Laser ablation catheter with shockwave balloon

Abstract

The application provides a laser ablation catheter with a shock wave balloon, comprising: a catheter, a guide wire cavity is formed in the catheter, the catheter is provided with a proximal end section, a gradual change section and a distal end section which are sequentially connected with each other, and the diameter of the proximal end section is smaller than that of the distal end section; a plurality of ablation optical fibers are arranged in the catheter; a plurality of ablation probes are arranged in the distal end section, the proximal end of each ablation probe is connected with the distal end of each ablation optical fiber, and the connecting section of the ablation probe connected with the ablation optical fiber is flared in the direction from the proximal end section to the distal end section; a balloon is arranged outside the catheter and located in the proximal end section, the balloon is connected with a liquid guide tube arranged in the catheter for charging and discharging conductive liquid to the balloon; a plurality of electrode pairs are arranged on the outer wall of the catheter and located inside the balloon, and a wire electrically connected with the electrode pairs is arranged in the catheter. The laser ablation catheter with the shock wave balloon has good blood vessel passing performance and high safety.

Description

Technical Field

[0001] This application belongs to the field of medical device technology, and more specifically, relates to a laser ablation catheter equipped with a shockwave balloon. Background Technology

[0002] CTO (chronic total occlusion) refers to a lesion in which the forward flow of the occluded segment is TIMI 0 and the occlusion time is greater than or equal to three months.

[0003] In related technologies, this type of lesion is generally treated with laser ablation or shock wave lithotripsy. Specifically, a laser ablation catheter is used, with an ablation probe placed at the distal end of the catheter to ablate the deposits within the artery; or a shock wave balloon is placed on the catheter to release any remaining lesions on the vessel wall, thereby effectively opening the narrowed segment of the blood vessel.

[0004] However, some multimode catheters combining laser ablation and shockwave balloon techniques exist. In these laser ablation catheters, because the shockwave balloon is positioned on the outer wall of the catheter, the cross-sectional area of ​​the laser ablation catheter at the shockwave balloon is larger than that at the ablation probe. This means the laser ablation area is smaller than the cross-sectional area of ​​the laser ablation catheter at the shockwave balloon. Consequently, after the ablation probe ablates the lesion directly in front of it, the ablation area is still insufficient for the shockwave balloon to pass through, thus affecting the catheter's passage through the blood vessel. To allow the shockwave balloon to pass, the laser ablation power needs to be increased, but higher ablation power can damage the blood vessel. Summary of the Invention

[0005] The purpose of this application is to provide a laser ablation catheter to solve the technical problem of poor passability of existing multimodal laser ablation catheters.

[0006] To achieve the above objectives, the technical solution adopted in this application is to provide a laser ablation catheter equipped with a shockwave balloon, which includes:

[0007] A catheter having a guidewire lumen formed therein, the catheter having a proximal segment, a transition segment and a distal segment connected sequentially to each other, and the diameter of the proximal segment being smaller than the diameter of the distal segment;

[0008] Several ablation optical fibers are disposed in the conduit;

[0009] A plurality of ablation probes are disposed in the distal segment, each ablation probe being connected to each ablation fiber. The connection section on the ablation probe that is connected to the ablation fiber is flared in the direction from the proximal segment to the distal segment, and the diameter of the proximal end of the ablation probe is smaller than the diameter of its distal end.

[0010] A balloon is disposed outside the catheter and located in the proximal segment. The balloon is connected to a fluid guide tube disposed in the catheter for inflating the balloon with conductive fluid. In the contracted state, the cross-sectional area of ​​the laser ablation catheter with shock wave balloon at the balloon is smaller than the cross-sectional area of ​​the distal segment.

[0011] Several electrode pairs are disposed on the outer wall of the catheter and located inside the balloon, and wires electrically connected to the electrode pairs are disposed in the catheter.

[0012] Optionally, the outer surface of the connecting segment on the ablation probe is a conical surface.

[0013] Optionally, each ablation probe is fused to each ablation fiber; or, each ablation probe and each ablation fiber are integrally formed by tapered wire drawing.

[0014] Optionally, the ablation probes are arranged in an array around the circumference of the guide wire cavity; the ablation probes are welded together or spaced apart on the same fixing ring.

[0015] Optionally, the electrode pair includes two opposing and spaced-apart electrode elements, and a limiting element is provided on the outer wall of the conduit to limit the axial position between the two electrode elements in the same electrode pair.

[0016] Optionally, the catheter includes an inner tube and an outer tube, and the ablation fiber, the wire, and the liquid guide tube are all disposed between the inner tube and the outer tube.

[0017] Optionally, the limiting member is a plug, and each of the electrode members is connected to the plug, which is fixedly inserted into the outer tube.

[0018] Optionally, an insulating element is provided between each of the electrode elements and the outer wall of the conduit, and the plug passes through the insulating element.

[0019] Optionally, an insulating element is sleeved on the outside of the conduit, and two of the electrodes in the same electrode pair are disposed on the insulating element.

[0020] Optionally, the electrode element is ring-shaped; a protrusion extending along the axial direction of the ring is provided on one side of the two electrode elements in the same electrode pair facing each other.

[0021] The laser ablation catheter with a shockwave balloon provided in this application has at least the following beneficial effects:

[0022] First, by connecting a transition section between the distal and proximal segments of the catheter, with the diameter of the distal segment being larger than that of the proximal segment, the balloon is positioned in the proximal segment, and the ablation probe is positioned in the distal segment. In this way, when the balloon is in a contracted state, the cross-sectional area of ​​the laser ablation catheter with the shockwave balloon at the balloon is smaller than the ablation area of ​​the ablation probe, thereby improving the passability of the laser ablation probe in complex blood vessels.

[0023] Furthermore, the connecting section on the ablation probe that connects to the ablation fiber is flared. This flared connecting section can disperse the laser beam, increasing the laser ablation area while controlling the laser intensity within a unit ablation area within a safe range, thereby improving the safety of laser ablation. Attached Figure Description

[0024] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0025] Figure 1 This is a schematic diagram of the outer tube of a laser ablation catheter with a shockwave balloon in some embodiments of this application;

[0026] Figure 2 This is a schematic diagram illustrating the internal structure of a laser ablation catheter equipped with a shockwave balloon in some other embodiments of this application;

[0027] Figure 3 This is a schematic diagram of the ablation fiber and ablation probe in some embodiments of this application;

[0028] Figure 4 This is a partial structural schematic diagram of the laser ablation catheter in some embodiments of this application;

[0029] Figure 5 This is a cross-sectional view of the laser ablation catheter with a shockwave balloon at the electrode in some embodiments of this application;

[0030] Figure 6 This is a schematic diagram of the electrode components assembled on the outside of the conduit in some embodiments of this application;

[0031] Figure 7 This is a schematic diagram of the assembly of the ablation probe in some embodiments of this application;

[0032] Figure 8 This is a schematic diagram showing the connection between a laser ablation catheter with a shockwave balloon, a shockwave pulse generator, and a laser emitter in some embodiments of this application.

[0033] The following are the labeling elements in the figure:

[0034] 100. Catheter;

[0035] 101. Inner tube; 1011. Guide wire lumen; 102. Outer tube;

[0036] 110. Distal segment; 120. Gradual transition segment; 130. Proximal segment;

[0037] 200. Ablation fiber;

[0038] 300. Ablation probe; 310. Connecting section;

[0039] 400, balloon;

[0040] 500. Liquid delivery tube;

[0041] 600, electrode pair;

[0042] 610. Electrode component; 611. Protrusion; 620. Connecting pin;

[0043] 700. Wire;

[0044] 800. Insulating components;

[0045] 900, retaining ring;

[0046] A. Laser emitter;

[0047] B. Shock wave pulse generator. Detailed Implementation

[0048] To make the technical problems, technical solutions and beneficial effects to be solved by this application clearer, the following describes this application in further detail with reference to the accompanying drawings and embodiments.

[0049] It should be understood that the specific embodiments described herein are merely illustrative of this application and are not intended to limit this application.

[0050] It should be noted that when a component is referred to as "fixed to" or "set on" another component, it can be directly on the other component or indirectly on that other component.

[0051] When a component is said to be "connected to" another component, it can be directly connected to the other component or indirectly connected to that other component.

[0052] 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. They 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. Therefore, they should not be construed as limitations on this application.

[0053] 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 with "first" or "second" may explicitly or implicitly include one or more of that feature.

[0054] In the description of this application, "multiple" means two or more, unless otherwise expressly and specifically defined.

[0055] Please refer to the following: Figures 1 to 8 The laser ablation catheter with a shockwave balloon provided in the embodiments of this application will now be described.

[0056] refer to Figures 1 to 3 The laser ablation catheter with a shockwave balloon described in this application includes a catheter 100, an ablation fiber 200, an ablation probe 300, a balloon 400, and an electrode pair 600.

[0057] Specifically, a guidewire lumen 1011 is formed in the catheter 100, and the catheter 100 has a proximal segment 130, a transition segment 120 and a distal segment 110 connected in sequence, and the diameter of the proximal segment 130 is smaller than the diameter of the distal segment 110.

[0058] Understandably, the guidewire lumen 1011 is connected to the end face of the distal segment 110 of the catheter 100. By providing the guidewire lumen 1011, an imaging device can be guided from the catheter 100 to the distal segment 110 to image lesions in the blood vessels.

[0059] Understandably, both the fluid guide tube 500 and the lead wire 700 are located inside the catheter 100. This prevents the lead wire 700 and the fluid guide tube 500 from detaching from the catheter 100 during the movement of the laser ablation catheter in the blood vessel, and also prevents the electrolyte from corroding the lead wire 700.

[0060] Several ablation optical fibers 200 are disposed within the conduit 100. Specifically, they can be disposed within the conduit 100, or fixed to the outer wall of the conduit 100 by adhesive bonding, or fixed to the conduit 100 by a bundle ring; the specific method is not limited to these. (Reference) Figure 8The near end of the ablation fiber 200 is used to connect to the laser transmitter A, and the far end is used to connect to the ablation probe 300. The laser transmitter A transmits the modulated laser through the ablation fiber 200 to the ablation probe 300, and the modulated laser is emitted from the exit surface in the ablation probe 300.

[0061] refer to Figure 2 and Figure 3 Several ablation probes 300 are also provided at the distal end 110 of the catheter 100, and the proximal end of each ablation probe 300 is connected to the distal end of each ablation fiber 200. It should be understood that the ablation probes 300 and the ablation fibers 200 are made of the same material.

[0062] Further reference Figure 2 and Figure 3 The connecting segment 310 on the ablation probe 300, which connects to the ablation fiber 200, is flared from the proximal segment 130 to the distal segment 110. That is, the diameter of the distal end of the connecting segment 310 on the ablation probe 300 is larger than the diameter of its proximal end. Specifically, the cross-sectional size of the connecting segment 310 on the ablation probe 300 at various points along the axial direction from its proximal end to its distal end can increase linearly or non-linearly, and is not limited to this.

[0063] The flared connecting section 310 on the ablation probe 300 is configured as follows:

[0064] On the one hand, it can expand and disperse the laser beam, that is, the laser ablation area acting on the vascular lesion is greater than the cross-sectional area of ​​the distal segment 110 of the catheter 100. Under the premise of meeting the laser ablation area, it can reduce the diameter of each ablation probe 300, that is, it can reduce the cross-sectional area of ​​the distal segment 110 of the catheter 100, thereby improving the passability of the laser ablation catheter in the blood vessel.

[0065] On the other hand, since the ablation probe 300 can expand and disperse the laser beam, the high-power modulated laser in the single ablation fiber 200 can be dispersed to irradiate a large area of ​​ablation. That is, the light intensity per unit ablation area can be controlled within a safe range, preventing excessive ablation power from causing burns to healthy tissue in blood vessels and other hidden dangers, thereby improving the safety of laser ablation.

[0066] On the other hand, combining the advantages of the two aspects mentioned above, in specific applications, the laser power transmitted by a single ablation fiber 200 can be controlled within a large range. Then, the laser beam is expanded and dispersed by the ablation probe 300 to reduce the laser intensity per unit area. Thus, under the condition that the total ablation power required in the ablation area is constant, the amount of ablation fiber 200 used can be reduced, ultimately achieving the goal of reducing the overall diameter of the laser ablation catheter. This can also improve the passability of the laser ablation catheter in blood vessels.

[0067] refer to Figure 2 and Figure 3 The balloon 400 is disposed on the outer wall of the catheter 100 and located on the proximal segment 130 of the catheter 100 near the transition segment 120. It is understood that the balloon 400 is connected to the distal end of the fluid-conducting tube 500, the proximal end of which is connected to a conductive fluid pressure pump. The conductive fluid pressure pump is used to inflate and deflate the balloon 400 with conductive fluid, causing the balloon 400 to expand or contract.

[0068] When the balloon 400 inflates, its outer wall can contact the side wall of the blood vessel. When the balloon 400 deflates, since it is positioned on the proximal segment 130 of the catheter 100, and the diameter of the proximal segment 130 is smaller than the diameter of the distal segment 110, the cross-sectional area of ​​the balloon 400 on the laser ablation catheter is smaller than the cross-sectional area of ​​the distal segment 110 when the balloon 400 is fully deflated. In other words, when the laser ablation catheter passes through the blood vessel, if the distal segment 110 of the catheter 100 can pass through, the balloon 400 on the catheter 100 can also pass through smoothly.

[0069] Several pairs of electrode pairs 600 are disposed on the outer wall of the catheter 100 and within the balloon 400. Each electrode pair 600 includes a positive and a negative electrode, and each positive and negative electrode pair has a corresponding wire 700 electrically connected to it. (See reference...) Figure 8 The wire 700 is connected to the shock wave pulse generator B.

[0070] After the balloon 400 is filled with conductive fluid until its sidewall contacts the blood vessel sidewall, the shock wave pulse generator B emits a pulse voltage, generating an arc discharge between the positive and negative electrodes of the same electrode pair 600, thereby generating a pulsed acoustic pressure wave within the conductive fluid inside the balloon 400. Because the sidewall of the balloon 400 is in contact with the blood vessel sidewall, the pulsed acoustic pressure wave can loosen calcified plaques attached to the inner wall of the blood vessel, as well as calcified plaques located between the intima and media that cannot be ablated by modulated lasers, without affecting the integrity of the intima during the loosening process.

[0071] Furthermore, in some embodiments of this application, the distal segment 110 of the catheter 100 is provided with a radiopaque ring, which improves the traceability of the catheter 100 and thus increases the success rate of treatment.

[0072] Further reference Figure 2 and Figure 3 In some embodiments of this application, the outer surface of the connecting section of the ablation probe 300 is a tapered surface, that is, the cross-sectional size of the ablation probe 300 increases linearly in the axial direction from its proximal end to its distal end.

[0073] The connection section 310 on the ablation probe 300 is configured in such a way that the laser reflection within the connection section 310 is more uniform, thereby improving the consistency of laser intensity in each area of ​​the ablation zone and thus enhancing the ablation effect.

[0074] Furthermore, based on the aforementioned embodiments, the ablation probe 300 and the ablation fiber 200 can be connected in the following ways.

[0075] In some embodiments, the ablation probe 300 is fused together with the ablation fiber 200. That is, the ablation probe 300 and the ablation fiber 200 are melted together by electrical discharge at the connection point, thereby creating a tapered transition at the connection point.

[0076] In other embodiments, the ablation probe 300 and the ablation fiber 200 are integrally formed. That is, both are tapered from the same thicker fiber, so that the same fiber is tapered to form sections with different diameters. The section with the larger diameter is the ablation probe 300, and the section with the smaller diameter is the ablation fiber 200. Furthermore, there is a gradual taper transition between the different sections.

[0077] This implementation method ensures that the surface of the connection between the connecting section 310 on the ablation probe 300 and the ablation fiber 200 is smooth, and the light energy loss is small during the process of the laser being transmitted from the ablation fiber 200 to the ablation probe 300 through the connecting section 310.

[0078] It is understood that in some embodiments of this application, the ablation probes 300 are arranged in an array around the guidewire cavity 1011 in a circumferential direction, that is, the outlet of the guidewire cavity 1011 in the catheter 100 is located between the ablation probes 300.

[0079] Specifically, the ablation probe 300 can be installed in the distal segment 110 in various ways.

[0080] For example, in some embodiments, the ablation probes 300 are welded together. Thus, there are no gaps between the ablation probes 300, which reduces the diameter of the distal segment 110 of the catheter 100, thereby further improving the permeability of the laser ablation catheter within the blood vessel.

[0081] For example, refer to Figure 7 In other embodiments, a fixing ring 900 is provided at the distal end 110 of the catheter 100. The fixing ring 900 has a through hole for avoiding the guidewire lumen 1011 in the catheter 100, and fixing holes are arranged in an array around the through hole in a circumferential direction. Each ablation probe 300 passes through the fixing hole to achieve fixation. In this way, the fixation of each ablation probe 300 is convenient and quick, the assembly accuracy is easy to control, and the assembly difficulty is low.

[0082] Understandably, reference Figure 4 and Figure 6 In some embodiments of this application, specifically, the electrode pair 600 includes two opposing and spaced-apart electrode elements 610. A wire 700 connected to the positive terminal of the shock wave pulse generator B is connected to one of the electrode elements 610, and a wire 700 connected to the negative terminal of the shock wave pulse generator B is connected to the other electrode element 610. The electrode elements 610 are the aforementioned positive and negative electrodes.

[0083] In practical applications, the electrode 610 can be in the form of a block, a ring, a sleeve, or a sheet. It is understood that in the case where the electrode 610 is in the form of a block, multiple electrode pairs 600 can be spaced apart along the same circumferential direction on the outer wall of the conduit 100.

[0084] In specific applications, the electrode 610 can be made of metals such as stainless steel, platinum-iridium, tungsten, and nickel.

[0085] Further reference Figure 4 and Figure 6 In the same electrode pair 600, the two electrode elements 610 are coaxial and arranged opposite each other, thus forming a discharge gap between the two electrode elements 610. For example, the gap between the two electrode elements 610 is 0.05 to 0.1 mm.

[0086] Further reference Figure 4 and Figure 5 A limiting member is provided on the outer wall of the conduit 100 to limit the axial position between the two electrode pieces 610 in the same electrode pair 600. It is understood that the limiting member is fixedly disposed on the conduit 100. For example, it can be a protrusion integrally formed on the outer wall of the conduit 100, or it can be a plug 620 inserted into the conduit 100 and connected to the electrode piece 610. Of course, the limiting member can also be in other forms.

[0087] By setting a limiting component, the stability of the axial position of the electrode 610 on the catheter 100 can be improved. When an arc discharge occurs between two electrode components 610 in the same electrode pair 600, the two electrode components 610 can maintain a stable axial position and avoid changes in the discharge gap caused by displacement. This allows the pulsed acoustic pressure wave generated in the conductive fluid inside the balloon 400 to achieve the expected effect, thus stabilizing the shockwave therapy effect of the balloon 400.

[0088] Understandably, reference Figure 4 and Figure 5 Based on the aforementioned embodiments, the catheter 100 includes an inner tube 101 and an outer tube 102.

[0089] Correspondingly, the aforementioned ablation fiber 200, ablation probe 300, liquid guide tube 500 and wire 700 are all disposed in the gap between the inner tube 101 and the outer tube 102, and the aforementioned guide wire cavity 1011 is the inner cavity of the inner tube 101.

[0090] It should be understood that the aforementioned ablation fiber 200, liquid guide tube 500 and wire 700 do not need to be fixedly installed in the gap between the inner tube 101 and the outer tube 102, while the ablation probe 300 can be fixedly installed in the distal section 110 of the catheter 100 according to the connection method in the aforementioned embodiment.

[0091] The catheter 100 is configured in such a way that the lead wire 700, the fluid guide tube 500, the ablation fiber optic cable 200 and the ablation probe 300 do not occupy the space of the guidewire lumen 1011 in the catheter 100, making the lumen wall of the guidewire lumen 1011 regular and smooth, so that imaging equipment and the like can be smoothly inserted into the lesion along the guidewire lumen 1011 to image the lesion.

[0092] Understandably, reference Figure 5 In the configuration of the conduit 100 having an inner tube 101 and an outer tube 102, the aforementioned limiting member is a plug 620.

[0093] Specifically, an insertion hole (not shown in the figure) is provided on the outer tube 102. One end of the insertion bolt 620 abuts or is fixedly connected to the electrode 610, and the other end passes through the insertion hole. In this way, the setting of the limiting member is convenient and quick, and the electrode 610 is conveniently and accurately fixed in the position outside the conduit 100.

[0094] Furthermore, it can be understood that at the same axial position on the outer wall of the catheter 100, the number of insertion plugs 620 is the same as the number of electrode components 610, and the two are set in a one-to-one correspondence.

[0095] In specific applications, depending on the arrangement of the electrode 610, the material of the plug 620 and the connection method between the plug 620 and the electrode 610 can also be different.

[0096] For example, when the electrode 610 is in the shape of a ring or a sleeve, the plug 620 can be made of the same metal material as the electrode 610, or it can be made of a non-metallic material. Specifically, when the plug 620 is made of a non-metallic material, one end of the plug 620 abuts against the electrode 610; while when the plug 620 is made of a metallic material, one end of the plug 620 can abut against the electrode 610, or it can be welded, or the plug 620 can be integrally formed with the electrode 610, and the end of the plug 620 inserted into the insertion hole is connected to the wire 700, thereby realizing the power supply to the electrode 610.

[0097] For example, when the electrode 610 is in the form of a block, the plug 620 is preferably made of metal and welded to the electrode 610. At the same time, the outer wall of the conduit 100 has the same number of insertion holes as the electrode 610. Similarly, one end of the plug 620 inserted into the insertion hole is connected to the wire 700.

[0098] Further reference Figure 5 and Figure 6 In some embodiments of this application, an insulating element 800 is provided between the electrode 610 and the outer wall of the conduit 100. The insulating element 800 may be made of insulating materials such as polytetrafluoroethylene, polyimide, ceramic, and polyamide.

[0099] In specific applications, electrode components 610 of different shapes correspond to insulating components 800 of different shapes. For example, when electrode component 610 is block-shaped, insulating component 800 is sheet-shaped; when electrode component 610 is ring-shaped or ring-shaped, insulating component 800 is ring-shaped.

[0100] The insulating component 800 is used to prevent the outer wall of the conduit 100 from being damaged due to excessive instantaneous voltage when the two electrode components 610 in the same electrode pair 600 generate an arc discharge. Correspondingly, a through hole is provided on the insulating component 800 for the plug 620 to pass through, so that the plug 620 can also fix the insulating component 800.

[0101] In other embodiments of this application, an insulating member 800 is sleeved on the outside of the conduit 100. The insulating member 800 is ring-shaped and can be made of insulating materials such as polytetrafluoroethylene, polyimide, ceramic, or polyamide. The length of the insulating member 800 is greater than or equal to the length of the electrode pair 600, and both electrode elements 610 in the same electrode pair 600 are disposed on the insulating member 800. In this way, the insulating member 800 not only provides insulation protection for the outer wall of the conduit 100 but also serves to position the electrode pair 600 during assembly.

[0102] Further reference Figure 6 Based on the aforementioned embodiments, the electrode 610 is annular; in the same electrode pair 600, a protrusion 611 extending axially along the ring is provided on the opposite side of the two electrode 610s. That is, in the same electrode pair 600, the gap between the protrusions 611 at the relative positions of the two electrode 610s is smaller than the gap between other parts of the two electrode 610s.

[0103] The two electrode elements 610 in the same electrode pair 600 are arranged in such a way that when an arc discharge occurs between the two electrode elements 610, the intensity of the arc discharge can be increased, and the discharge position on the electrode element 610 can be restricted between the two opposing protrusions 611. This allows the location of the shock wave in the balloon 400 to remain stable, thereby improving the accuracy and efficiency of clinical treatment.

[0104] It is understood that each electrode 610 may have only one protrusion 611 or multiple protrusions 611. For example, if multiple protrusions 611 are provided on the electrode 610, the protrusions 611 are arranged in an array along the circumferential direction of the end face of the electrode 610.

[0105] The above description is merely a preferred embodiment of this application and is not intended to limit this application. Any modifications, equivalent substitutions, and 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 with a shockwave balloon, characterized by, The utility model relates to a laser ablation catheter with shock wave balloon, which comprises a catheter with a guide wire lumen formed therein, a gradually changing section and a distal section connected to each other in sequence, and the diameter of the proximal section is smaller than that of the distal section; a plurality of ablation fibers arranged in the catheter; a plurality of ablation probes arranged in the distal section, each ablation probe being connected to each ablation fiber, the connecting section of the ablation probe connected to the ablation fiber being flared from the proximal section to the distal section, and the diameter of the proximal end of the ablation probe being smaller than that of the distal end; a balloon arranged outside the catheter and located at the proximal section, the balloon being connected to a liquid guide tube arranged in the catheter for charging and discharging conductive liquid to the balloon, the cross-sectional area of the laser ablation catheter with shock wave balloon at the balloon in the contracted state being smaller than that of the distal section; a plurality of electrode pairs arranged on the outer wall of the catheter and located inside the balloon, and a wire connected to the electrode pairs arranged in the catheter; each ablation probe is arranged in the circumferential direction of the guide wire lumen; each ablation probe is welded or spaced apart on the same fixed ring; the electrode pair comprises two oppositely arranged electrode members, a limiting member is arranged on the outer wall of the catheter, and the limiting member is used for limiting the axial position between the two electrode members of the same electrode pair; the limiting member is a plug, each electrode member is connected to the plug, the catheter comprises an inner tube and an outer tube, and the plug is fixedly inserted into the outer tube. The outer surface of the connecting section of the ablation probe is a tapered surface. Each ablation probe is welded or integrally formed with each ablation fiber through taper wire drawing. The ablation fiber, the wire and the liquid guide tube are arranged between the inner tube and the outer tube. An insulating member is arranged between each electrode member and the outer wall of the catheter, and the plug is arranged in the insulating member. An insulating member is arranged outside the catheter, and the two electrode members of the same electrode pair are arranged on the insulating member. The electrode member is in the form of a ring sleeve, and the opposite side of the two electrode members of the same electrode pair is provided with a protrusion extending in the axial direction of the ring sleeve. ​ ​ 2. The laser ablation catheter with a shockwave balloon of claim 1, wherein: ​ 3. The laser ablation catheter with a shockwave balloon of claim 1 or 2, wherein: ​ 4. The laser ablation catheter with a shockwave balloon of claim 1, wherein: ​ 5. The laser ablation catheter with a shockwave balloon of claim 1, wherein: ​ 6. The laser ablation catheter with a shockwave balloon of claim 1 or 4, wherein: ​ 7. The laser ablation catheter with a shockwave balloon of claim 6, wherein: ​

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