An ablation device with cutting function

Abstract

The application belongs to the technical field of medical devices, and provides an ablation device with a cutting function, which comprises a first channel through insulating sleeve; a hollow structure ablation electrode arranged at one end of the insulating sleeve, the ablation electrode having a plurality of ablation prongs, the ablation prongs being capable of expanding to the outside of the ablation electrode under a force state, wherein one or more ablation prongs on the ablation electrode are provided with a cutting edge for cutting; and a puncture needle head with a needle tip arranged at the second end of the ablation electrode; an external force is applied to the ablation electrode to expand the ablation electrode, and the ablation prongs of the ablation electrode are transformed from an initial state without force to an expanded state after force and maintained. The application can expand the plurality of ablation prongs under a force state, and the cutting edge arranged on the ablation prongs can separate and expand the tumor tissue, avoid the emergence of an ablation vacuum area, and completely ablate the tumor tissue.

Description

TECHNICAL FIELD

[0001] The present application belongs to the technical field of medical devices, in particular to an ablation device with cutting function. BACKGROUND

[0002] The application of pulsed electric field ablation technology in clinic is based on the electroporation effect of pulsed electric field. Data shows that electroporation is divided into reversible electroporation and irreversible electroporation. Irreversible electroporation refers to stronger electric field causing permanent permeability of cell membrane and leading to cell death.

[0003] The existing ablation device mainly enters the designated position through the bronchial tube through the endoscope, and the needle is pierced into the tumor site, and the ablation electrode is released and electroporation ablation is performed through the handle part. The release mode of the traditional ablation electrode cannot completely expand the tumor, or after expanding the tumor, it cannot cut the tumor, so as to form a vacuum area in the discharge ablation area, reduce the tumor ablation area, and cannot completely remove the tumor. SUMMARY

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

[0005] In order to achieve the above technical purpose, the present application adopts the following technical scheme:

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

[0007] An insulating sleeve having a first through channel;

[0008] An ablation electrode having a first end and a second end, the first end of the ablation electrode being arranged at one end of the insulating sleeve, the ablation electrode being a hollow structure, the ablation electrode having a plurality of ablation prongs, the ablation prongs being capable of expanding to the outside of the ablation electrode under stress, wherein one or more ablation prongs on the ablation electrode are provided with a cutting edge for cutting; and

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

[0010] In some embodiments, a needle tube is further included, which is fixedly arranged in the first channel of the insulation sleeve, one end of the needle tube connected with the ablation electrode is located in the insulation sleeve, one end of the needle tube is connected with the first end of the ablation electrode, and the needle tube is used for transmitting ablation energy to the ablation electrode.

[0011] In some embodiments, the needle tube has a second channel, a pull wire is arranged in the second channel of the needle tube, the pull wire can be axially moved relative to the needle tube, one end of the pull wire passes through the first end and the second end of the ablation electrode, and is connected with the second end of the ablation electrode.

[0012] In some embodiments, an outer sheath tube is further included, which is sleeved outside the insulation sleeve, the outer sheath tube has a third channel, the insulation sleeve can be axially moved relative to the outer sheath tube, and the ablation electrode and the puncture needle can be arranged in the third channel of the outer sheath tube.

[0013] In some embodiments, a handle is further included, which comprises a grip and a push rod, one end of the outer sheath tube is connected with the grip, one end of the insulation sleeve is connected with the push rod, and the push rod can be axially moved relative to the grip.

[0014] In some embodiments, the grip is provided with a fourth channel, the fourth channel is matched with the shape of the push rod, and part of the push rod is movably inserted into the fourth channel of the grip.

[0015] In some embodiments, the grip is provided with a first threaded hole, a locking knob is arranged on the first threaded hole, and one end of the locking knob can abut or be separated from the push rod.

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

[0017] In some embodiments, one end of the control channel is provided with a pull cap, the pull cap is connected with the pull wire, and the pull cap is movably arranged at one end of the control channel, so that the ablation electrode is expanded and maintained by moving the pull cap.

[0018] In some embodiments, a first limiting structure is arranged between the control channel and the pull cap, the first limiting structure comprising a first slot and a second slot arranged on the control channel in an interleaved manner and a first boss arranged on the pull cap, or a first boss arranged on the control channel and a first slot and a second slot arranged on the pull cap in an interleaved manner, the first boss being adapted with the first slot and the second slot, when the first boss is located on the first slot, the ablation electrode is in an unstressed state, when the first boss is clamped on the second slot, the ablation electrode is in a stressed state, and the ablation prong is in an outwardly expanded state and maintained.

[0019] In some embodiments, the first slot and the second slot have a preset height difference in the axial direction of the control channel, and the preset height difference is equal to the distance by which the second end of the ablation electrode moves towards the first end of the ablation electrode.

[0020] In some embodiments, a cable assembly is detachably arranged at one end of the energy channel, the cable assembly comprising a plug and a needle core arranged on the plug, when a part of the plug is inserted into the energy channel, the needle core abuts against the needle tube and is connected.

[0021] In some embodiments, the plug is provided with an insertion rod near one side of the energy channel, the insertion rod is provided with a preset taper, and the insertion rod is adapted with the energy channel.

[0022] In some embodiments, the insertion rod is provided with a rotating joint, the rotating joint is provided with a first internal thread, one end of the energy channel is provided with a first external thread adapted therewith, and the plug is detachably arranged on the push rod through the rotating joint.

[0023] In some embodiments, the insertion rod is provided with a second limiting structure, the second limiting structure comprises an annular limiting boss arranged on the outer surface of the insertion rod, and the inner wall of the rotating joint is provided with an annular clamping boss adapted therewith, the annular clamping boss abuts against the annular clamping boss to limit the rotating joint in the axial direction of the insertion rod.

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

[0025] In some embodiments, the outer sheath is provided with a developing device near one side of the ablation electrode, the developing device is barium sulfate paint or a platinum-iridium ring.

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

[0027] In some embodiments, an expandable balloon is provided 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 stress, 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 as in traditional ablation devices, thereby expanding the ablation area and enabling complete ablation of the tumor.

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

[0031] Figure 1 This 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 This is a schematic diagram of the overall structure of an ablation device with a cutting function according to the present invention;

[0033] Figure 3 This is a schematic structural diagram of an ablation electrode of an ablation device with a cutting function in a natural state without force;

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

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

[0036] Figure 6 This is a schematic diagram of the internal structure of a push rod of an ablation device with a 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 Cross-sectional view at the middle BB;

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

[0040] Figure 10 As Figure 9 Enlarged view at C;

[0041] Figure 11 Figure 1 is a perspective view of a cable assembly of an ablation device with cutting function according to the present application;

[0042] Figure 12 Figure 2 is a schematic view of a needle core bending of the cable assembly of the ablation device with cutting function according to the present application;

[0043] Figure 13 Figure 3 is a schematic view of the structure at the control channel of the ablation device with cutting function according to the present application. DETAILED DESCRIPTION

[0044] The present application will be further described below in conjunction with specific drawings. In the description of the present embodiment, unless otherwise specified, the terms "left", "right", and the like indicate the orientation or positional relationship shown in the drawings, and are only used to facilitate the description of the present application and simplify the description, and do not indicate or imply that the present application must have a particular orientation, be constructed and operated in a particular orientation, and therefore cannot be understood as a limitation on the present application.

[0045] As Figure 1 and Figure 2 As shown in FIG. 1, the ablation device with cutting function provided by the present application mainly comprises an insulating sleeve 300, an ablation electrode 100, and a puncture needle 104. The insulating sleeve 300 is a long strip tubular structure having a first channel passing through both ends thereof. The ablation electrode 100 is arranged at one end of the insulating sleeve 300. The ablation electrode 100 has a first end 102 and a second end 103. The first end 102 of the ablation electrode 100 is connected to the insulating sleeve 300. The ablation electrode 100 is a hollow structure. A plurality of ablation prongs 101 are arranged between the first end 102 and the second end 103 of the ablation electrode 100. In a stressed state, the ablation prongs 101 can expand from the central axis of the ablation electrode 100 to the outside of the ablation electrode 100, thereby forming a spherical structure or an ellipsoidal spherical structure, and can maintain this state. It needs to be particularly pointed out that, as shown in FIG. 2, the ablation prongs 101 are arranged in a staggered manner along the circumferential direction of the ablation electrode 100. Figure 3As shown, the plurality of ablation prongs 101 are provided with cutting edges 1011 for cutting, which are used to cut and expand the target tissue. In this embodiment, the number of ablation prongs 101 is four, and the number of cutting edges 1011 is four. Alternatively, the number of ablation prongs 101 can be five, six or any other number. To ensure better cutting effect, the number of cutting edges 1011 is consistent with the number of ablation prongs. In order to send the ablation electrode 100 into 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 piercing and cutting the tissue. It should be 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, and in this case, the puncture needle 104 needs to be insulated, such as being provided with a Parylene coating or an insulating coating made of polyimide solution. In this embodiment, the puncture needle 104 has a certain diameter, which is close to the size of the ablation electrode 100, so that after puncture, a certain space is provided for the ablation electrode 100 to enter the target tissue. The target tissue is pierced by the puncture needle 104, and then the ablation electrode 100 is sent into the target tissue by the insulating sleeve 300 to expand the ablation prongs 101, and then the target tissue is cut by the cutting edges 1011, and then discharge ablation is performed.

[0046] In this application, by providing a plurality of expandable ablation prongs 101 on the ablation electrode 100, and matching cutting edges 1011 on the ablation prongs 101, when the ablation electrode 100 enters the tumor tissue, the tumor tissue can be cut open, avoiding the situation that the structure of the traditional ablation electrode 100 cannot support the tumor to form an ablation vacuum area, resulting in incomplete ablation.

[0047] In one embodiment, in order to deliver ablation energy to the ablation electrode 100, the ablation device further comprises a needle tube 301 provided 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 wire performance, 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 in communication with an external energy generator. In this embodiment, the needle tube 301 has a certain supporting ability, which can provide a certain supporting force to the insulating sleeve 300 wrapped outside it. 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 curved 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 avoid the needle tube 301 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] Further, the needle tube 301 has a second channel through both ends thereof, and a traction wire 200 is arranged in the second channel of the needle tube 301 and can move relative to the needle tube 301 in the axial direction of the needle tube 301, wherein one end of the traction wire 200 penetrates the first end 102 of the hollow-structure ablation electrode 100 and is connected to the second end 103 of the ablation electrode 100. Specifically, due to the static state of the needle tube 301 and the insulating sleeve 300, the traction wire 200 is axially moved relative to the needle tube 301 by pulling the traction wire 200, so that the second end 103 of the ablation electrode 100 is moved towards the first end 102 of the ablation electrode 100, thereby expanding the ablation prongs 101 outward to form a spherical, ellipsoidal or columnar structure. As another variant of the embodiment, an inflatable balloon can also be arranged in the hollow-structure ablation electrode 100, and the inflatable balloon is arranged in communication with the outside through a control interface, and the inflatable balloon is controlled through the control interface, and in this case, the traction wire 200 is not required, and only the inflation control of the inflatable balloon is required. In the embodiment, the control of the inflatable balloon can be inflation or liquid filling through the second channel of the needle tube 301, so that the ablation electrode 100 is passively expanded in the state of balloon expansion. Alternatively, the needle tube 301 can also be arranged in a solid structure, and in this case, two independent channels are required to be arranged in the first channel of the insulating sleeve 300, one channel is for mounting the needle tube 301, and the other channel is for mounting the traction wire 200, and 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 is provided with the cutting blade 1011 and the front end of the ablation electrode 100 is provided with the puncture needle 104, the ablation electrode 100 needs to be very careful when being sent to the target position to avoid mechanical damage to normal tissues of the human body, and the ablation device further comprises an outer sheath 401 arranged outside the insulating sleeve 300, and the insulating sleeve 300 can axially relatively move relative to the outer sheath 401. Specifically, the outer sheath 401 is a flexible catheter, and the material thereof is PTFE (polytetrafluoroethylene) or PEEK or spring tube, etc., and the outer sheath 401 has a third channel through both ends thereof, and the inner diameter of the third channel is greater 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 shrunk in the outer sheath 401 before being transported to the destination, and when the ablation electrode 100 is transported to the destination, the ablation electrode 100 and the puncture needle 104 are stretched out of the third channel of the outer sheath 401 through the axial relative movement between the insulating sleeve 300 and the outer sheath 401, and then the puncture needle 104 pierces the target tissue through the relative movement between the insulating sleeve 300 and the outer sheath 401, and the ablation electrode 100 is transported into the target tissue to cut and ablate.

[0050] In one embodiment, as shown in Figure 4 In order to facilitate the pushing of the insulation sleeve 300, the ablation electrode 100 and the puncture needle 104 are withdrawn from the outer sheath 401 or are retracted into the outer sheath, the ablation device further comprises a handle. Specifically, the handle comprises a handle 400 and a push rod 500, wherein the handle 400 and the push rod 500 can axially move relative to each other. In this embodiment, the outer sheath 401 is connected to the handle 400, and a stress expansion tube 402 is arranged at the connection between the outer sheath 401 and the handle 400 and covers them. By arranging the stress expansion tube 402, the bending of the outer sheath 401 can be effectively prevented, and the outer sheath 401 is protected. By controlling the relative movement of the handle 400 and the push rod 500, the relative movement between the outer sheath 401 and the insulation sleeve 300 is controlled, and the retraction and release of the ablation electrode 100 and the puncture needle 104 are completed. Further, a fourth channel is arranged on the handle 400, a 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 part of 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. Alternatively, the structure of the push rod 500 and the structure of the fourth channel can be a columnar structure, such as a Mitsubishi column or a four-prism column or an elliptical column structure.

[0051] Further, as shown in Figure 4 and Figure 5As shown, in order to fix the position of the push rod 500, fix the position of the ablation electrode 100 and prevent movement, a first threaded hole is arranged on the shell 403 of the handle 400, a locking knob 404 is arranged on the first threaded hole, the first threaded hole penetrates the wall of the shell 403 and communicates with the fourth channel, the locking knob 404 is rotated on the first threaded hole to realize that one end of the locking knob 404 abuts against or is separated 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 cannot move axially relative to the outer sheath 401; when the locking knob 404 is separated from the push rod 500, at this time, the relative position between the push rod 500 and the shell 403 can be adjusted, so that the position of the ablation electrode 100 is adjusted, and the ablation electrode 100 and the puncture needle 104 are stored in or pushed out of the outer sheath 401. In order to make the fixing structure of the push rod 500 more stable, a first locking surface 5011 in a planar structure is arranged on the push rod 500, one end of the locking knob 404 close to the push rod 500 is arranged in a planar structure, the contact surface between the locking knob 404 and the push rod 500 is increased, the friction force is improved, and the push rod 500 is not easy to slide relative to the handle 400. Further, the relative movement length of one end of the locking knob 404 relative to the first locking surface 5011 should satisfy that the ablation electrode 100 and the puncture needle 104 are completely stored in the outer sheath 401 and the ablation electrode 100 and the puncture needle 104 can be completely pushed out of the outer sheath 401.

[0052] In one embodiment, one end of the push rod 500 is provided with a Y-shaped channel, 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 one axis, the energy channel 502 and the second channel of the needle tube 301 connected to the push rod 500 communicate, in this embodiment, the needle tube 301 located in the push rod 500 extends to the intersection of the Y-shaped channel, as shown in Figure 6 and Figure 7 The other end of the traction line 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 is expanded, the other end of the traction line 200 passes through the second channel of the needle tube 301 and extends to the control channel 503, the positional relationship among the traction line 200, the needle tube 301 and the insulating sleeve 300 is as shown in Figure 8 .

[0053] Further, one end of the control channel 503 is provided with a pull cap 504 for fixing the traction wire 200. The traction wire 200 is connected with the pull cap 504, and the operator controls the traction wire 200 by controlling the pull cap 504, so as to control the state of the ablation electrode 100, which is more convenient for the ablation electrode 100 to expand outwardly under stress and maintain the expanded state, as shown in Figure 1 When the operator releases the pull cap 504, the ablation electrode 100 returns to the initial state, i.e., the straight state, as shown in Figure 3 .

[0054] Further, referring again to Figure 5 , in order to realize the accurate control of the state of the ablation electrode 100 by controlling the position of the pull cap 504, a first limiting structure is arranged between the control channel 503 and the pull cap 504, and the first limiting structure comprises a first clamping groove 5031 and a second clamping groove 5032 arranged alternately on the control channel 503 and a first boss 5041 arranged on the pull cap 504, wherein the first boss 5041, the first clamping groove 5031 and the second clamping groove 5032 are adapted, when the first boss 5041 is located on the first clamping groove 5031, the ablation electrode 100 is in the initial state without stress, and when the first boss 5041 is located on the second clamping groove 5032, the ablation electrode 100 is in the expanded state and can continuously maintain this state. As a variant of the embodiment, the first clamping groove 5031 and the second clamping groove 5032 can also be arranged on the pull cap 504, and the first boss 5041 adapted thereto is arranged on the control channel 503, and the first clamping groove 5031 or the second clamping groove 5032 is controlled to be clamped with the first boss 5041 located on the control channel 503 by rotating the pull cap 504. It can be understood that the relative offset angle formed by the alternate arrangement of the first clamping groove 5031 and the second clamping groove 5032 is not limited by the present application.

[0055] In one embodiment, as shown in Figure 13 , the first clamping groove 5031 and the second clamping groove 5032 are arranged along the axis direction of the control channel 503, and a preset height difference 5033 is arranged between the first clamping groove 5031 and the second clamping groove 5032, wherein the preset height difference 5033 is equal to the distance by which the second end 103 of the ablation electrode 100 moves to the first end 102 of the ablation electrode 100. That is, when the first boss 5041 is located on the first clamping groove 5031, the ablation electrode is in the initial state without stress, and when the first boss 5041 is clamped on the second clamping groove 5032, the ablation electrode 100 is in the 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, so as to avoid the situation that the pull cap 504 moves and the ablation electrode 100 is still in the initial state, thereby enabling the operator to quickly determine the state of the ablation electrode 100 by the position of the first boss 5041.

[0056] In one embodiment, the ablation device further comprises a cable assembly 600 disposed at one end of the energy channel 502, the cable assembly 600 comprising a plug 601 and a needle core 602 disposed on the plug 601, the plug 601 being partially inserted into the energy channel 502 so that the needle core 602 can abut against the needle tube 301 and achieve electrical communication, so that the external energy generator can deliver ablation energy to the ablation electrode 100 through the needle core 602 and the needle tube 301.

[0057] Further, in order to facilitate the insertion between the push rod 500 and the cable assembly 600, an insertion rod 603 is provided on the plug 601, which is adapted to the outer shape of the energy channel 502. The insertion rod 603 is a conical structure with a preset taper, and the energy channel 502 is also a corresponding conical structure, so that the insertion rod 603 is inserted into the energy channel 502, and the rotation angle of the insertion rod 603 can be adjusted, so that the needle core 602 located on the plug 601 can better combine with the needle tube 301 in the push rod 500, and the good conduction performance is ensured. Further, in order to ensure the sealing performance of the combination of the energy channel 502 and the cable assembly 600, the taper of the insertion rod 603 and the taper of the energy channel 502 should meet the requirements of GB / 1962.1.

[0058] Alternatively, the insertion rod 603 can be a cylindrical structure, as long as it can rotate in the energy channel 502; alternatively, if the sealing performance between the two is not considered, the conical ratio of the insertion rod 603 can also be other ratio values.

[0059] In one embodiment, in order to avoid the plug 601 of the cable assembly 600 and the energy channel 502 of the push rod 500 being separated or the needle core 602 and the needle tube 301 being poorly contacted during operation, a screw joint 604 is provided on the insertion rod 603, the screw joint 604 is provided with a first internal thread 6041, and the outer wall of the energy channel 502 is provided with a matched first external thread 5021, and through the cooperation of the first external thread 5021 and the first internal thread 6041, the plug 601 can be detachably disposed on the energy channel 502 of the push rod 500 through the screw joint 604.

[0060] Further, since the cable assembly 600 and the push rod 500 are connected by thread cooperation, when the two are disassembled or connected, the screw joint 604 is movably disposed on the insertion rod 603, and the screw joint 604 only rotates around the axis of the insertion rod 603, and does not move in the axial direction of the insertion rod 603. Specifically, as shown in Figure 9 - Figure 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. Figure 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, thereby limiting the axial position of the rotary joint 604. 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 the 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. Figure 10 As shown, the first guide surface is an inclined surface structure, and optionally, it can also be an arc surface structure. Further, the rotary joint 604 is further limited in the axial direction, as shown in FIG. Figure 9 and Figure 11 As shown, the first distance 6042 between the surface where the annular clamping boss 6042 abuts against the annular limiting boss 6031 and the first end of the non-threaded structure of the rotary joint 604 is slightly smaller than or equal to the second distance 6032 between the annular limiting boss 6031 and one end of the plug-in rod 603, so as to form a clearance fit, so that the rotary joint 604 can rotate smoothly around the plug-in rod 603.

[0061] In one embodiment, the ablation claws 101 of the ablation electrode 100 are elastically deformable in the expanded state. When the external force is removed, the ablation claws 101 of the ablation electrode 100 return to their initial state. By configuring the ablation claws 101 with an elastic material, such as stainless steel or nickel-titanium shape memory alloy, the elastic deformation allows them to return to their initial state without external force. This allows the ablation electrode 100 to be reused 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 outer sheath 401 sends the ablation electrode 100, 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 position of the end of the outer sheath 401 provided with the developing device can be displayed, 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 Figure 12As shown, by bending one end of the needle core 602 to form a bending 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. Alternatively, the needle core 602 can not be bent, and the contact length of the needle core 602 and the needle tube 301 needs to be longer than the length of the needle core 602 when it is bent, so as to achieve a longer effective contact length and realize effective transmission of the ablation energy.

[0064] The above merely describes the preferred embodiments of the present application, and it should be noted that those skilled in the art can make several improvements and refinements without departing from the principles of the present application. These improvements and refinements should also be considered within the protection scope of the present application.

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 disposed at one end of the insulating sleeve, the ablation electrode being a hollow structure, and having a plurality of ablation claws, wherein the ablation claws can expand outward from 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; and a puncture needle having a needle tip, the puncture needle being disposed at the second end of the ablation electrode; applying an external force to the ablation electrode so as to bring the second end of the ablation electrode and the first end of the ablation electrode closer to each other, so that the ablation claw of the ablation electrode is transformed from an initial state without force to an expanded state after force is applied and maintained; A traction wire is movably arranged in the insulating sleeve, and one end of the traction wire is connected to the puncture needle; an outer sheath, movably sleeved on the outside of the insulating sheath, the outer sheath having a third through-channel, the insulating sheath being capable of axially moving relative to the outer sheath, and the ablation electrode and puncture needle being capable of being placed in the third channel of the outer sheath; A handle comprising a grip and a push rod, wherein one end of the outer sheath is connected to the grip, and one end of the insulating sleeve is connected to the push rod, and the push rod is axially movable relative to the grip; wherein a Y-shaped channel is provided at one end of the push rod away from the outer sheath, and the Y-shaped channel comprises a control channel and an energy channel, one end of the traction wire passes through the control channel and is movably provided at one end of the control channel, and the energy channel is used to connect the ablation electrode with an external energy generator; The handle is provided with a fourth channel, the fourth channel being 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; The handle is provided with a first threaded hole, and 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.

2. The ablation device with cutting function according to claim 1, characterized in that: It also includes a needle tube fixedly arranged in the first channel of the insulating sleeve, 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 connected to the energy channel for transmitting external 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, the traction wire is passed through the second channel, and the traction wire can move axially relative to the needle tube.

4. The ablation device with cutting function according to claim 1, 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.

5. The ablation device with cutting function according to claim 4, 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, the first boss is adapted to the first card slot and the second card slot, when the first boss is located on the first card slot, the ablation electrode is in an unstressed state, 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.

6. The ablation device with cutting function according to claim 5, 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.

7. The ablation device with cutting function according to claim 2, 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 and connects with the needle tube.

8. The ablation device with cutting function according to claim 7, 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 is adapted to the energy channel.

9. The ablation device with cutting function according to claim 8, characterized in that: The plug 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.

10. The ablation device with cutting function according to claim 9, 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.

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

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

13. The ablation device with cutting function according to claim 7, characterized in that: A pre-bending structure is provided on a side of the needle core away from the plug.

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