An ablation device with cutting function

Abstract

The present invention belongs to the technical field of medical devices, and provides an ablation device with a cutting function, including an insulating sleeve with a through first channel; an ablation electrode with a hollow structure, which is arranged at one end of the insulating sleeve, and the ablation electrode has a plurality of ablation claws, and the ablation claws can expand toward the outside direction of the ablation electrode under stress, wherein one or more ablation claws on the ablation electrode are provided with a cutting edge for cutting; and a puncture needle with a needle tip, which is arranged at the second end of the ablation electrode; by applying an external force to the ablation electrode to expand the ablation electrode, the ablation claws of the ablation electrode are transformed and maintained from an initial state without stress to an expanded state after stress. The present application arranges a plurality of ablation claws that can expand under stress, combined with the cutting edges arranged on the ablation claws, thereby achieving the separation and expansion of tumor tissue, avoiding the occurrence of an ablation vacuum zone, and allowing the tumor tissue to be completely ablated.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical devices, and in particular to an ablation device with a cutting function. Background Art

[0002] The application of pulsed electric field ablation technology in clinical practice is based on the electroporation effect of pulsed electric fields. According to the data, electroporation is divided into reversible electroporation and irreversible electroporation. Irreversible electroporation refers to a stronger electric field causing permanent permeability of the cell membrane and resulting in cell death.

[0003] Existing ablation devices mainly use endoscopes to enter the designated position through the bronchial tract, insert the needle into the tumor, and release the ablation electrode through the handle to perform electroporation ablation. The traditional release method of the ablation electrode cannot completely expand the tumor, or after expanding the tumor, it cannot be cut open, thus forming a vacuum area in the discharge ablation area, reducing the tumor ablation area, and failing to completely remove the tumor. Summary of the invention

[0004] The present invention provides an ablation device with a cutting function, which mainly solves the technical problem that the ablation electrode of the existing ablation device punctures into the tumor and cannot be completely released, thereby forming a vacuum area in the discharge ablation area, reducing the tumor ablation area, and failing to completely remove the tumor.

[0005] In order to achieve the above technical objectives, the present invention adopts the following technical solutions:

[0006] An ablation device with cutting function, comprising:

[0007] The insulating sleeve has a first through passage;

[0008] an ablation electrode having a first end and a second end, wherein the first end of the ablation electrode is arranged at one end of the insulating sleeve, the ablation electrode is a hollow structure, and the ablation electrode has a plurality of ablation claws, and the ablation claws can expand toward the outside of the ablation electrode under force, wherein one or more of the ablation claws on the ablation electrode are provided with a cutting edge for cutting;

[0009] A puncture needle having a needle tip, wherein the puncture needle is arranged at the second end of the ablation electrode; by applying an external force to the ablation electrode, the second end of the ablation electrode and the first end of the ablation electrode are brought close to each other, and the ablation claw of the ablation electrode is transformed from an initial state without force to an expanded state after force and maintained;

[0010] The outer sheath is sleeved on the outside of the insulating sleeve, and the outer sheath has a third through passage. The insulating sleeve can move axially relative to the outer sheath, and the ablation electrode and the puncture needle can be placed in the third passage of the outer sheath.

[0011] In some embodiments, it also includes a needle tube fixedly disposed in the first channel of the insulating sleeve, wherein one end of the needle tube connected to the ablation electrode is located in the insulating sleeve, and one end of the needle tube is connected to the first end of the ablation electrode, and the needle tube is used to transfer ablation energy to the ablation electrode.

[0012] In some embodiments, the needle tube has a second channel, and a traction wire is provided in the second channel of the needle tube. The traction wire can move axially relative to the needle tube, and one end of the traction wire passes through the first end and the second end of the ablation electrode and is connected to the second end of the ablation electrode.

[0013] In some embodiments, a handle is further included, wherein the handle includes a grip and a push rod, one end of the outer sheath is connected to the grip, one end of the insulating sleeve is connected to the push rod, and the push rod can move axially relative to the grip.

[0014] In some embodiments, a fourth channel is provided on the handle, the fourth channel is adapted to the shape of the push rod, and a portion of the push rod is movably inserted into the fourth channel of the handle.

[0015] In some embodiments, a first threaded hole is provided on the handle, a locking knob is provided on the first threaded hole, and one end of the locking knob can abut against or disengage from the push rod.

[0016] In some embodiments, a Y-shaped channel is provided at one end of the push rod away from the outer sheath tube, the Y-shaped channel comprising a control channel and an energy channel, one end of the traction wire passes through the control channel and is fixed to one end of the control channel, and the energy channel is used to connect the needle tube with an external energy generator.

[0017] In some embodiments, a pull cap is provided at one end of the control channel, the pull cap is connected to the traction wire, and the pull cap is movably provided at one end of the control channel. The ablation electrode is moved to and maintained in an expanded state by moving the pull cap.

[0018] In some embodiments, a first limiting structure is provided between the control channel and the pull cap, and the first limiting structure includes a first card slot and a second card slot alternately arranged on the control channel and a first boss arranged on the pull cap, or a first boss arranged on the control channel and a first card slot and a second card slot alternately arranged on the pull cap, and the first boss is adapted to the first card slot and the second card slot, and when the first boss is located on the first card slot, the ablation electrode is in an unstressed state, and when the first boss is connected to the second card slot, the ablation electrode is in a stressed state, and the ablation claw is in an outwardly expanded state and maintained.

[0019] In some embodiments, a preset height difference is provided between the first card slot and the second card slot in the axial direction of the control channel, and the preset height difference is equal to a distance that the second end of the ablation electrode moves toward the first end of the ablation electrode.

[0020] In some embodiments, it also includes a cable assembly that is detachably disposed at one end of the energy channel, the cable assembly includes a plug and a needle core disposed on the plug, when a portion of the plug is inserted into the energy channel, the needle core abuts against and is connected to the needle tube.

[0021] In some embodiments, a plug rod is provided on a side of the plug close to the energy channel, the plug rod is provided with a preset taper, and the plug rod is adapted to the energy channel.

[0022] In some embodiments, a rotary joint is provided on the plug-in rod, a first internal thread is provided on the rotary joint, a first external thread matching the internal thread is provided at one end of the energy channel, and the plug is detachably mounted on the push rod via the rotary joint.

[0023] In some embodiments, a second limiting structure is provided on the plug-in rod, and the second limiting structure is composed of an annular limiting boss arranged on the outer surface of the plug-in rod, and the inner wall of the rotary joint is provided with an adaptive annular clamping boss, and the annular clamping boss abuts against the annular clamping boss to limit the rotary joint in the axial direction of the plug-in rod.

[0024] In some embodiments, the ablation claw of the ablation electrode is elastically deformed in an expanded state, and when the external force is removed, the ablation claw of the ablation electrode returns to an initial state.

[0025] In some embodiments, a developing device is provided on a side of the outer sheath tube close to the ablation electrode, and the developing device is a barium sulfate coating or a platinum-iridium ring.

[0026] In some embodiments, a pre-bending structure is provided on a side of the needle core away from the plug.

[0027] In some embodiments, an expandable balloon is disposed in the ablation electrode, and the balloon is provided with a control interface, and the control interface is used to control the expansion and contraction of the expandable balloon.

[0028] Compared with the prior art, the present invention has the following beneficial effects:

[0029] The present application arranges the ablation electrode into a hollow expandable structure, and arranges a cutting edge on the ablation claw of the ablation electrode. When the ablation electrode is under force, the ablation claw is driven to bend and expand toward the outside of the ablation electrode, and the target tissue is cut by the cutting edge on the ablation claw, so that the discharge ablation area of ​​the ablation electrode will not have a vacuum area of ​​the traditional ablation device, thereby expanding the ablation area and allowing the tumor to be completely ablated.

[0030] Additional aspects and advantages of the present application will be partially given in the following description, which will become apparent from the following description, or will be understood through the practice of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] Figure 1 It is a schematic structural diagram of an expanded ablation electrode of an ablation device with a cutting function according to the present invention;

[0032] Figure 2 It is a schematic diagram of the overall structure of an ablation device with cutting function according to the present invention;

[0033] Figure 3 It is a schematic structural diagram of an ablation electrode of an ablation device with a cutting function according to the present invention in a natural state without being subjected to force;

[0034] Figure 4 It is a structural schematic diagram of a handle of an ablation device with cutting function according to the present invention;

[0035] Figure 5 It is a schematic structural diagram of a push rod of an ablation device with cutting function according to the present invention;

[0036] Figure 6 It is a schematic diagram of the internal structure of a push rod of an ablation device with cutting function according to the present invention;

[0037] Figure 7 for Figure 6 Enlarged view of point A in the middle;

[0038] Figure 8 for Figure 6 Sectional view at the middle BB;

[0039] Fig. 9 It is a partial structural cross-sectional view of a cable assembly of an ablation device with cutting function according to the present invention;

[0040] Fig.10 for Fig. 9 Enlarged view of point C in the middle;

[0041] Fig.11 It is a schematic diagram of the three-dimensional structure of a cable assembly of an ablation device with a cutting function according to the present invention without a rotary joint;

[0042] Fig.12 It is a schematic diagram of bending the needle core of a cable assembly of an ablation device with cutting function according to the present invention;

[0043] Fig.13 It is a schematic diagram of the structure of the control channel of an ablation device with cutting function of the present invention. DETAILED DESCRIPTION

[0044] The present application is further described in detail below in conjunction with specific drawings. In the description of this embodiment, unless otherwise specified, the terms "left", "right", etc. indicate directions or positional relationships based on the directions or positional relationships shown in the drawings, which are only for the convenience of describing the present application and simplifying the description, and do not indicate or imply that the present application must have a specific direction, be constructed and operated in a specific direction, and therefore cannot be understood as limiting the present application.

[0045] like Figure 1 and Figure 2 As shown, an ablation device with cutting function provided by the present invention mainly includes an insulating sleeve 300, an ablation electrode 100 and a puncture needle 104. Among them, the insulating sleeve 300 is a long tubular structure, and has a first channel running through both ends of itself; the ablation electrode 100 is arranged at one end of the insulating sleeve 300, and the ablation electrode 100 has a first end 102 and a second end 103, and the first end 102 of the ablation electrode 100 is connected to the insulating sleeve 300; the ablation electrode 100 is a hollow structure, and a plurality of ablation claws 101 are arranged between the first end 102 and the second end 103 of the ablation electrode 100, wherein the ablation claws 101 can expand from the central axis of the ablation electrode 100 to the outside direction of the ablation electrode 100 under force, thereby forming a spherical structure or an ellipsoidal spherical structure, and can maintain this state. It should be particularly noted that, as Figure 3As shown, a plurality of ablation claws 101 are provided with cutting edges 1011 for cutting, and the cutting edges 1011 are used to cut the target tissue and cut and stretch the target tissue. In this embodiment, the number of ablation claws 101 is 4, and the number of cutting edges 1011 is 4. Optionally, the number of cutting claws 101 can be 5, 6 or other numbers. To ensure a better cutting effect, the number of cutting edges 1011 is consistent with the number of cutting claws. In order to deliver the ablation electrode 100 to the target tissue, a puncture needle 104 is provided at the second end 103 of the ablation electrode 100, which has a needle tip. The front end of the puncture needle 104 has a cutting edge for puncturing and cutting the tissue. It should be particularly noted that the puncture needle 104 is an insulating structure and cannot conduct electricity. For example, the puncture needle 104 is made of ceramic or metal. In this case, the puncture needle 104 needs to be insulated, for example, a parylene coating or an insulating coating made of an insulating material such as a polyimide solution is provided on the puncture needle 104. In this embodiment, the puncture needle 104 has a certain diameter, and its size is close to that of the ablation electrode 100, so that a certain space can be provided after puncture to allow the ablation electrode 100 to enter the target tissue. The target tissue is punctured by the puncture needle 104, and the ablation electrode 100 is sent into the target tissue through the insulating sleeve 300 to expand the ablation claws 101, and the target tissue is cut by the cutting edge 1011, and then discharge ablation is performed.

[0046] In the present application, a plurality of expandable ablation claws 101 are provided on the ablation electrode 100, and matching cutting edges 1011 are provided on the ablation claws 101. When the ablation electrode 100 enters the tumor tissue, the tumor tissue can be cut open, thereby avoiding the situation where the structure of the traditional ablation electrode 100 cannot support the tumor, forming an ablation vacuum zone, and causing incomplete ablation.

[0047] In one embodiment, in order to transfer the ablation energy to the ablation electrode 100, the ablation device further includes a needle tube 301 disposed in the first channel of the insulating sleeve 300, and the insulating sleeve 300 and the needle tube 301 cannot move relative to each other. The needle tube 301 has the performance of a wire, and one end of the needle tube 301 is connected to the first end of the ablation electrode 100 for communication, and the other end of the needle tube 301 is connected to an external energy generator. In this embodiment, the needle tube 301 has a certain support capacity, which can provide a certain support force to the insulating sleeve 300 coated on the outside thereof, and at the same time, the needle tube 301 has a certain bending guide property, which can meet the bending operation of the human body in the tortuous cavity of the human body. At the same time, the end of the needle tube 301 connected to the ablation electrode 100 should be located inside the insulating sleeve 300, so as to prevent the needle tube 301 from extending out of the insulating sleeve 300 to form a discharge area for energy release, so that the ablation electrode 100 cannot accurately control the ablation range.

[0048] Furthermore, the needle tube 301 has a second channel running through both ends thereof, and a traction wire 200 is arranged in the second channel of the needle tube 301, and the traction wire 200 can move in the axial direction of the needle tube 301 relative to the needle tube 301, wherein one end of the traction wire 200 passes through the first end 102 of the ablation electrode 100 of the hollow structure and is connected to the second end 103 of the ablation electrode 100. Specifically, due to the stationary state of the needle tube 301 and the insulating sleeve 300, the traction wire 200 is pulled to make the traction wire 200 move axially relative to the needle tube 301, so that the second end 103 of the ablation electrode 100 is brought closer to the first end 102 of the ablation electrode 100, thereby making the ablation claw 101 expand outward to form a spherical, ellipsoidal or columnar structure. As another variant implementation of this embodiment, an inflatable balloon can be provided in the hollow structure of the ablation electrode 100. The inflatable balloon is provided with a control interface to communicate with the outside world, and the inflatable balloon is controlled through the control interface. In this case, there is no need to set the traction wire 200, and only the expansion control of the inflatable balloon needs to be performed. In this embodiment, the control of the inflatable balloon can be performed by inflating or filling liquid through the second channel of the needle tube 301, so that the ablation electrode 100 can be passively expanded when the balloon is expanded. Optionally, the needle tube 301 can also be set as a solid structure. In this case, two independent channels need to be set in the first channel of the insulating sleeve 300, one channel for the installation of the needle tube 301, and the other channel for the installation of the traction wire 200. In this case, the expansion and ablation of the ablation electrode 100 can also be completed.

[0049] In one embodiment, since the ablation electrode 100 has a cutting edge 1011 and a puncture needle 104 is provided at the front end of the ablation electrode 100, it is necessary to be very careful when delivering the ablation electrode 100 to the target position to avoid causing mechanical damage to normal human tissue. The ablation device also includes an outer sheath 401 arranged on the outside of the insulating sleeve 300, and the insulating sleeve 300 can move axially relative to the outer sheath 401. Specifically, the outer sheath 401 is a flexible catheter, and its material is PTFE (polytetrafluoroethylene) or PEEK or spring tube, etc. The outer sheath 401 has a third channel running through both ends. The inner diameter of the third channel is larger than the outer diameter of the insulating sleeve 300 and the maximum outer diameter of the ablation electrode 100 and the puncture needle 104, so that the ablation electrode 100 and the puncture needle 104 can be retracted in the outer sheath 401 before being transported to the destination. When the ablation electrode 100 is transported to the destination, the axial relative movement between the insulating sleeve 300 and the outer sheath 401 is used to make the ablation electrode 100 and the puncture needle 104 extend out of the third channel of the outer sheath 401, and then the relative movement between the insulating sleeve 300 and the outer sheath 401 is used to make the puncture needle 104 pierce the target tissue, and the ablation electrode 100 is transported to the target tissue for cutting and ablation.

[0050] In one embodiment, Figure 4 As shown, in order to facilitate the pushing of the insulating sleeve 300, the ablation electrode 100 and the puncture needle 104 are withdrawn from the outer sheath 401 or both are retracted into the outer sheath, and the ablation device also includes a handle. Specifically, the handle includes a grip 400 and a push rod 500, wherein the grip 400 and the push rod 500 can perform axial relative movement. In this embodiment, the outer sheath 401 is connected to the grip 400, and a stress expansion tube 402 is provided at the connection between the two to cover the two. By providing the stress expansion tube 402, the outer sheath 401 can be effectively prevented from bending, and the outer sheath 401 is protected. By controlling the relative movement of the grip 400 and the push rod 500, the relative movement between the outer sheath 401 and the insulating sleeve 300 is controlled, and the storage and release of the ablation electrode 100 and the puncture needle 104 are completed. Furthermore, a fourth channel is provided on the handle 400, and part of the push rod 500 is adapted to the fourth channel of the handle, and the push rod 500 is movably inserted into the fourth channel of the handle 400. In this embodiment, the push rod 500 inserted into the fourth channel of the handle 400 is a cylindrical structure, and the fourth channel is a cylindrical channel adapted thereto. Optionally, the structure of the push rod 500 and the structure of the fourth channel can be a columnar structure, such as a triangular prism, a quadrangular prism, or an elliptical cylindrical structure.

[0051] Furthermore, if Figure 4 and Figure 5As shown, in order to fix the position of the push rod 500 and make the position of the ablation electrode 100 fixed and immovable, a first threaded hole is set on the shell 403 of the handle 400, and a locking knob 404 is provided on the first threaded hole. The first threaded hole passes through the tube wall of the shell 403 and is connected to the fourth channel. The locking knob 404 rotates on the first threaded hole to achieve one end of it abutting or disengaging from the push rod 500. When the locking knob 404 abuts against the push rod 500, the position of the push rod 500 is fixed and cannot move axially. At this time, the position of the ablation electrode 100 is fixed, and the insulating sleeve 300 will not move axially relative to the outer sheath tube 401; when the locking knob 404 is separated from the push rod 500, the relative position between the push rod 500 and the shell 403 can be adjusted at this time, thereby realizing the position adjustment of the ablation electrode 100, and the ablation electrode 100 and the puncture needle 104 are stored in the outer sheath tube 401 or pushed out of the outer sheath tube 401. In order to make the fixed structure of the push rod 500 more stable, a first locking surface 5011 of a planar structure is provided on the push rod 500, and one end of the locking knob 404 close to the push rod 500 is provided with a planar structure, so as to increase the contact surface between the locking knob 404 and the push rod 500 and increase the friction force, so that the push rod 500 is not easy to slide relative to the handle 400. Furthermore, the relative movement length of one end of the locking knob 404 relative to the first locking surface 5011 should meet the requirements of the ablation electrode 100 and the puncture needle 104 being completely accommodated in the outer sheath 401 and being able to completely push the ablation electrode 100 and the puncture needle 104 out of the outer sheath 401.

[0052] In one embodiment, a Y-shaped channel is provided at one end of the push rod 500, and the Y-shaped channel includes an energy channel 502 and a control channel 503. In this embodiment, the energy channel 502 and the push rod 500 are on an axis, and the energy channel 502 is connected to the second channel of the needle tube 301 connected to the push rod 500. In this embodiment, the needle tube 301 located in the push rod 500 extends to the intersection of the Y-shaped channel, such as Figure 6 and Figure 7 One end of the traction wire 200 is connected to the puncture needle 104 on one side of the second end 103 of the ablation electrode 100. The puncture needle 104 is pulled to squeeze the ablation electrode 100, so that the ablation electrode 100 expands. The other end of the traction wire 200 passes through the second channel of the needle tube 301 and extends to the control channel 503. The positional relationship between the traction wire 200, the needle tube 301 and the insulating sleeve 300 is shown in FIG. Figure 8 shown.

[0053] Furthermore, a pull cap 504 is provided at one end of the control channel 503 for fixing the traction wire 200. The traction wire 200 is connected to the pull cap 504, and the operator pulls the traction wire 200 by controlling the pull cap 504, thereby controlling the state of the ablation electrode 100, making it easier for the ablation electrode 100 to expand outwards and maintain the expanded state. Figure 1 When the operator releases the pull cap 504, the ablation electrode 100 returns to its initial state, ie, a straight state, as shown in FIG. Figure 3 shown.

[0054] Further, refer again to Figure 5 In order to achieve precise control of the state of the ablation electrode 100 by controlling the position of the pull cap 504, a first limiting structure is set between the control channel 503 and the pull cap 504, and the first limiting structure includes a first card slot 5031 and a second card slot 5032 alternately arranged on the control channel 503 and a first boss 5041 arranged on the pull cap 504, wherein the first boss 5041 is adapted to the first card 5031 and the second card slot 5032, when the first boss 5041 is located on the first card slot 5031, the ablation electrode 100 is in an initial state without force, and when the first boss 5041 is located on the second card slot 5032, the ablation electrode 100 is in an expanded state and can continue to maintain this state. As a modified implementation of the present embodiment, the first card slot 5031 and the second card slot 5032 may be arranged on the pull cap 504, and a matching first boss 5041 may be arranged on the control channel 503, and the first card slot 5031 or the second card slot 5032 may be controlled to engage with the first boss 5041 on the control channel 503 by rotating the pull cap 504. It is understood that the relative offset angle formed by the staggered arrangement of the first card slot 5031 and the second card slot 5032 is not limited by the present invention.

[0055] In one embodiment, Fig.13 As shown, the first slot 5031 and the second slot 5032 are arranged along the axial direction of the control channel 503, and a preset height difference 5033 is arranged between the first slot 5031 and the second slot 5032, wherein the preset height difference 5033 is equal to the distance that the second end 103 of the ablation electrode 100 moves toward the first end 102 of the ablation electrode 100. That is, the first boss 5041 is located on the first slot 5031, and the ablation electrode is in an unstressed state. When the first boss 5041 is connected to the second slot 5032, the ablation electrode 100 is in a fully expanded state, that is, the movement of the pull cap 504 can make the state of the ablation electrode 100 respond in real time without delay, avoiding the situation that the pull cap 504 moves and the ablation electrode 100 is still in the initial state, so that the operator can quickly determine the state of the ablation electrode 100 through the position of the first boss 5041.

[0056] In one embodiment, the ablation device also includes a cable assembly 600 arranged at one end of the energy channel 502, the cable assembly 600 includes a plug 601 and a needle core 602 arranged on the plug 601, and the plug 601 is partially inserted into the energy channel 502 so that the needle core 602 can abut against the needle tube 301 and achieve electrical connection, thereby enabling an external energy generator to transfer ablation energy to the ablation electrode 100 through the needle core 602 and the needle tube 301.

[0057] Furthermore, in order to facilitate the plugging of the push rod 500 and the cable assembly 600, a plug rod 603 is provided on the plug 601, and the outer shape structure of the energy channel 502 is adapted thereto. The plug rod 603 is a conical structure with a preset taper, and the energy channel 502 is also a corresponding conical structure, so that the plug rod 603 is plugged into the energy channel 502, and the rotation angle of the plug rod 603 can be adjusted, so that the needle core 602 located on the plug 601 can be better combined with the needle tube 301 in the push rod 500, ensuring good conduction performance. Furthermore, in order to ensure the sealing performance at the junction of the energy channel 502 and the cable assembly 600, the taper of the plug rod 603 and the taper of the energy channel 502 should meet the requirements of GB / 1962.1.

[0058] Optionally, the plug rod 603 may be a cylindrical structure, as long as the plug rod 603 can rotate in the energy channel 502; optionally, if the sealing performance between the two is not considered, the cone ratio of the plug rod 603 can also be other proportional values.

[0059] In one embodiment, in order to avoid the plug 601 of the cable assembly 600 from being separated from the energy channel 502 of the push rod 500 or the needle core 602 from having poor contact with the needle tube 301 during operation, a rotary joint 604 is provided on the connecting rod 603, a first internal thread 6041 is provided on the rotary joint 604, and a matching first external thread 5021 is provided on the outer wall of the energy channel 502. Through the cooperation of the first external thread 5021 and the first internal thread 6041, the plug 601 can be detachably arranged on the energy channel 502 of the push rod 500 through the rotary joint 604.

[0060] Furthermore, since the cable assembly 600 and the push rod 500 are connected by threaded fitting, when the two are disassembled or connected, the rotary joint 604 needs to be rotated, so the rotary joint 604 is movably arranged on the plug rod 603, and the rotary joint 604 only rotates around the axis of the plug rod 603, and does not move in the axis direction of the plug rod 603. Specifically, Figure 9-11As shown, a second limiting structure is provided on the plug rod 603, and the second limiting structure includes an annular limiting boss 6031 provided on the outer surface of the plug rod, and an annular clamping boss 6042 is provided on the inner wall surface of the rotary joint 604. Fig.10 As shown, the outer diameter of the annular limiting boss 6031 is adapted to the insertion hole diameter on the rotary joint 604, so that the two can rotate relative to each other without large displacement in the radial direction. An annular clamping boss 6042 is provided on the inner wall of the insertion hole that cooperates with the plug rod 603 inside the rotary joint 604, and abuts against the annular limiting boss 6031, so as to limit the rotary joint 604 in the axial direction. When the first internal thread 6041 on the rotary joint 604 cooperates with the first external thread 5021 on the energy channel 502, the rotary joint 604 only rotates axially relative to the plug rod 603. Furthermore, a first guiding surface is provided on one side of the annular limiting boss 6031 close to the head end of the plug rod 603 to facilitate the clamping assembly of the rotary joint 604, as shown in FIG. Fig.10 As shown, the first guide surface is an inclined surface structure, and optionally, it can also be an arc surface structure. Further, the swivel joint 604 is further limited in the axial direction, such as Fig. 9 and Fig.11 As shown, a first spacing 6042 between a surface where the annular clamping boss 6042 abuts against the annular limiting boss 6031 and a first end of the non-threaded structure of the rotary joint 604 is slightly smaller than or equal to a second spacing 6032 between the annular limiting boss 6031 and one end of the plug-in rod 603, so as to form a clearance fit, thereby enabling the rotary joint 604 to rotate smoothly around the plug-in rod 603.

[0061] In one embodiment, the ablation claw 101 of the ablation electrode 100 is elastically deformed in the expanded state, and when the external force is removed, the ablation claw 101 of the ablation electrode 100 returns to the initial state. By using elastic materials such as stainless steel or nickel-titanium memory alloy to set the ablation claw 101, so that it is elastically deformed and can be restored to the initial state without external force, the ablation electrode 100 can be used multiple times, making the ablation device easier to operate.

[0062] In one embodiment, in order to be able to observe in real time the specific position to which the ablation electrode 100 is sent by the outer sheath 401, a developing device is provided at the end of the outer sheath 401 away from the handle 400, wherein the developing device is a barium sulfate or platinum-iridium ring, etc., and combined with CT, the end of the outer sheath 401 provided with the developing device can display the position, thereby observing in real time the position to which the ablation electrode 100 is sent.

[0063] In one embodiment, in order to achieve effective contact between the needle core 602 and the needle tube 301, the needle core 602 is bent, such as Fig.12As shown, by bending one end of the needle core 602 to form a bent portion 6022, the needle core 602 and the needle tube 301 are in closer contact, so that the ablation energy can be continuously and effectively transmitted to the ablation electrode 100. Optionally, the needle core 602 may not be bent, in which case the contact length between the needle core 602 and the needle tube 301 needs to be greater than the length when the needle core 602 is bent, so as to achieve a longer effective contact length and achieve effective transmission of ablation energy.

[0064] The above is only a preferred embodiment of the present invention. It should be noted that a person skilled in the art can make several improvements and modifications without departing from the principle of the present invention. These improvements and modifications should also be considered as the protection scope of the present invention.

Claims

1. An ablation device with cutting function, characterized in that: include: The insulating sleeve has a first through passage; an ablation electrode having a first end and a second end, wherein the first end of the ablation electrode is arranged at one end of the insulating sleeve, the ablation electrode is a hollow structure, and the ablation electrode has a plurality of ablation claws, and the ablation claws can expand toward the outside of the ablation electrode under force, wherein one or more of the ablation claws on the ablation electrode are provided with a cutting edge for cutting; A puncture needle having a needle tip, wherein the puncture needle is arranged at the second end of the ablation electrode; by applying an external force to the ablation electrode, the second end of the ablation electrode and the first end of the ablation electrode are brought close to each other, and the ablation claw of the ablation electrode is transformed from an initial state without force to an expanded state after force and maintained; The outer sheath is sleeved on the outside of the insulating sleeve, and the outer sheath has a third through passage. The insulating sleeve can move axially relative to the outer sheath, and the ablation electrode and the puncture needle can be placed in the third passage of the outer sheath.

2. The ablation device with cutting function according to claim 1, characterized in that: It also includes a needle tube fixedly disposed in the first channel of the insulating sleeve, wherein one end of the needle tube connected to the ablation electrode is located in the insulating sleeve, one end of the needle tube is connected to the first end of the ablation electrode, and the needle tube is used to transmit ablation energy to the ablation electrode.

3. The ablation device with cutting function according to claim 2, characterized in that: The needle tube has a second channel, and a traction wire is arranged in the second channel of the needle tube. The traction wire can move axially relative to the needle tube, and one end of the traction wire passes through the first end and the second end of the ablation electrode and is connected to the puncture needle.

4. The ablation device with cutting function according to claim 3, characterized in that: It also includes a handle, which includes a grip and a push rod. One end of the outer sheath is connected to the grip, and one end of the insulating sleeve is connected to the push rod. The push rod can move axially relative to the grip.

5. The ablation device with cutting function according to claim 4, characterized in that: The handle is provided with a fourth channel, the fourth channel is adapted to the shape of the push rod, and a part of the push rod is movably inserted into the fourth channel of the handle.

6. The ablation device with cutting function according to claim 4, characterized in that: The handle is provided with a first threaded hole, the first threaded hole is provided with a locking knob, and one end of the locking knob can abut against or be separated from the push rod.

7. The ablation device with cutting function according to claim 4, characterized in that: A Y-shaped channel is arranged at one end of the push rod away from the outer sheath tube, and the Y-shaped channel includes a control channel and an energy channel. One end of the traction wire passes through the control channel and is fixed to one end of the control channel. The energy channel is used to connect the needle tube with an external energy generator.

8. The ablation device with cutting function according to claim 7, characterized in that: A pull cap is provided at one end of the control channel, the pull cap is connected to the traction wire, and the pull cap is movably provided at one end of the control channel. The ablation electrode is moved to and maintained in an expanded state by moving the pull cap.

9. The ablation device with cutting function according to claim 8, characterized in that: A first limiting structure is provided between the control channel and the pull cap, and the first limiting structure includes a first card slot and a second card slot alternately arranged on the control channel and a first boss arranged on the pull cap, or a first boss arranged on the control channel and a first card slot and a second card slot alternately arranged on the pull cap, and the first boss is adapted to the first card slot and the second card slot, and when the first boss is located on the first card slot, the ablation electrode is in an unstressed state, and when the first boss is clamped on the second card slot, the ablation electrode is in a stressed state, and the ablation claw is in an outwardly expanded state and maintained.

10. The ablation device with cutting function according to claim 9, characterized in that: A preset height difference is provided between the first clamping slot and the second clamping slot in the axial direction of the control channel, and the preset height difference is equal to a distance that the second end of the ablation electrode moves toward the first end of the ablation electrode.

11. The ablation device with cutting function according to claim 7, characterized in that: It also includes a cable assembly that is detachably arranged at one end of the energy channel. The cable assembly includes a plug and a needle core arranged on the plug. When part of the plug is inserted into the energy channel, the needle core abuts against and is connected to the needle tube.

12. The ablation device with cutting function according to claim 11, characterized in that: The plug is provided with a plugging rod on one side close to the energy channel, the plugging rod is provided with a preset taper, and the plugging rod is adapted to the energy channel.

13. The ablation device with cutting function according to claim 12, characterized in that: The plug-in rod is provided with a rotary joint, the rotary joint is provided with a first internal thread, one end of the energy channel is provided with a first external thread adapted thereto, and the plug is detachably arranged on the push rod through the rotary joint.

14. The ablation device with cutting function according to claim 13, characterized in that: A second limiting structure is provided on the plug-in rod, and the second limiting structure is composed of an annular limiting boss arranged on the outer surface of the plug-in rod. The inner wall of the rotary joint is provided with an adaptive annular clamping boss, and the annular clamping boss abuts against the annular clamping boss to limit the rotary joint in the axial direction of the plug-in rod.

15. The ablation device with cutting function according to claim 1, characterized in that: The ablation claw of the ablation electrode is elastically deformed in an expanded state, and when the external force is removed, the ablation claw of the ablation electrode returns to an initial state.

16. The ablation device with cutting function according to claim 1, characterized in that: A developing device is arranged on a side of the outer sheath tube close to the ablation electrode, and the developing device is a barium sulfate coating or a platinum-iridium ring.

17. The ablation device with cutting function according to claim 11, characterized in that: A pre-bending structure is provided on a side of the needle core away from the plug.

18. The ablation device with cutting function according to claim 1, characterized in that: An expandable balloon is arranged inside the ablation electrode, and the balloon is provided with a control interface, and the control interface is used to control the expansion and contraction of the expandable balloon.

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