Optical diagnosis and treatment integrated system

Abstract

The invention provides an optical diagnosis and treatment integrated system. The optical diagnosis and treatment integrated system comprises an optical imaging module, a laser ablation module and a light path control module, the optical imaging module is used for emitting first light and forming an image of target tissue at least according to the first light; the laser ablation module is used for emitting second light to ablate the target tissue; the light path control module is at least used for receiving the first light and the second light and transmitting the first light and the second light to the target tissue; wherein the light path control module comprises a rotor unit; the rotor unit is used for at least driving the first light to rotate around a preset axis. Various optical modules can be combined for use and do not interfere with one another.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to an integrated optical diagnosis and treatment system. Background Art

[0002] Progressive degenerative diseases refer to diseases in which the function of tissues and organs decreases with the aging of the body. For example, vascular atherosclerosis is caused by the accumulation of plaques composed of lipids, cholesterol, calcium and other substances in the blood on the blood vessel wall, which can easily cause vascular obstruction, organ ischemia, and even life-threatening. In this regard, the prior art uses plaque ablation as one of the main treatment methods. Plaque ablation includes intracoronary plaque atherectomy, orbital atherectomy and laser ablation. Among them, non-laser plaque atherectomy has a high risk of restenosis, and has limitations in surgical treatment of indications such as in-stent restenosis, calcified lesions, severe stenosis and total occlusion lesions, and fibrotic soft plaques, which limits its clinical application. Therefore, laser ablation technology is generally used to treat plaques, such as Excimer Laser Coronary Atherectomy (ELCA).

[0003] ELCA achieves therapeutic effects mainly through three principles: photochemical effect, photothermal effect, and photomechanical effect. Among them, the excimer laser used in ELCA is a near-ultraviolet light with a wavelength of only 308nm. It uses xenon and hydrogen chloride as active media and is emitted in a pulsed manner (with enough time for cooling). The penetration depth of the tissue is less than 50μm. After the excimer laser is absorbed by the tissue, the carbon-carbon double bond of the tissue is broken, the cell molecular structure is destroyed, and the temperature in the cell rises, promoting the formation of water vapor and promoting cell rupture. At the same time, bubbles can be generated at the front end of the catheter, further destroying the intravascular atherosclerotic plaque tissue. The laser ablation device is used for laser ablation of diseased tissues in blood vessels, such as thrombus plaques, calcified lesions, etc. Different from the previous long-wavelength thermal laser, the new generation of excimer laser is a 308nm short-wavelength ultraviolet cold laser, which is very little absorbed in human blood and strongly absorbed in tissues. Because of its shallow ablation depth, less heat release, and less unnecessary tissue damage, its safety is guaranteed, and its application prospects in coronary arteries are also broader.

[0004] However, the incidence of restenosis in laser coronary plaque ablation is high, and one of the main causes is the lack of high-definition real-time image guidance technology in the blood vessels during the intervention, which causes vascular damage, especially damage to the membrane between the outermost layers of the artery (external elastic layer). In addition, the imaging resolution and real-time performance of existing real-time image guidance technology cannot meet its needs.

[0005] Optical coherence tomography (OCT) is an imaging technology with high-resolution, non-destructive, and real-time imaging capabilities. OCT can achieve non-destructive, non-contact, high-speed detection with depth resolution at micron-level resolution, and can be used to obtain high-resolution three-dimensional images of the sample being tested in real time, with micron-level resolution in the depth direction. Among them, intravascular OCT (IV-OCT) has become a commonly used imaging technology in percutaneous coronary intervention (PCI) surgery.

[0006] However, because the traditional intravascular OCT imaging system relies on the energy of the backscattered light returned by the sample, if it is combined with an excimer laser, the excessive energy of the excimer laser will affect the quality of OCT imaging. In addition, PCI surgery has strict requirements on the size of the catheter, and the OCT imaging catheter needs to be rotated, scanned, and retracted to achieve cardiovascular imaging. Its size is often too large, and the excimer laser ablation catheter is mostly a ring-shaped fiber bundle. Therefore, there is currently no technical solution that can combine OCT and excimer laser ablation. Summary of the invention

[0007] The object of the present invention is to provide an integrated optical diagnosis and treatment system to solve at least one of the problems of how to combine OCT and excimer laser ablation, and how to achieve the combined use of multiple optical modules without interfering with each other.

[0008] To achieve the above-mentioned objectives, the present invention provides an integrated optical diagnosis and treatment system, comprising an optical imaging module, a laser ablation module and an optical path control module; the optical imaging module is used to emit a first light, and to form an image of a target tissue at least based on the first light; the laser ablation module is used to emit a second light to ablate the target tissue; the optical path control module is used to at least receive the first light and the second light, and transmit them to the target tissue; wherein the optical path control module comprises a rotor unit; the rotor unit is used to at least drive the first light to rotate around a predetermined axis.

[0009] Optionally, the optical path control module further includes a stator unit, and the rotor unit is capable of rotating relative to the stator unit; wherein the first light and the second light are respectively incident on the target tissue through the stator unit.

[0010] Optionally, the stator unit includes a first light input end; and a first collimating lens group and a filter are disposed in the first light input end, and the first light is incident on the rotor unit through the first collimating lens group and the filter in sequence; wherein the filter is used to pass the first light and the scattered light after the first light passes through the target tissue, and can cut off the second light from returning to the first light input end.

[0011] Optionally, the stator unit further includes a second light input end, and a second collimating lens group is disposed in the second light input end; the second light is incident on the rotor unit through the second collimating lens group.

[0012] Optionally, the rotor unit includes a dove prism, a first light output end and a second light output end; wherein a first coupling lens group is arranged in the first light output end, and a second coupling lens group is arranged in the second light output end; the first light ray is incident on the target tissue via the dove prism and the first coupling lens group in sequence, and the second light ray is incident on the target tissue via the dove prism and the second coupling lens group in sequence.

[0013] Optionally, a laser channel is provided in the stator unit; the second light is incident on the target tissue through the laser channel; and the rotor unit includes a first light output end, and a first coupling lens group is provided in the first light output end; the first light is incident on the target tissue through the first coupling lens group.

[0014] Optionally, the optical path control module further includes a conduit; the first light is incident on the conduit after passing through the stator unit and the rotor unit in sequence, and the second light is incident on the conduit after passing through the stator unit or passing through the stator unit and the rotor unit in sequence.

[0015] Optionally, the catheter comprises a first pipeline and a second pipeline, the first pipeline is used for passing a guide wire; the second pipeline is used for transmitting the first light, the second light and the scattered light of the first light after passing through the target tissue; wherein the first light is transmitted via a first optical fiber strip, and the second light is transmitted via a second optical fiber strip; the first optical fiber strip and the second optical fiber strip are both arranged in the second pipeline.

[0016] Optionally, the catheter comprises a first tube, a second tube and a third tube, the first tube is used for passing a guide wire; the second tube is used for transmitting the first light and the scattered light of the first light after passing through the target tissue, and the third tube is used for transmitting the second light; wherein the first light is transmitted via a first optical fiber strip, and the second light is transmitted via a second optical fiber strip; the first optical fiber strip is disposed in the second tube and can rotate in the second tube with the rotor unit; the second optical fiber strip is disposed in the third tube.

[0017] Optionally, the first optical fiber strip is disposed close to the outer shell of the catheter, and a light beam window is disposed on the outer shell, wherein the light beam window is used to transmit the first light and receive scattered light of the first light after passing through the target tissue.

[0018] Optionally, an imaging probe is disposed at one end of the first optical fiber strip close to the target tissue; and an ablation probe is disposed at one end of the second optical fiber strip close to the target tissue.

[0019] Optionally, the imaging probe is cylindrical or spherical.

[0020] Optionally, the optical imaging module includes an optical coherence tomography device for providing the first light and forming an image of the target tissue.

[0021] Optionally, the optical coherence tomography imaging device includes a first light emitter, a fiber beam splitter coupler, a circulator, a light delay, a reflector, a fiber beam combiner coupler, a parallel detector and a host computer; wherein the first light emitter is used to provide the first light emitter, and the first light emitter is divided into a first frequency sweeping light splitter and a second frequency sweeping light splitter through the fiber beam splitter coupler; the first frequency sweeping light splitter is incident on the light delay and the reflector in sequence through the reference arm end of the circulator, and is reflected to the light delayer through the reflector, and then returns to the circulator through the light delay; the second frequency sweeping light splitter is emitted through the sample arm end of the circulator and forms the first light; the first light is incident on the target tissue through the optical path control module, and forms scattered light after passing through the target tissue, and the scattered light is then reflected back to the circulator through the optical path control module; the scattered light reflected back into the circulator and the first frequency sweeping light splitter form interference light through the fiber beam combiner coupler, and the interference light enters the host computer through the parallel detector and forms an image of the target tissue on the host computer.

[0022] Optionally, the optical coherence tomography imaging device includes a second light emitter, a fiber beam splitter coupler, a light delay device, a reflector, a spectrometer and a host computer; wherein,

[0023] The second light emitter is used to provide a spectral domain light source, and the spectral domain light source is divided into a first spectral domain light and a second spectral domain light by the optical fiber beam splitter coupler; the first spectral domain light is incident on the light delay device and the reflector in sequence, and is reflected to the light delay device by the reflector, and then returns to the optical fiber beam splitter coupler through the light delay device; the second spectral domain light forms the first light; the first light is incident on the target tissue through the optical path control module, and forms scattered light after passing through the target tissue, and the scattered light is then reflected back into the optical fiber beam splitter coupler through the optical path control module; the scattered light reflected back into the optical fiber beam splitter coupler and the first spectral domain light form interference light, and the interference light enters the host computer through the spectrometer and forms an image of the target tissue on the host computer.

[0024] Optionally, the laser ablation module includes an excimer laser device for providing the second light to ablate the target tissue.

[0025] Optionally, the excimer laser device includes an excimer laser, a beam reduction lens group, a homogenizer, a light coupling lens group and a multimode optical fiber bundle; the excimer laser is used to provide the second light, and the second optical light is sequentially incident on the optical path control module through the beam reduction lens group, the homogenizer, the optical fiber coupling lens group and the multimode optical fiber bundle, and then incident on the target tissue through the optical path control module to ablate the target tissue.

[0026] The integrated optical diagnosis and treatment system provided by the present invention has the following beneficial effects:

[0027] The integrated optical diagnosis and treatment system provided by the present invention includes an optical imaging module, a laser ablation module and an optical path control module; the optical imaging module is used to emit a first light and form an image of a target tissue at least based on the first light; the laser ablation module is used to emit a second light to ablate the target tissue; the optical path control module is used to at least receive the first light and the second light and transmit them to the target tissue; wherein the optical path control module includes a rotor unit; the rotor unit is used to at least drive the first light to rotate around a predetermined axis.

[0028] When the present invention is in use, the optical imaging module is used to perform imaging operations, and the rotor unit is used to realize rotational scanning imaging, which can be effectively applied to application scenarios such as OCT imaging; the laser ablation module can be used to perform laser ablation surgery, and the first optical fiber strip and the second optical fiber strip can be arranged in the same catheter to realize interventional treatment and obtain high-definition real-time images in the blood vessels at the same time, avoiding accidental injury to the blood vessels, and the optical paths of the two optical modules are independent and will not interfere with each other.

[0029] The integrated optical diagnosis and treatment system provided by the present invention utilizes the optical path control module to effectively combine the optical imaging module and the laser ablation module, so that when the laser ablation module ablates the target tissue during surgery, the optical imaging module can provide high-resolution real-time imaging, which helps doctors to adjust the ablation plan in time according to the feedback imaging information to avoid accidental injury to other tissues, and effectively improves the ablation effect and the success rate of the operation. In addition, the first light and the second light provided by the optical imaging module and the laser ablation module, respectively, are independently transmitted in the optical path control module to avoid light crosstalk between the two, thereby ensuring the ablation effect and imaging quality. In addition, the rotor unit in the optical path control module meets the rotational scanning imaging requirements of the optical imaging module, ensuring its better imaging quality. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] Figure 1 A schematic diagram of the structure of an integrated optical diagnosis and treatment system provided by a first embodiment of the present invention;

[0031] Figure 2 A schematic diagram of the structure of an integrated optical diagnosis and treatment system provided by a second embodiment of the present invention;

[0032] Figure 3 A schematic diagram of the structure of an integrated optical diagnosis and treatment system provided by a third embodiment of the present invention;

[0033] Figure 4 A schematic diagram of the structure of an integrated optical diagnosis and treatment system provided by a fourth embodiment of the present invention;

[0034] Figure 5 A cross-sectional view of an optical path control module provided in a first embodiment of the present invention;

[0035] Figure 6 for Figure 5 A partial enlarged schematic diagram of the middle A area;

[0036] Figure 7 A schematic diagram of the three-dimensional structure of a light path control module provided by the first embodiment of the present invention from a first viewing angle;

[0037] Figure 8 A schematic diagram of the three-dimensional structure of the light path control module provided by the first embodiment of the present invention from a second viewing angle;

[0038] Fig. 9 A cross-sectional view of an optical path control module provided in a second embodiment of the present invention;

[0039] Fig.10 A schematic diagram of the structure of an excimer laser device provided by an embodiment of the present invention;

[0040] Fig.11 A schematic diagram of the structure of a catheter provided by an embodiment of the present invention;

[0041] Fig.12 A schematic diagram of the three-dimensional structure of the distal end of a catheter provided by the first embodiment of the present invention;

[0042] Fig.13 A schematic diagram of the three-dimensional structure of the distal end of a catheter provided in a second embodiment of the present invention;

[0043] Fig.14 A schematic diagram of the three-dimensional structure of the distal end of a catheter provided in a third embodiment of the present invention;

[0044] The accompanying drawings are denoted as follows:

[0045] 110-fiber optic conduit; 111-imaging fiber; 112-sample; 113-stator unit; 1131-first collimating lens group; 1132-second collimating lens group; 114-filter; 115-rotor unit; 1151-first coupling lens group; 1152-second coupling lens group;

[0046] 200-excimer laser; 201-beam reduction lens group; 202-light homogenizer; 203-coupling lens group; 204-multimode fiber bundle; 205-laser fiber;

[0047] 301-first light emitter; 302-fiber beam splitter coupler; 303-circulator reference arm end; 304-fiber delay; 305-retroreflector; 306-fiber beam combiner coupler; 307-balanced detector; 308-circulator sample arm end; 309-host computer;

[0048] 401-SLD light source; 402-fiber beam splitter coupler; 403-fiber delay; 404-retroreflector; 405-spectrometer; 406-host computer; 407-circulator;

[0049] 511-linear motor; 512-inlet fiber holder; 513-linear motor support; 514-guide rail seat; 515-guide rod; 516-exit fiber holder; 521-stator housing; 522-small bearing; 531-slider base; 532-synchronous belt; 533-small pulley; 534-rotating motor; 535-tensioning wheel bearing; 536-tensioning wheel seat; 537-stop pin; 541-filter; 542-planetary gear bearing; 543-Dove prism gear bearing; 545-Dove prism mounting gear; 546-planetary gear; 551-rotor housing; 552-outer bearing; 553-outer belt pulley;

[0050] 601-fiber optic plug; 602-fiber optic plug; 611-beam window; 612-imaging probe; 613-laser probe; 614-guide wire support structure; 615-guide wire channel; 616-catheter housing; 617-first developing ring; 618-second developing ring;

[0051] 62-catheter; 621-beam window; 622-imaging probe; 623-laser probe; 624-guidewire support structure; 625-guidewire channel; 626-catheter housing;

[0052] 63-catheter; 631-guidewire; 632-catheter housing; 633-laser probe; 634-guidewire support structure; 635-imaging probe. DETAILED DESCRIPTION

[0053] In order to make the purpose, advantages and features of the present invention clearer, the present invention is further described in detail below in conjunction with the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale, and are only used to conveniently and clearly assist in explaining the purpose of the embodiments of the present invention. In addition, the structure shown in the drawings is often a part of the actual structure. In particular, the emphasis of each drawing is different, and sometimes different scales are used.

[0054] It should be understood that when an element or layer is referred to as "on...", "connected to" other elements or layers, it can be directly on other elements or layers, connected to other elements or layers, or there can be intervening elements or layers. On the contrary, when an element is referred to as "directly on...", "directly connected to" other elements or layers, there is no intervening element or layer. Although the terms first, second, third, etc. can be used to describe various elements, components, regions, layers and / or parts, these elements, components, regions, layers and / or parts should not be limited by these terms. These terms are only used to distinguish an element, component, region, layer or part from another element, component, region, layer or part. Therefore, without departing from the teachings of the present invention, the first element, component, region, layer or part discussed below can be represented as a second element, component, region, layer or part. Spatial relationship terms such as "under...", "below", "below", "above...", "above", "above", etc., can be used here for the convenience of description to describe the relationship between an element or feature shown in the figure and other elements or features. It should be understood that, in addition to the orientation shown in the figure, the spatial relationship terms are intended to include different orientations of the devices in use and operation. For example, if the device in the accompanying drawings is turned over, then, the elements or features described as "under...", "below", "below" will be oriented to be "on" other elements or features. The device can be oriented in addition (rotated 90 degrees or other orientations) and the spatial descriptors used herein are interpreted accordingly. The purpose of the terms used herein is only to describe specific embodiments and is not intended to be a limitation of the present invention. When used here, the singular forms of "one", "one" and "said / the" are also intended to include plural forms, unless the context clearly indicates another way. It should also be understood that the term "include" is used to determine the presence of features, steps, operations, elements and / or parts, but does not exclude the presence or addition of one or more other features, steps, operations, elements, parts and / or groups. When used here, the term "and / or" includes any and all combinations of the relevant listed items.

[0055] The “distal end” mentioned in the present invention refers to the end of the medical device away from the operator after being delivered into the human body, and the “proximal end” mentioned in the present invention refers to the end of the medical device close to the operator after being delivered into the human body.

[0056] The object of the present invention is to provide an integrated optical diagnosis and treatment system, which enables the combined use of multiple optical modules without interfering with each other.

[0057] To achieve the above-mentioned object, the present invention provides an integrated optical diagnosis and treatment system, comprising an optical imaging module, a laser ablation module and an optical path control module;

[0058] The optical imaging module is used to emit a first light and form an image of a target tissue at least according to the first light;

[0059] The laser ablation module is used to emit a second light to ablate the target tissue;

[0060] The optical path control module is at least used to receive the first light and the second light, and transmit them to the target tissue; wherein the optical path control module includes a rotor unit; the rotor unit is used to at least drive the first light to rotate around a predetermined axis.

[0061] When the present invention is in use, the optical imaging module is used to perform imaging operations, and the rotor unit is used to realize rotational scanning imaging, which can be effectively applied to application scenarios such as OCT imaging; the laser ablation module can be used to perform laser ablation surgery, and the first optical fiber strip and the second optical fiber strip can be arranged in the same catheter to realize interventional treatment and obtain high-definition real-time images in the blood vessels at the same time, avoiding accidental injury to the blood vessels, and the optical paths of the two optical modules are independent and will not interfere with each other.

[0062] It should be understood that the propagation of light between the components may use optical fiber as a propagation medium.

[0063] For details, please refer to Figure 1 , Figure 1 This is a schematic diagram of the structure of the integrated optical diagnosis and treatment system provided by the first embodiment of the present invention. Figure 1 As shown, the optical imaging module includes an optical coherence tomography device for providing the first light and forming an image of the target tissue. Specifically, it may include an OCT imaging module, which can be divided into a swept frequency OCT imaging module and a spectral domain OCT imaging module. The technical solution of the present invention is explained below in combination with the principles of the two OCT imaging modules.

[0064] Please continue to refer to Figure 1 ,like Figure 1As shown, the optical coherence tomography imaging device includes a first light emitter 301, a fiber beam splitter coupler 302, a circulator (including a circulator reference arm end 303 and a circulator sample arm end 308 according to the position), a light delay 304, a reflector 305, a fiber beam combiner coupler 306, a parallel detector 307 and a host computer 309; wherein, the first light emitter 301 is used to provide a swept frequency light source, and the swept frequency light source is divided into a first swept frequency split light and a second swept frequency split light through the fiber beam splitter coupler 302; the first swept frequency split light is incident on the light delay 304 and the reflector 305 in sequence through the reference arm end of the circulator, and is reflected by the reflector 305 to the light The light beam is transmitted through the optical fiber delay device 304 and then returns to the circulator through the optical fiber delay device 304; the second frequency-scanning spectroscopic light is emitted through the sample arm end 308 of the circulator to form the first light beam; the first light beam is incident on the target tissue (i.e., the sample 112 in the figure) through the optical path control module, and forms scattered light after passing through the target tissue, and the scattered light is then reflected back to the circulator through the optical path control module; the scattered light reflected back into the circulator and the first frequency-scanning spectroscopic light form interference light through the optical fiber beam combining coupler 306, and the interference light enters the host computer 309 through the parallel detector 307, and forms an image of the target tissue on the host computer 309.

[0065] Please refer to Figure 2 , Figure 2 A schematic diagram of the structure of an integrated optical diagnosis and treatment system provided in a second embodiment of the present invention. Figure 2 Examples and Figure 1 The difference of the embodiment is that Figure 1 The OCT imaging module is a swept frequency OCT imaging device. Figure 2 The OCT imaging module is a spectral domain OCT imaging device. Figure 2As shown, the optical coherence tomography imaging device includes a second light emitter 401, an optical fiber beam splitter coupler 402, a light delay 403, a reflector 404, a spectrometer 405 and a host computer 406; wherein the second light emitter 401 is used to provide a spectral domain light source, and the spectral domain light source is divided into a first spectral domain split light and a second spectral domain split light by the optical fiber beam splitter coupler 402; the first spectral domain split light is sequentially incident on the light delay 403 and the reflector 404, and is reflected by the reflector 404 to the light delay 403, and then returns to the light delay 403 through the light delay 403. The optical fiber beam splitter coupler 402 is used; the second spectral domain is split to form the first light; the first light is incident on the target tissue (i.e., the sample 112 in the figure) through the optical path control module, and forms scattered light after passing through the target tissue, and the scattered light is reflected back into the optical fiber beam splitter coupler 402 through the optical path control module; the scattered light reflected back into the optical fiber beam splitter coupler 402 and the first spectral domain are split to form interference light, and the interference light enters the host computer 406 through the spectrometer 4052, and forms an image of the target tissue on the host computer 406.

[0066] Please refer to Figure 1 and Figure 2 , because the OCT imaging device needs to perform 360-degree rotation scanning imaging on the sample 112, the rotor unit 115 drives the first optical fiber strip 101 to rotate around a predetermined axis, which can achieve 360-degree rotation scanning imaging in cooperation with the OCT imaging module. It should be understood that the rotor unit 115 can be used in conjunction with a stator, based on which the present invention provides the following technical solutions: the optical path control module also includes a stator unit 113, and the rotor unit 115 can rotate relative to the stator unit 113; wherein the first light and the second light are respectively incident on the target tissue through the stator unit 113.

[0067] Since scattered light from other modules may appear during the use of the present invention, for example, when the laser ablation module is an excimer laser device, the excimer laser may also return to the OCT imaging module along with the scattered light after the first light passes through the target tissue. Based on this, the present invention provides the following technical solutions: the stator unit 113 includes a first light input end; and a first collimating lens group 1131 and a filter 114 are arranged in the first light input end, and the first light is incident on the rotor unit 115 through the first collimating lens group 1131 and the filter 114 in sequence; wherein the filter 114 is used to pass the first light and the scattered light after the first light passes through the target tissue, and can cut off the second light from returning to the first light input end.

[0068] Please continue to refer to Figure 1 and Figure 2 ,exist Figure 1 and Figure 2 In the illustrated embodiment, a laser channel is disposed in the stator unit 113; the second light is incident on the target tissue via the laser channel; and the rotor unit 115 includes a first light output end, and a first coupling lens group 1151 is disposed in the first light output end; the first light is incident on the target tissue via the first coupling lens group 1151.

[0069] It can be seen that in Figure 1 and Figure 2 In the illustrated embodiment, the first light beam rotates alone around a predetermined axis, while the second light beam does not rotate.

[0070] Please refer to Figure 3 , Figure 3 This is a schematic diagram of the structure of an integrated optical diagnosis and treatment system provided by the third embodiment of the present invention. Figure 3 As shown, Figure 3 The examples in Figure 1 , Figure 2 The difference between the embodiments in is that Figure 3 The embodiment in includes a Dove prism 116.

[0071] In the embodiment including the dove prism 116 , the stator unit 113 further includes a second light input end, and a second collimating lens group 1132 is disposed in the second light input end; the second light is incident on the rotor unit 115 through the second collimating lens group 1132 .

[0072] The rotor unit 115 includes a dove prism 116, a first light output end and a second light output end; wherein, a first coupling lens group 1151 is arranged in the first light output end, and a second coupling lens group 1152 is arranged in the second light output end; the first light is incident on the target tissue via the dove prism 116 and the first coupling lens group 1151 in sequence, and the second light is incident on the target tissue via the dove prism 116 and the second coupling lens group 1152 in sequence.

[0073] The following is an overall description of the optical path relay path Figure 3 Detailed description of the illustrated embodiment.

[0074] The laser ablation module is connected to the optical path control module so that the second light can propagate between the laser ablation module and the optical path control module. The stator unit 113 includes a first collimating lens group 1131 and a second collimating lens group 1132. The first light enters the optical path control module through the first collimating lens group 1131, and the second light enters the optical path control module through the second collimating lens group 1132. The optical path control module also includes a dove prism 116. The rotor unit 115 also includes a first coupling lens group 1151 and a second coupling lens group 1152. The rotor unit 115 is in transmission connection with the dove prism 116. The transmission connection between the dove prism 115 and the dove prism 116 has a transmission ratio, so that when the dove prism 116, the first coupling lens group 1151, and the second coupling lens group 1152 rotate with the rotor unit 116, the first light ray can always be transmitted to the first optical fiber strip 101 through the first coupling lens group 1151 after being refracted by the dove prism 116, and the second light ray can always be transmitted to the second optical fiber strip 102 through the second coupling lens group 1152 after being refracted by the dove prism 116. Such a configuration can further realize the integrity of the optical imaging module and the laser ablation module, and the transmission mechanism including the dove prism 116 can be used to realize that the light between the two optical modules does not interfere with each other. In this way, when the optical imaging module is an OCT imaging module and the laser ablation module is an excimer laser device, the present invention can realize both 360-degree rotation scanning imaging and laser ablation, and the two optical paths can be realized without interference with each other by using the dove prism 116.

[0075] Please refer to Figure 4 , Figure 4 This is a schematic diagram of the structure of an integrated optical diagnosis and treatment system provided by the fourth embodiment of the present invention. Figure 4 As shown, Figure 4 Examples and Figure 3 The difference of the embodiment is that Figure 3 The OCT imaging module is a swept frequency OCT imaging module. Figure 4 The OCT imaging module is a spectral domain OCT imaging module.

[0076] The specific implementation of the present invention is described below in conjunction with a specific mechanical structure. It should be noted that the mechanical structure of the present invention is not limited to this.

[0077] In an exemplary embodiment, the optical path control module is disposed on a slide rail, the optical path control module is connected to the catheter, and the optical path control module can reciprocate along the slide rail to drive the catheter 110 and the first optical fiber strip 101 and the second optical fiber strip 102 in the catheter 110 to move, thereby achieving the advancement and retraction of the distal end in vitro during the treatment process. Figures 5 to 8 , Figure 5 A cross-sectional view of an optical path control module provided in a first embodiment of the present invention; Figure 6 for Figure 5 A partial enlarged schematic diagram of the middle A area; Figure 7 A schematic diagram of the three-dimensional structure of a light path control module provided by the first embodiment of the present invention from a first viewing angle; Figure 8 This is a schematic diagram of the three-dimensional structure of the light path control module provided by the first embodiment of the present invention from a second viewing angle. Figures 5 to 8As shown, specifically, the slide rail can be a guide rod 515, which is positioned through a blind hole of a guide rail seat 514 and fixed with glue. The two guide rods 515 pass through two through holes of a slider base 531 respectively, so that the slider base 531 can slide along the guide rod 515. The linear motor 511 is mounted on the linear motor support 513 by screws, and the linear motor support 513 is also mounted on the guide rail seat 514 by screws. The rotating screw of the linear motor 511 penetrates into the threaded through hole of the slider base 531, and the linear motor 511 drives the slider base 531 to slide along the guide rod 515 by rotating the screw. In this way, the present invention installs the linear motor 511 on the guide rail seat 514, and a rotating screw is extended from the linear motor 511, which is precisely matched with the threaded through hole on the slider base 531, so that the slider base 531 can move quickly and accurately in the axial direction of the guide rod 515. In addition, a double rail structure can be adopted to realize stable movement of the slider base 531 on the rail without shaking. The inlet fiber seat 512 and the outlet fiber seat 516 are installed on the rail seat 514 by screws. The rotating motor 534 is installed in the countersunk hole of the slider base 531 by screws, and the small pulley 533 is sleeved on the rotating shaft of the rotating motor 534 and fixed by glue or interference fit. The tensioning wheel seat 536 is installed on the slider base 531 by screws passing through its waist hole, and can be adjusted by sliding forward and backward along the direction of the line connecting the two centers of the waist hole. The inner ring of the tensioning wheel bearing 535 is fixed on the shaft of the tensioning wheel seat 536 by glue or interference fit. The synchronous belt 532 is wound around the tooth surfaces of the small pulley 533 and the large pulley 553, and by adjusting the position of the tensioning wheel seat 536, the synchronous belt 532 is tensioned with the outer ring of the tensioning wheel bearing 535 to achieve smooth transmission from the rotating motor 534 to the rotor housing 551. In this way, by setting the rotor pulley, the linear motor 511 can directly drive the rotor housing 551 to rotate at high speed through the pulley, and the rotation position of the rotor housing 551 is limited by two rotor outer bearings set on the rotor housing 551, so that the rotor housing 551 is conveniently assembled and fixed with the external slider base 531, and then the rotor housing 551 is conveniently rotated under the drive of the linear motor 511. The anti-rotation pin 537 passes through the through holes of the slider base 531 and the stator housing 521 at the same time and is fixed by glue to achieve anti-rotation of the stator unit 520.

[0078] The rotor unit includes an integrally formed rotor housing 551, which is installed in the through hole of the slider base 531 through two outer bearings 552, and the inner and outer rings of the bearings are fixed to the shaft holes matched with them by glue. The outer peripheral pulley 553 is sleeved on the outer circumferential surface of the rotor housing 551 and fixed by glue or interference fit. The stator housing 521 is installed in the through hole of the rotor housing 551 through two small bearings 522, and the inner and outer rings of the bearings are fixed to the shaft holes matched with them by glue. The planetary gear 546 is installed in the blind hole of the stator housing 521 by means of the planetary gear bearing 542 fixed by glue, and the outer tooth surface of the planetary gear 546 meshes with the inner tooth surface of the rotor housing 551. When the stator housing 521 revolves relative to the rotor housing 551, the planetary gear 546 rotates. The dove prism 116 is installed in the through hole of the dove prism mounting gear 545 and fixed by glue. The dove prism mounting gear 545 is sleeved on the outer circumference of the stator housing 521 through the dove prism gear bearing 543, and the inner and outer rings of the bearing are fixed to the shaft hole matched with the bearing by glue, and the outer tooth surface of the dove prism mounting gear 545 is meshed with the outer tooth surface of the planetary gear 546. The transmission ratio is controlled by adjusting the tooth number ratio between the outer tooth surface of the dove prism mounting gear 545 and the inner tooth surface of the rotor housing 551, so as to achieve a certain ratio of the rotation speed of the dove prism 116 and the rotor housing 551 relative to the stator housing 521 (this ratio is determined by the internal structure of the dove prism 116). Through the transmission structure of three gears, the dove prism 116 and the rotor housing 551 have a certain transmission ratio when they rotate relative to the stator housing 521, so that the continuous propagation of the dual-channel optical signal during the rotation process can be maintained without interruption and crossover. When the dove prism 116, the first coupling lens group 1151, and the second coupling lens group 1152 rotate with the rotor unit 116, the first light ray can always be transmitted to the first optical fiber 101 through the first coupling lens group 1151 after being refracted by the dove prism 116, and the second light ray can always be transmitted to the second optical fiber 102 through the second coupling lens group 1152 after being refracted by the dove prism 116. In this way, it can be ensured that when the two incident light rays of the stator housing 521 rotate at a certain angular velocity relative to the two outgoing light rays of the rotor housing 551, the two light rays can also be transmitted in a one-to-one correspondence without crossing. Therefore, the present invention realizes the rotation and transmission of dual-channel optical signals without mutual interference through the differential rotation of the dove prism 116 and the rotor housing 551 relative to the stator housing 521.

[0079] Please refer to Fig. 9 , Fig. 9 This is a cross-sectional view of an optical path control module provided in the second embodiment of the present invention. Fig. 9 As shown, Fig. 9 The examples in Figure 5 The difference between the embodiments in is that Fig. 9 The second optical fiber strip 102 is routed independently and Fig. 9 The embodiment does not include a Dove prism. It can be seen that Figure 5 The mechanical structure corresponds to the application Figure 1 and Figure 2 The optical diagnosis and treatment integrated system Fig. 9 The mechanical structure in the corresponding application Figure 3 and Figure 4 The integrated optical diagnostic and therapeutic system shown in .

[0080] In combination with the above specific mechanical structure, the optical path control module has the following advantages:

[0081] 1. The optical rotation transmission structure of the present invention is compact, consistent with the single-channel optical rotation transmission structure in appearance, driving mode and structure, which can save a lot of development costs and improve product versatility.

[0082] 2. The present invention enables the optical path to rotate 360° without restriction and the transmission signal is more stable.

[0083] It should be understood that the laser ablation module may include an excimer laser device for providing the second light to ablate the target tissue. Fig.10 , Fig.10 FIG. 1 is a schematic diagram of the structure of an excimer laser device provided by an embodiment of the present invention. Fig.10 As shown, in an exemplary embodiment, the excimer laser device includes an excimer laser 200, a beam reduction lens group 201, a light homogenizer 202, and a fiber coupling lens group 203, which can be coaxially arranged in sequence but are not limited thereto. The excimer laser is used to provide the second light, and the second light is incident on the optical path control module through the beam reduction lens group 201, the light homogenizer 202, the fiber coupling lens group 203, and the multimode optical fiber bundle 204 in sequence, and then incident on the target tissue after passing through the optical path control module to ablate the target tissue. When the excimer laser device is working, the excimer laser 200 emits the second light (generally a laser beam with a square spot), the size of which can be about 24*10mm. The laser beam is reduced to a smaller spot by the beam reduction lens group 201, and then the laser beam is multiplied to form a spot with uniform energy distribution after passing through the homogenizer 202 (which can be a homogenizer rod, a homogenizer sheet or a Fresnel lens or other homogenizer devices). The laser beam is then coupled into the multimode fiber bundle 204 (a fiber bundle composed of one or more multimode optical fibers) after passing through the coupling lens group 203 (a plano-convex lens, an aspheric lens or an achromatic cemented lens). The laser beam, i.e., the second light, can be divided into the following types: Figure 1 and Figure 2 The embodiment shown in the figure is transmitted through the second optical fiber strip 102, and can also be transmitted according to Figure 3 and Figure 4 The embodiment shown is transmitted into the optical path control system and then further transmitted out through the second optical fiber strip 102. With such an arrangement, the present invention can realize OCT and excimer laser ablation functions in the same machine by compositely transmitting excimer laser ablation and OCT imaging through dual-channel optical signals, which is convenient for doctors to use, and can save a machine, so that patients are spared the pain of two different examinations.

[0084] It can be concluded from the above description that when the rotor unit includes the dove prism 116, the first optical fiber strip 101 and the second optical fiber strip 102 will be driven to rotate together, otherwise the first optical fiber strip 101 rotates alone, so the internal structure of the conduit 110 needs to be designed accordingly to cooperate with the rotation. Based on this, the present invention provides the following technical solutions: the optical path control module also includes a conduit 110; the conduit 110 is connected to the rotor unit 115 and can rotate with the rotor unit 115; wherein the first light and the second light are incident into the conduit 110 after passing through the rotor unit 115.

[0085] Please refer to Figure 11 to Figure 12 , Fig.11 A schematic diagram of the structure of a catheter 110 provided in one embodiment of the present invention; Fig.12 The 3D structure diagram of the distal end of the catheter 110 provided by the first embodiment of the present invention. The rotor unit includes a dove prism 116. At this time, the second optical fiber strip 102 needs to rotate together with the first optical fiber strip 101. Based on this, the present invention provides the following technical solutions: The catheter 110 has a first pipeline and a second pipeline. The first pipeline is used to pass a guide wire (see Fig.14 The second pipeline is used to transmit the first light, the second light and the scattered light after the first light passes through the target tissue; wherein the first light is transmitted through the first optical fiber strip 101, and the second light is transmitted through the second optical fiber strip 102; the first optical fiber strip 101 and the second optical fiber strip 102 are both arranged in the second pipeline. Optical fiber fixing structures are also arranged at the optical fiber entrance and exit, such as Fig.11 The optical fiber quick plug 601 and the optical fiber quick plug 602 prevent the optical fiber from swinging during movement.

[0086] When the optical imaging module is an OCT imaging module, in order to enable the first optical fiber strip 101 to achieve 360-degree rotational scanning imaging, an imaging probe 612 is provided at the end of the first optical fiber strip 102, and an ablation probe 613 is provided at the end of the second optical fiber strip close to the target tissue. The imaging probe 612 is arranged close to the catheter housing 616, and a light beam window 611 is provided on the catheter housing 616. The imaging probe 612 uses the light beam window 611 to transmit the first light and receive the scattered light of the first light after passing through the target tissue, so that when the catheter 110 rotates 360 degrees around its own axis, the imaging probe 612 uses the light beam window 611 to achieve 360-degree scanning.

[0087] Please refer to Fig.13 , Fig.13 This is a schematic diagram of the three-dimensional structure of the distal end of the catheter 100 provided in the second embodiment of the present invention. Fig.13 The examples in Fig.12 The difference between the embodiments is that Fig.13 The imaging probe 622 in the embodiment is a columnar probe, which can provide clearer scanning. Fig.12 The imaging probe 612 in the figure is a spherical probe, and its scanning range is larger.

[0088] Please refer to Fig.14 , Fig.14 This is a schematic diagram of the three-dimensional structure of the distal end of the catheter 110 provided in the third embodiment of the present invention. Fig.14 The embodiment shown is Fig.12 , Fig.13 The difference between the illustrated embodiments is that the catheter 110 is further provided with a third pipeline. Furthermore, the first pipeline is used to pass the guide wire 631; the second pipeline is used to transmit the first light and the scattered light of the first light after passing through the target tissue; the third pipeline is used to transmit the second light. Wherein, the first light is transmitted through the first optical fiber strip 101, and the second light is transmitted through the second optical fiber strip 102; the first optical fiber strip 101 is arranged in the second pipeline, and can rotate in the second pipeline with the rotor unit; the second optical fiber strip 102 is arranged in the third pipeline. Preferably, an imaging probe 634 is also provided at one end of the first optical fiber strip 101 close to the target tissue, and the imaging probe 634 is not limited to a spherical probe or a cylindrical probe. And, an ablation probe is also provided at one end of the second optical fiber strip 102 close to the target tissue to achieve ablation of the target tissue.

[0089] It should be noted that Fig.14The first optical fiber strip 101 in the three-dimensional structure at the distal end of the catheter 110 shown is connected to the rotor unit separately so that the first optical fiber strip 101 can rotate independently in the second pipe, and the catheter 110 does not need to be connected to the rotor unit. That is, during the operation, the second optical fiber strip 102 in the catheter 110 may not rotate with the rotor unit, and only the first optical fiber strip 101 rotates with the rotor unit to meet the needs of rotational scanning imaging. Therefore, in this scenario, the imaging probe 635 will not rely on the beam window, and 360-degree scanning can be achieved by extending the catheter 110. Fig.14 The catheter 110 shown does not need to be provided with a beam window at the distal end.

[0090] In summary, the integrated optical diagnosis and treatment system provided by the present invention utilizes the optical path control module to effectively combine the optical imaging module and the laser ablation module, so that when the laser ablation module ablates the target tissue during the operation, the optical imaging module can provide high-resolution real-time imaging, which helps the doctor to adjust the ablation plan in time according to the feedback imaging information, avoid accidental injury to other tissues, and effectively improve the ablation effect and the success rate of the operation. In addition, the first light and the second light provided by the optical imaging module and the laser ablation module, respectively, are independently transmitted in the optical path control module to avoid light crosstalk between the two, thereby ensuring the ablation effect and imaging quality. In addition, the rotor unit in the optical path control module meets the rotational scanning imaging requirements of the optical imaging module, ensuring its better imaging quality.

[0091] It should be noted that the various embodiments in this specification are described in a progressive manner, and each embodiment focuses on the differences from other embodiments, and the same or similar parts between the various embodiments can be referred to each other. For the system disclosed in the embodiment, since it corresponds to the method disclosed in the embodiment, the description is relatively simple, and the relevant parts can be referred to the method part description.

[0092] It should also be noted that, although the present invention has been disclosed as a preferred embodiment, the above embodiment is not intended to limit the present invention. For any technician familiar with the art, without departing from the scope of the technical solution of the present invention, the technical content disclosed above can be used to make many possible changes and modifications to the technical solution of the present invention, or modified into equivalent embodiments of equivalent changes. Therefore, any simple modification, equivalent change and modification made to the above embodiments according to the technical essence of the present invention without departing from the content of the technical solution of the present invention still falls within the scope of protection of the technical solution of the present invention.

[0093] It should also be understood that, unless otherwise specified or indicated, the terms "first", "second", "third", etc. in the specification are merely used to distinguish between the various components, elements, steps, etc. in the specification, and are not used to indicate the logical relationship or sequential relationship between the various components, elements, steps, etc.

[0094] It should also be recognized that the terms described herein are used only to describe specific embodiments and are not intended to limit the scope of the invention. It should be noted that the singular forms "a" and "an" used herein and in the appended claims include plural references unless the context clearly indicates otherwise. For example, a reference to "a step" or "a device" means a reference to one or more steps or devices, and may include secondary steps and secondary devices. All conjunctions used should be understood in the broadest sense. And, the word "or" should be understood to have the definition of a logical "or", rather than a logical "exclusive or", unless the context clearly indicates otherwise. In addition, the implementation of embodiments of the present invention may include performing selected tasks manually, automatically, or in combination.

Claims

1. An integrated optical diagnosis and treatment system, characterized in that: It includes an optical imaging module, a laser ablation module and an optical path control module; The optical imaging module is used to emit a first light and form an image of a target tissue at least according to the first light; The laser ablation module is used to emit a second light to ablate the target tissue; The optical path control module is at least used to receive the first light and the second light, and transmit them to the target tissue; wherein the optical path control module includes a rotor unit; the rotor unit is used to at least drive the first light to rotate around a predetermined axis.

2. The integrated optical diagnosis and treatment system according to claim 1, characterized in that: The optical path control module further includes a stator unit, and the rotor unit can rotate relative to the stator unit; wherein the first light and the second light are incident on the target tissue respectively through the stator unit.

3. The integrated optical diagnosis and treatment system according to claim 2, characterized in that: The stator unit includes a first light input end; and a first collimating lens group and a filter are arranged in the first light input end, and the first light is incident on the rotor unit through the first collimating lens group and the filter in sequence; wherein the filter is used to pass the first light and the scattered light after the first light passes through the target tissue, and can cut off the second light from returning to the first light input end.

4. The integrated optical diagnosis and treatment system according to claim 3, characterized in that: The stator unit further includes a second light-incoming end, and a second collimating lens group is disposed in the second light-incoming end; the second light is incident on the rotor unit through the second collimating lens group.

5. The integrated optical diagnosis and treatment system according to any one of claims 1 to 4, characterized in that: The rotor unit includes a dove prism, a first light output end, and a second light output end; wherein a first coupling lens group is arranged in the first light output end, and a second coupling lens group is arranged in the second light output end; the first light is incident on the target tissue via the dove prism and the first coupling lens group in sequence, and the second light is incident on the target tissue via the dove prism and the second coupling lens group in sequence.

6. The integrated optical diagnosis and treatment system according to claim 3, characterized in that: A laser channel is provided in the stator unit; the second light is incident on the target tissue through the laser channel; and, The rotor unit includes a first light-emitting end, and a first coupling lens group is disposed in the first light-emitting end; the first light is incident on the target tissue through the first coupling lens group.

7. The integrated optical diagnosis and treatment system according to claim 2, characterized in that: The optical path control module further includes a catheter; the first light is incident on the catheter after passing through the stator unit and the rotor unit in sequence, and the second light is incident on the catheter after passing through the stator unit or passing through the stator unit and the rotor unit in sequence.

8. The integrated optical diagnosis and treatment system according to claim 7, characterized in that: The catheter is connected to the rotor unit and can rotate with the rotor unit; wherein the catheter has a first pipeline and a second pipeline; the first pipeline is used to pass a guide wire; the second pipeline is used to transmit the first light, the second light, and the scattered light of the first light after passing through the target tissue; Furthermore, the first light is transmitted through a first optical fiber strip, and the second light is transmitted through a second optical fiber strip; the first optical fiber strip and the second optical fiber strip are both disposed in the second pipe.

9. The integrated optical diagnosis and treatment system according to claim 7, characterized in that: The catheter has a first pipeline, a second pipeline and a third pipeline; the first pipeline is used to pass the guide wire; the second pipeline is used to transmit the first light and the scattered light of the first light after passing through the target tissue; The third pipeline is used to transmit the second light; Wherein, the first light is transmitted through a first optical fiber strip, and the second light is transmitted through a second optical fiber strip; the first optical fiber strip is disposed in the second pipe and can rotate with the rotor unit in the second pipe; The second optical fiber strip is arranged in the third pipe.

10. The integrated optical diagnosis and treatment system according to claim 8, characterized in that: The first optical fiber strip is arranged close to the outer shell of the catheter, and a light beam window is arranged on the outer shell. The light beam window is used to transmit the first light and receive scattered light of the first light after passing through the target tissue.

11. The integrated optical diagnosis and treatment system according to claim 8 or 9, characterized in that: An imaging probe is disposed at one end of the first optical fiber strip close to the target tissue; an ablation probe is disposed at one end of the second optical fiber strip close to the target tissue.

12. The integrated optical diagnosis and treatment system according to claim 11, characterized in that: The imaging probe is cylindrical or spherical.

13. The integrated optical diagnosis and treatment system according to claim 1, characterized in that: The optical imaging module includes an optical coherence tomography device for providing the first light and forming an image of the target tissue.

14. The integrated optical diagnosis and treatment system according to claim 13, characterized in that: The optical coherence tomography device comprises a first light emitter, a fiber beam splitter coupler, a circulator, a light delay device, a retroreflector, a fiber beam combiner coupler, a parallel detector and a host computer; wherein, The first light emitter is used to provide a first light emitter, and the first light emitter is divided into a first frequency sweeping light splitter and a second frequency sweeping light splitter through the optical fiber beam splitter coupler; the first frequency sweeping light splitter is incident on the light delay device and the reflector in sequence through the reference arm end of the circulator, and is reflected to the light delay device through the reflector, and then returns to the circulator through the light delay device; the second frequency sweeping light splitter is emitted through the sample arm end of the circulator and forms the first light; the first light is incident on the target tissue through the optical path control module, and forms scattered light after passing through the target tissue, and the scattered light is then reflected back to the circulator through the optical path control module; the scattered light reflected back into the circulator and the first frequency sweeping light splitter form interference light through the optical fiber beam combiner coupler, and the interference light enters the host computer through the parallel detector, and forms an image of the target tissue on the host computer.

15. The integrated optical diagnosis and treatment system according to claim 13, characterized in that: The optical coherence tomography device includes a second light emitter, a fiber beam splitter coupler, a light delay device, a reflector, a spectrometer and a host computer; wherein, The second light emitter is used to provide a spectral domain light source, and the spectral domain light source is divided into a first spectral domain light and a second spectral domain light by the optical fiber beam splitter coupler; the first spectral domain light is incident on the light delay device and the reflector in sequence, and is reflected to the light delay device by the reflector, and then returns to the optical fiber beam splitter coupler through the light delay device; the second spectral domain light forms the first light; the first light is incident on the target tissue through the optical path control module, and forms scattered light after passing through the target tissue, and the scattered light is then reflected back into the optical fiber beam splitter coupler through the optical path control module; the scattered light reflected back into the optical fiber beam splitter coupler and the first spectral domain light form interference light, and the interference light enters the host computer through the spectrometer and forms an image of the target tissue on the host computer.

16. The integrated optical diagnosis and treatment system according to claim 1, characterized in that: The laser ablation module includes an excimer laser device for providing the second light to ablate the target tissue.

17. The integrated optical diagnosis and treatment system according to claim 16, characterized in that: The excimer laser device comprises an excimer laser, a beam reduction lens group, a light homogenizer, a light coupling lens group and a multimode optical fiber bundle; the excimer laser is used to provide the second light, and the second optical light is incident on the optical path control module in sequence through the beam reduction lens group, the light homogenizer, the optical fiber coupling lens group and the multimode optical fiber bundle, and then incident on the target tissue through the optical path control module to ablate the target tissue.

Images