Laser shock wave lithotripsy imaging device

Abstract

The invention discloses a laser shock wave lithotripsy imaging device, and the device comprises a laser device which is used for generating laser beams with different parameters; the laser beam expanding and collimating system is used for expanding and collimating all laser beams generated by the laser; the laser coupling part is used for guiding the expanded and collimated laser beams into a guide pipe; the far end of the catheter is used for entering a blood vessel for treatment; wherein the catheter comprises a laser shock wave optical fiber and an OCT optical fiber. According to the scheme, laser energy can be generated through a high-energy source laser, the laser energy is transmitted in the catheter and output to generate shock waves, and the shock waves can break calcification at treatment sites including one or more vasculature in the vasculature. According to the scheme, in the treatment process of the laser shock wave optical fiber, the OCT optical fiber can watch the treatment effect in real time, so that laser shock wave parameters can be adjusted at any time, and the treatment effect is improved.

Description

Technical Field

[0001] The present application relates to the technical field of medical equipment, and in particular to a laser shock wave lithotripsy imaging device. Background Art

[0002] Vascular stenosis is a common clinical disease, mainly due to the deposition of substances such as calcification on the originally smooth vascular endothelium, which obstructs blood flow and easily causes some complications and even endangers life. Therefore, vascular dilation has become an urgent problem that needs to be solved.

[0003] In the prior art, voltage shock waves are used to make the electrode pairs form cavitation bubbles and then generate shock waves. The shock waves impact the calcified area to break up the calcified lesions. Although this method is widely used in clinical practice, it also has some defects. For example, during the treatment process, the calcification treatment status and progress cannot be obtained. Therefore, the electric energy is adjusted according to adaptability, resulting in poor lithotripsy and even possible balloon damage. In addition, the outer diameter of the catheter is too large (minimum 1.2mm), which cannot pass through severely narrow calcified lesions and requires grinding first, which has low treatment efficiency. Summary of the invention

[0004] An embodiment of the present application provides a laser shock wave lithotripsy imaging device.

[0005] An embodiment of the present application provides a laser shock wave lithotripsy imaging device, the laser shock wave lithotripsy imaging device comprising:

[0006] Lasers, used to generate laser beams with different parameters;

[0007] Laser beam expansion and collimation system, used to expand and collimate all laser beams generated by the laser;

[0008] A laser coupling part, used for guiding the expanded and collimated laser beam into the catheter;

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

[0010] The catheter includes a laser shock wave optical fiber and an OCT optical fiber.

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

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

[0013] A central cavity runs through the entire catheter, and the laser shock wave optical fiber is adjacent to the central cavity and fixed on the central cavity.

[0014] In one embodiment, an OCT optical fiber is located in the central cavity, and the OCT optical fiber extends to the distal end of the catheter.

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

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

[0017] In one embodiment, the laser coupling portion includes a fused-tapered optical fiber bundle and a coupled splice end;

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

[0019] The coupling plug end is used to control the on and off of the light beam transmitted by each optical fiber in the optical fiber bundle.

[0020] In one embodiment, the coupling plug end includes a host plug end and a catheter plug end;

[0021] The host plug-in end includes an optical switch, which is used to control the on and off of each optical fiber transmission light beam in the optical fiber bundle;

[0022] The catheter plug-in end comprises a multi-fiber connector, which is used for plug-in connection with the catheter.

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

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

[0025] In one embodiment, if the catheter includes an OCT optical fiber, the distal tip of the OCT optical fiber emits light sideways;

[0026] If the catheter includes at least two OCT optical fibers, the distal tips of all OCT optical fibers are imaged at the same circumference or at different circumferences.

[0027] In one embodiment, the laser beam expansion and collimation system comprises:

[0028] Plano-concave lens, used to expand the laser beam;

[0029] A plano-convex lens is used to collimate the laser beam after expansion;

[0030] Two plane reflectors are used to adjust the direction of the collimated laser beam.

[0031] Compared with the prior art, this application has the following beneficial effects:

[0032] The laser shock wave lithotripsy imaging device provided in the embodiment of the present application can generate laser energy through a high-energy source laser. The laser energy is transmitted in a catheter and output to generate shock waves, which can break up calcification at the treatment site including one or more vascular lesions in the vascular system.

[0033] The laser shock wave lithotripsy imaging device provided in the embodiment of the present application can make the catheter diameter smaller, making it easier to pass through blood vessels with a larger degree of stenosis, thereby improving treatment efficiency.

[0034] In the laser shock wave lithotripsy imaging device provided in the embodiment of the present application, the catheter includes at least one laser shock wave optical fiber and at least one OCT optical fiber, so that during the treatment process using the laser shock wave optical fiber, the OCT optical fiber can view the treatment effect in real time, so as to adjust the laser shock wave parameters at any time to improve the treatment effect.

[0035] In the laser shock wave lithotripsy imaging device provided in the embodiment of the present application, the laser coupling unit can control the on-off of at least one laser shock wave optical fiber and / or at least one OCT optical fiber optical path, thereby achieving precise treatment. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0037] Figure 1 A schematic diagram of the structure of a laser shock wave lithotripsy imaging device provided in an embodiment of the present application;

[0038] Figure 2 Schematic diagram of the structure of the catheter in the laser shock wave lithotripsy imaging device provided in the embodiment of the present application Figure 1 ;

[0039] Figure 3 Schematic diagram of the structure of the catheter in the laser shock wave lithotripsy imaging device provided in the embodiment of the present application Figure 2 ;

[0040] Figure 4 A schematic diagram of the optical path of a laser shock wave lithotripsy imaging device provided in an embodiment of the present application;

[0041] Figure 5Schematic diagram of the structure of the catheter in the laser shock wave lithotripsy imaging device provided in the embodiment of the present application Figure 3 ;

[0042] Figure 6 Schematic diagram of the structure of the catheter in the laser shock wave lithotripsy imaging device provided in the embodiment of the present application Figure 4 ;

[0043] Figure 7 Schematic diagram of the single-point lateral light emission of the laser shock wave optical fiber provided in the embodiment of the present application Figure 1 ;

[0044] Figure 8 Schematic diagram of the single-point lateral light emission of the laser shock wave optical fiber provided in the embodiment of the present application Figure 2 ;

[0045] Fig. 9 A schematic diagram of the stepped light output on one side of the laser shock wave optical fiber provided in an embodiment of the present application;

[0046] Fig.10 A schematic diagram of the catheter size provided for an embodiment of the present application;

[0047] Fig.11 Schematic diagram of a two-layer laser shock wave optical fiber provided in an embodiment of the present application. DETAILED DESCRIPTION

[0048] The following will be combined with the drawings in the embodiments of the present application to clearly and completely describe the technical solutions in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

[0049] In the description of the present application, it should be understood that the terms "center", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc., indicating orientations or positional relationships, are based on the orientations or positional relationships shown in the accompanying drawings, and are only for the convenience of describing the present application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be understood as a limitation on the present application.

[0050] In the description of the present application, it should be noted that, unless otherwise clearly specified and limited, the terms "installed", "connected" and "connected" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral connection. For ordinary technicians in this field, the specific meanings 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 understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of the features. In the description of this application, unless otherwise specified, "plurality" means two or more.

[0052] like Figure 1-11 As shown, it shows a schematic structural diagram of the laser shock wave lithotripsy imaging device provided in an embodiment of the present application.

[0053] Reference Figure 1-Figure 3 A laser shock wave lithotripsy imaging device provided in an embodiment of the present application may include:

[0054] A laser 10, used to generate laser beams with different parameters;

[0055] The laser beam expansion and collimation system 20 is used to expand and collimate all 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 catheter 40;

[0057] A catheter 40, wherein the distal end of the catheter 40 is used to enter a blood vessel for treatment;

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

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

[0060] The laser shock wave lithotripsy imaging device provided in this embodiment can generate laser energy through a high energy source laser, and the laser energy is transmitted in the catheter and output to generate shock waves, which can break up calcification at the treatment site including one or more vascular lesions in the vascular system. In addition, the catheter includes a laser shock wave optical fiber and an OCT optical fiber, so that during the treatment process using the laser shock wave optical fiber, the OCT optical fiber can view the treatment effect in real time, so as to adjust the laser shock wave parameters at any time and improve the treatment effect.

[0061] Wherein, the 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 optical fiber 41;

[0063] The OCT laser is used to emit an OCT imaging beam which enters the OCT optical 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, wherein the parameters of the shock wave beam and the OCT imaging beam are different.

[0065] Exemplarily, the shock wave laser light source has a wavelength of 355nm-2020nm, a single pulse energy of 1J, and a pulse width of 5us-500us adjustable. It can be understood that the shock wave laser light source has a wavelength of 2020nm, and correspondingly, the wavelength of the laser beam it generates is 2020nm, which belongs to the invisible infrared light region. Light of this wavelength can penetrate the skin and other tissues more deeply, and is suitable for deep treatment.

[0066] Exemplarily, the wavelength of the OCT laser light source is 1310nm, and the light source power is ≥20mw. It can be understood that the wavelength of the OCT laser light source is 1310nm, and correspondingly, the wavelength of the laser beam it generates is 1310nm, which is in the near-infrared region, so that it has good penetration ability corresponding to biological tissues and relatively low scattering loss. Moreover, at a wavelength of 1310nm, the OCT system can achieve relatively deep tissue imaging.

[0067] In one embodiment, the laser beam expansion and collimation system 20 includes:

[0068] Plano-concave lens, used to expand the laser beam;

[0069] A plano-convex lens is used to collimate the laser beam after expansion;

[0070] Two plane reflectors are used to adjust the direction of the collimated laser beam.

[0071] Specifically, the two plane reflectors adjust the direction of the collimated laser beam, which may include controlling the upward and downward and left and right directions of the laser beam.

[0072] Through the laser beam expansion and collimation system provided in this embodiment, the laser beam generated by the laser can be uniformly incident on the laser coupling part.

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

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

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

[0076] Specifically, the fused-tapered optical fiber bundle 31 is used to receive and transmit the laser beam emitted by the shock wave laser and the OCT laser, that is, to receive and transmit the laser beam expanded and collimated by the laser beam expansion and collimation system.

[0077] Melting and tapering the fiber bundle can make it easier for the laser beam expansion and collimation system to send the collimated laser beam to each optical fiber. By melting and tapering the fiber bundle, the gap between the optical fibers can be reduced, the loss efficiency of the beam can be reduced, and the size of the fiber bundle can be reduced.

[0078] The coupling plug end can control the on and off of the light beam transmitted by each optical fiber in the optical fiber bundle, thereby achieving precise treatment.

[0079] In one embodiment, the coupling plug end 32 includes a host plug end and a catheter plug end;

[0080] The host plug-in end includes an optical switch 321, which is used to control the on and off of each optical fiber transmission light beam in the optical fiber bundle;

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

[0082] Specifically, the catheter 40 also includes a catheter plug-in end, and the catheter plug-in end is connected by plugging and unplugging through the catheter plug-in end.

[0083] The coupling plug end 32 arranges all optical fibers in a line or in a circle, and uses a multi-fiber connector MPO 322 to achieve plug-in connection with the catheter 40. The optical switch 321 is used to control the on and off of each optical fiber transmission light beam in the optical fiber bundle.

[0084] The optical switch 321 may be a photoelectric switch, which utilizes the electro-optical 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 the electric field, and then utilizes light interference or polarization to cause a sudden change in light intensity or a change in light path, thereby achieving individual adjustment of each channel.

[0085] It can be understood that in the above embodiment, the fused-tapered optical fiber bundle 31, the coupling plug end 32 and the optical fiber in the catheter 40 correspond one to one.

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

[0087] like Figure 4 The figure shows a schematic diagram of the optical path of laser lithotripsy (Laser Intracorporeal Variable Lithotripsy, L-IVL) implemented by the laser shock wave lithotripsy imaging device provided in the embodiment of the present application. The laser 10 includes a shock wave laser and an OCT laser, and generates two laser beams with different parameters to enter the optical fiber in the catheter 40. The catheter 40 correspondingly includes at least two optical fibers, namely, at least one laser shock wave optical fiber and at least one OCT optical fiber.

[0088] The laser beam expansion and collimation system 20 evenly injects the laser beam into the optical fiber bundle 31 of the fused taper, wherein the optical fiber bundle 31 of the fused taper corresponds one-to-one with the optical fiber in the catheter 40. The laser beam expansion and collimation system 20 includes a plano-concave lens, a plano-convex lens and two plane reflectors. The plano-concave lens is used to expand the laser beam of the laser 10, and the plano-convex lens collimates the expanded laser beam. The two plane reflectors are used to control the up and down and left and right direction adjustment of the laser beam.

[0089] The laser coupling portion 30 (or called the coupling end) includes a fused-tapered optical fiber bundle 31 and a coupling plug end 32 .

[0090] The optical fiber bundle is melted and tapered, so that the laser beam expansion and collimation system 20 can send the collimated laser beam to each optical fiber. By melting and tapering the optical fiber bundle, the gap between optical fibers is reduced, and the loss efficiency of the laser beam is reduced.

[0091] The coupling plug end 32 includes a host plug end and a catheter plug end, the host plug end includes an optical switch 321, and the catheter plug end includes an MPO multi-fiber connector 322. The coupling plug end 32 arranges the optical fibers in a line or in a circle, and uses the MPO multi-fiber connector 322 to achieve plugging and unplugging with the catheter 40, and uses the optical switch 321 to control the on and off of each optical fiber transmission light beam in the optical fiber bundle.

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

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

[0094] A balloon 44, which is located at the distal end of the catheter 40 and is used to contain a shock wave solution, and the distal tip of the laser shock wave optical fiber 41 is located in the balloon 44;

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

[0096] Specifically, the central cavity 43 is a channel for allowing a guide wire to pass through, wherein the guide wire is used to guide the catheter to reach a specified position in the body (usually a lesion area), and can also allow the OCT fiber 42 to penetrate to obtain an image of the entire organ cavity. All laser shock wave 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] When the catheter enters the lesion area, the solution is filled into the balloon to expand the balloon until the outer surface of the balloon contacts the lesion area. At this time, the first laser beam output by the laser shock wave optical fiber 41 combines with the solution in the balloon 44 to generate a shock wave that breaks up the calcification.

[0098] It can be understood that the catheter 40 includes at least one laser shock wave optical fiber 41 and at least one OCT optical fiber 42 .

[0099] Specifically, since the range of the shock wave generated by a single laser shock wave fiber is limited, the plaque cannot be treated comprehensively. Therefore, multiple laser shock wave fibers can be set; and since the imaging range of a single OCT fiber is limited, the treatment situation cannot be observed comprehensively. Therefore, multiple OCT fibers can be set.

[0100] In one embodiment, if Figure 3 and Figure 6 As shown, the OCT optical fiber 42 is located in the central cavity 43 , and the OCT optical fiber 42 extends to the distal end of the catheter 40 .

[0101] Furthermore, the OCT optical fiber 42 is rotated in the central cavity 43 to be pulled back for imaging.

[0102] Specifically, the OCT optical fiber 42 is located in the central cavity 43. At this time, the catheter 40 includes only one OCT optical fiber. The OCT optical fiber 42 is imaged laterally and can be rotated and pulled back in the central cavity 43 to obtain the image of the entire lumen, thereby judging the progress and effect of shock wave therapy. Figure 6 shown.

[0103] After the central cavity 43 is guided by the guide wire to the target position, the guide wire is withdrawn and the OCT optical fiber 42 is inserted into the central cavity 43 to reach the target position for imaging, but the procedure is complicated. Therefore, when the OCT optical fiber 42 is located in the central cavity 43, in order to ensure the simplicity of the procedure and enable the catheter 40 to reach the target position more smoothly, the 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, such as Figure 6As shown. The guide wire can be a braided structure or a spring, and the distal end of the guide wire can be a curved structure, which is conducive to increasing flexibility and effectively preventing the guide wire from damaging the inner wall of the blood vessel. Of course, the distal end of the guide wire can also be a J-shaped structure to ensure safety. The guide wire length is 40-60mm, and the guide wire diameter is 0.3mm-0.4mm. Exemplarily, the guide wire length is 50mm, and the guide wire diameter is 0.36mm.

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

[0105] In another embodiment, referring to Figure 2 and Figure 5 The OCT optical fiber 42 is adjacent to the central cavity 43 and fixed on the central cavity 43 . The OCT optical fiber 42 extends to the distal end of the catheter 40 , and the distal tip of the OCT optical fiber 42 is located in the balloon 44 .

[0106] Specifically, in this embodiment, the OCT optical fiber 42 and the laser shock wave optical fiber 41 are both adjacent to the central cavity 43, and the tip of the OCT optical fiber 42 and the tip of the laser shock wave optical fiber 41 are both located in the balloon 44. Further, the two optical fibers can be evenly arranged, such as Figure 2 shown.

[0107] The distal tips of the laser shock wave optical fibers 41 are all located in the balloon 44, and the light is emitted from the side, so that the laser energy emitted by the laser shock wave optical fibers 41 can act evenly on the lesion area. In addition, the lateral light emission can make the laser energy less directly scattered backward or forward, reducing the risk of damage to surrounding tissues. When the distal tips of the OCT optical fibers 42 are all located in the balloon 44, and the light is emitted from the side, a better field of view can be provided to observe the condition of the lesion area in real time; in addition, the lateral light emission can also reduce the possible shadow area during the imaging process, improve the accuracy and reliability of the imaging, and enable doctors to more accurately evaluate the treatment effect.

[0108] Furthermore, the distal tips of the laser shock wave optical fibers 41 are evenly arranged in the balloon, which can ensure that the generated laser energy is evenly distributed on the surface of the lesion area, thereby improving the treatment efficiency; when the distal tips of the OCT optical fibers 42 are evenly arranged in the balloon, a wider scanning range can be provided, ensuring that possible blind spots are reduced during imaging, so that doctors can obtain more comprehensive information, thereby improving the doctor's medical effect. In addition, when the distal tips of all optical fibers are evenly arranged in the balloon, when the doctor needs to adjust the treatment or imaging angle, the operation can be more convenient and quick, without the need to frequently reposition or adjust the equipment.

[0109] It can be understood that the first laser beam output by the laser shock wave optical fiber 41 can generate various forms of shock waves in the balloon 44, such as point shock waves, segment shock waves, one circular shock wave, and several circular shock waves.

[0110] In one embodiment, if the catheter 40 includes a laser shock wave optical fiber 41, the distal tip of the laser shock wave optical 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 in the balloon 44 .

[0112] Specifically, the distal tip of the laser shock wave optical fiber 41 may emit light laterally inside the balloon 44 in the form of point light or segment light.

[0113] When there is only one laser shock wave optical 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 optical fiber 41 shown is a single point lateral light emission. The laser beam is totally reflected in the optical fiber core and emits light laterally. The grinding angle of the core is 30-60 degrees. The distal tip of the laser shock wave optical fiber 41 forms a point shock wave in the balloon 44.

[0115] in, Figure 7 The laser beam is transmitted in the fiber core and is totally reflected in the fiber core, and there is no cladding at the output light.

[0116] in, Figure 8 The fiber core is ground into a certain angle, and a reflective coating is applied to the ground surface. When the laser beam is emitted from the fiber core, the reflective coating will reflect the laser beam out of the fiber core. Note that there is no cladding at the exit point of the laser beam. It is understandable that the core of a single laser shock wave optical fiber 41 can also be ground in other ways to emit light, which is not limited here.

[0117] Since the shock wave generated by a single point of light is limited in area, it cannot fully treat the plaque. Therefore, the optical fiber can also emit light in segments to generate a shock wave in the balloon, which can more fully treat the plaque. Fig. 9 The figure shows that the distal tip of a single laser shock wave optical fiber 41 is ground into a stepped structure. Fig. 9The laser shock wave optical fiber 41 shown has a stepped light output on one side. The distal tip of the laser shock wave optical fiber 41 of this structure is located in the balloon 44, and the optical fiber can output light in segments in the balloon 44. One side of the optical fiber tip is ground into a plurality of stepped forms with decreasing diameters, and a reflective material is coated on the oblique side of each step, so that the laser beam can be evenly reflected from the oblique side of each step, thereby increasing the coverage of the treatment angle.

[0118] In addition, the distal tip of the single laser shock wave optical fiber 41 can also be ground into a spiral structure (not shown in the figure), and the optical fiber can emit light in a spiral lateral direction in the balloon 44. It can be understood that the distal tip of the single laser shock wave optical fiber 41 can also be ground into other structures for segmented light emission, which is not limited here.

[0119] In order to generate a 360-degree shock wave in the same circle in the balloon 44, at least two laser shock wave optical fibers 41 may be provided and evenly distributed, with the distal tips being in the same circle, and each emitting light laterally. Fig.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, the size of the balloon 44 can be 0.8 mm, that is, the diameters of the balloon 44 and the catheter 40 are relatively small, which is convenient for passing through blood vessels with a larger degree of stenosis, and can improve the treatment efficiency.

[0120] In order to generate a plurality of 360-degree shock waves of different circumferences in the balloon 44 , the laser shock wave optical fiber 41 may be provided with one layer, two layers, or more than two layers.

[0121] Among them, when a layer of laser shock wave optical fiber 41 is set, there are at least two laser shock wave optical fibers 41, each laser shock wave optical fiber 41 includes multiple light output points, and multiple laser shock wave optical fibers 41 can be arranged in a spiral manner to generate multiple 360-degree shock waves of different circumferences.

[0122] When a layer of laser shock wave optical fiber 41 is set, multiple laser shock wave optical fibers 41 can also be set, and they are located at different circumferences, with no less than two laser shock wave optical fibers 41 on each circumference. At this time, each laser shock wave optical fiber 41 emits light laterally to generate multiple 360-degree shock waves on different circumferences.

[0123] When two or more layers of laser shock wave optical fibers 41 are provided, the multiple layers of laser shock wave optical fibers 41, each layer of which is composed of multiple laser shock wave optical fibers 41 surrounding the same circumference 360 ​​degrees, each laser shock wave optical fiber 41 emits light laterally, thereby generating multiple shock waves of different circumferences 360 degrees. Fig.11 Shown is a schematic diagram of a two-layer laser shock wave optical fiber 41.

[0124] The above-mentioned generation of multiple shock waves of different circumferences, that is, multiple laser shock wave optical fibers can generate shock waves at different positions at the same time, can achieve simultaneous treatment of multiple parts of the lesion area, significantly reducing the total treatment time; in addition, by adjusting the position and light output angle of each laser shock wave optical fiber, all-round coverage of the lesion area can be achieved, ensuring that the lesion area can receive sufficient energy irradiation.

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

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

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

[0128] The light output of each OCT optical fiber 42 can be controlled individually through the optical switch 321 .

[0129] The specific structure and light emitting mode of the OCT optical fiber 42 can be set with reference to the laser shock wave optical fiber 41. For example, the optical fiber bundle of the OCT optical fiber 42 is arranged in a spiral shape, and the light is emitted laterally, which is convenient for 360-degree imaging, or each OCT optical fiber 42 can perform segment imaging without pulling back, that is, multiple light emitting points can be set on the OCT optical fiber 42, multiple layers of OCT optical fibers 42, etc., which are not limited here.

[0130] By combining laser shock waves with OCT imaging, OCT can provide real-time imaging and feedback on the treatment status during shock wave therapy, and then adjust the shock wave parameters based on the treatment status.

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

[0132] The above are only specific implementations of the present application, but the protection scope of the present application is not limited thereto. Any changes or substitutions within the technical scope disclosed in the present application should be included in the protection scope of the present application. Therefore, the protection scope of the present application should be based on the protection scope of the claims.

Claims

1. A laser shock wave lithotripsy imaging device, characterized in that: The laser shock wave lithotripsy imaging device comprises: A laser (10) for generating laser beams with different parameters; A laser beam expansion and collimation system (20), used for expanding and collimating all the laser beams generated by the laser (10); A laser coupling unit (30) is used to guide the expanded and collimated laser beam into the catheter (40); A catheter (40), wherein the distal end of the catheter (40) is used to enter a blood vessel for treatment; Wherein, the catheter (40) comprises a laser shock wave optical fiber (41) and an OCT optical fiber (42).

2. The laser shock wave lithotripsy imaging device according to claim 1, characterized in that: The catheter (40) further comprises: A balloon (44), the balloon (44) is located at the distal end of the catheter (40) and is used to contain a shock wave solution, and the distal tip of the laser shock wave optical fiber (41) is located in the balloon (44); A central cavity (43) is provided, wherein the central cavity (43) runs through the entire catheter (40), and the laser shock wave optical fiber (41) is adjacent to the central cavity (43) and is fixed on the central cavity (43).

3. The laser shock wave lithotripsy imaging device according to claim 2, characterized in that: The OCT optical fiber (42) is located in the central cavity (43), and the OCT optical fiber (42) extends to the distal end of the catheter (40).

4. The laser shock wave lithotripsy imaging device according to claim 3, characterized in that: The OCT optical fiber (42) is rotated in the central cavity (43) for pullback imaging.

5. The laser shock wave lithotripsy imaging device according to claim 2, characterized in that: The OCT optical fiber (42) is adjacent to the central cavity (43) and fixed on the central cavity (43). The OCT optical fiber (42) extends to the distal end of the catheter (40), and the distal tip of the OCT optical fiber (42) is located in the balloon (44).

6. The laser shock wave lithotripsy imaging device according to claim 4, characterized in that: The laser coupling part (30) comprises a fused tapered optical fiber bundle (31) and a coupling plug end (32); The fused taper optical 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 each optical fiber transmission light beam in the optical fiber bundle.

7. The laser shock wave lithotripsy imaging device according to claim 5, characterized in that: The coupling plug end (32) comprises a host plug end and a catheter plug end; The host plug-in end comprises an optical switch (321), and the optical switch (321) is used to control the on and off of each optical fiber transmission light beam in the optical fiber bundle; The catheter plug-in end comprises a multi-fiber connector (322), and the multi-fiber connector (322) is used for plug-in connection with the catheter (40).

8. The laser shock wave lithotripsy imaging device according to any one of claims 3 to 6, characterized in that: If the catheter (40) includes one laser shock wave optical fiber (41), the distal tip of the laser shock wave optical fiber (41) emits light laterally in the balloon (44); 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 shock waves of different circumferences in the balloon (44).

9. The laser shock wave lithotripsy imaging device according to any one of claims 3 to 6, characterized in that: If the catheter (40) includes one OCT optical fiber (42), the distal tip of the OCT optical fiber (42) emits light laterally; If the catheter (40) includes at least two OCT optical fibers (42), the distal tips of all the OCT optical fibers (42) are imaged on the same circumference or on different circumferences.

10. The laser shock wave lithotripsy imaging device according to claim 1, characterized in that: The laser beam expansion and collimation system (20) comprises: A plano-concave lens, used for expanding the laser beam; A plano-convex lens is used to collimate the laser beam after expansion; Two plane reflectors are used to adjust the direction of the collimated laser beam.

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