CN110448266B - Random laser confocal line scanning three-dimensional ophthalmoscope and imaging method - Google Patents
Random laser confocal line scanning three-dimensional ophthalmoscope and imaging method Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/0008—Apparatus for testing the eyes; Instruments for examining the eyes provided with illuminating means
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/1025—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for confocal scanning
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/14—Arrangements specially adapted for eye photography
Abstract
The invention discloses a random laser confocal line scanning three-dimensional ophthalmoscope and an imaging method. The random laser confocal line scanning three-dimensional ophthalmoscope comprises a random laser source, a shaping optical unit, a light splitting unit, a one-dimensional scanning unit, an imaging optical unit, a refractive index matching unit, an optical delay line unit, a collimating optical unit, a dispersive optical unit, a focusing optical unit and a two-dimensional photoelectric detection unit; the random laser source outputs divergent laser which comprises two orthogonal lasers in the electromagnetic wave oscillation direction, and the two orthogonal lasers in the electromagnetic wave oscillation direction are converted into light with collimation and convergence transmission characteristics after passing through the shaping optical unit. The random laser confocal line scanning three-dimensional ophthalmoscope provided by the invention adopts the randomly distributed feedback fiber laser as a light source, so that speckles of imaging are effectively reduced, and images are clear.
Description
Technical Field
The invention particularly relates to a random laser confocal line scanning three-dimensional ophthalmoscope and an imaging method, belonging to the technical field of laser imaging.
Background
Fundus examination is important and the pathological features of many ophthalmic diseases such as glaucoma, diabetic retinopathy appear first on the fundus retina and choroid. Meanwhile, many diseases such as hypertension and diabetes mellitus have eyeground pathological changes, so that the eyeground retina reflects the change of blood vessels of other organs of a human body to a certain extent. The confocal laser ophthalmoscope can be used for detecting pathological features of macular regions, optic papillae and other regions of the retina of the eye fundus of a patient, and therefore, the confocal laser ophthalmoscope is widely applied to ophthalmology. In addition, confocal laser ophthalmoscopes also play an important role in fundus fluorography, and compared with fundus camera-based fluorography, laser scanning can achieve better spatial resolution and vascular contrast.
At present, the mainstream confocal laser ophthalmoscope adopts a point scanning mode, and under the condition, in order to obtain fundus confocal images with a real-time refresh rate (more than 20 kHz), a resonance type galvanometer needs to be adopted to carry out fast axis scanning, so that the price is high, and the manufacturing cost of an imaging system is greatly increased. In addition, the huge noise of the resonance vibrating mirror during working brings very bad experience to patients and doctors operating instruments.
This problem can be avoided by using line scanning, but the line scanning does not satisfy the confocal condition in one dimension, so the imaging quality is reduced compared with the point scanning. It is generally believed that the imaging quality of the line scan can be improved by optimizing the imaging laser source, and the presently used amplified spontaneous emission laser diodes (or "super-fluorescent diodes") are expensive and do not appear to be the optimal choice for large-scale medical applications such as ophthalmoscopes. Redding et al published a paper in the Nature Photonics journal in 2012 (sixth volume, page 355-359) demonstrated that random laser sources can achieve better imaging than other light sources including superfluorescent diodes. However, this technique has not been applied to biomedical imaging, particularly ophthalmic imaging, to date.
Further, the confocal laser ophthalmoscope is a two-dimensional imaging mode, and thus it is difficult to obtain information in the depth direction of the fundus. At present, multispectral laser imaging is adopted for solving the problem, the choroid information is obtained through different penetration depths of lasers with different wavelengths, however, the information of an upper layer structure cannot be completely eliminated in the process, and the overlapping and mixing of the two brings difficulty to analysis and application.
Disclosure of Invention
The invention mainly aims to provide a random laser confocal line scanning three-dimensional ophthalmoscope and an imaging method, so as to overcome the defects in the prior art.
In order to achieve the purpose, the technical scheme adopted by the invention comprises the following steps:
the embodiment of the invention provides a random laser confocal line scanning three-dimensional ophthalmoscope, which is characterized by comprising a random laser source, a shaping optical unit, a light splitting unit, a one-dimensional scanning unit, an imaging optical unit, a refractive index matching unit, an optical delay line unit, a collimating optical unit, a dispersive optical unit, a focusing optical unit and a two-dimensional photoelectric detection unit;
the random laser source outputs divergent laser which comprises two orthogonal lasers in the electromagnetic wave oscillation direction, and the two orthogonal lasers in the electromagnetic wave oscillation direction are converted into light with collimation and convergence transmission characteristics after passing through the shaping optical unit;
a part of light output by the shaping optical unit passes through the light splitting unit in a transmission mode and then reaches the one-dimensional scanning unit, wherein the light with the collimation transmission characteristic expands in the direction, the light with the convergence transmission characteristic is converged and reflected on the one-dimensional scanning unit and then is in a divergent state, the light output by the one-dimensional scanning unit is converged and enters human eyes after passing through the imaging optical unit, and a linear laser form with one-dimensional focusing and the other-dimensional divergence is formed on the retina of the eye fundus;
the other part of light output by the shaping optical unit is reflected by the light splitting unit, then turns back after sequentially passing through the refractive index matching unit and the optical delay line unit and is converged with the returned human eye detection light, and reaches the dispersion optical unit through the collimating optical unit and then reaches the two-dimensional photoelectric detection unit through the focusing optical unit.
In some more specific embodiments, the random laser source includes a random laser including, but not limited to, any one of a powder material random laser and a fiber random laser.
Preferably, the random laser source provides a beam wavelength of 400-1100 nm.
In some more specific embodiments, the random laser includes two or more semiconductor lasers, each semiconductor laser is connected to an optical fiber through a beam combiner, and the input end of at least one beam combiner is further connected to at least one optical fiber ring.
Preferably, the optical fiber is a single-mode double-clad passive optical fiber.
In some more specific embodiments, the shaping optical unit comprises a shaping optical element.
In some more specific embodiments, the light splitting unit includes a light splitting element.
Preferably, the light splitting element includes any one of a light splitting prism and a light splitting plane sheet, but is not limited thereto.
In some more specific embodiments, the one-dimensional scanning unit comprises a one-dimensional scanning element.
Preferably, the one-dimensional scanning element includes any one of a scanning galvanometer, a micro-electromechanical system mirror, and a digital micro-mirror, but is not limited thereto.
Preferably, the scanning speed of the one-dimensional scanning element is greater than 10 Hz.
In some more specific embodiments, the imaging optics include imaging optics that include a lens that focuses light output by the one-dimensional scanning unit through the pupil, linearly to a retinal location, and that is capable of adjusting the focal length according to the pupil power.
In some more specific embodiments, the index matching unit includes an index matching element.
In some more specific embodiments, the index matching element comprises a transparent optical element having an index of refraction greater than 1.
In some more specific embodiments, the optical delay line unit includes any one of a reflective type and a transmissive type optical delay line, but is not limited thereto.
In some more specific embodiments, the collimating optical unit comprises a collimating optical element comprising a collimating lens.
In some more specific embodiments, the dispersive optical unit comprises a dispersive optical element.
In some more specific embodiments, the dispersive optical element includes any one of a transmissive dispersive optical element and a reflective dispersive optical element, but is not limited thereto.
In some more specific embodiments, the dispersive optical element includes any one of a prism and a grating, but is not limited thereto.
In some more specific embodiments, the focusing optical unit comprises a focusing optical element comprising a focusing lens.
In some specific embodiments, the two-dimensional photodetecting unit includes a two-dimensional photodetecting element, and the two-dimensional photodetecting element includes any one of a CCD sensor, a CMOS sensor, and a two-dimensional array of photosensors, but is not limited thereto.
In some more specific embodiments, the distance that the light ray reaches the fundus retina from the beam splitting unit and returns is equal to the distance that the light ray reflected by the beam splitting unit reaches the optical delay line unit and returns.
The embodiment of the invention provides an imaging method based on a random laser confocal line scanning three-dimensional ophthalmoscope, which comprises the following steps:
outputting divergent laser including two orthogonal laser in the oscillation direction of electromagnetic wave by a random laser source;
converting the laser light in the two orthogonal electromagnetic wave oscillation directions into light with collimation and convergence transmission characteristics by using a shaping optical unit;
part of light output by the shaping optical unit passes through the light splitting unit in a transmission mode and then reaches the one-dimensional scanning unit, wherein the light with the collimation transmission characteristic expands in the direction (namely the light transmission direction), the light with the convergence transmission characteristic is converged and reflected on the one-dimensional scanning unit and then is in a divergence state, the light output by the one-dimensional scanning unit is converged after passing through the imaging optical unit and enters human eyes, and a linear laser form with one-dimensional focusing and another-dimensional divergence is formed on the retina of the eye fundus, so that the surface scanning is realized;
and the other part of light output by the shaping optical unit is reflected by the light splitting unit, then returns after sequentially passing through the refractive index matching unit and the optical delay line unit and is converged with the returned human eye detection light, and reaches the dispersion optical unit through the collimating optical unit and then reaches the two-dimensional photoelectric detection unit through the focusing optical unit, so that a three-dimensional eye detection result is obtained.
Compared with the prior art, the invention has the advantages that:
1) the random laser device is used as the light source of the random laser based three-dimensional ophthalmoscope based on random laser common focusing line scanning, so that speckles of imaging are effectively reduced, and images are clearer;
2) the random laser confocal line scanning-based three-dimensional ophthalmoscope provided by the embodiment of the invention adopts a line scanning mode, and has higher speed compared with the traditional point scanning confocal laser ophthalmoscope, so that the acquisition time can be greatly reduced, and the image defect caused by the eye movement of an acquired person can be avoided;
3) compared with various existing laser ophthalmoscopes, the three-dimensional ophthalmoscope based on random laser confocal line scanning provided by the embodiment of the invention is added with an interference imaging design, and the eyeground information in the depth direction can be additionally obtained, so that more convenience is brought to diagnosis and treatment of ophthalmic diseases.
Drawings
FIG. 1 is a schematic diagram of a three-dimensional ophthalmoscope based on random confocal laser scanning according to an exemplary embodiment of the present invention;
FIG. 2 is a schematic diagram of a three-dimensional ophthalmoscope based on confocal random laser scanning according to another exemplary embodiment of the present invention;
fig. 3 is a comparison graph of pixel point light intensity probability densities of a random confocal laser scanning three-dimensional ophthalmoscope and a conventional amplified spontaneous emission laser light source according to an embodiment of the present invention.
Detailed Description
In view of the deficiencies in the prior art, the inventors of the present invention have made extensive studies and extensive practices to provide technical solutions of the present invention. The technical solution, its implementation and principles, etc. will be further explained as follows.
Referring to fig. 1, a random confocal line scanning three-dimensional ophthalmoscope according to some exemplary embodiments of the present invention may include a random laser source 101, a shaping optical unit 102, a beam splitting unit 103, a one-dimensional scanning unit 104, an imaging optical unit 105, a collimating optical unit 107, a dispersive optical unit 108, a focusing optical unit 109, a two-dimensional photodetection unit 110, a refractive index matching unit 111, and an optical delay line unit 112.
Wherein, the random laser source 101 outputs a divergent laser beam, and the divergent laser beam passes through the shaping optical unit 102, so that the laser beams in two orthogonal electromagnetic wave oscillation directions have different transmission characteristics: one-dimensional collimation and one-dimensional convergence; wherein, part of the laser beam emitted by the shaping optical element passes through the light splitting unit 103 in a transmission manner and reaches the one-dimensional scanning unit (which may be a scanning galvanometer) 104; wherein, the collimated laser beam reaches the one-dimensional scanning unit 104 in a collimated manner and expands in the direction (i.e. the propagation direction of light), and the converged laser beam is converged and reflected on the one-dimensional scanning unit 104 and then is in a divergent state; the two are converged through the pupil of a human eye 106 after passing through an imaging optical unit 105, a one-dimensional focusing and one-dimensional diverging linear laser form is formed on the retina of the eye fundus, and meanwhile, surface scanning is realized under the action of a one-dimensional scanning unit 104; the light splitting unit 103 reflects another part of the laser beam, and the reflected laser beam sequentially passes through a refractive index matching unit (i.e., a dispersion compensation unit, which mainly eliminates or weakens dispersion difference between light returned from human eyes (i.e., imaging light or detection light of human eyes) and reference light (i.e., light reflected by a reflection unit)) 111 and an optical delay line unit 112, and then is turned back and converged to reach a dispersion optical unit 108 through a collimating optical unit 107, and the dispersion optical unit (i.e., the dispersion optical unit is used for allowing a detector to detect light with different wavelengths) 108 spatially separates random laser beams with different wavelengths and reaches a two-dimensional photoelectric detection unit 110 through a focusing optical unit 109, so that fundus information in the depth direction can be recorded. Meanwhile, another one-dimensional imaging light beam (i.e., the human eye detection light returned by the human eye) arrives at different positions of the two-dimensional photodetection unit 110 corresponding to different positions of the laser detection line on the retina, and the imaging light beams at different times correspond to the laser lines at different scanning positions, so that transverse two-dimensional fundus information can be recorded.
In a more specific embodiment, referring to fig. 2, a random confocal line-scan three-dimensional ophthalmoscope can employ a random feedback fiber laser 101 as a random laser source, which is configured to: the laser comprises two-way pumped semiconductor lasers 201 and 202 which are coupled into a main optical path through beam combiners 203 and 204, a single-mode double-cladding passive optical fiber 206 which is used for providing Raman gain and Rayleigh scattering feedback required by random laser generation, and an optical fiber loop 205 which is similar to a high-reflection mirror in the laser and aims to enable the random laser to be output in a single direction; compared with other solutions of random laser sources, the optical fiber-based mode can obtain better beam quality, the full optical fiber structure is beneficial to integration and working under various environments, and in addition, the cost can be reduced, so that the random laser source is more optimized.
The laser output by the random fiber laser is divided into two paths by the fiber coupler 219, one path (defined as a "first path") enters human eyes, and the other path is defined as a "second path" and is transmitted in the optical fiber and the air at equal intervals with the path entering the human eyes, and is used as the reference light of three-dimensional interference imaging; the first path is firstly output to the air by the optical fiber end cap 207 before entering the human eye, then collimated and output by the convex lens 208, and then passes through the cylindrical lens 209 to obtain the line laser, a beam splitting cube 210 is adopted as a light splitting element, the one-dimensional scanning of the line laser is realized by the laser scanning galvanometer 211, then enters the human eye 214 through the scanning lens 212 and the ocular lens 213, and the laser backscattered from the human eye to the light path returns to the beam splitting cube and then is reflected to the imaging light path; on the other hand, the reference light is output as spatial light by the optical fiber end cap 221 through the optical fiber retarder 220, then is converged and interfered with the returned human eye detection light by the spectroscope 222, after passing through the lens 215, the wavelengths of the laser are spatially separated by the diffraction grating 216, the lens group 217 further focuses the laser on the CCD camera 218, and then the three-dimensional eye examination result can be obtained through data processing methods such as numerical dispersion compensation, fast fourier transform and the like.
As shown in fig. 3, the probability density of the imaging spot light intensity of the illumination with the random laser source compared to the conventional amplified spontaneous emission laser source can be seen to obtain smaller point spread function and lower noise with the random laser source, so that the quality of the acquired ophthalmic image can be significantly improved.
It should be noted that the imaging optical element in the present invention is composed of various lenses, and should realize the functions of converging the detection light through the pupil, focusing the detection light on the retina in a linear manner, and adjusting the focal length according to the diopter of the observed person; the refractive index matching element, namely a dispersion compensation element, mainly comprises a transparent material with the refractive index larger than 1 (in air); the optical delay line can be of a reflection type or a transmission type, if the optical delay line is of the transmission type, an additional element needs to be added in the system to enable the optical delay line to be converged with the fundus detection return light, and meanwhile, the equidistant condition is ensured to be unchanged; the dispersive optical element may be any such element, such as a prism, a grating, etc.; the dispersive optical element can be a transmission type or a reflection type, and if the dispersive optical element is the reflection type, the two-dimensional photoelectric detector and the focusing optical element in front of the two-dimensional photoelectric detector need to adjust the position according to the emergent direction of the dispersive optical element; the focusing optical element is composed of multiple lenses and is used for eliminating various optical distortions such as spherical aberration, chromatic aberration and the like while focusing; the two-dimensional photodetector may take many forms, such as a CCD or CMOS sensor, a two-dimensional array of photosensors, and the like.
It should be noted that, for various optical elements used in the embodiments of the present invention, such as a shaping optical element, a beam splitting element, a one-dimensional scanning element, an imaging optical element, a collimating optical element, a dispersing optical element, a focusing optical element, a two-dimensional photodetection element, a refractive index matching element, an optical delay line element, and the like, elements made of materials known to those skilled in the art may be used, and parameters thereof may be adjusted according to actual conditions, and they are all commercially available.
The random laser device is used as the light source of the random laser based three-dimensional ophthalmoscope based on random laser common focusing line scanning, so that speckles of imaging are effectively reduced, and images are clearer; the three-dimensional ophthalmoscope based on the random laser confocal line scanning adopts a line scanning mode, and has higher speed compared with the traditional point scanning confocal laser ophthalmoscope, so that the acquisition time can be greatly reduced, and the image defect caused by the eye movement of an acquired person can be avoided; therefore, compared with various existing laser ophthalmoscopes, the three-dimensional ophthalmoscope based on random laser confocal line scanning provided by the embodiment of the invention is added with an interference imaging design, and more convenience is brought to diagnosis and treatment of ophthalmic diseases because fundus information in the depth direction can be additionally obtained.
It should be understood that the above-mentioned embodiments are merely illustrative of the technical concepts and features of the present invention, which are intended to enable those skilled in the art to understand the contents of the present invention and implement the present invention, and therefore, the protection scope of the present invention is not limited thereby. All equivalent changes and modifications made according to the spirit of the present invention should be covered within the protection scope of the present invention.
Claims (21)
1. A random laser confocal line scanning three-dimensional ophthalmoscope is characterized by comprising a random laser source, a shaping optical unit, a light splitting unit, a one-dimensional scanning unit, an imaging optical unit, a refractive index matching unit, an optical delay line unit, a collimating optical unit, a dispersive optical unit, a focusing optical unit and a two-dimensional photoelectric detection unit;
the random laser source comprises a random laser, the random laser comprises more than two semiconductor lasers, each semiconductor laser is connected with an optical fiber through a beam combiner, and the input end of at least one beam combiner is also connected with at least one optical fiber ring; the random laser source outputs divergent laser which comprises two orthogonal lasers in the electromagnetic wave oscillation direction, and the two orthogonal lasers in the electromagnetic wave oscillation direction are respectively converted into light with collimation and convergence transmission characteristics after passing through the shaping optical unit;
a part of light output by the shaping optical unit passes through the light splitting unit in a transmission mode and then reaches the one-dimensional scanning unit, wherein the light with the collimation transmission characteristic expands in the direction, the light with the convergence transmission characteristic is converged and reflected on the one-dimensional scanning unit and then is in a divergent state, the light output by the one-dimensional scanning unit is converged and enters human eyes after passing through the imaging optical unit, and a linear laser form with one-dimensional focusing and the other-dimensional divergence is formed on the retina of the eye fundus;
the other part of light output by the shaping optical unit is reflected by the light splitting unit, then returns after sequentially passing through the refractive index matching unit and the optical delay line unit and is converged with the returned human eye detection light, and reaches the dispersion optical unit through the collimating optical unit and then reaches the two-dimensional photoelectric detection unit through the focusing optical unit, wherein the distance between the returned light and the fundus retina after reaching the light splitting unit is equal to the distance between the returned light and the optical delay line unit after being reflected by the light splitting unit.
2. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the random laser comprises any one of a powder material random laser and a fiber random laser.
3. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the random laser source provides a light beam with a wavelength of 400-1100 nm.
4. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 2, wherein: the optical fiber is a single-mode double-cladding passive optical fiber.
5. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the shaping optical unit includes a shaping optical element.
6. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 5, wherein: the light splitting unit includes a light splitting element.
7. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 6, wherein: the light splitting element comprises any one of a light splitting prism and a light splitting flat sheet.
8. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the one-dimensional scanning unit includes a one-dimensional scanning element.
9. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 8, wherein: the one-dimensional scanning element comprises any one of a scanning galvanometer, a micro-electromechanical system reflecting mirror and a digital micro-mirror.
10. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 8, wherein: the scanning speed of the one-dimensional scanning element is more than 10 Hz.
11. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the imaging optical unit comprises an imaging optical element which comprises a lens which enables the light output by the one-dimensional scanning unit to be converged through a pupil, linearly focused on a retina position and capable of adjusting a focal length according to the diopter of the pupil.
12. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the index matching unit includes an index matching element.
13. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 12, wherein: the index matching element comprises a transparent optical element having an index of refraction greater than 1.
14. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the optical delay line unit includes any one of a reflective type and a transmissive type optical delay line.
15. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the collimating optical unit includes a collimating optical element including a collimating lens.
16. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the dispersive optical unit comprises a dispersive optical element.
17. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 16, wherein: the dispersive optical element includes any one of a transmissive dispersive optical element and a reflective dispersive optical element.
18. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 16, wherein: the dispersive optical element includes any one of a prism and a grating.
19. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the focusing optical unit includes a focusing optical element including a focusing lens.
20. The random confocal laser line scanning three-dimensional ophthalmoscope of claim 1, wherein: the two-dimensional photoelectric detection unit comprises a two-dimensional photoelectric detection element, and the two-dimensional photoelectric detection element comprises any one of a CCD sensor, a CMOS sensor and a two-dimensional array of photoelectric sensors.
21. An imaging method based on a random laser confocal line scanning three-dimensional ophthalmoscope is characterized by comprising the following steps:
providing a random confocal laser scanning three-dimensional ophthalmoscope according to any one of claims 1 to 20;
outputting divergent laser including two orthogonal laser in the oscillation direction of electromagnetic wave by a random laser source;
converting the laser light in the two orthogonal electromagnetic wave oscillation directions into light with collimation and convergence transmission characteristics by using a shaping optical unit;
part of light output by the shaping optical unit passes through the light splitting unit in a transmission mode and then reaches the one-dimensional scanning unit, wherein the light with the collimation transmission characteristic expands in the direction, the light with the convergence transmission characteristic is converged and reflected on the one-dimensional scanning unit and then is in a divergent state, the light output by the one-dimensional scanning unit is converged after passing through the imaging optical unit and enters human eyes, and a linear laser form with one-dimensional focusing and the other-dimensional divergence is formed on the retina of the eye fundus, so that the surface scanning is realized;
and the other part of light output by the shaping optical unit is reflected by the light splitting unit, then returns after sequentially passing through the refractive index matching unit and the optical delay line unit and is converged with the returned human eye detection light, and reaches the dispersion optical unit through the collimating optical unit and then reaches the two-dimensional photoelectric detection unit through the focusing optical unit, so that a three-dimensional eye detection result is obtained.
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