Pulse ablation forceps

Abstract

The invention relates to the field of cardiac ablation, and provides a pair of pulse ablation forceps which comprises a forceps body and a jaw part, the jaw part is mounted on the forceps body and composed of a fixed forceps arm and a movable forceps arm parallel to the fixed forceps arm, the forceps body comprises a sliding groove, the fixed forceps arm is fixedly connected to the far end of the sliding groove, and the movable forceps arm gets close to or away from the fixed forceps arm along the sliding groove. In the extending direction of the jaw part, from the far end to the near end, n first electrodes are arranged on the movable clamp arm, n + 1 second electrodes are arranged on the fixed clamp arm, and n is larger than or equal to 2; in the direction perpendicular to the extending direction of the fixed clamp arm, the projection of each first electrode on the fixed clamp arm is located between the two second electrodes; all the first electrodes are arranged outside the sliding groove, and at least one part of the (n + 1) th second electrode is arranged in the sliding groove. According to the pulse ablation forceps, the situation of ablation leakage is avoided, meanwhile, electric arcs cannot be generated, and the ablation effect is improved.

Description

Technical Field

[0001] The present invention relates to the field of cardiac ablation, and particularly to a pulsed ablation forceps. Background Art

[0002] Atrial fibrillation is one of the most common arrhythmia conditions, and its symptoms are manifested as irregular heartbeats. The incidence of atrial fibrillation in the general population is 0.5% to 1.5%. There are 33.5 million atrial fibrillation patients worldwide, and about 8 million atrial fibrillation patients in China. The stroke risk of atrial fibrillation patients is very high. In China, stroke is an important cause of death, and strokes caused by atrial fibrillation usually have more severe clinical manifestations, higher mortality, and are more likely to recur. Therefore, the treatment of atrial fibrillation is urgent.

[0003] For the treatment of atrial fibrillation, the common method is intracardiac interventional catheter treatment, which has the advantages of less trauma, quick recovery, and high safety. However, for some relatively severe patients, surgical traumatic treatment is required. In the case of surgical thoracotomy, the commonly used devices are ablation forceps and ablation pens. At the same time, there are requirements for the treatment effect and treatment time, hoping to reduce the treatment time as much as possible while ensuring the treatment effect.

[0004] Most of the existing ablation forceps are radiofrequency ablation forceps. However, when using radiofrequency energy for ablation, the ablation damage range is not easy to control. The latest method is to use pulsed energy for ablation, and the ablation line is accurate, complete, and transmural, which is one of the effective methods for treating atrial fibrillation. The influencing factors of the ablation effect of pulsed ablation include voltage, current, pulse width, frequency, etc., which are mostly emitted by the ablation instrument within the rated safety range. For the operator, during the operation, more reliance is on experience or the preset values of the equipment for ablation, and the control of the process only lies in visually determining whether the clamping of the target ablation tissue is tight and reliable, with a large degree of uncertainty.

[0005] At the same time, in the existing ablation forceps, due to the relative movement of the two forceps arms, there is a reserved gap. When actually clamping the target ablation tissue, it is found that some tissues enter the reserved gap, and the target tissue cannot be completely ablated.

[0006] Moreover, after pulsed energy ablation, irreversible electroporation will occur in cells, but the result of this irreversible electroporation of cells cannot be directly detected and observed immediately, resulting in the inability to effectively determine the effect of pulsed ablation. Therefore, in order to reduce the possibility of surgical failure, it is necessary to improve the reliability of the ablation process as much as possible and avoid the situation of missed ablation. The current pulsed ablation forceps cannot meet the actual needs.

[0007] In view of this, a new pulsed ablation forceps is needed for surgical pulsed ablation. Summary of the Invention

[0008] To overcome the above problems existing in the prior art, the present invention provides an efficient and safe pulsed ablation forceps, which can avoid the situation of missed ablation.

[0009] The present invention provides a pulsed ablation forceps, including a forceps body and a jaw portion mounted on the forceps body and composed of a fixed jaw arm and a movable jaw arm parallel to the fixed jaw arm. The jaw portion realizes clamping or releasing of the target ablation tissue through the movement of the movable jaw arm relative to the fixed jaw arm. The forceps body includes a chute. The fixed jaw arm is fixedly connected to the distal end of the chute. The movable jaw arm approaches or moves away from the fixed jaw arm along the chute. Along the extending direction of the jaw portion, from the distal end to the proximal end, n first electrodes are provided on the movable jaw arm, and n + 1 second electrodes are provided on the fixed jaw arm, where n ≥ 2; in the direction perpendicular to the extending direction of the fixed jaw arm, the projection of each first electrode on the fixed jaw arm is located between two second electrodes; all the first electrodes are arranged outside the chute, and at least a part of the (n + 1)th second electrode is arranged inside the chute.

[0010] More preferably, n is 5.

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

[0012] More preferably, the interval range of the equal interval arrangement is 1.5 - 4 mm.

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

[0014] Preferably, on the fixed jaw arm and / or the movable jaw arm, there are insulating protrusions between adjacent first electrodes and / or between adjacent second electrodes.

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

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

[0017] Preferably, it further includes distance sensors correspondingly arranged on the fixed jaw arm and the movable jaw arm.

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

[0019] The technical effects achieved by the pulsed ablation forceps of the present invention are as follows: 1) The ablation forceps of the present invention uses pulsed energy for ablation. Compared with ablation using radiofrequency energy, the boundary / scope of pulsed ablation is obvious. Only when the voltage threshold is reached will irreversible electroporation be caused to the target ablation tissue, and myocardial tissue can be selectively ablated. It will not accidentally damage other organs as easily as radiofrequency ablation, and will not affect the tissue at non-ablation sites, greatly reducing the occurrence of complications. Using pulsed electric field energy for ablation has a short action time, hardly generates thermal effects, does not require cold saline perfusion for cooling, and has a faster recovery rate. Compared with cryoablation, the product structure is simpler.

[0020] 2) The pulsed ablation forceps of the present invention adopts two clamping arms with a parallel push-pull type clamping. Compared with scissor-type clamping arms, it can more easily hold the target ablation tissue between the two clamping arms, and the fixed clamping arm is located farther from the 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 close to the movable clamping arm), which can be more easily observed by the operator, so as to visually perceive whether the tissue is clamped.

[0021] 3) In actual applications, the inventor found that when the first electrode and the second electrode are arranged in one-to-one correspondence, that is, when the projection of the first electrode coincides with the second electrode in the direction perpendicular to the extension of the fixed clamping arm, and the upper and lower electrodes are respectively set as positive and negative electrodes for low-voltage discharge (800 - 1200V), an ablation area gap (such as Figure 6 O in) is likely to appear between the movable clamping arm and the fixed clamping arm. By setting the first electrode to have one less than the second electrode, and making the projection of the first electrode located between the two second electrodes in the direction perpendicular to the extension of the fixed clamping arm, that is, the first electrode and the second electrode are arranged in an interleaved manner, not only can the ablation scope be controlled more conveniently and efficiently by controlling the number and position of the discharging electrodes, avoiding the risk of arc generation due to the too-close distance between the first electrode and the second electrode, but also it is beneficial to reduce or eliminate the above-mentioned ablation area gap and make the ablation more complete.

[0022] 4) The inventors found that although the surgeon will place the target ablation tissue at the center of the clamp arm as much as possible during the operation, due to the volume of the target ablation tissue and other reasons, in the process of clamping the target ablation tissue, pushing the movable clamp arm will cause the target ablation tissue to be compressed / squeezed to both sides along the fixed clamp arm, and there is a possibility that the target ablation tissue will enter the slide groove. On conventional ablation clamps, the electrodes are usually a certain distance away from the slide groove, and will not be set in the slide groove, which will cause missed ablation. To solve this problem, the pulse ablation clamp of the present invention is provided with n+1 second electrodes on the fixed clamp arm, and the n+1 second electrode is at least partially set in the slide groove, so as to achieve ablation of the target ablation tissue entering the slide groove and prevent missed ablation. In addition, by setting the first electrode on the movable clamp arm outside the slide groove, the risk of arc and short circuit caused by setting both the first electrode and the second electrode in the slide groove and being too close is avoided.

[0023] 5) In addition, due to the distance between electrodes, pulse intensity and other reasons, during the ablation process, the pulse electric field generated between the positive and negative electrodes may not cover all the preset ablation ranges, such as Figure 10 , 12 , 17 and 23, there is an ablation gap M. The present invention can support the tissue to be ablated at the gap position and bring it into the range of the pulse electric field by providing insulating protrusions between adjacent electrodes of the fixed forceps arm and / or the movable forceps arm, thereby filling the ablation gap and avoiding missed ablation.

[0024] 6) When the pulse ablation forceps of the present invention are used, the position and number of electrodes clamping the target ablation tissue can be determined by detecting the impedance between the first electrode and the second electrode, thereby determining the working electrode, and avoiding the occurrence of short circuits and the like 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 ipsilateral forceps arm to determine the fit between the working electrode and the target ablation tissue, so as to avoid the occurrence of short circuits and the like caused by the unreliable fit between the working electrode and the target ablation tissue. In addition, the present invention can also set a pressure reminder to detect whether the pressure difference between the first electrode and the second electrode is within a certain range, and preliminarily determine the clamping condition of the ablation forceps on the target ablation tissue. In addition, when performing discharge ablation, the present invention preferably forms an electrode pair with the first electrode and the second electrode for discharge, thereby reducing and eliminating the ablation gap between the first electrode and the second electrode. The control method of the present invention also includes discharge protection control to avoid adverse consequences caused by excessive pulse signals applied to tissues. In summary, the control method of the present invention is safe and efficient, and can avoid the occurrence of short circuits, ablation gaps, and the like as much as possible. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1Schematic diagram of a pulsed ablation forceps according to an embodiment of the present invention; Figure 2 Exploded view of a pulsed ablation forceps according to an embodiment of the present invention; Figure 3 Schematic diagram of the fixed forceps arm and the movable forceps arm of a pulsed ablation forceps according to an embodiment of the present invention; Figure 4 Schematic diagram of the fixed forceps arm and the movable forceps arm of a pulsed ablation forceps according to another embodiment of the present invention; Figure 5 Schematic diagram of an ablation forceps of the prior art clamping a porcine atrial appendage; Figure 6 Simulation diagram of the ablation area of a pulsed ablation forceps of the prior art; Figure 7 Simulation diagram of the ablation area of a pulsed ablation forceps according to an embodiment of the present invention; Figure 8 Schematic diagram of the configuration of the first electrode and the second electrode in the fixed forceps arm and the movable forceps arm of a pulsed ablation forceps according to an embodiment of the present invention; Figure 9 For Figure 8 Schematic diagram of the electric field lines of an ablation method of the pulsed ablation forceps shown; Figure 10 For Figure 9 Schematic diagram of the ablation area generated by the ablation method shown; Figure 11 For Figure 8 Schematic diagram of the electric field lines of another ablation method of the pulsed ablation forceps shown; Figure 12 For Figure 11 Schematic diagram of the ablation area generated by the ablation method shown; Figure 13 For Figure 8 Schematic diagram of the electric field lines of another ablation method of the pulsed ablation forceps shown; Figure 14 For Figure 13 Schematic diagram of the ablation area generated by the ablation method shown; Figure 15 For Figure 8 Schematic diagram of the electric field lines of another ablation method of the pulsed ablation forceps shown; Figure 16 For Figure 13 And Figure 15 Schematic diagram of the ablation area generated by superimposing the ablation methods shown; Figure 17 Ablation simulation results of a pulsed ablation forceps according to an embodiment of the present invention on a potato; Figure 18The pulsed ablation forceps of an embodiment of the present invention, wherein the fixed forceps arm and the movable forceps arm are provided with insulating protrusions; Figure 19 is Figure 18 A schematic diagram of the electric field lines of an ablation method of the pulsed ablation forceps shown; Figure 20 is Figure 19 A schematic diagram of the ablation area generated by the ablation method shown; Figure 21 A schematic diagram of the configuration of the first electrode and the second electrode in the fixed forceps arm and the movable forceps arm of the pulsed ablation forceps of another embodiment of the present invention; Figure 22 is Figure 21 A schematic diagram of the electric field lines of an ablation method of the pulsed ablation forceps shown; Figure 23 is Figure 22 A schematic diagram of the ablation area generated by the ablation method shown; Figure 24 is Figure 21 A schematic diagram of the electric field lines of another ablation method of the pulsed ablation forceps shown; Figure 25 is Figure 24 A schematic diagram of the ablation area generated by the ablation method shown; Figure 26 is Figure 21 A schematic diagram of the electric field of another ablation method of the pulsed ablation forceps shown; Figure 27 is Figure 26 A schematic diagram of the ablation area generated by the ablation method shown; Figure 28 The pulsed ablation forceps of an embodiment of the present invention, wherein the fixed forceps arm is provided with insulating protrusions; Figure 29 is Figure 28 A schematic diagram of the electric field lines of an ablation method of the pulsed ablation forceps shown; Figure 30 is Figure 29 A schematic diagram of the ablation area generated by the ablation method shown; Figure 31 A schematic diagram of the pulsed ablation system of an embodiment of the present invention; Figure 32 A flowchart of the control method of an embodiment of the present invention; Figure 33 A schematic diagram of the discharge protection circuit of the present invention; Figure 34 A schematic diagram of the circuit for real-time collecting pulsed current to calculate ablation energy of the present invention. Detailed implementation manners

[0026] Definition Distal: In this specification, when referring to the "distal" side of the device of the present invention, this term means the side relatively far from the user. For the jaw portion of the present invention, the "distal" side refers to the side away from the chute.

[0027] Proximal: In this specification, when referring to the "proximal" side of the device of the present invention, this term means the side relatively close to the user. For the jaw portion of the present invention, the "proximal" side refers to the side close to the chute.

[0028] Distal end: In this specification, when referring to the "distal end" of the system or device of the present invention, this term generally means the end relatively far from the user. For the jaw portion of the present invention, the "distal end" refers to the end away from the chute.

[0029] Proximal end: In this specification, when referring to the "proximal end" of the system or device of the present invention, this term generally means the end relatively close to the user. For the jaw portion of the present invention, the "proximal end" refers to the end close to the chute.

[0030] Several: In this specification, "several" means more than one, that is, 2 or more, such as 2, 3, 4, 5, 6, 7, etc.

[0031] Terms such as "installed", "connected", "joined", "fixed", etc. should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or integrated; it can be a mechanical connection or an electrical connection; it can be directly connected or indirectly connected through an intermediate medium, and it can be the communication inside two components or the interaction relationship between two components, unless otherwise clearly defined. For those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood according to the specific circumstances.

[0032] The term "electroporation" refers to applying an electric field to the cell membrane to change the permeability of the cell membrane to the extracellular environment. As used herein, the term "irreversible electroporation" refers to applying an electric field to the cell membrane to permanently change the permeability of the cell membrane to the extracellular environment. For example, one or more pores can be observed to form in the cell membrane of cells subjected to irreversible electroporation, and the one or more pores still exist after the electric field is removed.

[0033] The preferred embodiments of the present invention will be 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 accompanying drawings are only used to illustrate the best implementation mode of the present invention, rather than limiting the scope of the present invention to these embodiments. The present invention can be variously improved and changed on the basis of the following embodiments. These improvements and changes are all within the scope of the present invention.

[0034] Figure 1 and Figure 2 FIG. shows a schematic diagram of a pulsed ablation forceps 100 according to an embodiment of the present invention, which is a parallel push-pull type ablation forceps applying pulsed energy, and includes a forceps body and a jaw portion mounted on the forceps body and composed of a fixed jaw arm 3 and a movable jaw arm 4 parallel to the fixed jaw arm 3. The jaw portion can clamp or release the target ablation tissue by the movement of the movable jaw arm 4 relative to the fixed jaw arm 3. The forceps body includes a chute 23, the fixed jaw arm 3 is fixedly connected to the distal end of the chute 23, and the movable jaw arm 4 approaches or separates from the fixed jaw arm 3 along the chute 23. The pulsed ablation forceps 100 of the present invention adopts two jaw arms 3 and 4 with parallel push-pull type clamping. Compared with the scissor-type jaw arms, it can more easily hold the target ablation tissue between the two jaw arms 3 and 4, and the fixed jaw arm 3 is located at a farther end than the movable jaw arm 4. The target ablation tissue is controlled between the fixed jaw arm 3 and the movable jaw arm 4 and is supported by the fixed jaw arm 3. When the movable jaw arm 4 is pushed to clamp the target ablation tissue, the change of the target ablation tissue is mainly controlled at the relative proximal end (the end close to the movable jaw arm 4), which can be more easily observed by the operator, so as to visually perceive whether the tissue is clamped.

[0035] The structure for making the movable jaw arm 4 approach or separate from the fixed jaw arm 3 along the chute 23 is known and easy to implement for those skilled in the art. For example, CN102198012A discloses driving the movable jaw to approach or separate from the fixed jaw by a push rod, and the present invention does not limit this.

[0036] Only as an example, the present invention provides the following structure. The pulsed ablation forceps 100 of the present invention includes a handle 1, an extension rod 2, a fixed jaw arm 3, and a movable jaw arm 4. The extension rod 2 is connected to the handle 1 and extends distally. A chute 23 is provided on the extension rod 2.

[0037] The handle 1 includes a handle housing 11, a push-pull member 12, and a button post 13. A gripping portion is provided on the handle housing 11. The gripping portion may be provided with anti-slip lines to increase the frictional force and facilitate gripping. The gripping portion is cooperatively provided with the push-pull member 12 for the convenience of the operator. During use, the palm of the operator contacts the push-pull member 12, and the fingers press the gripping portion. By applying force with the palm, the push-pull member 12 can be pushed to move the movable clamp arm 4, lock the pulsed ablation forceps 100, etc. Part of the push-pull member 12 is exposed outside the handle housing 11 and passes through the handle housing 11 to be connected to the extension rod 2. Pushing the push-pull member 12 will drive the inner tube 21 of the extension rod 2 to move, thereby pushing the movable clamp arm 4 to move 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 pushes the movable clamp arm 4 to move, and the first spring 122 and the second spring 123 play a reset role. During the process of the movable clamp arm 4 moving from the proximal side to the distal side, that is, during the process of the movable clamp arm 4 being pushed from away from the fixed clamp arm 3 to approaching the fixed clamp arm 3, the first spring 122 is compressed by force, and the second spring 123 is stretched. A button post 13 is provided on the handle housing 11. In an embodiment of the present invention, the button post 13 is a limit post at a fixed position, and a limit portion and a release portion (not shown in the figure) are correspondingly provided on the push-pull member 12. Before the movable clamp arm 4 of the pulsed ablation forceps 100 reaches the preset position after being pushed from the free state, the button post 13 is limited in the corresponding hole of the handle housing 11 by the limit portion 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 limit portion to reach the release portion. At this time, the button post 13 pops out of the handle housing 11 to form a limit, making the pulsed ablation forceps 100 in a limit-fixed state, thereby locking the pulsed ablation forceps 100. In the above embodiment, the first spring 122 is connected to the handle housing 11 and the inner tube 21 of the extension rod 2, and can provide the elastic force required for the inner tube 21 to rebound. The second spring 123 abuts against one 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 a limit, thereby solving the clamping and ablation of heart tissues with different thicknesses. The operator does not need to worry about the surgical difficulties caused by the differences in the heart wall thickness of each patient, effectively reducing the surgical difficulty, protecting the tissues to be ablated with different thicknesses from being damaged by the clamping force, and at the same time being able to effectively adhere to the surface of the ablation tissue. When the ablation is completed, pressing the button post 13, the movable clamp arm 4 will automatically push the extension rod 2 back under the action of the double-spring structure and return to the initial position, and ablation at the next position can be carried out. 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 object clamped between the fixed clamp arm 3 and the movable clamp arm 4 can be between 0 and 20 millimeters. In the present invention, the clamping force between the movable clamp arm 4 and the fixed clamp arm 3 is provided by the elastic forces of the two springs 122 and 123.Further, in other embodiments of the present application, the button post 13 is a starting device. In this embodiment, the handle 1 may further include a rotating device disposed within the handle housing 11. The rotating device is an electric device activated by the button post 13. After being activated by pressing the button post 13, the electric device pushes the movable jaw arm 4 to move until the reaction pressure exerted on the movable jaw arm 4 by the two springs 122 and 123 reaches a preset value. After ablation is completed, the rotating device can be reversed by pressing the button post 13 again to drive the movable jaw arm 4 away from the fixed jaw arm 3. In addition, the handle 1 includes a connecting cable for connecting to an external ablation device to achieve electrical connection.

[0038] The extension rod 2 is used to extend the length of the ablation forceps 100, facilitating the insertion of the jaw arms into the human body for operation. It includes an inner tube 21, an outer tube 22, and a chute 23. The outer tube 22 is fixedly connected to the handle housing 11, and the chute 23 is fixed to the distal end of the outer tube 22. The chute 23 is a component having an opening formed by two side walls and an inner wall connecting the two side walls. One side of the fixed jaw arm 3 and the movable jaw arm 4 enters through the opening and is connected to the chute 23. In a direction perpendicular to the outer tube 22, there is a certain distance from the opening of the chute 23 to its inner wall, so that the chute 23 has a depth to accommodate the fixed jaw arm 3 and the sliding jaw arm 4. And along the extending direction of the outer tube 22, the chute 23 has a certain length to accommodate the inner tube 21 and the sliding of the movable jaw arm 4. In a direction perpendicular to the outer tube 22, the cross-sectional shape of the chute 23 can be a semi-circular shape, a square shape, a rectangular shape, or a shape formed by two straight lines connected by an arc, etc., having an opening and being hollow, or it can be other shapes that can be adapted to the shape of the outer tube 22. The fixed jaw arm 3 is fixedly connected to the distal end of the chute 23. The outer tube 22 is sleeved outside the inner tube 21, and the inner tube 21 can move relative to the outer tube 22. The movable jaw 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 by 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 drives the movable jaw arm 4 to slide in the chute 23, and the movable jaw arm 4 moves parallel to the fixed jaw arm 3. Further, the inner tube 21 and the outer tube 22 can be made of a metal shaped hose, and the doctor can manually adjust the bending shape according to the specific tissue structure position to adapt to various surgical conditions.

[0039] As Figure 3 and Figure 4 shown, the fixed jaw arm 3 and the movable jaw arm 4 can be set to an arc shape with a length corresponding to the arc, or a straight shape with the same length. In addition to the above shapes, they can also be set to any applicable shape according to actual needs, as long as the fixed jaw arm 3 and the movable jaw arm 4 are arranged in parallel and can clamp the target ablation tissue. In one embodiment, along the direction of extension of the jaw opening part ( Figure 4in the X direction), the lengths of the fixed jaw arm 3 and the movable jaw arm 4 can be 5 - 10 cm. When they are arc-shaped, the radian can be 1 - 15°. Moreover, the angles of the fixed jaw arm 3 and the movable jaw arm 4 relative to the plane of the handle housing 11 are the same, and the angle can be 90 - 120°.

[0040] In the present invention, the fixed jaw arm 3 and the movable jaw arm 4 are oppositely arranged. Along the extending direction of the jaw portion, from the distal end to the proximal end, n (n≥2) first electrodes 43 are provided on the movable jaw arm 4, and n + 1 second electrodes 33 are provided on the fixed jaw arm 3. Each first electrode 43 and each second electrode 33 are respectively electrically connected to the pulse generator through wires, and each first electrode 43 and each second electrode 33 can be respectively set to be non-powered, negative or positive. The first electrode 43 is arranged outside the chute 23, and at least a part of the (n + 1)-th second electrode among several second electrodes 33 close to the chute 23 is arranged inside the chute 23. As Figure 3 and 4 shown, at least a part of the second electrode 33 marked by the dotted line box falls inside the chute 23. That is, along the extending direction of the chute 23 ( Figure 4 in the Y-axis direction), the projection of the chute 23 on the movable jaw arm 4 does not cover the first electrode 43, while the projection of the chute 23 on the fixed jaw arm 3 covers at least a part of the (n + 1)-th second electrode close to the chute 23. Along the extending direction of the fixed jaw arm 3 ( Figure 4 in the X-axis direction), the depth of the chute is generally 6 - 8 mm. In a preferred embodiment, the length of the second electrode 33 close to the chute 23 extending into the chute 23 is 1 - 4 mm, and the distance between the end of the (n + 1)-th second electrode close to the chute and the inner wall of the chute is 2 - 4 mm.

[0041] In practical applications, due to reasons such as the volume of the target ablation tissue, during the process of clamping the target ablation tissue, when pushing the movable jaw arm 4, the target ablation tissue will be compressed / squeezed along the fixed jaw arm 3 to both sides of the jaw arm, and there is a possibility that the target ablation tissue enters the chute 23. Figure 5Taking the auricle of a pig's heart as an example, it can be seen that when the ablation forceps clamps the auricle, some tissues will be clamped and squeezed into the space of the chute. In the ablation forceps of the prior art, since there is no electrode in the chute, there will be a situation of missed ablation. In the present invention, a plurality of second electrodes 33 are arranged on the fixed forceps arm 3, and at least a part of the second electrodes close to the chute 23 is arranged in the chute 23, so as to realize the ablation of the target ablation tissue entering the chute 23 and prevent the problem of missed ablation. Moreover, each electrode on the fixed forceps arm 3 and the sliding forceps arm 4 is connected with a corresponding wire, and these wires are attached to the inner wall of the chute 23 and introduced into the extension rod 2 through the chute 23, and these wires will occupy a part of the space in the chute 23. Arranging the first electrode 43 on the sliding forceps arm 4 outside the chute 23 can prevent problems such as breakdown caused by the electrode on the sliding forceps arm 4 extending into the chute 23 and the distance between the electrode and the inner wall of the chute 23 and / or the wire in the chute 23 being too close.

[0042] In addition, as Figure 6 shown, if the first electrode 43 and the second electrode 33 are in one-to-one correspondence up and down, that is, in the direction perpendicular to the extension of the forceps mouth part, the projection of the first electrode 43 on the fixed forceps 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 notch O in the ablation area is likely to appear between the fixed forceps arm 3 and the movable forceps arm 4. In the present invention, however, the first electrode 43 and the second electrode 33 are arranged in an alternating manner, that is, in the direction perpendicular to the extension of the fixed forceps arm 3, the projection of each first electrode 43 on the fixed forceps arm 3 is located between two second electrodes 33. For example, number the electrodes on the fixed forceps arm 3 and the movable forceps arm 4. From the direction away from the extension rod 2 to the direction close to the extension rod 2, the n first electrodes 43 on the movable forceps arm 4 are successively M1, M2, M3... M n , and the n + 1 second electrodes 33 on the fixed forceps arm 3 are successively S1, S2, S3... S n+1 , then in the direction perpendicular to the extension of the fixed forceps arm 3, the projection of M1 on the fixed forceps arm 3 is located between S1 and S2, the projection of M2 on the fixed forceps arm 3 is located between S2 and S3, and so on. The projection of M n on the fixed forceps arm 3 is located between S n and S n+1 , and M n does not extend into the chute 23, and at least a part of S n+1 falls into the chute 23. By setting like this, as Figure 7 shown, during low-voltage discharge, the pulsed ablation forceps 100 of the present invention can reduce and eliminate the above-mentioned notch O. Figure 17 For the simulated ablation carried out on a potato under the same conditions, it can be seen that no ablation notch appears at the intermediate position between the first electrode 43 and the second electrode 33.

[0043] By arranging the first electrode 43 and the second electrode 33 as described above, the pulsed ablation forceps 100 of the present invention can not only prevent the problems of ablation leakage and arc generation between the inside of the chute 23 and the two jaws, but also, the arrangement of the segmented electrodes can more conveniently and efficiently control the ablation range by controlling the number and position of the electrodes for discharging. For example, when the target ablation tissue to be clamped does not cover all the first electrodes 43 and the second electrodes 33, only the first electrodes 43 and the second electrodes 33 covered by the target ablation tissue can be used to ablate the target ablation tissue.

[0044] In a preferred embodiment of the present invention, n is 5, that is, 5 first electrodes 43 are provided on the sliding jaw arm 4, and 6 second electrodes 33 are provided on the fixed jaw arm 3. In a preferred embodiment of the present invention, the adjacent first electrodes 43 are arranged at equal intervals, and / or the adjacent second electrodes 33 are arranged at equal intervals. Preferably, the interval range of the equal interval arrangement is 1.5 - 4 mm. In a preferred embodiment of the present invention, each of the first electrodes 43 and / or the second electrodes 33 has the same length and area. Here, the length is the distance that each of the first electrodes 43 and the second electrodes 33 extends in the direction of extension of the jaw portion, and the area is the cross-sectional area of each of the first electrodes 43 and the second electrodes 33 with a plane parallel to the direction of extension of the jaw portion as the cross-section, that is, the area of the surface in contact with the target ablation tissue of the electrode. In a preferred embodiment of the present invention, the length of the first electrode 43 and the second electrode 33 is 6 mm, and the area is 16 mm 2 . By arranging the first electrodes 43 and the second electrodes 33 with the above length and area at equal intervals, not only can the target ablation tissue entering the chute be ablated, but also the ablation effect at each part of the target ablation tissue clamped between the sliding jaw arm 4 and the fixed jaw arm 3 can be made more consistent, and the ablation effect is better. There is no special limitation on the shapes of the first electrode 43 and the second electrode 33. In a preferred embodiment of the present invention, both the first electrode 43 and the second electrode 33 are elliptical. In the case of high voltage, the tips, protrusions, edges, etc. of the electrodes will all cause problems of tip discharge, resulting in the generation of arcs and a reduction in safety. Therefore, chamfering the original rectangular electrode sheet to form an ellipse can effectively prevent the problem of tip discharge.

[0045] In an embodiment of the present invention, as Figure 8As shown, the sliding jaw arm 4 includes a first jaw seat 41, a first insulating layer 42 provided on the first jaw seat 41, and a first electrode 43 provided within the first insulating layer 42 and having a surface for contacting the target ablation tissue. In the present embodiment, the first electrode 43 includes first electrodes 431, 432, 433, 434, and 435. Correspondingly, the fixed jaw arm 3 includes a second jaw seat 31, a second insulating layer 32 provided on the second jaw seat 31, and a second electrode 33 provided within the second insulating layer 32 and having a surface for contacting the target ablation tissue. In the present embodiment, the second electrode 33 includes second electrodes 331, 332, 333, 334, 335, and 336. Among them, in the direction perpendicular to the fixed jaw arm 3 (i.e., Figure 8 the Y-axis direction in), the projection of the first electrode 431 on the fixed jaw arm 3 is located between the second electrodes 331 and 332, the projection of the first electrode 432 on the fixed jaw arm 3 is located between the second electrodes 332 and 333, and so on. The projection of the first electrode 435 on the fixed jaw arm 3 is located between the second electrodes 335 and 336, and all the first electrodes 43 do not fall into the chute 23 (not shown), while at least a part of the second electrode 336 is provided within the chute 23.

[0046] According to Figure 8 the pulsed ablation forceps shown, different ablation methods can be adopted according to the size of the target ablation tissue. As Figure 9 and 10 shown, when the target ablation tissue D covers all the first electrodes 431, 432, 433, 434, 435 and the second electrodes 331, 332, 333, 334, 335, 336, all the first electrodes and the second electrodes participate in ablation. For example, an electrical signal is transmitted to all the first electrodes 431, 432, 433, 434, 435 through a pulse generator to make them negative electrodes, and an electrical signal is transmitted to all the second electrodes 331, 332, 333, 334, 335, 336 to make them positive electrodes (it is also possible to make all the first electrodes 43 positive electrodes and all the second electrodes 33 negative electrodes), thereby delivering pulsed energy to the target ablation tissue D. The electric field lines between all the first electrodes and the second electrodes are as Figure 9 shown, and the formed ablation region T is as Figure 10 shown. It can be seen that even if the target ablation tissue D enters the chute 23 (not shown) due to volume or extrusion reasons, since at least a part of the second electrode 336 is located within the chute 23, the formed ablation region T can cover the target ablation tissue D located within the chute 23, thus avoiding missed ablation. In addition, as Figure 11 and 12As shown, when the target ablation tissue D only covers part of the first electrodes 431, 432, 433 and the second electrodes 331, 332, 333, an electrical signal is transmitted to the covered first electrodes 431, 432, 433 and the second electrodes 331, 332, 333 through a pulse generator, making the first electrodes 431, 432, 433 the negative electrodes and the second electrodes 331, 332, 333 the positive electrodes respectively (it is also possible to make the first electrodes 431, 432, 433 the positive electrodes and the second electrodes 331, 332, 333 the negative electrodes), and no electrical signal is transmitted 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 Figure 11 shown, and the formed ablation region T is as Figure 12 shown. It can be seen that the ablation region only covers the target ablation tissue D. No electric field is generated between the first electrodes 434, 435 and the second electrodes 334, 335, 336, avoiding the occurrence of risks such as short circuits and arcs caused by the absence of target ablation tissue between the first electrode and the second electrode.

[0047] In some embodiments, when the target ablation tissue is relatively thin, ablation can also be performed using only the first electrode or the second electrode. As Figure 13 and 14 shown, no electrical signal is transmitted to all the first electrodes 431, 432, 433, 434, 435, and the adjacent second electrodes are respectively configured as positive and negative electrodes. In Figure 13 , the second electrode 331 is configured as the positive electrode, the second electrode 332 is configured as the negative electrode, and the second electrode 333 is configured as the positive electrode. An electric field is generated between the adjacent second electrodes, and the formed ablation region T is as Figure 14 shown. In addition, as Figure 15 shown, it can also be configured that no electrical signal is transmitted to all the second electrodes 331, 332, 333, 334, 335, 336, and the adjacent first electrodes are respectively configured as positive and negative electrodes. The first electrode 431 is configured as the positive electrode, the first electrode 432 is configured as the negative electrode, and the first electrode 433 is configured as the positive electrode. An electric field is generated between the adjacent first electrodes to form an ablation region. In addition, when the target ablation tissue is relatively thick, ablation using only one side of the electrode may not be complete. In this case, to avoid incomplete ablation using a single-sided electrode, as Figure 16 shown, it can be configured to first use the adjacent second electrodes for ablation and then use the adjacent first electrodes for secondary ablation, so that the superposition of the two ablation regions can avoid missed ablation. In addition, although Figure 13 - 16Only the case of ablation using partial first electrodes and second electrodes is shown, but those skilled in the art understand that when the target ablation tissue covers all the first electrodes and second electrodes, the ablation method shown in Figure 13 - 16 can also be used, and the same configuration can be made for all the first electrodes and second electrodes to ablate the target ablation tissue.

[0048] As Figure 10 and 12 show, when the polarities of the first electrode and the second electrode are opposite, due to the distance between two adjacent electrodes on the same clamping arm, there may be areas that cannot be covered by the electric field lines. Therefore, a notch M in the ablation area may be generated between two adjacent electrodes on the same clamping arm, and the target ablation tissue located at the notch M cannot be ablated. Figure 17 For the simulated ablation performed on a potato using the pulsed ablation forceps shown in Figure 8 in the discharge manner shown in Figure 9 , it can be seen that there is a notch M between the two electrodes. To prevent the problem of missed ablation of the target ablation tissue at the notch M, in an embodiment of the present invention, insulating protrusions are provided between two adjacent electrodes on the same clamping arm. The insulating protrusions can hold up the target ablation tissue at the notch M, making it enter the ablation area, and thus can prevent missed ablation. The insulating protrusions can be provided only between two adjacent first electrodes, or only between two adjacent second electrodes, or between two adjacent first electrodes and between two adjacent second electrodes. As Figure 18 shows, first protrusions 441, 442, 443, and 444 are respectively provided between first electrodes 431, 432, 433, 434, and 435, and second protrusions 341, 342, 343, 344, and 345 are respectively provided between second electrodes 331, 332, 333, 334, 335, and 336. As Figure 19 and 20 show, the first protrusions 441, 442, 443, 444 and the second protrusions 341, 342, 343, 344, 345 hold up the target ablation tissue at the corresponding positions, making the target ablation tissue originally located at the notch M enter the range of the electric field and fall into the ablation area T, so that it can be ablated. The shape of the insulating protrusions is not particularly limited, and an arch shape is preferred. In the cross-section of the insulating protrusions in a plane perpendicular to the extending direction of the clamping portion, the height of the insulating protrusions, that is, the longest distance that the insulating protrusions extend towards the opposite clamping jaw starting from the plane where the surface in contact with the electrode and the tissue is located, is less than or equal to 5 mm; the width of the insulating protrusions, that is, the longest distance that the insulating protrusions extend along the extending direction of the clamping jaw, is less than or equal to the distance between two adjacent electrodes, for example, 3.5 mm.

[0049] In another embodiment of the present invention, the pulsed ablation forceps of the present invention may also have the following structure: only one first electrode is provided on the movable forceps arm 4, and a plurality of second electrodes are provided on the fixed forceps arm 3. The first electrode is arranged outside the sliding groove 23, that is, it does not extend into the sliding groove, while at least a part of the second electrode close to the sliding groove 23 is arranged in the sliding groove 23. Thus, not only can the ablation of the target ablation tissue falling into the sliding groove 23 be realized, but also the generation of electric arcs due to the too-close distance between the first electrode and the second electrode can be avoided. At the same time, since only one first electrode is provided on the movable forceps arm 4, the structure is simpler. Figure 21 An example in the above embodiment is shown. In this embodiment, 6 second electrodes are taken as an example for illustration. Those skilled in the art can know that the number of second electrodes can be greater than or less than 6. As Figure 21 shown, only one first electrode 43' is provided on the movable forceps arm 4, and 6 second electrodes 33 are provided on the fixed forceps arm 3, namely second electrodes 331, 332, 333, 334, 335, and 336. At least a part of the second electrode 336 extends into the sliding groove 23 (not shown in the figure), and the first electrode 43' is arranged outside the sliding groove 23. The length of the first electrode 43' can be set according to the electrodes in the existing ablation forceps with a single electrode provided on one side of the forceps arm. For example, in order to contact the target ablation tissue as much as possible, the first electrode 43' extends along the extending direction of the sliding forceps arm 4, as long as the end close to the sliding groove 23 does not extend into the sliding groove 23. Preferably, in the direction perpendicular to the fixed forceps arm 3, the projection of the first electrode 43' on the fixed forceps arm 3 simultaneously covers at least a part of the second electrode 331 and the second electrode 336. By setting it in this way, the area of the ablation region can be enlarged and the occurrence of missed ablation can be reduced.

[0050] As Figure 21 shown in the pulsed ablation forceps, different ablation methods can be adopted according to the size of the target ablation tissue. As Figure 22 and 23 shown, when the target ablation tissue D covers the first electrode 43' and all the second electrodes 331, 332, 333, 334, 335, 336, the first electrode 43' and all the second electrodes participate in the ablation. For example, an electrical signal is transmitted to the first electrode 43' through a pulse generator to make it negative, and electrical signals are transmitted to all the second electrodes 331, 332, 333, 334, 335, 336 to make them positive (it can also make the first electrode 43' positive and all the second electrodes negative), thereby delivering pulsed 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, 336 are as Figure 22As shown, the formed ablation region T is as shown in 23. It can be seen that even if the target ablation tissue D enters the chute 23 (not shown) due to volume or extrusion reasons, since at least a part of the second electrode 336 is located in the chute 23, the formed ablation region T can cover the target ablation tissue D located in the chute 23, thus avoiding missed ablation. In addition, as Figure 24 and 25 shown, when the target ablation tissue D only covers a part of a part of the first electrode 43' and a part of the second electrodes 331, 332, 333, an electrical signal is transmitted to the first electrode 43' and the covered second electrodes 331, 332, 333 through a pulse generator, making the first electrode 43' the negative electrode and the second electrodes 331, 332, 333 the positive electrodes respectively (it is also possible to make the first electrode 43' the positive electrode and the second electrodes 331, 332, 333 the negative electrodes), and no electrical signal is transmitted to the remaining 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 electrode 43' and the second electrodes 331, 332, 333 are as Figure 24 shown, and the formed ablation region T is as Figure 25 shown. It can be seen that the ablation region only covers the target ablation tissue D. No electric field is generated between the first electrode 43' and the second electrodes 334, 335, 336, avoiding risks such as short circuit and arc.

[0051] In some embodiments, ablation can also be performed only using the second electrode. As Figure 26 shown, no electrical signal is transmitted to the first electrode 43', and adjacent second electrodes are respectively set as positive and negative electrodes. In Figure 26 , the second electrode 331 is configured as the positive electrode, the second electrode 332 is configured as the negative electrode, and the second electrode 333 is configured as the positive electrode. An electric field is generated between the adjacent second electrodes, and the formed ablation region T is as Figure 27 shown. In addition, although Figure 26 - 27 only shows the case of performing ablation using some second electrodes, those skilled in the art understand that when the target ablation tissue covers all the second electrodes, the ablation method shown in Figure 26 - 27 can also be used, and the same configuration is made for all the second electrodes to ablate the target ablation tissue.

[0052] In addition, as Figure 23 and 25As shown, when the polarity of the first electrode 43' and the second electrode are opposite, there may be an area that cannot be covered by the electric field lines due to the distance between the two adjacent second electrodes on the fixed clamp arm 3. Therefore, a gap M of the ablation area may be generated between the two adjacent second electrodes on the fixed clamp arm 3, and the target ablation tissue located at the gap M cannot be ablated. In order to prevent the problem of missed ablation of the target ablation tissue at the gap M, in one embodiment of the present invention, an insulating protrusion is provided between the two adjacent electrodes on the fixed clamp arm 3. The insulating protrusion can support the target ablation tissue at the gap M, allowing it to enter the ablation area, thereby preventing missed ablation. As shown in FIG. Figure 29 and 30 As shown, second protrusions 341, 342, 343, 344 and 345 are respectively arranged between the second electrodes 331, 332, 333, 334, 335 and 336. The second protrusions 341, 342, 343, 344, 345 support the target ablation tissue at the corresponding position, so that the target ablation tissue originally located at the gap M enters the range of the electric field and falls into the ablation area T, so that it can be ablated.

[0053] In one embodiment of the present invention, the pulse ablation forceps 100 of the present invention may also include a pressure sensor. When the sliding forceps arm 4 is pushed to move toward the fixed forceps arm 3 to clamp the target ablation tissue, the pressure sensor can sense the pressure at the location, and can transmit the pressure to the pressure detection module in the pulse ablation instrument connected to the pulse ablation forceps 100 of the present invention through the wire connected thereto. According to the detected pressure, the operator can adjust and control the clamping process in a targeted manner. The position of the pressure sensor can be set as needed. In one embodiment, the pressure sensor is arranged at the bottom of each first electrode and the second electrode. When clamping the tissue, the force on the electrode will be transmitted to the pressure sensor below. In another embodiment, the pressure sensor is arranged in the gap between two adjacent electrodes of the ipsilateral forceps arm and is not connected to the electrode. 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 of the ipsilateral forceps arm, the 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 provided on the handle 1 or on the pulse ablation apparatus to display the pressure sensed by the pressure sensor, so as to facilitate the operator's operation.

[0054] In one embodiment of the present invention, the pulsed ablation forceps 100 of the present invention may further include distance sensors, which are correspondingly arranged on the fixed forceps arm 3 and the movable forceps arm 4, and are electrically connected to the pulsed ablation instrument through conductors connected to each distance sensor, for sensing the distance between the fixed forceps arm 3 and the movable forceps arm 4. In a preferred embodiment, multiple pairs of pressure sensors are arranged at equal intervals on the fixed forceps arm 3 and the movable forceps arm 4, for measuring the thickness of the target ablation tissue clamped between the fixed forceps arm 3 and the sliding forceps arm 4 and whether the clamping is uniform.

[0055] In one embodiment of the present invention, the pulsed ablation forceps 100 of the present invention may further include an impedance detection module. The impedance detection module is configured with a dielectric constant detection unit, and the dielectric constant detection unit is used to output excitation signals to each first electrode and second electrode. After the excitation signals act on the human tissue through each first electrode and second electrode, complex impedance signals are generated, and the dielectric constant signals are obtained by processing the complex impedance signals, and the degree of contact between the plurality of ablation electrodes and the target tissue is detected through the dielectric constant signals. When the dielectric constant signal is less than the set threshold, there is a short-circuit phenomenon, and it is necessary to adjust the clamping angle or wipe and replace the ablation forceps. In addition, the impedance detection module can also be used to detect the impedance between each first electrode and second electrode on the fixed forceps arm and the movable forceps arm, so as to judge the range of the target ablation tissue clamped, and further select the number and position of the electrodes for ablation, avoiding problems such as short circuit caused by the discharge of the electrodes that do not clamp the target ablation tissue. In a preferred embodiment, the impedance detection module is a chip arranged at the handle 1 and is connected to the pulsed ablation instrument through a wire connected thereto. In addition, those skilled in the art can also set the impedance detection module at a suitable position of the pulsed ablation forceps or the pulsed ablation instrument according to needs.

[0056] In addition, in a preferred embodiment of the present invention, the pulsed ablation forceps 100 of the present invention may further include an identification module, and the structure of the pulsed ablation forceps itself connected thereto, such as the number, length, area of the electrodes, the ipsilateral forceps arms, the electrode spacing on both forceps arms, the length of the forceps arms, etc., are in one-to-one correspondence. When the pulsed ablation forceps 100 is connected to a pulsed ablation instrument for ablating a target ablation tissue, the pulsed ablation instrument can match corresponding ablation voltage, pulse width, pulse interval and other parameters according to the target ablation tissue by identifying the identification module on the pulsed ablation forceps 100. For example, the identification module may be a resistance element, and the resistance element may be disposed at any position of the pulsed ablation forceps 100 as long as it does not affect the operation of the pulsed ablation forceps 100. For example, the resistance element is disposed in the handle housing 11. Resistance elements with different resistance values respectively correspond to pulsed ablation forceps with different structures, and the pulsed ablation instrument identifies the pulsed ablation forceps by detecting the resistance value of the resistance element on the pulsed ablation forceps, and correspondingly matches corresponding ablation voltage, pulse width, pulse interval and other parameters. In addition, the identification module may also be in other suitable forms such as a chip.

[0057] Figure 31FIG. 0 shows a schematic diagram of a pulsed ablation system 1000 according to an embodiment of the present invention, which includes an ablation forceps 100 and a pulsed ablation instrument 200 electrically connected to the ablation forceps 100. The pulsed ablation instrument 200 includes an impedance detection module 230, a pulse generation module 240, an interaction control module 250, and a central control module 260. In a preferred embodiment, the pulsed ablation instrument 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 interaction 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 respectively. Among them, the impedance detection module 230 may not be provided in the pulsed ablation instrument 200, but provided on the ablation forceps 100, or impedance detection modules 230 are provided both on the ablation forceps 100 and in the pulsed ablation instrument 200. The impedance detection module 230 is configured to detect a first impedance between a first electrode on the movable jaw arm 4 and a second electrode on the fixed jaw arm 3, and to detect a second impedance between two adjacent electrodes on the same side jaw arm, and feedback to the central control module 260. The pulse generation module 240 is configured to generate and be able to separately send pulse signals to each of the first electrodes and the second electrodes under the control of the central control module 260. The central control module 260 is configured to receive information from other modules for processing, and feedback and / or display the processed information. The interaction control module 250 is configured to display information and receive control instructions from the user, such as a display, a keyboard, a touch screen, etc. The host identification module 210 is configured to identify the identification module on the ablation forceps 100 according to the instruction of the central control module 260 to obtain relevant parameter information of the ablation forceps 100. The pressure detection module 220 is configured to detect the pressure received by the first electrode on the movable jaw arm 4 and the second electrode on the fixed jaw arm 3, and feedback to the central control module 260.

[0058] In the pulsed ablation system 1000 of the present invention, the device architecture of the pulsed ablation instrument 200 is set as the central control module 260 and each functional module electrically connected thereto through a general communication bus. The above-mentioned modules can use devices or equipment known in the art, as long as they can realize the functions of each module, and there is no special limitation other than this.

[0059] For example, the central control module 260 is constructed based on a general-purpose processor or a programmable logic device, where the general-purpose processor includes a single-core or multi-core microcontroller, and the programmable logic device may include an FPGA, which has good stability, low latency and the advantage of hardware parallelism, and its computing power is better than that of a digital signal processor (DSP), which helps to improve the effectiveness of pulsed electric field ablation. In addition, the central control module 260 may further include components such as a random access memory, a read-only memory, a digital-to-analog converter, an analog-to-digital converter, a power management chip, and a communication chip.

[0060] The communication bus uses an isolated digital interface (such as optocoupler-isolated SPI, etc.) to achieve data interaction between the central control module and each functional module. Optionally, however, the pulsed 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 pulsed ablation system 1000 can be transmitted using any communication method, either wirelessly, such as Wifi, WLAN, and Bluetooth, or wired, such as optical fiber, network cable, USB, and serial port.

[0061] In one implementation, the acquired data can be presented to the operator through the interactive module 250 (such as devices like a display, microphone, and speaker, etc.) equipped in the pulsed ablation system. Additionally, the interactive module 250 can also be a touch display screen, physical buttons, status indicators, and expandable external input devices (such as a keyboard, mouse), etc., to achieve human-machine interaction with the operator. The interfaces of the above devices need to comply with the requirements of electrical isolation for medical devices.

[0062] For the pulse generation module 240, it can be set to generate high voltage by a switching power supply and output pulses through a power switching device. The switching power supply includes a high-frequency transformer and a rectifier filter unit, and the power switching device is controlled by an opto-isolated drive circuit, supporting the output of various pulses such as square waves.

[0063] In the above device architecture, each module is powered by a unified power supply layer, which, for example, includes a buck voltage regulator chip and a low-dropout linear regulator to provide multiple isolated power supplies for the system. The communication interfaces and power supply links of all functional modules comply with the general requirements of electrical isolation and electromagnetic compatibility in the safety standards for medical electrical equipment.

[0064] The following Figure 32 illustrates the control method of the present invention and the connection relationships and functions of the components in the pulsed ablation system 1000 of the present invention. As Figure 32 shown, the control method of the present invention includes S1 selection of the working electrode, S2 pre-inspection of the working electrode, and S3 discharge control. In a preferred implementation, the control method of the present invention can also include S1-b identification control and S1-a pressure reminder steps.

[0065] Since the size of the target ablation tissue and its position in the two jaws of the target ablation forceps 100 may vary, and discharging the electrodes that do not hold the target ablation tissue may cause short circuits and other situations, before officially starting the pulsed ablation, it is necessary to select the working electrodes so that the first electrode and the second electrode that hold the target ablation tissue are the working electrodes for subsequent ablation operations. Therefore, the control method of the present invention includes S1 selection of the working electrodes, which is achieved by controlling the relevant components of the ablation forceps and the ablation instrument. In the selection of the working electrodes in step S1, the working electrodes are selected based on the difference in impedance between the first electrode and the second electrode that hold and do not hold the target ablation tissue. Specifically, when both the movable jaw arm 4 and the fixed jaw arm 3 are segmented electrodes, the impedance detection module 230 detects the first impedance between the n first electrodes 43 on the movable jaw arm 4 and the n + 1 second electrodes 33 on the fixed jaw arm 3 in the following manner: the resistance between the m-th first electrode 43 on the movable jaw arm 4 and the m-th second electrode 33 on the fixed jaw arm 3; and the resistance between the m-th first electrode 43 on the movable jaw arm 4 and the m + 1-th second electrode 33 on the fixed jaw arm 3, where 1 ≤ m ≤ n. Then the impedance detection module 230 sends all the detected first impedances to the central control module 260, and the central control module 260 compares all the first impedances with the first threshold value and selects the working electrodes according to the comparison results. First, determine the second electrodes S a and the second electrode S b , the second electrode S a and the second electrode S b meet the following conditions: i) the resistance between the second electrode S a and the first electrode M a and the resistance between the second electrode S b and the first electrode M b-1 are both less than or equal to the first threshold value, where 1 ≤ a ≤ b ≤ n + 1, ii) the second electrode S a-1 does not exist, or when the second electrode S a-1 exists, the resistance between the second electrode S a-1 and the first electrode M a-1 is greater than the first threshold value, and iii) the second electrode S b+1 does not exist, or when the second electrode S b+1 exists, the resistance between the second electrode S b+1 and the first electrode M b is greater than the first threshold value; then the second electrodes S a , the second electrode S b , the second electrode S a and the second electrode S b between all the second electrodes, the first electrode M a , the first electrode Mb-1 and the first electrode M a and the first electrode M b-1 All the first electrodes between 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 to determine whether the resistance therebetween is less than or equal to the first threshold. When the resistance between the second electrode S a and the first electrode M a-1 is less than or equal to the first threshold, the first electrode M a-1 is also used as a working electrode; when b < n + 1, the second electrode S is further compared b and the first electrode M b to determine whether the resistance therebetween is less than or equal to the first threshold. When the resistance between the second electrode S b and the first electrode M b is less than or equal to the first threshold, the first electrode M b is also used as a working electrode.

[0066] When all the first impedances are less than or equal to the first threshold, it indicates that the target ablation tissue is clamped between all the first electrodes 43 and the second electrode 33 (as shown Figure 10 in the figure). At this time, all the first electrodes 43 and the second electrode 33 are selected as working electrodes. It is also possible to select all the first electrodes 43 and the second electrode 33 as working electrodes according to the conditions of the second electrodes S a and S b for judging the critical threshold. Taking Figure 10 as an example, from the distal end to the proximal end of the jaw portion, the first electrode and the second electrode 331 to the sixth electrode and the second electrode 336 are respectively arranged on the fixed jaw arm. For the determination of the electrode S a of the critical threshold near the distal end on the fixed jaw arm, the resistances between the second electrode 331 and the first electrode 431, between the second electrode 332 and the first electrode 432, between the second electrode 333 and the first electrode 433, between the second electrode 334 and the first electrode 434, and between the second electrode 335 and the first electrode 435 are all less than or equal to the first threshold, and the second electrodes 331, 332, 333, 334, and 335 all meet the condition i) of the second electrode S a for judging the critical threshold. When the second electrode 331 is regarded as S a , since the second electrode 331 is the first electrode from the distal end to the proximal end on the fixed jaw arm 3, S a-1 does not exist, meeting the condition ii) of the second electrode S a for judging the critical threshold; when the second electrode 332 is regarded as S a , a is 2, S a-1is the second electrode 331, and the resistance between the second electrode 331 and the first electrode 431 is less than or equal to the first threshold, and the second electrode S that does not meet the above critical threshold judgment condition a of condition ii); Similarly, the second electrodes 333, 334, and 335 also do not meet the condition ii) of the second electrode S for the above critical threshold judgment a Therefore, the second electrode S that simultaneously meets the condition i) and condition ii) of the above critical threshold judgment a The second electrode 331 that meets the condition i) and condition ii) of the second electrode S of the critical threshold is judged as the second electrode S of the critical threshold a For the determination of the second electrode S of the critical threshold near the proximal end on the fixed jaw 3 b The resistance between the second electrode 332 and the first electrode 431, the resistance between the second electrode 333 and the first electrode 432, the resistance between the second electrode 334 and the first electrode 433, the resistance between the second electrode 335 and the first electrode 434, and the resistance between the second electrode 336 and the first electrode 435 are all less than or equal to the first threshold, and the second electrodes 332, 333, 334, 335, and 336 all meet the condition i) of the second electrode S for the above critical threshold judgment b When the second electrode 332 is regarded as S b At this time, S b+1 is the second electrode 333, and the resistance between the second electrode 333 and the first electrode 432 is less than or equal to the first threshold, and it does not meet the condition iii) of the second electrode S for the above critical threshold judgment b Similarly, the second electrodes 333, 334, and 335 also meet the condition iii) of the second electrode S for the above critical threshold judgment b When the second electrode 336 is regarded as S b At this time, since the second electrode 336 is the last electrode on the fixed jaw from the distal end to the proximal end, S b+1 does not exist, and it meets the condition iii) of the second electrode S for the above critical threshold judgment b Therefore, the second electrode S that simultaneously meets the condition i) and condition iii) of the above critical threshold judgment b The second electrode 336 that meets the condition i) and condition iii) of the second electrode S of the critical threshold is judged as the second electrode S of the critical threshold b After determining that the second electrodes 331 and 336 are the electrodes of the critical threshold, the second electrodes 331 - 336 and the first electrodes 431 - 435 are selected as the working electrodes.

[0067] When some of the first impedances are less than or equal to the first threshold, it indicates that the target ablation tissue only covers some of the first electrodes and the second electrodes. Taking the situation shown Figure 12 as an example, for the electrode S of the critical threshold near the distal end on the fixed jaw aFor the determination, the resistances between the second electrode 331 and the first electrode 431, between the second electrode 332 and the first electrode 432, and between the second electrode 333 and the first electrode 433 are all less than or equal to the first threshold, and the second electrodes 331, 332, and 333 all satisfy the condition i) of the second electrode S for judging the critical threshold. When the second electrode 331 is regarded as S a Since the second electrode 331 is the first electrode on the fixed jaw 3 from the distal end to the proximal end, there is no second electrode S that satisfies the above judgment of the critical threshold a satisfying the condition ii); when the second electrode 332 is regarded as S a-1 a is 2, and S a is the second electrode 331, and the resistance between the second electrode 331 and the first electrode 431 is less than or equal to the first threshold, not satisfying the condition ii) of the second electrode S for judging the critical threshold a ; similarly, the second electrode 333 also does not satisfy the condition ii) of the second electrode S for judging the critical threshold a-1 . Therefore, the second electrode 331 that simultaneously satisfies the condition i) and ii) of the second electrode S for judging the critical threshold is judged as the second electrode S of the critical threshold a . For the determination of the second electrode S of the critical threshold near the proximal end on the fixed jaw 3, the resistances between the second electrode 332 and the first electrode 431, and between the second electrode 333 and the first electrode 432 are all less than or equal to the first threshold, and the second electrodes 332, 333 all satisfy the condition i) of the second electrode S for judging the critical threshold a . When the second electrode 332 is regarded as S a S is the second electrode 333, and the resistance between the second electrode 333 and the first electrode 432 is less than or equal to the first threshold, not satisfying the condition iii) of the second electrode S for judging the critical threshold a ; when the second electrode 333 is regarded as S b S is the second electrode 334, and the resistance between the second electrode 334 and the first electrode 433 is greater than the first threshold, satisfying the condition iii) of the second electrode S for judging the critical threshold b . Therefore, the second electrode 333 that simultaneously satisfies the condition i) and iii) of the second electrode S for judging the critical threshold is judged as the second electrode S of the critical threshold b ; b+1 b b b+1 b b b ​​​​​​After determining the second electrodes 331 and 333 of the two critical thresholds, the second electrodes 331, 332, 333 and the first electrodes 431, 432 are selected as working electrodes. At this time, since b is 3, which is less than the total number n + 1 (6) of the second electrodes on the fixed jaw arm, 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, the first electrode 433 is also selected as a working electrode. Figure 12 Only one case where the target ablation tissue covers part of the first and second electrodes is shown, that is, the target ablation tissue covers part of the electrodes near the distal end of the jaw portion. The specification of the present invention details how to determine the second electrodes of the critical thresholds and how to select the working electrodes. In other cases, such as when the target ablation tissue only covers the first and second electrodes in the middle part of the jaw portion and its edge does not cover the first electrode and the second electrode 331 on the fixed jaw arm 3, or when the target ablation tissue only covers part of the electrodes near the proximal end of the jaw portion, those skilled in the art can make the same judgments and selections according to the above judgment conditions, which will not be elaborated here.

[0068] When there is only one first electrode on the movable jaw arm 4 and there are multiple second electrodes on the fixed jaw arm 3, the first impedance between the first electrode and each second electrode is detected respectively, and each first impedance is compared with the first threshold. All the second electrodes and the first electrode with the first impedance less than the first threshold are selected as working electrodes.

[0069] In the control method of the present invention, the purpose of setting the first threshold is to distinguish between completely vacant electrodes (i.e., non-working electrodes) and electrodes holding the target ablation tissue (i.e., working electrodes). The specific impedance values between the working electrodes may have different results according to different target ablation tissues and different states. 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 configured with a dielectric constant detection unit. The dielectric constant detection unit outputs an excitation signal containing a voltage signal (such as a sine wave constant current source with a peak value of 10 uA) to the first electrode and the second electrode to be detected respectively. After the excitation signal acts on the target ablation tissue, a voltage will be generated. After processing the collected voltage according to the following formula 1, the resistance between the two electrodes can be obtained.

[0070] Formula 1: Y = KS + B, where Y is the collected voltage; S is the resistance to be measured; K and B are coefficients.

[0071] The central control module 260 sends the results of the selected working electrode to the interaction control module 250 for display. The results can be displayed in a commonly used manner in the art. For example, different colors can be used to label the working electrode and the non-working electrode.

[0072] Furthermore, during ablation, if the contact between the target ablation tissue and the electrode is poor, there is a risk of short circuit. Therefore, before formal pulsed ablation, it is necessary to pre-check the contact between the target ablation tissue and the electrode. The control method of the present invention includes the S2 working electrode pre-check step, which is achieved by controlling relevant components of the pulsed ablation forceps 100 and the pulsed ablation instrument 200. Specifically, the impedance detection module 230 detects the second impedance between two adjacent electrodes on the same side of the forceps 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 of the forceps arm with the 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 issues an instruction to the pulse generation module 240 to prohibit the electrode from discharging in the following manner: when j ≥ n / 2, prohibit the (j + 1)-th electrode from discharging; when j < n / 2, prohibit the j-th electrode from discharging. In the present invention, the second threshold is preferably 350 ohms. Similarly, the impedance between two adjacent electrodes can be detected by a method known in the art, such as through the above-mentioned dielectric constant detection unit. 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 interaction control module 250 for display, so as to facilitate the operator to adjust the ablation forceps accordingly. If it is found that the contact is not firm, the impedance between the connected electrodes can be adjusted within the second threshold range by adjusting the clamping angle of the ablation forceps or wiping and replacing the ablation forceps, etc. Specifically, according to the situation, after adjusting the clamping angle of the ablation forceps or wiping and replacing the ablation forceps, S1 and S2 can be repeated, or only S2 can be repeated.

[0073] After the selection and pre-check of the working electrode are completed, the S3 discharge control step is performed. The central control module 260 issues an instruction to the pulse generation module 240 to cause the pulse generation module 240 to send a pulse signal to the working electrode. The way the working electrode forms an electrode pair and the way of discharging can be as Figure 9 - 16, any one of 19 - 29, the relevant content has been described in detail in the previous part of the present invention and will not be elaborated 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 instruction of the central control module 260, making the first electrode in the electrode pair be one of the positive / negative electrodes, and making the second electrode in the electrode pair be the other of the positive / negative electrodes, where 1 ≤ k ≤ n. By discharging with the first electrode and the second electrode forming an electrode pair, the ablation gap of the target ablation tissue in the middle part between the first electrode and the second electrode can be reduced or eliminated ( Figure 6 O in).

[0074] In a preferred embodiment, step S3 further includes discharge protection control, where the generated pulse signal is converted into a current signal, and the current signal is compared with a third threshold. If the current signal is greater than the third threshold, the pulse output is terminated. Figure 33 FIG. is an illustrative diagram of a gated overcurrent protection circuit implemented by hardware. As Figure 33 shown, the gated overcurrent protection circuit includes the following structure: a pulse generation control unit U1, transformers TR1, TR2, a threshold unit VG1, and a threshold comparison output unit OP1, where N1 and N2 respectively represent the primary and secondary coils of the transformer. Among them, the pulse signal generated by the pulse generation control unit U1 serves as the input excitation for the subsequent circuit. The transformers TR1 and TR2 are used to realize the coupling and electrical isolation of the circuit signals. The threshold unit VG1 provides a current signal of the third threshold for the circuit, and the third threshold is used to compare with the excitation signal after being coupled by the transformer TR2. The threshold comparison output unit OP1 has two inputs and an output connected to the transformer TR1. The two inputs are respectively connected to the threshold unit VG1 set with the third threshold and the transformer TR2. The function of the threshold comparison output unit OP1 is to compare the signal obtained from the transformer TR2 with the signal provided by the threshold unit VG1, and output a corresponding level signal according to the comparison result, so as to judge whether the signal obtained from the 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 the transformer TR1 to terminate the pulse output.

[0075] In another preferred embodiment, step S3 further includes real-time collecting the ablation current value during the ablation process to calculate the ablation energy. By high-speed triggering AD sampling, the total current during the ablation process is sampled, and the ablation energy is deduced through an integration algorithm. As Figure 34As shown, specifically, the energy harvesting circuit includes the following structures: a pulse generation control unit U1, a transformer M1, a data processing unit U2, and a data buffering and filtering unit IOP1. Here, N1 and N2 represent the primary and secondary coils of the transformer respectively. During operation, the pulse generation control unit U1 generates pulses, and the pulse signals reach the secondary side through the coupling of the transformer M1. The secondary side signals are 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 caching problem. The data processing unit monitors the pulse current signal in real time and performs an integration operation 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, it can be adjusted by increasing or decreasing the ablation voltage or other means to ensure that the energy output meets the expectations.

[0076] Formula 2: E = P * T = U * I * T, where E is the ablation energy; P is the ablation-generated power; T is the sampling interval time; U is the pulse voltage; I is the pulse current.

[0077] In a preferred embodiment of the present invention, before step S1, it further includes step S-1a pressure reminder. In this embodiment, the pulsed ablation instrument 200 further includes a pressure detection module 220. The pressure detection module 220 is used to detect the pressures received by the first electrode on the movable clamp arm 4 and the second electrode on the fixed clamp arm 3, and feedback them to the central control module 260. The central control module 260 compares the pressures received by the first electrode and the second electrode, and feeds the result back to the interaction control module 250 for display. The pressures received by each electrode on both sides of the clamp arms are collected by pressure sensors on each clamp arm. Then, the pressure sensors send the pressures 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 interaction control module 250: when n is odd, compare the pressures received by the (n + 1) / 2-th second electrode, the (n + 3) / 2-th second electrode on the fixed clamp arm 3 and the (n + 1) / 2-th first electrode on the movable clamp arm 4 respectively; when n is even, compare the pressures received by the n / 2-th second electrode, the (n / 2 + 1)-th second electrode on the fixed clamp arm 3 and the n / 2-th first electrode on the movable clamp arm 4 respectively. The interaction control module 250 displays the above comparison results. Through the above operations, a preliminary judgment can be made on the clamping situation of the pulsed ablation forceps 100 on the target ablation tissue. When the pressure difference between the electrodes in the middle part of both clamp arms is less than or equal to 5%, it is determined that the electrode pressures on both clamp arms are similar, and the target ablation tissue is well clamped between the two clamp arms of the pulsed ablation forceps 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 forceps and the like, and step S-1a is repeated for detection until the pressure difference is less than or equal to 5%.

[0078] In a preferred embodiment, before step S-1a, it further includes step S-1b) identification control. In this embodiment, the pulsed ablation forceps 100 includes an identification module, and the identification module contains the parameter information of the pulsed ablation forceps 100. The pulsed ablation instrument 200 includes a host identification module 210. The host identification module 210 is connected to the central control module 260 and identifies the identification module according to the instruction of the central control module 260 to obtain the parameter information of the pulsed ablation forceps 100.

[0079] In summary, the pulsed ablation forceps and pulsed ablation instrument system of the present invention can ablate the target ablation tissue that enters the chute by arranging a plurality of second electrodes on the fixed forceps arm and setting at least a part of the electrode close to the chute inside the chute, avoiding missed ablation. At the same time, since the first electrode on the movable forceps arm is arranged outside the chute, the occurrence of phenomena such as electric arc and short circuit caused by the too-close distance between the first electrode and the second electrode is avoided. In addition, since there is a certain distance between the segmented electrodes and there is an ablation gap between the segmented electrodes during the ablation process, the present invention can support the ablation tissue to be ablated at the gap position by arranging insulating protrusions between adjacent electrodes of the forceps arm, so that it enters the range of the pulsed electric field, thereby making up for the ablation gap and avoiding missed ablation. Moreover, the control method of the present invention can avoid the occurrence of short circuits and other situations caused by the failure to clamp the target ablation tissue between the electrodes or the low degree of fit between the electrode and the target ablation tissue through the selection of the working electrode and the control of pre-inspection. At the same time, the control method of the present invention can avoid the missed ablation of the target ablation tissue at the middle position between the two forceps arms by controlling the cross-discharge of the electrodes on both sides of the forceps arm.

[0080] The embodiments of the present invention have been described in detail above in conjunction with 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 of those of ordinary skill in the art, various changes can also be made without departing from the gist of the present invention.

Claims

1. A pulse ablation forceps, comprising a forceps body and a jaw portion mounted on the forceps body and composed of a fixed forceps arm and a movable forceps arm parallel to the fixed forceps arm, wherein the jaw portion clamps or releases a target ablation tissue by moving the movable forceps arm relative to the fixed forceps arm, the forceps body comprises a slide groove, the fixed forceps arm is fixedly connected to the distal end of the slide groove, and the movable forceps arm approaches or moves away from the fixed forceps arm along the slide groove, characterized in that: Along the direction in which the jaw portion extends, from the distal end to the proximal end, n first electrodes are provided on the movable clamp arm, and n+1 second electrodes are provided on the fixed clamp arm, where n≥2; in a direction perpendicular to the extension of the fixed clamp arm, the projection of each first electrode on the fixed clamp arm is located between two second electrodes; all the first electrodes are arranged outside the slide groove, and at least a portion of the n+1th second electrode is arranged inside the slide groove.

2. The pulse ablation forceps according to claim 1, characterized in that: The n is 5.

3. The pulse ablation forceps according to claim 1, characterized in that: Along the extending direction of the jaw portion, adjacent first electrodes are arranged at equal intervals, and / or adjacent second electrodes are arranged at equal intervals.

4. The pulse ablation forceps according to claim 3, characterized in that: The interval range of the equally spaced arrangement is 1.5-4mm.

5. The pulse ablation forceps according to claim 1, characterized in that: 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 jaw portion extends; the area is the maximum cross-sectional area of ​​each of the first electrode and the second electrode with a plane parallel to the direction in which the jaw portion extends as a cross-section.

6. The pulse ablation forceps according to claim 1, characterized in that: On the fixed clamp arm and / or the movable clamp arm, there are insulating protrusions between adjacent first electrodes and / or between adjacent second electrodes.

7. The pulse ablation forceps according to claim 1, characterized in that: The n+1th second electrode extends into the slide groove by 1-4 mm, and the distance between the end of the n+1th second electrode close to the slide groove and the inner wall of the slide groove is 2-4 mm.

8. The pulse ablation forceps according to claim 1, characterized in that: A pressure sensor is also included.

9. The pulse ablation forceps according to claim 1, characterized in that: It also includes distance sensors correspondingly arranged on the fixed clamp arm and the movable clamp arm.

10. The pulse ablation forceps according to any one of claims 1 to 9, characterized in that: An impedance detection module is also included.

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