Pressure wave balloon catheter

Abstract

The application provides a pressure wave balloon catheter, which comprises a catheter, a balloon, a first conductor, a second conductor and a wire; the balloon is arranged at the front end of the catheter, the balloon and the peripheral wall of the catheter form a closed space, and the balloon is extended into the inside of blood vessel tissue under the driving of the catheter; the peripheral wall of the catheter is inwardly recessed to form a mounting groove; or the first conductor is coated on the peripheral wall of the catheter, the first conductor and the second conductor are connected in series on a pulse circuit through the wire, the first conductor is coated on the bottom wall of the mounting groove, the second conductor is arranged on one side of the first conductor, a communication channel is arranged between the first conductor and the second conductor, and the communication channel is used for connecting the first conductor and the second conductor and forming an electrode; and the electrode is used for generating a pressure wave in the balloon under a pulse voltage. According to the pressure wave balloon catheter provided by the application, the cross-sectional size of the balloon catheter can be reduced, and the passing property of the balloon in the blood vessel tissue can be effectively improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical equipment, and in particular to a pressure wave balloon catheter. BACKGROUND

[0002] Cardiovascular disease has always been one of the important factors of death in the world population. In the past half century, with the development of medical knowledge and medical technology, the mortality rate of cardiovascular disease has been greatly reduced. Among them, balloon dilatation angioplasty has played an important role in reducing the incidence and death of obstructive tubular arterial disease. Traditional catheter intervention therapy technology usually uses percutaneous transluminal angioplasty (PTA) to open calcified lesions in arterial and venous vessels. When the balloon expands and dilates the calcified lesions in the vessel wall, the balloon will gradually release pressure until the calcified lesions are broken; at the same time, the pressure accumulated in the balloon is released instantaneously, causing the balloon to expand to the maximum size, which may cause damage to the vessel wall.

[0003] In related technologies, the liquid-electric lithotripsy technology based on high-voltage underwater discharge is clinically applied to destroy calcified deposits or stones in the urethra or biliary tract; therefore, the high-voltage underwater discharge technology can also be applied to destroy calcified lesions in blood vessels. One or several pairs of discharge electrodes are placed in the angioplasty balloon to form a pressure wave generator, and then the electrodes are connected to the high-voltage pulse power host at the other end of the balloon dilatation catheter through wires. When the balloon is placed at the calcified lesion in the blood vessel, the host applies high-voltage pulses to make the pressure wave generator in the balloon release pressure, and the pressure wave can selectively destroy the calcified lesions in the blood vessel, while avoiding damage to the blood vessel.

[0004] However, the balloon in the related technology needs to install wires and electrodes on the balloon to generate pressure waves in the balloon, which makes the cross-sectional size of the balloon larger, resulting in poor passability of the balloon at the lesion site in the blood vessel. SUMMARY

[0005] The present application provides a pressure wave balloon catheter to solve the problem of poor passability of the balloon at the lesion site in the blood vessel due to the larger cross-sectional size of the balloon in the related technology.

[0006] According to one aspect of the present application, a pressure wave balloon catheter is provided, comprising: a catheter, a balloon, a first conductor, a second conductor, and a wire;

[0007] The balloon is arranged at the front end of the catheter, and the balloon and the peripheral wall of the catheter form a closed space, and the balloon is extended into the inside of the blood vessel tissue under the driving of the catheter;

[0008] The conduit is recessed inward on the peripheral wall inside the balloon to form a mounting groove; the first conductor and the second conductor are connected in series on a pulse circuit, the first conductor is covered on the bottom wall of the mounting groove, or the first conductor is covered on the peripheral wall of the conduit, the second conductor is located on one side of the first conductor, and a communication channel is arranged between the first conductor and the second conductor, the communication channel is used for connecting the first conductor and the second conductor and forming an electrode; the electrode is used to generate a pressure wave in the balloon under a pulse voltage.

[0009] In the embodiment of the application, the first conductor and the second conductor are embedded into the mounting groove by opening the mounting groove on the peripheral wall of the conduit, the second conductor is arranged on one side of the first conductor, and a communication channel is opened between the first conductor and the second conductor, so that the first conductor and the second conductor form an electrode through the communication channel. Therefore, the stacking of the electrode, the first conductor and the second conductor on the peripheral wall of the conduit is effectively reduced, the cross-sectional size of the conduit and the balloon can be reduced, and the passability of the balloon in the blood vessel tissue can be effectively improved.

[0010] In a possible design, the second conductor is located on the inner side of the first conductor, an insulating layer is arranged between the first conductor and the second conductor, and the communication channel penetrates the insulating layer inward from the peripheral wall of the first conductor; the communication channel includes a first hole section and a second hole section, the first hole section penetrates the first conductor, and the second hole section penetrates the insulating layer, and the aperture of the first hole section is larger than the aperture of the second hole section.

[0011] By setting the apertures of the first hole section and the second hole section to be different, a sufficient gap is formed between the first conductor and the second conductor, and the first conductor and the second conductor are not directly connected. In this way, effective arc discharge between the first conductor and the second conductor can be ensured.

[0012] In a possible design, the aperture of the first hole section is 0.25-0.6 mm, and the aperture of the second hole section is 0.1-0.4 mm.

[0013] In this way, a gap is formed between the first conductor and the second conductor, and the first conductor and the second conductor are not directly connected; and the gap is small, so that the breakdown voltage required by the electrode formed by the first conductor and the second conductor can be effectively reduced, and the loss of the electrode can be reduced.

[0014] In a possible design, the second conductor includes at least two wires, the wires are embedded in the conduit, and the front ends of the two wires are connected to the first conductor through the communication channel.

[0015] In this way, the wires are embedded in the conduit, so that the wires can be prevented from being stacked on the peripheral wall of the conduit, and the cross-sectional size of the conduit can be reduced.

[0016] In one possible design, the conduit is a solid or hollow structure, and the insulating layer includes a conduit between the first conductor and the second conductor.

[0017] In this way, using the conduit directly as an insulation layer will not increase the cross-sectional size of the conduit.

[0018] In one possible design, the thickness of the insulating layer is 0.02 to 0.2 mm.

[0019] In this way, the insulation layer will not accumulate a large thickness in the radial direction of the conduit, which can effectively reduce the cross-sectional size of the conduit.

[0020] In one possible design, the second conductor includes at least two metal sheets attached to the bottom wall of the mounting groove; the insulating layer has an annular structure and wraps around the outer periphery of the second conductor.

[0021] In one possible design, each of the metal plates corresponds to one of the communication channels, with one of the two metal plates connected to the positive terminal of the pulse power supply and the other connected to the negative terminal of the pulse power supply.

[0022] In this way, a uniform pressure wave or shock wave can be generated around the catheter, which can uniformly treat lesions on the perivascular wall.

[0023] In one possible design, the first conductor comprises a plurality of first conductors, which are arranged at intervals along the axial direction of the conduit; each first conductor has two metal plates on its inner side, and the metal plates are connected in series with the plurality of first conductors in the pulse circuit.

[0024] In this way, a uniform pressure wave or shock wave can be generated along the axial direction of the catheter, which can uniformly treat lesions on the perivascular wall.

[0025] In one possible design, the first conductor and the second conductor are spaced apart along the axial direction of the conduit and connected in series with the pulse circuit; the first conductor has a protrusion at its edge, and the second conductor has a recess at a position opposite to the protrusion, the protrusion and the recess forming the electrode.

[0026] This reduces the stacking of the second conductor and insulation layer on the catheter periphery, thereby effectively reducing the cross-sectional size of the catheter and improving the passage of the balloon through vascular tissue.

[0027] The structure of this application, as well as its other objects and beneficial effects, will be described in detail with reference to the accompanying drawings to make the description of the preferred embodiments more obvious and understandable. Attached Figure Description

[0028] To more clearly illustrate the technical solutions in the embodiments of this application 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 some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0029] Figure 1 This is a schematic diagram of the overall structure of the pressure wave balloon catheter system provided in the embodiments of this application;

[0030] Figure 2 This is a schematic diagram of the structure of the pressure wave balloon catheter provided in this application, showing the catheter located inside the balloon;

[0031] Figure 3 yes Figure 2 The main view;

[0032] Figure 4 yes Figure 3 Sectional view along line AA;

[0033] Figure 5 This is a schematic diagram of an assembly structure of the first conductor, the second conductor, and the insulating layer in an embodiment of this application;

[0034] Figure 6 yes Figure 5 The main view;

[0035] Figure 7 This is a schematic diagram of another assembly structure of the first conductor, the second conductor, and the insulating layer in an embodiment of this application;

[0036] Figure 8 This is a first cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in the embodiments of this application;

[0037] Figure 9 yes Figure 8 Cross-sectional view along the BB line;

[0038] Figure 10 This is a second cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in the embodiments of this application;

[0039] Figure 11 This is a third cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in the embodiments of this application;

[0040] Figure 12 This is the fourth cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in the embodiments of this application.

[0041] Explanation of reference numerals in the attached figures:

[0042] 10-Catheter; 20-Balloon; 30-First conductor; 40-Second conductor; 50-Wire; 60-Insulation layer; 70-Electrode; 80-Pulse power supply;

[0043] 11-Mounting groove; 31-Communication channel; 32-Protrusion; 41-Recess;

[0044] 311 - First hole section; 312 - Second hole section. Detailed Implementation

[0045] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0046] In the description of the embodiments of this application, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this application, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0047] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "linking," "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0048] In this application, unless otherwise expressly specified and limited, "above" or "below" the second feature can mean that the first feature is in direct contact with the second feature, or that the first feature is in indirect contact with the second feature through an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0049] In the description of this application, it should be understood that the terms "inner," "outer," "upper," "bottom," "front," and "rear," etc., indicate the orientation or positional relationship (if any) based on the appendix. Figure 1 The orientations or positional relationships shown are for the purpose of facilitating and simplifying the description of this application, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0050] Cardiovascular disease has long been a leading cause of death worldwide. Over the past half-century, advancements in medical knowledge and technology have significantly reduced cardiovascular mortality. Among these advancements, balloon angioplasty has played a crucial role in reducing the incidence and mortality of obstructive tubular artery disease. Traditional catheter-based interventional techniques typically employ percutaneous transluminal angioplasty (PTA) to open calcified lesions in arteries and veins. As the balloon inflates and dilates the calcified lesion in the vessel wall, it gradually releases pressure until the lesion ruptures. However, the simultaneous release of accumulated pressure within the balloon causes it to rapidly inflate to its maximum size, potentially damaging the vessel wall.

[0051] In recent years, with the development of electrohydraulic technology, a new technology based on high-voltage discharge for lithotripsy has gradually emerged. Electrohydraulic technology utilizes the "electrohydraulic effect" to generate shock waves or pressure waves in a liquid to treat calcified lesions. The main principle of the "electrohydraulic effect" is that under the action of a high-voltage, strong electric field, electrons in the liquid between the electrodes are accelerated, ionizing the liquid molecules near the electrodes. The ionized electrons in the liquid are further accelerated by the strong electric field between the electrodes, creating an electron avalanche. Plasma channels are formed in the ionized liquid molecules. As the ionization region expands, a discharge channel forms between the electrodes, and the liquid is broken down.

[0052] Once the discharge channel is formed, a large discharge current will be generated due to the very small discharge resistance. This discharge current heats the liquid surrounding the discharge channel, causing it to vaporize and expand rapidly. The rapidly expanding gas cavity generates a powerful shock wave in the liquid medium. Depending on the discharge current and discharge time, the shock wave acts on the surrounding medium in the form of impulse or impact pressure.

[0053] A pressure wave generator is formed by placing one or more pairs of discharge electrodes inside the angioplasty balloon. The electrodes are then connected via wires to a high-voltage pulse power supply unit at the other end of the balloon dilation catheter. When the balloon is placed at the calcified lesion in the blood vessel, the power supply unit applies a high-voltage pulse, causing the pressure wave generator inside the balloon to release pressure. The pressure wave selectively destroys the calcified lesion in the blood vessel while avoiding damage to the blood vessel itself.

[0054] For example, Shockwave Medical in the United States uses shockwaves or pressure waves to remove calcified lesions in blood vessels. This typically requires generating high-pressure pulses within the body, which cause the fluid filling the balloon to bubble. When these bubbles rupture, they act on the balloon wall, and subsequently on the calcified lesions, thus breaking them down.

[0055] However, electrode fabrication requires mounting leads and electrodes on the inner tube of the balloon catheter. The leads connect the electrodes to the positive and negative terminals of a pulsed power supply. This allows the power supply to provide a pulsed voltage to the electrodes, causing an electric arc breakdown between them, generating pressure or shock waves within the balloon. This increases the cross-sectional size of the balloon catheter. However, when lesions (such as calcifications) appear in vascular tissue, the cross-sectional size of the blood vessel decreases, meaning the vascular passage narrows. A larger balloon cross-section makes it difficult to pass through the narrow passage at the location of the lesion in the vascular tissue; in other words, the balloon's passage through the blood vessel is poor.

[0056] To address the aforementioned problems, this application provides a pressure wave balloon catheter. The main idea is to connect two conductors in series between the positive and negative terminals of a pulsed power supply. An inwardly extending mounting groove is formed on the peripheral wall of the catheter, and an insulating layer is placed between the two conductors. After stacking, the catheter is embedded into the mounting groove. A through-hole is formed from the outside of the outer conductor inwards, penetrating the insulating layer, thus connecting the two conductors to form an electrode for arc discharge. This prevents the electrodes from stacking on the peripheral wall of the catheter, effectively reducing the cross-sectional size of the catheter and consequently the cross-sectional size of the balloon catheter, thereby improving the balloon catheter's passage through vascular tissue.

[0057] Figure 1 This is a schematic diagram of the overall structure of the pressure wave balloon catheter provided in the embodiments of this application. Figure 2 This is a schematic diagram of the structure of the pressure wave balloon catheter provided in this application, showing the catheter located inside the balloon. Figure 3 yes Figure 2 The main view, Figure 4 yes Figure 3 A cross-sectional view along line AA.

[0058] Specifically, refer to Figures 1-4As shown, this application provides a pressure wave balloon catheter, characterized in that it includes: a catheter 10, a balloon 20, a first conductor 30, a second conductor 40, and a wire 50;

[0059] Optionally, in this embodiment of the application, the catheter 10 may be provided with a guide wire. The main function of the guide wire is to guide the front end of the pressure wave balloon catheter into the vascular tissue and along the blood vessel to the lesion site (e.g., the calcified lesion), so as to carry out targeted treatment on the lesion in the vascular tissue.

[0060] In some possible ways, a guidewire can be placed inside the catheter 10. For example, the catheter 10 can be made into a hollow structure so that the guidewire can pass through the catheter 10.

[0061] In other possible examples, a lumen structure may be provided at the tip of catheter 10 for the passage of a guidewire. For example, when catheter 10 is a solid structure.

[0062] Understandably, since the balloon 20 is to be inserted into the vascular tissue along with the tip of the catheter 10, the balloon 20 is positioned at the tip of the catheter 10, and the balloon 20 and the peripheral wall of the catheter 10 form a closed space. This closed space is connected to the filling port of the catheter seat. Conductive fluid is injected into the balloon through the filling port, and the balloon is inflated. The conductive fluid can be physiological saline or a mixture of physiological saline and contrast agent.

[0063] Reference Figure 2 , Figure 3 and Figure 4 As shown, the catheter 10 is recessed inward on the peripheral wall inside the balloon 20 to form an installation groove 11. The installation groove 11 can be formed together with the catheter 10 during its molding process. For example, it can be formed using a mold during molding. It is understood that the installation groove 11 can also be obtained through secondary processing after the catheter 10 has been molded.

[0064] The first conductor 30 and the second conductor 40 are connected in series in the pulse circuit via a wire 50. The first conductor 30 is wrapped around the bottom wall of the mounting groove 11, and the second conductor 40 is located on one side of the first conductor 30.

[0065] In some possible ways, the peripheral wall of the conduit 10 may not have an installation groove 11. In this case, the first conductor 30 covers the peripheral wall of the conduit 10, and the second conductor 40 is located inside the first conductor 30 or the second conductor 40 is arranged side by side with the first conductor 30 on the peripheral wall of the conduit 10.

[0066] Specifically, in the embodiments of this application, the first conductor 30 and the second conductor 40 can be made of metal materials such as stainless steel, copper, silver, or tungsten. The first conductor 30 has a ring structure, and the second conductor 40 can be a sheet-like metal component or a wire.

[0067] It should be noted that, since the first conductor 30 and the second conductor 40 are connected in series in the pulse circuit, the pulse circuit can be a circuit connected between the positive and negative terminals of the pulse power supply 80. Therefore, in this embodiment, a connecting channel 31 is provided between the first conductor 30 and the second conductor 40. The connecting channel 31 is used to connect the first conductor 30 and the second conductor 40 and form an electrode 70; the electrode 70 is used to generate a pressure wave inside the balloon 20 under pulse voltage.

[0068] Specifically, in the embodiments of this application, the pulse power supply 80 can be a single positive pulse power supply or a dual positive and negative pulse power supply. The positive pulse on-time width (i.e., positive pulse width) and negative pulse on-time width (i.e., negative pulse width) of the positive and negative pulse power supplies can be adjusted throughout the entire cycle.

[0069] It is understood that the pulse mode of the pulse power supply in the embodiments of this application can be a square wave pulse, also known as a single pulse. A single pulse power supply generally outputs a unidirectional pulse current with fixed parameters.

[0070] Of course, in some possible ways, the pulse power supply can also be a dual-pulse power supply or a multi-pulse power supply.

[0071] Optionally, in this embodiment, the pulse power supply 80 can provide a pulse voltage of 500 to 5000V, and its pulse width can be 0.1 to 5μs.

[0072] Optionally, in this embodiment, a catheter seat is provided at the rear end of the catheter 10, and the rear end of the catheter 10 is connected to the pulse power supply 80 through the catheter seat and a wire.

[0073] In this way, under the pulse voltage provided by the pulse power supply 80, the first conductor 30 and the second conductor 40 undergo an arc discharge phenomenon, i.e. a breakdown phenomenon, through the opened connecting channel 31, thereby making the first conductor 30 and the second conductor 40 conduct and generating pressure waves or shock waves in the balloon 20, thereby treating lesions in the vascular tissue through the balloon 20.

[0074] In this embodiment, by creating an mounting groove 11 on the peripheral wall of the catheter 10, both the first conductor 30 and the second conductor 40 are embedded within the mounting groove 11. The second conductor 40 is positioned on one side of the first conductor 30. Furthermore, by creating a connecting channel 31 between the first conductor 30 and the second conductor 40, an electrode 70 is formed between them through the connecting channel 31. This effectively reduces the stacking of the electrode 70, the first conductor 30, and the second conductor 40 on the peripheral wall of the catheter 10, thereby reducing the cross-sectional size of the catheter 10 and effectively improving the permeability of the balloon catheter in vascular tissue.

[0075] It is understandable that, since electrode 70 is essentially equivalent to a capacitor, it will disconnect the circuit in the pulse circuit. Therefore, electrode 70 can only undergo arc discharge under the pulse voltage provided by pulse power supply 80, thereby generating pressure waves or shock waves within the balloon 20. To prevent electrode 70 from being directly conductive, in this embodiment, an insulating layer 60 can be provided between the first conductor 30 and the second conductor 40; see reference... Figures 3-7 As shown, Figure 5 This is a schematic diagram of an assembly structure of the first conductor, the second conductor, and the insulating layer in an embodiment of this application. Figure 6 yes Figure 5 The main view, Figure 7 This is a schematic diagram of another assembly structure of the first conductor, the second conductor, and the insulating layer in an embodiment of this application. In this embodiment, the second conductor 40 is located inside the first conductor 30, and an insulating layer 60 is provided between the first conductor 30 and the second conductor 40. The connecting channel 31 extends from the peripheral wall of the first conductor 30 through the insulating layer 60.

[0076] In this embodiment, the insulating layer 60 can be made of one or more of the following materials: polyamide, polyimide, polyether block polyamide, etc.

[0077] The connecting channel 31 includes a first hole segment 311 and a second hole segment 312. The first hole segment 311 penetrates the first conductor 30, and the second hole segment 312 penetrates the insulating layer 60. The diameter of the first hole segment 311 is larger than the diameter of the second hole segment 312.

[0078] In other words, in this embodiment of the application, by setting the apertures of the first hole segment 311 and the second hole segment 312 to be different, sufficient gap is provided between the first conductor 30 and the second conductor 40, preventing direct conduction. This ensures effective arc discharge between the first conductor 30 and the second conductor 40.

[0079] Optionally, the diameter of the first hole section 311 is 0.25 to 0.6 mm, and the diameter of the second hole section 312 is 0.1 to 0.4 mm.

[0080] In this way, the diameter difference between the first hole segment 311 and the second hole segment 312 is only between 0.15 and 0.5 mm, that is, the radius difference is only between 0.075 and 0.25 mm. Thus, there is a gap between the first conductor 30 and the second conductor 40, and they will not be directly connected. Moreover, the small gap can effectively reduce the breakdown voltage required for the electrode 70 formed by the first conductor 30 and the second conductor 40, and can reduce electrode loss.

[0081] Optional, refer to Figures 5-7 As shown in the embodiment of this application, the first hole segment 311 can be an irregularly shaped hole. The cross-section of the first hole segment 311 can be any shape other than a circle, such as an ellipse, a polygon, or a racetrack shape.

[0082] In some possible ways, radial protrusions can be provided on the wall of the circular hole, for example... Figures 5-7 The diagram shows a planar convex portion or a sharp convex portion. It is understood that when the convex portion is a sharp convex portion, the included angle of the convex portion can be 30°, 45°, 90° or 150°; of course, it can also be any angle between 0 and 180°.

[0083] Optionally, the protrusion can be located at one end of the diameter of the first hole segment 311, meaning that only one protrusion can be provided within the first hole segment 311. Alternatively, the protrusion can be located at both ends of the diameter of the first hole segment 311, i.e., two mutually symmetrical protrusions can be provided.

[0084] This allows a tip discharge to form between the first conductor 30 and the second conductor 40, thereby increasing the arc discharge intensity of the electrode 70.

[0085] In one possible example, refer to Figure 8 and Figure 9 As shown, Figure 8 This is a first cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in the embodiments of this application. Figure 9 yes Figure 8 A cross-sectional view along line BB. In this embodiment, the second conductor 40 includes at least two wires, which are embedded in the conduit 10. The front ends of the two wires are respectively connected to the first conductor 30 through the connecting channel 31.

[0086] Specifically, the conduit 10 is a solid or hollow structure, and the insulating layer 60 includes the conduit 10 between the first conductor 30 and the second conductor 40.

[0087] In some possible configurations, the second conductor 40 may be embedded inside the conduit 10. In this case, the insulation layer 60 may be a portion of the conduit located between the first conductor 30 and the second conductor 40.

[0088] byFigure 8 As an example, in a practical implementation, the rear end of one wire can be connected to the positive terminal of the pulse power supply, and the rear end of the other wire can be connected to the negative terminal of the pulse power supply. Since the front ends of the two wires are embedded within the conduit 10, they are insulated from each other. Then, the first conductor 30 is wrapped around the peripheral wall of the conduit 10, and a connecting channel 31 is formed from the peripheral wall of the first conductor 30 inwards, extending through to the wire.

[0089] In this way, the connecting channel 31 is filled with the conductive fluid stored in the balloon 20. When the pulse power supply 80 generates a pulse voltage, the positive current flows through one of the wires and arcs with the first conductor 30 at the connecting channel 31 (i.e., the electrode 70 is broken down), thus forming a pressure wave. Furthermore, the current on the first conductor 30 arcs with the wire connected to the negative terminal through another connecting channel 31 and flows into the negative terminal of the pulse voltage. This forms the complete circuit loop of the pulse circuit.

[0090] Understandably, we should continue to refer to... Figure 8 and Figure 9 As shown, multiple first conductors 30 can be arranged axially along the conduit 10, with the multiple first conductors 30 spaced apart. At this time, the number of wires serving as second conductors 40 can be increased accordingly, for example... Figure 3 In the case where there are two first conductors 30, as shown, there can be three wires. One of them can be placed between the two first conductors 30 and form an electrode 70 with both first conductors 30.

[0091] In this way, multiple electrodes 70 can be formed along the axial direction of the catheter 10. When multiple electrodes 70 are connected in series, they can all generate electric arcs, that is, they can all generate pressure waves or shock waves. When the pressure waves or shock waves generated by multiple electrodes 70 are superimposed, the diffusion range of the pressure waves or shock waves can be increased, which can effectively target large blood vessels or eccentric lesions for treatment.

[0092] Optionally, the thickness of the insulating layer 60 is 0.02 to 0.2 mm. In this way, the insulating layer 60 will not have a large thickness in the radial direction of the conduit 10, which can effectively reduce the cross-sectional size of the conduit 10.

[0093] Optional, refer to Figure 10 and Figure 11 As shown, Figure 10 This is a second cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in this application embodiment. Figure 11This is a third cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in this application embodiment. In this application embodiment, the second conductor 40 includes at least two metal sheets attached to the bottom wall of the mounting groove 11; the insulating layer 60 has an annular structure and wraps around the outer periphery of the second conductor 40.

[0094] Specifically, each metal piece corresponds to a connecting channel 31, and one of the two metal pieces is connected to the positive terminal of the pulse power supply, while the other is connected to the negative terminal of the pulse power supply.

[0095] In this embodiment, the second conductor 40 is configured as two metal sheets. Thus, the second conductor 40 can form electrodes 70 with the first conductor 10 on both sides of the catheter 10. That is, arc discharge can occur on both sides of the catheter 10, thereby generating pressure waves or shock waves. This allows for the generation of uniform pressure waves or shock waves around the catheter 10, enabling uniform treatment of lesions on the vessel wall.

[0096] Furthermore, the first conductor 30 includes multiple first conductors 30, which are arranged at intervals along the axial direction of the conduit 10; each first conductor 30 has two metal plates on its inner side, and the metal plates are connected in series with the multiple first conductors 30 in the pulse circuit.

[0097] Specifically, refer to Figure 10 and Figure 11 As shown, when there are two first conductors 30, the current starts from the positive terminal of the pulse power supply 80 and first flows through a metal plate at the front end of the conduit 10. Figure 10 The second conductor 40 shown on the left side of the middle section, this metal sheet undergoes an arc discharge with the first conductor 30 at the front end of the conduit 10, current flows through the first conductor 30, the first conductor 30 undergoes an arc discharge with another metal sheet, this metal sheet passes through the wire 50 and connects with another metal sheet inside the first conductor 30 ( Figure 10 The second conductor 40 shown on the right is electrically connected. After the current flows through this metal plate, it arcs with the first conductor 30. The first conductor 30 then arcs with another metal plate, and the current flows back to the negative terminal of the pulse power supply 80. It can be understood that in this embodiment, the positive and negative terminals of the pulse power supply 80 can also be reversed, so that the current flows in the opposite direction as described above.

[0098] Understandable Figure 11 The connection method of the metal sheet serving as the second conductor 40 can be the same as or similar to the method described above, and will not be repeated in this embodiment. Figure 10 The difference lies in the fact that the four electrode holes are more evenly distributed around the circumference of the inner tube.

[0099] In this way, uniform pressure waves or shock waves can be generated in both the axial and circumferential directions of the conduit 10.

[0100] Optional, refer to Figure 12 As shown, Figure 12 This is the fourth cross-sectional view of the balloon and catheter in the pressure wave balloon catheter provided in the embodiments of this application.

[0101] The first conductor 30 and the second conductor 40 are arranged at intervals along the axial direction of the conduit 10 and connected in series in the pulse circuit; the first conductor 30 has a protrusion 32 on its edge, and the second conductor 40 has a recess 41 at the position opposite to the protrusion 32, and the protrusion 32 and the recess 41 form an electrode 70.

[0102] This reduces the stacking of the second conductor 40 and the insulating layer 60 on the periphery of the catheter 10, thereby effectively reducing the cross-sectional size of the catheter 10 and improving the passage of the balloon catheter through vascular tissue.

[0103] It is understood that in the embodiments of this application, the positions of the protrusion 32 and the recess 41 can also be interchanged.

[0104] It should be noted that, in this embodiment, an insulating layer 60 may also be provided between the first conductor 30 and the second conductor 40, and the connecting channel 31 penetrates the insulating layer 60 at the protrusion 32 and the recess 41, thereby forming an electrode 70 between the protrusion 32 and the recess 41.

[0105] Of course, in this embodiment, an insulating layer 60 may not be provided between the first conductor 30 and the second conductor 40. Due to the presence of the protrusion 32 and the recess 41, a tip discharge will occur between the first conductor 30 and the second conductor 40 through the protrusion 32 and the recess 41, instead of discharge from other parts.

[0106] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A pressure wave balloon catheter, characterized in that, include: The catheter (10), balloon (20), first conductor (30), second conductor (40), and wire (50); The balloon (20) is disposed at the front end of the catheter (10), and the balloon (20) and the peripheral wall of the catheter (10) form a closed space. The balloon (20) extends into the interior of the vascular tissue under the drive of the catheter (10). The catheter (10) is recessed inward on the peripheral wall inside the balloon (20) to form an installation groove (11); the first conductor (30) and the second conductor (40) are both embedded in the installation groove (11), and the first conductor (30) and the second conductor (40) are connected in series to the pulse circuit through the wire (50). The first conductor (30) covers the bottom wall of the installation groove (11), and the second conductor (40) is located inside the first conductor (30). An insulating layer (60) is provided between the first conductor (30) and the second conductor (40); the insulating layer (60) has a ring structure. The first conductor (30) and the second conductor (40) are wrapped around the outer periphery of the second conductor (40); a connecting channel (31) is provided between the first conductor (30) and the second conductor (40), the connecting channel (31) includes a first hole segment (311) and a second hole segment (312), the first hole segment (311) penetrates the first conductor (30), the second hole segment (312) penetrates the insulating layer (60), the aperture of the first hole segment (311) is larger than the aperture of the second hole segment (312), the connecting channel (31) is used to connect the first conductor (30) and the second conductor (40) and form an electrode (70); wherein, the first hole segment (311) is a circular hole; The electrode (70) is used to generate a pressure wave within the balloon (20) under a pulsed voltage.

2. The pressure wave balloon catheter according to claim 1, characterized in that, The diameter of the first hole section (311) is 0.25-0.6 mm, and the diameter of the second hole section (312) is 0.1-0.4 mm.

3. The pressure wave balloon catheter according to claim 1, characterized in that, The second conductor (40) includes at least two wires embedded in the conduit (10), and the front ends of the two wires are respectively connected to the first conductor (30) through the connecting channel (31).

4. The pressure wave balloon catheter according to claim 1, characterized in that, The thickness of the insulating layer (60) is 0.02 to 0.2 mm.

5. The pressure wave balloon catheter according to claim 1, characterized in that, The second conductor (40) includes at least two metal sheets attached to the bottom wall of the mounting groove (11).

6. The pressure wave balloon catheter according to claim 5, characterized in that, Each of the metal plates corresponds to one of the communication channels (31), and one of the two metal plates is connected to the positive terminal of the pulse power supply, while the other is connected to the negative terminal of the pulse power supply.

7. The pressure wave balloon catheter according to claim 5, characterized in that, The first conductor (30) includes a plurality of first conductors (30), which are arranged at intervals along the axial direction of the conduit (10); each first conductor (30) has two metal plates on its inner side, and the metal plates are connected in series on the pulse circuit through the plurality of first conductors (30).

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