CN219895706U - Parathyroid gland function imaging system and endoscope - Google Patents
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- Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)
Abstract
The utility model discloses a parathyroid gland function imaging system and an endoscope, wherein the imaging system comprises: the light source assembly comprises a white light source and a laser source; the light wave transmission component is integrated in the endoscope and is used for transmitting light waves and transmitting light waves reflected after the parathyroid gland is irradiated; the optical imaging component is used for generating a color image, a near infrared fluorescence image and a laser speckle image of the parathyroid gland from the light waves reflected after the parathyroid gland is irradiated; the image acquisition component is used for acquiring color images, near infrared fluorescent images and laser speckle images; and the processor is used for controlling the operation of the optical imaging assembly and processing the image data acquired by the image acquisition assembly. The utility model uses near infrared fluorescence technology in endoscope to locate parathyroid gland, laser speckle technology displays speckle contrast image of parathyroid gland, and further knows whether blood transport is lost or not, and whether transplantation is needed, so as to guide diagnosis of parathyroid gland function in thyroid operation.
Description
Technical Field
The utility model relates to the field of medical imaging, in particular to a parathyroid gland function imaging system and an endoscope.
Background
Thyroid tumors have increased in incidence year by year, with thyroid cancer having risen to the first malignancy of the head and neck, and after radical surgery for these thyroid cancers, a significant proportion of patients have transient hypoparathyroidism followed by hypercalcemia, with some studies reporting an incidence of up to 47%; of which about 3% present with permanent hypoparathyroidism and dysregulation of blood calcium. While hypocalcemia can lead to arrhythmias, muscle spasms, tics, and severe end-use mortality in the patient. This complication places great economic and physical burden on the patient and his home, which is also one of the main causes of post-thyroid surgery medical malpractice.
Parathyroid glands are the smallest endocrine organs in the human body, usually located in front of the human neck, behind the lateral lobes of the thyroid gland. The parathyroid glands of 80% normal adults are generally 4, each gland is 3-8 mm long, 2-5 mm wide and 0.5-2 mm thick, the mass is generally about 0.05-0.3 g, the parathyroid glands are in a brown yellow oval shape and are attached to the back of thyroid, but the position and number variation are not few, and the parathyroid glands are difficult to distinguish and confirm by color distinction in operation. Therefore, the parathyroid gland is easily resected by mistake in operation and damaged by blood circulation. The thyroid surgery technology rapidly develops nowadays, from open surgery to endoscopic assisted surgery, from thoraco-endoscopic access to transoral vestibular scarless (NOTES) surgery, from field surgery to remote robot assisted surgery, the change of over-the-earth occurs, but the accurate positioning and functional protection of parathyroid glands in the current surgery are difficult to realize.
The related prior art has the problems of destructiveness (such as a local lancing observation method and a multi-caine swelling observation method), low judgment accuracy (such as a rapid detection method in parathyroid hormone operation), inconvenient use (such as an indocyanine green (ICG) angiography method) and the like when detecting parathyroid glands.
Disclosure of Invention
The present utility model aims to solve at least one of the technical problems existing in the prior art. Therefore, the utility model provides the parathyroid gland function imaging system and the endoscope, which can avoid the problems of destructiveness, low judgment accuracy, inconvenient use and the like in the process of detecting parathyroid glands in the prior art.
An embodiment of the utility model according to the first aspect provides a parathyroid function imaging system, comprising: the light source assembly comprises a white light source and a laser source; the light wave transmission component is integrated in the endoscope and is used for transmitting light waves output by the white light source and the laser source to irradiate parathyroid glands in a human body and transmitting light waves reflected after the parathyroid glands are irradiated; an optical imaging assembly for generating a color image, a near infrared fluorescence image and a laser speckle image of the parathyroid gland from the light waves reflected after the parathyroid gland is irradiated; the image acquisition component is used for acquiring a color image, a near infrared fluorescence image and a laser speckle image of the parathyroid gland; and the processor is respectively connected with the optical imaging assembly and the image acquisition assembly and is used for controlling the operation of the optical imaging assembly and processing the image data acquired by the image acquisition assembly.
An embodiment of the parathyroid function imaging system according to the first aspect of the present utility model has at least the following advantages: the utility model obtains clear color images of the surgical visual field background by applying a white light imaging technology in an endoscope, then utilizes a near infrared fluorescence technology to position the parathyroid gland, and uses a laser speckle technology to display speckle contrast images of the parathyroid gland, so as to know whether the blood circulation of the parathyroid gland is lost or not and whether the parathyroid gland needs to be transplanted or not, and the white light imaging technology is used for guiding judgment of the parathyroid gland function in thyroid surgery, thereby reducing the occurrence of the parathyroid gland hypofunction after the operation. Compared with other existing methods, the method can objectively reflect parathyroid gland functions, does not need to additionally inject exogenous contrast agents, is simple and practical, and the like.
According to some embodiments of the first aspect of the utility model, the optical imaging assembly comprises: a first optical splitter for splitting the light reflected by the parathyroid gland into a first coupled light wave and a second coupled light wave; a color imaging unit for receiving the first coupled light waves and separating visible light waves therefrom to generate a color image of the parathyroid gland; the second light splitter is used for receiving the second coupled light waves and is provided with a change-over switch for switching an output path of the second coupled light waves, the output path comprises a first path and a second path, and the change-over switch is connected with the processor; a near infrared fluorescence imaging unit for receiving the second coupled light waves of the first path and separating near infrared fluorescence light waves therefrom to generate a near infrared fluorescence image of the parathyroid gland; and the laser speckle imaging unit is used for receiving the second coupling light wave of the second path and separating the laser light wave from the second coupling light wave to generate a laser speckle image of the parathyroid gland.
According to some embodiments of the first aspect of the utility model, the image acquisition assembly comprises an RGB camera for acquiring the color image, a first fluorescent camera for acquiring the near infrared fluorescent image, and a second fluorescent camera for acquiring the laser speckle.
According to some embodiments of the first aspect of the present utility model, the color imaging unit includes a 400-700nm band-pass filter and a color photoelectric imaging device sequentially disposed between the first beam splitter and the RGB camera.
According to some embodiments of the first aspect of the present utility model, the near infrared fluorescence imaging unit includes a 785nm laser filter, a first bandpass filter, and a first condenser lens sequentially disposed in the first path.
According to some embodiments of the first aspect of the present utility model, the laser speckle imaging unit includes a second bandpass filter, a neutral density filter, and a second condenser lens sequentially disposed in the second path.
According to some embodiments of the first aspect of the present utility model, the light wave transmission assembly includes a single mode fiber, a multimode fiber and an image transmission fiber, which are integrated in an endoscope, the single mode fiber is used for transmitting the light wave output by the laser source, the multimode fiber is used for transmitting the light wave output by the white light source, the image transmission fiber is used for transmitting the light wave reflected by the parathyroid gland after being irradiated, the front ends of the single mode fiber, the multimode fiber and the image transmission fiber are provided with an endoscope probe, a first linear polarizer covering the top ends of the single mode fiber and the multimode fiber is arranged in the endoscope probe, and a second linear polarizer is arranged between the second beam splitter and the second band-pass filter.
According to some embodiments of the first aspect of the utility model, the first beam splitter front end is provided with an achromat and a tunable lens.
According to some embodiments of the first aspect of the utility model, the optical imaging assembly further comprises a converging lens disposed between the first and second optical splitters.
According to the second aspect of the utility model, the endoscope comprises a main case, a display, a perspective tube and the parathyroid endoscope imaging system, wherein the light source assembly, the optical imaging assembly, the image acquisition assembly and the processor are all arranged in the main case, the processor is connected with the display, the display is used for displaying a color image of the parathyroid gland, an image fused by near infrared fluorescent images and the color image and an image fused by laser speckle images and the color image, the light wave transmission assembly is integrated in the perspective tube, and one end of the perspective tube is connected with the main case, and the other end of the perspective tube is connected with an endoscope probe.
An endoscope according to an embodiment of the second aspect of the present utility model has at least the following advantageous effects: the utility model obtains clear color images of the surgical visual field background by applying a white light imaging technology in an endoscope, then utilizes a near infrared fluorescence technology to position the parathyroid gland, and a laser speckle technology displays speckle contrast images of the parathyroid gland so as to know whether the blood circulation of the parathyroid gland is lost or not and whether the parathyroid gland needs to be transplanted or not, so as to guide the judgment of the parathyroid gland function in thyroid surgery and reduce the occurrence of the postoperative parathyroid gland hypofunction. Compared with other existing methods, the method can objectively reflect parathyroid gland functions, does not need to additionally inject exogenous contrast agents, is simple and practical, and the like.
Additional aspects and advantages of the utility model will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the utility model.
Drawings
The foregoing and/or additional aspects and advantages of the utility model will become apparent and may be better understood from the following description of embodiments taken in conjunction with the accompanying drawings in which:
FIG. 1 is a schematic diagram of a parathyroid endoscopic imaging system in accordance with an embodiment of the first aspect of the present utility model;
FIG. 2 is an exploded view of an endoscopic probe according to an embodiment of the first aspect of the present utility model;
FIG. 3 is a cross-sectional view of an endoscopic probe according to an embodiment of the first aspect of the present utility model;
fig. 4 is a schematic diagram of an endoscope according to an embodiment of the second aspect of the present utility model.
Detailed Description
Embodiments of the present utility model are described in detail below, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to like or similar elements or elements having like or similar functions throughout. The embodiments described below by referring to the drawings are illustrative only and are not to be construed as limiting the utility model.
In the description of the present utility model, it should be understood that references to orientation descriptions such as upper, lower, front, rear, left, right, etc. are based on the orientation or positional relationship shown in the drawings, are merely for convenience of description of the present utility model and to simplify the description, and do not indicate or imply that the apparatus or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and thus should not be construed as limiting the present utility model.
In the description of the present utility model, unless explicitly defined otherwise, terms such as arrangement, installation, connection, etc. should be construed broadly and the specific meaning of the terms in the present utility model can be reasonably determined by a person skilled in the art in combination with the specific contents of the technical scheme.
Before describing the present technical solution, two existing technologies mainly adopted in the present technical solution, namely, near infrared auto fluorescence (NIRAF) imaging technology and laser speckle contrast technology (LSCI) need to be clarified, wherein the near infrared auto fluorescence (NIRAF) imaging technology is that after a parathyroid gland is excited by near infrared light, the near infrared auto fluorescence (NIRAF) imaging technology emits a stronger NIRAF signal, and the NIRAF is detected by an imaging system, and the parathyroid gland displays a gray image in the imaging system, so that the parathyroid gland is identified.
The laser speckle contrast technology (LSCI) irradiates a measured object with a laser with a certain wavelength, and the laser speckle of different motion states in the measured object is different due to the interference characteristic of the laser, so that the motion state of the measured object can be obtained according to the probability statistics of the speckle. LSCI is sensitive to microvascular blood flow, can perform real-time full-field imaging with high space-time resolution on living organism microcirculation blood flow, has the advantages of non-contact, non-invasive, quick imaging, large imaging area, high resolution and the like, and is widely applied to biomedical imaging research and clinical diagnosis. This technique produces bright and dark spots of constructive and destructive interference, respectively, called speckle patterns, by analyzing interference patterns produced when coherent light is incident on a surface, with small differences in path length produced by scattering of light waves from different areas. Such fluctuations in the speckle pattern depend on the speed at which the particles move within a few hundred microns of the surface, and blurring of the speckle pattern can occur when the motion is fast relative to the integration time of the detector. Analysis of this spatial blur provides a contrast between areas of faster and slower motion and forms the basis of the LSCI. This technique is sensitive to microvascular perfusion and has been applied to various tissues where blood vessels of interest, such as the retina, skin and brain, are typically located at the surface. Parathyroid gland is dense in blood vessel, and parathyroid gland secretes parathyroid hormone to whole body. In addition, their small size (3-8 mm) makes many blood vessels shallow, making these glands suitable target organs for evaluation using LSCI.
Referring to fig. 1, there is shown a parathyroid function imaging system in accordance with an embodiment of the first aspect of the present utility model, comprising:
a light source assembly 100, the light source assembly 100 including a white light source 110 and a laser source 120; wherein, the white light source 110 preferably adopts a high-power four-color LED visible light source, the laser source 120 preferably adopts a 785nm Laser Diode (LD), and a control switch can be independently arranged or controlled by a processor in a combined way;
a light wave transmission assembly 200 integrated in the endoscope and used for transmitting light waves output by the white light source 110 and the laser source 120 to irradiate the parathyroid gland 10 in the human body and transmitting light waves reflected after the parathyroid gland 10 is irradiated; the flexible cable structure is adopted, so that the flexible cable structure can conveniently extend into the human body and is connected with instruments and equipment outside the human body;
an optical imaging assembly 300, configured to generate a color image, a near infrared fluorescence image, and a laser speckle image of the parathyroid gland 10 from the light waves reflected after the parathyroid gland 10 is irradiated, and mainly composed of a plurality of optical devices;
an image acquisition component 400 for acquiring color images, near infrared fluorescence images, and laser speckle images of the parathyroid gland 10;
the processor 500 is respectively connected with the optical imaging assembly 300 and the image acquisition assembly 400, and is used for controlling the operation of the optical imaging assembly 300 and processing the image data acquired by the image acquisition assembly 400, and is installed in a computer, so that instruction input, external control and internal data processing are mainly realized.
The main working process of the present utility model is that an endoscope including the present system is placed near the tissue of the parathyroid gland 10 in the operation, a light source assembly is started, a white light source 110 and a laser source 120 output visible light and laser light respectively, the visible light and the laser light are coupled out through a light wave transmission assembly 200 and irradiated near the tissue of the parathyroid gland 10 from an endoscope probe, the parathyroid gland 10 reflects the coupled light waves of the visible light, near infrared self fluorescence (NIRAF) and the laser light and enters an image acquisition channel of the light wave transmission assembly 200 from the endoscope probe, an optical imaging assembly 300 can respectively generate a color image, a near infrared fluorescence image and a laser speckle image of the parathyroid gland 10, and a processor 500 controls the image acquisition assembly 400 to respectively acquire the color image, the near infrared fluorescence image and the laser speckle image of the parathyroid gland 10, and an image of the fusion of the near infrared fluorescence image and the color image and an image of the fusion of the laser speckle image of the parathyroid gland 10 can be formed on a display 600.
As described above, the utility model obtains clear color images of the background of the surgical field by applying the white light imaging technology in the endoscope, and then uses the near infrared fluorescence technology to position the parathyroid gland 10, so as to solve the problem of identifying the parathyroid gland 10 in the thyroid surgery, and the laser speckle technology displays speckle contrast images of the parathyroid gland, so as to know whether the blood circulation is lost or not and whether transplantation is needed, so as to guide the judgment of the function of the parathyroid gland 10 in the thyroid surgery, and reduce the occurrence of the hypofunction of the parathyroid gland 10 after the surgery. Compared with the existing other methods, the method can objectively reflect the function of the parathyroid gland 10, does not need to additionally inject exogenous contrast agent, and is simple and practical.
In some embodiments of the first aspect of the present utility model, the optical imaging assembly 300 includes:
a first beam splitter 310 for splitting the light reflected by the parathyroid gland 10 into a first coupled light wave and a second coupled light wave, preferably using a dichroic beam splitter DBS having a splitting ratio of 50/50;
a color imaging unit 320 for receiving the first coupled light waves and separating visible light waves therefrom to generate a color image of the parathyroid gland 10;
a second optical splitter 330, configured to receive the second coupled optical wave and provide a change-over switch 331 for switching an output path of the second coupled optical wave, where the output path includes a first path and a second path, and the change-over switch 331 is connected to the processor 500; the second beam splitter 330 can adopt a rotating prism to realize different output paths of the laser light waves, and the change-over switch 331 controls the rotation angle of the rotating prism. The second beam splitter 330 may also directly adopt a one-to-two optical splitter, and then cooperate with an optical amplifier to realize two output paths, and then the processor 500 controls the image acquisition assembly 400 to not acquire near infrared fluorescent images and laser speckles at the same time; the second beam splitter 330 may also employ a dichroic beam splitter DBS having a splitting ratio of 50/50.
A near infrared fluorescence imaging unit 340 for receiving the second coupled light waves of the first path and separating near infrared fluorescence light waves therefrom to generate a near infrared fluorescence image of the parathyroid gland 10;
a laser speckle imaging unit 350 for receiving the second coupled light wave of the second path and separating the laser light wave therefrom to generate a laser speckle image of the parathyroid gland 10.
In some embodiments of the first aspect of the present utility model, the image acquisition assembly 400 includes an RGB camera 410 for acquiring the color image, a first fluorescent camera 420 for acquiring the near infrared fluorescent image, and a second fluorescent camera 430 for acquiring the laser speckle. The RGB camera 410 may be replaced by other known color image sensors, and the first fluorescent camera 420 is preferably but not limited to a digital camera with the same area size as the second fluorescent camera 430, so as to achieve direct fusion of the color structural image and the blood flow functional image, and no image cropping and scaling operations are needed. Video cameras/CCD cameras, etc. may also be selected. The second fluorescent camera 430 is preferably but not limited to an area array CCD camera with 8 bits of analog-to-digital conversion to collect laser speckle images formed by the reflection of laser light from the parathyroid gland 10, and an area array digital CCD camera/camera with an analog-to-digital conversion of not less than 12 bits, or an area array digital CMOS camera/camera, may be selected.
Specifically, in some embodiments of the first aspect of the present utility model, the color imaging unit 320 includes a 400-700nm band-pass filter 321 and a color photo-imaging device 322, which are sequentially disposed between the first beam splitter 310 and the RGB camera 410, wherein the 400-700nm band-pass filter 321 only allows visible light to pass through and limits laser light and near infrared fluorescence to pass through, and the color photo-imaging device 322 may be composed of an optical lens that improves resolution and relative illuminance and reduces distortion.
Further, in some embodiments of the first aspect of the present utility model, the near infrared fluorescence imaging unit 340 includes a 785nm laser filter 341, a first bandpass filter 342, and a first condensing lens 343 sequentially disposed in the first path. Wherein the 785nm laser filter 341 is used to filter the 785nm excitation light and allow near infrared fluorescence to pass, the first bandpass filter 342 is a 808nm bandpass filter and allows only 1/100 of visible light and almost all infrared light longer than 808nm to pass, so that the relative position information of the parathyroid gland 10 can be given while highlighting the fluorescence image of the parathyroid gland 10, and the first condensing lens 343 is a 85mm lens focused to the first fluorescent camera 420.
Further, in some embodiments of the first aspect of the present utility model, the laser speckle imaging unit 350 includes a second bandpass filter 351, a neutral density filter 352, and a second condenser lens 353 sequentially disposed in the second path. Among them, the second bandpass filter 351 is preferably but not limited to a narrowband filter having a center wavelength of 785nm for filtering out a spectrum other than the center wavelength of laser light only by laser light. The neutral density filter 352 is used to reduce the laser intensity so that it does not saturate the second fluorescent camera 430. In one embodiment, the neutral density filter is a 1.3o.d. neutral density filter. Alternatively, if the laser power is insufficient, it may not be needed, or a lower optical density, e.g., 0.5o.d., may be used. The second condenser lens 353 focuses to the second fluorescent camera 430 using an 85mm lens.
In addition, as shown in fig. 2 and 3, in some embodiments of the first aspect of the present utility model, the light wave transmission assembly 200 includes a single mode fiber 210, a multimode fiber 220 and an image transmission fiber 230 integrated in an endoscope, the image transmission fiber 230 is located at a central position, the single mode fiber 210 and the multimode fiber 220 are located outside the image transmission fiber 230, the single mode fiber 210 is used for transmitting the light wave output by the laser source 120, the multimode fiber 220 is used for transmitting the light wave output by the white light source 110, the image transmission fiber 230 is used for transmitting the light wave reflected after the parathyroid gland 10 is irradiated, the front ends of the single mode fiber 210, the multimode fiber 220 and the image transmission fiber 230 are provided with an endoscope probe 240, a first linear polarizer 250 covering the top ends of the single mode fiber 210 and the multimode fiber 220 is disposed in the endoscope probe 240, and a second linear polarizer 354 is disposed between the second beam splitter 330 and the second band pass filter 351. The first linear polarizer 250 cooperates with the second linear polarizer 354 to form a crossed polarizer assembly that effectively reduces specular reflection from tissue, thereby producing a smoother image.
In some embodiments of the first aspect of the present utility model, the front end of the first beam splitter 310 is provided with an acromatic lens 360 and a tunable lens 370, the acromatic lens 360 being capable of eliminating chromatic aberration between different colors of light, the tunable lens 370 being used to achieve remote image focusing to help ensure the concentration of images obtained during surgery.
Further, in some embodiments of the first aspect of the present utility model, the optical imaging assembly 300 further includes a converging lens 380 disposed between the first beam splitter 310 and the second beam splitter 330, and the converging lens 380 may collect scattered light waves due to scattering of the light waves impinging on the tissue.
Referring to fig. 4, an endoscope according to a second aspect of the present utility model includes a main case 700, a display 600, a perspective tube 800, and the parathyroid endoscope imaging system, where the light source assembly 100, the optical imaging assembly 300, the image acquisition assembly 400, and the processor 500 are all disposed in the main case, the processor 500 is connected to the display 600, the display 600 is used for displaying a color image of the parathyroid gland 10, an image obtained by fusing a near infrared fluorescent image with the color image, and an image obtained by fusing a laser speckle image with the color image, the optical wave transmission assembly 200 is integrated in the perspective tube 800, and one end of the perspective tube 800 is connected to the main case 700, and the other end is connected to an endoscope probe.
The utility model obtains clear color images of the surgical visual field background by applying a white light imaging technology in an endoscope, and then utilizes a near infrared fluorescence technology to position the parathyroid gland 10, so that the difficult problem of identifying the parathyroid gland 10 in thyroid surgery can be solved, and the laser speckle technology displays speckle contrast images of the parathyroid gland, so as to know whether the blood circulation of the parathyroid gland is lost or not and whether the parathyroid gland needs to be transplanted, so as to guide the judgment of the function of the parathyroid gland 10 in thyroid surgery and reduce the occurrence of hypofunction of the parathyroid gland 10 after the operation. Compared with the existing other methods, the method can objectively reflect the function of the parathyroid gland 10, does not need to additionally inject exogenous contrast agent, and is simple and practical.
In the description of the present specification, reference to the terms "one embodiment," "some embodiments," "illustrative embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the utility model. In this specification, schematic representations of the above terms do not necessarily refer to the same embodiments or examples. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.
While embodiments of the present utility model have been shown and described, it will be understood by those of ordinary skill in the art that: many changes, modifications, substitutions and variations may be made to the embodiments without departing from the spirit and principles of the utility model, the scope of which is defined by the claims and their equivalents.
Claims (10)
1. A parathyroid function imaging system, characterized by: comprising
The light source assembly comprises a white light source and a laser source;
the light wave transmission component is integrated in the endoscope and is used for transmitting light waves output by the white light source and the laser source to irradiate parathyroid glands in a human body and transmitting light waves reflected after the parathyroid glands are irradiated;
an optical imaging assembly for generating a color image, a near infrared fluorescence image and a laser speckle image of the parathyroid gland from the light waves reflected after the parathyroid gland is irradiated;
the image acquisition component is used for acquiring a color image, a near infrared fluorescence image and a laser speckle image of the parathyroid gland;
and the processor is respectively connected with the optical imaging assembly and the image acquisition assembly and is used for controlling the operation of the optical imaging assembly and processing the image data acquired by the image acquisition assembly.
2. A parathyroid function imaging system in accordance with claim 1, wherein: the optical imaging assembly comprises
A first optical splitter for splitting the light reflected by the parathyroid gland into a first coupled light wave and a second coupled light wave;
a color imaging unit for receiving the first coupled light waves and separating visible light waves therefrom to generate a color image of the parathyroid gland;
the second light splitter is used for receiving the second coupled light waves and is provided with a change-over switch for switching an output path of the second coupled light waves, the output path comprises a first path and a second path, and the change-over switch is connected with the processor;
a near infrared fluorescence imaging unit for receiving the second coupled light waves of the first path and separating near infrared fluorescence light waves therefrom to generate a near infrared fluorescence image of the parathyroid gland;
and the laser speckle imaging unit is used for receiving the second coupling light wave of the second path and separating the laser light wave from the second coupling light wave to generate a laser speckle image of the parathyroid gland.
3. A parathyroid function imaging system in accordance with claim 2, wherein: the image acquisition component comprises an RGB camera used for acquiring the color image, a first fluorescent camera used for acquiring the near infrared fluorescent image and a second fluorescent camera used for acquiring the laser speckle.
4. A parathyroid function imaging system in accordance with claim 3, wherein: the color imaging unit comprises a 400-700nm band-pass filter and a color photoelectric imaging device which are sequentially arranged between the first beam splitter and the RGB camera.
5. A parathyroid function imaging system in accordance with claim 2, wherein: the near infrared fluorescence imaging unit comprises a 785nm laser filter, a first band-pass filter and a first condensing lens which are sequentially arranged in the first path.
6. A parathyroid function imaging system in accordance with claim 2, wherein: the laser speckle imaging unit comprises a second band-pass filter, a neutral density filter and a second condensing lens which are sequentially arranged in the second path.
7. A parathyroid function imaging system in accordance with claim 6, wherein: the optical wave transmission assembly comprises a single mode optical fiber, a multimode optical fiber and an image transmission optical fiber which are integrated in an endoscope, wherein the single mode optical fiber is used for transmitting optical waves output by the laser source, the multimode optical fiber is used for transmitting optical waves output by the white light source, the image transmission optical fiber is used for transmitting optical waves reflected by parathyroid glands after being irradiated, the front ends of the single mode optical fiber, the multimode optical fiber and the image transmission optical fiber are provided with an endoscope probe, a first linear polarizer which covers the top ends of the single mode optical fiber and the multimode optical fiber is arranged in the endoscope probe, and a second linear polarizer is arranged between the second optical splitter and the second bandpass filter.
8. A parathyroid function imaging system in accordance with claim 2, wherein: the front end of the first beam splitter is provided with an achromatic lens and a tunable lens.
9. A parathyroid function imaging system in accordance with claim 2, wherein: the optical imaging assembly further includes a converging lens disposed between the first and second optical splitters.
10. An endoscope, characterized in that: the system comprises a main case, a display, a perspective tube and the parathyroid endoscope imaging system according to any one of claims 1 to 9, wherein the light source assembly, the optical imaging assembly, the image acquisition assembly and the processor are all arranged in the main case, the processor is connected with the display, the display is used for displaying the color image of the parathyroid gland, the image fused by the near infrared fluorescent image and the color image and the image fused by the laser speckle image and the color image, the light wave transmission assembly is integrated in the perspective tube, and one end of the perspective tube is connected with the main case, and the other end of the perspective tube is connected with the endoscope probe.
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