Varicosity ablation catheter

Abstract

The utility model provides a varicosity ablation catheter. The varicosity ablation catheter comprises a radiation generation assembly, a matching piece, an insulating medium and a coaxial cable. The matching piece is arranged on one side of the radiation generation assembly; the insulating medium is arranged between the radiation generation assembly and the insulating medium; the coaxial cable penetrates through the radiation generation assembly, the matching piece and the insulating medium; wherein the radiation generating assembly is connected with the coaxial cable, the matching piece is connected with the coaxial cable, and the insulating medium is movably connected with the coaxial cable. The microwave ablation catheter solves the problems that in the prior art, the radiation end of a microwave ablation catheter is not prone to bending, the passing ability of the catheter is greatly limited, and the ablation area is shortened.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and more specifically, to a varicose vein ablation catheter. Background Technology

[0002] A varicose vein ablation catheter is an interventional treatment device for varicose veins. It is inserted through a catheter channel to reach the varicose veins and uses energy such as radiofrequency, microwave or laser to heat and ablate the inner wall of the vein, thereby causing the vein to contract, close, redistribute blood flow and reduce blood supply, thus achieving the therapeutic goal of curing varicose veins.

[0003] Currently, there are two main types of ablation catheters available for the treatment of varicose veins: radiofrequency ablation catheters and microwave ablation catheters.

[0004] Radiofrequency ablation catheters have become the mainstream in the market. Their advantages include ultra-flexibility, allowing passage through blood vessels at smaller angles, and a long ablation area, capable of achieving an ablation area of ​​5cm or longer in a single session. However, their disadvantages include a longer ablation time per session, generally requiring more than 20 seconds, and the need to use skin electrodes.

[0005] Microwave ablation catheters offer the advantages of rapid ablation and eliminate the need for skin electrodes. However, they suffer from a short ablation zone, making them less suitable for cavities with small angles. The main issue lies in the radiating end's sheath structure, typically composed of interlocking metal and plastic materials. This solid material results in high rigidity, making the radiating end difficult to bend and unable to return to its original shape once bent. Consequently, its bending performance is relatively poor. Improving the bending performance of the radiating end usually involves shortening the radiating head, but this shortens the ablation zone. Therefore, current microwave ablation catheters often sacrifice a certain amount of ablation zone length to maintain a certain level of bending performance.

[0006] There is currently no effective solution to the above problems. Utility Model Content

[0007] The main objective of this invention is to provide a varicose vein ablation catheter to solve the problem that the radiating end of the microwave ablation catheter in the prior art is not easy to bend, which greatly restricts the passage of the catheter and shortens the ablation area.

[0008] To achieve the above objectives, according to one aspect of the present invention, a varicose vein ablation catheter is provided, comprising: a radiation generating assembly; a mating component disposed on one side of the radiation generating assembly; an insulating medium disposed between the radiation generating assembly and the mating component; and a coaxial cable passing through the radiation generating assembly, the mating component, and the insulating medium; wherein the radiation generating assembly is connected to the coaxial cable, the mating component is connected to the coaxial cable, and the insulating medium is movably connected to the coaxial cable.

[0009] Furthermore, the included angle formed by one end of the insulating medium relative to the axis of the mating component can be adjusted.

[0010] Furthermore, the mating part is a bushing, and the mating part is fixedly connected to the coaxial cable.

[0011] Furthermore, a first clearance gap is formed between the first end of the insulating medium and the radiation generating component, and a second clearance gap is formed between the second end of the insulating medium and the mating component.

[0012] Furthermore, the radiation generating assembly includes a radiation head, which is fixedly connected to a coaxial cable.

[0013] Furthermore, the radiation generating assembly also includes a radiation ring and a dielectric ring. The radiation ring is located between the radiation head and the insulating dielectric. The radiation ring is fixedly connected to the coaxial cable, and the dielectric ring is movably connected to the coaxial cable. The coaxial cable passes through the radiation ring and the dielectric ring.

[0014] Furthermore, there are multiple radiating rings, which are spaced apart along the axial direction of the coaxial cable. Each radiating ring is located between the radiating head and the insulating medium, and a dielectric ring is provided between adjacent radiating rings and / or between a radiating ring and the radiating head.

[0015] Furthermore, a third clearance gap is formed between the end of the dielectric ring along the axial direction of the coaxial cable and the adjacent radiating ring and / or adjacent radiating head.

[0016] Furthermore, at least one end of the dielectric ring along the axial direction of the coaxial cable is formed with a first curved surface structure; a radiating head disposed adjacent to the first curved surface structure, and / or a radiating ring disposed adjacent to the first curved surface structure is provided with a second curved surface structure; the first curved surface structure and the second curved surface structure are adapted to form a third clearance gap between the dielectric ring and the adjacent radiating ring, and / or between the dielectric ring and the adjacent radiating head.

[0017] Furthermore, the insulating medium has a third curved surface structure formed at at least one end along the axial direction of the coaxial cable; a radial ring is disposed adjacent to the third curved surface structure, and / or a mating member is disposed adjacent to the third curved surface structure with a fourth curved surface structure; the third curved surface structure and the fourth curved surface structure are adapted to form a first clearance gap between the radial ring and the adjacent radial ring, and / or to form a second clearance gap between the radial ring and the adjacent mating member.

[0018] Furthermore, the varicose vein ablation catheter also includes: a sheath covering the outside of the radiating ring, the dielectric ring, the insulating medium, the radiating head, and the mating parts.

[0019] Furthermore, the varicose vein ablation catheter also includes: a flexible catheter, the first end of which is disposed between the inner surface of the covering sheath and the outer peripheral surface of the mating component, the second end of which extends away from the mating component, and a catheter channel is formed in the second end of the flexible catheter, with the end of the coaxial cable away from the radiating head extending and arranged in the catheter channel.

[0020] Furthermore, the varicose vein ablation catheter also includes a water-circulating inner tube, which is located inside the catheter channel and positioned outside the coaxial cable to perform cooling operations on the coaxial cable.

[0021] By applying the technical solution of this utility model, and through optimizing the connection method between the radiation generating component and the coaxial cable, introducing a movable insulating medium, and adding a mating component on one side of the radiation generating component, a dual breakthrough in catheter flexibility and ablation efficiency is achieved. The radiation generating component is directly connected to the coaxial cable, ensuring efficient microwave energy transmission; the addition of the mating component not only stabilizes the catheter structure but also enhances the overall maneuverability of the catheter through its connection with the coaxial cable. The movable connection design between the insulating medium and the coaxial cable allows for free adjustment between components when the catheter passes through curved blood vessels, significantly improving the catheter's bending performance. This application solves the problem in the prior art where the radiating end of the microwave ablation catheter is difficult to bend, resulting in greatly limited catheter passage and a shortened ablation area. Attached Figure Description

[0022] The accompanying drawings, which form part of this application, are used to provide a further understanding of the present invention. The illustrative embodiments of the present invention and their descriptions are used to explain the present invention and do not constitute an undue limitation of the present invention. In the drawings:

[0023] Figure 1 A schematic diagram of the structure of a first embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0024] Figure 2 A schematic diagram of the structure of a second embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0025] Figure 3 A schematic diagram of the structure of a third embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0026] Figure 4 A schematic diagram of the fourth embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0027] Figure 5 A schematic diagram of the fifth embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0028] Figure 6 A schematic diagram of the sixth embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0029] Figure 7 A schematic diagram of the radiation field according to an embodiment of a conventional ablation catheter is shown;

[0030] Figure 8 A schematic diagram of the radiation field of an embodiment of the varicose vein ablation catheter according to the present invention is shown;

[0031] Figure 9 A schematic diagram of a seventh embodiment of the varicose vein ablation catheter according to the present invention is shown.

[0032] The above figures include the following reference numerals:

[0033] 1. Radial end section; 2. Conduit section; 3. Handle section; 4. Cooling water pipe section;

[0034] 101. Radiation head; 102. Dielectric ring; 103. Radiation ring; 104. Insulating medium; 105. Fitting parts; 106. Sheath; 107. Coaxial cable; 108. Water circulation inner pipe; 109. Flexible conduit. Detailed Implementation

[0035] It should be noted that, unless otherwise specified, the embodiments and features described in this application can be combined with each other. The present invention will now be described in detail with reference to the accompanying drawings and embodiments.

[0036] It should be noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the exemplary embodiments according to this application. As used herein, the singular form is intended to include the plural form as well, unless the context clearly indicates otherwise. Furthermore, it should be understood that when the terms "comprising" and / or "including" are used in this specification, they indicate the presence of features, steps, operations, devices, components, and / or combinations thereof.

[0037] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such terms can be used interchangeably where appropriate so that the embodiments of this application described herein can be implemented, for example, in orders other than those illustrated or described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover a non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or apparatus.

[0038] Exemplary embodiments according to this application will now be described in more detail with reference to the accompanying drawings. However, these exemplary embodiments may be implemented in many different forms and should not be construed as being limited to the embodiments set forth herein. It should be understood that these embodiments are provided so that the disclosure of this application is thorough and complete, and that the concept of these exemplary embodiments is fully conveyed to those skilled in the art. In the drawings, for clarity, the thickness of layers and regions may be exaggerated, and the same reference numerals are used to denote the same devices, and therefore their description will be omitted.

[0039] Combination Figures 1 to 6 , Figures 8 to 9 As shown in the specific embodiment of this application, a varicose vein ablation catheter is provided.

[0040] Specifically, the varicose vein ablation catheter includes: a radiation generating component, a mating part 105, an insulating medium 104, and a coaxial cable 107. The mating part 105 is disposed on one side of the radiation generating component; the insulating medium 104 is disposed between the radiation generating component and the mating part 105; the coaxial cable 107 passes through the radiation generating component, the mating part 105, and the insulating medium 104; wherein, the radiation generating component is connected to the coaxial cable 107, the mating part 105 is connected to the coaxial cable 107, and the insulating medium 104 is movably connected to the coaxial cable 107.

[0041] By applying the technical solution of this utility model, and optimizing the connection method between the radiation generating component and the coaxial cable 107, introducing a movable insulating medium 104, and adding a mating component 105 on one side of the radiation generating component, a dual breakthrough in catheter flexibility and ablation efficiency is achieved. The radiation generating component is directly connected to the coaxial cable 107, ensuring efficient transmission of microwave energy; the addition of the mating component 105 not only stabilizes the catheter structure but also enhances the overall maneuverability of the catheter through its connection with the coaxial cable 107. The movable connection design between the insulating medium 104 and the coaxial cable 107 allows for free adjustment between components when the catheter passes through curved blood vessels, significantly improving the catheter's bending performance. This application solves the problem in the prior art where the radiation end of the microwave ablation catheter is not easy to bend, which greatly limits the catheter's passage and shortens the ablation area.

[0042] Furthermore, the angle formed by one end of the insulating medium 104 relative to the axis of the mating member 105 is adjustable. This design allows the catheter to bend more flexibly when encountering complex vascular pathways, improving the convenience and success rate of surgical procedures.

[0043] Specifically, the mating component 105 is a bushing, and it is fixedly connected to the coaxial cable 107. Using a bushing as the mating component 105 not only enhances the stability of the coaxial cable 107 and the overall structural strength of the catheter, but also ensures high-precision energy transmission even when ablation is performed in hard-to-reach areas such as deep veins. This design significantly improves energy transfer efficiency and reduces energy loss during surgery, thereby shortening the treatment time.

[0044] like Figure 1 As shown, in this embodiment, the fixed connection between the mating component 105 and the coaxial cable 107 is achieved through a welding process. Specifically, the mating component 105 is tightly fitted onto the outer layer of the coaxial cable 107 and welded at specific locations to ensure a stable connection between the two. Welding ensures a stable connection between the mating component 105 and the coaxial cable 107, preventing loosening or detachment due to mechanical stress or vibration during use, thereby ensuring the structural stability and signal transmission continuity of the ablation catheter during operation. Welding also provides a good sealing effect, preventing cooling water or other liquids from seeping in from the connection point, interfering with microwave energy transmission or damaging internal circuitry, ensuring the waterproof performance and electrical isolation of the catheter's interior.

[0045] Furthermore, a first clearance gap is formed between the first end of the insulating medium 104 and the radiation generating component, and a second clearance gap is formed between the second end of the insulating medium 104 and the mating component 105.

[0046] like Figure 3As shown, the length and diameter of the insulating medium 104 are precisely designed and machined to ensure that when assembled between the radiation generating assembly and the mating component 105, the two ends of the insulating medium 104 do not come into close contact with the radiation generating assembly and the mating component 105, but rather leave small gaps, forming a first clearance gap and a second clearance gap. The existence of the first clearance gap and the second clearance gap allows the components to bend and deform freely when encountering tortuous blood vessels, without limiting their bending performance due to rigid contact between the insulating medium 104 and other components. This significantly improves the maneuverability of the catheter in complex vascular pathways.

[0047] Furthermore, the radiation generating assembly includes a radiation head 101, which is fixedly connected to a coaxial cable 107. The fixed connection of the radiation head 101 ensures the high efficiency and stability of energy transmission, thereby improving the ablation effect.

[0048] The radiating head 101 is typically made of highly conductive materials such as brass or stainless steel to ensure efficient microwave energy transmission. Its internal structure is designed to optimize energy distribution for optimal ablation results. The tip of the radiating head may be designed with a sharp or rounded shape to adapt to different vascular environments.

[0049] The coaxial cable 107 serves as the microwave energy transmission channel, with one end fixedly connected to the radiator head 101 by welding. The fixed connection point is typically where the center conductor of the coaxial cable is connected to the internal conductive structure of the radiator head 101, enabling lossless transmission of microwave energy from the coaxial cable to the radiator head.

[0050] Furthermore, the radiation generating assembly also includes a radiation ring 103 and a dielectric ring 102. The radiation ring 103 is located between the radiation head 101 and the insulating dielectric 104. The radiation ring 103 is fixedly connected to the coaxial cable 107, and the dielectric ring 102 is movably connected to the coaxial cable 107. The coaxial cable 107 passes through the radiation ring 103 and the dielectric ring 102. The combined use of the radiation ring and the dielectric ring not only enables precise control of energy release but also protects the coaxial cable from thermal damage and extends the service life of the conduit.

[0051] The radiation ring 103 is located between the radiation head 101 and the insulating medium 104. Its function is to diffuse and regulate the microwave energy transmitted from the coaxial cable. When microwave energy is transmitted from the coaxial cable 107 to the radiation head 101, the radiation ring 103 helps to evenly diffuse the concentrated energy to a wider area, thereby increasing the length and range of ablation and improving the treatment effect. The radiation ring 103 is directly fixed to the outer conductor of the coaxial cable 107 through a welding process. This fixed connection ensures the stability and continuity of microwave energy during transmission from the coaxial cable to the radiation ring 103. This connection method helps to reduce energy loss during transmission, ensures sufficient energy for the ablation process, and improves ablation efficiency.

[0052] The media ring 102 is movably connected to the coaxial cable 107, allowing the media ring 102 to slide relative to the coaxial cable 107 when the catheter is bent, reducing friction and rigidity between components, thereby improving the overall bending performance and adaptability of the catheter to complex vascular structures.

[0053] The dielectric ring 102 is mainly made of insulating materials, such as ceramics and PTFE (polytetrafluoroethylene). It serves to isolate the coaxial cable 107 from the radiating ring 103 and the radiating head 101, preventing current from directly passing through these conductive components and ensuring the electrical safety and stability inside the conduit. The dielectric ring 102 also has good temperature resistance and heat dissipation, absorbing the heat generated during the ablation process and promoting the uniform distribution and dissipation of heat, thus avoiding overheating damage to the internal structure of the conduit and surrounding tissues.

[0054] The coaxial cable 107 serves as both a microwave energy transmission channel and a supporting structure for the radiation ring 103 and the dielectric ring 102. The central conductor of the coaxial cable 107 transmits microwave energy, while the outer conductor connects to components such as the radiation ring 103, forming a stable energy transmission path. The coaxial cable 107 is threaded through the center of the radiation ring 103 and the dielectric ring 102, ensuring proper alignment between components and efficient energy transmission.

[0055] Specifically, there are multiple radiation rings 103, which are spaced apart along the axial direction of the coaxial cable 107. Each radiation ring is located between the radiation head 101 and the insulating medium 104. A medium ring 102 is provided between adjacent radiation rings 103 and / or between a radiation ring 103 and the radiation head 101.

[0056] By spaced multiple radiation rings 103 on the coaxial cable 107, the total ablation length can be significantly increased, allowing microwave energy to be uniformly diffused along a longer axis, thus forming a longer ablation zone. Each radiation ring 103 can independently radiate energy outward, ensuring continuous and uniform microwave ablation of the entire diseased blood vessel segment, thereby improving the reliability and consistency of the ablation effect.

[0057] A media ring 102 is provided between adjacent radiating rings 103 and / or between radiating ring 103 and radiating head 101. This provides the necessary flexibility for the catheter. Because the media rings 102 are movably connected to the coaxial cable 107, they can move freely as the catheter bends, reducing rigid contact between components and making the catheter easier to bend when encountering complex vascular pathways, thus improving the flexibility and comfort of surgical procedures.

[0058] like Figure 2 As shown, this embodiment sets two radiation rings 103 and two dielectric rings 102. More dielectric rings 102 and radiation rings 103 can be added according to actual needs.

[0059] Specifically, a third clearance gap is formed between the end of the dielectric ring 102 along the axial direction of the coaxial cable 107 and the adjacent radiating ring 103 and / or the adjacent radiating head 101.

[0060] The dielectric ring 102 is typically made of an insulating material with a certain degree of elasticity and compressibility, such as PTFE (polytetrafluoroethylene) or FEP (fluorinated ethylene propylene copolymer). These materials can deform under slight pressure, thus naturally forming a third clearance gap during assembly. During assembly, the dielectric ring 102 is fitted onto the coaxial cable 107, but is not fixedly connected to the coaxial cable, the radiating ring 103, or the radiating head 101. This movable assembly method ensures that the dielectric ring 102 can move relative to the cable when bent or deformed, maintaining the integrity of the third clearance gap.

[0061] like Figure 4 As shown, the third clearance gap allows the media ring 102 to slide freely when the catheter bends, reducing the mechanical stress between the media ring 102 and the radiating ring 103 or radiating head 101. This improves the overall flexibility and bending performance of the catheter, enabling it to pass more smoothly when encountering curved blood vessels. The third clearance gap can achieve a certain bending angle (e.g., 15°), the specific bending angle of which is determined according to the actual situation. After bending, the third clearance gap becomes smaller on the side closer to the bend and larger on the side farther away. The heat generated during ablation can be dissipated more effectively through the third clearance gap, avoiding heat accumulation caused by close contact of components and protecting the internal structure of the catheter and surrounding tissues from thermal damage.

[0062] Because there is a gap between the medium ring 102 and the radiation ring 103 or the radiation head 101, if the medium ring 102 is damaged during use, it can be replaced relatively easily without affecting the structure and performance of the entire conduit.

[0063] Furthermore, at least one end of the dielectric ring 102 along the axial direction of the coaxial cable 107 is formed with a first curved surface structure; the radiating head 101 and / or the radiating ring 103 adjacent to the first curved surface structure are provided with a second curved surface structure; the first curved surface structure and the second curved surface structure are adapted to form a third clearance gap between the dielectric ring 102 and the adjacent radiating ring 103, and / or between the dielectric ring 102 and the adjacent radiating head 101.

[0064] Compared to planar structures, curved structures adapt to deformation more easily when encountering bends, reducing friction and rigid contact between components. When the catheter bends, the first curved structure formed at the end of the media ring 102 and the second curved structure adjacent to the radiating head 101 or radiating ring 103 can move relatively more smoothly, reducing mechanical stress inside the catheter. This significantly improves the catheter's bending performance when passing through curved or narrow blood vessels, allowing the ablation catheter to be operated more flexibly and reach complex lesion sites.

[0065] Furthermore, the second curved surface structure can improve the transmission and diffusion of microwave energy between the radiating head 101 and the radiating ring 103. The reflection and diffraction characteristics of microwaves on the curved surface help to distribute energy more evenly and avoid excessive local energy concentration. This not only increases the length and uniformity of the ablation zone, but also reduces the risk of thermal damage to surrounding healthy tissues.

[0066] By adapting the first curved surface structure to the second curved surface structure to form a stable third clearance gap, the need for precise fixing between components is reduced, the assembly process is simplified, the manufacturing difficulty and cost are reduced, and the production efficiency and quality consistency of the conduit are improved.

[0067] Furthermore, the insulating medium 104 has a third curved surface structure formed at at least one end along the axial direction of the coaxial cable 107; the radial ring 103 is disposed adjacent to the third curved surface structure, and / or the mating member 105 is disposed adjacent to the third curved surface structure and has a fourth curved surface structure; the third curved surface structure and the fourth curved surface structure are adapted to form a first clearance gap between the radial ring 103 and the adjacent radial ring 103, and / or form a second clearance gap between the radial ring 103 and the adjacent mating member 105.

[0068] The adaptive design between the third and fourth curved surface structures allows for the natural formation of a small first or second clearance gap between the insulating medium 104 and the radial ring 103, or between the insulating medium 104 and the mating part 105, during assembly. For example... Figure 6As shown, the presence of these gaps allows for minute relative movement between components, especially when the catheter is bent or encounters external forces, thereby reducing the catheter's rigidity and enhancing its bending performance. Compared to conventional catheter structures, the catheter structure in this embodiment can smoothly pass through smaller and more curved lumens. Figure 5 The diagram shows the structure of a traditional catheter, which cannot bend when encountering small bends, thus limiting the ablation area.

[0069] Furthermore, the varicose vein ablation catheter also includes a sheath 106, which covers the outer side of the radiating ring 103, the dielectric ring 102, the insulating medium 104, the radiating head 101, and the mating component 105. The introduction of the sheath 106 not only provides an additional protective layer for the catheter, reducing the impact of external environmental factors such as pressure and friction on the internal structure of the catheter, but also improves the durability and safety of the catheter in complex environments.

[0070] Specifically, a polymer material with good temperature resistance and some elasticity and non-stick properties can be selected as the covering sleeve 106, such as PTFE or FEP. The temperature resistance of the covering sleeve 106 helps to reduce the conduction of heat generated during the ablation process to the outside, protecting the tissue around the catheter from thermal damage. PTFE and FEP materials have moderate elasticity, which allows the covering sleeve 106 to deform with the bending of the catheter, and at the same time, it can return to its original shape after bending, improving the flexibility and durability of the catheter.

[0071] Optionally, the sealing design of the sheath 106 ensures that tissue fluid does not flow into the gaps of the radiation generating components during use, while also protecting the electronic components inside the catheter from the effects of a humid environment.

[0072] Furthermore, the varicose vein ablation catheter also includes: a flexible catheter 109, the first end of which is disposed between the inner surface of the covering sleeve 106 and the outer peripheral surface of the mating member 105, the second end of which extends away from the mating member 105, and a catheter channel is formed in the second end of the flexible catheter 109, with one end of the coaxial cable 107 away from the radiating head 101 extending into the catheter channel.

[0073] The first end of the flexible catheter 109 is positioned between the inner surface of the sheath 106 and the outer peripheral surface of the mating component 105, forming a nested structure. This structure not only ensures the tight assembly of all internal components but also allows for a certain degree of freedom of movement to adapt to different curvatures and pressure environments within the blood vessel. The flexible catheter 109 also achieves a seal on the internal structure of the catheter, preventing leakage of coolant or tissue fluid.

[0074] A conduit channel is formed within the second end of the flexible conduit 109, and the end of the coaxial cable 107 furthest from the radiating head 101 extends into the conduit channel. The conduit channel of the flexible conduit 109 not only provides a transmission path for the coaxial cable 107 but also serves as a coolant delivery channel. The coolant circulates through the conduit channel, carrying away the heat generated by ablation and ensuring that the temperature within the ablation area is controlled within a safe and effective range.

[0075] Furthermore, the varicose vein ablation catheter also includes a water-circulating inner tube 108, which is located within the catheter channel and positioned outside the coaxial cable 107 to perform cooling operations on the coaxial cable 107. Through continuous cooling, the temperature of the coaxial cable is effectively controlled during high energy output.

[0076] During ablation, the coaxial cable 107 transmits high-energy microwaves, generating significant heat in the cable itself and surrounding area. Without timely cooling, excessively high temperatures can damage the coaxial cable, as well as the patient's blood vessel walls and surrounding tissues, potentially leading to complications. Cooling water continuously flows within the water-circulating inner tube 108, positioned outside the coaxial cable 107. The heat generated during ablation is transferred through the coaxial cable 107 to the wall of the water-circulating inner tube 108, where it is absorbed by the cooling water. The cooled water continues to flow within the water-circulating inner tube 108 and eventually exits the catheter. The water-circulating inner tube 108 ensures that the coaxial cable 107 remains at its optimal operating temperature, reducing thermal damage, extending catheter lifespan, lowering surgical risks, and improving the safety and efficiency of treatment.

[0077] It needs to be further explained that, Figure 7 The radiation field of a traditional ablation catheter. Figure 8 The radiation field of the ablation catheter with the improved structure of this scheme can be clearly seen. Under the same operating parameters, the added dielectric ring 102 and radiation ring 103 can diffuse microwave radiation, making its radiation field longer. This results in a larger ablation area than the traditional structure.

[0078] It needs to be further explained that, such as Figure 9 As shown, the microwave catheter for varicose veins mainly consists of four parts: radiating end part 1, catheter part 2, handle part 3, and cooling water pipe part 4.

[0079] The radiating end portion 1 contains key components such as the radiating head 101, dielectric ring 102, radiating ring 103, and insulating dielectric 104. These components are connected to the handle portion 3 via a coaxial cable 107. During ablation, the handle portion 3 transmits microwave energy to the radiating end portion 1 via the coaxial cable 107. The design of the radiating ring 103 and dielectric ring 102 inside the radiating end portion 1 facilitates uniform energy diffusion, allowing the microwave energy to form a relatively long ablation zone within the diseased blood vessel.

[0080] The conduit section 2 is a long tube connecting the radiating end section 1 and the handle section 3, and is mainly made of flexible conduit materials such as PTFE or FEP. It not only provides a physical path for the transmission of microwave energy, but also houses the water circulation inner tube 108 and the coaxial cable 107.

[0081] Handle section 3 is the interface for the operator to interact with the catheter. It typically includes devices for controlling microwave energy output, a monitoring system, and an interface for connecting to an external microwave generator. The operator can control the intensity and duration of microwave energy through the handle, monitor temperature and pressure during the ablation process, and ensure the safety and effectiveness of the treatment.

[0082] Cooling water pipe section 4 is the internal circulation system of the conduit, used to remove the heat generated during ablation and prevent overheating of the coaxial cable and surrounding tissue. Coolant (usually water) enters from the handle section, circulates through the cooling water pipes within the radiating end section 1 and the conduit section, carries away heat, and then exits from the other end.

[0083] As can be seen from the above description, the embodiments of this utility model achieve the following technical effects:

[0084] By optimizing the structural design of the radiation generating component, introducing a media ring and a radiation ring, and forming a first and second clearance gap between the components, this invention significantly improves the bending performance of the varicose vein ablation catheter, making it easier to pass through complex vascular pathways, including tortuous and narrow vascular lumens, thereby expanding its applicability and treatment flexibility. The added media ring and radiation ring not only improve the catheter's bending performance but also extend the ablation radiation area, enabling the ablation of a longer distance of diseased blood vessels within the same timeframe, shortening the operation time, improving surgical efficiency, and providing patients with a more comprehensive treatment outcome.

[0085] For ease of description, spatial relative terms such as "above," "on top of," "on the upper surface of," "above," etc., are used herein to describe the spatial positional relationship of a device or feature as shown in the figures to other devices or features. It should be understood that spatial relative terms are intended to encompass different orientations in use or operation beyond the orientation of the device as described in the figures. For example, if the device in the figures were inverted, a device described as "above" or "on top of" other devices or structures would subsequently be positioned as "below" or "under" other devices or structures. Thus, the exemplary term "above" can include both "above" and "below." The device may also be positioned in other different ways (rotated 90 degrees or in other orientations), and the spatial relative descriptions used herein will be interpreted accordingly.

[0086] In addition to the above, it should be noted that the terms "one embodiment," "another embodiment," and "embodiment" used in this specification refer to specific features, structures, or characteristics described in connection with that embodiment, which are included in at least one embodiment described in the general description of this application. The appearance of the same expression in multiple places in the specification does not necessarily refer to the same embodiment. Furthermore, when a specific feature, structure, or characteristic is described in connection with any embodiment, the intention is to suggest that implementing such a feature, structure, or characteristic in conjunction with other embodiments also falls within the scope of this utility model.

[0087] In the above embodiments, the descriptions of each embodiment have different focuses. For parts not described in detail in a certain embodiment, please refer to the relevant descriptions in other embodiments.

[0088] The above description is merely a preferred embodiment of this utility model and is not intended to limit the utility model. Various modifications and variations can be made to this utility model by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this utility model should be included within the protection scope of this utility model.

Claims

1. A varicose vein ablation catheter, characterized in that, include: Radiation generating components; A mating component (105) is disposed on one side of the radiation generating assembly; An insulating medium (104) is disposed between the radiation generating component and the mating component (105); Coaxial cable (107); the coaxial cable (107) is inserted into the radiation generating component, the mating component (105) and the insulating medium (104); The radiation generating component is connected to the coaxial cable (107), the mating part (105) is connected to the coaxial cable (107), and the insulating medium (104) is movably connected to the coaxial cable (107).

2. The varicose vein ablation catheter according to claim 1, characterized in that, The included angle formed by one end of the insulating medium (104) relative to the axis of the mating member (105) is adjustable.

3. The varicose vein ablation catheter according to claim 1, characterized in that, The mating part (105) is a bushing, and the mating part (105) is fixedly connected to the coaxial cable (107).

4. The varicose vein ablation catheter according to claim 1, characterized in that, A first clearance gap is formed between the first end of the insulating medium (104) and the radiation generating component, and a second clearance gap is formed between the second end of the insulating medium (104) and the mating member (105).

5. The varicose vein ablation catheter according to claim 4, characterized in that, The radiation generating assembly includes a radiation head (101) which is fixedly connected to the coaxial cable (107).

6. The varicose vein ablation catheter according to claim 5, characterized in that, The radiation generating assembly further includes a radiation ring (103) and a dielectric ring (102). The radiation ring (103) is located between the radiation head (101) and the insulating dielectric (104). The radiation ring (103) is fixedly connected to the coaxial cable (107), and the dielectric ring (102) is movably connected to the coaxial cable (107). The coaxial cable (107) passes through the radiation ring (103) and the dielectric ring (102).

7. The varicose vein ablation catheter according to claim 6, characterized in that, There are multiple radiation rings (103), which are spaced apart along the axial direction of the coaxial cable (107). Each radiation ring is located between the radiation head (101) and the insulating medium (104). A dielectric ring (102) is provided between adjacent radiation rings (103) and / or between a radiation ring (103) and the radiation head (101).

8. The varicose vein ablation catheter according to claim 7, characterized in that, The end of the dielectric ring (102) along the axial direction of the coaxial cable (107) forms a third clearance gap with the adjacent radiating ring (103) and / or the adjacent radiating head (101).

9. The varicose vein ablation catheter according to claim 8, characterized in that, The dielectric ring (102) has a first curved surface structure at at least one end along the axial direction of the coaxial cable (107); the radiating head (101) and / or the radiating ring (103) adjacent to the first curved surface structure are provided with a second curved surface structure; the first curved surface structure and the second curved surface structure are adapted to form the third clearance gap between the dielectric ring (102) and the adjacent radiating ring (103), and / or between the dielectric ring (102) and the adjacent radiating head (101).

10. The varicose vein ablation catheter according to claim 7, characterized in that, The insulating medium (104) has a third curved surface structure at at least one end along the axial direction of the coaxial cable (107); the radial ring (103) disposed adjacent to the third curved surface structure, and / or the mating member (105) disposed adjacent to the third curved surface structure, is provided with a fourth curved surface structure; the third curved surface structure and the fourth curved surface structure are adapted to form a first clearance gap between the radial ring (103) and the adjacent radial ring (103), and / or to form a second clearance gap between the radial ring (103) and the adjacent mating member (105).

11. The varicose vein ablation catheter according to claim 6, characterized in that, The varicose vein ablation catheter also includes: A covering sleeve (106) is used to cover the outside of the radiation ring (103), the dielectric ring (102), the insulating medium (104), the radiation head (101), and the mating part (105).

12. The varicose vein ablation catheter according to claim 11, characterized in that, The varicose vein ablation catheter also includes: A flexible conduit (109) is provided at its first end between the inner surface of the covering sleeve (106) and the outer peripheral surface of the mating member (105). The second end of the flexible conduit (109) extends away from the mating member (105). A conduit channel is formed in the second end of the flexible conduit (109). The coaxial cable (107) extends away from the radiating head (101) and is arranged in the conduit channel.

13. The varicose vein ablation catheter according to claim 12, characterized in that, The varicose vein ablation catheter also includes: A water circulation inner tube (108) is located inside the conduit channel and is disposed on the outside of the coaxial cable (107) to perform cooling operations on the coaxial cable (107).

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