only, the present invention provides the following structure: the pulse ablation forceps 100 of the present invention includes a handle 1, an extension rod 2, a fixed forceps arm 3, and a movable forceps arm 4. The extension rod 2 is connected to the handle 1 and extends distally, and the extension rod 2 is provided with a sliding groove 23.

[0072] The handle 1 includes a handle housing 11, a push-pull member 12, and a button post 13. The handle housing 11 has a grip portion, which may have anti-slip textures to increase friction and facilitate gripping. The grip portion cooperates with the push-pull member 12 to facilitate operator use. During use, the operator's palm contacts the push-pull member 12, and their fingers press the grip portion; applying force with the palm pushes the push-pull member 12 to move the movable clamp arm 4 and lock the pulse ablation forceps 100. Part of the push-pull member 12 protrudes from the handle housing 11 and passes through it to connect to the extension rod 2. Pushing the push-pull member 12 moves the inner tube 21 of the extension rod 2, thereby moving the movable clamp arm 4 relative to the fixed clamp arm 3. The push-pull member 12 includes a push handle 121, a first spring 122, and a second spring 123. The push handle 121 moves the movable clamp arm 4, while the first spring 122 and the second spring 123 provide a reset function. During the movement of the movable clamp arm 4 from the proximal side to the distal side, that is, during the pushing process of the movable clamp arm 4 from away from the fixed clamp arm 3 to close to the fixed clamp arm 3, the first spring 122 is compressed and the second spring 123 is stretched. A button post 13 is provided on the handle housing 11. In one embodiment of the present invention, the button post 13 is a fixed position limiting post, and a limiting part and a release part (not shown in the figure) are correspondingly provided on the push-pull member 12. From the time the movable clamp arm 4 of the pulse ablation clamp 100 is in a free state until the push-pull member 12 is pushed to the preset position, the button post 13 is limited by the limiting part in the corresponding hole of the handle housing 11 and cannot pop out of the handle housing 11. When the push-pull member 12 is pushed to the preset position, the button post 13 slides past the limiting part and reaches the release part. At this time, the button post 13 pops out of the handle housing 11 and forms a limiting position, so that the pulse ablation clamp 100 becomes a limited fixed state, thereby locking the pulse ablation clamp 100. In the above embodiment, the first spring 122 is connected to the inner tube 21 of the handle housing 11 and the extension rod 2, providing the spring force required for the inner tube 21 to rebound. The second spring 123 abuts against the end of the handle 1 away from the extension rod 2, and can still provide a constant rebound force within a certain range after the button post 13 provides the limit, thereby solving the problem of clamping and ablation of cardiac tissue of different thicknesses. The surgeon 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, pressing the button post 13 will cause the movable clamp arm 4 to automatically push back the extension rod 2 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 post 13 is locked into the handle 1 to form an automatic limit, under the action of the double spring structure, the thickness of the clamping object between the fixed clamp arm 3 and the movable clamp arm 4 can be between 0 and 20 mm. In this invention, the clamping force between the movable clamp arm 4 and the fixed clamp arm 3 is provided by the elastic force of two springs 122 and 123.Furthermore, in other embodiments of this application, the button post 13 serves as an activation device. In this embodiment, the handle 1 may also include a rotating device disposed within the handle housing 11. This rotating device is an electric device activated by the button post 13. After activation by pressing the button post 13, the electric device pushes the movable clamp arm 4 to move until the reaction pressure from the two springs 122 and 123 on the movable clamp arm 4 reaches a preset value. After ablation is completed, pressing the button post 13 again causes the rotating device to move in the opposite direction, driving the movable clamp arm 4 away from the fixed clamp arm 3. In addition, the handle 1 includes a connecting cable for connecting an external ablation device to achieve electrical connection.

[0073] The extension rod 2 is used to extend the length of the ablation forceps 100, facilitating the insertion of the forceps arms into the human body for operation. It includes an inner tube 21, an outer tube 22, and a sliding groove 23. The outer tube 22 is fixedly connected to the handle housing 11, and the sliding groove 23 is fixed to the distal end of the outer tube 22. The sliding groove 23 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 3 and the movable forceps arm 4 enters through the opening and connects to the sliding groove 23. In a direction perpendicular to the outer tube 22, there is a certain distance from the opening of the sliding groove 23 to its inner wall, thus giving the sliding groove 23 a depth to accommodate the fixed forceps arm 3 and the sliding forceps arm 4. Furthermore, along the direction of extension of the outer tube 22, the sliding groove 23 has a certain length to accommodate the sliding of the inner tube 21 and the movable forceps arm 4. In the direction perpendicular to the outer tube 22, the cross-sectional shape of the groove 23 can be a hollow semi-circle, square, rectangle, or a shape formed by two straight lines connected by an arc, or other shapes that can adapt to the shape of the outer tube 22. The fixed clamp arm 3 is fixedly connected to the distal end of the groove 23. The outer tube 22 is sleeved over the inner tube 21, and the inner tube 21 can move relative to the outer tube 22. The movable clamp arm 4 is fixed to the distal end of the inner tube 21. The inner tube 21 is connected to the push-pull member 12 via a first spring 122 and can move relative to the outer tube 22 under the action of the push-pull member 12. The movement of the inner tube 21 relative to the outer tube 22 causes the movable clamp arm 4 to slide in the groove 23, and the movable clamp arm 4 moves parallel to the fixed clamp arm 3. Furthermore, the inner tube 21 and outer tube 22 can be made of metal-shaped flexible tubing, allowing doctors to manually adjust the bending shape according to the specific tissue structure location to adapt to various surgical conditions.

[0074] like Figure 3 and Figure 4 As shown, the fixed clamp arm 3 and the movable clamp arm 4 can be configured as arcs with lengths corresponding to their curvatures, or as straight lines with the same length. Besides the shapes described above, they can be configured into any suitable shape according to actual needs, as long as the fixed clamp arm 3 and the movable clamp arm 4 are arranged in parallel and can clamp the target ablation tissue. In one embodiment, along the direction extending from the jaws ( Figure 4In the X direction, the lengths of the fixed clamp arm 3 and the movable clamp arm 4 can be 5-10cm, and when they are arc-shaped, the arc can be 1-15°. Furthermore, the fixed clamp arm 3 and the movable clamp arm 4 have the same angle relative to the plane of the handle housing 11, and the angle can be 90-120°.

[0075] In this invention, the fixed clamp arm 3 and the movable clamp arm 4 are arranged opposite each other. Along the direction extending from the distal end to the proximal end of the jaws, the movable clamp arm 4 has n (n≥2) first electrodes 43, and the fixed clamp arm 3 has n+1 second electrodes 33. Each first electrode 43 and each second electrode 33 are electrically connected to a pulse generator via a wire, and each first electrode 43 and each second electrode 33 can be configured to be de-energized, negative, or positive. The first electrodes 43 are disposed outside the slide groove 23, and at least a portion of the (n+1)th second electrode closest to the slide groove 23 is disposed within the slide groove 23. Figure 3 and 4 As shown, at least a portion of the second electrode 33, marked by the dashed box, falls within the groove 23. That is, along the extending direction of the groove 23 ( Figure 4 (In the Y-axis direction), the projection of the slide groove 23 onto the movable clamp arm 4 does not cover the first electrode 43, while the projection of the slide groove 23 onto the fixed clamp arm 3 covers at least a portion of the (n+1)th second electrode closest to the slide groove 23. Along the extending direction of the fixed clamp arm 3 ( Figure 4 In the X-axis direction), the depth of the groove is generally 6~8mm. In a preferred embodiment, the length of the second electrode 33 near the groove 23 extending into the groove 23 is 1-4mm, and the distance between the end of the (n+1)th second electrode near the groove and the inner wall of the groove is 2-4mm.

[0076] In practical applications, due to factors such as the volume of the target ablated tissue, pushing the movable clamp arm 4 during the clamping process may cause the target ablated tissue to be compressed / squeezed to both sides of the clamp arm along the fixed clamp arm 3, which may result in the target ablated tissue entering the slide groove 23. Figure 5Taking the auricle of a pig heart as an example, it can be seen that when the ablation forceps clamp the auricle, some tissue is squeezed into the space of the groove. In the existing ablation forceps, since there are no electrodes in the groove, incomplete ablation occurs. This invention solves the problem by setting several second electrodes 33 on the fixed clamp arm 3 and placing at least a portion of the second electrodes near the groove 23 inside the groove 23, thereby achieving ablation of the target ablation tissue entering the groove 23 and preventing incomplete ablation. Furthermore, each electrode on the fixed clamp arm 3 and the sliding clamp arm 4 is connected to a corresponding wire. These wires are attached to the inner wall of the groove 23 and introduced into the extension rod 2 through the groove 23. These wires will occupy part of the space inside the groove 23. Placing the first electrode 43 on the sliding clamp arm 4 outside the groove 23 can prevent problems such as breakdown caused by the electrode on the sliding clamp arm 4 extending into the groove 23 and the distance between the electrode and the inner wall of the groove 23 and / or the wire inside the groove 23 being too close.

[0077] In addition, such as Figure 6 As shown, if the first electrode 43 and the second electrode 33 are in a one-to-one correspondence, that is, in the direction perpendicular to the extension of the jaws, the projection of the first electrode 43 on the fixed clamp arm 3 coincides with the second electrode 33, when the first electrode 43 and the second electrode 33 are respectively positive and negative electrodes for low-voltage discharge (800-1200V), a gap O in the ablation region is likely to appear between the fixed clamp arm 3 and the movable clamp arm 4. In this invention, the first electrode 43 and the second electrode 33 are staggered, that is, in the direction perpendicular to the extension of the fixed clamp arm 3, the projection of each first electrode 43 on the fixed clamp arm 3 is located between two second electrodes 33. For example, the electrodes on the fixed clamp arm 3 and the movable clamp arm 4 are numbered, from the direction away from the extension rod 2 to the direction closer to the extension rod 2, the n first electrodes 43 on the movable clamp arm 4 are M1, M2, M3...M n The n+1 second electrodes 33 on the fixed clamp arm 3 are sequentially named S1, S2, S3...S n+1 In the direction perpendicular to the extension of the fixed clamp arm 3, the projection of M1 onto the fixed clamp arm 3 lies between S1 and S2, the projection of M2 onto the fixed clamp arm 3 lies between S2 and S3, and so on. n The projection on the fixed clamp arm 3 is located at S. n and S n+1 Between, and M n Not extending into groove 23, S n+1 At least a portion of it falls into the chute 23. By setting it in this way, as... Figure 7 As shown, during low-voltage discharge, the pulse ablation clamp 100 of the present invention can reduce or eliminate the aforementioned gap O. Figure 17 Simulated ablation was performed on potatoes under the same conditions. It can be seen that no ablation gap appeared in the middle position between the first electrode 43 and the second electrode 33.

[0078] The pulse ablation clamp 100 of the present invention, by arranging the first electrode 43 and the second electrode 33 as described above, not only prevents incomplete ablation and arcing within the groove 23 and between the two clamping jaws, but also allows for more convenient and efficient control of the ablation range by controlling the number and position of the discharging electrodes through segmented electrode arrangement. For example, when the clamped target ablation tissue does not cover all of the first electrode 43 and the second electrode 33, the target ablation tissue can be ablated using only the first electrode 43 and the second electrode 33 covering the target ablation tissue.

[0079] In a preferred embodiment of the present invention, n is 5, meaning that the sliding clamp arm 4 is provided with 5 first electrodes 43, and the fixed clamp arm 3 is provided with 6 second electrodes 33. In a preferred embodiment of the present invention, adjacent first electrodes 43 are arranged at equal intervals, and / or adjacent second electrodes 33 are arranged at equal intervals; preferably, the interval between these equal intervals is 1.5-4 mm. In a preferred embodiment of the present invention, each first electrode 43 and / or second electrode 33 has the same length and area. Here, the length is the distance that each first electrode 43 and second electrode 33 extends in the direction of the jaw extension, and the area is the cross-sectional area of ​​each first electrode 43 and second electrode 33, i.e., the area of ​​the surface of the electrode in contact with the target ablated tissue, with a plane parallel to the direction of jaw extension. In a preferred embodiment of the present invention, the length of the first electrode 43 and the area of ​​the second electrode 33 are 6 mm and the area is 16 mm². 2 By arranging the first electrode 43 and the second electrode 33, which have the aforementioned length and area, at equal intervals, not only can the target tissue entering the chute be ablated, but the ablation effect on the target tissue held between the sliding clamp arm 4 and the fixed clamp arm 3 can also be made more consistent, resulting in a better ablation effect. The shapes of the first electrode 43 and the second electrode 33 are not particularly limited. In a preferred embodiment of the invention, both the first electrode 43 and the second electrode 33 are elliptical. Under high voltage conditions, the tips, protrusions, and edges of the electrodes can cause point discharge problems, resulting in arcing and reduced safety. Therefore, chamfering the original rectangular electrode sheet to form an elliptical shape can effectively prevent point discharge problems.

[0080] In one embodiment of the present invention, such as Figure 8As shown, the sliding clamp arm 4 includes a first jaw seat 41, a first insulating layer 42 disposed on the first jaw seat 41, and a first electrode 43 disposed within the first insulating layer 42 and having a surface for contacting the target ablated tissue. In this embodiment, the first electrode 43 includes first electrodes 431, 432, 433, 434, and 435. Correspondingly, the fixed clamp arm 3 includes a second jaw seat 31, a second insulating layer 32 disposed on the second jaw seat 31, and a second electrode 33 disposed within the second insulating layer 32 and having a surface for contacting the target ablated tissue. In this embodiment, the second electrode 33 includes second electrodes 331, 332, 333, 334, 335, and 336. Wherein, in the direction perpendicular to the fixed clamp arm 3 (i.e.... Figure 8 In the Y-axis direction), the projection of the first electrode 431 on the fixed clamp arm 3 is located between the second electrodes 331 and 332, the projection of the first electrode 432 on the fixed clamp arm 3 is located between the second electrodes 332 and 333, and so on. The projection of the first electrode 435 on the fixed clamp arm 3 is located between the second electrodes 335 and 336, and none of the first electrodes 43 fall into the slide groove 23 (not shown), while at least a portion of the second electrode 336 is disposed in the slide groove 23.

[0081] according to Figure 8 The pulse ablation clamp shown can employ different ablation methods depending on the size of the target tissue. For example... Figure 9 and 10 As shown, when the target ablation tissue D covers all first electrodes 431, 432, 433, 434, 435 and second electrodes 331, 332, 333, 334, 335, 336, all first and second electrodes participate in ablation. For example, an electrical signal is transmitted to all first electrodes 431, 432, 433, 434, 435 via a pulse generator, making them negative, and an electrical signal is transmitted to all second electrodes 331, 332, 333, 334, 335, 336, making them positive (or all first electrodes 43 can be positive and all second electrodes 33 negative), thereby delivering pulse energy to the target ablation tissue D. The electric field lines between all first and second electrodes are shown below. Figure 9 As shown, the ablation region T formed is as follows Figure 10 As shown, even if the target ablation tissue D enters the groove 23 (not shown) due to volume or compression, the ablation area T formed by at least a portion of the second electrode 336 is located within the groove 23, thus covering the target ablation tissue D within the groove 23 and preventing incomplete ablation. Furthermore, as... Figure 11 and 12As shown, when the target ablation tissue D only partially covers the first electrodes 431, 432, 433 and the second electrodes 331, 332, 333, an electrical signal is transmitted via a pulse generator to the covered first electrodes 431, 432, 433 and the covered second electrodes 331, 332, 333, respectively, making the first electrodes 431, 432, 433 negative and the second electrodes 331, 332, 333 positive (or the first electrodes 431, 432, 433 positive and the second electrodes 331, 332, 333 negative), without transmitting electrical signals to the remaining first electrodes 434, 435 and the second electrodes 334, 335, 336, thereby transmitting pulse energy to the target ablation tissue D. In this case, the electric field lines between the first electrodes 431, 432, 433 and the second electrodes 331, 332, 333 are as follows: Figure 11 As shown, the ablation region T formed is as follows Figure 12 As shown, the ablation area only covers the target ablation tissue D. No electric field is generated between the first electrodes 434 and 435 and the second electrodes 334, 335 and 336, avoiding the risks of short circuits and arcs caused by the absence of target ablation tissue between the first and second electrodes.

[0082] In some implementations, when the target ablation tissue is thin, ablation can be performed using only the first electrode or the second electrode, such as... Figure 13 and 14 As shown, no electrical signals are transmitted to any of the first electrodes 431, 432, 433, 434, and 435. Adjacent second electrodes are configured as positive and negative poles, respectively. Figure 13 In this configuration, second electrode 331 is configured as the positive electrode, second electrode 332 as the negative electrode, and second electrode 333 as the positive electrode. An electric field is generated between adjacent second electrodes, forming an ablation region T. Figure 14 As shown. Furthermore, as... Figure 15 As shown, it can also be configured such that: no electrical signals are transmitted to all second electrodes 331, 332, 333, 334, 335, and 336; adjacent first electrodes are configured as positive and negative electrodes respectively; first electrode 431 is configured as positive, first electrode 432 as negative, and first electrode 433 as positive; an electric field is generated between adjacent first electrodes to form an ablation zone. Furthermore, when the target ablation tissue is thick, ablation using only one electrode may not be complete. In this case, to avoid incomplete ablation using only one electrode, such as... Figure 16 As shown, it can be configured to first use the adjacent second electrode for ablation, and then use the adjacent first electrode for a second ablation. The superposition of the two ablation regions can thus avoid missed ablation. Furthermore, although... Figure 13-16The illustration only shows ablation using a portion of the first and second electrodes; however, those skilled in the art will understand that ablation can also be performed when the target ablation tissue covers both the first and second electrodes. Figure 13-16 The ablation method shown uses the same configuration for all first and second electrodes to ablate the target tissue.

[0083] like Figure 10 and 12 As shown, when the polarities of the first electrode and the second electrode are opposite, there may be areas that the electric field lines cannot cover due to the distance between two adjacent electrodes on the same clamp arm. Therefore, a gap M of the ablation region may be generated between two adjacent electrodes on the same clamp arm, and the target ablation tissue located at the gap M cannot be ablated. Figure 17 For use Figure 8 The pulse ablation clamp shown is used to Figure 9 The simulated ablation on a potato using the discharge method shown can be observed, with a gap M between the two electrodes. To prevent incomplete ablation of the target ablation tissue at gap M, in one embodiment of the invention, an insulating protrusion is provided between two adjacent electrodes on the same clamp arm. The insulating protrusion supports the target ablation tissue at gap M, allowing it to enter the ablation region, thereby preventing incomplete ablation. The insulating protrusion may be provided only between two adjacent first electrodes, only between two adjacent second electrodes, or between two adjacent first electrodes and two adjacent second electrodes. Figure 18 As shown, first protrusions 441, 442, 443, and 444 are respectively provided between the first electrodes 431, 432, 433, 434, and 435, and second protrusions 341, 342, 343, 344, and 345 are respectively provided between the second electrodes 331, 332, 333, 334, 335, and 336. Figure 19 and 20 As shown, the first protrusions 441, 442, 443, 444 and the second protrusions 341, 342, 343, 344, 345 support the target ablation tissue at the corresponding positions, allowing the target ablation tissue originally located at the notch M to enter the range of the electric field and fall into the ablation region T, thus enabling it to be ablated. The shape of the insulating protrusion is not particularly limited, but an arch shape is preferred. In a cross-section of the insulating protrusion in a plane perpendicular to the direction of extension of the jaws, the height of the insulating protrusion, i.e., the longest distance the insulating protrusion extends from the plane containing the surface in contact with the electrode and the tissue towards the opposite jaw, is less than or equal to 5 mm; the width of the insulating protrusion, i.e., the longest distance the insulating protrusion extends along the direction of extension of the jaws, is less than or equal to the distance between two adjacent electrodes, for example, 3.5 mm.

[0084] In another embodiment of the present invention, the pulse ablation clamp of the present invention may also have the following structure: the movable clamp arm 4 has only one first electrode, and the fixed clamp arm 3 has several second electrodes. The first electrode is disposed outside the slide groove 23, that is, it does not extend into the slide groove, while at least a portion of the second electrode near the slide groove 23 is disposed inside the slide groove 23. Thus, not only can ablation of the target ablation tissue falling into the slide groove 23 be achieved, but also arcing will not occur due to the close proximity of the first and second electrodes. Furthermore, since the movable clamp arm 4 has only one first electrode, the structure is simpler. Figure 21 An example of the above-described embodiment is shown, illustrating the use of six second electrodes. Those skilled in the art will understand that the number of second electrodes can be greater or less than six. For example... Figure 21 As shown, the movable clamp arm 4 has only one first electrode 43', while the fixed clamp arm 3 has six second electrodes 33, namely second electrodes 331, 332, 333, 334, 335, and 336. At least a portion of the second electrode 336 extends into the groove 23 (not shown in the figure), and the first electrode 43' is disposed outside the groove 23. The length of the first electrode 43' can be set according to the electrodes in existing ablation clamps with a single electrode on one side of the clamp arm. For example, in order to contact as much of the target ablation tissue as possible, the first electrode 43' extends along the extension direction of the sliding clamp arm 4, as long as its end near the groove 23 does not extend into the groove 23. Preferably, in the direction perpendicular to the fixed clamp arm 3, the projection of the first electrode 43' on the fixed clamp arm 3 simultaneously covers at least a portion of the second electrodes 331 and 336. By such an arrangement, the area of ​​the ablation zone can be expanded and the occurrence of incomplete ablation can be reduced.

[0085] like Figure 21 The pulse ablation clamp shown can employ different ablation methods depending on the size of the target tissue. For example... Figure 22 and 23 As shown, when the target ablation tissue D covers the first electrode 43' and all the second electrodes 331, 332, 333, 334, 335, and 336, the first electrode 43' and all the second electrodes participate in ablation. For example, an electrical signal is transmitted to the first electrode 43' via a pulse generator, making it the negative electrode, and an electrical signal is transmitted to all the second electrodes 331, 332, 333, 334, 335, and 336, making them the positive electrodes (or the first electrode 43' can be the positive electrode and all the second electrodes the negative electrodes), thereby delivering pulse energy to the target ablation tissue D. The electric field lines between the first electrode 43' and the second electrodes 331, 332, 333, 334, 335, and 336 are shown in the figure. Figure 22As shown in Figure 23, the formed ablation region T is as shown in Figure 23. It can be seen that even if the target ablation tissue D enters the groove 23 (not shown) due to volume or compression, since at least a portion of the second electrode 336 is located within the groove 23, the formed ablation region T can still cover the target ablation tissue D located within the groove 23, thereby preventing incomplete ablation. Furthermore, as shown in Figure 23... Figure 24 and 25 As shown, when the target ablation tissue D only covers a portion of the first electrode 43' and a portion of the second electrodes 331, 332, and 333, an electrical signal is transmitted to the first electrode 43' and the covered second electrodes 331, 332, and 333 via a pulse generator. This makes the first electrode 43' the negative electrode and the second electrodes 331, 332, and 333 the positive electrodes (or the first electrode 43' can be the positive electrode and the second electrodes 331, 332, and 333 the negative electrode), respectively. No electrical signal is transmitted to the remaining second electrodes 334, 335, and 336, thereby transmitting pulse energy to the target ablation tissue D. In this case, the electric field lines between the first electrode 43' and the second electrodes 331, 332, and 333 are as follows: Figure 24 As shown, the ablation region T formed is as follows Figure 25 As shown, the ablation area only covers the target ablation tissue D. No electric field is generated between the first electrode 43' and the second electrodes 334, 335, and 336, thus avoiding the risks of short circuits and electric arcs.

[0086] In some implementations, ablation can also be performed using only the second electrode, such as Figure 26 As shown, no electrical signal is transmitted to the first electrode 43', and the adjacent second electrodes are respectively set as positive and negative poles. Figure 26 In this configuration, second electrode 331 is configured as the positive electrode, second electrode 332 as the negative electrode, and second electrode 333 as the positive electrode. An electric field is generated between adjacent second electrodes, forming an ablation region T. Figure 27 As shown. Furthermore, although Figure 26-27 The illustration only shows a case where ablation is performed using a portion of the second electrode; however, those skilled in the art will understand that it is also possible to use the second electrode when the target ablation tissue covers the entire second electrode. Figure 26-27 The ablation method shown uses the same configuration for all second electrodes to ablate the target tissue.

[0087] In addition, such as Figure 23 and 25As shown, when the polarities of the first electrode 43' and the second electrode are opposite, due to the distance between two adjacent second electrodes on the fixing clamp arm 3, there may be areas that the electric field lines cannot cover. Therefore, a gap M in the ablation region may be generated between two adjacent second electrodes on the fixing clamp arm 3, and the target ablation tissue located at the gap M cannot be ablated. To prevent the problem of incomplete ablation of the target ablation tissue at the gap M, in one embodiment of the present invention, an insulating protrusion is provided between two adjacent electrodes on the fixing clamp arm 3. The insulating protrusion can support the target ablation tissue at the gap M, allowing it to enter the ablation region, thereby preventing incomplete ablation. Figure 29 and 30 As shown, second protrusions 341, 342, 343, 344, and 345 are respectively provided between the second electrodes 331, 332, 333, 334, 335, and 336. The second protrusions 341, 342, 343, 344, and 345 support the target ablation tissue at the corresponding positions, so that the target ablation tissue originally located at the notch M enters the range of the electric field and falls into the ablation region T, thereby being ablated.

[0088] In one embodiment of the present invention, the pulse ablation forceps 100 may further include a pressure sensor. When the sliding forceps arm 4 is moved toward the fixed forceps arm 3 to clamp the target ablation tissue, the pressure sensor can sense the pressure at its location and transmit this pressure through a connected wire to the pressure detection module in the pulse ablation device connected to the pulse ablation forceps 100. Based on the detected pressure, the operator can adjust and control the clamping process accordingly. The position of the pressure sensor can be set as needed. In one embodiment, the pressure sensor is located at the bottom of each first electrode and second electrode, and when clamping tissue, the force on the electrodes is transmitted to the pressure sensor below. In another embodiment, the pressure sensor is located in the gap between two adjacent electrodes on the same side of the forceps arm and is not connected to the electrodes. In this case, the pressure sensor can directly sense the pressure during the clamping process. When there is an insulating protrusion between two adjacent electrodes on the same side of the forceps arm, this insulating protrusion can be used as the sensing part of the pressure sensor to sense the pressure during the clamping process. In one embodiment of the present invention, the pulse ablation forceps 100 of the present invention further includes a pressure display device, which can be installed on the handle 1 or on the pulse ablation device, for displaying the pressure sensed by the pressure sensor, so as to facilitate the operator's operation.

[0089] In one embodiment of the present invention, the pulse ablation clamp 100 may further include distance sensors, which are correspondingly disposed on the fixed clamp arm 3 and the movable clamp arm 4. These distance sensors are electrically connected to the pulse ablation device via a conductive connection to each distance sensor, and are used to sense the distance between the fixed clamp arm 3 and the movable clamp arm 4. In a preferred embodiment, multiple pairs of pressure sensors are provided, equally spaced on the fixed clamp arm 3 and the movable clamp arm 4, for measuring the thickness of the target ablation tissue clamped between the fixed clamp arm 3 and the movable clamp arm 4, and whether the clamping is uniform.

[0090] In one embodiment of the present invention, the pulse ablation clamp 100 may further include an impedance detection module. The impedance detection module is equipped with a dielectric constant detection unit, which outputs an excitation signal to each first electrode and second electrode. The excitation signal, after acting on human tissue through each first electrode and second electrode, generates a complex impedance signal. The complex impedance signal is processed to obtain a dielectric constant signal, which is used to detect the degree of contact between the multiple ablation electrodes and the target tissue. When the dielectric constant signal is less than a set threshold, a short circuit occurs, requiring adjustment of the clamping angle or cleaning and replacement of the ablation clamp. Furthermore, the impedance detection module can also be used to detect the impedance between each first electrode and second electrode on the fixed clamp arm and the movable clamp arm, thereby determining the range of the target ablation tissue being clamped, and subsequently selecting the number and position of electrodes for ablation, avoiding short circuits caused by discharge from electrodes not clamping the target ablation tissue. In a preferred embodiment, the impedance detection module is a chip located at the handle 1 and connected to the pulse ablation device via a connected wire. Furthermore, those skilled in the art can also place the impedance detection module at a suitable position on the pulse ablation clamp or pulse ablation device as needed.

[0091] Furthermore, in a preferred embodiment of the present invention, the pulse ablation clamp 100 may further include an identification module. This identification module and the structure of the pulse ablation clamp itself, such as the number, length, and area of ​​electrodes, the electrode spacing on the same side clamp arm, and the length of the clamp arm on both sides, correspond one-to-one. When the pulse ablation clamp 100 is connected to a pulse ablation device for ablation of target tissue, the pulse ablation device, by identifying the identification module on the pulse ablation clamp 100, can match the corresponding ablation voltage, pulse width, pulse interval, and other parameters according to the target ablation tissue. For example, the identification module can be a resistive element, which can be placed at any position on the pulse ablation clamp 100, as long as it does not affect the operation of the pulse ablation clamp 100. For example, the resistive element can be placed inside the handle housing 11. Resistive elements with different resistance values ​​correspond to pulse ablation clamps with different structures. The pulse ablation device identifies the pulse ablation clamp by detecting the resistance value of the resistive element on the pulse ablation clamp and matches the corresponding ablation voltage, pulse width, pulse interval, and other parameters. In addition, the identification module can also be a chip or other suitable form.

[0092] Figure 31A schematic diagram of a pulse ablation system 1000 according to one embodiment of the present invention is shown, which includes an ablation clamp 100 and a pulse ablation device 200 electrically connected to the ablation clamp 100. The pulse ablation device 200 includes an impedance detection module 230, a pulse generation module 240, an interactive control module 250, and a central control module 260. In a preferred embodiment, the pulse ablation device 200 of the present invention further includes a host identification module 210 and a pressure detection module 220. The impedance detection module 230, the pulse generation module 240, the interactive control module 250, and preferably the host identification module 210 and the pressure detection module 220 are electrically connected to the central control module 260. Alternatively, the impedance detection module 230 may not be located in the pulse ablation device 200, but may be located on the pulse ablation clamp 100, or the impedance detection module 230 may be located in both the pulse ablation clamp 100 and the pulse ablation device 200. Impedance detection module 230 is used to detect the first impedance between the first electrode on the movable clamp arm 4 and the second electrode on the fixed clamp arm 3, and to detect the second impedance between two adjacent electrodes on the same side clamp arm, and feeds the results back to the central control module 260. Pulse generation module 240 is used to generate and send pulse signals individually to each of the first and second electrodes under the control of the central control module 260. Central control module 260 receives information from other modules, processes it, and feeds back and / or displays the processed information. Interactive control module 250 displays information and accepts user control commands, such as from a monitor, keyboard, or touchscreen. Host identification module 210 identifies the identification module on the pulse ablation clamp 100 according to the instructions of the central control module 260 to obtain relevant parameter information of the pulse ablation clamp 100. Pressure detection module 220 detects the pressure on the first electrode on the movable clamp arm 4 and the second electrode on the fixed clamp arm 3, and feeds the results back to the central control module 260.

[0093] In the pulse ablation system 1000 of the present invention, the device architecture of the pulse ablation device 200 is configured as a central control module 260 and various functional modules electrically connected thereto via a universal communication bus. The aforementioned modules may use devices or equipment known in the art, as long as they can perform the functions of each module; there are no other particular limitations.

[0094] For example, the central control module 260 is built based on a general-purpose processor or a programmable logic device. The general-purpose processor includes a single-core or multi-core microcontroller, and the programmable logic device may include an FPGA. FPGAs offer advantages such as high stability, low latency, and hardware parallelism, and their computing power surpasses that of digital signal processors (DSPs), thus contributing to improved effectiveness of pulsed electric field ablation. Additionally, the central control module 260 may also include components such as random access memory, read-only memory, digital-to-analog converters, analog-to-digital converters, power management chips, and communication chips.

[0095] The communication bus uses an isolated digital interface (such as optocoupler-isolated SPI) to realize data interaction between the central control module and various functional modules. However, optionally, the pulse ablation system 1000 can also be equipped with an independent wireless communication module (such as Bluetooth Low Energy protocol). That is, the data stream in the pulse ablation system 1000 can be transmitted using any communication method. Wireless methods such as Wi-Fi, WLAN, and Bluetooth can be selected, as well as wired methods such as fiber optic, network cable, USB, and serial port.

[0096] In one implementation, the acquired data can be displayed to the operator via an interactive module 250 (such as a display, microphone, and speaker) equipped with the pulse ablation system. Alternatively, the interactive module 250 can also be a touchscreen display, physical buttons and status indicator lights, as well as expandable external input devices (such as a keyboard and mouse) to enable human-computer interaction with the operator. The interfaces of the aforementioned devices must comply with the electrical isolation requirements for medical devices.

[0097] The pulse generation module 240 can be configured to generate high voltage from a switching power supply and output pulses through power switching devices. The switching power supply includes a high-frequency transformer and a rectifier and filter unit. The power switching devices are controlled by an opto-isolated drive circuit and support various pulse outputs such as square waves.

[0098] In the above device architecture, all modules are powered through a unified power layer, which includes, for example, buck regulator chips and low-dropout linear regulators, providing multiple isolated power supplies for the system. The communication interfaces and power supply links of all functional modules comply with the general requirements for electrical isolation and electromagnetic compatibility in medical electrical equipment safety standards.

[0099] The following is combined with Figure 32 This describes the control method of the present invention, as well as the connection relationships and functions of the components in the pulse ablation system 1000 of the present invention. For example... Figure 32 As shown, the control method of the present invention includes S1 selection of the working electrode, S2 pre-detection of the working electrode, and S3 discharge control. In a preferred embodiment, the control method of the present invention may further include S1-b identification control and S1-a pressure reminder steps.

[0100] Since the size of the target ablation tissue and its position in the two jaws of the target ablation clamp 100 may differ, and discharging an electrode that does not clamp the target ablation tissue may cause short circuits, it is necessary to select a working electrode before formally starting pulse ablation. The first and second electrodes clamping the target ablation tissue are designated as working electrodes for subsequent ablation operations. Therefore, the control method of this invention includes S1, the selection of the working electrode, which is achieved by controlling the operation of the ablation clamp and related components of the ablation device. In step S1, the working electrode is selected based on the difference in impedance between the first and second electrodes clamping and not clamping the target ablation tissue. Specifically, when both the movable clamp arm 4 and the fixed clamp arm 3 have segmented electrodes, the impedance detection module 230 detects the first impedance between the n first electrodes 43 on the movable clamp arm 4 and the n+1 second electrodes 33 on the fixed clamp arm 3 in the following manner: the resistance between the m-th first electrode 43 on the movable clamp arm 4 and the m-th second electrode 33 on the fixed clamp arm 3; and the resistance between the m-th first electrode 43 on the movable clamp arm 4 and the (m+1)-th second electrode 33 on the fixed clamp arm 3, where 1 ≤ m ≤ n. Then, the impedance detection module 230 sends all detected first impedances to the central control module 260. The central control module 260 compares all first impedances with a first threshold and selects the working electrode based on the comparison result. First, the second electrode S with the critical threshold at both ends of the fixed clamp arm 3 is determined. a Second electrode S b Second electrode S a Second electrode S b The following conditions must be met: i) The second electrode S a and the first electrode M a The resistance between and the second electrode S b and the first electrode M b-1 The resistances between them are all less than or equal to the first threshold, where 1≤a≤b≤n+1, ii) the second electrode S a-1 It does not exist, or when the second electrode S a-1 When present, the second electrode S a-1 and the first electrode M a-1 The resistance between them is greater than the first threshold, and iii) the second electrode S b+1 It does not exist, or when the second electrode S b+1 When present, the second electrode S b+1 and the first electrode M b The resistance between them is greater than the first threshold; then the second electrode S a Second electrode S b Second electrode S a Second electrode S b All the second electrodes and the first electrode M between a First electrode Mb-1 and the first electrode M a and the first electrode M b-1 All the first electrodes between them are used as working electrodes. In a preferred embodiment, when a > 1, the second electrode S is further compared. a and the first electrode M a-1 Whether the resistance between the two electrodes is less than or equal to the first threshold, when the second electrode S a and the first electrode M a-1 When the resistance between them is less than or equal to the first threshold, the first electrode M is... a-1 It also serves as the working electrode; when b < n+1, the second electrode S is further compared. b and the first electrode M b Whether the resistance between the two electrodes is less than or equal to the first threshold, when the second electrode S b and the first electrode M b When the resistance between them is less than or equal to the first threshold, the first electrode M is... b It is also used as a working electrode.

[0101] When all first impedances are less than or equal to the first threshold, it indicates that the target ablation tissue is sandwiched between all first electrodes 43 and second electrodes 33 (e.g., Figure 10 (As shown in the diagram), in this case, all first electrodes 43 and second electrodes 33 are selected as working electrodes. Alternatively, the second electrode S, which determines the critical threshold as described above... a and S b The conditions are such that all first electrodes 43 and second electrodes 33 are selected as working electrodes. Figure 10 For example, from the distal end to the proximal end of the jaws, the fixed jaw arms are respectively provided with the first electrode, second electrode 331 to the sixth electrode, second electrode 336. For the electrode S on the fixed jaw arm near the distal end of the critical threshold... a The resistances between the second electrode 331 and the first electrode 431, the second electrode 332 and the first electrode 432, the second electrode 333 and the first electrode 433, the second electrode 334 and the first electrode 434, and the second electrode 335 and the first electrode 435 are all less than or equal to the first threshold. Therefore, the second electrodes 331, 332, 333, 334, and 335 all satisfy the above-mentioned critical threshold condition for the second electrode S. a Condition i). When the second electrode 331 is considered as S a At that time, since the second electrode 331 is the first electrode on the fixed clamp arm 3 from the distal end to the proximal end, S a-1 There is no second electrode S that satisfies the above-mentioned critical threshold. a Condition ii); when the second electrode 332 is considered as S a When a is 2, S a-1The second electrode 331 has a resistance less than or equal to a first threshold value between it and the first electrode 431. Therefore, the second electrode S does not meet the aforementioned critical threshold judgment. a Condition ii); similarly, the second electrodes 333, 334, and 335 also do not satisfy the above-mentioned critical threshold judgment for the second electrode S. a Condition ii). Therefore, the second electrode S that simultaneously satisfies the above-mentioned critical threshold judgment will be... a Conditions i) and ii) The second electrode S is judged to be the critical threshold. a For the second electrode S near the proximal end of the fixed clamp arm 3, the critical threshold is... b The resistances between the second electrode 332 and the first electrode 431, the second electrode 333 and the first electrode 432, the second electrode 334 and the first electrode 433, the second electrode 335 and the first electrode 434, and the second electrode 336 and the first electrode 435 are all less than or equal to the first threshold. Therefore, the second electrodes 332, 333, 334, 335, and 336 all satisfy the above-mentioned critical threshold condition for the second electrode S. b Condition i). When the second electrode 332 is considered as S b At that time, S b+1 The second electrode 333 has a resistance less than or equal to a first threshold value between it and the first electrode 432. The second electrode S does not meet the aforementioned critical threshold judgment. b Condition iii); similarly, the second electrodes 333, 334, and 335 also satisfy the above-mentioned condition for judging the critical threshold of the second electrode S. b (condition iii) when the second electrode 336 is considered S b At that time, since the second electrode 336 is the last electrode on the fixed clamp arm from the distal end to the proximal end, S b+1 There is no second electrode S that satisfies the above-mentioned critical threshold. b Condition iii). Therefore, the second electrode S that simultaneously satisfies the above-mentioned critical threshold judgment will be... b The second electrode 336 under conditions i) and iii) is judged to be the second electrode S with a critical threshold. b Once the second electrodes 331 and 336 are determined as the electrodes for the critical threshold, the second electrodes 331-336 and the first electrodes 431-435 are selected as the working electrodes.

[0102] When the partial first impedance is less than or equal to the first threshold, it indicates that the target ablation tissue only covers a portion of the first and second electrodes, in order to Figure 12 Taking the case shown as an example, for the electrode S near the distal end of the fixed clamp arm, which is at the critical threshold... aThe determination is that the resistance between the second electrode 331 and the first electrode 431, the resistance between the second electrode 332 and the first electrode 432, and the resistance between the second electrode 333 and the first electrode 433 are all less than or equal to the first threshold. Therefore, the second electrodes 331, 332, and 333 all satisfy the above-mentioned critical threshold condition for the second electrode S. a Condition i). When the second electrode 331 is considered as S a At that time, since the second electrode 331 is the first electrode S on the fixed clamp arm 3 from the distal end to the proximal end... a-1 There is no second electrode S that satisfies the above-mentioned critical threshold. a Condition ii); when the second electrode 332 is considered as S a When a is 2, S a-1 The second electrode 331 has a resistance less than or equal to a first threshold value between it and the first electrode 431. Therefore, the second electrode S does not meet the aforementioned critical threshold judgment. a Condition ii); similarly, the second electrode 333 also does not satisfy the above-mentioned judgment critical threshold second electrode S. a Condition ii). Therefore, the second electrode S that simultaneously satisfies the above-mentioned critical threshold judgment will be... a Conditions i) and ii) The second electrode S is judged to be the critical threshold. a For the second electrode S near the proximal end of the fixed clamp arm 3, the critical threshold is... b The resistance between the second electrode 332 and the first electrode 431, and the resistance between the second electrode 333 and the first electrode 432 are both less than or equal to the first threshold. Therefore, the second electrodes 332 and 333 both satisfy the above-mentioned critical threshold condition for the second electrode S. b Condition i). When the second electrode 332 is considered as S b At that time, S b+1 The second electrode 333 has a resistance less than or equal to a first threshold value between it and the first electrode 432. The second electrode S does not meet the aforementioned critical threshold judgment. b Condition iii); when the second electrode 333 is considered as S b At that time, S b+1 The second electrode 334 has a resistance greater than a first threshold value between it and the first electrode 433. The second electrode S satisfies the aforementioned critical threshold condition. b Condition iii). Therefore, the second electrode S that simultaneously satisfies the above-mentioned critical threshold judgment will be... b The second electrode 333 under conditions i) and iii) is judged to be the second electrode S with a critical threshold. bAfter determining the two critical thresholds for the second electrodes 331 and 333, the second electrodes 331, 332, and 333 and the first electrodes 431 and 432 are selected as working electrodes. At this time, since b is 3, which is less than the total number of second electrodes on the fixed clamp arm n+1 (6), in order to further optimize the ablation effect, the relationship between the resistance between the second electrode 333 and the first electrode 433 and the first threshold is further compared. If the resistance between the second electrode 333 and the first electrode 433 is less than or equal to the first threshold, then the first electrode 433 is also selected as the working electrode. Figure 12 This invention only illustrates one scenario where the target ablation tissue covers a portion of the first and second electrodes, specifically when the target ablation tissue covers a portion of the electrodes near the distal end of the jaws. The specification details how to determine the critical threshold for the second electrode and how to select the working electrode. In other cases, such as when the target ablation tissue only covers the middle portion of the first and second electrodes of the jaws, without its edges covering the first and second electrodes 331 on the fixed clamp arm 3, or when the target ablation tissue only covers a portion of the electrodes near the proximal end of the jaws, those skilled in the art can similarly determine and select the appropriate electrode based on the aforementioned criteria; further details are omitted here.

[0103] When there is only one first electrode on the movable clamp arm 4 and multiple second electrodes on the fixed clamp arm 3, the first impedance between the first electrode and each second electrode is detected respectively, and each first impedance is compared with a first threshold. All second electrodes with a first impedance less than the first threshold, as well as the first electrode, are selected as working electrodes.

[0104] In the control method of this invention, the purpose of setting the first threshold is to distinguish between completely unused electrodes (i.e., non-working electrodes) and electrodes holding the target ablation tissue (i.e., working electrodes). The specific impedance value between the working electrodes may vary depending on the target ablation tissue and its state. Those skilled in the art can set different first thresholds according to the target ablation tissue. Preferably, the first threshold is 500 ohms. Those skilled in the art can use known methods to detect the impedance between the electrodes. For example, the impedance detection module 230 is equipped with a dielectric constant detection unit. The dielectric constant detection unit outputs an excitation signal containing a voltage signal (e.g., a sinusoidal constant current source with a peak value of 10uA) to the first electrode and the second electrode to be detected. After the excitation signal is applied to the target ablation tissue, a voltage is generated. After processing the collected voltage according to the following formula 1, the resistance between the two electrodes can be obtained.

[0105] Equation 1: Y = KS + B

[0106] Where Y is the collected voltage;

[0107] S is the resistance to be measured;

[0108] K and B are coefficients.

[0109] The central control module 260 sends the results of selecting the working electrode to the interactive control module 250 for display. The results can be displayed in a manner commonly used in the art, such as using different colors to mark the working electrode and the non-working electrode.

[0110] Furthermore, during ablation, if the target ablation tissue does not adhere well to the electrode, there is a risk of short circuit. Therefore, before performing formal pulse ablation, it is necessary to pre-check the adhesion between the target ablation tissue and the electrode. The control method of this invention includes a working electrode pre-check step S2, which achieves the above objective by controlling the pulse ablation clamp 100 and related components of the pulse ablation device 200. Specifically, the impedance detection module 230 detects the second impedance between two adjacent electrodes on the same side clamp arm and feeds it back to the central control module 260. The central control module 260 compares the second resistance between the j-th electrode and the (j+1)-th electrode on the same side clamp arm with a second threshold to determine whether the electrode meets the discharge standard. When the second resistance is less than the second threshold, the central control module 260 sends a command to the pulse generation module 240, causing the pulse generation module 240 to prohibit electrode discharge in the following manner: when j≥n / 2, the (j+1)-th electrode is prohibited from discharging; when j<n / 2, the j-th electrode is prohibited from discharging. In this invention, the second threshold is preferably 350 ohms. Similarly, the impedance between two adjacent electrodes can be detected using methods known in the art, such as the dielectric constant detection unit described above. In a preferred embodiment, the central control module 260 sends the comparison result of the impedance between adjacent electrodes and the second threshold to the interactive control module 250 for display, so as to facilitate the operator to adjust the ablation clamp accordingly. If a loose fit is found, the impedance between the connected electrodes can be adjusted to be within the second threshold range by adjusting the clamping angle of the ablation clamp or wiping and replacing the ablation clamp. Specifically, depending on the situation, after adjusting the clamping angle of the ablation clamp or wiping and replacing the ablation clamp, S1 and S2 can be repeated, or only S2 can be repeated.

[0111] After the selection and pre-inspection of the working electrode are completed, the S3 discharge control step is performed. The central control module 260 sends an instruction to the pulse generation module 240, causing the pulse generation module 240 to send a pulse signal to the working electrode. The method of forming an electrode pair and the method of discharge of the working electrode can be as follows: Figure 9-16Any of 19-29, the relevant content has been described in detail in the prior sections of this invention, and will not be repeated here. In a preferred embodiment, the k-th first electrode forms an electrode pair with the k-th second electrode and the (k+1)-th second electrode, respectively. The pulse generation module 240 sends pulse signals to one or more of the above electrode pairs according to the instructions of the central control module 260, so that the first electrode in the electrode pair is one of the positive / negative poles, and the second electrode in the electrode pair is the other of the positive / negative poles, where 1≤k≤n. By discharging the first electrode and the second electrode forming an electrode pair, the ablation gap of the target ablation tissue located in the middle part of the first electrode and the second electrode can be reduced or eliminated. Figure 6 (O in the text).

[0112] In a preferred embodiment, step S3 further includes discharge protection control, wherein the generated pulse signal is converted into a current signal, the current signal is compared with a third threshold, and if the current signal is greater than the third threshold, the pulse output is terminated. Figure 33 This is an example diagram illustrating a hardware-based gated overcurrent protection circuit. For example... Figure 33 As shown, the gated overcurrent protection circuit includes the following structure: a pulse generation control unit U1, transformers TR1 and TR2, a threshold unit VG1, and a threshold comparison output unit OP1, where N1 and N2 represent the primary and secondary coils of the transformer, respectively. The pulse signal generated by the pulse generation control unit U1 serves as the input excitation for subsequent circuits. Transformers TR1 and TR2 are used to couple and electrically isolate circuit signals. The threshold unit VG1 provides a third threshold current signal to the circuit, which is compared with the excitation signal coupled through transformer TR2. The threshold comparison output unit OP1 has two inputs and one output connected to transformer TR1. The two inputs are connected to the threshold unit VG1 (with the third threshold set) and transformer TR2, respectively. The function of the threshold comparison output unit OP1 is to compare the signal obtained from transformer TR2 with the signal provided by the threshold unit VG1, and output a corresponding level signal based on the comparison result to determine whether the signal obtained from transformer TR2 reaches or exceeds the set third threshold. If it exceeds the third threshold, the threshold comparison output unit OP1 outputs a feedback signal, which is sent to the pulse generation control unit U1 via transformer TR1 to terminate pulse output.

[0113] In another preferred embodiment, step S3 further includes summarizing and collecting ablation current values ​​in real time during the ablation process to calculate ablation energy. This is achieved by high-speed triggered AD sampling to sample the total current during the ablation process, and by using an integral algorithm to extrapolate the ablation energy. Figure 34As shown, specifically, the energy harvesting circuit includes the following structure: a pulse generation and control unit U1, a transformer M1, a data processing unit U2, and a data buffer and filtering unit IOP1, where N1 and N2 represent the primary and secondary coils of the transformer, respectively. During operation, the pulse generation and control unit U1 generates pulses. The pulse signal is coupled to the secondary side via the transformer M1, and the secondary side signal is transmitted to the data filtering and buffering unit IOP1. The data processed by IOP1 reaches the data processing unit U2. The data processing unit U2 uses triggered sampling to solve the data buffering problem. The data processing unit monitors the pulse current signal in real time and performs integration calculations on the pulse current signal according to the following formula 2 to obtain the actual output energy. If the actual output energy is lower or higher than expected, adjustments can be made by increasing or decreasing the ablation voltage to ensure that the energy output meets expectations.

[0114] Equation 2: E=P*T=U*I*T,

[0115] Where E represents the ablation energy;

[0116] P represents the power generated by ablation;

[0117] T is the sampling interval time;

[0118] U is the pulse voltage;

[0119] I represents the pulse current.

[0120] In a preferred embodiment of the present invention, before step S1, a pressure reminder step S-1a is included. In this embodiment, the pulse ablation device 200 further includes a pressure detection module 220. The pressure detection module 220 is used to detect the pressure on the first electrode on the movable clamp arm 4 and the second electrode on the fixed clamp arm 3, and feeds it back to the central control module 260. The central control module 260 compares the pressure on the first electrode and the second electrode and feeds the result back to the interactive control module 250 for display. The pressure on each electrode on both clamp arms is collected by pressure sensors on each clamp arm, and then the pressure sensors send the pressure to the pressure detection module 220. In a preferred embodiment, the central control module 260 compares whether the pressure difference between the first electrode and the second electrode is less than or equal to 5% in the following manner, and feeds the result back to the interactive control module 250: when n is odd, the pressures on the (n+1) / 2nd second electrode and the (n+3) / 2nd second electrode on the fixed clamp arm 3 and the (n+1) / 2nd first electrode on the movable clamp arm 4 are compared respectively; when n is even, the pressures on the (n / 2)th second electrode and the (n / 2)+1th second electrode on the fixed clamp arm 3 and the (n / 2)th first electrode on the movable clamp arm 4 are compared respectively. The interactive control module 250 displays the comparison results. Through the above operations, a preliminary judgment can be made on the clamping condition of the pulse ablation clamp 100 on the target ablation tissue. When the electrode pressure difference in the middle part of the two clamp arms is less than or equal to 5%, it is determined that the electrode pressures on the two clamp arms are similar, and the target ablation tissue is well clamped between the two clamp arms of the pulse ablation clamp 100. If the pressure difference between the electrodes on both clamp arms does not meet the above requirements, it can be adjusted by changing the clamping angle of the ablation clamp, and step S-1a can be repeated to test until the pressure difference is less than or equal to 5%.

[0121] In a preferred embodiment, before step S-1a, there is also step S-1b) identification control. In this embodiment, the pulse ablation clamp 100 includes an identification module containing parameter information of the pulse ablation clamp 100. The pulse ablation device 200 includes a host identification module 210, which is connected to the central control module 260 and identifies the identification module according to the instructions of the central control module 260 to obtain the parameter information of the pulse ablation clamp 100.

[0122] In summary, the pulse ablation clamp and pulse ablation device system of the present invention, by setting several second electrodes on the fixed clamp arm and placing at least a portion of the electrodes near the groove within the groove, can ablate the target tissue entering the groove, avoiding missed ablation. Simultaneously, because the first electrode on the movable clamp arm is located outside the groove, it avoids phenomena such as arcing and short circuits caused by the close proximity of the first and second electrodes. Furthermore, since there is a certain distance between the segmented electrodes, ablation gaps exist between the segmented electrodes during the ablation process. The present invention, by setting insulating protrusions between adjacent electrodes of the clamp arm, can support the tissue to be ablated at the gap location, allowing it to enter the range of the pulse electric field, thereby compensating for the ablation gap and avoiding missed ablation. Moreover, the control method of the present invention, through the selection of the working electrode and pre-inspection control, avoids short circuits caused by the electrodes not clamping the target tissue or poor adhesion between the electrodes and the target tissue. At the same time, the control method of the present invention, by controlling the cross-discharge of the electrodes on both clamp arms, avoids missed ablation of the target tissue at the middle position of the two clamp arms.

[0123] 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 forceps, comprising a forceps body and a forceps head mounted on the forceps body and consisting of a fixed forceps arm and a movable forceps arm parallel to the fixed forceps arm, the forceps head achieving clamping or releasing a target ablation tissue through movement of the movable forceps arm relative to the fixed forceps arm, the forceps body comprising a sliding slot, the fixed forceps arm being fixedly connected at a distal end of the sliding slot, the movable forceps arm moving along the sliding slot towards or away from the fixed forceps arm, characterized in that, n first electrodes are arranged on the movable jaw arm and n+1 second electrodes are arranged on the fixed jaw arm in the direction along which the jaw part extends from the distal end to the proximal end, n≥2; in the direction perpendicular to the extension of the fixed jaw arm, the projection of each of the first electrodes on the fixed jaw arm is located between two of the second electrodes; all of the first electrodes are arranged outside the sliding slot, and at least a part of the n+1th second electrode is arranged inside the sliding slot.

2. The ablation forceps according to claim 1, wherein, The n is 5.

3. The ablation forceps according to claim 1, wherein, In the direction along which the jaw part extends, the adjacent first electrodes are arranged at equal intervals, and / or the adjacent second electrodes are arranged at equal intervals.

4. The ablation forceps according to claim 3, wherein, The interval of the equal interval arrangement is 1.5-4 mm.

5. The ablation forceps according to claim 1, wherein, Each of the first electrodes and / or the second electrodes has the same length and area; the length is the distance along which each of the first electrodes and the second electrodes extends in the direction along which the jaw part extends; the area is the maximum cross-sectional area of each of the first electrodes and the second electrodes with a plane parallel to the direction along which the jaw part extends as the cross section.

6. The ablation forceps according to claim 1, wherein, The fixed jaw arm and / or the movable jaw arm has a protrusion with insulation between the adjacent first electrodes and / or between the adjacent second electrodes.

7. The ablation forceps according to claim 1, wherein, The n+1th second electrode extends into the sliding slot by 1-4 mm, and the distance between the end of the n+1th second electrode close to the sliding slot and the inner wall of the sliding slot is 2-4 mm.

8. The ablation forceps according to claim 1, wherein, Further comprising a pressure sensor.

9. The ablation forceps according to claim 1, wherein, Further comprising a distance sensor arranged correspondingly on the fixed jaw arm and the movable jaw arm.

10. The ablation forceps according to any of claims 1-9, wherein, Further comprising an impedance detection module.

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