Ablation catheter

Abstract

The invention relates to an ablation catheter. The ablation catheter comprises an outer tube, a bearing frame and a first ablation piece. The bearing frame is arranged at the far end of the outer tube, the bearing frame is of a support structure capable of being contracted and expanded in the radial direction, the bearing frame comprises a plurality of bearing components, and the bearing components are arranged around the axis of the outer tube at intervals in the circumferential direction; a linear attaching face is formed on the outer surface of each bearing component and used for being attached to a target ablation area to conduct linear ablation, and the first ablation pieces are correspondingly arranged on the bearing components and used for being connected with an external energy source so as to transmit ablation energy output by the external energy source to the target ablation area.

Description

Technical Field

[0001] The present application belongs to the technical field of interventional medical devices, and relates to cardiac interventional treatment devices, and in particular to an ablation catheter. Background Art

[0002] Atrial fibrillation is one of the major diseases that has emerged in recent years and threatens human life and health. Since the hazards of atrial fibrillation are mainly manifested in high mortality, high disability, and high recurrence rates, the quality of life of patients with atrial fibrillation is far worse than that of patients without atrial fibrillation. Atrial fibrillation is divided into paroxysmal atrial fibrillation, persistent atrial fibrillation, long-term persistent atrial fibrillation, and permanent atrial fibrillation. For persistent atrial fibrillation and long-term persistent atrial fibrillation, the main sites of ablation treatment are currently the ablation isolation of the mitral isthmus line, the tricuspid isthmus line, and the left atrial top line. The mitral isthmus line refers to a diameter from the left pulmonary vein to the mitral valve ring, and the tricuspid isthmus refers to a diameter from the inferior vena cava to the tricuspid valve ring.

[0003] In recent years, electrophysiology centers have developed rapidly, and catheter ablation technology has been widely used in paroxysmal atrial fibrillation. However, when the relevant ablation catheter is used for persistent atrial fibrillation or even long-term persistent atrial fibrillation, the following problems will occur: First, the stability of the relevant ablation catheter is poor. Since the atrial wall is inherently smooth, the position where the ablation catheter is attached may shift during treatment, which greatly reduces the actual ablation effect. Second, when the relevant ablation catheter is currently used for persistent atrial fibrillation and long-term persistent atrial fibrillation, it is often necessary to perform multiple ablations at the ablation path. For areas with thicker or even thicker walls, multiple or even repetitive ablation operations are required to achieve the treatment purpose. However, such operations will result in a long operation time and cause greater damage to the patient. Therefore, it is necessary to provide a new ablation catheter for the treatment of persistent atrial fibrillation or even long-term persistent atrial fibrillation. Summary of the invention

[0004] The purpose of the present application is to provide an ablation catheter to meet the needs of ablation of more complex lesions (such as persistent atrial fibrillation, long-term persistent atrial fibrillation, etc.).

[0005] The present application provides an ablation catheter, which includes an outer tube, a bearing frame and a first ablation component. The bearing frame is arranged at the distal end of the outer tube and is a radially contractible and expandable stent structure. The bearing frame includes a plurality of bearing components, which are arranged around the axis of the outer tube at circumferential intervals. The outer surface of each bearing component forms a linear abutment surface for abutting against a target ablation area for linear ablation. The first ablation component is correspondingly arranged on the bearing component, and the first ablation component is used to connect to an external energy source to transmit the ablation energy output by the external energy source to the target ablation area.

[0006] In the ablation catheter of the present application, a load-bearing frame is arranged at the distal end of the outer tube. The load-bearing frame is cooperated with a plurality of load-bearing components to form a contractible and expandable stent structure. The plurality of load-bearing components are arranged circumferentially at intervals around the axis of the outer tube. The outer surface of each load-bearing component forms a linear abutment surface, which facilitates the use of the linear abutment surface of a single load-bearing component to abut the target ablation area to achieve linear ablation. The linear abutment surface fits the ablation diameter of persistent atrial fibrillation and long-term atrial fibrillation, and can achieve ablation of ablation areas for persistent atrial fibrillation and long-term atrial fibrillation (such as the atrial wall and ablation locations such as the mitral isthmus and the tricuspid isthmus). Compared with the general linear structure, the support structure and structural stability of the support frame in this embodiment are better. Therefore, the abutment of multiple linear abutment surfaces formed by the support structure can be more stable. The first ablation component is correspondingly arranged on the support member. Under the premise that a single support member can be stably abutted against the target ablation area, the ablation energy transmitted to the target ablation area by the first ablation component for tissue ablation can also be more accurate, which is conducive to improving the ablation effect and reducing the number of repeated ablations. In addition, any support member on the support frame can be used alone for ablation, without having to limit the ablation abutment of the entire support frame, thus greatly improving the operational convenience and flexibility of the ablation catheter. BRIEF DESCRIPTION OF THE DRAWINGS

[0007] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for use in the implementation will be briefly introduced below. Obviously, the drawings described below are some implementation methods of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0008] Figure 1 It is a structural schematic diagram of positioning an ablation catheter in a target ablation area provided by one embodiment of the present application.

[0009] Figure 2 yes Figure 1 Schematic diagram of the three-dimensional structure of the ablation catheter.

[0010] Figure 3 yes Figure 2 Schematic diagram of the three-dimensional structure of the ablation catheter in the contracted state.

[0011] Figure 4 yes Figure 2 A partial enlarged view of part A.

[0012] Figure 5 It is a schematic diagram of the three-dimensional structure of an ablation catheter provided in another embodiment of the present application.

[0013] Figure 6 yes Figure 5 Schematic diagram of the structure of the ablation catheter from another perspective.

[0014] Figure 7 It is a schematic diagram of the three-dimensional structure of an ablation catheter provided in yet another embodiment of the present application.

[0015] The following are the descriptions of the reference numerals:

[0016] 10-outer tube; 100-ablation catheter; 101-target ablation area; 20-carrying frame; 21-carrying member; 211-carrying rod; 212-first carrying rod; 213-second carrying rod; 2131-rod body; 2133-insulating layer; 213A-first rod structure; 213B-second rod structure; 213C-third rod structure; 213D-fourth rod structure; 215-third carrying rod; 2151-rod part; 2153-insulating sleeve; 30-first ablation component; 31-head electrode; 40-support frame; 41-first main rod; 43-first branch rod; 45-second main rod; 46-second branch rod; 47-connecting rod; 50-traction component; 51-positioning sensor; 53-second ablation component. DETAILED DESCRIPTION

[0017] The technical solutions in the embodiments of the present application will be described clearly and completely below in conjunction with the drawings in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

[0018] The following descriptions of the embodiments are made with reference to the attached drawings to illustrate specific implementations of the present application. Directional terms mentioned in the present application, such as "top", "bottom", "front", "back", "left", "right", "inside", "outside", "side", etc., are only with reference to the directions of the attached drawings. Therefore, the directional terms used are for better and clearer explanation and understanding of the present application, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, be constructed and operate in a specific orientation, and should not be understood as a limitation on the present application.

[0019] In the description of the present application, it should be noted that, unless otherwise clearly specified and limited, the terms "installed", "connected", "connected", and "set on..." should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection; it can be a direct connection, or it can be an indirect connection through an intermediate medium, or it can be an internal connection between two elements.

[0020] In the field of interventional medical devices, the proximal end refers to the end close to the operator, while the distal end refers to the end away from the operator. Axial refers to the direction of the axis of the device, radial refers to the direction perpendicular to the axial direction and where the radius or diameter is located, and circumferential refers to the direction perpendicular to and surrounding the axial direction. For ordinary technicians in this field, the specific meanings of the above terms in this application can be understood according to specific circumstances.

[0021] In this application, the terms "first", "second", and "third" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, a feature defined as "first", "second", and "third" may explicitly or implicitly include one or more of the features.

[0022] The ablation catheter provided in the embodiment of the present application is used to ablate the target ablation area by pulse ablation or radiofrequency ablation or any other suitable form of ablation energy to achieve the effect of electrical isolation. It is delivered to the target ablation area by a delivery device (sheath) through percutaneous puncture. The target ablation area can be located at a specific position of the heart, such as the mitral isthmus, the tricuspid isthmus, the top of the left atrium, the pulmonary vein, the left atrial appendage, or a triggering focus with typical atrial flutter and non-pulmonary vein origin (such as the superior vena cava, the coronary venous sinus ostium). It can be understood that the target ablation area is not limited to the heart, but can also be other body tissues, which is not limited here.

[0023] First embodiment

[0024] See also Figures 1 to 3 The embodiment of the present application provides an ablation catheter 100 . The ablation catheter 100 includes an outer tube 10 , a carrier frame 20 , and a first ablation component 30 .

[0025] Among them, the outer tube 10 is a hollow tubular structure, and the outer tube 10 has a single axial lumen or a central lumen. According to the needs, multiple lumens can be placed in the inner cavity of the outer tube 10 along its axial direction to accommodate pull wires, leads, sensor cables and any other wires, cables and / or tubes that may be required in a specific application through multiple lumens. It can be understood that at least part of the outer tube 10 is flexible, which is convenient for adjusting the degree and direction of bending. The outer tube 10 can be radially bent to adapt to the curved structure inside the heart. The outer tube 10 can also be any suitable structure, and the radial cross-sectional shape of the outer tube 10 can be circular, oblate, smoothly transitioned rectangular or other shapes. The outer tube 10 can be made of any suitable material, and the outer tube 10 can be made of a biocompatible material such as a metal material or a polymer material, such as stainless steel 316L, tungsten, tantalum, nickel titanium, polyethylene, polyamide, polypropylene, polyurethane, polyether block amide, etc. The outer diameter of the outer tube 10 can be 2-3mm. Exemplarily, the outer tube 10 in the embodiment of the present application is a circular tubular catheter made of polyurethane with an outer diameter of 2.5 mm, that is, a 7.5F catheter.

[0026] The carrier frame 20 is disposed at the distal end of the outer tube 10. The carrier frame 20 defines a longitudinal axis and is configured to expand radially outward relative to the longitudinal axis, and to contract radially inward relative to the longitudinal axis and to extend longitudinally. In the contracted state, the carrier frame 20 is movably accommodated in the sheath (the sheath is the medium for the ablation catheter 100 to enter the heart). In the expanded state, the distal end and the proximal end of the carrier frame 20 are both exposed (released) from the distal end of the sheath, and the outer contour of the carrier frame 20 is roughly a spherical structure.

[0027] The distal end of the carrier frame 20 forms a converged end, and the proximal end of the carrier frame 20 is converged and connected to the distal end of the outer tube 10. Since the carrier frame 20 is elastic and can shrink, when the carrier frame 20 is accommodated in the sheath tube, under the resistance of the inner wall of the sheath tube, the carrier frame 20 can be stretched so that the carrier frame 20 is stretched into a straight line, that is, stretched into a roughly linear state, such as Figure 3 As shown in FIG. 1 , the straightened support frame 20 can easily pass through the sheath. When the support frame 20 reaches the vicinity of the target ablation area through the sheath, the resistance of the inner wall of the sheath is removed, so the support frame 20 can expand from the linear state to the original spherical structure, as shown in FIG. Figure 1 and Figure 2 As shown, the radially expanded carrier frame 20 can be used for example Figure 1 The target ablation area 101 in the ablation catheter 100 is, for example, a circumferential ablation isolation of the pulmonary vein vestibule. At this time, the spherical structure of the support frame 20 is stable in structure, has good support performance, is easier to adhere to the tissue, and has high ablation quality. It should be noted that during the entire process of using the ablation catheter 100 for surgery, the ablation catheter 100 does not need to be guided to the ablation site using a guide wire.

[0028] Still see Figures 1 to 3 The carrier frame 20 includes a plurality of carrier components 21. The plurality of carrier components 21 are arranged around the axis of the outer tube 10 at intervals in the circumferential direction. The distal ends of the plurality of carrier components 21 converge and connect together, and at the same time, the proximal ends of the plurality of carrier components 21 also converge and connect together and connect to the distal end of the outer tube 10. The plurality of carrier components 21 are spherical or other geometric shapes as a whole. The outer surface of each carrier component 21 forms a linear abutment surface, which can be used to abut the target ablation area for linear ablation, for example, linear ablation of the atrial wall, the mitral isthmus line, the tricuspid isthmus line and the like can be achieved. The number of the plurality of carrier components 21 used in the carrier frame 20 can be two, three, four, five or any other suitable number. The carrier components 21 can be evenly spaced and distributed circumferentially. Of course, the carrier components 21 can also be unevenly spaced and distributed circumferentially. For example, when the number of the carrier components 21 is four, the projections of the four carrier components 21 on the plane perpendicular to the axis of the outer tube 10 are X-shaped.

[0029] The first ablation piece 30 is disposed on the bearing member 21, and the first ablation piece 30 is connected to an external energy source. When the bearing member 21 is close to the target ablation area, the first ablation piece 30 can be used to provide ablation energy and perform tissue ablation. In other embodiments, the first ablation piece 30 can also be used for electrophysiological signal mapping, thereby realizing other functions such as cardiac mapping. It can be understood that the number and position of the first ablation piece 30 can be reasonably arranged according to the size of the bearing member 21.

[0030] In this embodiment, the external energy source can provide electric pulses to perform electroporation surgery. The external energy source can deliver multiple different pulses of various waveforms or shapes to achieve electroporation ablation of the target ablation area, including but not limited to sinusoidal AC pulses, DC pulses, square wave pulses, exponentially decaying waveforms, or other pulse shapes for electrical ablation, such as combined AC / DC pulses or DC offset signals. The energy pulse train provided by the external energy source includes single-phase pulses or biphasic pulses. The external energy source can be configured with single-phase or biphasic pulses with different parameters such as voltage, pulse width, repetition frequency, duty cycle and number of pulses. For example, high-voltage pulses can be selected as the form of energy transmitted by the external energy source, and other forms of ablation energy can be emitted additionally or alternatively, such as radio frequency energy or any other suitable form of energy. In other examples, the ablation energy delivered by the external energy source can also be radio frequency energy, microwave energy or ultrasonic energy, etc., which are not specifically limited here.

[0031] The ablation catheter 100 of this embodiment has the following advantages: 1. The bearing frame 20 can be expanded into a spherical structure with excellent support performance and structural stability; 2. The outer surface of each bearing member 21 is linearly arranged along the axial direction of the outer tube 10, so as to match the ablation diameter of the target ablation area, so that the ablation catheter 100 can achieve linear ablation close to the target ablation area. Linear ablation can match the ablation diameter of persistent atrial fibrillation and long-term atrial fibrillation. Therefore, the ablation catheter 100 of the embodiment of the present application can meet the ablation of more complex diseases (such as persistent atrial fibrillation and long-term atrial fibrillation). 3. In addition to using the bearing member 21 for linear ablation, the spherical structure of the bearing frame 20 can also be used to treat paroxysmal atrial fibrillation (for example, ablation of the pulmonary vein vestibule), that is, there is no need to use other catheters for annular ablation isolation, which expands the treatment range of the ablation catheter 100 of this embodiment, increases the treatment of symptoms applicable to the ablation catheter 100, and has good application prospects.

[0032] Still see Figures 1 to 3 In some embodiments, each bearing member 21 includes a plurality of bearing rods 211, and the plurality of bearing rods 211 are arranged at intervals in the circumferential direction. The outer surfaces of the plurality of bearing rods 211 jointly form a linear abutment surface, and the first ablating member 30 is correspondingly arranged on the bearing rods 211. Compared with a single bearing rod 211 as an abutment surface for linear ablation, the plurality of bearing rods 211 abut together, and the abutment degree of the plurality of bearing rods 211 together is better, the abutment requirement is lower, and the ablation field strength of the linear abutment surface formed by the plurality of bearing rods 211 can be greater, so that a deeper ablation depth and a faster ablation through-the-wall speed can be achieved.

[0033] In some embodiments, the ablation catheter 100 further includes a support frame 40 , which is used to connect adjacent load-bearing rods 211 , so as to pull the load-bearing rods 211 after the load-bearing frame 20 expands, prevent the load-bearing rods 211 from shifting in position, and maintain the distance between adjacent load-bearing rods 211 . When the support rod 211 is close to the tissue for ablation, the support rod 211 will be subjected to an external force perpendicular to its own axis or inclined to its own axis. The support frame 40 connected to the support rod 211 subjected to the external force can transfer the external force to the adjacent support rod 211, thereby pulling the adjacent support rod 211. The support rod 211 has the performance of maintaining its own structure and state, thereby forming a reverse force on the adjacent support rod 211 to buffer or offset the force. The adjacent support rods 211 generate a reaction force perpendicular to the axis or inclined to the axis to the support rod 211 subjected to the external force, counteracting the external force, thereby maintaining a distance between adjacent support rods 211, maintaining the stability of the position of the support rod 211, and effectively maintaining the stability of the relative position of the ablation element 300 on the support rod 211 or the connecting frame 220, preventing the first ablation element 30 of the ablation catheter 100 from contacting each other and short-circuiting during operation, effectively avoiding penetrating damage to the target tissue and reducing the occurrence of serious adverse complications.

[0034] Still see Figures 1 to 3 In some embodiments, the support frame 40 is arranged along the axial direction, the support frame 40 is connected to the distal end of the bearing frame 20, the proximal end of the bearing frame 20 is connected to the distal end of the outer tube 10, the distal end of the bearing frame 20 is connected to the proximal end of the support frame 40, and the distal end of the support frame 40 is gathered into one. The connection method of the proximal end of the bearing frame 20 may include but is not limited to one or more combination of welding, clamping, bonding, hot melting, threaded connection, sealing connection, etc. The support frame 40 is used to connect multiple bearing rods 211 to maintain the relative position relationship between the multiple bearing rods 211 and prevent the multiple bearing rods 211 from positional displacement.

[0035] In other embodiments, the support frame 40 can also be connected to the proximal end of the carrier frame 20, the proximal end of the support frame 40 is connected to the distal end of the outer tube 10, the distal end of the support frame 40 is connected to the proximal end of the carrier frame 20, and the distal end of the carrier frame 20 is gathered into one. The connection method of the proximal end of the support frame 40 can include but is not limited to one or more combination connections such as welding, clamping, bonding, hot melting, threaded connection, and sealing connection. The support frame 40 is used to connect multiple carrier rods 211, to maintain the relative position relationship between the multiple carrier rods 211, and to prevent the multiple carrier rods 211 from shifting in position.

[0036] Combination Figure 4In some embodiments, the support frame 40 includes a plurality of first main rods 41 and a plurality of first branch rods 43 distributed circumferentially around the axis of the outer tube 10. Each first main rod 41 is connected to a plurality of first branch rods 43 at one end facing the support frame 20. The ends of the plurality of first main rods 41 away from the support frame 20 are combined together. The plurality of first main rods 41 may be uniformly distributed circumferentially around the axis of the outer tube 10, or may be non-uniformly distributed circumferentially around the axis of the outer tube 10.

[0037] Each bearing member 21 includes at least one first bearing rod 212 and at least one second bearing rod 213, and the at least one first bearing rod 212 and the at least one second bearing rod 213 are arranged at intervals in the circumferential direction. The first bearing rod 212 is connected to the first main rod 41 through the first branch rod 43. Specifically, one end of each first bearing rod 212 facing the support frame 40 is connected to the corresponding plurality of first branch rods 43, and the other end of the plurality of first branch rods 43 connected to the same first bearing rod 212 is connected to a different first main rod 41. Different first bearing rods 212 connected by the same first main rod 41 and the plurality of first branch rods 43 can disperse the stress thereon through the mutual connection between the first main rod 41 and the plurality of first branch rods 43, thereby maintaining the stability of the position of the first bearing rod 212. The second bearing rod 213 is directly connected to the first main rod 41. Specifically, one end of each second bearing rod 213 facing the support frame 40 is connected to one end of the corresponding first main rod 41 facing the bearing frame 20.

[0038] In some embodiments, the radial dimension of the support frame 40 formed by multiple first main rods 41 and multiple first branch rods 43 is smaller than the radial dimension of the support frame 20 formed by multiple first bearing rods 212 and multiple second bearing rods 213. The maximum outer diameter of the support frame 40 is smaller, and the maximum outer diameter of the bearing frame 20 is larger. Therefore, after expansion, the bearing frame 20 can be more closely attached to the target ablation area, with a higher degree of adhesion and better ablation effect. The smaller support frame 40 can facilitate guidance and play a supporting role, thereby facilitating the bearing frame 20 to stably fit the target ablation area, perform linear ablation, and improve the success rate of the operation.

[0039] Schematically, see Figure 2There are two first bearing rods 212 and one second bearing rod 213. Each bearing member 21 includes two first bearing rods 212 and one second bearing rod 213 which are circumferentially spaced apart, and the second bearing rod 213 is located between the two first bearing rods 212. Two first branch rods 43 are arranged at one end of each first main rod 41 facing the bearing frame 20. The other ends of the two first branch rods 43 connected to the same first main rod 41 extend in directions away from each other. Two adjacent first branch rods 43 connected to different first main rods 41 are connected to the same first bearing rod 212. The end of each first branch rod 43 facing the bearing frame 20 is combined with the end of the adjacent first branch rod 43 facing the bearing frame 20, that is, the first branch rod 43 connected to the end of each first branch rod 43 facing the bearing frame 20 is different from the first branch rod 43 connected to the end away from the bearing frame 20. A plurality of first branch rods 43 are connected end to end to form a wave-shaped ring structure, one end of each first main rod 41 facing the support frame 20 is connected to a corresponding wave crest of the wave-shaped ring structure, and one end of each first bearing rod 212 facing the support frame 40 is connected to a corresponding wave trough of the wave-shaped ring structure. Only one of two adjacent first main rods 41 has one end facing the support frame 20 connected to a corresponding second bearing rod 213, and one end of the first main rod 41 connected to the second bearing rod 213 facing the support frame 20 is combined with the two first branch rods 43 and the second bearing rod 213.

[0040] In some embodiments, see Figure 4 The two first branch rods 43 connected to one of the two adjacent first main rods 41 form a first angle A1, and the two first branch rods 43 connected to the other first main rod 41 form a second angle A2, the first angle A1 is smaller than the second angle A2, the distal end of the second bearing rod 213 is located in the first angle A1 and is connected to the corresponding first main rod 41, so that the second bearing rod 213 is located between the two adjacent first bearing rods 212 with a smaller spacing, when the bearing frame 20 and the support frame 40 radially expand, the second bearing rod 213 can be used to reinforce the radial bending shape of the two adjacent first bearing rods 212, so that the frame surrounded by the bearing frame 20 and the support frame 40 approximately maintains a spherical shape, when the bearing frame 20 and the support frame 40 radially shrink, the multiple first bearing rods 212 and the multiple second bearing rods 213 will not be nonlinearly twisted due to the circular sheathing channel. In addition, the second bearing rod 213 is located between two adjacent first bearing rods 212 with a smaller spacing. Although the spacing between the two adjacent first bearing rods 212 is smaller, since the second bearing rod 213 is located between the two, the second bearing rod 213 can also prevent the two adjacent first bearing rods 212 from getting close to or touching each other, thereby avoiding the risk of short circuit.

[0041] Please continue to see Figure 1 to Figure 2The carrier frame 20 and the support frame 40 are connected and enclosed to form a spherical structure, which has better support performance and stability. It can be understood that the structure enclosed by the carrier frame 20 and the support frame 40 can also be other structures, such as pumpkin shape, lantern shape, oval shape, etc. The carrier frame 20 and the support frame 40 can shrink and expand radially.

[0042] The carrier frame 20 and the support frame 40 can be made by cutting elastic metal pipes, or by weaving elastic metal wires, or by processing by partial weaving combined with partial pipe cutting, and different parts can be welded or fixed to each other by connectors. The material of the pipe is metal or non-metallic material, preferably memory metal material or nickel-titanium alloy material. In this embodiment, the carrier frame 20 and the support frame 40 are cut and shaped by a nickel-titanium alloy pipe, and the cross-section of the cutting rod that surrounds the carrier frame 20 is the same as the cross-section of the cutting rod that surrounds the support frame 40. The carrier frame 20 and the support frame 40 are manufactured by integral cutting, which improves the efficiency of production and manufacturing. At the same time, the integrally cut carrier frame 20 and the support frame 40 make the materials of various parts of the carrier frame 20 and the support frame 40 the same, effectively ensuring that the elastic coefficients of various parts of the carrier frame 20 and the support frame 40 are the same, thereby ensuring the stable expansion of the carrier frame 20 and the support frame 40, so that the ablation catheter 100 of the present application has a stable and uniform radial support force, which can act more stably on the target ablation area. In other embodiments, the cross-section of the cutting rods forming the carrying frame 20 and the cross-section of the cutting rods forming the supporting frame 40 may also be different.

[0043] In some embodiments, see Figures 1 to 3 At least one first ablation element 30 is disposed on the second supporting rod 213. Specifically, one or more first ablation elements 30 may be disposed on one second supporting rod 213, or multiple first ablation elements 30 may be disposed on all second supporting rods 213, or multiple first ablation elements 30 may be disposed on some of the second supporting rods 213.

[0044] The first ablation component 30 is disposed on the second supporting rod 213. When the second supporting rod 213 is in contact with the target ablation area, the first ablation component 30 can be used to provide ablation energy for tissue ablation. The ablation energy provided by the first ablation component 30 can be pulse energy, radio frequency energy, microwave energy or ultrasonic energy, etc., which is not specifically limited here.

[0045] The support frame 40 and the plurality of first bearing rods 212 can be made of a metal material as a whole, and have a conductive skeleton, and then the conductive skeleton is used in conjunction with the first ablation piece 30 to transfer ablation energy to the target ablation area. Specifically, the conductive skeleton is connected to one pole of an external energy source, and the first ablation piece 30 is connected to the other pole of the external energy source to form an electric field that transfers ablation energy to the target ablation area. In other examples, the conductive skeleton or the first ablation piece 30 can also be connected to one pole of an external energy source, and the other pole of the external energy source can be connected to an electrode plate attached to the patient's body surface to transfer ablation energy to the target ablation area.

[0046] In some embodiments, the first ablation element 30 is an ablation electrode, and the material of the ablation electrode can be platinum, iridium, gold, silver, etc., which are medical metals that can be used for interventional treatment. Figure 1 As shown, the first ablation component 30 is an ablation electrode, and is a ring electrode. It can be understood that the ablation electrode can be a ring electrode, a semicircular patch electrode, a flexible patch electrode, a bellows electrode, a point electrode or a spherical electrode, etc., and this embodiment does not make any specific limitations.

[0047] The ablation electrode is sleeved on the second bearing rod 213. On the same second bearing rod 213, multiple ablation electrodes are provided and arranged at intervals along the axial direction. In the multiple second bearing rods 213, the ablation electrodes correspond to each other one by one along the axial direction and are arranged at intervals circumferentially around the axis of the bearing frame 20. Schematically, as shown in FIG. Figure 1 As shown, three ablation electrodes are arranged on the second bearing rod 213, and the three ablation electrodes are arranged at intervals along the axial direction. On the plurality of second bearing rods 213, the ablation electrodes correspond to each other along the axial direction, and each ablation electrode surrounds the axis of the outer tube 10 to form three rings, and each ring is perpendicular to the axis of the bearing frame 20.

[0048] Of course, on multiple second supporting rods 213, multiple ablation electrodes can also be staggered along the axial direction. The number of ablation electrodes on the same second supporting rod 213 can also be one, two, three, four, eight or any other suitable number, which can be set according to needs and the size of the second supporting rod 213 without specific limitation here.

[0049] When the second bearing rod 213 is attached to the target ablation area, the ablation electrode can be used to provide ablation energy to perform tissue ablation. In other embodiments, the ablation electrode can also be used for electrophysiological signal mapping to achieve other functions such as cardiac mapping. It is understandable that the ablation energy provided by the ablation electrode can be pulse energy, radio frequency energy, microwave energy or ultrasonic energy, etc., which is not specifically limited here.

[0050] In some embodiments, Figure 2As shown, the second bearing rod 213 includes a rod body 2131 and an insulating layer 2133 sleeved on the outside of the rod body 2131, and the material of the insulating layer 2133 is a coating, a polyether block amide tube or other polymer insulating materials. The insulating layer 2133 can be one layer, two layers or multiple layers, which is not limited here. The cross-sectional shape of the rod body 2131 can be circular, semicircular, drum or other shapes, which is not limited here. In this embodiment, the second bearing rod 213 is a single arc shape, or it can be a combination of arcs and other curved shapes. In this embodiment, the rod body 2131 is made of nickel-titanium wire, so that the rod body 2131 has excellent elastic properties and strength, so that it can be well attached to the target ablation area. It can be understood that the rod body 2131 can also be made of other materials, such as nickel-titanium tube cutting or polymer materials.

[0051] The ablation electrode is sleeved on the insulating layer 2133. The insulating layer 2133 not only ensures the insulation between the ablation electrode and the rod body 2131, but also improves the conductive skeleton as one pole, so that the overall support structure can withstand high voltage and avoid short circuit caused by electrical breakdown. The inner wall of the ablation electrode is welded with an insulated wire (or multiple ablation electrodes are connected to the same insulated wire, and the number of ablation electrodes connected to the insulated wire depends on the requirements of the positive and negative poles). The insulated wire is installed between the rod body 2131 and the insulating layer 2133, that is, each ablation electrode inner surface passes through the surface of the insulating layer 2133 through an insulated wire, and is connected to the connector on the external handle along the rod body 2131 and the outer tube 10, and is electrically connected to the external energy source through the connector. The ablation electrode and the insulated wire are connected by welding or other special processes. In some embodiments, the insulated wire can be an enameled wire, which has insulation properties and can withstand a voltage greater than or equal to 500V.

[0052] In other embodiments, the second supporting rod 213 may also be provided with a microelectrode, which may be used alone to achieve regional discharge or for mapping, while the ablation electrode is only used for ablation.

[0053] In some embodiments, the ablation catheter 100 further includes a head electrode 31. When the carrier frame 20 is disposed at the distal end relative to the support frame 40, the head electrode 31 is disposed at the farthest end of the carrier frame 20, and the far end of the carrier frame 20 converges to the head electrode 31; when the support frame 40 is disposed at the farthest end relative to the carrier frame 20, the head electrode 31 is disposed at the farthest end of the support frame 40. Figure 2 As shown, the distal end of the support frame 40 converges at the head electrode 31 , and the head electrode 31 is connected to the distal ends of a plurality of first main rods 41 of the support frame 40 .

[0054] The head electrode 31 can have the functions of potential mapping and delivering ablation energy to the target tissue area. The ablation energy delivered by the head electrode 31 can be pulse energy, radiofrequency energy, or other forms of energy. Medical staff can make targeted ablation strategies and adjust them according to the different conditions of patients, thereby expanding the ablation range of the lesion location and meeting the ablation requirements of more indications.

[0055] For the ablation catheter 100 of the embodiment of the present application, the ablation energy can be transmitted to the target ablation area through the cooperation of the conductive frame, the head electrode 31 and the first ablation component 30. Specifically, the conductive frame and the head electrode 31 can be connected to one pole of the external energy source, and the first ablation component 30 is connected to the other pole of the external energy source to form an electric field between the first ablation component 30 and the conductive frame and the head electrode 31 (or within a certain range around them), thereby achieving ablation of the target ablation area.

[0056] In other examples, the head electrode 31 may be used only in conjunction with the conductive skeleton for ablation, or may be used only in conjunction with the first ablation component 30 for ablation. It should be noted that when the head electrode 31 cooperates with the first ablation component 30, the number of energized first ablation components 30 is not specifically limited. Some of the first ablation components 30 may be connected to one pole of the external energy source, or all of the first ablation components 30 may be connected to one pole of the external energy source.

[0057] In other examples, a conductive skeleton can be placed against the tissue wall and connected to an external energy source, such as an external pulse ablation device, to detect the impedance of the tissue, thereby distinguishing different target ablation areas and performing targeted ablation electric field strength. For example, a corresponding pulse voltage can be set according to the tolerance of the target ablation area, thereby improving the ablation effect of the diseased tissue.

[0058] In other examples, the head electrode 31 can be used only as a mapping electrode for three-dimensional modeling of the patient's heart. When the head electrode 31 is used for mapping, the ablation catheter 100 can achieve energy ablation through the conductive frame and the first ablation member 30. For details, please refer to the above text and will not be repeated here.

[0059] In some embodiments, see Figure 1 and Figure 2When the carrier frame 20 is disposed at the distal end relative to the support frame 40, the distal end surface of the carrier frame 20 is an arc surface, and the distal end surface of the head electrode 31 is tangent to the arc surface of the carrier frame 20. Specifically, the distal end surface of the carrier frame 20 is provided with a mounting hole, and the mounting hole is used to mount the head electrode 31. When the head electrode 31 is connected to an external energy source and used to transmit ablation energy to the target ablation area, the head electrode 31 and the arc surface at the distal end of the carrier frame 20 are in the same cutting plane, so that the head electrode 31 can be stably attached to the target ablation area, and can be ablated at any angle in the target ablation area, thereby achieving a fast, efficient and high-quality ablation effect. From the doctor's point of view, especially for inexperienced doctors, it is helpful to reduce the difficulty of the doctor's learning curve.

[0060] In other embodiments, when the support frame 40 is disposed at the distal end relative to the bearing frame 20, and the head electrode 31 is disposed at the farthest end of the support frame 40, the distal end surface of the support frame 40 is an arc surface, and the distal end surface of the head electrode 31 is tangent to the arc surface of the support frame 40. The distal end surface of the support frame 40 is provided with a mounting hole, and the mounting hole is used to mount the head electrode 31.

[0061] In other examples, when the head electrode 31 is not installed, the mounting hole can be used to install a sensor (such as a pressure sensor, a temperature sensor, a thermocouple, etc.) or a miniature lighting device, a miniature real-time camera, or a miniature camera.

[0062] Second embodiment

[0063] See also Figures 5 and 6 The ablation catheter 100 of the second embodiment has substantially the same structure as the ablation catheter 100 of the first embodiment. The ablation catheter 100 of this embodiment also includes an outer tube 10, a carrier frame 20, a first ablation component 30, and a support frame 40. The structural forms of the outer tube 10, the carrier frame 20, and the support frame 40 in the second embodiment, as well as the arrangement of the first ablation component 30 and the energy transfer method are the same as those in the first embodiment and will not be described in detail herein.

[0064] The ablation catheter 100 of the second embodiment differs from the ablation catheter 100 of the first embodiment mainly in that the ablation catheter 100 of the present embodiment further comprises a traction member 50, which is coaxially disposed in the outer tube 10, and the distal end of the traction member 50 extends out of the distal end of the outer tube 10; when the support frame 40 is disposed at the distal end relative to the carrier frame 20, the distal end of the traction member 50 is connected to the distal end of the support frame 40, and the proximal end of the carrier frame 20 is connected to the distal end of the outer tube 10. The carrier frame 20 is disposed at the distal end relative to the support frame 40, the distal end of the traction member 50 is connected to the distal end of the carrier frame 20, and the proximal end of the support frame 40 is connected to the distal end of the outer tube 10.

[0065] In this embodiment, the traction member 50 is a steel cable, a flexible polyimide tube, a fluoropolyethylene tube, a stainless steel tube, or other polymer materials. The spherical structure formed by the bearing frame 20 and the support frame 40 is sleeved on the outer periphery of the distal end of the traction member 50. When the traction member 50 is a tubular structure, the traction member 50 has a certain structural strength, so that it can buffer the external force on the spherical structure and support the spherical structure, making the spherical support structure more stable and not easily affected by the environment and deformed to a large extent, resulting in uneven electric field distribution.

[0066] In some embodiments, the traction member 50 is slidably disposed in the outer tube 10 along the axial direction, so that the traction member 50 can move axially relative to the outer tube 10. The traction member 50 moves distally relative to the outer tube 10, and can drive the first main rod 41, the first branch rod 43 of the support frame 40, and the first bearing rod 212 and the second bearing rod 213 of the bearing frame 20 to gradually approach the traction member 50 radially, so that the spherical structure shrinks to an elliptical or even roughly linear structure, thereby facilitating smooth sheathing. After the elliptical or roughly linear structure is released from the sheath tube, due to the removal of external force, the elliptical or roughly linear structure can expand into a spherical structure again. Of course, in other ways, the elliptical or roughly linear structure can also be expanded into a spherical structure under the action of the traction member 50. Specifically, after the elliptical or roughly linear structure is released from the sheath, the traction member 50 is driven to move proximally relative to the outer tube 10, so that the first main rod 41, the first branch rod 43 of the support frame 40, and the first bearing rod 212 and the second bearing rod 213 of the bearing frame 20 can be driven to gradually move radially away from the traction member 50, so that the elliptical or roughly linear structure expands into a spherical structure. In other examples, the spherical structure can also be adjusted by axially moving the traction member 50, so that the various angles of the compliance of the spherical structure fit the target ablation area without sudden deformation, greatly reducing the situation of uneven force caused by sudden deformation, improving the adaptability to the anatomical morphology of different target ablation areas, facilitating operation, and achieving better ablation effect.

[0067] In some embodiments, a positioning sensor 51 is provided in the traction member 50, and the positioning sensor 51 is used to establish the motion trajectory of the ablation catheter 100 and establish a three-dimensional model of the target ablation area. The positioning sensor 51 moves with the ablation catheter 100, and can continuously build multi-point models. In a stable magnetic field environment, the positioning sensor 51 on the ablation catheter 100 receives a signal, quickly establishes the motion trajectory diagram of the ablation catheter 100 and the three-dimensional model of the heart cavity, and monitors the changes of the heart cavity in real time and from multiple angles. The positioning sensor 51 can be a magnetic positioning sensor or a magnetoelectric positioning sensor.

[0068] In some embodiments, a plurality of second ablating members 53 are provided on the traction member 50, and the plurality of second ablating members 53 are arranged at intervals along the axial direction of the traction member 50, and the second ablating members 53 are used to be paired with at least one first ablating member 30 and connected to an external energy source to form an electric field. By adding the second ablating member 53, and the second ablating member 53 is used to cooperate with at least one first ablating member 30 for ablation, a more uniform and stable electric field can be obtained, and the ablation effect and ablation depth can be better.

[0069] In some embodiments, see Figure 5 The second ablation member 53 may be an ablation electrode, and the ablation electrode is a ring electrode. The traction member 50 is provided with three ring electrodes spaced apart along the axial direction. It can be understood that the present embodiment does not limit the shape and number of the ablation electrodes.

[0070] In some embodiments, see Figure 5 and Figure 6 In order to avoid ablation energy loss and make full use of ablation energy, the ablation catheter 100 in this embodiment can achieve 360° zoned ablation. When any load-bearing member 21 is attached to the target ablation area for linear ablation, the first ablation piece 30 on the abutting load-bearing member 21 can be connected to one pole of the external energy source, and the first ablation piece 30 on the adjacent load-bearing member 21 and the multiple second ablation pieces 53 on the traction member 50 are connected to the other pole of the external energy source to form an electric field that transmits ablation energy to the target ablation area 101, while the first ablation piece 30 on the load-bearing member 21 far away from the target ablation area is not energized, so that the electric field accumulates in the target ablation area. The stronger the field strength, the higher the ablation depth, and the better the effect of transmural ablation.

[0071] The following is a detailed description of the 360° zoned ablation of the ablation catheter 100 by taking as an example an example in which a supporting frame 20 includes four supporting components 21, and the four supporting components 21 are evenly distributed around the axial center line of the outer tube 10, each supporting component 21 includes two first supporting rods 212 arranged at intervals along the circumference and a second supporting rod 213 located between the two first supporting rods 212, the proximal end of the support frame 40 is connected to the distal end of the supporting frame 20, and the proximal end of the supporting frame 20 is connected to the distal end of the outer tube 10.

[0072] For the convenience of explanation, the four second bearing rods 213 are respectively recorded as the first rod structure 213A, the second rod structure 213B, the third rod structure 213C, and the fourth rod structure 213D. Schematically, when the fourth rod structure 213D is close to the target ablation area, the first ablation member 30 on the second rod structure 213B far from the target ablation area can be selected not to be energized, and the first ablation member 30 of the fourth rod structure 213D is selected to be connected to one pole of the external energy source, and the first ablation member 30 on the first rod structure 213A and the third rod structure 213C and the second ablation member 53 on the traction member 50 are connected to the other pole of the external energy source, so that the electric field is concentrated at the fourth rod structure 213D, so that the ablation depth of the target ablation area at the fourth rod structure 213D is higher, and transmural ablation is achieved.

[0073] The ablation catheter 100 in this embodiment can be freely selected and defined in different areas, so that the doctor can operate more flexibly and improve the success rate of the operation; and it can discharge freely in different areas and make full use of pulse energy to avoid more consumption of pulse energy. It should be understood that when one of the first rod structure 213A, the second rod structure 213B or the third rod structure 213C is close to the target ablation area for linear ablation, its operation method is similar to that of the fourth rod structure 213D, so it will not be repeated.

[0074] In other embodiments, the number of the bearing members 21 may be two, three, four, eight or any other suitable number, which is not limited herein. The bearing members 21 may be evenly distributed or unevenly distributed around the axial centerline of the outer tube 10 .

[0075] Third embodiment

[0076] See also Figure 7 The structure of the ablation catheter 100 of the third embodiment is substantially the same as that of the ablation catheter 100 of the second embodiment. The ablation catheter 100 of this embodiment also includes an outer tube 10, a carrier frame 20, a first ablation component 30, a support frame 40 and a traction component 50. The structures of the outer tube 10, the first ablation component 30 and the traction component 50 in the third embodiment are the same as those in the second embodiment and are not described in detail herein.

[0077] The ablation catheter 100 of the third embodiment differs from the ablation catheter 100 of the second embodiment mainly in that the structure of the bearing member 21 included in the bearing frame 20, the structure of the support frame 40, the arrangement of the first ablation component 30, the bending function of the traction component 50 and the energy transmission method are different from those of the ablation catheter 100 of the second embodiment.

[0078] The differences between the ablation catheter 100 of the third embodiment and the ablation catheter 100 of the second embodiment are described in detail below.

[0079] See also Figure 7 In this embodiment, the support frame 40 of the ablation catheter 100 includes a plurality of second main rods 45, a plurality of second branch rods 46, and a plurality of connecting rods 47 distributed circumferentially around the axis of the outer tube 10. The plurality of second main rods 45 and the plurality of connecting rods 47 are combined together at one end away from the bearing frame 20; each second main rod 45 is connected to two second branch rods 46 at one end facing the bearing frame 20, and two second branch rods 46 connected to the same second main rod 45 are respectively connected to a connecting rod 47 at one end facing the bearing frame 20. Each bearing member 21 of this embodiment includes two third bearing rods 215 spaced apart along the circumferential direction, and the third bearing rod 215 is connected to the corresponding second branch rod 46 and connecting rod 47 at one end facing the support frame 20.

[0080] The first ablation component 30 is arranged on the third bearing rod 215, and the third bearing rod 215 includes a rod portion 2151 and an insulating sleeve 2153 sleeved on the outside of the rod portion 2151. The first ablation component 30 is sleeved on the insulating sleeve 2153. The structure of the third bearing rod 215 is similar to that of the second bearing rod 213 mentioned above, which will not be repeated here.

[0081] Compared with the ablation catheter 100 of the previous embodiment, the ablation catheter 100 of this embodiment omits the first supporting rod 212 , thereby simplifying the structure of the ablation catheter 100 .

[0082] In some embodiments, the bearing frame 20 includes two bearing members 21, and the two bearing members 21 are located on both sides of the traction member 50. The two bearing members 21 and the traction member 50 are in the same plane (that is, at least one first ablation member 30 and the second ablation member 53 can be paired to form an ablation surface area). When the ablation catheter 100 of this embodiment transmits ablation energy to the target ablation area, the first ablation member 30 and the second ablation member 53 can be paired to form an electric field for ablation. Specifically, the first ablation member 30 is connected to one pole of the external energy source, and the second ablation member 53 is connected to the other pole of the external energy source, thereby forming an ablation surface area, thereby performing surface ablation on the target ablation area. For ablation areas that require large-area ablation, the ablation efficiency can be greatly improved. For example, the first ablation member 30 on the two third bearing rods 215 is selected to be connected to one pole of the external energy source, and at least one second ablation member 53 on the traction member 50 is connected to the other pole of the external energy source. Of course, in other embodiments, at least one first ablation element 30 on one of the third bearing rods 215 may be connected to one pole of the external energy source, and at least one second ablation element 53 on the traction element 50 may be connected to the other pole of the external energy source; or at least one first ablation element 30 on one of the third bearing rods 215 may be connected to one pole of the external energy source, and at least one first ablation element 30 on the other third bearing rod 215 may be connected to the other pole of the external energy source.

[0083] In some embodiments, Figure 7 As shown, each third bearing rod 215 is provided with a plurality of first ablating elements 30, and the plurality of first ablating elements 30 are arranged at intervals along the length direction of the third bearing rod 215, and the plurality of first ablating elements 30 on two adjacent third bearing rods 215 are staggered from each other along the axial direction. The plurality of first ablating elements 30 are staggered and distributed on each two adjacent third bearing rods 215 along the axial direction, and can form a W-shaped radial line or a linear radial line during ablation, which can better fit the ablation radial line of the patient, reduce the number of ablations, and reduce the harm to the patient.

[0084] In some embodiments, during the process of the traction member 50 moving toward the proximal end relative to the outer tube 10, the axial dimension of the bearing members 21 located on both sides of the traction member 50 decreases, and the radial dimension increases, and the four third bearing rods 215 located around the traction member 50 are in an X-shape, that is, the axial dimension of the four third bearing rods 215 around the traction member 50 shrinks as the traction member 50 moves toward the proximal end, and at the same time, the radial dimension of the third bearing rods 215 increases, so that the projection of the four third bearing rods 215 on the plane perpendicular to the axis of the traction member 50 is in an X-shape, so that pulmonary vein ablation isolation can be performed. The traction member 50 also has a bending adjustment function, and the traction member 50 has a certain flexibility. The part of the traction member 50 extending out of the outer tube 10 can be bent relative to the axis of the outer tube 10, that is, the traction member 50 bends to one side, so that the four third bearing rods 215 located around the traction member 50 undergo linear deformation, so as to better fit the tissue shape where the target ablation area is located, which can improve the ablation effect and reduce the number of ablations.

[0085] It should be noted that, in the absence of conflict, the embodiments and features in the embodiments of the present application can be combined with each other, and any combination of features in different embodiments is also within the scope of protection of the present application. In other words, the multiple embodiments described above can also be arbitrarily combined according to actual needs. It should be noted that all the above-mentioned drawings are exemplary illustrations of the present application and do not represent the actual size of the product. And the dimensional ratio relationship between the components in the drawings is not intended to limit the actual product of the present application. The description of the above embodiments is only used to help understand the method and core idea of ​​the present application. The scope of protection of the present application is not limited to this. Any technician familiar with the art can easily think of changes or replacements within the technical scope disclosed in the present application, which should be covered within the scope of protection of the present application. In summary, the content of this specification should not be understood as a limitation on the present application.

Claims

1. An ablation catheter, characterized in that: include: External pipe; A bearing frame is disposed at the distal end of the outer tube and is a radially contractible and expandable stent structure. The bearing frame includes a plurality of bearing members, which are arranged around the axis of the outer tube at circumferential intervals. The outer surface of each bearing member forms a linear abutment surface for abutting against the target ablation area to perform linear ablation. The first ablation component is correspondingly arranged on the bearing member, and the first ablation component is used to connect to an external energy source to transmit the ablation energy output by the external energy source to the target ablation area.

2. The ablation catheter according to claim 1, characterized in that: Each of the bearing components includes a plurality of bearing rods arranged at intervals in the circumferential direction, the outer surfaces of the plurality of bearing rods form the linear abutment surface, and the first ablation element is correspondingly arranged on the bearing rods.

3. The ablation catheter according to claim 2, characterized in that: The ablation catheter also includes an axially arranged support frame, the support frame is connected to the support frame at one end axially facing the support frame, the support frame is combined together at one end axially away from the support frame, and the support frame is combined together at one end axially away from the support frame; the support frame is used to connect multiple support rods to prevent the multiple support rods from positional displacement.

4. The ablation catheter according to claim 3, characterized in that: The support frame includes a plurality of first main rods and a plurality of first branch rods circumferentially distributed around the axial center line of the outer tube, the plurality of first main rods are combined together at one end away from the bearing frame, and each of the first main rods is connected to a plurality of first branch rods at one end facing the bearing frame; each of the bearing members includes at least one first bearing rod and at least one second bearing rod arranged at circumferential intervals; the first bearing rod is connected to a corresponding plurality of first branch rods at one end facing the support frame, the other ends of the plurality of first branch rods connected to the same first bearing rod are connected to different first main rods, and the second bearing rod is connected to a corresponding first main rod at one end facing the support frame.

5. The ablation catheter according to claim 4, characterized in that: Each of the bearing components includes two first bearing rods arranged at a circumferential interval and one second bearing rod located between the two first bearing rods, and each of the first main rods is connected to two first branch rods at one end facing the bearing frame, the other ends of the two first branch rods connected to the same first main rod extend in directions away from each other, and two adjacent first branch rods connected to different first main rods are connected to the same first bearing rod.

6. The ablation catheter according to claim 5, characterized in that: Two adjacent first main rods, one of which is connected to two first branch rods, form a first angle, while the other of which is connected to two first branch rods, form a second angle. The first angle is smaller than the second angle, and one end of the second bearing rod facing the support frame is connected to the first main rod corresponding to the first angle.

7. The ablation catheter according to claim 3, characterized in that: The support frame includes a plurality of second main rods, a plurality of second branch rods and a plurality of connecting rods which are circumferentially distributed around the axial center line of the outer tube, and the plurality of second main rods and the plurality of connecting rods are combined together at one end away from the bearing frame; two second branch rods are connected to one end of each second main rod facing the bearing frame, and two second branch rods connected to the same second main rod are respectively connected to one connecting rod at one end facing the bearing frame; each of the bearing components includes two third bearing rods spaced apart along the circumferential direction, and the third bearing rods are connected to the corresponding second branch rods and the connecting rods at one end facing the support frame.

8. The ablation catheter according to claim 4, characterized in that: At least one of the first ablation components is disposed on the second supporting rod, and the support frame and the plurality of the first supporting rods form a conductive skeleton with conductivity, and the conductive skeleton is connected to one pole of the external energy source, and at least one of the first ablation components is connected to the other pole of the external energy source to form an electric field for transmitting ablation energy to the target ablation area.

9. The ablation catheter according to claim 8, characterized in that: The ablation catheter also includes a head electrode. When the carrying frame is arranged at the distal end relative to the supporting frame, the head electrode is arranged at the farthest end of the carrying frame; when the supporting frame is arranged at the distal end relative to the carrying frame, the head electrode is arranged at the farthest end of the supporting frame; the head electrode is used for potential mapping and / or for pairing with the conductive skeleton and at least one of the first ablation components to connect with the external energy source to form an electric field.

10. The ablation catheter according to claim 8, characterized in that: When the carrying frame is arranged at the distal end relative to the supporting frame, the distal end surface of the carrying frame is an arc surface, and the distal end surface of the head electrode is tangent to the arc surface of the carrying frame; when the supporting frame is arranged at the distal end relative to the carrying frame, when the head electrode is arranged at the farthest end of the supporting frame, the distal end surface of the supporting frame is an arc surface, and the distal end surface of the head electrode is tangent to the arc surface of the supporting frame.

11. The ablation catheter according to claim 8, characterized in that: The first ablation component is an ablation electrode. Each of the second bearing rods is provided with a plurality of the ablation electrodes along its length direction. Among the plurality of the second bearing rods, the ablation electrodes correspond one to one along the axial direction and are arranged circumferentially at intervals around the axis of the bearing frame.

12. The ablation catheter according to claim 4 or 7, characterized in that: The ablation catheter also includes a traction member, which is coaxially arranged in the outer tube, and the distal end of the traction member extends out of the distal end of the outer tube; when the bearing frame is arranged at the distal end relative to the support frame, the distal end of the traction member is connected to the distal end of the bearing frame, and the proximal end of the support frame is connected to the distal end of the outer tube; when the support frame is arranged at the distal end relative to the bearing frame, the distal end of the traction member is connected to the distal end of the support frame, and the proximal end of the bearing frame is connected to the distal end of the outer tube.

13. The ablation catheter according to claim 12, characterized in that: The traction member is slidably arranged in the outer tube along the axial direction, so that the traction member can move axially relative to the outer tube; during the axial movement of the traction member relative to the outer tube, the bearing frame and the support frame shrink or expand radially.

14. The ablation catheter according to claim 12, characterized in that: A positioning sensor is arranged in the traction member, and the positioning sensor is used to establish the motion trajectory of the ablation catheter and to establish a three-dimensional model of the target ablation area.

15. The ablation catheter according to claim 12, characterized in that: The traction member is provided with a plurality of second ablation members, which are spaced apart along the axial direction of the traction member. The second ablation members are used to be paired with at least one of the first ablation members and connected with the external energy source to form an electric field.

16. The ablation catheter according to claim 15, characterized in that: When any one of the load-bearing members is abutted against the target ablation area for linear ablation, the first ablation member on the abutted load-bearing member is connected to one pole of the external energy source, and the first ablation member on the adjacent load-bearing member and multiple second ablation members on the traction member are commonly connected to the other pole of the external energy source to form an electric field for transmitting ablation energy to the target ablation area.

17. The ablation catheter according to claim 15, characterized in that: When the bearing member includes two third bearing rods spaced circumferentially, the number of the bearing members is two, the two bearing members are located on both sides of the traction member, and at least one of the first ablation members is paired with the second ablation member to form an electric field for ablation, and the ablation area obtained by ablation is a planar area.

18. The ablation catheter according to claim 15, characterized in that: When the bearing component includes two third bearing rods arranged at intervals along the circumferential direction, each of the third bearing rods is provided with a plurality of the first ablation components, the plurality of the first ablation components are arranged at intervals along the length direction of the third bearing rod, and the plurality of first ablation components on two adjacent third bearing rods are staggered from each other along the axial direction.

19. The ablation catheter according to claim 17, characterized in that: The traction member has a bending adjustment function. When the traction member is bent to one side, the two third bearing rods located on the other side of the traction member undergo linear deformation.

20. The ablation catheter according to claim 17, characterized in that: The traction member can move axially relative to the outer tube. During the movement of the traction member toward the proximal end relative to the outer tube, the axial size of the bearing components located on both sides of the traction member becomes smaller and the radial size becomes larger, and the four third bearing rods located around the traction member are in an X shape.

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