An adjustable bendable intravascular shockwave catheter assembly

Abstract

This utility model discloses an adjustable-bend intravascular shockwave catheter assembly, relating to the field of medical device technology. It includes a catheter, an electrode holder, a balloon, a forward shockwave generating electrode pair, a handle, a balloon control assembly, a shockwave control assembly, and a bend control assembly. The electrode holder and balloon are disposed at one end of the catheter. The forward shockwave generating electrode pair is disposed on the electrode holder and located inside the balloon. The handle is connected to the other end of the catheter. The balloon control assembly is connected to the balloon. The shockwave control assembly is connected to the forward shockwave generating electrode pair. The bend control assembly is connected to either the electrode holder or the forward shockwave generating electrode pair. The unique design of this utility model allows for compatibility with plaque-opening electrode pairs, enabling forward opening of occluded plaques, allowing the catheter to smoothly pass through lesions with high stenosis. Furthermore, the catheter can smoothly pass through various difficult tortuous blood vessels without the aid of a guidewire, allowing the catheter to successfully reach the lesion site and commence treatment.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to an adjustable bendable intravascular shockwave catheter assembly. Background Technology

[0002] Chronic total occlusion (CTO) is a term used to describe highly calcified atherosclerotic vessels, to the point that the vessel lumen is completely blocked. CTO can occur in the heart or peripheral arteries, significantly increasing the risk of heart failure and lower limb amputation. Operating room CTO cases are particularly challenging because it is difficult to pass the lesion with a conventional guidewire, resulting in nearly double the operation time and fluoroscopic exposure.

[0003] The emergence of new technologies and devices has helped cardiac teams increase the chances of successful revascularization in patients with CTO. Most importantly, a set of guidewire-passing techniques following a standardized algorithm has been developed to accommodate different lesion morphologies. Using a specially designed guidewire, skilled operators can pass through the CTO in significantly less time. Once passed, standard angioplasty balloon dilation and stent placement can be performed.

[0004] However, a significant problem remains: while the guidewire can pass through the lesion, the balloon angioplasty catheter cannot due to its larger profile. These lesions, known as balloon-passable lesions, require the use of further specialized devices called passing devices or penetrating catheters. These devices are tracked along the guidewire, and when a balloon-passable lesion is reached, various techniques are used to create a larger channel through which the balloon angioplasty catheter can pass.

[0005] Since the advent of chronic total occlusion techniques in percutaneous coronary intervention (CTO-PCI), numerous devices and techniques have been described over time, ranging from simple mechanical methods that use high-rPM catheters to drill through the lesions, to those that utilize laser and radiofrequency energy to ablate and remove calcified material.

[0006] Current angioplasty involves placing an expandable balloon inside the blood vessel. The rapid expansion of the balloon applies mechanical stress to the calcified lesions, causing them to break up. However, balloon angioplasty is only suitable for large, concentrated calcified deposits and cannot address scattered or deep-seated calcifications in the ventricles, resulting in low and incomplete calcium removal efficiency. If the patient has severe arterial calcification or a long, narrowed segment of the vessel, balloon angioplasty is less effective.

[0007] Rapid balloon dilation can cause sudden pressure changes in the blood vessel wall, easily damaging the vessel and even causing thrombosis. Furthermore, balloon dilation requires very high pressure (sometimes reaching 20 to 30 atmospheres, or even 40 atmospheres). Such pressure typically leads to a significantly increased probability of rebound stenosis, dissection, perforation, and rupture of the blood vessel. These surgical events are particularly severe in cases of eccentric calcified lesions because the balloon pressure acts on the non-calcified soft tissue.

[0008] When a patient's blood vessels have hard plaques and severe narrowing, the balloon may not be able to pass through the calcified area at all, thus failing to achieve a therapeutic effect. Therefore, more effective medical devices are needed to solve this problem. Utility Model Content

[0009] To address the aforementioned technical problems, this utility model provides an adjustable-bend intravascular shockwave catheter assembly, the specific technical solution of which is as follows:

[0010] An adjustable-bend intravascular shockwave catheter assembly includes:

[0011] catheter;

[0012] An electrode holder is located at one end of the conduit;

[0013] A balloon is connected to the end of the electrode holder furthest from the catheter;

[0014] A forward shock wave generating electrode pair is disposed on the electrode fixing base and located inside the balloon;

[0015] Handle, connected to the other end of the conduit;

[0016] Balloon control assembly, connected to the balloon;

[0017] Shock wave control component, connected to the forward shock wave generating electrode pair;

[0018] A bending control component is located inside the conduit and is connected to the electrode holder or the forward shock wave generating electrode pair.

[0019] Preferably, the forward shock wave generating electrode pair includes:

[0020] The outer electrode has a sleeve-shaped structure. One end of the outer electrode is sleeved on the electrode fixing seat, and the other end is surrounded by a plurality of first inner electrode mounting holes.

[0021] The number of inner electrodes is consistent with the number of the first inner electrode mounting holes. One end of the inner electrode is connected to the electrode fixing seat, and the other end passes through the first inner electrode mounting hole. The end face of the inner electrode is lower than the hole face of the first inner electrode mounting hole.

[0022] The injection cavity is formed between the first inner electrode mounting hole and the inner electrode.

[0023] Preferably:

[0024] The other end of the outer electrode is also provided with a connecting part, which is located at the center of a plurality of first inner electrode mounting holes;

[0025] The balloon has a ring-shaped structure, with the connecting part connected to the inner circumference of the ring-shaped structure and the outer circumference connected to the outer circumference of the catheter.

[0026] Preferably, the balloon control assembly includes an infusion tube disposed within the catheter, one end of the infusion tube being connected to the balloon, and the other end passing through the handle and extending outside the handle.

[0027] Preferably, the connecting part has a perforated structure, and the end of the infusion tube connected to the balloon has a side-opening structure, the side-opening structure comprising:

[0028] The closed end passes through the hole structure and connects to the inner circumference of the annular structure.

[0029] A first connecting hole is provided on the side of the closed end, and a second connecting hole is provided on the outer peripheral surface of the catheter opposite to the first connecting hole. The infusion tube is connected to the balloon through the first connecting hole and the second connecting hole.

[0030] Preferably:

[0031] The electrode holder has a second inner electrode mounting hole at a position opposite to the first inner electrode mounting hole, and one end of the inner electrode is fixed in the second inner electrode mounting hole;

[0032] The electrode holder has an infusion tube mounting hole at the position opposite to the connection part, and the infusion tube passes through the infusion tube mounting hole.

[0033] Preferably:

[0034] The external electrode is provided with a connecting groove on each of its two ends near one end of the conduit.

[0035] The bending control component includes two pull wires, one end of which is connected to the connecting groove and the other end is located in the handle.

[0036] Preferably:

[0037] The balloon control assembly also includes a Luer connector, which is connected to the end of the infusion tubing away from the balloon.

[0038] The shock wave control assembly includes an external electrode wire and an internal electrode wire. One end of the external electrode wire is connected to the external electrode, and the other end passes through the conduit and extends to the outside of the handle to be connected to an electrical control connector. One end of the internal electrode wire is connected to the internal electrode, and the other end passes through the conduit and extends to the outside of the handle to be connected to the electrical control connector.

[0039] The adjustable bendable intravascular shockwave catheter assembly provided by this utility model has the following beneficial effects:

[0040] 1. The guidewire-free catheter structure design is a low-profile catheter assembly.

[0041] 2. The unique design structure is compatible with plaque opening electrode pairs. The opening electrode pairs of the catheter can open the occluded plaques forward, allowing the catheter to pass smoothly through lesion sites with high stenosis.

[0042] 3. The unique bending structure and multiple bending shapes ensure that the catheter can pass smoothly through various difficult and tortuous blood vessels without the aid of a guidewire, allowing the catheter to reach the lesion site smoothly and carry out treatment. Attached Figure Description

[0043] To more clearly illustrate the technical solutions in the embodiments of this utility model or the prior art, 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 recorded in this utility model. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0044] Figure 1 A three-dimensional structural schematic diagram of the adjustable bendable intravascular shockwave catheter assembly provided for an embodiment of this utility model;

[0045] Figure 2 A connection structure diagram of the balloon and catheter provided for an embodiment of this utility model;

[0046] Figure 3 A three-dimensional structural schematic diagram of the forward shock wave generating electrode pair provided for an embodiment of this utility model;

[0047] Figure 4 An exploded view of the forward shock wave generating electrode pair provided for an embodiment of this utility model;

[0048] Figure 5 A front cross-sectional view of the distal end of the adjustable bendable intravascular shockwave catheter assembly provided in this embodiment of the utility model.

[0049] Figure 6 A schematic diagram of the single-sided bending of the adjustable bending intravascular shockwave catheter assembly provided for an embodiment of this utility model.

[0050] Figure 7 A schematic diagram of the bilateral bending of the adjustable intravascular shockwave catheter assembly provided for an embodiment of this utility model.

[0051] Figure Labels

[0052] 1-Conduit; 11-Second connecting hole;

[0053] 2-Electrode holder; 21-Second inner electrode mounting hole; 22-Infusion tubing mounting hole;

[0054] 3-Balloon;

[0055] 4-Forward shock wave generating electrode pair; 41-Outer electrode; 411-First inner electrode mounting hole; 412-Connecting part; 413-Connecting groove; 42-Inner electrode; 43-Injection chamber;

[0056] 5-Handle;

[0057] 6-Balloon control assembly; 61-Infusion tubing; 611-Closed end; 612-First connecting hole; 62-Luer connector;

[0058] 7-Shock wave control assembly; 71-Outer electrode wire; 72-Inner electrode wire; 73-Electrical control connector;

[0059] 8-Bending control component; 81-Guide wire. Detailed Implementation

[0060] To enable those skilled in the art to better understand the technical solution of this utility model, the present utility model will be described in detail below with reference to the accompanying drawings. The description in this part is only exemplary and explanatory, and should not be used to limit the scope of protection of this utility model in any way.

[0061] It should be noted that similar labels in the following figures indicate similar items; therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures.

[0062] It should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship commonly used when the product is in use. They are only for the convenience of describing the present invention 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 the present invention. In addition, the terms "first," "second," etc., are only used to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0063] Furthermore, terms such as "horizontal," "vertical," and "sag" do not imply that components must be absolutely horizontal or suspended, but rather that they can be slightly tilted. For example, "horizontal" simply means that its direction is more horizontal relative to "vertical," and does not mean that the structure must be completely horizontal, but can be slightly tilted.

[0064] In the description of this utility model, it should also be noted that, unless otherwise explicitly specified and limited, the terms "set," "install," "connect," and "link" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; 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; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model based on the specific circumstances.

[0065] Please see Figures 1 to 7 This embodiment provides an adjustable-bend intravascular shockwave catheter assembly, including a catheter 1, an electrode fixation seat 2, a balloon 3, a forward shockwave generating electrode pair 4, a handle 5, a balloon control assembly 6, a shockwave control assembly 7, and a bending control assembly 8.

[0066] Electrode holder 2 is located at one end of conduit 1.

[0067] The balloon 3 is connected to the electrode holder 2 at the end away from the catheter 1.

[0068] The forward shock wave generating electrode pair 4 is disposed on the electrode fixing seat 2 and located inside the balloon 3.

[0069] Handle 5 connects to the other end of conduit 1.

[0070] The balloon control assembly 6 is connected to the balloon 3.

[0071] Shock wave control component 7 is connected to forward shock wave generating electrode pair 4.

[0072] The bending control component 8 is located inside the conduit 1 and is connected to the electrode fixing seat 2 or the forward shock wave generating electrode pair 4.

[0073] The balloon 3 can be a compliant balloon made of soft materials such as natural latex, silicone, or TPU. The effective length of the balloon 3 after inflation is 3–18 mm, and its diameter is 2–12 mm. The catheter 1 has an effective length of 50–150 cm and a diameter of 1–3 mm. The balloon control component 6 injects liquid into the balloon 3, causing it to inflate. After inflation, the balloon 3 adheres tightly to the occlusive plaque within the blood vessel. The shock wave control component 7 controls the forward shock wave generating electrode pair 4 to generate an instantaneous high voltage arc. The expansion and collapse of the air bubble generated by the arc produce a shock wave. The shock wave generated by the electrode pair is radially conducted through the liquid inside the balloon 3 to its surface, and then further conducted to the calcified lesion. When the shock wave is forward-conducted to the calcified lesion, the compressive stress causes the calcified tissue at the vascular occlusion site to soften and rupture, allowing the balloon catheter to pass through the occlusion site and achieve a good vascular opening effect. A shock wave of appropriate intensity can destroy calcified tissue without placing additional burden on the soft tissue surrounding the calcified tissue.

[0074] The bending control component 8 can be used to control the bending of the conduit 1. The bending methods can be divided into single-sided bending and double-sided bending, and the types can be divided into F-bend, L-bend, E-bend, T-bend, FF-bend, LL-bend, EE-bend, TT-bend, etc. See details. Figure 6 and Figure 7 .

[0075] The adjustable bendable intravascular shockwave catheter assembly provided in this embodiment has the following beneficial effects:

[0076] 1. The guidewire-free catheter structure design is a low-profile catheter assembly.

[0077] 2. The unique design structure is compatible with plaque opening electrode pairs. The opening electrode pairs of the catheter can open the occluded plaques forward, allowing the catheter to pass smoothly through lesion sites with high stenosis.

[0078] 3. The unique bending structure and multiple bending shapes ensure that the catheter can pass smoothly through various difficult and tortuous blood vessels without the aid of a guidewire, allowing the catheter to reach the lesion site smoothly and carry out treatment.

[0079] Further, please see Figure 3 and Figure 4 The forward shock wave generating electrode pair 4 includes an outer electrode 41, an inner electrode 42, and a liquid injection chamber 43.

[0080] The outer electrode 41 has a sleeve-shaped structure. One end of the outer electrode 41 is sleeved on the electrode fixing seat 2, and the other end is surrounded by multiple first inner electrode mounting holes 411.

[0081] The number of inner electrodes 42 is consistent with the number of first inner electrode mounting holes 411. One end of the inner electrode 42 is connected to the electrode fixing seat 2, and the other end passes through the first inner electrode mounting hole 411. The end face of the inner electrode 42 is lower than the hole surface of the first inner electrode mounting hole 411.

[0082] The injection chamber 43 is formed between the first inner electrode mounting hole 411 and the inner electrode 42.

[0083] The outer electrode 41 is in the shape of a wine glass cylinder with a diameter of 0.1 to 1.0 mm and a wall thickness of 0.03 to 0.3 mm. The material of the outer electrode 41 can be stainless steel, tungsten, platinum-iridium, nickel, iron, steel and / or other conductive materials.

[0084] The diameter of the first inner electrode mounting hole 411 can be 0.2 to 1.0 mm, and the number of holes can be one or more, preferably three. Therefore, the number of forward electrode pairs can be one to eight.

[0085] The electrode holder 2 can be made of materials such as polyethylene, polypropylene, polycarbonate, Peek, nylon 12, nylon 66, polyurethane, polyimide, PET, etc.

[0086] The liquid inside the balloon 3 can flow into the injection chamber 43. When a momentary high pressure is applied to the electrode pair, an electric arc is generated between the outer electrode 41 and the inner electrode 42. The expansion and collapse of the bubbles generated by the electric arc are accompanied by shock waves. Since the end face of the inner electrode 42 is lower than the hole surface of the first inner electrode mounting hole 411, the shock wave is guided forward by the inner sidewall of the first inner electrode mounting hole 411.

[0087] Furthermore, the other end of the outer electrode 41 is provided with a connecting part 412, which is located at the center of a plurality of first inner electrode mounting holes 411.

[0088] The balloon 3 has a ring structure. The inner circumferential side of the ring structure is connected to the connecting part 412, and the outer circumferential side is connected to the outer circumferential surface of the catheter 1, so that the balloon 3 can cover the forward shock wave generating electrode pair 4.

[0089] Further, please see Figure 5 The balloon control assembly 6 includes an infusion tube 61 disposed within the catheter 1. One end of the infusion tube 61 is connected to the balloon 3, and the other end passes through the handle 5 and extends outside the handle 5, thereby injecting liquid into the balloon 3.

[0090] Further, please see Figure 4 and Figure 5 The connecting part 412 has a hole-type structure, and the end of the infusion tube 61 that connects to the balloon 3 has a side opening structure, which includes a closed end 611 and a first connecting hole 612.

[0091] The closed end 611 is inserted into the hole structure and connected to the inner circumference of the annular structure.

[0092] The first connecting hole 612 is opened on the side of the closed end 611. The outer peripheral surface of the catheter 1 is provided with a second connecting hole 11 opposite to the first connecting hole 612. The infusion tube 61 is connected to the balloon 3 through the first connecting hole 612 and the second connecting hole 11.

[0093] The connection between the inner circumference of the annular structure and the closed end 611, and the connection between the outer circumference and the outer circumference of the catheter 1, can be achieved through adhesive bonding, welding, or binding. The connecting part 412 is for passage through the closed end 611, and its diameter can be 0.2–2.0 mm. The first connecting hole 612 and the second connecting hole 11 can be formed by laser drilling or other methods. The closed end 611 is located at the farthest end of the infusion tube 61 to ensure that the balloon 3 can be smoothly inflated.

[0094] Further, please see Figure 4 The electrode mounting base 2 has a second inner electrode mounting hole 21 located relative to the first inner electrode mounting hole 411, and one end of the inner electrode 42 is fixed in the second inner electrode mounting hole 21.

[0095] An infusion tube mounting hole 22 is provided on the electrode holder 2 at the position opposite to the connecting part 412, and the infusion tube 61 passes through the infusion tube mounting hole 22.

[0096] The diameter of the second inner electrode mounting hole 21 can be 0.2 to 1.0 mm, and the number of the second inner electrode mounting holes 21 is consistent with the number of the first inner electrode mounting holes 411; the diameter of the infusion tube mounting hole 22 can be 0.2 to 2.0 mm.

[0097] Furthermore, the external electrode 41 is provided with a connecting groove 413 on each of the two ends of one end of the conduit 1.

[0098] The bending control component 8 includes two pull cables 81. One end of each pull cable 81 is connected to the connecting groove 413, and the other end is located in the handle 5.

[0099] The connecting groove 413 is 0.1-0.6mm wide and 0.5-5mm long. The pull wire 81 has a rectangular cross-section and can be made of stainless steel, tungsten, platinum-iridium, nickel, iron, steel and / or other materials. The pull wire 81 is fixed in the connecting groove 413 by brazing, laser welding, resistance welding, adhesive bonding and other methods.

[0100] Furthermore:

[0101] The balloon control assembly 6 also includes a Luer connector 62, which connects to the end of the infusion tubing 61 away from the balloon 3.

[0102] The shock wave control assembly 7 includes an external electrode wire 71 and an internal electrode wire 72. One end of the external electrode wire 71 is connected to the external electrode 41, and the other end passes through the conduit 1 and extends to the outside of the handle 5 to be connected to the electrical control connector 73. One end of the internal electrode wire 72 is connected to the internal electrode 42, and the other end passes through the conduit 1 and extends to the outside of the handle 5 to be connected to the electrical control connector 73.

[0103] The connection between the outer electrode 41 and the outer electrode wire 71, and the connection between the inner electrode 42 and the inner electrode wire 72, can be achieved by brazing, laser welding, resistance welding, conductive silver paste connection, etc.

[0104] Explanation of the principle:

[0105] Balloon 3 can be a compliant balloon made of soft materials such as natural latex, silicone, or TPU. The effective length of balloon 3 after inflation is 3–18 mm, and its diameter is 2–12 mm. The effective length of catheter 1 is 50–150 cm, and its diameter is 1–3 mm. Balloon control component 6 injects liquid into balloon 3, causing it to inflate. After inflation, balloon 3 adheres tightly to the occlusive plaque within the blood vessel. Shock wave control component 7 controls the forward shock wave generating electrode pair 4 to create a momentary high voltage arc. The expansion and collapse of the air bubble generated by the arc produce a shock wave. This shock wave is radially conducted through the liquid inside balloon 3 to its surface, and then further conducted to the calcified lesion. When the shock wave is forward-conducted to the calcified lesion, the compressive stress causes the calcified tissue at the vascular occlusion site to soften and rupture, allowing the balloon catheter to pass through the occlusion site and achieve a good vascular opening effect. A shock wave of appropriate intensity can destroy calcified tissue without placing additional burden on the soft tissue surrounding the calcified tissue.

[0106] The bending control component 8 can be used to control the bending of the conduit 1. The bending methods can be divided into single-sided bending and double-sided bending, and the types can be divided into F-bend, L-bend, E-bend, T-bend, FF-bend, LL-bend, EE-bend, TT-bend, etc. See details. Figure 6 and Figure 7 .

[0107] It should be noted that, in this document, the terms “comprising,” “including,” or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, article, or apparatus.

[0108] This article uses specific examples to illustrate the principles and implementation methods of this utility model. The descriptions of the above embodiments are only for the purpose of helping to understand the method and core ideas of this utility model. The above are only preferred embodiments of this utility model. It should be noted that due to the limitations of textual expression, while there are objectively infinite specific structures, those skilled in the art can make several improvements, modifications, or changes without departing from the principles of this utility model, and can also combine the above technical features in an appropriate manner. These improvements, modifications, changes, or combinations, or the direct application of the concept and technical solution of the utility model to other occasions without modification, should all be considered within the protection scope of this utility model.

Claims

1. An adjustable-bend intravascular shockwave catheter assembly, characterized in that, include: Catheter (1); An electrode holder (2) is located at one end of the conduit (1); A balloon (3) is connected to the end of the electrode holder (2) away from the catheter (1); Forward shock wave generating electrode pair (4) is disposed on the electrode fixing seat (2) and located inside the balloon (3); Handle (5), connected to the other end of the conduit (1); A balloon control assembly (6) is connected to the balloon (3); Shock wave control component (7) is connected to the forward shock wave generating electrode pair (4); The bending control component (8) is located inside the conduit (1) and is connected to the electrode fixing seat (2) or the forward shock wave generating electrode pair (4).

2. The adjustable-bend intravascular shockwave catheter assembly according to claim 1, characterized in that, The forward shock wave generating electrode pair (4) includes: The outer electrode (41) has a sleeve-shaped structure. One end of the outer electrode (41) is sleeved on the electrode fixing seat (2), and the other end is surrounded by a plurality of first inner electrode mounting holes (411). The number of inner electrodes (42) is consistent with the number of the first inner electrode mounting holes (411). One end of the inner electrode (42) is connected to the electrode fixing seat (2), and the other end is inserted into the first inner electrode mounting hole (411). The end face of the inner electrode (42) is lower than the hole surface of the first inner electrode mounting hole (411). The injection cavity (43) is formed between the first inner electrode mounting hole (411) and the inner electrode (42).

3. The adjustable-bend intravascular shockwave catheter assembly according to claim 2, characterized in that: The other end of the outer electrode (41) is also provided with a connecting part (412), which is located at the center of a plurality of first inner electrode mounting holes (411); The balloon (3) has an annular structure, with the connecting part (412) connected to the inner circumference of the annular structure and the outer circumference connected to the outer circumference of the catheter (1).

4. The adjustable-bend intravascular shockwave catheter assembly according to claim 3, characterized in that, The balloon control assembly (6) includes an infusion tube (61) disposed within the catheter (1), one end of which is connected to the balloon (3), and the other end passes through the handle (5) and extends to the outside of the handle (5).

5. The adjustable-bend intravascular shockwave catheter assembly according to claim 4, characterized in that, The connecting part (412) has a perforated structure, and the end of the infusion tube (61) connected to the balloon (3) has a side-opening structure, which includes: The closed end (611) passes through the hole structure and connects to the inner circumference of the annular structure; A first connecting hole (612) is provided on the side of the closed end (611). A second connecting hole (11) is provided on the outer peripheral surface of the catheter (1) opposite to the first connecting hole (612). The infusion tube (61) is connected to the balloon (3) through the first connecting hole (612) and the second connecting hole (11).

6. The adjustable-bend intravascular shockwave catheter assembly according to claim 4, characterized in that: The electrode holder (2) is provided with a second inner electrode mounting hole (21) at a position opposite to the first inner electrode mounting hole (411), and one end of the inner electrode (42) is fixed in the second inner electrode mounting hole (21); The electrode holder (2) is provided with an infusion tube mounting hole (22) at a position opposite to the connecting part (412), and the infusion tube (61) passes through the infusion tube mounting hole (22).

7. The adjustable-bend intravascular shockwave catheter assembly according to claim 2, characterized in that: The external electrode (41) has a connecting groove (413) on each of its two ends near one end of the conduit (1); The bending control component (8) includes two pull wires (81), one end of which is connected to the connecting groove (413) and the other end is located in the handle (5).

8. The adjustable-bend intravascular shockwave catheter assembly according to claim 4, characterized in that: The balloon control assembly (6) also includes a Luer connector (62) connected to the end of the infusion tubing (61) away from the balloon (3); The shock wave control assembly (7) includes an external electrode wire (71) and an internal electrode wire (72). One end of the external electrode wire (71) is connected to the external electrode (41), and the other end passes through the conduit (1) and extends to the outside of the handle (5) to be connected to the electrical control connector (73). One end of the internal electrode wire (72) is connected to the internal electrode (42), and the other end passes through the conduit (1) and extends to the outside of the handle (5) to be connected to the electrical control connector (73).

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