Catheter assembly and medical device

Abstract

This invention provides a catheter assembly and a medical device. The catheter assembly includes a tube body assembly, a shock wave generating assembly, and a gas-permeable liquid-blocking device. The tube body assembly forms a first receiving cavity, and the cavity wall of the first receiving cavity has a liquid inlet for supplying a liquid medium into the first receiving cavity. The first receiving cavity has a distal cavity wall away from the liquid inlet. The shock wave generating assembly is disposed within the first receiving cavity and located at the distal end of the first receiving cavity. The shock wave generating assembly is used to generate a shock wave in the liquid medium within the first receiving cavity. The gas-permeable liquid-blocking device is disposed on the distal cavity wall and is used to separate the gas in the first receiving cavity from the liquid medium, and to discharge the gas in the first receiving cavity so that the liquid medium fills the first receiving cavity. Thus, the catheter assembly has a smaller radial dimension to pass through relatively narrow positions, and effectively improves the effect of the shock wave and the stability of the catheter assembly when generating the shock wave.

Description

Technical Field

[0001] This utility model relates to the technical field of endovascular interventional devices, specifically to a catheter assembly and medical device. Background Technology

[0002] In the treatment of vascular stenosis, balloon catheter interventional surgery is increasingly accepted by doctors and patients due to its advantages such as minimal invasiveness, good efficacy, and few side effects. However, for cases of severe vascular calcification, conventional balloon catheters, and even interventional devices such as cutting balloon catheters and rotational atherectomy devices, cannot achieve sufficiently satisfactory therapeutic results due to their respective limitations. For deep vascular calcification lesions, shockwave balloon catheters, because they can lyse deep calcified tissue without damaging blood vessels and other soft tissues, have a very good therapeutic effect on highly calcified vascular tissue, and therefore have a very broad prospect for development in interventional treatment.

[0003] However, shockwave balloon catheters have a relatively large radial dimension, making them difficult to pass through occlusive lesions or even lesions with high stenosis rates in practical use. Currently, in clinical practice, it is usually necessary to first open the highly stenotic lesion site with a conventional balloon catheter before using shockwave therapy. This increases the complexity of the procedure and the cost of treatment, and results in a poor patient experience. Furthermore, when using shockwave balloon catheters for treatment, the presence of gas within the liquid medium can affect the impact of the shockwave to some extent, thus impacting the treatment outcome. Utility Model Content

[0004] To at least partially address the problems existing in the prior art, according to one aspect of the present invention, a conduit assembly is provided. The conduit assembly includes a tube body assembly, a shock wave generating assembly, and a venting-waterproofing element. The tube body assembly forms a first receiving cavity, the cavity wall of which has an injection port for supplying a liquid medium into the first receiving cavity. The first receiving cavity has a distal cavity wall located away from the injection port. The shock wave generating assembly is disposed within the first receiving cavity and located at the distal end of the first receiving cavity, and is used to generate a shock wave in the liquid medium within the first receiving cavity. The venting-waterproofing element is disposed on the distal cavity wall, and is used to separate gas from the liquid medium within the first receiving cavity and to discharge gas from the first receiving cavity, thereby filling the first receiving cavity with the liquid medium.

[0005] The catheter assembly of this invention can supply a liquid medium into the first receiving cavity through the injection port on the catheter assembly. The shock wave generating component can be located in the liquid medium and release electrical energy under the action of a power source, causing the liquid medium near the shock wave generating component to vaporize, rapidly forming and bursting bubbles to generate shock waves. The venting and liquid-sealing component can discharge the gas in the first receiving cavity. In this way, the gas in the first receiving cavity can be discharged through the existing guidewire cavity, etc., without the need to set up other gas discharge pipes. This ensures that the catheter assembly can have a small size in the radial direction, so that the catheter assembly can pass through relatively narrow positions. Furthermore, the venting and liquid-sealing component can reduce the interference of the gas in the first receiving cavity on the transmission of shock waves, effectively improving the effect of the shock waves and the stability of the catheter assembly when generating shock waves, thereby improving the treatment effect using the catheter assembly.

[0006] For example, the tube assembly includes a first part and a second part, which are connected by a breathable liquid barrier.

[0007] For example, the tube assembly is provided with a mounting hole communicating with the first receiving cavity, and the ventilated liquid-proof component is embedded in the mounting hole.

[0008] For example, the tube assembly is provided with multiple air-permeable liquid-separating grooves, and the multiple air-permeable liquid-separating grooves cooperate to form an air-permeable liquid-separating component.

[0009] For example, the tube assembly includes a first tube and a second tube sleeved outside the first tube, an injection port is provided on the second tube, a first receiving cavity for receiving liquid medium is formed between the first tube and the second tube, and a breathable liquid-proof component is provided on the first tube.

[0010] For example, the shock wave generating component includes two conductive elements and an electrode. The electrode is sleeved on the first tube body. The two conductive elements are respectively connected to the positive and negative terminals of the power supply. The discharge ends of the two conductive elements form discharge gaps with the electrodes. When the two conductive elements are excited by the power supply, they interact with the electrodes to form a current breakdown in the discharge gap, thereby generating a shock wave in the liquid medium in the first accommodating cavity.

[0011] For example, a first communicating cavity is formed inside the first tube body, a guide wire inlet is provided at the proximal end of the first communicating cavity, and a guide wire outlet is provided at the distal end of the first communicating cavity.

[0012] For example, the guidewire inlet is formed at the end of the proximal end of the second tube; or, the guidewire inlet is formed on the sidewall of the distal end of the second tube, with the guidewire inlet and guidewire outlet located on opposite sides of the ventilated liquid barrier.

[0013] For example, an electrode is disposed at the distal end of the first tube body, the electrode having a first end and a second end, and the discharge ends of two conductive elements forming discharge gaps with the first end and the second end of the electrode, respectively.

[0014] For example, the tube assembly includes a third tube and a fourth tube arranged side by side. The injection port is provided on the third tube. A second cap is provided on the distal end of the third tube. A second receiving cavity is formed inside the second cap. A first receiving cavity is formed inside the third tube. The second receiving cavity is connected to the injection port through the first receiving cavity to contain the liquid medium. A second communicating cavity is formed inside the fourth tube. A guide wire inlet and a guide wire outlet are formed at the two ends of the second communicating cavity, respectively.

[0015] For example, the shock wave generating component includes two conductive elements disposed in the cavity wall of the third tube. The two conductive elements are respectively connected to the positive and negative terminals of the power supply. The discharge ends of the two conductive elements are respectively located in the second receiving cavity. A discharge gap is formed between the discharge ends of the two conductive elements. The two conductive elements interact with each other under the excitation of the power supply, so as to form a current breakdown in the discharge gap, thereby generating a shock wave in the liquid medium in the second receiving cavity.

[0016] For example, the ventilated liquid barrier is disposed on the outer wall of the distal end of the third tube, and the ventilated liquid barrier is disposed closer to the liquid injection port than the discharge end of the conductive element.

[0017] For example, there are multiple shock wave generating components, which are spaced apart within the first receiving cavity, and / or multiple ventilated liquid-proof components, which are spaced apart on the distal cavity wall.

[0018] According to another aspect of the present invention, a medical device is also provided, including a main unit and a catheter assembly as described above. The main unit is electrically connected to a shock wave generating assembly, and the main unit is used to send an electrical excitation signal to the shock wave generating assembly to excite the shock wave generating assembly to generate shock waves in a liquid medium.

[0019] The medical device of this invention has the beneficial effects of the aforementioned catheter assembly. In addition, the main unit can precisely control the timing and intensity of the shock wave emitted by the shock wave generating component, thereby achieving high-precision control of the catheter assembly.

[0020] For example, the host is equipped with a power supply that is electrically connected to the shock wave generating component to send an electrical excitation signal to the shock wave generating component.

[0021] The above description is merely an overview of the technical solution of this utility model. In order to better understand the technical means of this utility model and to implement it in accordance with the contents of the specification, and to make the above and other objects, features and advantages of this utility model more obvious and understandable, specific embodiments of this utility model are given below. Attached Figure Description

[0022] The above and other objects, features, and advantages of this utility model will become more apparent from the more detailed description of the embodiments thereof in conjunction with the accompanying drawings. The drawings are provided to further illustrate the embodiments of this utility model and form part of the specification. They are used together with the embodiments of this utility model to explain the utility model and do not constitute a limitation thereof. In the drawings, the same reference numerals generally represent the same components or steps.

[0023] Figure 1 A perspective view of a catheter assembly according to an exemplary embodiment of the present invention is shown;

[0024] Figure 2 A front view of a catheter assembly according to an exemplary embodiment of the present invention is shown;

[0025] Figure 3 A perspective view of a catheter assembly according to another exemplary embodiment of the present invention is shown;

[0026] Figure 4 A front view of a catheter assembly according to another exemplary embodiment of the present invention is shown;

[0027] Figure 5 A partial perspective view of a catheter assembly according to yet another exemplary embodiment of the present invention is shown;

[0028] Figure 6 A partial front view of a catheter assembly according to yet another exemplary embodiment of the present invention is shown;

[0029] Figure 7 A partial perspective view of a catheter assembly according to yet another exemplary embodiment of the present invention is shown;

[0030] Figure 8 A partial front view of a catheter assembly according to yet another exemplary embodiment of the present invention is shown;

[0031] Figure 9 A partial side view of a catheter assembly according to yet another exemplary embodiment of the present invention is shown.

[0032] The components indicated by the reference numerals in the figures are as follows:

[0033] 1. Tube assembly; 11. First tube; 111. First connecting cavity; 12. Second tube; 13. Third tube; 131. Second cap; 132. Second receiving cavity; 14. Fourth tube; 15. First receiving cavity; 16. Injection port; 2. Shock wave generating assembly; 21. Electrode; 211. First end; 212. Second end; 22. Conductive component; 3. Breathable liquid-proof component; 4. Guide wire inlet; 5. Guide wire outlet; 6. Guide tube seat; 7. Cable interface; 8. First cap. Detailed Implementation

[0034] To make the objectives, technical solutions, and advantages of this utility model more apparent, exemplary embodiments according to this utility model will be described in detail below with reference to the accompanying drawings. Obviously, the described embodiments are merely some embodiments of this utility model, and not all embodiments of this utility model. It should be understood that this utility model is not limited to the exemplary embodiments described herein. Based on the embodiments of this utility model described herein, all other embodiments obtained by those skilled in the art without inventive effort should fall within the protection scope of this utility model.

[0035] In the following description, numerous details are provided to enable a thorough understanding of the present invention. However, those skilled in the art will appreciate that the following description merely illustrates preferred embodiments of the present invention, which may be practiced without one or more of these details. Furthermore, to avoid confusion with the present invention, some technical features well-known in the art have not been described in detail.

[0036] To fully understand the embodiments of this utility model, a detailed structure will be presented in the following description. Obviously, the implementation of the embodiments of this utility model is not limited to the specific details familiar to those skilled in the art. Preferred embodiments of this utility model are described in detail below; however, in addition to these detailed descriptions, this utility model may have other embodiments.

[0037] One embodiment of this utility model provides a conduit assembly that can effectively improve the effect of the generated shock wave and its stability during shock wave generation while reducing the radial dimension. A detailed description of a conduit assembly according to an embodiment of this utility model will follow with reference to the accompanying drawings.

[0038] like Figure 1As shown, the catheter assembly includes a tube body assembly 1, a shock wave generating assembly 2, and a venting and liquid-blocking element 3. The tube body assembly 1 forms a first receiving cavity 15, with an injection port 16 on its wall. The injection port 16 is used to supply liquid medium into the first receiving cavity 15. The first receiving cavity 15 has a distal cavity wall away from the injection port 16. The shock wave generating assembly 2 is disposed within the first receiving cavity 15 and located at its distal end. The shock wave generating assembly 2 is used to generate shock waves in the liquid medium within the first receiving cavity 15. The venting and liquid-blocking element 3 is disposed on the distal cavity wall. The venting and liquid-blocking element 3 is used to separate the gas from the liquid medium within the first receiving cavity 15 and to discharge the gas from the first receiving cavity 15, allowing the liquid medium to fill the first receiving cavity 15.

[0039] It should be noted that, Figures 1 to 4 The catheter assembly shown is a simplified depiction; the actual catheter assembly is a long tubular structure, with an overall length exceeding one meter, to allow for deep insertion into the blood vessel. During insertion, the proximal end of the catheter assembly can be outside the patient's body, while the distal end can be inside.

[0040] The distal end can be represented as the end furthest from the operator. Similarly, the proximal end can be represented as the end closest to the operator.

[0041] The tube assembly 1 can be made of flexible material, specifically linear nylon material. This application does not make any specific limitation; any flexible material with bio-friendly properties is acceptable.

[0042] Shock wave generating component 2 can generate a hydroelectric effect in a liquid medium. Specifically, the shock wave generating component 2, located in the liquid medium, can output a high-voltage electric field under the action of a power source. When the high-voltage electric field passes through the liquid medium, it can generate energy and vaporize, expand, and cause an explosion in the nearby liquid medium, thereby generating a shock wave. The shock wave can pass through the tube assembly 1 and propagate towards the distal end or radially of the tube assembly 1. When the catheter assembly is used to treat intravascular calcified lesions, the shock wave generated by the shock wave generating component 2 can lyse the calcified lesion tissue without affecting or damaging the blood vessel.

[0043] The liquid medium can be a sodium chloride solution, a contrast agent solution, or a mixture of the two; this application does not specifically limit this.

[0044] The ventilated liquid-proof component 3 can prevent the permeation of liquid molecules while allowing gas molecules to pass through. This allows gas within the first receiving cavity 15 to be discharged through the ventilated liquid-proof component 3 when liquid medium is injected into the first receiving cavity 15 through the injection port 16, thereby filling the first receiving cavity 15 with liquid medium. Specifically, the ventilated liquid-proof component 3 can be made of materials with microporous structures such as expanded polytetrafluoroethylene (ePTFE), high-density polyethylene fiber (Tyvek), multilayer structural materials, or composite materials; this application does not specifically limit its application to this.

[0045] The aforementioned distal cavity wall can be understood as the distal end of the cavity wall of the first receiving cavity 15, and the shape of the distal cavity wall can be cylindrical, frustum-shaped, or similar. When the distal cavity wall is frustum-shaped, its radial dimension can gradually decrease from the proximal end to the distal end to facilitate the passage of the tubular assembly 1 within the patient's blood vessels. The aforementioned ventilated liquid-proof element 3 can be disposed on the inner or outer wall of the distal cavity wall; this application does not specifically limit its placement.

[0046] like Figure 1 As shown, the tube assembly 1 may further include a conduit seat 6, which can be connected to the proximal end of the tube assembly 1. The conduit seat 6 may also be provided with a cable interface 7, which can be used to thread wires. The shock wave generating assembly 2 can be connected to a power source via the wires, thereby allowing the power source to supply electrical energy to the shock wave generating assembly 2. Figure 3 As shown, the cable interface 7 can also be set on the side wall of the tube assembly 1, thereby simplifying the connection structure of the tube assembly 1.

[0047] Traditional balloon catheters have a large radial dimension, making it difficult to pass smoothly through narrow blood vessels. The catheter assembly of this application eliminates the balloon and, through a rational layout, reduces the radial dimension of the catheter assembly, allowing it to pass smoothly through narrow blood vessels. Furthermore, compared to traditional balloon catheters, the catheter assembly of this application utilizes a venting and liquid-sealing element 3 to expel gas from the catheter, thus preventing the degradation of the liquid medium's performance due to gas, thereby reducing the effect of the shock wave generated by the shock wave generating component 2, and improving the overall stability of the catheter assembly when generating shock waves.

[0048] The catheter assembly of this invention can supply liquid medium into the first receiving cavity 15 through the injection port 16 on the catheter assembly. The shock wave generating component 2 can be located in the liquid medium and release electrical energy under the action of a power source, so that the liquid medium near the shock wave generating component 2 vaporizes, rapidly forming bubbles that expand and burst, thereby generating shock waves. The venting and liquid-blocking component 3 can discharge the gas in the first receiving cavity 15. In this way, the gas in the first receiving cavity can be discharged through the existing guidewire channel, etc., without the need to set up other gas discharge pipes, thereby ensuring that the catheter assembly can have a small size in the radial direction, so that the catheter assembly can pass through relatively narrow positions in blood vessels. Furthermore, the venting and liquid-blocking component 3 can reduce the interference of the gas in the first receiving cavity 15 on the transmission of shock waves, effectively improving the effect of shock waves and the stability of the catheter assembly when generating shock waves, thereby improving the treatment effect using the catheter assembly.

[0049] In some embodiments, the tube assembly 1 includes a first part and a second part, which are connected by a breathable liquid-proof element 3.

[0050] Specifically, the first part, the breathable liquid-proof component 3, and the second part can be connected by splicing. The splicing method can be adhesive connection or plug-in connection, etc., and this application does not specifically limit it.

[0051] In the above embodiments, by splicing the first part, the ventilated liquid-proof component 3 and the second part, it is possible to ensure that the ventilated liquid-proof component 3 can discharge the gas in the first receiving cavity 15, while also avoiding the situation where the radial dimension of the tube assembly 1 is increased due to the ventilated liquid-proof component 3 being set on the side wall of the tube assembly 1, thus effectively ensuring the miniaturization and practicality of the conduit assembly.

[0052] In some embodiments, the tube assembly 1 is provided with a mounting hole communicating with the first receiving cavity 15, and the ventilated liquid-proof component 3 is embedded in the mounting hole.

[0053] In the above embodiments, the breathable liquid-proof component 3 can be embedded in the mounting hole on the tube assembly 1, which effectively simplifies the connection structure between the two and greatly facilitates the disassembly and assembly of the breathable liquid-proof component 3 when it is necessary to replace it.

[0054] In some embodiments, the tube assembly 1 is provided with a plurality of breathable liquid-proof grooves, and the plurality of breathable liquid-proof grooves cooperate to form a breathable liquid-proof component 3.

[0055] The shape of the venting and liquid-blocking groove can be round, strip-shaped, etc. Multiple venting and liquid-blocking grooves can be spaced apart on the pipe assembly 1 to form a venting and liquid-blocking component 3.

[0056] Specifically, the tube assembly 1 can be processed to make it breathable but impermeable to liquid. For example, micropores or microslits can be made on the tube assembly 1 to form a breathable and liquid-proof component 3.

[0057] In the above embodiments, multiple air-permeable liquid-separating grooves can be directly opened on the tube assembly 1, and the air-permeable liquid-separating component 3 can be formed by the cooperation of multiple air-permeable liquid-separating grooves. In this way, while ensuring that the gas in the first receiving cavity 15 can be discharged through the air-permeable liquid-separating grooves, the manufacturing difficulty of the air-permeable liquid-separating component 3 is effectively simplified and the manufacturing cost of the air-permeable liquid-separating component 3 is reduced.

[0058] In some embodiments, such as Figures 1 to 6 As shown, the tube assembly 1 includes a first tube 11 and a second tube 12 sleeved outside the first tube 11. A liquid inlet 16 is provided on the second tube 12. A first receiving cavity 15 for receiving liquid medium is formed between the first tube 11 and the second tube 12. A breathable liquid-proof component 3 is provided on the first tube 11.

[0059] It is understood that both the first part and the second part mentioned above can belong to the first tube body 11. The ventilated liquid-blocking component 3, the first part, and the second part can be connected together to the first tube body 11. The aforementioned mounting hole can also be provided on the first tube body 11, allowing the ventilated liquid-blocking component 3 to be embedded within the mounting hole on the first tube body 11. The aforementioned plurality of ventilated liquid-blocking grooves can also be spaced apart on the first tube body 11 to form the ventilated liquid-blocking component 3. In an embodiment not shown, the ventilated liquid-blocking component 3 can be provided on the second tube body 12, or the plurality of ventilated liquid-blocking grooves can be spaced apart on the second tube body 12.

[0060] Both the first tube 11 and the second tube 12 can be hollow tubular in shape. The diameter of the second tube 12 can be larger than the diameter of the first tube 11. When the second tube 12 is fitted onto the first tube 11, a first receiving cavity 15 can be formed between the inner wall of the second tube 12 and the outer wall of the first tube 11. Of course, the first tube 11 and the second tube 12 can each be composed of a multi-cavity structure, so that other components in the catheter assembly can be inserted simultaneously, effectively improving the versatility of the catheter assembly.

[0061] The distal end of the first tube 11 can be connected to the distal end of the second tube 12, and the proximal end of the first tube 11 can be connected to the proximal end of the second tube 12, thereby forming a closed first receiving cavity 15.

[0062] The shock wave generating component 2 can be disposed on the outer wall of the first tube 11 and located inside the first receiving cavity 15. When liquid medium is injected into the first receiving cavity 15 through the injection port 16 on the second tube 12, the shock wave generating component 2 can be placed inside the liquid medium, thereby providing the shock wave generating component 2 with the environmental conditions for generating shock waves. Furthermore, the gas in the first receiving cavity 15 can be discharged into the chamber inside the first tube 11 by the venting and liquid-blocking device 3 disposed on the first tube 11, thereby filling the first receiving cavity 15 with liquid medium.

[0063] The ventilated liquid-proof component 3 can be disposed on the outer wall of the distal end of the first tube 11. The ventilated liquid-proof component 3 can be disposed further away from the injection port 16 than the shock wave generating component 2. Specifically, the injection port 16 can be disposed at the proximal end of the second tube 12. In other words, the injection port 16 can be connected to the proximal end of the first receiving cavity 15. When liquid medium is injected into the first receiving cavity 15 through the injection port 16, the liquid medium can squeeze the gas in the first receiving cavity 15 from the proximal end of the first receiving cavity 15 to the distal end of the first receiving cavity 15, so that the gas in the first receiving cavity 15 can be discharged more quickly.

[0064] The shape of the breathable liquid barrier 3 can be annular. The annular breathable liquid barrier 3 can be sleeved on the first tube 11 or constructed as part of the first tube 11. This application does not make specific limitations in this regard.

[0065] like Figures 1 to 6 As shown, the tube assembly 1 may further include a first cap 8, which can be formed on the second tube and is correspondingly disposed with respect to the shock wave generating assembly 2. A liquid medium can fill the first receiving cavity 15 between the first tube 11 and the first cap 8. The shock wave generated by the shock wave generating assembly 2 can pass through the first cap 8 and propagate outwards to reduce energy loss of the shock wave. The first cap 8 can be made of a flexible material, specifically linear nylon. This application does not impose a specific limitation; any flexible material with bio-friendly properties that can transmit shock waves is acceptable.

[0066] In the above embodiments, by using the first tube 11 and the second tube 12, it is possible to ensure that the gas in the first accommodating cavity 15 is discharged and the shock wave generating component 2 is placed in the liquid medium, while also optimizing the overall structural layout of the conduit assembly, effectively reducing the size of the conduit assembly in the radial direction, so that the conduit assembly can be applied to different application scenarios, effectively improving the practicality and versatility of the conduit assembly.

[0067] In some embodiments, such as Figures 1 to 6As shown, the shock wave generating component 2 includes two conductive elements 22 and an electrode 21. The electrode 21 is sleeved on the first tube 11. The two conductive elements 22 are respectively connected to the positive and negative terminals of the power supply. The discharge ends of the two conductive elements 22 form discharge gaps with the electrode 21. When the two conductive elements 22 are excited by the power supply, they interact with the electrode 21 to form a current breakdown in the discharge gap, thereby generating a shock wave in the liquid medium in the first accommodating cavity 15.

[0068] Electrode 21 can be made of conductive metal materials such as stainless steel, platinum-iridium alloy or nickel-titanium alloy, or flexible conductive materials such as graphite. This application does not make specific limitations in this regard.

[0069] The shape of the electrode 21 can be linear, sheet-like, ring-shaped, or spiral. This application does not specifically limit the shape of the electrode 21, but it is preferably ring-shaped. The ring-shaped electrode 21 can be sleeved on the first tube 11 to facilitate the installation and fixation of the electrode 21.

[0070] Electrode 21 can be electrically connected to a power source via conductive element 22. The power source can be located in another power supply device outside the conduit assembly. There can be two conductive elements 22, which can be arranged in pairs and located on opposite sides of electrode 21 along the radial direction of the first tube 11. The end of each conductive element 22 closest to electrode 21 can be a discharge terminal, which can be connected to the positive and negative terminals of the power source respectively to form a conductive path with electrode 21. In an embodiment not shown, the two conductive elements 22 can also be arranged on the same side of electrode 21 along the radial direction of the first tube 11.

[0071] A discharge gap can be formed between the conductive element 22 and the electrode 21. When electrical energy is supplied to the conductive element 22 through a power source, the discharge end of the conductive element 22 can break down the liquid medium within the discharge gap, thereby causing the liquid medium within the discharge gap to undergo a hydroelectric effect and generate a shock wave. The two conductive elements 22 are located on opposite sides of the electrode 21, which not only form a conductive path with the electrode 21 to ensure that the shock wave generating component 2 can generate a shock wave, but also generate shock waves simultaneously on both sides of the electrode 21. That is, the shock wave generating component 2 can generate shock waves outward along the circumferential direction of the conduit assembly, effectively increasing the radiation range of the shock wave.

[0072] The conductive element 22 can be a wire, and the shape of the conductive element 22 can be flat, thereby further reducing the size of the conduit assembly in the radial direction.

[0073] The shape of the discharge end of the conductive element 22 is not specifically limited in this application. For example, when the conductive element 22 is a wire, the end of the wire near the electrode 21 may not have an insulating layer and form an exposed conductive part. The exposed conductive part can be bent to increase the discharge area of ​​the wire, thereby improving the discharge efficiency of the wire.

[0074] In the above embodiment, the conductive element 22 can be attached to the outer wall of the first tube 11 along the length direction of the first tube 11, and the discharge gap formed between it and the electrode 21 sleeved on the first tube 11 can not only enable the shock wave generating component 2 to generate shock waves, but also simplify the connection structure of the shock wave generating component 2, reduce the volume occupied by the shock wave generating component 2, and further improve the layout rationality of the conduit assembly.

[0075] In some embodiments, such as Figure 1 and Figure 2 As shown, a first connecting cavity 111 is formed inside the first tube body 11. A guide wire inlet 4 is provided at the proximal end of the first connecting cavity 111, and a guide wire outlet 5 is provided at the distal end of the first connecting cavity 111.

[0076] A hollow cavity can be formed within the first tube 11 along its length, and the first connecting cavity 111 can be understood as the aforementioned hollow cavity. When performing vascular interventional therapy using the catheter assembly, a guidewire can be first inserted into the target location within the blood vessel, and then the catheter assembly can be threaded onto the guidewire through the guidewire inlet 4 and guidewire outlet 5. The guidewire can then guide the catheter assembly to the target location. Alternatively, the catheter assembly can be threaded onto the guidewire first, and then, when the guidewire is inserted into the target location within the blood vessel, the catheter assembly can be simultaneously moved to that target location.

[0077] The first connecting cavity 111 can be connected to the first receiving cavity 15 through the ventilated liquid-proof component 3. It can be understood that the gas in the first receiving cavity 15 can enter the first connecting cavity 111 through the ventilated liquid-proof component 3, while preventing the liquid medium from entering the first connecting cavity 111, so that the liquid medium can fill the first receiving cavity 15.

[0078] In the above embodiments, the guidewire inlet 4 and guidewire outlet 5 respectively provided at both ends of the first connecting cavity 111 can be conveniently inserted onto the guidewire, effectively simplifying the operation steps when using the catheter assembly for treatment and improving the convenience of using the catheter assembly.

[0079] In some embodiments, such as Figures 1 to 4 As shown, the guide wire inlet 4 is formed at the end near the proximal end of the second tube 12; or, the guide wire inlet 4 is formed on the side wall at the distal end of the second tube 12, and the guide wire inlet 4 and the guide wire outlet 5 are located on opposite sides of the ventilated liquid barrier 3.

[0080] like Figure 1 and Figure 2 As shown, the distal end of the first connecting cavity 111 is provided with a guide wire outlet 5, and the proximal end of the second tube 12 is provided with a guide wire inlet 4. The proximal end of the first connecting cavity 111 is connected to the guide wire inlet 4, so that the guide wire can pass through the tube assembly 1 along its length. Specifically, the proximal end of the first connecting cavity 111 can pass through the proximal end of the second tube 11 to connect with the guide wire inlet 4 on the second tube 12, and the distal end of the first connecting cavity 111 can pass through the distal end of the second tube 11 to form the guide wire outlet 5. It can be understood that the proximal end of the first connecting cavity 111 can be connected to the external environment through the guide wire inlet 4, and the distal end of the first connecting cavity 111 can be connected to the external environment through the guide wire outlet 5.

[0081] like Figure 3 and Figure 4 As shown, a guide wire inlet 4 is provided on the side wall of the distal end of the second tube 12, and the proximal end of the first communicating cavity 111 is connected to the guide wire inlet 4, thereby allowing the guide wire to enter the first communicating cavity 111 from the side wall of the distal end of the second tube 12. Further, as... Figure 3 As shown, the guide wire inlet 4 can be located close to the ventilated liquid barrier 3 on the side wall of the second tube 12, and the guide wire inlet 4 and the guide wire outlet 5 are located on opposite sides of the ventilated liquid barrier 3, which can effectively shorten the length of the first connecting cavity 111 and thus simplify the manufacturing difficulty of the first tube 11.

[0082] In the above embodiment, a guidewire inlet 4 may be provided on the side wall of the second tube 12. When the catheter assembly is inserted into the patient's body, the guidewire inlet 4 can be located inside or outside the patient's body, depending on the actual usage. Thus, when the guidewire needs to be replaced, the guidewire inlet 4 on the second tube 12 can be used for easy removal and insertion of the guidewire, further improving the flexibility, convenience, and practicality of the catheter assembly.

[0083] In some embodiments, such as Figure 5 and Figure 6 As shown, electrode 21 is disposed at the distal end of the first tube 11. Electrode 21 has a first end 211 and a second end 212. The discharge ends of the two conductive elements 22 form discharge gaps with the first end 211 and the second end 212 of electrode 21, respectively.

[0084] The second end 212 of electrode 21 is closer to the distal end of the catheter assembly 1 than the first end 211 of electrode 21. When the discharge end of one of the conductive elements 22 forms a discharge gap with the second end 212 of electrode 21, the generated shock wave can propagate not only outward along the circumferential direction of the catheter assembly, but also forward along the axial direction of the catheter assembly. The shock wave propagating forward along the axial direction of the catheter assembly can more accurately act on the target location within the blood vessel, improving the targeting and effectiveness of the treatment, and further enhancing the opening effect on relatively narrow locations within the blood vessel.

[0085] In some other embodiments, the two conductive elements 22 may form a discharge gap with the second end 212 of the electrode 21, which is not specifically limited in this application.

[0086] In the above embodiment, one of the two conductive elements 22 can form a discharge gap with the second end 212 of the electrode 21, so that the shock wave generated by the shock wave generating component 2 can propagate both along the circumferential direction of the conduit assembly and along the radial direction of the conduit assembly, thereby enabling the conduit assembly to meet more usage scenarios and usage requirements, and further improving the practicality of the conduit assembly.

[0087] In some embodiments, such as Figures 7 to 9 As shown, the tube assembly 1 includes a third tube 13 and a fourth tube 14 arranged side by side. An injection port 16 is provided on the third tube 13. A second cap 131 is provided on the distal end of the third tube 13. A second receiving cavity 132 is formed inside the second cap 131. A first receiving cavity 15 is formed inside the third tube 13. The second receiving cavity 132 is connected to the injection port 16 through the first receiving cavity 15 to contain the liquid medium. A second connecting cavity is formed inside the fourth tube 14. A guide wire inlet 4 and a guide wire outlet 5 are formed at both ends of the second connecting cavity, respectively.

[0088] In embodiments not shown, the aforementioned breathable liquid-proof component 3 may also be disposed on the third tube 13, or the aforementioned plurality of breathable liquid-proof grooves may also be disposed at intervals on the third tube 13.

[0089] Both the third tube 13 and the fourth tube 14 can be hollow tubular. The third tube 13 can accommodate the shock wave generating component 2 and the ventilated liquid-proof component 3, etc., to emit shock waves to the target location within the blood vessel. The fourth tube 14 can be used to insert a guidewire and guide the third tube 13 to the target location within the blood vessel. The proximal end of the fourth tube 14 can be located outside the patient's body to facilitate guidewire insertion. Of course, the third tube 13 and the fourth tube 14 can each be composed of a multi-lumen structure to allow simultaneous insertion of other components in the catheter assembly, effectively improving the versatility of the catheter assembly. Understandably, since the third tube 13 and the fourth tube 14 are arranged side by side, the first receiving cavity 15 within the third tube 13 and the second communicating cavity within the fourth tube 14 are not connected to avoid the guidewire affecting or interfering with the shock wave generating component 2 or the ventilated liquid-proof component 3.

[0090] The proximal end of the third tube 13 can be located outside the patient's body, and an injection port 16 can be provided on the proximal end of the third tube 13. A second cap 131 can be provided on the distal end of the third tube 13. The shape of the second cap 131 can be hemispherical, and a second receiving cavity 132 is formed inside the hemispherical second cap 131. When liquid medium is injected into the first receiving cavity 15 through the injection port 16 on the third tube 13, the liquid medium can fill the second receiving cavity 132 through the first receiving cavity 15.

[0091] The second cap 131 can be made of a flexible material to prevent hard contact between the second cap 131 at the end of the catheter assembly and the blood vessel wall as the catheter assembly moves through the patient's body, effectively reducing the risk of damage to the blood vessel wall.

[0092] In the above embodiments, the third tube 13 and the fourth tube 14, arranged side by side, can be used to perform different operations simultaneously. Specifically, liquid medium can be injected through the third tube 13 while guidewires can be passed through the fourth tube 14, effectively improving the efficiency of the catheter assembly. Furthermore, the fourth tube 14 provides an independent passage for the guidewire, effectively reducing interference between the guidewire and other components during passage, thus improving the reliability and safety of the catheter assembly.

[0093] In some embodiments, such as Figure 7 As shown, the shock wave generating assembly 2 includes two conductive elements 22 disposed in the cavity wall of the third tube 13. The two conductive elements 22 are respectively connected to the positive and negative terminals of the power supply. The discharge ends of the two conductive elements 22 are respectively located in the second receiving cavity 132. A discharge gap is formed between the discharge ends of the two conductive elements 22. The two conductive elements 22 interact under the excitation of the power supply, causing current breakdown to form in the discharge gap, so as to generate a shock wave in the liquid medium in the second receiving cavity 132.

[0094] The two conductive elements 22 can be connected to the positive and negative terminals of a power source, respectively. The power source can be located in another power supply device outside the conduit assembly. The two conductive elements 22 can be spaced apart along the length of the third tube 13 within the cavity wall of the third tube 13. This reduces the radial dimension of the third tube 13, thereby reducing the radial dimension of the conduit assembly and facilitating its passage through narrow spaces.

[0095] The ends of the two conductive elements 22 near the second cap 131 can be discharge ends. Specifically, the conductive element 22 can be a wire, and the discharge end of the conductive element 22 can be the end of the wire. By utilizing the cooperation between the conductive element 22 and the liquid medium, a conductive path can be formed, and the connection structure of the shock wave generating component 2 can be simplified, thereby reducing the manufacturing cost and difficulty of the shock wave generating component 2.

[0096] The distance between the discharge ends of the two conductive elements 22 can be less than or equal to 200 micrometers (μm), for example, 10μm, 50μm, 100μm, 150μm, 200μm, etc., to avoid the situation where the distance between the discharge ends of the two conductive elements 22 is too large, thus making it impossible to form a conductive path.

[0097] In the above embodiment, the discharge ends of the two conductive elements 22 can be located in the second receiving cavity 132 on the distal end of the third tube 13, which not only simplifies the mechanical structure of the shock wave generating assembly 2, but also allows the generated shock wave to propagate forward along the axial direction of the conduit assembly when a hydroelectric reaction occurs between the conductive element 22 and the liquid medium. Furthermore, since the discharge ends of the conductive elements 22 are located at the distal end of the third tube 13, other components of the conduit assembly can be prevented from obstructing and interfering with the forward propagating shock wave, further enhancing the effect of the shock wave generated by the shock wave generating assembly 2.

[0098] In some embodiments, such as Figure 7 and Figure 8 As shown, the ventilated liquid-proof component 3 is disposed on the outer wall of the distal end of the third tube 13, and the ventilated liquid-proof component 3 is disposed closer to the liquid injection port 16 than the discharge end of the conductive component 22.

[0099] In the above embodiment, the ventilated liquid-proof component 3 is positioned closer to the injection port 16 than the discharge end of the conductive component 22. This ensures that the ventilated liquid-proof component 3 can discharge the gas in the first accommodating cavity 15 and the second accommodating cavity 132, while also ensuring that the discharge end of the conductive component 22 is located at the far end of the third tube body 13. This allows the shock wave generated by the shock wave generating component 2 to propagate forward along the axial direction of the conduit assembly, effectively improving the rationality of the conduit assembly layout.

[0100] In some embodiments, there are multiple shock wave generating components 2, which are spaced apart within the first receiving cavity 15, and / or multiple air-permeable liquid-separating components 3, which are spaced apart on the distal cavity wall.

[0101] When the catheter assembly is used to treat intravascular calcified lesions, the operator can determine the number of shock wave generating components 2 according to actual needs and usage scenarios. For example, when a strong shock wave needs to be emitted towards the intravascular calcified lesion, multiple shock wave generating components 2 can be spaced apart within the first receiving cavity 15. The intensity of the emitted shock wave is increased by superimposing the shock waves generated by multiple shock wave generating components 2. Alternatively, when the area of ​​the intravascular calcified lesion is large, multiple shock wave generating components 2 can be used to emit shock waves simultaneously to improve the ability to treat multiple calcified lesions at the same time.

[0102] Multiple breathable liquid-proof components 3 are spaced apart on the distal cavity wall to ensure that the gas in the first receiving cavity 15 can be completely discharged, thereby further ensuring the effect of the shock wave generated by the shock wave generating component 2.

[0103] In the above embodiments, multiple shock wave generating components 2 can be spaced apart within the first receiving cavity 15 to enhance the intensity of the generated shock waves and the efficiency of treating intravascular calcified lesions. Multiple ventilated and liquid-sealing components 3 can be spaced apart on the distal cavity wall to increase the ventilated and liquid-sealing area, thereby improving the ventilation efficiency and facilitating the rapid discharge of gas from the first receiving cavity 15. This allows the catheter assembly to be applied to different usage scenarios and needs, further enhancing the practicality and versatility of the catheter assembly.

[0104] According to another aspect of the present invention, a medical device is also provided, including a main unit and a catheter assembly as described above. The main unit is electrically connected to a shock wave generating assembly 2, and the main unit is used to send an electrical excitation signal to the shock wave generating assembly 2 to excite the shock wave generating assembly 2 to generate a shock wave in a liquid medium.

[0105] The catheter assembly can be electrically connected to the main unit via wires. The main unit can send an electrical excitation signal to the shock wave generating component 2, thereby providing a basis for the stable operation of the catheter assembly and effectively ensuring the accuracy and reliability of medical device control.

[0106] The medical device of this invention has the beneficial effects of the above-mentioned catheter assembly. In addition, the main unit can precisely control the timing and intensity of the shock wave emitted by the shock wave generating component 2, thereby achieving high-precision control of the catheter assembly.

[0107] In some embodiments, a power supply is provided in the host, which is electrically connected to the shock wave generating component 2 to send an electrical excitation signal to the shock wave generating component 2.

[0108] The power supply can be installed inside the host. The power supply can directly supply power to the shock wave generating component 2, or it can store electrical energy to supply power to the shock wave generating component 2 when needed. This application does not specifically limit the power supply method.

[0109] In the above embodiment, the power supply located inside the host can continuously supply electrical energy to the shock wave generating component 2. This not only effectively ensures the performance of the medical device, but also simplifies the structural layout and connection structure of the medical device, avoiding the cumbersome assembly steps caused by setting the power supply outside the host.

[0110] Although exemplary embodiments have been described herein with reference to the accompanying drawings, it should be understood that these exemplary embodiments are merely illustrative and are not intended to limit the scope of the invention. Various changes and modifications can be made therein by those skilled in the art without departing from the scope and spirit of the invention. All such changes and modifications are intended to be included within the scope of the invention as claimed in the appended claims.

[0111] For ease of description, the term "connection" may be used herein to describe the relationship between one or more elements or features shown in the figure and other elements or features. It should be understood that "connection" may include direct connections or indirect connections via other elements or features, and this document is intended to encompass all such cases.

[0112] It should be noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the exemplary embodiments according to this application. As used herein, the singular form is intended to include the plural form as well, unless the context clearly indicates otherwise. Furthermore, it should be understood that when the terms "comprising" and / or "including" are used in this specification, they indicate the presence of features, steps, operations, parts, components, and / or combinations thereof.

[0113] It should be noted that the terms "first," "second," etc., used in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of this application described herein can be implemented in sequences other than those illustrated or described herein.

[0114] This utility model has been described through the above embodiments. However, it should be understood that the above embodiments are for illustrative purposes only and are not intended to limit the utility model to the described embodiments. Furthermore, those skilled in the art will understand that this utility model is not limited to the above embodiments, and many more variations and modifications can be made based on the teachings of this utility model, all of which fall within the scope of protection claimed by this utility model. The scope of protection of this utility model is defined by the appended claims and their equivalents.

Claims

1. A catheter assembly, characterized in that, include: A tube assembly having a first receiving cavity, the cavity wall of which has a liquid inlet for supplying a liquid medium into the cavity, the cavity having a distal cavity wall away from the liquid inlet; A shock wave generating component is disposed within the first receiving cavity and located at the distal end of the first receiving cavity, and the shock wave generating component is used to generate a shock wave in the liquid medium within the first receiving cavity. as well as A ventilated liquid-isolating component is disposed on the distal cavity wall. The ventilated liquid-isolating component is used to separate the gas and liquid medium in the first receiving cavity and to discharge the gas in the first receiving cavity so that the liquid medium fills the first receiving cavity.

2. The catheter assembly according to claim 1, characterized in that, The tube assembly includes a first part and a second part, which are connected by the breathable liquid-proof component.

3. The catheter assembly according to claim 1, characterized in that, The tube assembly is provided with a mounting hole that communicates with the first receiving cavity, and the breathable liquid-proof component is embedded in the mounting hole.

4. The catheter assembly according to claim 1, characterized in that, The tube assembly is provided with multiple air-permeable liquid-separating grooves, and the multiple air-permeable liquid-separating grooves cooperate to form the air-permeable liquid-separating component.

5. The catheter assembly according to claim 1, characterized in that, The tube assembly includes a first tube and a second tube sleeved outside the first tube. The injection port is disposed on the second tube. A first receiving cavity for receiving the medium is formed between the first tube and the second tube. The air-permeable liquid-blocking component is disposed on the first tube.

6. The catheter assembly according to claim 5, characterized in that, The shock wave generating component includes two conductive elements and an electrode. The electrode is sleeved on the first tube. The two conductive elements are respectively connected to the positive and negative terminals of the power supply. The discharge ends of the two conductive elements form discharge gaps with the electrodes. When the two conductive elements are excited by the power supply, they interact with the electrodes to form a current breakdown in the discharge gap, thereby generating a shock wave in the liquid medium in the first accommodating cavity.

7. The catheter assembly according to claim 5, characterized in that, The first tube body has a first communicating cavity inside, a guide wire inlet is provided at the proximal end of the first communicating cavity, and a guide wire outlet is provided at the distal end of the first communicating cavity.

8. The catheter assembly according to claim 7, characterized in that, The guidewire inlet is formed at the proximal end of the second tube; or, the guidewire inlet is formed on the side wall of the distal end of the second tube, and the guidewire inlet and the guidewire outlet are respectively located on opposite sides of the ventilated liquid barrier.

9. The catheter assembly according to claim 6, characterized in that, The electrode is disposed at the distal end of the first tube body. The electrode has a first end and a second end. The discharge ends of the two conductive elements form the discharge gap with the first end and the second end of the electrode, respectively.

10. The catheter assembly according to claim 1, characterized in that, The tubular assembly includes a third tubular body and a fourth tubular body arranged side by side. The injection port is located on the third tubular body. A second cap is provided on the distal end of the third tubular body. A second receiving cavity is formed inside the second cap. A first receiving cavity is formed inside the third tubular body. The second receiving cavity is connected to the injection port through the first receiving cavity to contain the liquid medium. A second communicating cavity is formed inside the fourth tubular body. A guide wire inlet and a guide wire outlet are respectively formed at both ends of the second communicating cavity.

11. The catheter assembly according to claim 10, characterized in that, The shock wave generating assembly includes two conductive elements disposed within the cavity wall of the third tube. The two conductive elements are respectively connected to the positive and negative terminals of a power source. The discharge ends of the two conductive elements are respectively located within the second accommodating cavity. A discharge gap is formed between the discharge ends of the two conductive elements. The two conductive elements interact under the excitation of the power source, causing current breakdown to occur within the discharge gap, thereby generating a shock wave in the liquid medium within the second accommodating cavity.

12. The catheter assembly according to claim 11, characterized in that, The breathable liquid-proof component is disposed on the outer wall of the distal end of the third tube, and the breathable liquid-proof component is disposed closer to the injection port than the discharge end of the conductive component.

13. The catheter assembly according to claim 1, characterized in that, The shock wave generating components are multiple, and the multiple shock wave generating components are spaced apart within the first accommodating cavity, and / or the air-permeable liquid-separating components are multiple, and the multiple air-permeable liquid-separating components are spaced apart on the distal cavity wall.

14. A medical device, characterized in that, The device includes a host and a conduit assembly as described in any one of claims 1 to 13, wherein the host is electrically connected to the shock wave generating assembly, and the host is configured to send an electrical excitation signal to the shock wave generating assembly to excite the shock wave generating assembly to generate a shock wave in a liquid medium.

15. The medical device according to claim 14, characterized in that, The host is equipped with a power supply, which is electrically connected to the shock wave generating component to send an electrical excitation signal to the shock wave generating component.

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