Laser shock wave lithotripsy imaging device

Abstract

The application discloses a laser shock wave lithotripsy imaging device, which comprises a laser for generating laser beams with different parameters, a laser beam expanding and collimating system for expanding and collimating all the laser beams generated by the laser, a laser coupling part for guiding the expanded and collimated laser beams into a catheter, and the catheter with a distal end for entering a blood vessel for treatment, wherein the catheter comprises a laser shock wave optical fiber and an OCT optical fiber. The high-energy source laser can generate laser energy, which is transmitted in the catheter and output to generate a shock wave, and the shock wave can break the calcification at a treatment site including one or more blood vessel lesions in the vasculature. In the treatment process by using the laser shock wave optical fiber, the OCT optical fiber can be used to observe the treatment effect in real time, so that the laser shock wave parameters can be adjusted at any time, and the treatment effect is improved.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to a laser shockwave lithotripsy imaging device. Background Technology

[0002] Vascular stenosis is a common clinical condition, mainly caused by the deposition of calcifications and other substances on the originally smooth inner lining of blood vessels, which obstructs blood flow and can easily lead to complications or even endanger life. Therefore, vasodilation has become an urgent problem to be solved.

[0003] In existing technologies, voltage shock waves are used to create cavitation bubbles on electrode pairs, generating shock waves that impact the calcified area and break up the calcified lesions. While this method is widely used clinically, it also has some drawbacks. For example, it is impossible to obtain information about the calcification treatment progress during the procedure, thus requiring adaptive adjustments to the electrical energy, which can lead to poor lithotripsy results and even balloon rupture. Additionally, the catheter's outer diameter is often too large (minimum 1.2 mm), making it unable to pass through severely narrowed calcified lesions, necessitating procedures such as rotational atherectomy, resulting in low treatment efficiency. Summary of the Invention

[0004] An embodiment of this application provides a laser shockwave lithotripsy imaging device.

[0005] Embodiments of this application provide a laser shock wave lithotripsy imaging device, which includes:

[0006] A laser is used to generate laser beams with different parameters.

[0007] A laser beam expander and collimator system is used to expand and collimate all laser beams generated by a laser.

[0008] The laser coupling section is used to guide the expanded and collimated laser beam into the conduit.

[0009] A catheter, the distal end of which is used to enter a blood vessel for treatment;

[0010] The conduit includes laser shock wave fiber and OCT fiber.

[0011] In one embodiment, the catheter further includes:

[0012] A balloon, located at the distal end of the catheter, is used to contain the shock wave solution, and the distal tip of the laser shock wave fiber is located inside the balloon;

[0013] A central cavity extends through the entire conduit, and the laser shock wave fiber is adjacent to and fixed to the central cavity.

[0014] In one embodiment, the OCT fiber is located within the central cavity and extends to the distal end of the conduit.

[0015] In one embodiment, the OCT fiber is rotated back for imaging within the central cavity.

[0016] In one embodiment, the OCT fiber is adjacent to and fixed to the central cavity, the OCT fiber extends to the distal end of the conduit, and the distal tip of the OCT fiber is located inside the balloon.

[0017] In one embodiment, the laser coupling section includes a fused taper fiber bundle and a coupling plug;

[0018] The fused taper fiber bundle is used to receive and transmit laser beams emitted by shock wave lasers and OCT lasers;

[0019] The coupling connector is used to control the on / off state of the beam transmitted by each fiber in the fiber bundle.

[0020] In one embodiment, the coupling connector includes a host connector and a conduit connector;

[0021] The host connector includes an optical switch, which is used to control the on / off state of the beam transmitted by each fiber in the fiber bundle.

[0022] The catheter insertion end includes a multi-fiber connector for insertion and removal of the catheter.

[0023] In one embodiment, if the catheter includes a laser shock wave fiber, the distal tip of the laser shock wave fiber emits light laterally within the balloon.

[0024] If the catheter includes at least two laser shock wave fibers, the distal tips of all the laser shock wave fibers will generate shock waves of the same circumference or different circumferences within the balloon.

[0025] In one embodiment, if the conduit includes an OCT fiber, the distal tip of the OCT fiber emits light laterally.

[0026] If the conduit includes at least two OCT fibers, the distal tips of all OCT fibers can be imaged in the same or different circumferences.

[0027] In one embodiment, the laser beam expanding and collimating system includes:

[0028] Plano-concave lenses are used to expand laser beams;

[0029] A plano-convex lens is used to collimate an expanded laser beam.

[0030] Two planar mirrors are used to adjust the direction of the collimated laser beam.

[0031] This application has the following advantages over the prior art:

[0032] The laser shockwave lithotripsy imaging device provided in this application embodiment can generate laser energy through a high-energy laser source. The laser energy is transmitted in a catheter and outputs a shock wave that can break up calcifications at the treatment site, including one or more vascular lesions, within the vascular system.

[0033] The laser shockwave lithotripsy imaging device provided in this application embodiment can have a smaller catheter diameter, making it easier to pass through blood vessels with greater stenosis, thereby improving treatment efficiency.

[0034] The laser shockwave lithotripsy imaging device provided in this application includes a catheter comprising at least one laser shockwave optical fiber and at least one OCT optical fiber. This allows the OCT optical fiber to monitor the treatment effect in real time during laser shockwave optical fiber treatment, enabling the adjustment of laser shockwave parameters at any time to improve the treatment effect.

[0035] In the laser shock wave lithotripsy imaging device provided in this application embodiment, the laser coupling unit can control the on / off state of at least one laser shock wave optical fiber and / or at least one OCT optical fiber path, which can achieve precise treatment. Attached Figure Description

[0036] 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 only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0037] Figure 1 This is a schematic diagram of the structure of the laser shockwave lithotripsy imaging device provided in the embodiments of this application;

[0038] Figure 2 A schematic diagram of the conduit structure in the laser shockwave lithotripsy imaging device provided in this application embodiment. Figure 1 ;

[0039] Figure 3 A schematic diagram of the conduit structure in the laser shockwave lithotripsy imaging device provided in this application embodiment. Figure 2 ;

[0040] Figure 4 This is a schematic diagram of the optical path of the laser shockwave lithotripsy imaging device provided in the embodiments of this application;

[0041] Figure 5A schematic diagram of the conduit structure in the laser shockwave lithotripsy imaging device provided in this application embodiment. Figure 3 ;

[0042] Figure 6 A schematic diagram of the conduit structure in the laser shockwave lithotripsy imaging device provided in this application embodiment. Figure 4 ;

[0043] Figure 7 A schematic diagram of single-point lateral light emission from a laser shockwave fiber provided in this embodiment of the application. Figure 1 ;

[0044] Figure 8 A schematic diagram of single-point lateral light emission from a laser shockwave fiber provided in this embodiment of the application. Figure 2 ;

[0045] Figure 9 A schematic diagram of stepped light output from one side of the laser shock wave fiber provided in an embodiment of this application;

[0046] Figure 10 A schematic diagram of catheter dimensions provided for an embodiment of this application;

[0047] Figure 11 A schematic diagram of a two-layer laser shockwave fiber provided in an embodiment of this application. Detailed Implementation

[0048] 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, and 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.

[0049] In the description of this application, it should be understood that the terms "center", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0050] In the description of this application, it should be noted that, unless otherwise expressly specified and limited, the terms "installation", "connection" and "joining" should be interpreted broadly, for example, they can refer to fixed connection, detachable connection, or integral connection; for those skilled in the art, the specific meaning of the above terms in this application can be understood according to the specific circumstances.

[0051] The terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, unless otherwise stated, "a plurality of" means two or more.

[0052] like Figure 1-11 As shown, it illustrates a schematic diagram of the structure of the laser shockwave lithotripsy imaging device provided in an embodiment of this application.

[0053] Reference Figures 1-3 The laser shockwave lithotripsy imaging device provided in this application embodiment may include:

[0054] Laser 10 is used to generate laser beams with different parameters;

[0055] The laser beam expanding and collimating system 20 is used to expand and collimate all the laser beams generated by the laser 10.

[0056] The laser coupling part 30 is used to guide the expanded and collimated laser beam into the conduit 40;

[0057] Catheter 40, the distal end of which is used to enter a blood vessel for treatment;

[0058] The conduit 40 includes a laser shock wave fiber 41 and an OCT fiber 42.

[0059] Specifically, the laser shockwave fiber 41 can output a first laser beam to generate a shock wave that breaks up calcifications. The OCT fiber 42 can output a second laser beam to achieve vascular imaging, observe the process and effect of calcification breaking up in real time, and then adjust the parameters of the first laser beam. That is, the energy of the first laser beam is adjusted by observing the effect of calcification breaking up in the blood vessel through the OCT fiber 42. If the calcifications are not broken up, the energy of the first laser beam needs to be increased.

[0060] The laser shockwave lithotripsy imaging device provided in this embodiment generates laser energy through a high-energy laser source. This laser energy is transmitted within a catheter and outputs a shockwave. The shockwave can break up calcifications at the treatment site, including one or more vascular lesions, within the vascular system. Furthermore, the catheter includes a laser shockwave fiber optic cable and an OCT fiber optic cable, allowing for real-time monitoring of the treatment effect during laser shockwave fiber optic treatment. This enables adjustments to the laser shockwave parameters as needed to improve the treatment outcome.

[0061] Among them, laser 10 includes a shock wave laser and an OCT laser;

[0062] The shock wave laser is used to emit a shock wave beam, which enters the laser shock wave fiber 41;

[0063] The OCT laser is used to emit an OCT imaging beam, which enters the OCT fiber 42.

[0064] Specifically, the shock wave laser is used to generate a shock wave beam, which enters the laser shock wave fiber 41; the OCT (Optical Coherence Tomography) laser is used to generate an OCT imaging beam, which enters the OCT fiber 42. The parameters of the shock wave beam and the OCT imaging beam are different.

[0065] For example, the shockwave laser source has a wavelength of 355nm-2020nm, a single pulse energy of 1J, and an adjustable pulse width of 5µs-500µs. It can be understood that with a shockwave laser source wavelength of 2020nm, the corresponding wavelength of the generated laser beam is 2020nm, which falls within the invisible infrared region. Light of this wavelength can penetrate deeply into the skin and other tissues, making it suitable for deep treatment.

[0066] For example, the OCT laser source has a wavelength of 1310 nm and a power ≥20 mW. It can be understood that with a 1310 nm wavelength, the generated laser beam has a wavelength of 1310 nm, which is in the near-infrared region, giving it good penetration ability into biological tissues while exhibiting relatively low scattering loss. Furthermore, at a wavelength of 1310 nm, the OCT system can achieve relatively deep tissue imaging.

[0067] In one embodiment, the laser beam expanding and collimating system 20 includes:

[0068] Plano-concave lenses are used to expand laser beams;

[0069] A plano-convex lens is used to collimate an expanded laser beam.

[0070] Two planar mirrors are used to adjust the direction of the collimated laser beam.

[0071] Specifically, adjusting the direction of the collimated laser beam using two planar mirrors can include controlling the up-down and left-right directions of the laser beam.

[0072] The laser beam expanding and collimating system provided in this embodiment can uniformly incident the laser beam generated by the laser onto the laser coupling part.

[0073] In one embodiment, the laser coupling section 30 includes a fused taper fiber bundle 31 and a coupling plug end 32;

[0074] The fused taper fiber bundle 31 is used to receive and transmit laser beams emitted by the shock wave laser and the OCT laser;

[0075] The coupling plug 32 is used to control the on / off state of the beam transmitted by each fiber in the fiber bundle.

[0076] Specifically, the fused taper fiber bundle 31 is used to receive and transmit the laser beams emitted by the shock wave laser and the OCT laser, referring to receiving and transmitting the laser beam after expansion and collimation by the laser beam expansion and collimation system.

[0077] Fused tapering of fiber bundles facilitates the transmission of the collimated laser beam to each fiber in a laser beam expander and collimator system. Fused tapered fiber bundles reduce gaps between fibers, lower beam loss efficiency, and also reduce the overall size of the fiber bundle.

[0078] The coupling connector can control the on / off state of the beam transmitted by each fiber in the fiber bundle, enabling precise treatment.

[0079] In one embodiment, the coupling connector 32 includes a host connector and a conduit connector;

[0080] The host connector includes an optical switch 321, which is used to control the on / off state of the transmission beam of each fiber in the fiber bundle.

[0081] The catheter insertion end includes a multi-fiber connector 322, which is used for insertion and removal connection with the catheter 40.

[0082] Specifically, catheter 40 also includes a catheter insertion end, which enables insertion and removal connection.

[0083] The coupling connector 32 arranges all optical fibers in a line or in a circle, and uses a multi-fiber connector MPO322 to achieve plug-in connection with the conduit 40. An optical switch 321 controls the on / off state of the beam transmission in each optical fiber bundle.

[0084] Among them, the optical switch 321 can be a photoelectric switch, which utilizes the electro-optic effect or electro-absorption effect of the material to change the refractive index of the material and the phase of light under the action of an electric field, and then uses light interference or polarization to cause sudden changes in light intensity or optical path conversion, thereby realizing individual adjustment of each channel.

[0085] It is understandable that in the above embodiments, the fiber bundle 31 of the fused taper, the coupling plug end 32 and the fiber in the conduit 40 correspond one-to-one.

[0086] The laser coupling unit can control the on / off state of at least one laser shock wave fiber and / or at least one OCT fiber, enabling precise treatment.

[0087] like Figure 4 The diagram shows the optical path of laser intracorporeal variable lithotripsy (L-IVL) implemented using the laser shock wave lithotripsy imaging device provided in this application. The laser 10 includes a shock wave laser and an OCT laser, generating two laser beams with different parameters that enter the optical fiber in the conduit 40. The conduit 40 includes at least two optical fibers: at least one laser shock wave fiber and at least one OCT fiber.

[0088] The laser beam expanding and collimating system 20 uniformly incidents the laser beam into the fused abductor tapered fiber bundle 31, wherein the fused abductor tapered fiber bundle 31 corresponds one-to-one with the fiber in the guide tube 40. The laser beam expanding and collimating system 20 includes a plano-concave lens, a plano-convex lens, and two plane mirrors. The plano-concave lens expands the laser beam from the laser 10, and the plano-convex lens collimates the expanded laser beam. The two plane mirrors are used to control the vertical and horizontal adjustment of the laser beam.

[0089] The laser coupling section 30 (or coupling end) includes a fused taper fiber bundle 31 and a coupling plug end 32.

[0090] The fiber bundle is fused tapered, which facilitates the laser beam expansion and collimation system 20 in sending the collimated laser beam into each fiber. By fused tapering the fiber bundle, the gaps between the fibers are reduced, thereby lowering the loss efficiency of the laser beam.

[0091] The coupling connector 32 includes a host connector and a conduit connector. The host connector includes an optical switch 321, and the conduit connector includes an MPO multi-fiber connector 322. The coupling connector 32 arranges the optical fibers in a line or in a circle. The MPO multi-fiber connector 322 is used to connect and disconnect the fiber to the conduit 40, and the optical switch 321 is used to control the on / off state of the beam transmission of each fiber in the fiber bundle.

[0092] The distal end of catheter 40 is used to enter a blood vessel for treatment.

[0093] In one embodiment, such as Figure 2 , Figure 3 and Figure 5 , Figure 6 As shown, catheter 40 also includes:

[0094] Balloon 44 is located at the distal end of catheter 40 and is used to contain the shock wave solution. The distal tip of laser shock wave fiber 41 is located inside balloon 44.

[0095] The central cavity 43 runs through the entire conduit 40. The laser shock wave fiber 41 is adjacent to the central cavity 43 and fixed on the central cavity 43.

[0096] Specifically, the central cavity 43 is a channel that allows the guidewire to pass through, guiding the catheter to a designated location within the body (typically the lesion area). It also allows the OCT fiber 42 to penetrate to obtain images of the entire cavity. All laser shockwave fibers 41 are adjacent to the central cavity 43. The balloon 44 can be made of a transparent material to facilitate OCT fiber imaging.

[0097] Once the catheter enters the lesion area, a solution is filled into the balloon, causing it to inflate until its outer surface contacts the lesion area. At this point, the first laser beam output from the laser shockwave fiber optic 41 combines with the solution in the balloon 44 to generate a shockwave that breaks up the calcification.

[0098] Understandably, the conduit 40 includes at least one laser shock wave fiber 41 and at least one OCT fiber 42.

[0099] Specifically, since the range of the shock wave generated by a single laser shock wave fiber is limited, it cannot treat plaques comprehensively. Therefore, multiple laser shock wave fibers can be set up. Similarly, since the imaging range of a single OCT fiber is limited, it cannot observe the treatment situation comprehensively. Therefore, multiple OCT fibers can be set up.

[0100] In one embodiment, such as Figure 3 and Figure 6 As shown, the OCT fiber 42 is located inside the central cavity 43 and extends to the distal end of the conduit 40.

[0101] Furthermore, the OCT fiber 42 is rotated and pulled back for imaging within the central cavity 43.

[0102] Specifically, the OCT fiber 42 is located within the central cavity 43. At this point, the catheter 40 consists of only one OCT fiber. Lateral imaging with the OCT fiber 42 allows for rotation and retraction within the central cavity 43 to acquire an image of the entire cavity, thereby determining the progress and effectiveness of the shockwave therapy. Figure 6 As shown.

[0103] After the central cavity 43 is guided by a guide wire to the target position by the conduit 40, the guide wire is withdrawn, and the OCT fiber 42 is inserted into the central cavity 43 to reach the target position for imaging. However, this procedure is complex. Therefore, when the OCT fiber 42 is located within the central cavity 43, to ensure the simplicity of the procedure and to facilitate the smoother arrival of the conduit 40 at the target position, a guide wire is connected to the tip of the central cavity 43, and the proximal end of the guide wire is welded to the distal end of the central cavity 43, as shown below. Figure 6As shown. The guidewire can be a braided structure or a spring, and the distal end can be curved to increase flexibility and effectively prevent damage to the blood vessel wall. Alternatively, the distal end can be J-shaped to ensure safety. The guidewire length is 40-60 mm, and the diameter is 0.3 mm-0.4 mm. For example, the guidewire length is 50 mm, and the diameter is 0.36 mm.

[0104] The OCT fiber is located inside the central cavity, which can reduce the diameter of the conduit and enable more comprehensive imaging of the entire cavity, making the shock wave more efficient.

[0105] In another embodiment, reference is made to Figure 2 and Figure 5 The OCT fiber 42 is adjacent to and fixed to the central cavity 43. The OCT fiber 42 extends to the distal end of the conduit 40, and the distal tip of the OCT fiber 42 is located inside the balloon 44.

[0106] Specifically, in this embodiment, both the OCT fiber 42 and the laser shock wave fiber 41 are adjacent to the central cavity 43, and the tips of both the OCT fiber 42 and the laser shock wave fiber 41 are located within the spherical capsule 44. Furthermore, the two fibers can be uniformly arranged, such as... Figure 2 As shown.

[0107] The distal tips of the laser shockwave fiber 41 are all located within the balloon 44, and all emit light laterally. This allows the laser energy emitted by the laser shockwave fiber 41 to be evenly distributed over the lesion area. Furthermore, lateral emission reduces direct backward or forward scattering of laser energy, lowering the risk of damage to surrounding tissues. When the distal tips of the OCT fiber 42 are all located within the balloon 44 and emit light laterally, a wider field of view is provided, allowing for real-time observation of the lesion area. Lateral emission also reduces potential shadow areas during imaging, improving imaging accuracy and reliability, enabling doctors to more accurately assess treatment effectiveness.

[0108] Furthermore, the distal tips of the laser shockwave fiber 41 are evenly distributed within the balloon, ensuring uniform distribution of the generated laser energy on the surface of the lesion area, thus improving treatment efficiency. When the distal tips of the OCT fiber 42 are evenly distributed within the balloon, a wider scanning range can be provided, ensuring that potential blind spots are reduced during imaging, allowing doctors to obtain more comprehensive information and thereby improving medical outcomes. In addition, when the distal tips of all fibers are evenly distributed within the balloon, doctors can operate more conveniently and quickly when adjustments to treatment or imaging angles are needed, without the need for frequent repositioning or adjustment of the equipment.

[0109] Understandably, the first laser beam output from the laser shock wave fiber 41 can generate various forms of shock waves in the spherical capsule 44, such as point shock waves, segment shock waves, one circular shock wave, and several circular shock waves.

[0110] In one embodiment, if the conduit 40 includes a laser shock wave fiber 41, the distal tip of the laser shock wave fiber 41 emits light laterally within the balloon 44.

[0111] If the catheter 40 includes at least two laser shock wave optical fibers 41, the distal tips of all the laser shock wave optical fibers 41 generate shock waves of the same circumference or multiple shock waves of different circumferences within the balloon 44.

[0112] Specifically, the distal tip of the laser shockwave fiber 41 can emit light laterally inside the balloon 44, which may include point emission or segment emission.

[0113] When there is only one laser shock wave fiber 41, a point shock wave or a segment shock wave can be formed.

[0114] like Figure 7 , Figure 8 The distal tip of the laser shock wave fiber 41 shown is a single-point lateral light emission. The laser beam is totally internally reflected and emitted laterally within the fiber core. The grinding angle of the fiber core is 30-60 degrees. The distal tip of this laser shock wave fiber 41 forms a point shock wave within the balloon 44.

[0115] in, Figure 7 The laser beam is transmitted in the fiber core and undergoes total internal reflection in the fiber core, with no cladding at the exit point.

[0116] in, Figure 8 The fiber core is ground at a certain angle, and a reflective coating is applied to the ground surface. When the laser beam exits from the fiber core, the reflective coating reflects the laser beam out of the fiber core. Note that there is no cladding at the exit point of the laser beam. Understandably, the fiber core of a single laser shockwave fiber 41 can also be ground in other ways to achieve point light emission, and this is not a limitation.

[0117] Because the shock wave generated by a single point of light emission has a limited area, it cannot treat plaques comprehensively. Therefore, optical fibers can also emit light in segments, generating a segment of shock wave within the balloon for more comprehensive plaque treatment. For example... Figure 9 The image shows the distal tip of a single laser shockwave fiber 41 being ground into a stepped structure. Figure 9The laser shockwave fiber 41 shown has a stepped light emission from one side. The distal tip of the laser shockwave fiber 41 with this structure is located inside the balloon 44, and the fiber can emit light in segments within the balloon 44. By grinding one side of the fiber tip into multiple stepped shapes with decreasing diameters, and coating the beveled side of each step with a reflective material, the laser beam can be uniformly reflected from the beveled side of each step, increasing the coverage of the treatment angle.

[0118] Alternatively, the distal tip of the single laser shockwave fiber 41 can be ground into a helical structure (not shown in the figure), allowing the fiber to emit light in a helical lateral segment within the capsule 44. Understandably, the distal tip of the single laser shockwave fiber 41 can also be ground into other structures for segmental light emission, and this is not a limitation.

[0119] To generate a 360-degree circular shock wave within the balloon 44, at least two laser shock wave fibers 41 can be installed, evenly distributed, with their distal tips aligned on the same circumference, each emitting light laterally. At this time, if... Figure 10 As shown, when the size of the central cavity 43 is 0.35 mm, the size of the laser shock wave fiber 41 is 0.1 mm, and the size of the balloon 44 can be 0.8 mm, that is, the diameter of the balloon 44 and the catheter 40 is small, which makes it easier to pass through blood vessels with a large degree of stenosis and can improve the treatment efficiency.

[0120] To generate multiple 360-degree shock waves with different circumferences inside the balloon 44, the laser shock wave fiber 41 can be set with one, two, or more layers.

[0121] When a layer of laser shock wave fiber 41 is set, there are at least two laser shock wave fibers 41, each laser shock wave fiber 41 contains multiple light emission points, and multiple laser shock wave fibers 41 can be arranged in a spiral to generate multiple 360-degree shock waves with different circumferences.

[0122] When setting up a layer of laser shock wave fiber 41, multiple laser shock wave fibers 41 can also be set up and located on different circumferences, with no less than two laser shock wave fibers 41 on each circumference. At this time, each laser shock wave fiber 41 emits light from the side, thereby generating multiple 360-degree shock waves on different circumferences.

[0123] When two or more layers of laser shock wave fiber 41 are set, each layer consists of multiple laser shock wave fiber 41 arranged around the same circumference 360 ​​degrees. In this case, each laser shock wave fiber 41 emits light laterally, thereby generating multiple shock waves with different circumferences of 360 degrees. For example... Figure 11 The diagram shows a two-layer laser shock wave fiber 41.

[0124] The above-mentioned generation of multiple shock waves with different circumferences means that multiple laser shock wave fibers can generate shock waves at different positions simultaneously, enabling simultaneous treatment of multiple parts of the lesion area and significantly reducing the total treatment time. In addition, by adjusting the position and emission angle of each laser shock wave fiber, it is possible to achieve full coverage of the lesion area and ensure that the lesion area receives sufficient energy irradiation.

[0125] In one embodiment, if the conduit 40 includes an OCT optical fiber 42, the distal tip of the OCT optical fiber 42 emits light laterally.

[0126] If the conduit 40 includes at least two OCT optical fibers 42, the distal tips of all OCT optical fibers 42 are imaged in the same circumference or in multiple different circumferences.

[0127] Specifically, the lateral light emission from the distal tip of the OCT fiber 42 can include point imaging or segment imaging.

[0128] The optical switch 321 can be used to individually control the light output of each OCT fiber 42.

[0129] The specific structure and light emission method of the OCT fiber 42 can be set with reference to the laser shock wave fiber 41. For example, the fiber bundle of the OCT fiber 42 is arranged in a spiral and emits light from the side, which is convenient for 360-degree imaging. Alternatively, each OCT fiber 42 can perform segment imaging without pull-back, that is, multiple light emission points can be set on the OCT fiber 42, multi-layer OCT fiber 42, etc., without limitation.

[0130] By combining laser shockwave with OCT imaging, OCT can provide real-time imaging and feedback on the treatment progress during shockwave therapy, and then adjust the shockwave parameters according to the treatment progress.

[0131] It is understandable that the laser shock wave fiber 41 and the OCT fiber 42 can be combined using any of the above structures or forms.

[0132] The above are merely specific embodiments of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions within the technical scope 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 lithotripsy imaging device, comprising: The laser shock wave lithotripsy imaging device comprises: a laser (10) for generating laser beams with different parameters; a laser beam expander and collimator system (20) for expanding and collimating all the laser beams generated by the laser (10); a laser coupling part (30) for guiding the expanded and collimated laser beams into a catheter (40); the catheter (40) has a distal end for entering a blood vessel for treatment; wherein the catheter (40) comprises a laser shock wave fiber (41) and an OCT fiber (42); the catheter (40) further comprises: a balloon (44) located at the distal end of the catheter (40) for containing a shock wave solution, and a distal tip of the laser shock wave fiber (41) is located in the balloon (44); a central cavity (43) extending through the entire catheter (40), the laser shock wave fiber (41) is adjacent to and fixed on the central cavity (43); the laser coupling part (30) comprises a fused taper fiber bundle (31) and a coupling plug end (32); the laser (10) comprises a shock wave laser and an OCT laser; the shock wave laser is used to emit a shock wave beam into the laser shock wave fiber (41); the OCT laser is used to emit an OCT imaging beam into the OCT fiber (42); the fused taper fiber bundle (31) is used to receive and transmit the laser beams emitted by the shock wave laser and the OCT laser; the coupling plug end (32) is used to control the on-off of the transmission of the light beams by each fiber in the fiber bundle; the coupling plug end (32) comprises a host plug end and a catheter plug end; the host plug end comprises an optical switch (321) for controlling the on-off of the transmission of the light beams by each fiber in the fiber bundle; the catheter plug end comprises a multi-fiber connector (322) for plugging connection with the catheter (40); a distal tip of a single laser shock wave fiber (41) is ground into a stepped structure with diameters decreasing in steps, and each step side is coated with a reflective material to uniformly reflect the laser beams from each step side.

2. The lithotripsy imaging device of claim 1, wherein, The OCT fiber (42) is located in the central cavity (43) and extends to the distal end of the catheter (40).

3. The lithotripsy imaging device of claim 2, wherein, The OCT fiber (42) rotates back in the central cavity (43) for imaging.

4. The lithotripsy imaging device of claim 1, wherein, The OCT fiber (42) is adjacent to and fixed on the central cavity (43), the OCT fiber (42) extends to the distal end of the catheter (40), and a distal tip of the OCT fiber (42) is located in the balloon (44).

5. The lithotripsy imaging apparatus of any of claims 1-4, wherein, If the catheter (40) comprises a single laser shock wave fiber (41), a distal tip of the laser shock wave fiber (41) emits light laterally in the balloon (44). If the catheter (40) comprises at least two laser shock wave fibers (41), the distal tips of all the laser shock wave fibers (41) generate shock waves at the same circumference or at different circumferences within the balloon (44).

6. The lithotripsy imaging apparatus of any of claims 1-4, wherein, If the catheter (40) comprises one OCT fiber (42), the distal tip of the OCT fiber (42) emits light laterally; If the catheter (40) comprises at least two OCT fibers (42), the distal tips of all the OCT fibers (42) image at the same circumference or at different circumferences.

7. The lithotripsy imaging device of claim 1, wherein, The laser beam expanding and collimating system (20) comprises: a plano-concave lens for expanding the laser beam; a plano-convex lens for collimating the expanded laser beam; two plane mirrors for adjusting the direction of the collimated laser beam.

Images