Laser ablation catheter

Abstract

The application relates to the technical field of medical equipment, and provides a laser ablation catheter, which comprises a pipe body structure and an ablation structure, the pipe body structure comprises an outer pipe and an inner pipe arranged in the inner pipe, the ablation structure is arranged between the inner pipe and the outer pipe, and at least one ablation structure is arranged, the ablation structure comprises a first optical fiber and a second optical fiber connected to the distal end of the first optical fiber, the cross-sectional area of the second optical fiber is larger than that of the first optical fiber, the second optical fiber is used for expanding the outgoing light of the first optical fiber, and the lesion tissue is ablated through the expanded light. The laser ablation catheter can effectively reduce the number of ablation structures under the condition of achieving the same ablation effect, thereby effectively reducing the outer diameter size of the laser ablation catheter and effectively improving the pushing performance and passing performance of the laser ablation catheter.

Description

Technical Field

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

[0002] Currently, in the medical field, in order to treat lesions such as plaques in blood vessels, laser ablation catheters are usually used to transmit lasers to the lesions to ablate them and achieve the therapeutic goal.

[0003] In existing laser ablation catheters, multiple ablation fibers are usually integrated to ensure ablation efficiency. This inevitably results in a larger outer diameter of the laser ablation catheter, leading to poorer passage performance. Summary of the Invention

[0004] The purpose of this application is to provide a laser ablation catheter to solve the problem that in practical applications, existing laser ablation catheters usually integrate multiple ablation fibers, which inevitably leads to a large outer diameter of the laser ablation catheter, resulting in poor throughput.

[0005] To achieve the above objectives, the technical solution adopted in this application is: a laser ablation catheter, comprising:

[0006] The tube structure includes an outer tube and an inner tube disposed inside the outer tube;

[0007] An ablation structure is disposed between the inner tube and the outer tube, and at least one such structure is provided. The ablation structure includes a first optical fiber and a second optical fiber connected to the distal end of the first optical fiber. The cross-sectional area of ​​the second optical fiber is larger than that of the first optical fiber. The second optical fiber is used to expand the beam emitted from the first optical fiber and to ablate the lesion tissue via the expanded beam.

[0008] In one embodiment, a transition fiber segment is provided between the first optical fiber and the second optical fiber, and the radial dimension of the transition fiber segment is gradually increased in the direction close to the second optical fiber.

[0009] In one embodiment, the laser ablation catheter further includes an adjustment structure disposed between the inner tube and the outer tube, the adjustment structure being capable of bending the distal end of the tube structure and the distal end of the ablation structure.

[0010] In one embodiment, the laser ablation catheter further includes a first imaging component and a guiding structure, wherein the first imaging component is used for real-time imaging, and the guiding structure is used to guide the movement path of the catheter structure and the ablation structure;

[0011] The first imaging component and the guiding structure are both inserted into the inner tube. The first imaging component is relatively fixed relative to the inner tube and does not protrude from the distal end face of the first optical fiber.

[0012] Alternatively, the first imaging component and the guide structure may be alternately inserted into the inner tube.

[0013] In one embodiment, the first imaging component and the guiding structure are both inserted into the inner tube, and the inner tube is divided into a first cavity and a second cavity. The first imaging component is inserted into the first cavity, and the guiding structure is inserted into the second cavity.

[0014] In one embodiment, the centerline of the first lumen is offset from the centerline of the tube structure.

[0015] In one embodiment, the outer diameter of the inner tube is tapered towards the distal end.

[0016] In one embodiment, the first cavity does not protrude beyond the distal end face of the first optical fiber.

[0017] In one embodiment, the laser ablation catheter further includes at least one second imaging component disposed between the outer tube and the inner tube, the second imaging component not protruding from the distal end face of the first optical fiber, for real-time imaging;

[0018] When there are multiple second imaging components, the multiple second imaging components are arranged in a circular array.

[0019] In one embodiment, the laser ablation catheter further includes a mounting sleeve sleeved over each of the first optical fibers, and each of the second imaging components is respectively mounted on the outer periphery of the mounting sleeve;

[0020] When multiple second imaging components are provided, the mounting sleeve is a polygonal tube, and each second imaging component is respectively mounted on each side of the mounting sleeve.

[0021] In one embodiment, the second imaging component includes a chip connected to the side of the mounting sleeve opposite to the inner tube, and at least one ultrasonic transducer connected to and electrically connected to the chip on the side of the chip opposite to the mounting sleeve.

[0022] In one embodiment, multiple ultrasonic transducers are provided, and the multiple ultrasonic transducers are arranged at intervals between each other.

[0023] In one embodiment, the ultrasonic transducer is a piezoelectric micromechanical ultrasonic transducer.

[0024] In one embodiment, the outer tube has a probe port that is disposed opposite to the second imaging component and connects the interior of the outer tube to the outside.

[0025] In one embodiment, at least the portion of the outer tube disposed opposite to the second imaging component is made of a material having ultrasonic coupling properties.

[0026] The beneficial effects provided by this application are as follows:

[0027] The laser ablation catheter provided in this application embodiment, by setting the ablation structure as a first optical fiber and a second optical fiber connected to the distal end of the first optical fiber, expands the emitted light from the first optical fiber through the second optical fiber. Thus, while achieving the same ablation effect, the number of first optical fibers used can be effectively reduced, which in turn reduces the number of ablation structures used. This effectively reduces the outer diameter of the laser ablation catheter, effectively improving its delivery and throughput performance. Simultaneously, by placing the ablation structure between the inner and outer tubes, the tube structure supports and protects the ablation structure, effectively enhancing the flexibility of the laser ablation catheter and reducing the risk of breakage. Therefore, while ensuring the flexibility of the laser ablation catheter, it also effectively reduces its outer diameter, improves its delivery and throughput performance, expands its ablation range, and enhances its overall performance. Attached Figure Description

[0028] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0029] Figure 1 This is a schematic diagram of the laser ablation catheter provided in Embodiment 1 of this application. Figure 1 ;

[0030] Figure 2 This is a cross-sectional view of the laser ablation catheter provided in Embodiment 1 of this application. Figure 1 ;

[0031] Figure 3 This is a cross-sectional view of the laser ablation catheter provided in Embodiment 1 of this application. Figure 2 ;

[0032] Figure 4 This is a cross-sectional view of the laser ablation catheter provided in Embodiment 1 of this application. Figure 3 ;

[0033] Figure 5This is a schematic diagram of the ablation structure provided in Embodiment 1 of this application;

[0034] Figure 6 This is a cross-sectional view of the laser ablation catheter provided in Embodiment 2 of this application;

[0035] Figure 7 This is a cross-sectional view of the laser ablation catheter provided in Embodiment 3 of this application;

[0036] Figure 8 This is a cross-sectional view of the laser ablation catheter provided in Embodiment 5 of this application.

[0037] Explanation of icon numbers:

[0038] 10-Tube body structure; 11-Outer tube; 111-Detection port; 12-Inner tube; 121-First cavity; 122-Second cavity; 20-Ablation structure; 21-First optical fiber; 22-Second optical fiber; 23-Transition optical fiber segment; 30-First imaging component; 40-Guiding structure; 50-Adjustment structure; 60-Second imaging component; 61-Chip; 62-Ultrasonic transducer; 70-Mounting sleeve; 80-Sealing structure; L1-Centerline of tube body structure; L2-Centerline of first cavity; a-Distal end; b-Proximal end. Detailed Implementation

[0039] To make the technical problems, technical solutions, and beneficial effects to be solved by this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and are not intended to limit the scope of this application.

[0040] In the description of this application, it should be understood that the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0041] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means two or more, unless otherwise explicitly specified.

[0042] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "linking," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0043] Please see Figure 2 , Figure 3 In this application, the proximal end b is always the end closer to the operator, and the distal end a is always the end farther away from the operator.

[0044] The specific implementation of this application will be described in more detail below with reference to specific embodiments:

[0045] Example 1

[0046] Please see Figure 1 , Figure 2 This application provides a laser ablation catheter, including a tube body structure 10 and an ablation structure 20.

[0047] The tube structure 10 includes an outer tube 11 and an inner tube 12 disposed inside the outer tube 11. An ablation structure 20 is disposed between the inner tube 12 and the outer tube 11, and at least one such structure is provided. The ablation structure 20 includes a first optical fiber 21 and a second optical fiber 22 connected to the distal end of the first optical fiber 21. The cross-sectional area of ​​the second optical fiber 22 is larger than that of the first optical fiber 21. The second optical fiber 22 is used to amplify the emitted light from the first optical fiber 21, and ablate the lesion tissue via the amplified light. The cross-sectional area of ​​the first optical fiber 21 is the area of ​​its cross-section perpendicular to its centerline. The cross-sectional area of ​​the second optical fiber 22 is the area of ​​its cross-section perpendicular to its centerline.

[0048] Based on this, when performing ablation surgery on lesions in blood vessels using a laser ablation catheter, the laser ablation catheter is first moved to the location of the lesion. Then, the beam emitted from the first fiber 21 is expanded by the second fiber 22, and the lesion is ablated by the expanded beam, thus achieving the purpose of treatment.

[0049] Based on this, by configuring the ablation structure 20 as a first optical fiber 21 and a second optical fiber 22 connected to the distal end of the first optical fiber 21, the emitted light from the first optical fiber 21 is amplified through the second optical fiber 22. Thus, while achieving the same ablation effect, the number of first optical fibers 21 used can be effectively reduced, which in turn reduces the number of ablation structures 20 used. This effectively reduces the outer diameter of the laser ablation catheter, improves its delivery and throughput performance, and consequently expands its ablation range, thereby enhancing its overall performance. Furthermore, the production cost of the ablation structure 20 can be effectively reduced, thereby lowering the overall production cost of the laser ablation catheter.

[0050] Based on this, by placing the ablation structure 20 between the inner tube 12 and the outer tube 11, the ablation structure 20 is supported and protected by the tube structure 10, which effectively improves the flexibility of the laser ablation catheter, effectively reduces the risk of the ablation structure 20 easily breaking, and further improves the pushing and passing performance of the laser ablation catheter, further expands the ablation range of the laser ablation catheter, and further improves the performance of the laser ablation catheter.

[0051] In summary, the laser ablation catheter provided in this application embodiment, by setting the ablation structure 20 as a first optical fiber 21 and a second optical fiber 22 connected to the distal end of the first optical fiber 21, expands the emitted light from the first optical fiber 21 through the second optical fiber 22. Thus, while achieving the same ablation effect, the number of first optical fibers 21 used can be effectively reduced, which also effectively reduces the number of ablation structures 20 used. This effectively reduces the outer diameter of the laser ablation catheter, effectively improving its pushing and passing performance. Simultaneously, by placing the ablation structure 20 between the inner tube 12 and the outer tube 11, and using the tube structure 10 to support and protect the ablation structure 20, the flexibility of the laser ablation catheter is effectively improved, effectively reducing the risk of breakage. Therefore, while ensuring the flexibility of the laser ablation catheter, the outer diameter of the laser ablation catheter is effectively reduced, the pushing and passing performance of the laser ablation catheter is effectively improved, the ablation range of the laser ablation catheter is effectively expanded, and the overall performance of the laser ablation catheter is effectively improved.

[0052] Specifically, please refer to Figure 1 , Figure 2 Multiple ablation structures 20 are provided, and the second optical fibers 22 of each ablation structure 20 are arranged in a circular array. Among them, the second optical fibers 22 of each ablation structure 20 are arranged in a circular array around the center line L1 of the tube structure 10.

[0053] By adopting the above scheme, multiple ablation structures 20 are arranged in a circumferential array using the second optical fibers 22, which are arranged around the center line L1 of the tube structure 10. This fully utilizes the installation space between the outer tube 11 and the inner tube 12, and achieves the purpose of arranging multiple ablation structures 20 without increasing the outer diameter of the laser ablation catheter. In other words, it achieves the purpose of arranging multiple ablation structures 20 without affecting the passage performance of the laser ablation catheter. Furthermore, the lesions can be ablated by multiple ablation structures 20 working together, which can effectively increase the ablation area and thus effectively improve the ablation efficiency. It also makes the output light spots of each second optical fiber 22 relatively uniform, which helps to ensure that the output light spots of each ablation structure 20 can be closely connected, effectively reducing the gaps between the output light spots. This effectively reduces the possibility of local lesions not being ablated during ablation, effectively improves the ablation effect and ablation efficiency, and effectively protects and improves the performance of the laser ablation catheter.

[0054] Specifically, in one possible implementation, the second optical fibers 22 of two adjacent ablation structures 20 are connected. Based on this, by connecting the second optical fibers 22 of two adjacent ablation structures 20, the ablation structure 20 can be fixed and the second optical fibers 22 of each ablation structure 20 can be arranged in a circumferential array, effectively simplifying the structure of the laser ablation catheter and effectively reducing the design and production costs of the laser ablation catheter.

[0055] In another possible implementation, the laser ablation catheter further includes a partition structure sleeved between the inner tube 12 and the outer tube 11. The partition structure has fixing holes arranged in a circumferential array, and the second optical fibers 22 of the ablation structures 20 are fixedly connected to the fixing holes one by one. Based on this, by setting the partition structure sleeved between the inner tube 12 and the outer tube 11, and fixing the second optical fibers 22 of the ablation structures 20 to the fixing holes one by one, the circumferential array arrangement of the second optical fibers 22 of each ablation structure 20 can be achieved. At the same time, it is also beneficial to set adjacent second optical fibers 22 at a preset interval, so as to effectively reduce the number of second optical fibers 22 while achieving the same ablation area and ablation effect, that is, to effectively reduce the number of ablation structures 20, thereby effectively reducing the production cost of the laser ablation catheter. Furthermore, this design allows for a larger gap between the first optical fibers 21 of each ablation structure 20. This facilitates the arrangement of other functional components within the gaps between the first optical fibers 21 without increasing the outer diameter of the laser ablation catheter. In other words, it allows for the arrangement of other functional components without affecting the passage performance of the laser ablation catheter, thereby achieving a highly integrated design of the various functional components of the laser ablation catheter and effectively ensuring and improving its passage and performance. Additionally, the partition structure effectively and reliably seals the distal gap between the outer tube 11 and the inner tube 12, thereby effectively reducing the risk of blood entering between the outer tube 11 and the inner tube 12 and effectively ensuring the performance of the laser ablation catheter. This embodiment does not impose any limitations on this aspect.

[0056] Please see Figure 5 In this embodiment, a transition fiber segment 23 is provided between the first optical fiber 21 and the second optical fiber 22, and the radial dimension of the transition fiber segment 23 gradually increases in the direction close to the second optical fiber 22. Preferably, the transition fiber segment 23 is conical.

[0057] By adopting the above scheme, on the one hand, it is beneficial to achieve the transmission of the emitted light from the first optical fiber 21 to the second optical fiber 22 with almost no loss, effectively improving the coupling efficiency of the first optical fiber 21 and the second optical fiber 22, effectively reducing the risk of light energy loss, thereby ensuring that the energy density of the emitted light from the second optical fiber 22 can meet the requirements for ablation, and effectively ensuring the performance of the laser ablation catheter; on the other hand, it can also achieve a smooth transition connection between the first optical fiber 21 and the second optical fiber 22, thereby effectively reducing the stress at the connection point of the first optical fiber 21 and the second optical fiber 22, effectively ensuring the structural strength at the connection point of the first optical fiber 21 and the second optical fiber 22, and thus effectively ensuring the overall structural strength of the ablation structure 20, and effectively ensuring the performance of the laser ablation catheter.

[0058] Specifically, the transition fiber segment 23 can be formed by extending the first fiber 21, extending the second fiber 22, or being formed by extending both the first fiber 21 and the second fiber 22. This embodiment does not impose any limitations on this.

[0059] Specifically, in one possible implementation, the connection between the first optical fiber 21 and the second optical fiber 22 can be melted by electrode discharge to form a fusion splice with a tapered gradient, that is, to form a transition optical fiber segment 23 with a tapered gradient. In another possible implementation, a thick optical fiber can also be formed into an optical fiber with a tapered gradient by tapering a single thick optical fiber, that is, the ablation structure 20 can also be produced by directly tapering a single thick optical fiber. In this case, the ablation structure 20 includes the first optical fiber 21, the second optical fiber 22, and the transition optical fiber segment 23 with a tapered gradient. This embodiment does not limit this.

[0060] Of course, for other possible implementations, please refer to Figure 2 The first optical fiber 21 and the second optical fiber 22 can also be connected by welding. In this case, there is no transition fiber segment 23 between the first optical fiber 21 and the second optical fiber 22. Based on this, the design and manufacturing difficulty of the ablation structure 20 can be effectively reduced. Preferably, the centers of the connection ends of the first optical fiber 21 and the second optical fiber 22 are aligned. This facilitates a relatively uniform distribution of the emitted light spot of the second optical fiber 22, thereby ensuring that the emitted light spots of each ablation structure 20 can be tightly connected, effectively reducing the gaps between the emitted light spots, and thus effectively reducing the possibility of local lesions not being ablated during ablation. This effectively improves the ablation effect and efficiency, and effectively guarantees and improves the performance of the laser ablation catheter. This embodiment does not limit this aspect.

[0061] Please see Figure 2 , Figure 3 In this embodiment, the laser ablation catheter also includes an adjustment structure 50 disposed between the inner tube 12 and the outer tube 11. The adjustment structure 50 can drive the distal end of the tube structure 10 and the distal end of the ablation structure 20 to bend.

[0062] By adopting the above scheme and setting the adjustment structure 50, the distal ends of the tube structure 10 and the ablation structure 20 are bent through the adjustment structure 50. The movement direction and orientation of the laser ablation catheter are adjusted in real time according to the bending changes of the blood vessel. This can effectively improve the passability of the laser ablation catheter and also facilitate the alignment of the distal port of the laser ablation catheter with the lesion tissue to be ablated, thereby performing precise ablation of the lesion tissue. This effectively improves the ablation accuracy of the laser ablation catheter and effectively protects and improves the performance of the laser ablation catheter.

[0063] Furthermore, by placing the adjustment structure 50 between the inner tube 12 and the outer tube 11, the installation space of the inner tube 12 and the outer tube 11 can be fully utilized. The arrangement of the adjustment structure 50 can be achieved without increasing the outer diameter of the catheter. That is, while ensuring the passage performance of the laser ablation catheter, the loading of the adjustment structure 50 can also be achieved, effectively ensuring and improving the performance of the laser ablation catheter.

[0064] The adjustment structure 50 can be symmetrically arranged relative to the centerline L1 of the tube structure 10 as needed. This embodiment does not impose any restrictions on this.

[0065] Specifically, the adjustment structure 50 is columnar, and its outer diameter does not exceed 150 μm. This ensures the performance of the adjustment structure 50 while also making its outer diameter suitable.

[0066] Specifically, the adjustment structure 50 is made of a non-biotoxic metal material, such as food-grade stainless steel. This ensures both the performance and safety of the adjustment structure 50 during use.

[0067] Specifically, when the laser ablation catheter has a partition structure, the adjustment structure 50 can be connected to the proximal end face of the partition structure, or it can be without protruding from the partition structure. This embodiment does not impose any restrictions on this.

[0068] Please see Figure 2 In this embodiment, the laser ablation catheter further includes a first imaging component 30 and a guiding structure 40. The first imaging component 30 is used for real-time imaging, and the guiding structure 40 is used to guide the movement path of the catheter body structure 10 and the ablation structure 20. The first imaging component 30 and the guiding structure 40 are simultaneously inserted into the inner tube 12. The first imaging component 30 is relatively fixed relative to the inner tube 12 and does not protrude from the distal end face of the first optical fiber 21. At this time, the first imaging component 30 can perform imaging from the side of the laser ablation catheter.

[0069] By adopting the above scheme, when performing ablation surgery on lesions in blood vessels using a laser ablation catheter, the guiding structure 40 first shuttles through the inner tube 12 to guide the movement path of the tube body structure 10 and the ablation structure 20, so that the tube body structure 10 and the ablation structure 20 can move smoothly to the location of the lesion. Subsequently, the lesion is ablated by the ablation structure 20. At the same time, by rotating the tube body structure 10, the first imaging component 30 is rotated around the center line L1 of the tube body structure 10, so that the first imaging component 30 can perform circumferential detection on the outside of the laser ablation catheter. This allows for real-time, all-round imaging of the intravascular condition and the ablation process. The system can also determine in real time whether the ablation structure 20 is acting on the blood vessel wall based on the imaging image. If the ablation structure 20 is not acting on the blood vessel wall, the ablation continues. If the ablation structure 20 is acting on the blood vessel wall, the ablation is stopped, and the position of the distal end of the laser ablation catheter can be adjusted in time until the ablation structure 20 no longer acts on the blood vessel wall before continuing the ablation.

[0070] Therefore, by simultaneously inserting the first imaging component 30 and the guiding structure 40 into the inner tube 12, on the one hand, the guiding structure 40 guides the movement path of the tube structure 10 and the ablation structure 20, allowing them to move smoothly to or through the lesion tissue, effectively improving the efficiency of the ablation procedure. On the other hand, by using the first imaging component 30 to perform real-time imaging of the intravascular condition and ablation status during ablation, it is possible to determine in real time whether the ablation structure 20 has acted on the vessel wall, effectively reducing the risk of damage to the vessel wall caused by the ablation structure 20 acting on the vessel wall, thus effectively improving the safety during ablation. Furthermore, it is possible to determine the lesion tissue in real time based on the imaging images. By identifying any missed areas of tissue that have not been ablated, the position of the distal end of the laser ablation catheter can be adjusted in a timely manner to effectively and reliably ablate any missed areas of the lesion, thus ensuring the ablation effect and accuracy of the laser ablation catheter and effectively guaranteeing and improving its performance. On the other hand, without increasing the outer diameter of the laser ablation catheter, the internal space of the inner tube 12 can be fully utilized to arrange the guiding structure 40 and the first imaging component 30. That is, while ensuring the pushing and passing performance of the laser ablation catheter, the guiding structure 40 and the first imaging component 30 can also be mounted, effectively improving the performance of the laser ablation catheter.

[0071] Of course, medical personnel can also manually control the movement path of the tube structure 10 and the ablation structure 20 to move them to the location of the lesion. This embodiment does not impose any limitations on this.

[0072] Based on this, by setting the first imaging component 30 to be relatively fixed relative to the inner tube 12, the first imaging component 30 is fixed in the inner tube 12. At this time, the guide structure 40 can pass through the gap between the first imaging component 30 and the inner wall of the inner tube 12, and the detection light of the first imaging component 30 can be emitted through the gap between the first optical fibers 21. Thus, on the one hand, although some imaging quality is sacrificed, since the outer diameter of the first optical fiber 21 is often small, most of the detection light from the first imaging component 30 can be emitted through the gap between the first optical fibers 21. At this time, the imaging effect of the first imaging component 30 is still sufficient to meet the needs of judging the ablation status. At the same time, the outer diameter of the laser ablation catheter can be increased without increasing the size of the laser ablation catheter. That is, while ensuring the pushing and passing performance of the laser ablation catheter, the loading of the first imaging component 30 can be achieved, effectively ensuring and improving the performance of the laser ablation catheter. On the other hand, the first imaging component 30 does not need to be pulled out of the inner tube 12 to allow the guide structure 40 to pass through the inner tube 12 and achieve the guiding function of the guide structure 40, effectively saving the operation time of alternating operation of the guide structure 40 and the first imaging component 30, thereby effectively improving the efficiency of the ablation surgery. Furthermore, by storing and protecting the first imaging component 30 through the inner tube 12, the risk of the first imaging component 30 being contaminated or lost can also be effectively reduced.

[0073] Based on this, by setting the first imaging component 30 not to protrude from the far end face of the first optical fiber 21, the risk of the second optical fiber 22 blocking too much of the probe light of the first imaging component 30 and affecting the imaging effect can be effectively reduced, thus effectively ensuring the imaging effect of the first imaging component 30 and effectively ensuring the performance of the first imaging component 30.

[0074] Specifically, the first imaging component 30 is an OCT (Optical Coherence Tomography) imaging component. Thus, high-resolution tomographic imaging can be obtained using low-coherence interferometry with a broadband light source, which helps medical personnel to more accurately assess the type and extent of intravascular lesions, effectively ensuring and improving the performance of the first imaging component 30.

[0075] Specifically, both the inner tube 12 and the outer tube 11 are made of materials with light-transmitting properties, such as FEP (Fluorinated ethylene propylene), PTFE (Teflon), and PC (Polycarbonate). Based on the excellent light transmission properties, biocompatibility, non-toxicity to humans, and chemical stability of materials like FEP, PTFE, and PC, both the inner tube 12 and outer tube 11 possess superior light transmission properties. This ensures that the detection light from the first imaging component 30 can smoothly pass through the inner tube 12 and outer tube 11 and be emitted outwards towards the tube structure 10, effectively guaranteeing the imaging effect. Furthermore, it effectively ensures the safety of the inner tube 12 and outer tube 11 in use, and effectively guarantees the performance of the tube structure 10. Preferably, the inner tube 12 is made of PTFE material. Due to the extremely low coefficient of friction of PTFE material, the guide structure 40 can move smoothly relative to the inner tube 12, further improving the passage performance and usability of the laser ablation catheter.

[0076] Specifically, the thickness of the outer tube 11 is less than 200 μm. Based on this, the outer tube 11 can have a high light transmittance, thereby ensuring the imaging effect of the first imaging component 30. It can also ensure the performance of the outer tube 11 while making the thickness of the outer tube 11 more suitable, further reducing the outer diameter of the laser ablation catheter, and further ensuring and providing the passage performance, pushing performance and performance of the laser ablation catheter.

[0077] In this design, when the adjustment structure 50 is installed in the laser ablation catheter, the adjustment structure 50 does not protrude from the proximal end of the imaging probe of the first imaging component 30. This effectively reduces the risk of the adjustment structure 50 obstructing the detection light of the first imaging component 30 and affecting the imaging effect. In addition, during ablation, if it is determined from the imaging image of the first imaging component 30 that the ablation structure 20 is acting on the blood vessel wall, the position of the distal end of the laser ablation catheter can be adjusted in time by the adjustment structure 50 until the ablation structure 20 no longer acts on the blood vessel wall before continuing ablation, effectively improving safety during ablation. Furthermore, the ablation effect of the lesion area can be determined from the imaging image of the first imaging component 30, so the movement of the laser ablation catheter can be controlled in time by adjusting the structure to reach the unablated lesion tissue area before continuing ablation.

[0078] Please see Figure 2 In this embodiment, the first imaging component 30 and the guide structure 40 are simultaneously installed in the inner tube 12. The inner tube 12 is divided into a first cavity 121 and a second cavity 122. The first imaging component 30 is installed in the first cavity 121, and the guide structure 40 is installed in the second cavity 122.

[0079] By adopting the above scheme, the inner tube 12 is divided into a first cavity 121 and a second cavity 122, so that the first imaging component 30 passes through the first cavity 121 and the guide structure 40 passes through the second cavity 122. This can effectively and reliably separate the first imaging component 30 and the guide component, effectively reduce the risk of mutual interference and collision between the guide structure 40 and the first imaging component 30 when the guide structure 40 passes through the inner tube 12, effectively ensure the performance of the first imaging component 30 and the guide structure 40, and effectively ensure the performance of the laser ablation catheter.

[0080] Please see Figure 2 In this embodiment, the centerline L2 of the first cavity 121 is offset from the centerline L1 of the tube structure 10.

[0081] By adopting the above scheme, and by setting the centerline L2 of the first lumen 121 to deviate from the centerline L1 of the tube structure 10, the first imaging component 30 is offset from the centerline L1 of the tube structure 10 and is set off-center. At the same time, the guiding structure 40 is close to the centerline L1 of the tube structure 10 for guidance. In this way, a setting of central guidance and lateral imaging can be achieved. This ensures that the guiding structure 40 guides the tube structure 10 and the ablation structure 20 smoothly and reliably within the blood vessel, while also effectively reducing the risk of the guiding structure 40 blocking the detection light of the first imaging component 30, thus effectively ensuring the imaging effect of the first imaging component 30.

[0082] Please see Figure 2 In this embodiment, the outer diameter of the inner tube 12 is gradually reduced towards the distal end.

[0083] By adopting the above scheme, by setting the outer diameter of the inner tube 12 to gradually decrease towards the distal end, the outer diameter of the distal end of the inner tube 12 is smaller, which in turn makes the outer diameter of the distal end of the entire tube structure 10 smaller, thereby further reducing the outer diameter of the distal end of the laser ablation catheter and further improving the pushing and passing performance of the laser ablation catheter.

[0084] Please see Figure 2 In this embodiment, the first cavity 121 does not protrude from the distal end face of the first optical fiber 21.

[0085] By adopting the above scheme, on the one hand, it can effectively ensure that the first imaging component 30 does not protrude from the distal end face of the first optical fiber 21, thereby reducing the risk that the second optical fiber 22 will block the detection light of the first imaging component 30 too much and affect the imaging effect, and effectively ensuring the performance of the first imaging component 30; on the other hand, by eliminating the first cavity 121 corresponding to the portion protruding from the distal end face of the first optical fiber 21, it is beneficial to achieve that the outer diameter of the inner tube 12 portion protruding from the first cavity 121 is smaller than the outer diameter of the inner tube 12 portion opposite to the first cavity 121, which also facilitates the purpose of gradually narrowing the outer diameter of the inner tube 12 towards the distal end.

[0086] Please see Figure 3 In this embodiment, the laser ablation catheter further includes at least one second imaging component 60 disposed between the outer tube 11 and the inner tube 12. The second imaging component 60 does not protrude from the distal end face of the first optical fiber 21 and is used for real-time imaging. The second imaging component 60 and the first imaging component 30 are of different types.

[0087] Similarly, for example, the first imaging component 30 can be an OCT imaging component, and the second imaging component 60 can be an IVUS0 (Intravascular ultrasound) imaging component. In this case, the second imaging component 60 can perform imaging from the side of the laser ablation catheter.

[0088] By adopting the above scheme, at least one second imaging component 60 is provided between the outer tube 11 and the inner tube 12 to perform real-time imaging of the intravascular condition and ablation status.

[0089] The ability to determine in real-time whether the ablation structure 20 has acted on the blood vessel wall based on imaging images effectively reduces the risk of damage to the blood vessel wall caused by the ablation structure 20, thus improving safety during ablation and ensuring and enhancing the performance of the laser ablation catheter. Furthermore, it allows for real-time assessment of whether any lesions have been missed and thus can be adjusted in a timely manner to effectively and reliably ablate any missed lesions.

[0090] Ablation effectively ensures the ablation effect and accuracy of the laser ablation catheter. In addition, without increasing the outer diameter of the laser ablation catheter, the second imaging component 60 can be arranged by making full use of the installation space between the inner tube 12 and the outer tube 11. That is, while ensuring the pushing and passing performance of the laser ablation catheter, the second imaging component 60 can also be installed, effectively improving the performance of the laser ablation catheter.

[0091] By ensuring that the second imaging component 60 does not protrude from the distal end face of the first optical fiber 21, the risk of excessive obstruction of the detection signal of the second imaging component 60 by the second optical fiber 22, thus affecting the imaging effect, can be effectively reduced.

[0092] This effectively ensures the imaging effect of the second imaging component 60 and effectively ensures the performance of the second imaging component 60.

[0093] Specifically, please refer to Figure 4 When multiple second imaging components 60 are provided, they are arranged in a circular array. Specifically, the multiple second imaging components 60 are arranged in a circular array around the center line L1 of the tube structure 10. Based on this, by arranging multiple second imaging components 60 in a circular array around the center line L1 of the tube structure 10, comprehensive and large-area real-time imaging of the intravascular condition and ablation status can be performed simultaneously using multiple second imaging components 60. This results in good imaging quality, facilitating a comprehensive and reliable analysis and judgment of whether the ablation structure 20 has acted on the vessel wall, further reducing the risk of damage to the vessel wall caused by the ablation structure 20, and further improving safety during ablation.

[0094] Please refer to Figure 3 When the adjustment structure 50 is provided in the laser ablation catheter, the adjustment structure 50 does not protrude from the proximal end of the imaging probe of the second imaging component 60, or the adjustment structure 50 is located on the side of the first optical fiber 21 facing the inner tube 12. In this way, the risk of the adjustment structure 50 blocking the detection signal of the second imaging component 60 and affecting the imaging effect can be effectively reduced. In addition, the ablation effect of the lesion area can be judged according to the imaging image of the second imaging component 60. Thus, the movement of the laser ablation catheter can be controlled in a timely manner by adjusting the structure to reach the lesion tissue area that has not been ablated and continue ablation, effectively ensuring the performance of the laser ablation catheter.

[0095] Please see Figure 3 , Figure 4 In this embodiment, the laser ablation catheter also includes an installation sleeve 70 sleeved outside each of the first optical fibers 21, and each of the second imaging components 60 is respectively installed on the outer periphery of the installation sleeve 70.

[0096] By adopting the above scheme, each second imaging component 60 is installed on the outer periphery of the mounting sleeve 70, which supports the second imaging component 60. The mounting sleeve 70 is then fitted over each first optical fiber 21, enabling the installation of both the mounting sleeve 70 and the second imaging components 60. The installation operation is very convenient and simple, effectively improving the assembly yield of the second imaging components 60. Simultaneously, it greatly reduces the risk of the first optical fiber 21 obstructing the detection signal of the second imaging component 60, thus affecting the imaging effect and effectively ensuring and improving the imaging effect of the second imaging component 60. Furthermore, the mounting sleeve 70 integrates each second imaging component 60 into a single unit. The integrated design also helps to reduce the overall thickness of the mounting sleeve 70 and the second imaging component 60, thereby effectively reducing the space occupied by the second imaging component 60 and the mounting sleeve 70. It also facilitates the smooth and convenient installation of the second imaging component 60 and the mounting sleeve 70 without increasing the outer diameter of the tube structure 10. In other words, it also facilitates the smooth and convenient integration of the second imaging component 60 while ensuring the passability of the laser ablation catheter. In addition, it also facilitates the bending of the mounting sleeve 70 in conjunction with the tube structure 10, effectively shortening the non-bendable part at the distal end of the laser ablation catheter, thereby further improving the passability and pushing performance of the laser ablation catheter.

[0097] Of course, in other possible implementations, the mounting sleeve 70 can also be fitted over the inner tube 12, in which case the detection signal of the second imaging component 60 is emitted through the gap between the first optical fibers 21. This embodiment does not limit this.

[0098] Of course, in other possible implementations, the second imaging component 60 can be directly installed on the inner wall of the outer tube 11. In this case, the risk of the first optical fiber 21 blocking the detection signal of the second imaging component 60 and affecting the imaging effect can be greatly reduced, effectively ensuring and improving the imaging effect of the second imaging component 60. The second imaging component 60 can also be disposed in the gap between the first optical fibers 21 to make full use of the installation space between the outer tube 11 and the inner tube 12, and can effectively reduce the risk of the first optical fiber 21 blocking the detection signal of the second imaging component 60 and affecting the imaging effect. The second imaging component 60 can also be disposed close to the outside of the first optical fiber 21. This embodiment does not limit this.

[0099] Specifically, please refer to Figure 4When multiple second imaging components 60 are provided, the mounting sleeve 70 is a polygonal tubular shape, with each second imaging component 60 mounted on a different side of the mounting sleeve 70. For example, when six second imaging components 60 are provided, the mounting sleeve 70 is a hexagonal tubular shape. Thus, by setting the mounting sleeve 70 to a polygonal tubular shape, the mounting area of ​​each second imaging component 60 can be effectively guaranteed, and the risk of interference between the second imaging components 60, preventing installation, can be effectively reduced, thus effectively ensuring...

[0100] Specifically, the mounting sleeve 70 can be a flexible circuit board, or it can be a mounting sleeve 70 made of other flexible materials. This embodiment does not limit this.

[0101] Please see Figure 3 , Figure 4 In this embodiment, the second imaging component 60 includes a chip 61 connected to the side of the mounting sleeve 70 away from the inner tube 12, and at least one ultrasonic transducer 62 connected to the side of the chip 61 away from the mounting sleeve 70 and electrically connected to the chip 61.

[0102] By adopting the above scheme, by setting the second imaging component 60 as the chip 61 and the ultrasonic transducer 62 electrically connected to the chip 61, the ablation effect can be observed by using ultrasonic imaging through the second imaging component 60. The size of the blood vessel lumen and lesion tissue can be accurately measured, which is especially beneficial for medical staff to make more accurate assessments of complex lesions, effectively ensuring and improving the performance of the second imaging component 60.

[0103] Please see Figure 4 In this embodiment, multiple ultrasonic transducers 62 are provided, and the multiple ultrasonic transducers 62 are arranged at intervals. Preferably, the multiple ultrasonic transducers 62 are arranged at intervals with a preset spacing (e.g., 90 μm).

[0104] By adopting the above scheme and setting multiple (e.g., 10) ultrasonic transducers 62, the second imaging component 60 can be used to perform detection together, which helps to meet the requirements of higher imaging frequencies (e.g., above 20MHz), effectively ensuring and improving the performance of the second imaging component 60.

[0105] Please see Figure 3 , Figure 4 In this embodiment, the ultrasonic transducer 62 is a piezoelectric micromachined ultrasonic transducer (PMUT).

[0106] By adopting the above scheme, based on the piezoelectric micromechanical ultrasonic transducer, which can be used as both an actuator (emitting sound waves) and a sensor (receiving sound waves), and has the characteristics of high reliability and consistency, the production cost of the ultrasonic transducer 62 is effectively reduced while ensuring its performance.

[0107] Please see Figure 3 In this embodiment, at least the portion of the outer tube 11 that is disposed opposite to the second imaging component 60 is made of a material with ultrasonic coupling properties. For example, materials such as RTV (room temperature vulcanized silicone rubber).

[0108] By adopting the above scheme, by setting at least the part of the outer tube 11 that is opposite to the second imaging component 60 to be made of a material with ultrasonic coupling characteristics, the detection signal of the second imaging component 60 can be effectively ensured to be smoothly transmitted through the outer tube 11 toward the outside of the tube structure 10, effectively ensuring the imaging effect of the second imaging component 60 and effectively ensuring the performance of the second imaging component 60.

[0109] Example 2

[0110] The difference between this embodiment and Embodiment 1 is that:

[0111] Please see Figure 7 In this embodiment, the first imaging component 30 and the guiding structure 40 are alternately inserted into the inner tube 12. The inner tube 12 has a central lumen, and the first imaging component 30 and the guiding structure 40 are alternately inserted into the central lumen of the inner tube 12. At this time, the first imaging component 30 can acquire and image through the distal end of the inner tube 12; that is, the first imaging component 30 can perform imaging from the front of the laser ablation catheter.

[0112] By adopting the above scheme, when performing ablation surgery on lesions in blood vessels using a laser ablation catheter, the guiding structure 40 first shuttles through the central lumen of the inner tube 12 to guide the movement path of the tube body structure 10 and the ablation structure 20, so that the tube body structure 10 and the ablation structure 20 can move smoothly to the location of the lesion. Subsequently, the guiding structure 40 is removed from the central lumen of the inner tube 12 and replaced by the first imaging component 30, which shuttles through the central lumen of the inner tube 12. At the same time, the lesion is ablated by the ablation structure 20. The first imaging component 30 can then perform real-time imaging of the intravascular condition and the ablation process, and determine in real time whether the ablation structure 20 is acting on the blood vessel wall based on the imaging image. If the ablation structure 20 is not acting on the blood vessel wall, the ablation continues. If the ablation structure 20 is acting on the blood vessel wall, the ablation is stopped, and the position of the distal end of the laser ablation catheter can be adjusted in time until the ablation structure 20 no longer acts on the blood vessel wall before continuing the ablation.

[0113] Therefore, by having the guiding structure 40 and the first imaging component 30 alternately shuttle through the inner tube 12, on the one hand, the guiding structure 40 guides the movement path of the tube body structure 10 and the ablation structure 20, allowing them to move smoothly to or through the lesion tissue, effectively improving the efficiency of the ablation procedure; on the other hand, the first imaging component 30 performs real-time imaging of the intravascular condition and ablation status during ablation, allowing for real-time determination of whether the ablation structure 20 has acted on the vessel wall, effectively reducing the risk of damage to the vessel wall caused by the ablation structure 20, and effectively improving safety during ablation. Furthermore, it allows for real-time determination of whether any lesion tissue has been missed and not ablated, enabling timely adjustment of the distal port of the laser ablation catheter to address any missed lesions. Effective and reliable ablation is achieved by the laser ablation catheter, ensuring its ablation effect and accuracy, and improving its performance. Furthermore, by having the guide structure 40 and the first imaging component 30 alternately pass through the inner tube 12 while sharing its internal space, the outer diameter of the inner tube 12 can be kept relatively small, thus meeting the space requirements for the guide structure 40 and the first imaging component 30 without increasing its size. This allows for the installation of the guide structure 40 and the first imaging component 30 while maintaining a smaller laser ablation catheter size without increasing its outer diameter. In other words, while ensuring the laser ablation catheter's passage and pushing performance, the guide structure 40 and the first imaging component 30 can also be mounted, effectively guaranteeing and improving the performance of the laser ablation catheter.

[0114] It should be noted that the ablation process is usually carried out while the ablation is being performed. During the ablation, the first imaging component 30 can move synchronously with the laser ablation catheter to ensure the imaging effect of the first imaging component 30 on the ablation situation and the intravascular situation. This effectively reduces the risk of poor imaging effect or even failure to image due to the obstruction of the first imaging component 30 by the ablation structure 20 during the ablation process, and effectively ensures the performance of the first imaging component 30.

[0115] Preferably, please refer to Figure 7 When the distal end of the first imaging component 30 reaches / moves to the distal end of the inner tube 12, the first imaging component 30 can acquire and image through the distal port of the inner tube 12. This effectively reduces the risk of poor imaging or even failure to image due to obstruction of the first imaging component 30 by the ablation structure 20 during ablation, effectively ensuring the imaging effect of the first imaging component 30 on the ablation process and the intravascular condition, and effectively guaranteeing the performance of the first imaging component 30.

[0116] Example 3

[0117] The difference between this embodiment and Embodiment 1 is that:

[0118] Please see Figure 6 In this embodiment, the distal end of the inner tube 12 is provided with a sealing structure 80. It should be noted that, at this time, the laser ablation catheter does not have a guiding structure 40. The movement path of the tube structure 10 and the ablation structure 20 is directly controlled manually by medical personnel to move the tube structure 10 and the ablation structure 20 to the location of the lesion tissue.

[0119] By adopting the above solution, by setting a sealing structure 80 at the distal end of the inner tube 12 to seal the distal end of the inner tube 12, the risk of blood entering the lumen of the inner tube 12 from the distal end can be effectively reduced, thereby effectively reducing the risk of blood affecting the use effect of the medical device loaded in the inner tube 12 and effectively ensuring the performance of the laser ablation catheter.

[0120] Specifically, in one possible implementation, the sealing structure 80 is made of a radiopaque material, for example, a stainless steel head. By making the sealing structure 80 a radiopaque material, it can be radiopaque under specific imaging conditions, such as X-ray irradiation, and thus appear brightly displayed. This allows for real-time tracking of the distal end of the laser ablation catheter within the blood vessel when it enters, facilitating observation and positioning by medical personnel. In another possible implementation, the sealing structure 80 is made of a light-transmitting material, such as FEP, PTFE, or PC. This provides good light transmission, allowing the detection light from the first imaging component 30 to exit through the sealing structure 80 from the distal end of the inner tube 12 to the outside of the tube structure 10 for forward imaging, effectively ensuring the imaging effect and performance of the first imaging component 30. This embodiment does not limit the scope of the implementation.

[0121] Example 4

[0122] The difference between this embodiment and Embodiment 1 is that:

[0123] Please see Figure 2 In this embodiment, the first optical fibers 21 of each ablation structure 20 are bundled together to the side of the guide structure 40 away from the first imaging component 30.

[0124] By adopting the above scheme, by bundling the first optical fibers 21 of each ablation structure 20 to the side of the guide structure 40 away from the first imaging component 30, the risk of the first optical fibers 21 blocking the probe light of the first imaging component 30 and affecting the imaging effect can be effectively eliminated, thus effectively ensuring the imaging effect of the first imaging component 30 and effectively ensuring the performance of the first imaging component 30.

[0125] Specifically, the first optical fibers 21 of each ablation structure 20 can be bundled together on the side of the guide structure 40 away from the first imaging component 30 by pinching, for example, by using a metal clamp. In this way, the method of bundling the first optical fibers 21 of each ablation structure 20 is very simple and easy to operate.

[0126] Specifically, the first imaging component 30 does not protrude from the pinched portion of the first optical fiber 21. Based on this, the risk of the pinched portion of the first optical fiber 21 blocking the probe light of the first imaging component 30 and affecting the imaging effect can be effectively eliminated, thus effectively ensuring the imaging effect of the first imaging component 30 and effectively ensuring the performance of the first imaging component 30.

[0127] Example 5

[0128] The difference between this embodiment and Embodiment 1 is that:

[0129] Please see Figure 8 In this embodiment, the outer tube 11 is provided with a detection port 111 that is disposed opposite to the second imaging component 60 and connects the interior of the outer tube 11 to the outside.

[0130] By adopting the above scheme, by setting a detection port 111 on the outer tube 11 opposite to the second imaging component 60, the risk of poor imaging effect caused by the outer tube 11 blocking the detection signal of the second imaging component 60 is effectively reduced. This facilitates the smooth transmission of the detection signal of the second imaging component 60 through the detection port 111 towards the outside of the tube structure 10, effectively ensuring the imaging effect of the second imaging component 60 and effectively ensuring the performance of the second imaging component 60.

[0131] Example 6

[0132] The difference between this embodiment and Embodiment 1 is that:

[0133] Please see Figure 2 In this embodiment, an organic liquid or gel is injected between the outer tube 11 and the inner tube 12.

[0134] By adopting the above scheme, by injecting organic liquid or gel between the outer tube 11 and the inner tube 12, the ablation structure 20, the inner tube 12 and the outer tube 11 can be connected into one unit by organic liquid or gel, making the laser ablation catheter less prone to breakage and effectively ensuring the performance of the laser ablation catheter.

[0135] Specifically, when the first imaging component 30 for lateral imaging is set in the laser ablation catheter of the multi-segment fiber, the organic liquid and gel are organic liquids with low optical impedance. In this way, the detection light of the first imaging component 30 can pass smoothly through the organic liquid or gel and be emitted outside the tube structure 10, effectively reducing the risk that the detection light will be blocked too much by the organic liquid or gel and affect the imaging effect, effectively ensuring the performance of the first imaging component 30 and the laser ablation catheter.

[0136] Specifically, when the second imaging component 60 is installed in the laser ablation catheter of the multi-segment fiber, the organic liquid is an ultrasonic coupling fluid or the gel is a low-impact gel. In this way, while fixing the second imaging component 60 with the organic liquid or gel, it can also effectively ensure that the detection signal of the second imaging component 60 is smoothly transmitted to the outside of the tube structure 10 through the organic liquid or gel, effectively ensuring the imaging effect of the second imaging component 60 and effectively ensuring the performance of the second imaging component 60.

[0137] The above are merely preferred embodiments of this application and are not intended to limit this application. Any modifications, equivalent substitutions, or improvements made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. A laser ablation catheter, characterized in that, include: The tube structure includes an outer tube and an inner tube disposed inside the outer tube; An ablation structure is disposed between the inner tube and the outer tube, and at least one such structure is provided. The ablation structure includes a first optical fiber and a second optical fiber connected to the distal end of the first optical fiber. The cross-sectional area of ​​the second optical fiber is larger than that of the first optical fiber. The second optical fiber is used to expand the beam emitted from the first optical fiber and ablate the lesion tissue via the expanded beam. A transition fiber segment is provided between the first optical fiber and the second optical fiber, and the radial dimension of the transition fiber segment is gradually increased in the direction close to the second optical fiber; The laser ablation catheter also includes an adjustment structure disposed between the inner tube and the outer tube, the adjustment structure being able to cause the distal end of the tube structure and the distal end of the ablation structure to bend. The laser ablation catheter further includes at least one second imaging component disposed between the outer tube and the inner tube. The second imaging component does not protrude from the distal end face of the first optical fiber and is used for real-time imaging. The adjustment structure does not protrude from the proximal end of the imaging probe of the second imaging component. When there are multiple second imaging components, the multiple second imaging components are arranged in a circular array.

2. The laser ablation catheter as described in claim 1, characterized in that, The laser ablation catheter also includes a first imaging component and a guiding structure. The first imaging component is used for real-time imaging, and the guiding structure is used to guide the movement path of the catheter structure and the ablation structure. The first imaging component and the guiding structure are both inserted into the inner tube. The first imaging component is relatively fixed relative to the inner tube and does not protrude from the distal end face of the first optical fiber. Alternatively, the first imaging component and the guide structure may be alternately inserted into the inner tube.

3. The laser ablation catheter as described in claim 2, characterized in that, The first imaging component and the guide structure are both inserted into the inner tube. The inner tube is divided into a first cavity and a second cavity. The first imaging component is inserted into the first cavity, and the guide structure is inserted into the second cavity.

4. The laser ablation catheter as described in claim 3, characterized in that, The centerline of the first cavity is offset from the centerline of the tube structure; And / or, the outer diameter of the inner tube is tapered towards the distal end; And / or, the first cavity does not protrude beyond the distal end face of the first optical fiber.

5. The laser ablation catheter as described in claim 1, characterized in that, The laser ablation catheter also includes a mounting sleeve sleeved over each of the first optical fibers, and each of the second imaging components is respectively mounted on the outer periphery of the mounting sleeve; When multiple second imaging components are provided, the mounting sleeve is a polygonal tube, and each second imaging component is respectively mounted on each side of the mounting sleeve.

6. The laser ablation catheter as described in claim 5, characterized in that, The second imaging component includes a chip connected to the side of the mounting sleeve opposite to the inner tube, and at least one ultrasonic transducer connected to the chip on the side opposite to the mounting sleeve and electrically connected to the chip.

7. The laser ablation catheter as described in claim 6, characterized in that, The ultrasonic transducer is provided in multiple ways, and the multiple ultrasonic transducers are arranged at intervals between each other. Alternatively, the ultrasonic transducer may be a piezoelectric micromechanical ultrasonic transducer; Alternatively, the outer tube may have a detection port that is positioned opposite to the second imaging component and connects the interior of the outer tube to the outside; Alternatively, at least the portion of the outer tube that is positioned opposite the second imaging component may be made of a material with ultrasonic coupling properties.

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