Laser-induced shock wave balloon catheter system

Abstract

The invention provides a laser-induced shock wave balloon catheter system. The laser-induced shock wave balloon catheter system comprises a balloon catheter and a laser device, the balloon catheter is used for containing a filling agent, and the laser is used for applying laser energy to the filling agent applied to the balloon catheter and enabling the filling agent to generate shock waves. The laser-induced shock wave balloon catheter system is used for treating vascular calcification lesions, and when the system works, laser generated by the laser induces the filling agent in the balloon catheter to form shock waves, so that an electrode does not need to be arranged in the balloon, the outer diameter of the balloon catheter in a pressing and holding state is reduced, and the turning performance of the balloon catheter is improved.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical devices, and particularly relates to a laser-induced shock wave balloon catheter system. Background Art

[0002] The pathological manifestations of coronary artery and peripheral vascular calcification lesions are the abnormal deposition of calcium salts in the vascular wall, resulting in vascular wall stiffness, reduced compliance, and further causing serious complications such as myocardial ischemia, thrombosis, and plaque rupture.

[0003] Traditional vascular interventional treatment methods such as simple balloon dilation and stent implantation, although improving vascular patency to a certain extent, still have various problems. For example, simple balloon dilation is prone to vascular elastic recoil, resulting in a high restenosis rate. At the same time, the balloon is difficult to fully dilate the blood vessel, and forced dilation may also lead to serious complications such as blood vessel rupture. While stent implants can effectively support blood vessels, they may be accompanied by complications such as in-stent thrombosis and intimal hyperplasia, and the long-term effects are not satisfactory. Other treatment methods such as rotational atherectomy and laser ablation can handle calcification lesions, but have problems such as complex operations and large damage to blood vessels. Against this background, shock wave balloon technology has emerged.

[0004] Shock wave balloon technology (Intravascular Lithotripsy, IVL) uses non-focused, low-energy pulsed waves to selectively rupture calcified plaques while preserving the integrity of the vascular intima, significantly improving the treatment effect of calcification lesions. This technology has been proven to be effective in treating superficial and deep calcifications and providing more ideal lumen conditions for subsequent stent implantation. However, existing shock wave balloon technologies generally use high-voltage electrode discharges, which require multiple electrodes to be arranged inside the balloon, resulting in an overly large outer diameter of the balloon, reducing the flexibility and pushability of the balloon catheter, making it difficult to push the balloon when entering tortuous blood vessels and unable to reach the lesion site smoothly. In view of this, in order to smoothly apply shock wave balloon technology, it is necessary to pre-dilate the lesion site before performing shock wave balloon technology. In addition, the introduction of electrodes and other components such as matching wires also makes the structure of the balloon catheter complex and requires high processing precision, which is not conducive to shortening the processing time of the balloon catheter, nor to improving the qualification rate and product stability of the balloon catheter. Summary of the Invention

[0005] The purpose of the present invention is to provide a laser-induced shock wave balloon catheter system, and the balloon catheter of this laser-induced shock wave balloon catheter system has a smaller outer diameter, better bending performance, low processing difficulty, and good batch stability of the product.

[0006] To achieve the above object, the present invention provides a laser-induced shock wave balloon catheter system, comprising: a balloon catheter, including a connector, a catheter body, and a balloon; the connector is a hollow structure with an inner cavity; the proximal end of the catheter body is connected to the connector, a fluid flow channel is formed on the catheter body, and the fluid flow channel communicates with the inner cavity; the balloon is connected to the distal end of the catheter body, the balloon has a filling cavity, and the filling cavity communicates with the fluid flow channel; the filling cavity, the fluid flow channel, and the inner cavity are used to accommodate a filling agent; and,

[0007] a laser, disposed outside the connector and configured to apply laser energy to the filling agent located in the inner cavity, so that the filling agent located in the inner cavity generates a shock wave, and the shock wave is transmitted to the balloon through the filling agent located in the fluid flow channel and the filling cavity.

[0008] Optionally, an opening is provided on the wall of the connector, and the opening penetrates the wall of the connector;

[0009] The laser-induced shock wave balloon catheter system further includes a light condensing structure, at least part of the light condensing structure is connected to the connector and closes the opening; the light condensing structure has an incident light surface and an emergent light surface, the incident light surface is located outside the inner cavity, the emergent light surface faces the inner cavity, and the focus on the side of the emergent light surface is located in the inner cavity;

[0010] The laser is disposed on the side of the incident light surface of the light condensing structure.

[0011] Optionally, the light condensing structure includes a plane mirror and a convex lens; the plane mirror is connected to the connector and closes the opening; the convex lens is disposed on the side of the plane mirror away from the inner cavity;

[0012] The surface of the plane mirror facing the inner cavity constitutes the emergent light surface, and the surface of the convex lens away from the plane mirror constitutes the incident light surface.

[0013] Optionally, the balloon catheter and the plane mirror constitute at least a part of a first assembly; the convex lens is connected to the laser and constitutes at least a part of a second assembly;

[0014] The first assembly and the second assembly are detachably connected.

[0015] Optionally, the light condensing structure includes a convex lens; the convex lens is connected to the connector and closes the opening; the surface of the convex lens facing the inner cavity constitutes the emergent light surface, and the surface of the convex lens away from the inner cavity constitutes the incident light surface.

[0016] Optionally, the balloon catheter further includes a one-way valve, which is connected to the connector and configured to open when the pressure in the inner cavity is less than the external pressure so that the inner cavity communicates with the external space.

[0017] Optionally, the wavelength of the laser emitted by the laser is 190 nm to 10,600 nm, and the order of magnitude of the pulse width of the laser pulse is from millisecond level to femtosecond level.

[0018] Optionally, the laser includes any one of a solid-state laser, a fiber laser, a dye laser, and a gas laser.

[0019] To achieve the above object, the present invention further provides a balloon catheter device, including:

[0020] A connector assembly, including a connector and a light-transmitting element; the connector is a hollow structure with an inner cavity, and an opening is further provided on the wall of the connector, and the opening penetrates through the wall of the connector; the light-transmitting element is connected to the connector and closes the opening;

[0021] A catheter body, having a fluid flow channel; the proximal end of the catheter body is connected to the connector, and the fluid flow channel communicates with the inner cavity; and,

[0022] A balloon, having an inflation cavity; the balloon is connected to the distal end of the catheter body, and the inflation cavity communicates with the fluid flow channel.

[0023] Optionally, the light-transmitting element is a plano-convex lens or a convex lens.

[0024] Optionally, the balloon catheter device further includes a one-way valve, which is connected to the connector and configured to open when the pressure in the inner cavity is less than the external pressure so that the inner cavity communicates with the external space.

[0025] Optionally, when the balloon is in a compressed state, the outer diameter of the balloon is 0.5 mm to 5.0 mm.

[0026] Compared with the prior art, the laser-induced shock wave balloon catheter system of the present invention has the following advantages:

[0027] The aforementioned laser-induced shock wave balloon catheter system includes a balloon catheter and a laser. The balloon catheter includes a connector, a catheter body, and a balloon. The connector is a hollow structure with an inner cavity. The proximal end of the catheter body is connected to the connector, and a fluid flow channel is formed on the catheter body and is in communication with the inner cavity. The balloon is connected to the distal end of the catheter body, and the balloon has a filling cavity that is in communication with the fluid flow channel. The filling cavity, the fluid flow channel, and the inner cavity are used to accommodate a filling agent. The laser is disposed outside the connector and is used to apply laser energy to the filling agent located in the inner cavity, so that the filling agent located in the inner cavity generates a shock wave, and the shock wave is transmitted to the balloon through the filling agent located in the fluid flow channel and the filling cavity. When using the laser-induced shock wave balloon catheter system to treat vascular calcification lesions, a shock wave is generated by laser-induced filling agent, and then the shock wave is transmitted to the balloon through the filling agent and acts on the calcified lesion site to mechanically break the calcified plaque. This method of shock wave generation and transmission enables the interior of the balloon catheter to be free of components such as electrodes and wires, greatly reducing the outer diameter of the balloon catheter in the crimped state, simplifying the structure of the balloon catheter, improving the bending performance of the distal end of the balloon catheter, reducing the manufacturing difficulty of the balloon catheter, and improving product stability. Brief Description of the Drawings

[0028] The drawings are used to better understand the present invention and do not constitute an improper limitation to the present invention. Among them:

[0029] Figure 1 is a schematic structural diagram of the laser-induced shock wave balloon catheter system provided by the present invention according to an embodiment;

[0030] Figure 2 is Figure 1 a partial structural diagram of the laser-induced shock wave balloon catheter system provided;

[0031] Figure 3 is a partial structural diagram of the laser-induced shock wave balloon catheter system provided by the present invention according to an alternative embodiment.

[0032] [Description of the reference numerals is as follows]: 100 - laser-induced shock wave balloon catheter system, 110 - balloon catheter, 111 - connector, 1111 - inner cavity, 1112 - liquid replenishing port, 112 - catheter body, 113 - balloon, 114 - one-way valve, 120 - light condensing structure, 1201 - light incident surface, 1202 - light exit surface, 121 - plano mirror, 1211 - first surface, 1212 - second surface, 122 - convex lens, 1221 - third surface, 1222 - fourth surface, 130 - laser, 101 - first assembly, 102 - second assembly. Detailed implementation manners

[0033] The following uses specific specific examples to illustrate the implementation manners of the present invention. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. The present invention can also be implemented or applied through other different specific implementation manners. Various details in this specification can also be modified or changed based on different viewpoints and applications without departing from the spirit of the present invention. It should be noted that the diagrams provided in this embodiment only illustrate the basic concept of the present invention in a schematic manner. Therefore, only the components related to the present invention are shown in the diagrams, rather than being drawn according to the number, shape, and size of the components in actual implementation. The type, quantity, and ratio of each component in actual implementation can be arbitrarily changed, and the component layout type may also be more complex.

[0034] In addition, each embodiment of the following description content has one or more technical features. However, this does not mean that those who use the present invention must implement all the technical features in any one embodiment at the same time, or can only separately implement some or all of the technical features in different embodiments. In other words, on the premise that implementation is possible, those skilled in the art can, according to the disclosure content of the present invention and depending on the design specifications or implementation requirements, selectively implement some or all of the technical features in any one embodiment, or selectively implement the combination of some or all of the technical features in multiple embodiments, thereby increasing the flexibility when implementing the present invention.

[0035] As used in this specification, the term "or" is generally used in the sense of including "and / or", unless the content clearly indicates otherwise, and the terms "install", "connect", "couple" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral connection. It can be a mechanical connection or an electrical connection. It can be directly connected or indirectly connected through an intermediate medium. It can be the internal communication of two components or the interaction relationship between two components. For those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood according to specific situations.

[0036] To make the purpose, advantages, and features of the present invention clearer, the following further details the present invention with reference to the accompanying drawings. It should be noted that the drawings are all in a very simplified form and use non-precise scales, only for the purpose of conveniently and clearly assisting in explaining the embodiments of the present invention. The same or similar reference numerals in the drawings represent the same or similar components.

[0037] Figure 1 Shows a schematic diagram of the overall structure of the laser-induced shock wave balloon catheter system 100 provided by an embodiment of the present invention. Figure 2 is Figure 1Schematic diagram of the local structure of the provided laser-induced shock wave balloon catheter system 100 Figure 3 It is a schematic diagram of the local structure of the laser-induced shock wave balloon catheter system 100 provided by another embodiment of the present invention. As Figures 1 to 3 shown, the laser-induced shock wave balloon catheter system 100 includes a balloon catheter 110 and a laser 130. The balloon catheter 110 is used to accommodate a filling agent, and the laser 130 is used to apply laser energy to the filling agent accommodated in the balloon catheter 110, and cause the filling agent to generate a shock wave.

[0038] Among them, the balloon catheter 110 includes a connector 111, a catheter body 112, and a balloon 113. The connector 111 is a hollow structure with an inner cavity 1111. A fluid flow channel (not shown in the figure) is formed on the catheter body 112. The proximal end of the catheter body 112 is connected to the connector 111, and the proximal end of the fluid flow channel is communicated with the inner cavity 1111. The balloon 113 has a filling cavity (not shown in the figure). The balloon 113 is connected to the distal end of the catheter body 112, and the filling cavity is communicated with the distal end of the fluid flow channel. The filling cavity, the fluid flow channel, and the inner cavity 1111 jointly accommodate the filling agent. The laser 130 is disposed outside the connector 111 and is used to apply laser energy to the filling agent located in the inner cavity 1111, so as to cause the filling agent located in the inner cavity 1111 to generate a shock wave. The shock wave generated in the inner cavity 1111 is transmitted to the balloon 113 through the filling agent located in the fluid flow channel and the filling cavity, and further acts on the calcified lesion.

[0039] When using the laser-induced shock wave balloon catheter system 100 to treat vascular calcified lesions, a shock wave is generated by laser induction of the filling agent located in the balloon catheter 110, and the shock wave is transmitted to the balloon 113 through the filling agent, and then acts on the calcified lesion site to mechanically break the calcified plaque. This shock wave generation and transmission method enables no need to arrange components such as electrodes and wires inside the balloon catheter 110, greatly reduces the outer diameter of the balloon catheter 110 in the crimped state, simplifies the structure of the balloon catheter 110, improves the bending performance of the distal end of the balloon catheter 110, and also reduces the manufacturing difficulty of the balloon catheter 110 and improves the product stability.

[0040] Further, an opening (not labeled in the figure) is provided on the wall of the connector 111, and the opening penetrates the wall of the connecting wall 111. The laser-induced shock wave balloon catheter system further includes a light condensing structure 120. The light condensing structure 120 is at least partially connected to the connector 111 and closes the opening. The light condensing structure 120 has a light incident surface 1201 and a light exit surface 1202. The light incident surface 1201 is located outside the inner cavity 111, the light exit surface 1202 faces the inner cavity, and the focus on the side of the light exit surface 1202 is within the inner cavity 1111. The laser 130 is disposed on the side of the light incident surface 1201 of the light condensing structure 120.

[0041] Therefore, a specific process of treating vascular calcification lesions by using the laser-induced shock wave balloon catheter system is as follows, including:

[0042] Step S1: Introduce the balloon 113 of the balloon catheter 110 into the calcification lesion site of the blood vessel by conventional means.

[0043] Step S2: Let the filling agent reach the filling cavity of the balloon 113 through the inner cavity 1111 of the connector 111 and the fluid flow path, so that the balloon 113 is filled until the outer wall of the balloon 113 abuts against the blood vessel wall. After this step is completed, the inner cavity 1111, the fluid flow path, and the filling cavity are all filled with the filling agent.

[0044] Step S3: Let the laser 130 continuously generate laser pulses. In this step, each laser pulse generated by the laser 130 is incident into the light condensing structure 120 through the light incident surface 1201, then exits from the light exit surface 1202, and then is focused to form a light spot. Since the size of the light spot is extremely small and the energy density is extremely high, the filling agent located at the light spot is vaporized or even ionized within a very short time to form a cavity, and then the cavity first expands and then collapses and disappears. The generation, expansion, and collapse of the cavity cause the filling agent around the cavity to generate a pressure change and form a shock wave, and this shock wave is transmitted to the balloon 113 through the filling agent in the fluid flow path and the filling agent in the filling cavity, and further transmitted and acts on the calcification lesion on the blood vessel wall to mechanically break the calcified plaque.

[0045] That is, in the embodiments of the present invention, the laser 130 disposed outside the connector 111 induces a shock wave in the filling agent within the balloon catheter 110. In this way, there is no need to provide an electrode for discharging and a wire for transmitting electric energy within the balloon 113, thereby greatly reducing the outer diameter of the balloon 113 in the crimped state, simplifying the structure of the balloon catheter 110, enabling the distal end of the balloon catheter 110 to have better flexibility and bending performance, being easily passed through tortuous blood vessels, and at the same time enabling the balloon catheter 110 to have the advantages of low manufacturing difficulty, short processing time, and high batch stability of the product.

[0046] In practice, when using the laser-induced shock wave balloon catheter system to treat calcified lesions of blood vessels, by reasonably configuring the operating parameters of the laser 130, the intensity of the shock wave transmitted to the balloon 113 reaches 2 MPa to 50 MPa to effectively break up calcified plaques.

[0047] Here, the filling agent is a liquid that can absorb laser energy. In practice, the filling agent is, for example, water, or physiological saline, or a contrast agent such as at least one of iohexol, iopamidol, and iodixanol, or a mixture of physiological saline and a contrast agent. When the filling agent is a mixture of physiological saline and a contrast agent, the volume ratio of the contrast agent to physiological saline can be 1:1.

[0048] In addition, when the balloon 113 is crimped, its outer diameter can be as small as 0.5 mm to 5.0 mm. The outer diameter of the filled balloon 113 can be 1.0 mm to 30.0 mm, and the length can be 5 mm to 300 mm. The length of the balloon catheter 110 is 1000 mm to 3000 mm.

[0049] The laser-induced shock wave balloon catheter system 100 also has the following characteristics: during the process of the cavitation bubble increasing, the cavitation bubble squeezes a part of the filling agent in the inner cavity 1111 of the connector 111 into the balloon 113. In response to this, a liquid replenishing port 1112 communicating with the inner cavity 111 is further provided on the connector 111. The balloon catheter 110 further includes a one-way valve 114 disposed at the liquid replenishing port 1112. The one-way valve 114 is configured to open to communicate the inner cavity 1111 with the external space when the pressure in the inner cavity 1111 is less than the external pressure, and to close to isolate the inner cavity 1111 from the external space when the pressure in the inner cavity 1111 is greater than or equal to the external pressure. "External" here refers to the outside of the balloon catheter 110.

[0050] The one-way valve 114 is used to connect to a filling agent supply device (not shown in the figure). As described above, during the cavitation bubble expansion process, the cavitation bubble squeezes a part of the filling agent in the inner cavity 1111 into the balloon 113. This causes the pressure in the inner cavity 1111 to drop and become lower than the pressure of the external filling agent supply device. At this time, the one-way valve 114 opens, enabling the filling agent supply module to replenish the filling agent into the inner cavity 1111 so that the pressure in the inner cavity 1111 increases to be equal to the external pressure. In this way, the filling agent squeezed into the balloon 113 by the cavitation bubble can be retained in the balloon 113, so that the filling pressure of the balloon 113 gradually increases, thereby gradually increasing the supporting force of the balloon 113 on the blood vessel wall to gradually expand the blood vessel and improve the blood vessel dilation effect.

[0051] In some embodiments, the step S2 can also be executed based on the one-way valve 114. In other embodiments, other fluid inlets can be further provided on the connector 111, and the step S2 can be executed based on the other fluid inlets.

[0052] In some embodiments, the light condensing structure 120 includes a plano mirror 121 and a convex lens 122. The plano mirror 121 is connected to the connector 111 and closes the opening. The convex lens 122 is disposed on the side of the plano mirror 121 facing away from the inner cavity 1111. The laser 130 is disposed on the side of the convex lens 122 away from the plano mirror 121.

[0053] In this embodiment, the two opposite surfaces of the plano mirror 121 are respectively referred to as the first surface 1211 and the second surface 1212, and the two opposite surfaces of the convex lens 122 are respectively referred to as the third surface 1221 and the fourth surface 1222. Among them, the first surface 1211 faces the inner cavity 1111, the second surface 1212 faces away from the inner cavity 1111, the third surface 1221 faces the second surface 1212, the fourth surface 1222 faces away from the second surface 1212, and the fourth surface 1222 constitutes the light incident surface 1201 of the light condensing structure 120, and the first surface 1211 constitutes the light exit surface 1202 of the light condensing structure 120.

[0054] In this way, the transmission path of the laser beam (such as the dotted line in Figure 2 ) emitted by the laser 130 is as follows: first, it is incident on the fourth surface 1222, then exits from the third surface 1221, then is incident on the second surface 1212, and then exits from the first surface 1211 and is focused.

[0055] It is easy to understand that the presence of the plano - mirror 121 causes the focus of the light - condensing structure 120 to deviate slightly from the focus on the side of the third surface 1221 of the convex lens 122 on the optical axis of the convex lens 122 (not shown in the figure).

[0056] In this embodiment, the laser - induced shock - wave balloon catheter system 100 can be divided into two parts, namely a first assembly 101 and a second assembly 102 (as Figure 1 marked). Among them, the first assembly 101 includes the balloon catheter 110 and the plano - mirror 121 connected as a whole, and the second assembly 102 includes the laser 130 and the convex lens 122 connected as a whole. Preferably, the first assembly 101 and the second assembly 102 are detachably connected, so that the first assembly 101 can be used as a disposable consumable, while the second assembly 102 can be reused.

[0057] In an alternative embodiment, as Figure 3 shown, the light - condensing structure 120 only includes the convex lens 122. That is, the convex lens 122 is arranged on the connector 111 and closes the opening. In this case, the focus of the light - condensing structure 120 is the focus on the side of the third surface 1221 of the convex lens 122.

[0058] Still, the two opposite surfaces of the convex lens 122 are respectively called the third surface 1221 and the fourth surface 1222, and the third surface 1221 faces the inner cavity 1111, and the fourth surface 1222 faces away from the inner cavity 1111. Then the fourth surface 1222 constitutes the light - incident surface 1201, and the third surface 1221 constitutes the light - emitting surface 1202. The transmission path of the laser beam (as shown by the dotted line in Figure 3 ) emitted by the laser 130 is: first incident on the fourth surface 1222, and then emitted from the third surface 1221 and focused.

[0059] In this embodiment, the laser - induced shock - wave balloon catheter system 100 can be divided into a third assembly and a fourth assembly (not marked in the figure). The third assembly includes the balloon catheter 111 and the convex lens 122 connected as a whole, and the fourth assembly includes the laser 130. The third assembly and the fourth assembly are detachably connected, so that the third assembly can be used as a disposable consumable, and the fourth assembly can be reused.

[0060] In addition, it should be noted that the connector 111 and the part of the light - condensing structure 120 arranged on the connector 111 can be integrally formed, or can be formed separately and then connected as a whole.

[0061] The laser 130 can be any one of a solid-state laser, a dye laser, a gas laser, and an optical fiber laser. As long as the wavelength of the laser beam emitted by the laser 130 is 190 nm to

[0062] 10600 nm, and the order of magnitude of the pulse width of the laser pulse is from millisecond level to femtosecond level.

[0063] Next, the laser-induced shock wave balloon catheter system 100 will be described through several embodiments.

[0064] <Example 1>

[0065] The condenser structure 120 includes the plano mirror 121 and the convex lens 122. The laser 130 is a frequency-tripled Nd:YAG laser, and the wavelength of the laser pulse it emits is 355 nm, and the pulse width is of nanosecond order. Since the laser emitted by the laser 130 is ultraviolet light, the filling agent may include a contrast agent with strong absorption ability for ultraviolet light.

[0066] In this embodiment, the pumping method of the laser 130 can be lamp pumping or semiconductor laser pumping. When lamp pumping is adopted, the laser frequency is less than 40 Hz. When semiconductor laser pumping is adopted, the laser frequency is greater than 100 Hz.

[0067] <Example 2>

[0068] The difference between this embodiment and Example 1 is that: the laser 130 is an Er:YAG laser, and the wavelength of the laser pulse it emits is 2940 nm, the pulse width is of microsecond order, and the single-pulse energy reaches several joules; the pumping method of the laser 130 is lamp pumping, and the laser frequency is not higher than 50 Hz. Since water has strong absorption for the laser with a wavelength of 2940 nm, the filling agent can be water or physiological saline.

[0069] <Example 3>

[0070] In this embodiment, the laser 130 is an ultrafast laser, that is, the pulse width of the laser pulse emitted by the laser 130 is of picosecond order or femtosecond order. The specific type of the laser 130 can be a solid-state laser or an optical fiber laser.

[0071] The repetition frequency of the ultrafast laser is relatively large, being kHz or even MHz, and the energy of a single pulse is relatively low. Therefore, the pulse train mode can be selected so that one pulse train generates one cavitation bubble. The peak light intensity of the laser pulse generated by the ultrafast laser is extremely high, and the laser beam focusing can ionize air. Therefore, the filling agent can be water, physiological saline, contrast agent, or a mixture of physiological saline and contrast agent.

[0072] In addition, an embodiment of the present invention further provides a balloon catheter device, still referring to Figures 1 to 3 , the balloon catheter device includes a connector assembly, a catheter body 112, and a balloon 113. The connector assembly includes a connector 111 and a light-transmitting element. The connector 111 is a hollow structure with an inner cavity 1111. An opening is further provided on the wall of the connector 111, and the opening penetrates the wall of the connector 111. The light-transmitting element is connected to the connector 111 and closes the opening.

[0073] In some embodiments, the light-transmitting element is a plano-convex lens 121. Thus, the balloon catheter device is at least a part of the first combination 101 described above. Therefore, the balloon catheter device can be used in combination with a convex lens 122 and a laser 130 to treat calcified lesions of blood vessels. The specific treatment process is as described in steps S1, S2, and S3 above.

[0074] In some other embodiments, the light-transmitting element is a convex lens 122. Thus, the balloon catheter device is at least a part of the third combination described above. Therefore, the balloon catheter device can be used in combination with a laser 130 to treat calcified lesions of blood vessels. The specific treatment process is also as described in steps S1, S2, and S3 above.

[0075] Furthermore, a liquid replenishing port 1112 communicating with the inner cavity 1111 can be further provided on the wall of the connector 111. And, the balloon catheter device may further include a one-way valve 114. The one-way valve 114 is provided at the liquid replenishing port 1112 and is configured to open when the pressure in the inner cavity 1111 is less than the external pressure, so that the inner cavity 1111 communicates with the external space.

[0076] In addition, the outer diameter of the balloon 113 when compressed and held can be 0.5 mm to 5.0 mm, and the outer diameter of the balloon 113 when inflated can be 1.0 mm to 30 mm, and the length can be 5 mm to 300 mm.

[0077] Although the present invention is disclosed as above, it is not limited thereto. Those skilled in the art can make various changes and modifications to the present invention without departing from the spirit and scope of the present invention. Thus, if these modifications and variations of the present invention fall within the scope of the claims of the present invention and their equivalent technologies, the present invention also intends to include these modifications and variations.

Claims

1. A laser-induced shock wave balloon catheter system, characterized in that: include: A balloon catheter comprises a connector, a catheter body and a balloon; the connector is a hollow structure with an inner cavity; the proximal end of the catheter body is connected to the connector, a fluid flow channel is formed on the catheter body, and the fluid flow channel is communicated with the inner cavity; the balloon is connected to the distal end of the catheter body, the balloon has a filling cavity, and the filling cavity is communicated with the fluid flow channel; the filling cavity, the fluid flow channel and the inner cavity are used to accommodate a filling agent; as well as, A laser is arranged outside the connector and is used to apply laser energy to the filling agent located in the inner cavity so that the filling agent located in the inner cavity generates a shock wave, and the shock wave is transmitted to the balloon via the filling agent located in the fluid flow channel and the filling cavity.

2. The laser-induced shock wave balloon catheter system according to claim 1, characterized in that: An opening is provided on the wall of the connector, and the opening passes through the wall of the connector; The laser-induced shock wave balloon catheter system further comprises a light-focusing structure, which is at least partially connected to the connector and closes the opening; the light-focusing structure has a light-entry surface and a light-exit surface, the light-entry surface is located outside the inner cavity, the light-exit surface faces the inner cavity, and a focus of one side of the light-exit surface is within the inner cavity; The laser is arranged on one side of the light incident surface of the light focusing structure.

3. The laser-induced shock wave balloon catheter system according to claim 2, characterized in that: The light focusing structure includes a flat mirror and a convex lens; the flat mirror is connected to the connector and closes the opening; the convex lens is arranged on a side of the flat mirror away from the inner cavity; The surface of the plano mirror facing the inner cavity constitutes the light emitting surface, and the surface of the convex lens away from the plano mirror constitutes the light incident surface.

4. The laser-induced shock wave balloon catheter system according to claim 3, characterized in that: The balloon catheter and the flat mirror constitute at least a part of the first assembly; the convex lens is connected to the laser and constitutes at least a part of the second assembly; The first assembly is detachably connected to the second assembly.

5. The laser-induced shock wave balloon catheter system according to claim 2, characterized in that: The light-focusing structure includes a convex lens; the convex lens is connected to the connector and closes the opening; the surface of the convex lens facing the inner cavity constitutes the light-emitting surface, and the surface of the convex lens away from the inner cavity constitutes the light-entering surface.

6. The laser-induced shock wave balloon catheter system according to claim 1, characterized in that: The balloon catheter further includes a one-way valve connected to the connector and configured to open when the pressure in the inner cavity is lower than the external pressure so as to allow the inner cavity to communicate with the external space.

7. The laser-induced shock wave balloon catheter system according to claim 1, characterized in that: The wavelength of the laser emitted by the laser is 190nm to 10600nm, and the magnitude of the pulse width of the laser pulse is in the millisecond level to the femtosecond level.

8. The laser-induced shock wave balloon catheter system according to claim 7, characterized in that: The laser includes any one of a solid laser, a fiber laser, a dye laser, and a gas laser.

9. The balloon catheter device according to claim 1, characterized in that: When the balloon is in a compressed state, the outer diameter of the balloon is 0.5 mm to 5.0 mm.

10. A balloon catheter device, characterized in that: include: A connector assembly, comprising a connector and a light-transmitting element; The connector is a hollow structure with an inner cavity, and an opening is also provided on the wall of the connector, and the opening passes through the wall of the connector; The light-transmitting element is connected to the connector and closes the opening; a catheter body having a fluid flow channel; a proximal end of the catheter body is connected to the connector, and the fluid flow channel is in communication with the inner cavity; and, The balloon has a filling cavity; the balloon is connected to the distal end of the catheter body, and the filling cavity is communicated with the fluid flow channel.

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