Pulse energy ablation device

Abstract

The invention provides a pulse energy ablation device, and relates to the technical field of medical instruments, the pulse energy ablation device comprises an outer tube, an inner tube, a mandrel and an ablation electrode, the inner tube is arranged in the outer tube; the core shaft is movably arranged in the inner pipe in a penetrating mode in the axial direction. The ablation electrode and the outer tube are coaxially arranged, the ablation electrode is used for being in communication connection with a pulse energy generator, the near end of the ablation electrode is fixedly connected with the far end of the outer tube, the far end of the ablation electrode is fixedly connected with the far end of the mandrel, and the ablation electrode can be expanded and contracted by pushing and pulling the mandrel; a connecting structure is further arranged on the outer tube and used for adjusting the position of the ablation electrode, so that the ablation electrode is evenly attached to the inner wall of the tissue. The position of the ablation electrode can be adjusted, the side wall of the ablation electrode can be evenly attached to the inner wall of tissue, and the uniformity of the ablation effect is guaranteed.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a pulse energy ablation device. Background Art

[0002] In chronic bronchitis-type COPD, the epithelial goblet cells in the bronchial mucosa abnormally proliferate, secreting excessive mucus, resulting in airflow restriction in the bronchi and affecting normal gas exchange in the lungs. Currently, new technologies are used to treat chronic bronchitis, forming pulsed electric fields to perform ablation in the lower respiratory tract and lung bronchi of the human body. The specific operation is to use a metal stent to stick to the bronchial bronchi, and form a high-voltage electric field with electrodes connected to the outside of the human body, causing irreversible electroporation of the epithelial goblet cells in the bronchus, causing cell apoptosis, and achieving the purpose of treatment. During ablation, the ablation electrode needs to be as completely attached to the bronchial wall as possible to cover more tissue.

[0003] Existing ablation electrodes such as Figure 13 As shown, it is usually made of woven metal wire and has a closed design at both ends. When entering a tortuous bronchus, the metal woven ablation electrode often has the following problems: the ablation catheter needs to be inserted into the bronchoscope to enter the human body, and the working cavity in the bronchoscope is not coaxial with the mirror body itself, resulting in the ablation catheter being not coaxial with the mirror body after passing through the working cavity. This will cause the axis of the ablation catheter to be far away from the axis of the bronchus, and it is difficult to make the axis of the ablation catheter coincide with the axis of the bronchus as much as possible by adjusting the bronchoscope, resulting in the ablation electrode always biased to one side of the bronchus, and the ablation effect is uneven.

[0004] Therefore, it is very necessary to design an ablation catheter that can correct the position of the ablation electrode and prevent the ablation electrode from being eccentric. Summary of the Invention

[0005] The purpose of the present invention is to provide a pulse energy ablation device to solve the problems existing in the above-mentioned prior art, and to be able to adjust the position of the ablation electrode so that the side wall of the ablation electrode can be evenly fitted with the inner wall of the tissue to ensure the uniformity of the ablation effect.

[0006] To achieve the above object, the present invention provides the following solutions:

[0007] A pulse energy ablation device comprises an outer tube, an inner tube, a core shaft and an ablation electrode, wherein the inner tube is arranged inside the outer tube; the core shaft is axially movably inserted into the inner tube; the ablation electrode is coaxially arranged with the outer tube for communicating with a pulse energy generator, the proximal end of the ablation electrode is fixedly connected to the distal end of the outer tube, and the distal end of the ablation electrode is fixedly connected to the distal end of the core shaft, and the core shaft can be pushed and pulled to expand and contract the ablation electrode; a connecting structure is also provided on the outer tube, and the connecting structure is used to adjust the position of the ablation electrode so that the ablation electrode fits evenly with the inner wall of the tissue.

[0008] As one embodiment, the outer tube includes a tube body and a bent tube segment connected to the distal end of the tube body, the tube body is used to be inserted into a bronchoscope, and the bent tube segment includes a first tube segment, a connecting tube segment and a second tube segment connected in sequence, the first tube segment and the second tube segment are arranged in parallel, the proximal end of the first tube segment is connected to the distal end of the tube body, and the second tube segment is coaxial with the bronchoscope.

[0009] As one embodiment, a symmetrical threading channel is provided in the radial direction in the side wall of the outer tube, a traction wire is passed through the threading channel, the distal end of the traction wire is fixedly connected to the distal end of the outer tube, and the proximal end of the traction wire is used to apply force.

[0010] As one embodiment, it also includes a bending adjustment mechanism, which includes a fixed seat, a wire reel and a knob. The wire reel is rotatably set on the fixed seat, and the traction wire is wound on the wire reel. The two ends of the traction wire are passed through the threading channel and connected to the distal end of the outer tube; the knob is connected to the wire reel through a damper.

[0011] As one embodiment, a wire electrically connected to the ablation electrode is provided in the outer tube, and the pulse energy ablation device also includes a catheter seat, which is fixedly connected to the proximal end of the outer tube and the proximal end of the inner tube. The catheter seat is also connected to a pulse input cable, which is electrically connected to the wire. A plug is provided at the end of the pulse input cable, which is used to be plugged into the pulse energy generator; the proximal end of the core shaft extends from the proximal end of the catheter seat.

[0012] As an embodiment, the wire is located inside the wall of the outer tube or in the gap between the outer tube and the inner tube.

[0013] As an embodiment, a handle is further included, wherein the fixing seat, the wire reel and the catheter seat are all arranged in the handle, and a push-pull button is slidably provided on the shell of the handle, and the push-pull button is connected to the proximal end of the core shaft.

[0014] As one embodiment, a silicone ring is further provided in the handle and is sleeved on the outer side of the proximal end of the core shaft. The silicone ring is used to provide friction to the core shaft to lock the core shaft.

[0015] As an embodiment, a slit is provided on the outer wall of the distal end of the outer tube for improving the flexibility of the outer tube, and a seal is provided between the slit and the inner tube.

[0016] As one embodiment, a sheath is provided on the outside of the outer tube, and a correction bracket is also fixed to the distal end of the outer tube. The correction bracket is located on the outside of the ablation electrode. The correction bracket has a contraction and resetting performance. In the contracted state, the correction bracket is located in the sheath. In the expanded state, the correction bracket is entirely or partially located on the distal side of the sheath for abutting against the inside of the tissue. After the ablation electrode expands, it abuts against the inner wall of the correction bracket to achieve electrical connection between the ablation electrode and the correction bracket.

[0017] Compared with the prior art, the present invention has the following technical effects:

[0018] The present invention is provided with a connecting structure. When the outer tube enters the trachea at a position eccentric to the bronchoscope, the connecting structure can adjust the position of the ablation electrode, so that the side wall of the ablation electrode is evenly fitted with the inner wall of the tissue, thereby ensuring the uniformity of the ablation effect.

[0019] The connection structure in the present invention has two structural forms: a bent tube segment and a bending adjustment using a traction wire. The structural form of the bent tube segment is simpler and has lower cost; the outer tube is bent using a traction wire, and the adjustment angle of the outer tube is larger, which can be applied to the inner walls of tissues with different degrees of curvature and has stronger applicability.

[0020] The present invention also provides a correction stent. The ablation electrode and the correction stent can be electrically connected after expansion. On the one hand, the correction stent can be used to perform ablation treatment on the target position in a larger range. On the other hand, the correction stent is not connected to the core shaft, resulting in its own excellent bending performance. The shape of the correction stent after expansion is highly adaptable to the inner wall of the tissue, but the proximal closing position and other positions may not fit tightly with the inner wall of the tissue; after expansion, the ablation electrode can squeeze the correction stent, reducing the possibility of the correction stent not fitting tightly with the inner wall of the tissue, making the correction stent more closely fitted with the inner wall of the tissue, and further improving the uniformity of the ablation effect. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0022] Figure 1 This is a schematic structural diagram of a pulse energy ablation device in one embodiment of the present invention;

[0023] Figure 2 This is a schematic diagram of the exploded structure of a handle in one embodiment of the present invention;

[0024] Figure 3 A partial cross-sectional schematic diagram of a pulse energy ablation device according to one embodiment of the present invention;

[0025] Figure 4 This is a schematic structural diagram of an embodiment of the present invention in which the outer tube has a bent tube section;

[0026] Figure 5 This is a schematic diagram of the structure in which a traction wire drives the distal end of the outer tube to bend in one embodiment of the present invention;

[0027] Figure 6 A schematic diagram of a radial cross-section of a catheter in a pulsed energy ablation device according to one embodiment of the present invention;

[0028] Figure 7 A schematic radial cross-sectional view of a catheter assembly in a pulsed energy ablation device according to another embodiment of the present invention;

[0029] Figure 8 This is a schematic structural diagram of an embodiment of the present invention in which the distal end portion of the outer tube has a slit;

[0030] Figure 9 This is a schematic structural diagram of an embodiment of the present invention in which both the correction stent and the ablation stent are in an expanded state;

[0031] Figure 10 This is a schematic structural diagram of a correction stent in a contracted state according to an embodiment of the present invention;

[0032] Figure 11 This is a schematic diagram of the arrangement of a correction stent in tissue according to one embodiment of the present invention;

[0033] Figure 12 This is a schematic structural diagram of an opening at the distal end of a correction stent in one embodiment of the present invention;

[0034] Figure 13 It is a structural diagram of the prior art.

[0035] Description of reference numerals:

[0036] 1. Outer tube; 2. Inner tube; 3. Core shaft; 4. Ablation electrode; 5. Bronchoscope; 6. Bent tube segment; 7. Traction wire; 8. Fixing seat; 9. Wire reel; 10. Knob; 11. Damper; 12. Wire; 13. Catheter seat; 14. Pulse input cable; 15. Plug; 16. Handle; 17. Upper shell; 18. Lower shell; 19. Sheath; 20. Four-way tube joint; 21. Silicone reinforcement tube; 22. Silicone ring; 23. Slit; 24. Sheath; 25. Correction bracket; 26. Push-pull button; 27. Core shaft seat. DETAILED DESCRIPTION

[0037] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0038] The purpose of the present invention is to provide a pulse energy ablation device to solve the problems existing in the prior art. It can adjust the position of the ablation electrode to facilitate the uniform fit of the side wall of the ablation electrode with the inner wall of the tissue, thereby ensuring the uniformity of the ablation effect.

[0039] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the present invention is further described in detail below with reference to the accompanying drawings and specific embodiments.

[0040] like Figures 1 to 12 As shown, this embodiment provides a pulse energy ablation device, including an outer tube 1, an inner tube 2, a core shaft 3 and an ablation electrode 4, wherein the inner tube 2 is arranged in the outer tube 1, and the inner tube 2 and the outer tube 1 are relatively fixed; the core shaft 3 is movably arranged in the inner tube 2 along the axial direction; the ablation electrode 4 is coaxially arranged with the outer tube 1, and is used for communicating with the pulse energy generator. The ablation electrode 4 has a plurality of metal wires, and the metal wires are arranged at intervals along the circumferential direction. The proximal end of the ablation electrode 4 (i.e., the proximal end of the metal wire) is fixedly connected to the distal end of the outer tube 1, and the distal end of the ablation electrode 4 (i.e., the distal end of the metal wire) is fixedly connected to the distal end of the core shaft 3; the core shaft 3 can expand and contract by pushing and pulling. A connecting structure is also provided on the outer tube 1, and the connecting structure is used to adjust the position of the ablation electrode 4.

[0041] The distal end in this embodiment refers to the end away from the operator, and the proximal end refers to the end close to the operator.

[0042] During use, the outer tube 1 is usually inserted into the bronchoscope 5 and placed into the human body (e.g., the human trachea). During the process of inserting the outer tube 1 into the human body, the ablation electrode 4 is in a contracted state, which facilitates the insertion of the outer tube 1. After the ablation electrode 4 reaches the target position, the core shaft 3 is pulled proximally, the ablation electrode 4 expands, the outer wall of the ablation electrode 4 abuts against the inner wall of the tissue, the pulse energy generator is turned on, and the position of the ablation electrode 4 and the negative plate of the human body form a pulse electric field, which ablates the cells at the target position and achieves the purpose of treatment. Since the present embodiment is provided with a connection structure, when the outer tube 1 enters the trachea at a position eccentric to the bronchoscope 5, the connection structure can adjust the position of the ablation electrode 4, so that the side wall of the ablation electrode 4 is evenly fitted with the inner wall of the tissue, thereby ensuring the uniformity of the ablation effect.

[0043] like Figure 4 As shown, in this embodiment, the outer tube 1 includes a tube body and a bent tube segment 6 connected to the distal end of the tube body. The tube body is used to pass through the bronchoscope 5. The bent tube segment 6 includes a first tube segment, a connecting tube segment, and a second tube segment connected in sequence. The first tube segment and the second tube segment are arranged in parallel. The proximal end of the first tube segment is connected to the distal end of the tube body, and the second tube segment is coaxial with the bronchoscope 5. At this time, the bent tube segment 6 forms a connecting structure. Specifically, the distal end of the outer tube 1 can be thermoformed into a bent tube segment 6. When the bent tube segment 6 is passed through the lumen of the bronchoscope 5, the bent tube segment 6 is straightened. After passing through the lumen of the bronchoscope 5, the bent tube segment 6 returns to its bent shape, which can make the second tube segment coaxial with the bronchoscope 5, which is equivalent to making the ablation electrode 4 coaxial with the bronchoscope 5, making it easier for the ablation electrode 4 to be evenly fitted to the inner wall of the tissue. If the second tube section 6 is not coaxial with the bronchoscope 5 after the bent tube section 6 passes through the bronchoscope 5, the outer tube 1 or the bronchoscope 5 can be rotated to make the two coaxial.

[0044] In this embodiment, the axial distance between the first tube segment and the second tube segment is equal to the distance between the cavity on the bronchoscope 5 for passing the outer tube 1 and the axis of the bronchoscope 5, which is usually 5mm to 10mm, and the axial distance from the proximal end of the first tube segment to the distal end of the second tube segment is 10mm to 20mm.

[0045] As another specific form of connection structure, such as Figure 2 、 Figure 5 、 Figure 6 As shown, in this embodiment, the sidewall of the outer tube 1 is provided with a radially symmetrical threading channel, through which a traction wire 7 is passed. The distal end of the traction wire 7 is fixedly connected to the distal end of the outer tube 1, and the proximal end of the traction wire 7 is used to apply a force. When tension is applied to the traction wire 7 on one side and the traction wire 7 on the other side is relaxed, the distal end of the outer tube 1 bends toward one side, also causing the ablation electrode 4 to bend, so that the ablation electrode 4 conforms to the curvature of the tissue inner wall, facilitating a uniform contact between the ablation electrode 4 and the tissue inner wall.

[0046] like Figure 2 As shown, this embodiment also includes a bending adjustment mechanism, which includes a fixed seat 8, a wire reel 9 and a knob 10. The wire reel 9 is rotatably mounted on the fixed seat 8. One or more turns of traction wire 7 are wound around the wire reel 9. The two ends of the traction wire 7 are passed through the threading channel and connected to the distal end of the outer tube 1. The knob 10 is connected to the wire reel 9 via a damper 11. The damper 11 allows the wire reel 9 (i.e., the catheter bending angle) to be self-locking at any rotational position. The damper 11 can adopt an existing device.

[0047] The outer tube 1 of this embodiment is provided with a wire 12 electrically connected to the ablation electrode 4. The pulse energy ablation device also includes a catheter seat 13. The catheter seat 13 is fixedly connected to the proximal end of the outer tube 1 and the proximal end of the inner tube 2. The catheter seat 13 is also connected to a pulse input cable 14. The pulse input cable 14 is electrically connected to the wire 12. A plug 15 is provided at the end of the pulse input cable 14. The plug 15 is used to connect to the pulse energy generator; the proximal end of the core shaft 3 extends from the proximal end of the catheter seat 13, which is convenient for the staff to push and pull the core shaft 3.

[0048] In this embodiment, a cavity for passing a wire 12 may be further provided in the side wall of the outer tube 1 . The wire 12 is located inside the wall of the outer tube 1 , or the wire 12 may be located in the gap between the outer tube 1 and the inner tube 2 .

[0049] This embodiment also includes a handle 16, and the fixing seat 8, the wire reel 9 and the catheter seat 13 are all arranged in the handle 16. A push-pull button 26 is slidably provided on the shell of the handle 16, and the push-pull button 26 is connected to the proximal end of the core shaft 3. By operating the push-pull button 26, the staff can push and pull the core shaft 3, and then adjust the position of the ablation electrode 4. In this embodiment, the shell of the handle 16 includes an upper shell 17, a lower shell 18 and a sheath 19 located at the distal end. The upper shell 17 and the lower shell 18 are detachably connected by bolts. After connection, the upper shell 17 and the lower shell 18 clamp the sheath 19. The pulse input cable 14 passes through the interior of the shell from the sheath 19. In this embodiment, a four-way pipe joint 20 is also provided in the shell. The axial opening of the four-way pipe joint 20 is used to pass through the outer tube 1, and the other two openings of the four-way pipe joint 20 are symmetrically arranged relative to the outer tube 1, and are respectively used to pass through the two ends of the traction wire 7.

[0050] In order to prevent the outer tube 1 from being severely bent and damaged at the distal end of the shell, a silicone reinforcement tube 21 is provided at the distal end of the shell and is sleeved on the outside of the outer tube 1.

[0051] In this embodiment, a silicone ring 22 is further provided in the handle 16 and is sleeved on the outer side of the proximal end of the core shaft 3. The silicone ring 22 is used to provide friction to the core shaft 3 to lock the core shaft 3.

[0052] like Figure 2 、 Figure 3As shown, the core shaft 3 of this embodiment is located in the shell and a core shaft seat 27 is provided on the outside of the part exposed from the catheter seat 13, and the core shaft seat 27 is fixedly connected to the catheter seat 13; the silicone ring 22 is sleeved on the outside of the core shaft seat 27, and the push-pull button 26 is connected to the core shaft seat 27.

[0053] like Figure 8 As shown, in this embodiment, the outer wall of the distal end of the outer tube 1 has a slit 23 for increasing the flexibility of the outer tube 1. Specifically, the slit 23 can be within a range of 10 mm to 15 mm from the distal end of the outer tube 1. The slit 23 can be semicircular, with multiple slits 23 spaced apart along the axial direction of the outer tube 1. The slits 23 are distributed on both sides of the outer tube 1, and the slits 23 on both sides are staggered in the axial direction. The slits 23 can be formed by removing material from the outer tube 1. By providing the slits 23 on the distal wall of the outer tube 1 in this embodiment, the flexibility of the distal portion of the outer tube 1 can be increased, making it easier to bend the distal end of the outer tube 1. In this embodiment, the slits 23 can be sealed with glue between the inner tube 2 to prevent liquid from entering the outer tube 1.

[0054] like Figures 9 to 12 As shown, in this embodiment, the outer side of the outer tube 1 is provided with a sheath 24, and the distal end of the outer tube 1 is also fixed with a correction bracket 25, and the correction bracket 25 is bonded, welded or connected to the outer wall of the outer tube 1 by other processes. The correction bracket 25 is located on the outside of the ablation electrode 4. The correction bracket 25 has a contraction and reset performance. In the absence of restrictions, it can self-expand into a cylinder with a diameter greater than 20 mm. Specifically, the correction bracket 25 can be made of memory alloy. In the contracted state, the correction bracket 25 is located in the sheath 24. When the sheath 24 and the outer tube 1 are placed in the human body and the target position is reached, the sheath 24 is pulled proximally for a certain distance, and the sheath 24 loses its restrictive effect on the correction bracket 25. The correction bracket 25 expands to abut against the inner wall of the tissue. Mandrel 3 is then pulled backward, causing ablation electrode 4 to expand. The maximum expanded diameter of ablation electrode 4 is larger than the maximum expanded diameter of correction stent 25. After expansion, ablation electrode 4 abuts the inner wall of correction stent 25, establishing an electrical connection between ablation electrode 4 and correction stent 25. Correction stent 25 forms a pulsed electric field with the body's negative electrode, ablating cells at the target location and achieving the therapeutic goal.

[0055] The ablation electrode 4 in this embodiment is electrically connected to the correction bracket 25. On the one hand, the correction bracket 25 can be used to perform ablation treatment on the target position in a larger range. On the other hand, the correction bracket 25 is not connected to the core shaft 3, resulting in its own bending performance being relatively good. The shape of the correction bracket 25 after expansion is highly adaptable to the inner wall of the tissue, but the proximal closing position and other positions may not fit tightly with the inner wall of the tissue; after expansion, the ablation electrode 4 can squeeze the correction bracket 25, reducing the possibility of the correction bracket 25 not fitting tightly with the inner wall of the tissue, making the correction bracket 25 more closely fitted with the inner wall of the tissue, and further improving the uniformity of the ablation effect.

[0056] In this embodiment, the distal end of the correction bracket 25 can be a closed structure or an open structure.

[0057] In this embodiment, the correction stent 25 has a certain axial length. When in use, the protruding length of the correction stent 25 from the sheath tube 24 can be controlled by adjusting the retraction distance of the sheath tube 24, thereby adjusting the self-expansion length of the sheath tube 24.

[0058] Adaptive changes based on actual needs are all within the scope of protection of the present invention.

[0059] The present invention uses specific examples to illustrate the principles and implementation methods of the present invention. The above examples are only intended to help understand the method and core concept of the present invention. At the same time, those skilled in the art will find that the specific implementation methods and application scopes may vary based on the concept of the present invention. In summary, the contents of this specification should not be construed as limiting the present invention.

Claims

1. A pulse energy ablation device, characterized in that: include: External control; an inner tube, the inner tube being disposed inside the outer tube; a core shaft, the core shaft being movably disposed in the inner tube along the axial direction; and an ablation electrode, which is coaxially arranged with the outer tube and is used for communicating with the pulse energy generator, wherein the proximal end of the ablation electrode is fixedly connected to the distal end of the outer tube, and the distal end of the ablation electrode is fixedly connected to the distal end of the core shaft, and the core shaft can be pushed and pulled to expand and contract the ablation electrode; The outer tube is also provided with a connecting structure, which is used to adjust the position of the ablation electrode so that the ablation electrode is evenly fitted to the inner wall of the tissue.

2. The pulse energy ablation device according to claim 1, characterized in that: The outer tube includes a tube body and a bent tube segment connected to the distal end of the tube body. The tube body is used to be inserted into a bronchoscope. The bent tube segment includes a first tube segment, a connecting tube segment and a second tube segment connected in sequence. The first tube segment and the second tube segment are arranged in parallel. The proximal end of the first tube segment is connected to the distal end of the tube body, and the second tube segment is coaxial with the bronchoscope.

3. The pulse energy ablation device according to claim 1, characterized in that: A symmetrical threading channel is provided in the radial direction of the side wall of the outer tube. A traction wire is passed through the threading channel. The distal end of the traction wire is fixedly connected to the distal end of the outer tube, and the proximal end of the traction wire is used to apply a force.

4. The pulse energy ablation device according to claim 3, characterized in that: It also includes a bending adjustment mechanism, which includes a fixed seat, a wire reel and a knob. The wire reel is rotatably set on the fixed seat, and the traction wire is wound on the wire reel. The two ends of the traction wire are passed through the threading channel and connected to the distal end of the outer tube; the knob is connected to the wire reel through a damper.

5. The pulse energy ablation device according to claim 4, characterized in that: A wire electrically connected to the ablation electrode is provided in the outer tube, and the pulse energy ablation device also includes a catheter seat, which is fixedly connected to the proximal end of the outer tube and the proximal end of the inner tube. The catheter seat is also connected to a pulse input cable, which is electrically connected to the wire. A plug is provided at the end of the pulse input cable, which is used to be plugged into the pulse energy generator; the proximal end of the core shaft extends from the proximal end of the catheter seat.

6. The pulse energy ablation device according to claim 5, characterized in that: The wire is located inside the wall of the outer tube or in the gap between the outer tube and the inner tube.

7. The pulse energy ablation device according to claim 5, characterized in that: It also includes a handle, the fixing seat, the wire reel and the catheter seat are all arranged in the handle, and a push-pull button is slidably provided on the shell of the handle, and the push-pull button is connected to the proximal end of the core shaft.

8. The pulse energy ablation device according to claim 7, characterized in that: A silicone ring is also provided in the handle and is sleeved on the outer side of the proximal end of the core shaft. The silicone ring is used to provide friction to the core shaft to lock the core shaft.

9. The pulse energy ablation device according to claim 1, characterized in that: A slit is provided on the outer wall of the distal end of the outer tube for improving the flexibility of the outer tube, and a sealing arrangement is provided between the slit and the inner tube.

10. The pulse energy ablation device according to claim 1, characterized in that: A sheath is provided on the outside of the outer tube, and a correction bracket is also fixed to the distal end of the outer tube. The correction bracket is located on the outside of the ablation electrode. The correction bracket has a contraction and resetting performance. In the contracted state, the correction bracket is located in the sheath. In the expanded state, the correction bracket is entirely or partially located on the distal side of the sheath for abutting against the inside of the tissue. After the ablation electrode expands, it abuts against the inner wall of the correction bracket to achieve electrical connection between the ablation electrode and the correction bracket.

Images