Ablation catheter and ablation system

Abstract

This application relates to the field of medical device technology and proposes an ablation catheter and ablation system, comprising: a handle; a main tube, the hardness of which gradually decreases from the end near the handle to the end away from the handle; an inner tube slidably disposed within the main tube; and an ablation assembly, the ablation assembly including at least one connector, the connectors being spaced apart circumferentially along the inner tube, the end of the connector facing the handle being connected to the main tube, and the end of the connector away from the handle being connected to the end of the inner tube away from the handle; the ablation assembly also includes electrodes, each connector having at least one electrode, each electrode being connected to an insulated wire; the axial movement of the inner tube along the main tube can cause the connectors to deform; this application features a main tube with gradually changing hardness to allow the ablation assembly to move smoothly to the target position, and an inner tube that can slide relative to the main tube, thereby adjusting the shape of the connectors to adapt to tissue cells of different shapes, making it highly practical.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to an ablation catheter and ablation system. Background Technology

[0002] Pulsed electric field ablation is considered a non-thermal ablation technique, meaning that the ablation process does not generate heat or tissue temperature rise. It can eliminate the heat sink effect of traditional ablation methods such as radiofrequency, microwave, and cryoablation. Therefore, pulsed electric field ablation is considered to have a strong advantage in ablation of temperature-sensitive tissues (such as tissues near the gallbladder, bile duct, and esophagus), especially when performing ablation for the treatment of atrial fibrillation. Pulsed electric field ablation has the advantages of short ablation time and protection of the treatment area or blood vessels and other tissues.

[0003] Pulsed electric field ablation catheters for myocardial tissue are energy delivery tools that travel through blood vessels to the heart chambers. During punctures and other catheter procedures, not only is high maneuverability of the catheter required, but also a relatively small diameter. Smaller diameter catheters reduce the difficulty and risk of the procedure, resulting in less trauma to the patient. However, current ablation catheters have poor maneuverability, making it difficult to approach the target tissue and perform bending maneuvers, thus hindering their advancement to the target location. Summary of the Invention

[0004] To address the aforementioned issues, this application provides an ablation catheter and ablation system, which at least solves the problem of poor maneuverability of ablation catheters in prior art.

[0005] This application provides an ablation catheter, comprising: handle; A main tube, one end of which is connected to the handle, wherein the hardness of the main tube gradually increases from the end closer to the handle to the end further away from the handle; An inner tube, which is slidably inserted through the main body tube, with one end of the inner tube away from the handle extending outside the main body tube; An ablation assembly includes multiple connectors spaced apart circumferentially along the inner tube. One end of each connector facing the handle is connected to the main tube, and the other end of each connector is connected to the end of the inner tube away from the handle. Each connector has at least one electrode, and each electrode is connected to an insulated wire. The electrode is sleeved on the connector, and the surface of the electrode near the inner tube can be attached to the inner tube. The surface of the electrode near the inner tube is a plane or an arc-shaped surface. The cross-sectional shape of the connector is the same as that of the electrode.

[0006] In one embodiment, the electrode is sleeved on the connector, and the surface of the electrode near the inner tube can be attached to the inner tube. The surface of the electrode near the inner tube is a planar or arc-shaped surface. The cross-sectional shape of the connector is the same as that of the electrode.

[0007] In one embodiment, the cross-section of the connector is elliptical, the cross-section of the electrode is elliptical, and the electrode is fixedly sleeved on the corresponding connector.

[0008] In one embodiment, the cross-section of the connector is formed by a first arc and a first straight line, wherein the central angle of the arc is greater than 180° and less than 360°; The cross-section of the electrode is formed by a second arc and a second straight line. The central angle of the arc is greater than 180° and less than 360°. The diameter of the second arc is greater than the diameter of the first arc, and the first straight line is parallel to the second straight line.

[0009] In one embodiment, the cross-section of the connector is formed by a third arc and a fourth arc, and the centers of the third arc and the fourth arc are located on the same side of the cross-section of the connector. The cross-section of the electrode is formed by the fifth arc and the sixth arc, and the centers of the fifth arc and the sixth arc are located on the same side of the cross-section of the connector.

[0010] In one embodiment, the number of connectors is 3-8; and the number of electrodes on each connector is 2-4.

[0011] In one embodiment, the axial movement of the inner tube along the main tube can cause the connector to deform in a direction away from the inner tube.

[0012] In one embodiment, the main tube includes a tube wall that forms an inner tube channel, and the inner tube is slidably disposed within the inner tube channel; The tube wall has a wire channel inside, the insulated wire passes through the wire channel, and the end of the insulated wire away from the electrode extends outside the main tube.

[0013] In one embodiment, the insulated wire includes a semiconductor core, an insulating layer, and a protective layer, wherein the insulating layer is sleeved on the semiconductor core and the protective layer is sleeved on the insulating layer.

[0014] In one embodiment, the insulated wire is fitted with an insulating sleeve.

[0015] In one embodiment, the ablation catheter further includes a traction component, one end of which is disposed on the handle, and the other end of which is connected to the main tube. The traction component is used to drive the end of the main tube away from the handle to move and cause the main tube to bend and deform.

[0016] In one embodiment, the traction assembly includes a traction guide wire disposed within the tube wall, one end of the traction guide wire being connected to the handle, and the other end of the traction guide wire away from the handle being disposed at the end of the main tube away from the handle.

[0017] This application also proposes an ablation system, including: The host; and the ablation catheter, wherein the end of the insulated wire of the ablation catheter away from the electrode is connected to an interface assembly for electrical connection with the host.

[0018] This application addresses the problem of poor maneuverability of ablation catheters in prior art by making an improved design, which has the following beneficial effects: 1. Set up the main tube and gradually change its hardness. The end of the main tube closer to the handle has low hardness to facilitate deformation and bending, so that the ablation component can move to different target positions. The end of the main tube further away from the handle has high hardness to provide support for the ablation component, so that the ablation component can be smoothly pushed to the target position, improving the maneuverability of the ablation catheter. 2. An inner tube that can slide relative to the main tube is provided, and one end of the connector of the ablation component is connected to the inner tube, while the other end of the connector is connected to the main tube. The sliding of the inner tube can deform the connector and form different shapes to adapt to tissues of different shapes, further improving the maneuverability of the ablation catheter. The ablation catheter and ablation system provided in this application are easy to operate. The main tube with gradually changing hardness is set so that the ablation components can move smoothly to the target position. The inner tube is set so as to adjust the shape of the connector to adapt to tissue cells of different shapes, which improves the maneuverability of the ablation catheter and makes it highly practical. Attached Figure Description

[0019] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0020] Figure 1 This is a front view schematic diagram of the ablation catheter provided in an embodiment of this application.

[0021] Figure 2 This is a front view schematic diagram of the ablation catheter bending as provided in an embodiment of this application.

[0022] Figure 3 for Figure 2 A magnified view of a portion of point A in the middle.

[0023] Figure 4 for Figure 1 The diagram shown is a left-hand view of the ablation component in the ablation catheter when it is open.

[0024] Figure 5 for Figure 1 The diagram shows a cross-sectional view of the connectors and electrodes in the ablation catheter.

[0025] Figure 6 In another embodiment Figure 1 The diagram shows a cross-sectional view of the connectors and electrodes in the ablation catheter.

[0026] Figure 7 In yet another embodiment Figure 1 The diagram shows a cross-sectional view of the connectors and electrodes in the ablation catheter.

[0027] Figure 8 for Figure 7 The diagram shows a cross-sectional view of the connector, electrode, and inner tube when the ablation assembly is in the retracted state.

[0028] Figure 9 for Figure 1 The diagram shows a cross-sectional view of the main tube of the ablation catheter.

[0029] Figure 10 for Figure 1 The diagram shows a cross-sectional view of the insulated wires and insulated sleeve in the ablation catheter.

[0030] Figure 11 for Figure 1 The diagram shows a front view of the handle in the ablation catheter.

[0031] The markings in the diagram mean: 100. Ablation catheter; 10. Handle; 11. First adjustment component; 12. Interface component; 20. Main pipe; 201. Pipe wall; 2011. Conductor channel; 202. Inner pipe channel; 30. Inner tube; 40. Ablation assembly; 41. Connector; 411. First arc; 412. First straight line; 413. Third arc; 414. Fourth arc; 42. Electrode; 421. Second arc; 422. Second straight line; 423. Fifth arc; 424. Sixth arc; 43. Insulated wire; 431. Semiconductor core; 432. Insulating layer; 433. Protective layer; 44. Insulating sleeve; 50. Traction assembly; 51. Traction guide wire; 52. Second adjustment assembly. Detailed Implementation

[0032] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0033] It should be noted that when a component is referred to as "fixed to" or "set on" another component, it can be directly or indirectly attached to that other component. When a component is referred to as "connected to" another component, it can be directly or indirectly connected to that other component. The terms "upper," "lower," "left," "right," etc., indicate orientations or positional relationships based on the orientations or positional relationships shown in the accompanying drawings, and are for descriptive convenience only, not indicating or implying that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation on the patent. The terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features. "A plurality" means two or more, unless otherwise explicitly defined.

[0034] It should also be noted that in the embodiments of this application, the same reference numerals are used to represent the same component or part. For the same part in the embodiments of this application, the reference numerals may only be used to mark one part or component as an example. It should be understood that the reference numerals are also applicable to other identical parts or components.

[0035] Pulsed electric field ablation catheters for myocardial tissue are energy delivery tools that travel through blood vessels to the heart chambers. During punctures and other catheter procedures, not only is high maneuverability of the catheter required, but also a relatively small diameter. Smaller diameter catheters reduce the difficulty and risk of the procedure, resulting in less trauma to the patient. However, current ablation catheters have poor maneuverability, making it difficult to approach the target tissue and perform bending maneuvers, thus hindering their advancement to the target location.

[0036] Therefore, this application provides an ablation catheter, which has a main tube and gradually changes its hardness so that the main tube has both support and bending capabilities; and has an inner tube that can slide relative to the main tube. The sliding of the inner tube can deform the connector and form different shapes so as to adapt to tissues of different shapes.

[0037] The ablation catheter can perform high-voltage pulse ablation on tissues in different lesions, such as myocardium, phrenic nerve, esophagus, and blood vessels. When ablating different tissues, it is only necessary to set the pulse voltage according to the voltage penetration threshold of different tissues. This application uses myocardial cells as an example for illustration.

[0038] To illustrate the technical solutions described in this application, the following description is provided in conjunction with specific accompanying drawings and embodiments.

[0039] refer to Figures 1 to 3 , Figure 9 This application provides an ablation catheter 100, which includes a handle 10, a main tube 20, an inner tube 30, and an ablation component 40.

[0040] The handle 10 provides a fixed base for the main tube 20 and the inner tube 30, and also makes it easy for the user to hold. The user can push the main tube 20 into the patient's body by holding the handle 10.

[0041] One end of the main tube 20 is connected to the handle 10. The main tube 20 is used to accommodate the inner tube 30 and also to provide a fixed base for the ablation component 40. The main tube 20 can enter the patient's body and bend within the patient's body, pushing the ablation component 40 to the target position in the patient's body along the blood vessels. The hardness of the main tube 20 gradually increases from the end near the handle 10 to the end away from the handle 10. The end of the main tube 20 near the handle 10 has low hardness, allowing the main tube 20 to bend with the blood vessels, so that the main tube 20 can push the ablation component 40 to the required target position. The end of the main tube 20 away from the handle 10 has high hardness, so as to provide support for the ablation component 40.

[0042] The inner tube 30 is slidably disposed inside the main tube 20. The inner tube 30 can slide along the axial direction of the main tube 20, and at the same time, the inner tube 30 can bend synchronously with the main tube 20.

[0043] The ablation component 40 is used to ablate the target tissue. The ablation component 40 is located at the end of the main tube 20 away from the handle 10. The ablation component 40 includes a connector 41 and an electrode 42. One end of the connector 41 is connected to the main tube 20, and the other end is connected to the inner tube 30. The inner tube 30 can slide along the main tube 20 to cause the connector 41 to bend and deform. The electrode 42 is located on the connector 41. An insulated wire 43 is connected to the electrode 42. The other end of the insulated wire 43 is connected to an external device to deliver a pulse voltage to the electrode 42. The pulse voltage can be applied to the tissue through the electrode 42. The application of a short-term high pulse voltage to the tissue can generate a high electric field strength of hundreds to thousands of volts per centimeter. The cell membrane of the tissue under this high electric field strength will produce pores, resulting in the destruction of the cell membrane. Among them, the voltage penetration threshold of myocardial cells is relatively low compared with other tissues (such as the phrenic nerve, esophagus, and blood vessels). Therefore, the voltage amplitude range of the pulse square wave can be controlled to selectively ablate myocardial cells without affecting other non-target tissues.

[0044] There may be one or more connectors 41. One end of the connector 41 is connected to the end of the main tube 20 away from the handle 10 and the other end is connected to the end of the inner tube 30 away from the handle 10. When there are multiple connectors 41, the multiple connectors 41 are arranged at intervals along the circumference of the inner tube 30. As the inner tube 30 moves toward the handle 10, the connectors 41 gradually bend. During the movement of the inner tube 30 toward the handle 10, the inner tube 30 can stop moving at any position and the connectors 41 are in different states so that the electrode 42 can fit with tissues of different shapes. When the inner tube 30 moves toward the handle 10 to the limit position, the two ends of the connector 41 abut against each other.

[0045] Each connector 41 has at least one electrode 42.

[0046] Electrode 42 is sleeved on connector 41. The surface of electrode 42 near inner tube 30 can be attached to inner tube 30. The surface of electrode 42 near inner tube 30 is flat or arc-shaped so that when ablation component 40 is in the retracted state, electrode 42 can be attached to inner tube 30 to reduce the space occupied by ablation component 40. Optionally, the cross-sectional shape of connector 41 is the same as the cross-sectional shape of electrode 42 so that electrode 42 can be better attached to connector 41, reducing the gap between electrode 42 and connector 41, and reducing the space occupied by ablation component 40 in the retracted state.

[0047] The operation process in this embodiment is as follows: the user holds the handle 10 and inserts the ablation component 40 into the patient's body; then the user pushes the handle 10 and pushes the ablation component 40 to the target position; then the external device delivers pulse voltage to the electrode 42 through the insulated wire 43 to perform pulse ablation on the target tissue.

[0048] The beneficial effects of this embodiment are as follows: A main tube 20 is provided, and the hardness of the main tube 20 gradually changes. The end of the main tube 20 closer to the handle 10 has lower hardness, so that the main tube 20 can deform and bend, thereby allowing the ablation component 40 to move to different target positions. The end of the main tube 20 further away from the handle 10 has higher hardness, so as to provide support for the ablation component 40, allowing the ablation component 40 to be smoothly pushed to the target position, thus improving the maneuverability of the ablation catheter 100. An inner tube 30 that can slide relative to the main tube 20 is provided, and one end of the connector 41 of the ablation component 40 is connected to the inner tube 30, and the other end of the connector 41 is connected to the main tube 20. The sliding of the inner tube 30 allows the connector 41 to deform and form different shapes, so as to adapt to tissues of different shapes, further improving the maneuverability of the ablation catheter 100.

[0049] refer to Figure 1 , Figure 3 , Figure 4 In one embodiment, the number of connectors 41 is 3-8, and the multiple connectors 41 are arranged at intervals along the circumference of the inner tube 30.

[0050] Figure 1 In the middle, the ablation component 40 is in the retracted state. At this time, the end of the inner tube 30 away from the handle 10 is at the extreme position farthest from the handle 10. Each connector 41 abuts against the inner tube 30, and the end of the inner tube 30 away from the handle 10 is the farthest from the handle 10.

[0051] Figure 3 In the middle, the ablation component 40 is in an intermediate state, and the multiple connectors 41 continue to bend. At this time, the inner tube 30 is in an intermediate state during the movement towards the handle 10. At this time, the multiple connectors 41 are all in a bent state, and the multiple connectors 41 together form a cage shape.

[0052] Figure 4 In the middle, the ablation component 40 is in the open state. At this time, the end of the inner tube 30 away from the handle 10 is in the extreme position closest to the handle 10. The two ends of each connector 41 abut against each other, and multiple connectors 41 together form a petal shape.

[0053] In this embodiment, the number of electrodes 42 on each connector 41 is 2-4; optionally, the number of electrodes 42 on each connector 41 is 2.

[0054] In this embodiment, the cross-sectional shapes of the connector 41 and the electrode 42 can be of various shapes, so that adjacent electrodes 42 can be fully attached when the ablation component 40 is in the retracted state, and each electrode 42 can be fully attached to the inner tube 30 when the ablation component 40 is in the retracted state, so as to further reduce the outer diameter of the ablation component 40 in the retracted state.

[0055] refer to Figure 5 In one embodiment, the cross-sectional shape of the connector 41 is elliptical.

[0056] The cross-sectional shape of electrode 42 is an elliptical ring, and electrode 42 is fixedly sleeved on connector 41. At this time, the surface of connector 41 facing inner tube 30 is an arc-shaped surface.

[0057] When the ablation assembly 40 is in the retracted state, this configuration allows the electrodes 42 to better fit together and fit better with the inner tube 30, thereby reducing the gaps between electrodes 42 and between electrodes 42 and the inner tube 30, reducing the space occupied by the electrodes 42, reducing the outer diameter of the ablation assembly 40 in the retracted state, and making the space occupied by the ablation assembly 40 in the retracted state smaller, so as to reduce the damage that may be caused when the ablation catheter 100 enters the patient's body, reduce the difficulty of the operation, and improve the safety of the operation.

[0058] refer to Figure 6 In another embodiment, the cross-sectional shape of the connector 41 is irregular, and the cross-sectional shape of the electrode 42 is also irregular. Specifically, the cross-sectional shapes of the connector 41 and the motor 42 are bun-shaped, and the electrode 42 is fixedly sleeved on the connector 41.

[0059] The cross section of the connector 41 is formed by the first arc 411 and the first straight line 412. The central angle of the first arc 411 is greater than 180°. The two ends of the first straight line 412 are respectively connected to the two ends of the first arc 411 and enclosed to form the cross section of the connector 41. The first straight line 412 of the cross section of the connector 41 faces the inner tube 30.

[0060] The cross-section of electrode 42 is formed by the second arc 421 and the second straight line 422. The central angle of the second arc 421 is greater than 180°. The two ends of the second straight line 422 are connected to the two ends of the second arc 421 respectively and enclose the cross-section of electrode 42. Since electrode 42 is sleeved on connector 41, the cross-section of electrode 42 is actually a closed ring. The second arc 421 is opposite to the first arc 411, and the second straight line 422 is opposite to the first straight line 412. Optionally, the central angle of the second arc 421 is the same as that of the first arc 411.

[0061] refer to Figure 7 , Figure 8 In another embodiment, the cross-sectional shape of the connector 41 is irregular, and the cross-sectional shape of the electrode 42 is also irregular. Specifically, the cross-sectional shapes of the connector 41 and the motor 42 are crescent-shaped.

[0062] The cross section of the connector 41 is formed by the third arc 413 and the fourth straight line 414. The centers of the third arc 413 and the fourth arc 414 are located outside the cross section of the connector 41, and both are located on the side of the connector 41 facing the inner tube 30. The third arc 413 and the fourth arc 414 enclose the cross section of the connector 41 in a crescent shape, and the fourth arc 414 of the cross section of the connector 41 faces the inner tube 30.

[0063] The cross-section of electrode 42 is formed by the fifth arc 423 and the sixth arc 424. The centers of the fifth arc 423 and the sixth arc 424 are located outside the cross-section of electrode 42 and are both located on the side of electrode 42 facing the inner tube 30. Since electrode 42 is sleeved on connector 41, the cross-section of electrode 42 is actually a closed ring. The fifth arc 423 is opposite to the third arc 413, and the sixth arc 424 is opposite to the fourth arc 414. Optionally, the center angle of the third arc 413 is the same as that of the fifth arc 423, and the center angle of the fourth arc 414 is the same as that of the sixth arc 424.

[0064] When the ablation component 40 is in the retracted state, this configuration allows the electrodes 42 to better fit together. Specifically, each electrode 42 can abut against and fit with the adjacent electrode 42 without overlapping. At the same time, the electrodes 42 can also fit better into the inner tube 30, thereby reducing the gaps between electrodes 42 and between electrodes 42 and the inner tube 30, reducing the space occupied by the electrodes 42, and reducing the outer diameter of the ablation component 40 in the retracted state. This makes the ablation component 40 occupy less space in the retracted state, thereby reducing the potential damage when the ablation catheter 100 enters the patient's body, reducing the difficulty of the operation, and improving the safety of the operation.

[0065] In this embodiment, the cross-sectional shapes of the connector 41 and the electrode 42 can be elliptical, dome-shaped, or crescent-shaped, or other irregular shapes, so that adjacent electrodes 42 can be fully fitted when the ablation component 40 is in the retracted state, and each electrode 42 can be fully fitted with the inner tube 30 when the ablation component 40 is in the retracted state, so as to further reduce the outer diameter of the ablation component 40 in the retracted state.

[0066] refer to Figure 9 In one embodiment, the main tube 20 includes a tube wall 201 and an inner tube channel 202. The inner tube channel 202 is opened in the main tube 20 along the axial direction and passes through the main tube 20, while forming the tube wall 201. The inner tube 30 is slidably disposed in the inner tube channel 202 along the axial direction. The inner tube 30 sliding relative to the main tube 20 in the inner tube channel 202 can drive the connector 41 to deform.

[0067] In this embodiment, a wire channel 2011 is provided inside the tube wall 201. The wire channel 2011 is used to accommodate the insulated wire 43 and can also be used to accommodate the traction guide wire 51.

[0068] refer to Figure 10 In one embodiment, one end of the insulated wire 43 is connected to the electrode 42, and the end of the insulated wire 43 away from the electrode 42 passes through the tube wall 201 and extends to the outside of the end of the main tube 20 away from the electrode 42. That is, the insulated wire 43 is located inside the tube wall 201. The tube wall 201 can protect the insulated wire 43, prevent the insulated wire 43 from being exposed to the outside world or from contacting the patient's internal tissues, and at the same time prevent the inner tube 30 from contacting the insulated wire 43 during the movement, so as to prevent the insulated wire 43 from getting tangled in the inner tube 30.

[0069] In this embodiment, the insulated wire 43 includes a semiconductor core 431, an insulating layer 432, and a protective layer 433.

[0070] The insulating layer 432 is disposed on the semiconductor core 431. Specifically, the insulating layer 432 covers the semiconductor core 431 circumferentially. The protective layer 433 is disposed on the insulating layer 432. Specifically, the protective layer 433 covers the insulating layer 432 circumferentially.

[0071] The beneficial effects of this embodiment are as follows: it provides a three-layer protection structure for the insulated wire 43, which protects the semiconductor core 431 in sequence through the insulating layer 432 and the protective layer 433. The insulating layer 432 is used to protect the semiconductor core 431 to avoid leakage or reduce the impact of partial discharge. In addition to protecting the semiconductor core 431, the protective layer 433 can also protect the insulating layer 432, reducing the occurrence of failure due to damage to the insulating layer 432.

[0072] In this embodiment, the insulated wire 43 is covered with an insulating sleeve 44. Through the multiple protections of the insulating layer 432, the insulating sleeve 44 and the tube wall 201, the influence of partial discharge is further reduced, so as to ensure that the insulated wire 43 still has good insulation under ultra-high voltage conditions.

[0073] refer to Figure 9 , Figure 11 In one embodiment, the ablation catheter 100 further includes a traction component 50, one end of which is disposed on the handle 10, and the other end of which is disposed away from the handle 10 on the main tube 20. The traction component 50 can drive the end of the main tube 20 away from the handle 10 to move and bend. The traction component 50 can be a guide wire or other various traction guide components that can drive the main tube 20 to bend.

[0074] In this embodiment, the traction assembly 50 includes a traction guide wire 51 and a second adjustment assembly 52.

[0075] One end of the traction guide wire 51 is located at the handle 10, and the other end of the traction guide wire 51 away from the handle 10 is located at the other end of the main tube 20 away from the handle 10. The end of the traction guide wire 51 facing the handle 10 can move inside the handle 10, thereby causing the other end of the main tube 20 away from the handle 10 to bend. The traction guide wire 51 can be a stainless steel wire, a nickel-titanium wire, or other various guide wires. The traction guide wire 51 can be a hollow tubular structure and sleeved outside the insulating sleeve 44. The traction guide wire 51 can also be a solid filament structure and located outside the insulating sleeve 44.

[0076] The second adjustment component 52 is used to drive the guide wire 51 toward one end of the handle 10, thereby controlling the bending of the main tube 20.

[0077] Optionally, there are four traction guide wires 51, which are evenly spaced within the tube wall 201. The second adjustment component 52 can independently control the movement of the four traction guide wires 51 so as to control the main tube 20 to bend in the direction of the four traction guide wires 51.

[0078] refer to Figure 9 In one embodiment, the handle 10 is provided with a first adjustment component 11, which is connected to the end of the inner tube 30 away from the ablation component 40. The first adjustment component 11 is used to drive the inner tube 30 to move relative to the main tube 20. The first adjustment component 11 can be a telescopic cylinder or other structures that can drive the inner tube 30 to move.

[0079] The operation process of the ablation catheter 100 provided in this application embodiment is as follows: the user holds the handle 10 and inserts the ablation component 40 into the patient's body; then the user pushes the handle 10 and pushes the ablation component 40 to the target position. During this process, the main tube 20 can be bent by the second adjustment component 52 and the traction guide wire 51 so that the ablation component 40 reaches the target position; then the inner tube 30 moves relative to the main tube 20 and the ablation component 40 is placed in any position, such as a retracted state, an open state, or an intermediate state, as needed; then the external device delivers pulse voltage to the electrode 42 through the insulated wire 43 to perform pulse ablation on the target tissue.

[0080] This application also provides an ablation system, including a host and an ablation catheter 100.

[0081] The host is used to provide pulse voltage to electrode 42. The host can also monitor the patient's physical values, such as heart rate changes, through the electrical signals transmitted back by electrode 42 and insulated wire 43.

[0082] The handle 10 of the ablation catheter 100 is provided with an interface component 12. The interface component 12 is electrically connected to the end of the insulated wire 43 away from the ablation component 40. The interface component 12 can also be connected to the host. Optionally, the interface component 12 has multiple interfaces, so that the insulated wire 43 can also be connected to other devices.

[0083] The operation process of the ablation system provided in this application embodiment is as follows: when the ablation component 40 of the ablation catheter 100 reaches the target position, the host transmits a pulse signal to the electrode 42 to perform ablation; at the same time, the host can also monitor the patient's body parameters through the electrical signals transmitted back by the electrode 42 and the insulated wire 43, thereby playing a detection role.

[0084] The above embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application, and should all be included within the protection scope of this application.

Claims

1. An ablation catheter, characterized in that, include: handle; A main tube, one end of which is connected to the handle, wherein the hardness of the main tube gradually increases from the end closer to the handle to the end further away from the handle; An inner tube, which is slidably inserted through the main body tube, with one end of the inner tube away from the handle extending outside the main body tube; An ablation assembly includes multiple connectors spaced apart circumferentially along the inner tube. One end of each connector facing the handle is connected to the main tube, and the other end of each connector is connected to the end of the inner tube away from the handle. Each connector has at least one electrode, and each electrode is connected to an insulated wire. The electrode is sleeved on the connector, and the surface of the electrode near the inner tube can be attached to the inner tube. The surface of the electrode near the inner tube is a flat or arc-shaped surface. The cross-sectional shape of the connector is the same as that of the electrode. The main tube includes a tube wall, which forms an inner tube channel, and the inner tube is slidably disposed within the inner tube channel; The inside of the pipe wall is provided with a conductor channel, the insulated conductor passes through the conductor channel, and the insulated conductor is covered with an insulating sleeve; The ablation catheter further includes a traction assembly, one end of which is located on the handle, and the other end of which is connected to the main tube. The traction assembly is used to move the end of the main tube away from the handle and cause the main tube to bend and deform. The lead channel is also used to accommodate a traction guide wire. The traction assembly includes a traction guide wire located inside the tube wall. The traction guide wire is a hollow tubular structure and is sleeved outside the insulating sleeve. Alternatively, the traction guide wire is a solid filament structure and is located outside the insulating sleeve.

2. The ablation catheter according to claim 1, characterized in that, Both the connector and the electrode have elliptical cross-sections.

3. The ablation catheter according to claim 1, characterized in that, The cross-section of the connector is formed by a first arc and a first straight line, wherein the central angle of the first arc is greater than 180° and less than 360°. The cross-section of the electrode is formed by a second arc and a second straight line. The central angle of the second arc is greater than 180° and less than 360°. The diameter of the second arc is greater than the diameter of the first arc, and the first straight line is parallel to the second straight line.

4. The ablation catheter according to claim 1, characterized in that, The cross-section of the connector is formed by a third arc and a fourth arc, and the centers of the third arc and the fourth arc are both located on the side of the connector facing the inner tube. The cross-section of the electrode is formed by the fifth arc and the sixth arc, and the centers of the fifth arc and the sixth arc are both located on the side of the connector facing the inner tube.

5. The ablation catheter according to any one of claims 1-4, characterized in that, The number of connectors is 3-8; the number of electrodes on each connector is 2-4.

6. The ablation catheter according to claim 1, characterized in that, The movement of the inner tube along the axial direction of the main tube can cause the connector to deform in a direction away from the inner tube.

7. The ablation catheter according to claim 1, characterized in that, The end of the insulated wire away from the electrode extends outside the main tube.

8. The ablation catheter according to claim 1, characterized in that, The insulated wire includes a semiconductor core, an insulating layer, and a protective layer. The insulating layer is sleeved on the semiconductor core, and the protective layer is sleeved on the insulating layer.

9. The ablation catheter according to claim 1, characterized in that, One end of the traction guide wire is located inside the handle, and the other end of the traction guide wire away from the handle is connected to the end of the main tube away from the handle.

10. An ablation system, characterized in that, include: Host; as well as, The ablation catheter as described in any one of claims 1-9, wherein the end of the insulated wire of the ablation catheter away from the electrode is connected to an interface assembly, the interface assembly being used for electrical connection with the body.

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