Radio frequency ablation electrode

Abstract

The invention discloses a radiofrequency ablation electrode, and relates to the technical field of medical instruments, the radiofrequency ablation electrode comprises a working end, the working end comprises a main working electrode and an auxiliary working electrode which are coaxially arranged, the main working electrode and the auxiliary working electrode are separated by an insulating device which is coaxially arranged, and the axial distance between the main working electrode and the auxiliary working electrode can be adjusted; two electrodes of the radio frequency generation source are respectively connected with the main working electrode and the auxiliary working electrode through radio frequency leads; the cooling system can introduce a circulating refrigerant medium into the inner channels of the main working electrode and the auxiliary working electrode; the micro-permeation structure comprises permeation openings formed in the side wall of the main working electrode and the side wall of the auxiliary working electrode respectively, the permeation opening in the main working electrode is communicated with the inner channel, the permeation opening in the auxiliary working electrode is communicated with the permeation channel of the auxiliary working electrode, and part of refrigerant media flowing back by the cooling system can enter the permeation channel. The main working electrode and the auxiliary working electrode are each provided with an independent micro-permeation structure, and in the ablation process, the problems that tissue carbonization is serious, and the ablation range is limited can be solved.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a radio frequency ablation electrode. Background Art

[0002] With the gradual maturity of various ablation techniques, minimally invasive ablation techniques such as microwave ablation, radiofrequency ablation and cryoablation have achieved good clinical feedback in the treatment of diseases such as gastrointestinal tumors, solid tumors of the liver, lung, kidney, prostate hyperplasia, benign thyroid nodules, etc.

[0003] Radiofrequency ablation technology is widely used in situations where precise ablation is required due to its safety and controllability. According to the working end structure, radiofrequency ablation electrode consumables can be divided into monopolar electrodes and bipolar electrodes. The monopolar electrode needs to be combined with a neutral electrode sheet to form a current loop. The neutral electrode sheet needs to be attached to the patient's muscles and blood-rich areas before surgery. However, for patients wearing pacemakers and those with metal implants in their bodies, the radiofrequency current loop will generate heat through metal objects and damage normal tissues. The pacemaker may stop working under the interference of high-frequency current, causing the patient's death.

[0004] The radio frequency bipolar electrode can solve the above problems. The main working pole and the auxiliary working pole of the radio frequency bipolar electrode are at the two ends of the total working end, and the radio frequency current flows between the two poles. There is no need to stick a neutral electrode sheet, which saves the tedious operation process. For patients with metal implants in their bodies, this design avoids the heat generated by the radio frequency current loop through the metal object and reduces damage to normal tissues. If the patient wears a pacemaker, the radio frequency bipolar electrode can also prevent the high-frequency current from interfering with the normal operation of the pacemaker, reducing the risk of causing adverse reactions.

[0005] However, conventional radiofrequency bipolar electrodes only have a simple cold circulation structure, and both the main working electrode and the auxiliary working electrode have no micro-permeability structure. During the ablation process, tissue carbonization is severe and the ablation range is limited.

[0006] Therefore, in view of the above problems, it is urgent to provide a new radiofrequency ablation electrode to solve the above problems existing in the prior art. Summary of the invention

[0007] The purpose of the present invention is to provide a radiofrequency ablation electrode to solve the problems existing in the above-mentioned prior art. Both the main working electrode and the auxiliary working electrode have a micro-permeable structure. During the ablation process, the problems of severe tissue carbonization and limited ablation range can be avoided. The axial distance between the main working electrode and the auxiliary working electrode can be adjusted, so that the total working end length can be changed to achieve a change in the ablation range. It is suitable for the ablation of multiple lesions of different sizes. The total working end length includes the main working electrode length plus the spacing length between the main working electrode and the auxiliary working electrode plus the auxiliary working electrode length. During the change of the total working end length, the length of the main working electrode and the auxiliary working electrode can be kept unchanged, thereby maintaining the balance of energy density on the main working electrode and the auxiliary working electrode, and maintaining the balance of the ablation range. The phenomenon of less ablation range at the front and more at the back, or more at the front and less at the back will not occur.

[0008] To achieve the above object, the present invention provides the following solutions:

[0009] The present invention provides a radiofrequency ablation electrode, comprising:

[0010] A working end, wherein the working end comprises a coaxially arranged main working pole and an auxiliary working pole, wherein the main working pole and the auxiliary working pole are separated by a coaxially arranged insulating device, wherein the insulating device of the present invention is a polymer plastic tube, and the axial distance between the main working pole and the auxiliary working pole can be adjusted;

[0011] A radio frequency generating source, the two electrodes of which are respectively connected to the main working electrode and the auxiliary working electrode through radio frequency wires;

[0012] The cooling system can respectively introduce circulating cold medium into the inner channels of the main working electrode and the auxiliary working electrode. The cold medium can be physiological saline, so as to cool the main working electrode, the polymer plastic tube, the auxiliary working electrode and the adjacent tissues; it can prevent the working end from adhering to the tissue, expand the ablation range, and reduce the degree of carbonization of the lesion.

[0013] The micro-permeable structure comprises permeable openings respectively opened on the side walls of the main working pole and the side walls of the auxiliary working pole, the permeable opening on the main working pole is connected to the inner channel, the permeable opening on the auxiliary working pole is connected to the permeable channel of the auxiliary working pole, part of the refrigerant medium refluxed by the cooling system can enter the permeable channel, the permeable opening and the permeable channel of the auxiliary working pole will move in real time with the forward and backward movement of the auxiliary working pole, and the permeable opening is always evenly maintained on the auxiliary working pole; the physiological saline that seeps out in small amounts from the micro-permeable structure can infiltrate the tissues around the working end, further avoiding tissue adhesion, facilitating mobile ablation of the thyroid gland, avoiding tissue carbonization, and facilitating postoperative recovery; at the same time, the physiological saline that seeps out in small amounts can enhance the electrical conductivity of the tissue, reduce the working impedance, facilitate the continuous injection of radio frequency energy, further expand the ablation range, facilitate the ablation of larger lesions of prostatic hyperplasia and larger lesions of myocardial hypertrophy, improve the ablation efficiency, and achieve complete ablation at one time.

[0014] Optionally, the main working electrode is fixed and the auxiliary working electrode can move axially; the permeation port and permeation channel of the auxiliary working electrode will move in real time with the axial movement of the auxiliary working electrode, and the permeation port of the auxiliary working electrode is always evenly maintained on the auxiliary working electrode.

[0015] Optionally, the main working electrode and the auxiliary working electrode can simultaneously realize radiofrequency ablation and steam ablation. The trace amount of exuded physiological saline is converted into water vapor under the action of radiofrequency current, and the water vapor can be used as an auxiliary ablation medium to simultaneously realize radiofrequency ablation and steam ablation of the main working electrode, and radiofrequency ablation and steam ablation of the auxiliary working electrode, thereby expanding the ablation range and enhancing the ablation effect.

[0016] Optionally, it also includes an inner needle tube, a first outer needle tube, and a second outer needle tube; a needle tip is fixedly provided at one end of the first outer needle tube, and the end surface diameter of the needle tip connected to the first outer needle tube is larger than the outer diameter of the first outer needle tube; the main working electrode is sleeved on the first outer needle tube, and one end thereof abuts against the end surface of the needle tip, and the other end is sealed and connected to a first connecting portion sleeved on the first outer needle tube; the first connecting portion is sequentially sleeved with the insulating device and the second outer needle tube; the second outer needle tube is fixedly sleeved with the auxiliary working electrode at the port close to the insulating device, and the insulating device, that is, the polymer plastic tube has a minimum length of 0.6 to 1.0 mm and is fixed on the first insulating device. On the tube, the front end is close to the rear end of the main working electrode. The outer diameter of the polymer plastic tube is larger than the inner diameter of the second outer needle tube, and the inner diameter is smaller than the outer diameter of the second outer needle tube. It can play a blocking role on the front end surface of the second outer needle tube, and can avoid the auxiliary working electrode from contacting the two poles and causing a short circuit during the sliding back and forth of the auxiliary working electrode relative to the main working electrode; the tail end of the second outer needle tube is slidably penetrated into a sealed cavity tube, and the sealed cavity tube can be connected to the cooling system; the inner channel is formed between the inner needle tube and the first outer needle tube, and the penetration channel of the auxiliary working electrode is formed between the inner wall of the second outer needle tube and the first connecting part; the radio frequency wires of the radio frequency generator are respectively connected to the first outer needle tube and the second outer needle tube.

[0017] Optionally, the end of the auxiliary working pole away from the insulating device is sealed with a second connecting part sleeved on the second outer needle tube; the tail end surface of the second connecting part is fixedly sleeved with an adjusting block, and the adjusting block can drive the second connecting part, the second outer needle tube and the auxiliary working pole to move axially synchronously, and during the movement, the tail end of the second outer needle tube is always in the sealing cavity tube.

[0018] Optionally, the first connecting portion is a first insulating tube disposed on the first outer needle tube, and the second connecting portion is a second insulating tube disposed on the second outer needle tube.

[0019] Optionally, the sealed cavity tube includes a circular sleeve with a sealed tail end, and the front end of the circular sleeve is sealed and connected to a flexible plastic sealing block; the second outer needle tube seal slides through the flexible plastic sealing block and extends into the circular sleeve; when the second outer needle tube slides, the tail end of the second outer needle tube does not exceed the flexible plastic sealing block, and the second insulating tube on the second outer needle tube never enters the flexible plastic sealing block.

[0020] Optionally, the penetration port of the main working pole includes a plurality of circles of square holes opened along the axial direction of the main working pole, and a plurality of circles of micropores arranged along the axial direction are opened on the side wall on which the first outer needle tube is sleeved with the main working pole, and the micropores and the square holes are arranged alternately. After the cold medium flows out from the micropores, it can enter the gap between the first outer needle tube and the main working pole, and flow out from the square holes, thereby realizing micro-penetration of the tissue surrounding the main working pole; the penetration port of the auxiliary working pole includes a plurality of circles of injection holes opened along the axial direction of the auxiliary working pole, and one end of the injection hole passes through the side wall of the second outer needle tube and is connected to the interior of the second outer needle tube; in another preferred embodiment, the end of the second outer needle tube is fixedly and sealedly connected to one end of the auxiliary working pole, so that the interior of the second outer needle tube is connected to the interior of the auxiliary working pole, and the injection hole passes through the side wall of the auxiliary working pole, so as to realize the function of connecting the injection hole with the penetration channel of the auxiliary working pole.

[0021] Optionally, the cooling system includes a return water chamber, a water inlet chamber, a water inlet pipe and a return water pipe, the inner cavity of the inner needle tube forms the water inlet pipe, the inner channel between the outer wall of the inner needle tube and the inner wall of the first outer needle tube forms the return water pipe, and the front end of the water inlet pipe is connected with the front end of the return water pipe; a partition device is provided between the water inlet chamber and the return water chamber, and the rear end of the inner needle tube passes through the return water chamber and the partition device and is connected with the water inlet chamber; the rear end of the first outer needle tube is penetrated into the return water chamber; the return water chamber can be connected with the sealing chamber tube through a reflux pipe; the return water chamber and the water inlet chamber are respectively connected with liquid supply devices.

[0022] Optionally, the liquid supply device includes a refrigerant medium source and a refrigerant medium recovery device, wherein the refrigerant medium source can provide the refrigerant and allow the refrigerant to flow into the water chamber through a water inlet pipe, and the refrigerant medium recovery device can recover the refrigerant, and the refrigerant flows from the return water chamber through a return water pipe into the refrigerant medium recovery device.

[0023] Optionally, the injection hole expands successively from the proximal end to the distal end, and the injection hole size range at the proximal end is 0.1-0.4 mm, and the injection hole size range at the distal end is 0.5-1 mm; to ensure that the micro-permeability structure along the entire length of the auxiliary working electrode can evenly permeate the liquid, and because the liquid flowing to the injection hole on the auxiliary working electrode and the front port of the second outer needle tube has first passed through the return water chamber and the gap space between the inner wall of the second outer needle tube and the outer wall of the first insulating tube for pressure relief, the liquid will not be sprayed out from the injection hole and the front port of the second outer needle tube on the auxiliary working electrode, but will seep out slowly without the need for adding a sleeve to relieve pressure.

[0024] Optionally, a multi-channel valve is fixedly connected to the side wall of the sealed cavity tube, which is an N-channel valve, including an output port and N-1 input ports. The valve can be controlled to achieve switching of independent connection between different input ports and output ports. Only one input port can be connected to the output port at a time, and other input ports are not connected to the input and output ports. The output port of the multi-channel valve is connected to the inside of the sealed cavity tube, one of the input ports of the multi-channel valve is connected to the reflux pipe, and the remaining input ports of the multi-channel valve are provided with Luer female connectors. The multi-channel valve can be switched to make its output port independently connected to any input port.

[0025] Taking two input ports as an example, the second input port of the multi-channel valve is always connected to the tail end of the reflux pipe. When the valve of the multi-channel valve is switched to the second input port, the second input port is connected to the output port, and the first input port is not connected to the second input port and the output port. A small part of the reflux water at the tail end of the reflux pipe will flow to the output port through the second input port, flow to the micro-osmosis channel of the auxiliary working pole through the output port, and flow out from the injection hole, thereby realizing micro-permeation of the surrounding tissues of the auxiliary working pole.

[0026] The first input port is a standard Luer female connector port, which is in a suspended state when not in use. When the valve of the multi-channel valve is switched to the first input port, the first input port is connected to the output port, and the second input port is not connected to the first input port and the output port. At this time, the Luer male connector of the output port of the syringe can be connected to the Luer female connector of the first input port of the multi-channel valve to realize the injection of external drugs into the tissue through the micro-permeation structure of the auxiliary working pole. At the same time, the liquid in the lesion tissue can also be sucked through the micro-permeation channel on the auxiliary working pole.

[0027] Optionally, the length of the main working pole is different from that of the auxiliary working pole, and the maximum range of the adjustable axial distance between the main working pole and the auxiliary working pole is the length of the shorter one of the main working pole and the auxiliary working pole.

[0028] Optionally, the length of the main working pole is the same as that of the auxiliary working pole, and the maximum range of the adjustable axial distance between the main working pole and the auxiliary working pole is the length of the main working pole or the length of the auxiliary working pole.

[0029] Optionally, the RF wire includes a first RF wire and a second RF wire, the front end of the first RF wire is connected to the main working pole, the front end of the second RF wire is connected to the auxiliary working pole, the tail end of the first RF wire is connected to the first RF plug, and the tail end of the second RF wire is connected to the second RF plug; the first RF plug and the second RF plug are respectively connected to the two poles of the RF source; the RF current is conducted between the main working pole and the auxiliary working pole to ablate the tissue, the RF current is conducted between the two poles and does not flow to tissues outside the lesion. During ablation, there is no need to stick a neutral electrode sheet.

[0030] Optionally, a conduction switch is provided between the first RF wire and the second RF wire to realize the conversion from bipolar to monopolar. When the conduction switch is turned on, the first RF wire and the second RF wire are electrically connected. At this time, the main working pole and the auxiliary working pole are converted into monopolar electrodes, that is, the RF ablation electrode is a monopolar electrode, and a neutral electrode sheet needs to be attached during ablation, and the ablation range is larger. When the conduction switch is disconnected, the first RF wire and the second RF wire are not connected. At this time, the main working pole and the auxiliary working pole are converted into bipolar electrodes, that is, the RF ablation electrode is a bipolar electrode, and a neutral electrode sheet does not need to be attached during ablation, and the ablation range is large and precisely controllable.

[0031] Compared with the prior art, the present invention has achieved the following technical effects:

[0032] The working end of the present invention is a bipolar composite structure of a main working pole and an auxiliary working pole, and a radio frequency current self-circuit is formed between the main working pole and the auxiliary working pole. No neutral electrode sheet is required during ablation, which not only maintains the precise and controllable advantages of radio frequency ablation, but is also particularly suitable for patients with metal or pacemakers in their bodies who have relatively high requirements for ablation accuracy and a relatively large ablation range. The cooling system can prevent the working end from adhering to tissues, expand the ablation range, and reduce the degree of carbonization of lesions. The external micro-permeable structure of the main working pole and the external micro-permeable structure of the auxiliary working pole, a small amount of exuded physiological saline can infiltrate the surrounding tissues of the working end, further avoiding tissue adhesion, facilitating mobile ablation of the thyroid gland, avoiding tissue carbonization, and facilitating postoperative recovery. The infiltration channel and infiltration port of the auxiliary working pole of the present invention can be connected through a reflux tube. Part of the refrigerant medium that enters the return water cavity realizes the self-circulation of the refrigerant medium in the infiltration channel and the infiltration port of the auxiliary working electrode. No external pump or syringe or other structures are required. The refrigerant medium that flows back through the cooling system can realize micro-perfusion of liquid in the infiltration channel and the infiltration port of the auxiliary working electrode. At the same time, the trace amount of seeped physiological saline can enhance the electrical conductivity of the tissue, reduce the working impedance, and facilitate the continuous injection of radio frequency energy, further expand the ablation range, facilitate the ablation of larger lesions of prostate hyperplasia and larger lesions of myocardial hypertrophy, improve the ablation efficiency, and achieve complete ablation at one time. During the ablation process, both the main working electrode and the auxiliary working electrode can produce radio frequency ablation and water vapor ablation, and radio frequency resistance heat and water vapor heat conduction act on the tissue at the same time, which improves the ablation efficiency and expands the ablation range. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments will be briefly introduced below. 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 creative work.

[0034] Figure 1 It is a schematic diagram of the overall structure of a radiofrequency ablation electrode in an embodiment of the present invention;

[0035] Figure 2 Schematic diagram of the assembly process of the main working pole in an embodiment of the present invention;

[0036] Figure 3 This is a schematic diagram of the assembly of the inner needle tube in an embodiment of the present invention;

[0037] Figure 4 This is a schematic diagram of assembling a polymer plastic tube and a first insulating tube in an embodiment of the present invention;

[0038] Figure 5 Schematic diagram of the assembly process of the auxiliary working electrode in an embodiment of the present invention;

[0039] Figure 6 Schematic diagram of the micro-permeability structure of the auxiliary working electrode in an embodiment of the present invention;

[0040] Figure 7 Schematic diagram of the minimum adjustment range between the main working pole and the auxiliary working pole in an embodiment of the present invention;

[0041] Figure 8 Schematic diagram of the real-time adjustment range between the main working pole and the auxiliary working pole in an embodiment of the present invention;

[0042] Fig. 9 It is a schematic diagram of realizing the secondary working micro-permeation function through the second input port in an embodiment of the present invention;

[0043] Fig.10 It is a schematic diagram of realizing the injection function of the auxiliary working pole through the first output port in an embodiment of the present invention;

[0044] Fig.11 It is a schematic diagram of realizing the liquid suction function of the auxiliary working electrode through the first output port in an embodiment of the present invention;

[0045] Fig.12 Schematic diagram of the wiring of the conduction switch in an embodiment of the present invention.

[0046] Explanation of reference numerals: 1. needle tip; 2. main working electrode; 201. sleeve; 202. square hole; 3. polymer plastic tube; 4. secondary working electrode; 401. injection hole; 402. exposed tube; 5. second insulating tube; 6. second outer needle tube; 7. gap cavity; 8. first insulating tube; 9. first outer needle tube; 901. micropore; 10. inner needle tube; 11. adjustment block; 12. handle; 13. flexible plastic sealing block; 14. round sleeve; 15. multi-channel valve; 151. first input port; 152. control valve; 153. second input port; 154. output port; 16. return pipe; 17. return water chamber; 18. water inlet chamber; 19. first RF wire; 20. first welding point; 21. second RF wire; 22. second welding point; 23. RF wire; 24. conduction switch; 25. first RF plug; 26. second RF plug; 27. water inlet pipe; 28. return water pipe; 29. ​​syringe. DETAILED DESCRIPTION

[0047] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. 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 creative work are within the scope of protection of the present invention.

[0048] The purpose of the present invention is to provide a radiofrequency ablation electrode to solve the problems existing in the above-mentioned prior art. Both the main working electrode and the auxiliary working electrode have a micro-permeable structure. During the ablation process, the problems of severe tissue carbonization and limited ablation range can be avoided. The axial distance between the main working electrode and the auxiliary working electrode can be adjusted, so that the total working end length can be changed to achieve a change in the ablation range. It is suitable for the ablation of multiple lesions of different sizes. The total working end length includes the main working electrode length plus the spacing length between the main working electrode and the auxiliary working electrode plus the auxiliary working electrode length. During the change of the total working end length, the length of the main working electrode and the auxiliary working electrode can be kept unchanged, thereby maintaining the balance of energy density on the main working electrode and the auxiliary working electrode, and maintaining the balance of the ablation range. The phenomenon of less ablation range at the front and more at the back, or more at the front and less at the back will not occur.

[0049] 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.

[0050] The radio frequency bipolar electrode known to the inventor has only a simple cold circulation structure, the main working pole has no micro-permeability structure, and the auxiliary working pole has no micro-permeability structure. During the ablation process, the tissue is severely carbonized and the ablation range is limited. There is no injection channel, and it is impossible to combine drugs for treatment. For lesions with relatively large prostatic hyperplasia or relatively large myocardial hypertrophy, a single ablation cannot be completely ablated, and the ablation efficiency is low. Steam ablation is often used in clinical ablation treatment of prostatic hyperplasia. Steam ablation uses a steam generator to generate high-temperature water vapor, and then injects the water vapor into the lesion tissue to produce thermal damage through heat conduction. In order to avoid damaging the normal physiological function of the prostate, steam ablation often requires repeated multi-point ablation to complete the treatment, and the ablation efficiency is also low.

[0051] For the treatment of large lesions, cold circulation single needle electrodes or perfusion single needle electrodes are often used. For example, an adjustable water-injection ablation electrode needle known to the inventor only has a perfusion structure, but no cold circulation structure. The cold medium (physiological saline) flows out of the liquid storage tank and is directly injected into the lesion tissue through a plurality of micropores provided on the outer needle tube, and no cold medium flows back to the liquid storage tank. The physiological saline penetrates into the tissue, changes the impedance of the lesion tissue, and makes the radiofrequency ablation range larger. At the same time, the structure has the following disadvantages: there is no cold circulation structure, the cold medium is only perfused, not refluxed, and the heat of the working end and its surrounding tissues cannot be taken away in time, resulting in tissue adhesion to the working end, thereby causing the micropores on the working end to be blocked. When the flow rate of the cold medium remains unchanged, the blocked hole causes the liquid in the needle tube to flow out from other micropores, and the amount of liquid flowing out of the micropores increases, which may spread in a jet-like manner to the surroundings, resulting in irregular ablation shapes, affecting the safety of ablation.

[0052] In order to solve the problems encountered in the above-mentioned technology, the present invention provides a radiofrequency ablation electrode, such as Figure 1 to Figure 5As shown, it includes a working end, a radio frequency source, a cooling system and a micro-permeation structure. The working end of this embodiment includes a coaxially arranged main working pole 2 and an auxiliary working pole 4. The main working pole 2 and the auxiliary working pole 4 are separated by a coaxially arranged polymer plastic tube 3, and the axial distance between the main working pole 2 and the auxiliary working pole 4 can be adjusted; the two poles of the radio frequency source are respectively connected to the main working pole 2 and the auxiliary working pole 4 through a radio frequency wire; the cooling system can introduce a circulating refrigerant medium into the inner channels of the main working pole 2 and the auxiliary working pole 4 to achieve cooling of the main working pole 2, the polymer plastic tube 3, the auxiliary working pole 4 and adjacent tissues; it can prevent the working end from adhering to tissues, expand the ablation range, and reduce the degree of carbonization of the lesion.

[0053] In one embodiment, the micro-permeable structure includes permeable ports respectively opened on the side walls of the main working pole 2 and the side walls of the auxiliary working pole 4. The permeable port on the main working pole 2 is connected to the inner channel, and the permeable port on the auxiliary working pole 4 is connected to the permeable channel of the auxiliary working pole 4. The permeable port and the permeable channel of the auxiliary working pole 4 will move in real time with the forward and backward movement of the auxiliary working pole 4, and the permeable port is always evenly maintained on the auxiliary working pole 4; the physiological saline that seeps out in small amounts from the micro-permeable structure can infiltrate the tissues around the working end, further avoiding tissue adhesion, facilitating mobile ablation of the thyroid gland, avoiding tissue carbonization, and facilitating postoperative recovery; at the same time, the physiological saline that seeps out in small amounts can enhance the conductivity of the tissue, reduce the working impedance, facilitate the continuous injection of radio frequency energy, further expand the ablation range, facilitate the ablation of larger lesions of prostatic hyperplasia and larger lesions of myocardial hypertrophy, improve the ablation efficiency, and achieve complete ablation at one time.

[0054] In a preferred embodiment, in order to realize the functions of the working end, the cooling system and the micro-permeation structure, the present embodiment designs structures such as an inner needle tube 10, a first outer needle tube 9, and a second outer needle tube 6. The first outer needle tube 9 is sleeved on the inner needle tube 10, and the main working pole 2 is located at the end of the first outer needle tube 9 close to the needle tip. The main working pole 2 of the present embodiment includes a sleeve 201, and the sleeve 201 is installed on the first outer needle tube 9 close to the needle tip. A first welding point 20 is provided on the side wall of the end of the first outer needle tube 9 away from the needle tip. The first welding point is connected to the radio frequency source through a radio frequency wire, and the inner needle tube 10 is extended into the first outer needle tube 9. The front end of the inner needle tube 10 is extended into the front end of the needle tip. A layer of first insulating tube 8 is provided on the surface of the first outer needle tube 9 behind the main working pole 2. The first insulating tube 8 of the present embodiment is a heat shrink tube with a thin-walled structure. A small section of polymer plastic tube 3 is sleeved on the front end surface of the first insulating tube 8. The rear end of the first insulating tube 8 is close to the first welding point 20. The polymer plastic tube 3 is The end is close to the tail end of the main working electrode 2, and a second outer needle tube 6 is sleeved on the rear of the polymer plastic tube 3. The second outer needle tube 6 is sleeved on the surface of the first insulating tube 8. The inner wall of the second outer needle tube 6 is close to the first insulating tube 8. The front end of the second outer needle tube 6 is close to the tail end of the polymer plastic tube 3. The auxiliary working electrode 4 is located at one end of the second outer needle tube 6 close to the tail end of the polymer plastic tube 3. A second insulating tube 5 is provided on the second outer needle tube 6 at the rear end of the auxiliary working electrode 4. The second insulating tube 5 of this embodiment also adopts a heat shrink tube with a thin-walled structure; a second welding point 22 is provided on the side wall of the second outer needle tube 6, and the second welding point 22 is connected to the radio frequency source through a corresponding radio frequency wire; the tail end of the second outer needle tube 6 is slidably penetrated into a sealed cavity tube, and the sealed cavity tube can be connected to the cooling system; the gap cavity 7 between the inner needle tube 10 and the first outer needle tube 9 forms a common inner channel for the main working electrode 2 and the auxiliary working electrode 4, and a penetration channel for the auxiliary working electrode 4 is formed between the inner wall of the second outer needle tube 6 and the first insulating tube 8.

[0055] In the present embodiment, it is also necessary to explain that the needle tip 1 is welded to the front end of the first outer needle tube 9, the diameter of the tail end of the needle tip 1 is larger than the diameter of the first outer needle tube 9, and the diameter of the tail end of the needle tip 1 is the same as the outer diameter of the sleeve 201, which is convenient for puncture; the first outer needle tube 9 and the second outer needle tube 6 are both made of metal, which is convenient for conductivity, and the polymer plastic tube 3 is made of silicone, which is an insulator, isolating current and preventing short circuit; the front end of the inner needle tube 10 extends into the needle tip 1, so that the cold medium can reach the needle tip 1 and reduce the carbonization of the tissue at the needle tip 1.

[0056] like Figure 6 , Figure 7 and Figure 8As shown, in this embodiment, the auxiliary working pole 4 also includes an adjustment structure, and the adjustment block 11 of the adjustment structure is fixed on the second insulating tube 5. The rear end surface of the second insulating tube 5 is flush with the rear end surface of the adjustment block 11. The sealing cavity tube of this embodiment includes a circular sleeve 14 with one end closed and the other end sealed and connected to a flexible plastic sealing block 13. The second outer needle tube 6 passes through the flexible plastic sealing block 13 and extends into the circular sleeve 14. The rear end of the circular sleeve 14 is sealed. When the adjustment block 11 slides, it drives the second outer needle tube 6, the auxiliary working pole 4 and the second insulating tube 5 on the second outer needle tube 6 to move forward and backward. The rear end of the second outer needle tube 6 is always in the circular sleeve 14, so that the auxiliary working pole 4 on the second outer needle tube 6 and the injection hole 401 on the auxiliary working pole 4 move forward and backward, and the distance between them relative to the main working pole 2 changes. The micro-permeability structure on the auxiliary working electrode 4 can be adjusted forward and backward. As the auxiliary working electrode 4 moves forward and backward, the micro-permeability liquid on the auxiliary working electrode 4 can always remain uniform, and the ablation range is always evenly maintained on the auxiliary working electrode, thereby expanding the ablation range and making the ablation range more regular; the liquid outlet of the micro-permeability structure on the auxiliary working electrode 4 is the injection hole 401, which is located on the exposed tube 402 of the auxiliary working electrode, thereby improving the conductivity of the adjacent tissue, expanding the ablation range, and ensuring the uniformity and regularity of the ablation range.

[0057] In the present embodiment, it is also necessary to explain that the outer diameter of the polymer plastic tube 3 is larger than the inner diameter of the second outer needle tube 6, and the inner diameter of the polymer plastic tube 3 is smaller than the outer diameter of the second outer needle tube 6, which can block the front end surface of the second outer needle tube 6, and can prevent the auxiliary working electrode 4 from sliding back and forth relative to the main working electrode 2, causing the two electrodes to contact and cause a short circuit; during the adjustment process, the adjustment range is limited, and the minimum range is not less than the length of the polymer plastic tube 3 to prevent the two electrodes from being too close and causing a short circuit, and the maximum range is the length of the shorter one of the main working electrode 2 and the auxiliary working electrode 4 to prevent the two electrodes from being too far apart and causing an irregular ablation range, such as Figure 7 and Figure 8As shown, in the figure, X is the distance that the auxiliary working electrode 4 can move axially, L is the length of the polymer plastic tube 3, the maximum length of L+X is the length of the shorter electrode between the main working electrode 2 and the auxiliary working electrode 4, and the minimum length of L+X is the length of the polymer plastic tube 3. The distance between the main working pole 2 and the auxiliary working pole 4 is adjustable, and the total working end length can be changed to achieve a change in the ablation range. The total working end length includes the length of the main working pole 2 plus the distance between the main working pole and the auxiliary working pole 4 plus the length of the auxiliary working pole 4: the present invention can achieve a change in the ablation range by changing the length of the total working end, and is suitable for ablation of multiple lesions of different sizes. The change in the total working end length is achieved by changing the distance between the main working pole 2 and the auxiliary working pole 4, rather than changing the length of the main working pole 2 or the length of the auxiliary working pole. In the process of adjusting the total working end length, the present invention can keep the length of the main working pole 2 and the auxiliary working pole 4 unchanged, thereby maintaining the balance of the energy density on the main working pole 2 and the auxiliary working pole 4, and maintaining the balance of the ablation range, and there will be no phenomenon that the ablation range is less at the front and more at the back, or more at the front and less at the back. Therefore, the present invention can not only achieve bipolar radiofrequency ablation, but also achieve the adjustable ablation range, improve the accuracy of ablation, and achieve the balance of the ablation range.

[0058] In this embodiment, if Figure 1 As shown, the liquid supply device includes a refrigerant medium source and a refrigerant medium recovery device. The refrigerant medium source can provide refrigerant medium, and the refrigerant medium flows into the water chamber 18 through the water inlet pipe 27. The refrigerant medium recovery device can recover the refrigerant medium, and the refrigerant medium flows from the return water chamber 17 through the return water pipe 28 into the refrigerant medium recovery device; the water inlet chamber 18 and the return water chamber 17 are both located in the handle 12, the water inlet chamber 18 is located at the rear end of the first outer needle tube 9, the water inlet chamber 18 is connected with the water inlet pipe 27, and the return water chamber 17 is located at the rear end of the inner needle tube 10 and is connected with the return water pipe 28; the water inlet chamber 18 and the return water chamber 17 are separated by a partition device, and the rear end of the inner needle tube 10 passes through the return water chamber 17 and the partition device, and is connected with the water inlet chamber 18. The inner needle tube 10 and the partition device are sealed at the penetration position to avoid leakage; the rear end of the first outer needle tube 9 is penetrated in the return water chamber 17; the return water chamber 17 can be connected with the round sleeve 14 through the return pipe 16; in this embodiment, as Figure 1 to Figure 6As shown, the main working electrode 2 and the auxiliary working electrode 4 share a cooling system to achieve cooling of the main working electrode 2, the polymer plastic tube 3, the auxiliary working electrode 4 and the adjacent tissues; the cooling system includes a water inlet pipe and a water return pipe, the water inlet pipe is composed of an inner needle tube 10, and the water return pipe is composed of an annular channel between the outer wall of the inner needle tube 10 and the inner wall of the first outer needle tube 9, that is, the gap cavity 7, the front end of the water inlet pipe is connected with the front end of the water return pipe, and the liquid inlet port of the micro-permeation structure of the main working electrode 2 is connected with the front end of the water return pipe of the cooling system, and is located at the front end of the first outer needle tube 9. The refrigerant source can provide refrigerant, which flows into the water inlet chamber 18 through the water inlet pipe 27, enters the inner needle tube 10 through the water inlet chamber 18, flows to the end of the inner needle tube 10, enters the annular inner channel between the inner needle tube 10 and the first outer needle tube 9, and then flows back to the return water chamber 17. During this period, part of the refrigerant seeps out to the working position through the micro-permeation structure of the main working pole 2. The refrigerant recovery device can recover the refrigerant, and the refrigerant flows from the return water chamber 17 through the return water pipe 28 into the refrigerant recovery device.

[0059] In this embodiment, a multi-channel valve 15 is fixedly connected to the side wall of the circular sleeve 14, and the circular sleeve 14 is connected to the output port 154 of the multi-channel valve 15. One of the input ports of the multi-channel valve 15 is connected to the return pipe 16, and the other end of the return pipe 16 is connected to the return pipe 28, so that a part of the refrigerant medium refluxed from the return chamber 17 enters the circular sleeve 14 through the return pipe 16, and flows to the position of the auxiliary working pole 4 through the second outer needle tube 6, and then flows out to the working position through the outlet at the end of the second outer needle tube 6 and the injection hole 401 of the auxiliary working pole 4. Only one input port can be connected to the output port 154 at a time, which ensures the independent connection of the output port 154, and the input channel can be switched, so that the liquid permeation port of the micro-permeation structure of the auxiliary working pole 4 can switch different functions.

[0060] like Fig. 9As shown, a multi-channel valve 15 with two input ports is used as an example for explanation. In this embodiment, the second input port 153 of the multi-channel valve 15 is connected to the tail end of the return pipe 16. For example, before ablation, the valve of the multi-channel valve 15 can be switched to the first input port 151, and anesthetic drugs are injected through the external syringe 29. The anesthetic drugs enter the circular sleeve 14 through the output port 154 of the multi-channel valve 15, and finally seep out from the micro-permeable structure of the auxiliary working electrode 4. The anesthetic drugs can be directly injected into the lesion to achieve the injection of anesthetic drugs. During the ablation process, the multi-channel valve 15 can be switched to the second input port 153 by adjusting the position of the control valve 152. The second input port 153 is always connected to the return pipe 16 of the cooling system, and the coolant enters the output port 154 through the second input port 153 of the multi-channel valve 15. The coolant enters the micro-permeable structure of the auxiliary working pole through the output port 154 of the multi-channel valve 15, and seeps out from the micro-permeable structure to achieve cooling of the auxiliary working pole 4 and the adjacent tissues of the auxiliary working pole 4, avoid tissue carbonization and adhesion, and reduce tissue impedance to achieve a larger ablation range. After the ablation is completed, the valve of the multi-channel valve 15 can also be switched to the first input port 151, and the combined therapeutic drug can be injected through an external syringe. The micro-permeable structure of the present invention has a small space, which can prevent more drugs from being retained in the permeation space. Usually, drugs are relatively expensive, so drug waste is avoided.

[0061] Specifically, when the valve of the multi-channel valve 15 is switched to the second input port 153, a small portion of the return water at the tail end of the return pipe 28 enters the return pipe 16, and then flows to the output port 154 through the second input port 153, flows into the circular sleeve 14 through the output port 154, and reaches the micro-permeation structure of the auxiliary working electrode 4 through the gap between the second outer needle tube 6 and the first insulating tube 8. During the ablation process, the cooling and micro-permeation functions of the two working electrodes can be achieved without external injection, simplifying the surgical operation process. The infiltration port of the micro-permeation structure of the auxiliary working electrode 4 includes an exposed tube along the auxiliary working electrode 4. Multiple circles of injection holes 401 are axially opened in 402, and one end of the injection hole 401 penetrates the side wall of the second outer needle tube 6 and is connected with the interior of the second outer needle tube 6; in another preferred embodiment, the end of the second outer needle tube 6 is fixedly sealed and connected with one end of the exposed tube 402 of the auxiliary working electrode 4, so that the interior of the second outer needle tube 6 is connected with the interior of the auxiliary working electrode 4, and the injection hole 401 penetrates the side wall of the auxiliary working electrode 4, so as to realize the function of connecting the injection hole 401 with the penetration channel of the auxiliary working electrode 4; realize micro-penetration of the tissues around the auxiliary working electrode 4, maintain a low impedance environment throughout the process, energy injection is smooth, and tissue carbonization is slight.

[0062] The cold medium that seeps out of the main working electrode 2 and the auxiliary working electrode 4 further cools the total working end and its surrounding tissues. The cold medium is usually sterile saline, which can conduct radio frequency current during the seepage process, enhance the conductivity of the tissue, reduce the impedance between the main working electrode and the auxiliary working electrode before ablation, maintain a low-impedance working environment between the main working electrode and the auxiliary working electrode during ablation, and continuously output high power throughout the entire ablation process, solving the problem of energy injection, improving ablation efficiency, and expanding the ablation range; trace amounts of saline that seeps out are converted into water vapor under the action of radio frequency current, and water vapor can be used as an auxiliary ablation medium, which can simultaneously realize radio frequency ablation and steam ablation of the main working electrode, and radio frequency ablation and steam ablation of the auxiliary working electrode, thereby expanding the ablation range and enhancing the ablation effect.

[0063] The main working electrode 2 and the auxiliary working electrode 4 of this embodiment use the same cooling system, which can realize cooling of the main working electrode 2, the auxiliary working electrode 4 and the adjacent tissues. The main working electrode 2 and the auxiliary working electrode 4 have micro-permeable structures. During the ablation process, the cold medium can be automatically injected into the lesion tissue through the micro-permeable structure on the main working electrode 2 and the micro-permeable structure on the auxiliary working electrode 4, respectively, to cool the total working end and the adjacent tissues, avoid high temperature causing carbonization and adhesion of tissues, and expand the ablation range. At the same time, the cold medium injected into the lesion can enhance the conductivity of the tissue and further expand the ablation range. The problem of the small ablation range of conventional bipolar radiofrequency ablation electrodes is solved, and the unique safety and controllability of radiofrequency ablation is maintained. It can be used on patients with metal or pacemakers installed in their bodies, especially for lesion tissues that require a large ablation range and high ablation accuracy, such as myocardial hypertrophy, prostatic hyperplasia and other lesion tissues with relatively high requirements.

[0064] like Fig.10 , Fig.11 As shown, in this embodiment, a Luer connector is used to achieve connection between ports. When the valve of the multi-channel valve 15 is switched to the first input port 151, the first input port 151 is connected to the output port 154. The Luer male connector of the output port of the syringe can be connected to the Luer female connector of the first input port 151 of the multi-channel valve 15 to achieve injection of external drugs into surrounding tissues through the micro-permeation structure of the auxiliary working electrode 4. At the same time, the micro-permeation structure on the auxiliary working electrode 4 can also be used to achieve suction of the liquid in the lesion tissue.

[0065] In this embodiment, if Figure 2As shown, the micro-permeability structure of the main working electrode 2 includes a plurality of circles of micropores 901 axially arranged on the first outer needle tube 9, and a plurality of circles of square holes 202 are axially arranged on the sleeve 201 of the main working electrode 2, and the micropores 901 and the square holes 202 are staggered from front to back along the axial direction of the first outer needle tube 9, that is, along the axial direction, the position of the micropores 901 on the first outer needle tube 9 corresponds to the tube wall of the sleeve 201 (the position where the square holes 202 are not arranged), and the micropores 901 can be shielded by the tube wall of the sleeve 201 to prevent the cold medium from being sprayed out; a small gap is left between the sleeve 201 and the first outer needle tube 9, and after the cold medium flows out from the micropores 901, it can enter the gap between the first outer needle tube 9 and the sleeve 201 and seep out from the square holes 202. This design not only ensures the cold circulation function of the electrode, but also ensures that the tiny gap between the micropore 901, the first outer needle tube 9 and the sleeve 201 is not blocked during the ablation process, causing tissue carbonization and adhesion, and ensures that the cold medium can continuously and evenly seep out from each hole.

[0066] like Fig.12 As shown, the RF wire 23 includes a first RF wire 19 and a second RF wire 21. The front end of the first RF wire 19 is connected to the main working pole 2 through a first welding point 20, and the front end of the second RF wire 21 is connected to the auxiliary working pole 4 through a second welding point 22. The tail end of the first RF wire 19 is connected to a first RF plug 25, and the tail end of the second RF wire 21 is connected to a second RF plug 26; the first RF plug 25 and the second RF plug 26 are respectively connected to the two poles of the RF source; the RF current is conducted between the main working pole 2 and the auxiliary working pole 4 to ablate the tissue, and the RF current is conducted between the two poles and does not flow to the tissue outside the lesion. During ablation, there is no need to stick a neutral electrode sheet. A conduction switch 24 is provided between the first RF wire 19 and the second RF wire 21 to realize the conversion from bipolar to monopolar. The conduction switch 24 of this embodiment is a boat-shaped switch. In this embodiment, the conduction switch 24 can connect the first RF wire 19 and the second RF wire 21. When the conduction switch 24 is pressed, the main working pole 2 is electrically connected to the auxiliary working pole 4 to realize the conversion from bipolar to monopolar. At this time, a neutral electrode needs to be connected, and the ablation range is larger; when the conduction switch 24 is disconnected, the first RF wire 19 and the second RF wire 21 are not connected. At this time, the conversion from monopolar to bipolar is realized, that is, the RF ablation electrode is a bipolar electrode, and there is no need to stick a neutral electrode during ablation. The ablation range is large and accurately controllable.

[0067] The present invention uses specific examples to illustrate the principles and implementation methods of the present invention. The above examples are only used to help understand the method and core ideas of the present invention. At the same time, for those skilled in the art, according to the ideas of the present invention, there will be changes in the specific implementation methods and application scope. In summary, the content of this specification should not be understood as limiting the present invention.

Claims

1. A radiofrequency ablation electrode, characterized in that: include: A working end, wherein the working end comprises a coaxially arranged main working pole and an auxiliary working pole, the main working pole and the auxiliary working pole are separated by a coaxially arranged insulating device, and the axial distance between the main working pole and the auxiliary working pole is adjustable; A radio frequency generating source, the two electrodes of which are respectively connected to the main working electrode and the auxiliary working electrode through radio frequency wires; A cooling system capable of introducing circulating refrigerant into the inner channels of the main working electrode and the auxiliary working electrode; The micro-permeation structure includes permeation ports respectively opened on the side walls of the main working electrode and the auxiliary working electrode. The permeation port on the main working electrode is connected to the inner channel, and the permeation port on the auxiliary working electrode is connected to the permeation channel of the auxiliary working electrode. Part of the refrigerant medium refluxed by the cooling system can enter the permeation channel.

2. The radiofrequency ablation electrode according to claim 1, characterized in that: The main working electrode is fixed, and the auxiliary working electrode can move axially; the permeation port and permeation channel of the auxiliary working electrode will move in real time with the axial movement of the auxiliary working electrode, and the permeation port of the auxiliary working electrode is always evenly maintained on the auxiliary working electrode.

3. The radiofrequency ablation electrode according to claim 1, characterized in that: The main working electrode and the auxiliary working electrode can simultaneously realize radiofrequency ablation and steam ablation.

4. The radiofrequency ablation electrode according to claim 1, characterized in that: It also includes an inner needle tube, a first outer needle tube, and a second outer needle tube; a needle tip is fixedly provided at one end of the first outer needle tube, and the end face diameter of the needle tip connected to the first outer needle tube is larger than the outer diameter of the first outer needle tube, the main working electrode is sleeved on the first outer needle tube, and one end thereof abuts against the end face of the needle tip, and the other end is sealed and connected with a first connecting part sleeved on the first outer needle tube; the first connecting part is sleeved with the insulating device and the second outer needle tube in sequence; the second outer needle tube is fixedly sleeved with the auxiliary working electrode at the port close to the insulating device; the tail end of the second outer needle tube is slidably penetrated into a sealed cavity tube, and the sealed cavity tube can be connected with the cooling system; the inner channel is formed between the inner needle tube and the first outer needle tube, and the infiltration channel of the auxiliary working electrode is formed between the inner wall of the second outer needle tube and the first connecting part; the radio frequency wires of the radio frequency generating source are respectively connected with the first outer needle tube and the second outer needle tube.

5. The radiofrequency ablation electrode according to claim 4, characterized in that: The end of the auxiliary working pole away from the insulating device is sealed with a second connecting part sleeved on the second outer needle tube; the tail end surface of the second connecting part is fixedly sleeved with an adjusting block, and the adjusting block can drive the second connecting part, the second outer needle tube and the auxiliary working pole to move axially synchronously, and during the movement, the tail end of the second outer needle tube is always in the sealed cavity tube.

6. The radiofrequency ablation electrode according to claim 5, characterized in that: The first connection portion is a first insulating tube disposed on the first outer needle tube, and the second connection portion is a second insulating tube disposed on the second outer needle tube.

7. The radiofrequency ablation electrode according to claim 4, characterized in that: The sealed cavity tube comprises a round sleeve with a sealed tail end, and a flexible plastic sealing block is sealedly connected to the front end of the round sleeve; the second outer needle tube seal slides through the flexible plastic sealing block and extends into the round sleeve.

8. The radiofrequency ablation electrode according to claim 4, characterized in that: The penetration port of the main working pole includes multiple circles of square holes opened along the axial direction of the main working pole, and the side wall of the first outer needle tube connected to the main working pole is provided with multiple circles of micro holes arranged along the axial direction, and the micro holes and the square holes are arranged alternately; the penetration port of the auxiliary working pole includes multiple circles of injection holes opened along the axial direction of the auxiliary working pole, and one end of the injection hole passes through the side wall of the second outer needle tube and is connected to the interior of the second outer needle tube.

9. The radiofrequency ablation electrode according to claim 4, characterized in that: The cooling system includes a return water chamber, a water inlet chamber, a water inlet pipe and a return water pipe. The inner cavity of the inner needle tube forms the water inlet pipe, the inner channel between the outer wall of the inner needle tube and the inner wall of the first outer needle tube forms the return water pipe, and the front end of the water inlet pipe is connected with the front end of the return water pipe; a partition device is provided between the water inlet chamber and the return water chamber, and the rear end of the inner needle tube passes through the return water chamber and the partition device and is connected with the water inlet chamber; the rear end of the first outer needle tube is penetrated in the return water chamber; the return water chamber can be connected with the sealing chamber tube through a reflux pipe; the return water chamber and the water inlet chamber are respectively connected with liquid supply devices.

10. The radiofrequency ablation electrode according to claim 9, characterized in that: The liquid supply device includes a refrigerant source and a refrigerant recovery device. The refrigerant source can provide the refrigerant and allow the refrigerant to flow into the water chamber through a water inlet pipe. The refrigerant recovery device can recover the refrigerant and the refrigerant flows from the return water chamber through a return water pipe into the refrigerant recovery device.

11. The radiofrequency ablation electrode according to claim 8, characterized in that: The injection holes are expanded from the proximal end to the distal end, the injection holes at the proximal end have a diameter range of 0.1 to 0.4 mm, and the injection holes at the distal end have a diameter range of 0.5 to 1 mm.

12. The radiofrequency ablation electrode according to claim 9, characterized in that: A multi-channel valve is fixedly connected to the side wall of the sealed cavity tube, the output port of the multi-channel valve is connected to the inside of the sealed cavity tube, one of the input ports of the multi-channel valve is connected to the reflux pipe, and the remaining input ports of the multi-channel valve are provided with Luer female connectors. The multi-channel valve can be switched so that its output port is independently connected to any input port.

13. The radiofrequency ablation electrode according to claim 1, characterized in that: The length of the main working pole is different from that of the auxiliary working pole, and the maximum range of the adjustable axial distance between the main working pole and the auxiliary working pole is the length of the shorter one of the main working pole and the auxiliary working pole.

14. The radiofrequency ablation electrode according to claim 1, characterized in that: The length of the main working pole is the same as that of the auxiliary working pole, and the maximum range of the adjustable axial distance between the main working pole and the auxiliary working pole is the length of the main working pole or the length of the auxiliary working pole.

15. The radiofrequency ablation electrode according to claim 1, characterized in that: The RF wire includes a first RF wire and a second RF wire, the front end of the first RF wire is connected to the main working pole, the front end of the second RF wire is connected to the auxiliary working pole, the tail end of the first RF wire is connected to the first RF plug, and the tail end of the second RF wire is connected to the second RF plug; the first RF plug and the second RF plug are respectively connected to the two poles of the RF source.

16. The radiofrequency ablation electrode according to claim 15, characterized in that: A conduction switch is provided between the first radio frequency wire and the second radio frequency wire. When the conduction switch is turned on, the first radio frequency wire and the second radio frequency wire are electrically connected. At this time, the main working electrode and the auxiliary working electrode are converted into monopolar electrodes. When the conduction switch is turned off, the first radio frequency wire and the second radio frequency wire are not connected, and at this time, the main working electrode and the auxiliary working electrode are converted into bipolar electrodes.

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