CN117357057A

CN117357057A - Myopia detection system and detection method

Info

Publication number: CN117357057A
Application number: CN202311382419.3A
Authority: CN
Inventors: 秦培武; 连丽津; 陈正林; 肖楚凡; 陈嘉驹; 彭翠仪; 彭博远; 邵蕾; 董力; 魏文斌
Original assignee: Beijing Tongren Hospital; Shenzhen International Graduate School of Tsinghua University
Current assignee: Beijing Tongren Hospital; Shenzhen International Graduate School of Tsinghua University
Priority date: 2023-10-24
Filing date: 2023-10-24
Publication date: 2024-01-09

Abstract

The invention discloses a myopia detection system and a myopia detection method, wherein the system comprises a fundus imaging component, a first half lens configured to have a first working position, a second half lens configured to have a second working position, an OCT detection component and a refraction detection component, when the first half lens is located at the first working position and the second half lens is located outside the second working position, fundus images are acquired through the fundus imaging component, meanwhile, the axial length of an eye is acquired through the OCT detection component, and when the second half lens is located at the second working position and the first half lens is located outside the first working position, refraction parameters are acquired through the refraction detection component. The invention realizes the simultaneous measurement of refractive parameters, ocular axial length, fundus images and other myopia indexes during single myopia detection, thereby not only reducing the volume of equipment and the myopia detection cost, but also improving the detection efficiency and detection precision of myopia detection and reducing the probability of misdiagnosis of myopia. The invention is applied to the technical field of optical measurement.

Description

Myopia detection system and detection method

Technical Field

The invention relates to the technical field of optical measurement, in particular to a myopia detection system and a myopia detection method.

Background

The eye is the most important sensory organ of the human body, when the human eye is in a state of accommodation and relaxation, parallel rays enter the human eye, and the rays are focused in front of the retina of the human eye, so that clear imaging cannot be formed on the retina, and this phenomenon is called myopia. In the related technology, myopia parameters of a patient are acquired through specific optical equipment such as a diopter detector, a refractometer and the like, and myopia screening and detection are carried out on the patient according to the myopia parameters of the patient, so that myopia problems such as poor eyesight, refractive deviation and the like are screened out, and early diagnosis and early intervention treatment of myopia are facilitated.

However, the existing specific optical device generally can only collect a single myopia parameter, cannot collect other types of myopia parameters, cannot collect multiple myopia parameters at the same time, and needs to collect other types of myopia parameters by adopting other specific optical devices to complete the collection of parameters. The myopia detection method has the advantages that the myopia detection steps are more complicated, the myopia detection efficiency is reduced, the situations of data dispersion and single data are easy to occur, the processing and analysis of multiple myopia parameters are not facilitated, and the intelligent degree of equipment and the myopia detection precision are required to be improved.

In addition, in addition to refractive errors, some myopic patients may develop pathological myopic fundus changes such as chorioretinal atrophy, retinal cleavage or choroidal neovascularization, which may cause irreversible vision impairment to the patient. However, existing specific optical devices do not enable monitoring of ocular fundus morphology changes while measuring myopic parameters of a patient's eye, and it is difficult to identify early ocular fundus morphology changes that are myopic to blindness.

Disclosure of Invention

The present invention aims to solve at least one of the technical problems existing in the prior art to a certain extent.

Therefore, an object of the present invention is to provide a myopia detection system and a detection method.

In order to achieve the technical purpose, the technical scheme adopted by the embodiment of the invention comprises the following steps:

in one aspect, embodiments of the present invention provide a myopia detection system comprising:

the fundus imaging assembly comprises a fundus incidence light path, a third semi-lens and a fundus imaging light path, wherein the third semi-lens is respectively connected with the fundus incidence light path and the fundus imaging light path in a coupling way;

a first half lens configured to have a first working position between the fundus imaging assembly and the human eye under test;

A second half lens configured to have a second working position located between the first working position and the fundus imaging assembly, the first working position, the second working position, the fundus imaging optical path, and the measured human eye being coaxial;

the OCT detection assembly comprises an OCT light source, a coupler, a reference arm, a sample arm and a data processing module, wherein the reference arm and the sample arm are positioned on one side of the coupler, and the OCT light source and the data processing module are positioned on the other side of the coupler;

the refraction detection assembly comprises a refraction incidence light path, a fourth semi-lens and a refraction acquisition light path, wherein the fourth semi-lens is respectively connected with the refraction incidence light path and the refraction acquisition light path in a coupling way;

wherein, when the OCT detection component or the fundus imaging component works, the first semi-lens is positioned at the first working position, and the second semi-lens is positioned outside the second working position; when the refraction detection assembly works, the second semi-transparent lens is located at the second working position, and the first semi-transparent lens is located outside the first working position.

In addition, the myopia detection system according to the above embodiment of the present invention may further have the following additional technical features:

Further, in an embodiment of the present invention, the first half lens, the second half lens, the third half lens, and the fourth half lens are half mirrors.

Further, in one embodiment of the present invention, the fundus imaging assembly further includes a omentum objective lens disposed between the second working position and the third semi-transparent mirror, the fundus incident light path includes a first light source, a first lens group, a first stop, a first mirror, and a first focusing lens, and the fundus imaging light path includes an imaging objective lens and an imaging acquisition module disposed coaxially; the first light source, the first lens group, the first diaphragm and the first reflecting mirror are coaxial, the first reflecting mirror, the first focusing lens and the third semi-transparent mirror are coaxial, and the axes of the first focusing lens and the third semi-transparent lens are perpendicular to the axes of the first light source and the first diaphragm.

Further, in one embodiment of the present invention, the first lens group includes a diffusion sheet and a thin film sheet, and the diffusion sheet is disposed between the thin film sheet and the first diaphragm.

Further, in one embodiment of the present invention, the fundus incident light path includes a flash lamp and a beam splitter, the beam splitter is located between the first light source and the first lens group, the flash lamp and the beam splitter are coaxial, and an axis of the flash lamp and the beam splitter is coaxial with an axis of the first lens group and the first light source.

Further, in one embodiment of the present invention, the sample arm includes a first collimating lens, a scanning galvanometer, and a second lens group, and the reference arm includes a second collimating lens, a second focusing lens, and a second reflecting mirror coaxially disposed; the axes of the first collimating lens and the scanning galvanometer are perpendicular to the axes of the second lens group and the scanning galvanometer, and the second lens group is coaxial with the first working position.

Further, in an embodiment of the present invention, the second lens group includes a sample objective lens and a sample eyepiece lens, and the sample objective lens and the sample target are coaxially disposed.

Further, in one embodiment of the invention, the data processing module includes a third collimating lens, a grating, a third focusing lens, a photosensor, and a data processor.

Further, in one embodiment of the present invention, the refractive incident light path includes a second light source and a second diaphragm coaxially disposed, and the refractive acquisition light path includes a refractive acquisition module and a focusing light path coaxially disposed; the second diaphragm is located between the fourth half lens and the second light source, the focusing light path is located between the fourth half lens and the refraction acquisition module, the axis of the refraction incident light path is perpendicular to the axis of the refraction acquisition light path, and the refraction acquisition light path, the fourth half lens and the second working position are coaxial.

Further, in one embodiment of the present invention, the focusing optical path includes at least three coaxially disposed focusing lenses.

In another aspect, an embodiment of the present invention provides a myopia detection method applied to the above-mentioned myopia detection system, including the following steps:

cutting the first half lens to a first working position;

controlling the OCT detection assembly and the fundus imaging assembly to work, performing fundus OCT scanning on the detected human eye through the OCT detection assembly to obtain the axial length of the detected human eye, and acquiring fundus images of the detected human eye through the fundus imaging assembly to obtain fundus images of the detected human eye;

moving the first half lens out of the first working position, and simultaneously cutting the second half lens into a second working position;

controlling the refraction detection assembly to work, and carrying out refraction measurement on the measured human eye through the refraction detection assembly to obtain refraction parameters of the measured human eye;

and obtaining a myopia detection result of the detected human eye according to the eye axial length, the fundus image and the refraction parameters of the detected human eye.

Further, in an embodiment of the present invention, the collecting, by the fundus imaging assembly, a fundus image of the tested eye, and obtaining the fundus image of the tested eye includes:

Controlling a first light source to be started, collimating light emitted by the first light source through a first lens group, forming first annular light with a first diaphragm, reflecting the first annular light to a first focusing lens through a first reflecting mirror, and focusing the first annular light to a third half lens through the first focusing lens;

reflecting the first annular light through the third half-lens to a web objective, the first annular light transmitted through the web objective to a first half-lens in the first operating position;

the first annular light is projected to the human eye to be detected through a first half lens positioned at the first working position, and first scattered light formed after being scattered by the human eye to be detected sequentially passes through the first half lens, the net film objective lens, the third half lens and the imaging objective lens to enter an imaging acquisition module;

and generating a fundus image of the tested human eye based on the first scattered light through the imaging acquisition module.

Further, in an embodiment of the present invention, the collecting, by the fundus imaging assembly, a fundus image of the tested eye, and further includes:

by changing the position of the imaging acquisition module or the imaging objective in the horizontal direction, the distance between the imaging acquisition module and the imaging objective is changed.

Further, in an embodiment of the present invention, the performing fundus OCT scanning on the tested human eye by the OCT detection component, to obtain an axial length of the tested human eye, includes:

controlling the OCT light source to be started, and decomposing light emitted by the OCT light source into reference light and sample light through a coupler, wherein the reference light is incident to a reference arm, and the sample light is incident to a sample arm;

in the reference arm, the reference light is collimated by a second collimating lens and then enters a second focusing lens, the reference light is focused to a second reflecting mirror by the second focusing lens, and the reference light is reflected by the second reflecting mirror so as to be returned to the coupler;

in the sample arm, the sample light is collimated to a scanning galvanometer through a first collimating lens, the scanning galvanometer is controlled to vibrate in the horizontal direction and the vertical direction, the sample light is reflected to a second lens group through the scanning galvanometer, the sample light is focused to a first half lens positioned at a first working position through the second lens group, the sample light is reflected to a tested human eye through the first half lens positioned at the first working position, and second scattered light formed after being scattered by the tested human eye returns to the coupler through the sample arm;

Interfering the second scattered light with reference light returned by the reference arm through the coupler to form interference light;

and carrying out image reconstruction on the interference light through a data processing module, and calculating the length of the eye axis of the detected human eye according to the reconstructed image.

Further, in an embodiment of the present invention, the reconstructing the image of the interference light by the data processing module, and calculating the length of the eye axis of the tested human eye according to the reconstructed image includes:

according to the relation between the pixel points of the photoelectric sensor and the wavelength, the illumination intensity received by each pixel point of the photoelectric sensor is integrated to form an initial spectrogram;

performing wavelength-wave number conversion on the initial spectrogram to generate a wave number domain spectrogram;

performing cubic spline interpolation, addition of a hanning window, dispersion compensation and fast Fourier transform on the wave number domain spectrogram to obtain a relation between a refractive index and depth corresponding to the wave number domain spectrogram;

and calculating the length of the eye axis of the tested human eye according to the relation between the refractive index and the depth.

Further, in one embodiment of the present invention, a positive correlation between the pixel points from left to right and the wavelength of the photoelectric sensor is used as the relationship between the pixel points and the wavelength of the photoelectric sensor.

Further, in one embodiment of the present invention, the step of obtaining the refractive parameter of the measured human eye by performing refractive measurement on the measured human eye through the refractive detection component includes:

controlling the second light source to be started, and forming second annular light through a refraction incident light path;

the second annular light is reflected to a second half lens positioned at a second working position through a fourth half lens, the second annular light is reflected to the human eye to be tested through the second half lens positioned at the second working position, and third scattered light formed after being scattered by the human eye to be tested sequentially passes through the second half lens, the fourth half lens and a focusing light path to enter a refraction acquisition module;

and calculating the refraction parameters of the tested human eye based on the third scattered light through a refraction acquisition module.

In yet another aspect, embodiments of the present invention provide a computer-readable storage medium in which a processor-executable program is stored, which when executed by a processor, is configured to perform the above-described myopia detection method.

The beneficial effects of the invention are as follows: the optical path for OCT detection, the optical path for refraction detection and the optical path for fundus imaging are integrated into the same detection system, switching of different detection optical paths is realized by changing the working positions of the first half lens and the second half lens, and when the first half lens is positioned at the first working position and the second half lens is positioned outside the second working position, the fundus image of the detected human eye is detected through the fundus imaging component while the axial length of the detected human eye is detected through the OCT detection component; and when the first semi-transparent lens is positioned outside the first working position and the second semi-transparent lens is positioned in the second working position, the refraction parameter of the tested human eye is measured through the refraction detection assembly. The invention not only effectively reduces the volume of special optical equipment for myopia detection and reduces the cost for myopia detection, but also realizes the simultaneous measurement of refractive parameters, ocular axial length, fundus images and other myopia indexes in the single myopia detection process, can measure the myopia indexes and monitor the change of the fundus morphology of human eyes, improves the detection efficiency and detection precision of myopia detection, reduces the probability of missed diagnosis and misdiagnosis of myopia, is beneficial to preventing and controlling myopia, and has high availability.

Additional features and advantages of the application will be set forth in the description which follows, and in part will be obvious from the description, or may be learned by practice of the application. The objectives and other advantages of the application will be realized and attained by the structure particularly pointed out in the written description and claims hereof as well as the appended drawings.

Drawings

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following description is made with reference to the accompanying drawings of the embodiments of the present invention or the related technical solutions in the prior art, and it should be understood that the drawings in the following description are only for convenience and clarity of describing some embodiments in the technical solutions of the present invention, and other drawings may be obtained according to these drawings without the need of inventive labor for those skilled in the art.

FIG. 1 is a block diagram of a myopia detection system according to the present invention;

FIG. 2 is a schematic view of a first half of a lens of the present invention in a first operative position;

FIG. 3 is a schematic illustration of a second semi-transparent mirror according to the present invention in a second operative position;

FIG. 4 is a block diagram of a fundus imaging assembly provided by the present invention;

FIG. 5 is a block diagram of an OCT detection assembly provided by the present invention;

FIG. 6 is a block diagram of a refractive detection assembly provided by the present invention;

FIG. 7 is another block diagram of a myopia detection system provided by the present invention;

fig. 8 is a flowchart of a myopia detection method provided by the present invention.

Detailed Description

In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be further described in detail with reference to the accompanying drawings and examples. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the present application.

The present application is further described below with reference to the drawings and specific examples. The described embodiments should not be construed as limitations on the present application, and all other embodiments, which may be made by those of ordinary skill in the art without the exercise of inventive faculty, are intended to be within the scope of the present application.

In the following description, reference is made to "some embodiments" which describe a subset of all possible embodiments, but it is to be understood that "some embodiments" can be the same subset or different subsets of all possible embodiments and can be combined with one another without conflict.

Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing embodiments of the present application only and is not intended to be limiting of the present application.

Aiming at the problems and defects existing in the related art, the embodiment of the invention provides a myopia detection system and a myopia detection method, which can carry out refractive measurement, OCT (Optical Coherence tomography ) measurement and fundus imaging based on an ophthalmic optical principle, further obtain myopia indexes such as refractive parameters, eye axial length, fundus images and the like, and realize quick detection and screening of myopia. The invention reduces the volume of myopia screening equipment, simultaneously enables a patient to obtain a plurality of myopia indexes through one-time myopia detection, realizes the monitoring of ocular fundus morphology change while measuring the myopia parameters of the patient's eyes, improves the myopia detection efficiency and precision, and has high availability.

Embodiments of the present application are further described below with reference to the accompanying drawings.

First, an implementation structure of the myopia detection system according to the embodiments of the present invention will be described in detail below.

Referring to fig. 1, fig. 1 is a block diagram of a myopia detection system according to the present invention, and the myopia detection system according to the present invention mainly includes a fundus imaging assembly 100, a first half-lens 200, a second half-lens 300, an OCT detection assembly 500, and a refraction detection assembly 600, wherein:

the fundus imaging assembly 100 mainly comprises a fundus incidence light path 110, a third half lens 120 and a fundus imaging light path 130, wherein the third half lens 120 is respectively coupled with the fundus incidence light path 110 and the fundus imaging light path 130, and the axes of the third half lens 120 and the fundus incidence light path 110 are mutually perpendicular to the axes of the third half lens 120 and the fundus imaging light path 130.

The first half lens 200 is configured to have a first operative position between the fundus imaging assembly 100 and the human eye 400 under test. The second half lens 300 is configured with a second operative position, which is located between the first operative position and the fundus imaging assembly 100. Further, the first working position, the second working position, the fundus imaging optical path 130, and the human eye 400 under test are coaxial.

OCT detection assembly 500 mainly includes OCT light source 510, coupler 520, reference arm 530, sample arm 540, and data processing module 550. Wherein the reference arm 530 and the sample arm 540 are located at one side of the coupler 520, the OCT light source 510 and the data processing module 550 are located at the other side of the coupler 520, and the coupler 520 is coupled with the reference arm 530, the sample arm 540, the OCT light source 510 and the data processing module 550, respectively.

Alternatively, OCT light source 510 may be an infrared broadband light source, or may be another infrared light source, such as a low coherence gaussian infrared light source, which is not particularly limited by the present invention. The wavelength of the OCT light source 510 may be 980nm or other wavelength parameters, and the present invention is not limited thereto.

Alternatively, coupler 520 is a fiber optic coupler.

The refraction detection assembly 600 mainly includes a refraction incident light path 610, a fourth half lens 620 and a refraction collection light path 630, wherein the fourth half lens 620 is coupled with the refraction incident light path and the refraction collection light path 630 respectively, and axes of the refraction incident light path 610 and the fourth half lens 620 are perpendicular to axes of the refraction collection light path 630 and the fourth half lens 620.

The first half lens 200, the second half lens 300, the third half lens 120, and the fourth half lens 620 are half mirrors.

It is understood that a half mirror is a special optical device that has both light transmitting and light reflecting properties.

Further, referring to fig. 2, fig. 2 is a schematic diagram of the first half lens 200 in the first working position provided in the embodiment of the present invention, when the OCT detection assembly 500 or the fundus imaging assembly 100 is working, the first half lens 200 is in the first working position, and the second half lens 300 is located outside the second working position, at this time, the axial length measurement of the tested human eye 400 can be achieved by the OCT detection assembly 500, and the collection of the fundus image of the tested human eye 400 can be achieved by the fundus imaging assembly 100. Wherein, when OCT detection assembly 500 is in operation, first half lens 200 in the first operating position is reflective; when the fundus imaging assembly 100 is in operation, the first half lens 200 in the first operating position is transmissive.

It should be emphasized that, when fundus image acquisition and eye axial length measurement are performed, the second half lens 300 needs to be cut out beyond the second working position, so as to avoid the negative influence of the second half lens 300 located at the second working position on stray light on the fundus imaging optical path 130 and the OCT detection optical path, so as to ensure accuracy of the eye axial length detection result and fundus imaging.

Further, referring to fig. 3, fig. 3 is a schematic diagram of the second half lens 300 in the second working position according to the embodiment of the invention, when the refraction detecting assembly 600 is working, the second half lens 300 is in the second working position, and the first half lens 200 is located outside the first working position, so that the refraction detection of the tested human eye 400 can be achieved by the refraction detecting assembly 600. Wherein, when the refraction detecting assembly 600 is operated, the second half lens 300 in the second operating position is reflected.

It should be emphasized that, during the refraction measurement, the first half lens 200 needs to be cut out beyond the first working position, so as to avoid the negative influence of the first half lens 200 located at the first working position on the refraction acquisition optical path 630 caused by stray light, so as to ensure the accuracy of the refraction detection result.

In some embodiments of the present invention, referring to fig. 4, fig. 4 is a block diagram of a fundus imaging assembly provided in an embodiment of the present invention, where fundus imaging assembly 100 further includes a webcam objective 140 disposed between a second working position and third half-lens 120, fundus incident light path 110 mainly includes a first light source 111, a first lens group, a first diaphragm 112, a first mirror 113, and a first focusing lens 114, fundus imaging light path 130 includes an imaging objective 131 and an imaging acquisition module 132 coaxially disposed, where first light source 111, first lens group, first diaphragm 112, and first mirror 113 are coaxial, first mirror 113, first focusing lens 114, and third half-lens 120 are coaxial, and axes of first focusing lens 114 and third half-lens 120 are perpendicular to axes of first light source 111 and first diaphragm 112.

Alternatively, the first light source 111 may be a halogen lamp, and may be other visible light sources, which is not particularly limited in the present invention.

Alternatively, the omentum objective 140 may be a 22D indirect ophthalmoscope with a 60 degree field of view, a large aperture of 52mm, which can improve light transmission and advanced anti-reflection coatings. However, in other embodiments of the present invention, the web objective 140 may be an indirect ophthalmoscope of other specifications, which is not particularly limited by the present invention.

Further, the first lens group includes a diffusion sheet 115 and a thin film sheet 116, and the diffusion sheet 115 is disposed between the thin film sheet 116 and the first diaphragm 112.

Alternatively, film sheet 116 is a UV-blocking film sheet.

Further, the fundus incident light path 110 may further include a flash 117 and a light-splitting plate 118, the light-splitting plate 118 is located between the first light source 111 and the thin film sheet 116, the flash 117 is coaxial with the light-splitting plate 118, and an axis of the flash 117 and the light-splitting plate 118 is coaxial with an axis of the first lens group and the first light source 111.

In the embodiment of the present invention, the principle and process of implementing the collection of fundus images by the fundus imaging assembly 100 are as follows:

first, the first half lens 200 is cut into the first working position, the second half lens 300 is cut out to the outside of the second working position, the first light source 111 is controlled to be turned on, the visible light emitted by the first light source 111 is expanded and then enters the thin film piece 116, the thin film piece 116 changes the light spot quality of the visible light, so that the light spot quality of the visible light projected onto the scattering piece 115 is uniform, the visible light is scattered to the first diaphragm 112 through the scattering piece 115, the imaging annular light with stray light eliminated through the first diaphragm 112 is obtained, the first reflecting mirror 113 reflects the imaging annular light to the first focusing lens 114, and the first focusing lens 114 focuses the imaging annular light to the third half lens 120.

Then, the third half lens 120 reflects the annular light for imaging to the web objective 140, the annular light for imaging is transmitted to the first half lens 200 located at the first working position through the web objective 140, the first half lens 200 located at the first working position projects the first annular light to the human eye 400 to be tested, the first scattered light formed after being scattered by the human eye 400 to be tested sequentially passes through the first half lens 200 and the web objective 140 to enter the third half lens 120, the third half lens 120 transmits the first scattered light to the imaging objective 131, the imaging objective 131 is used for enhancing focusing capability, so that the image focused by the web objective 140 can entirely cover the sensor of the imaging acquisition module 132, and the first scattered light enters the imaging acquisition module 132 through the imaging objective 131.

Finally, the imaging collection module 132 collects the first scattered light and generates a fundus image of the tested human eye 400 according to the first scattered light, thereby achieving collection of the fundus image.

In addition, in the process of collecting the fundus image, the distance between the imaging objective lens 131 and the imaging collecting module 132 can be adjusted according to the focusing index, so as to set the imaging focal length, and the fundus imaging assembly 100 is supplemented with light through the flash 117 and the light splitting plate 118, so as to obtain a fundus image with better quality.

It should be noted that the focusing index may be used to determine whether the blood vessel on the retina is imaged clearly, or may be used as well as other focusing indexes such as whether the imaging brightness of the retina reaches the brightness index, and the invention is not limited thereto.

Optionally, the distance between the imaging objective 131 and the imaging acquisition module 132 is 35 mm.

In some embodiments of the present invention, referring to fig. 5, fig. 5 is a block diagram of an OCT detection assembly provided by an embodiment of the present invention, in an OCT detection assembly 500 provided by an embodiment of the present invention, a sample arm 540 includes a first collimating lens 541, a scanning galvanometer 542, and a second lens group, a reference arm 530 includes a second collimating lens 531, a second focusing lens 532, and a second reflecting mirror 533 coaxially disposed, and a data processing module 550 includes a third collimating lens 551, a grating 552, a third focusing lens 553, a photosensor 554, and a data processor 555. Wherein, the axes of the first collimating lens 541 and the scanning galvanometer 542 are perpendicular to the axes of the second lens group and the scanning galvanometer 542, and the second lens group is coaxial with the first working position.

Optionally, the photosensor 554 is a CCD sensor.

Further, the second lens group includes a sample objective 543 and a sample eyepiece 544, and the sample objective 543 and the sample target are coaxially provided.

In the embodiment of the present invention, the principle and process of implementing the detection of the eye axis length by the OCT detection assembly 500 are as follows:

first, the first half lens 200 is cut into the first working position, and the OCT light source 510 is controlled to be turned on, and the OCT light source 510 emits infrared light. The coupler 520 splits the infrared light into reference light and sample light, the reference light being incident on the reference arm 530 and the sample light being incident on the sample arm 540.

In the reference arm 530, the second collimating lens 531 collimates the reference light to ensure that the incident reference light can be narrowed and collimated. The collimated reference light is incident on the second focusing lens 532, the second focusing lens 532 focuses the reference light to the second reflecting mirror 533, and the second reflecting mirror 533 reflects the reference light so that the reference light is returned back to the coupler 520.

In the sample arm 540, a first collimating lens 541 collimates the sample light, ensuring that the incident sample light energy is narrowed and collimated. The scanning galvanometer 542 is disposed at a position before the optical path enters the second lens group, and the scanning galvanometer 542 is controlled to vibrate in the horizontal direction and the vertical direction, so that the sample light is reflected to the second lens group through the scanning galvanometer 542, is focused to the first half lens 200 positioned at the first working position through the sample objective lens 543 and the sample eyepiece 544 in sequence, is reflected to the human eye 400 to be tested through the first half lens 200, and is reflected to the sample arm 540 through the first half lens 200, and is returned to the coupler 520 through the sample arm 540.

Then, the second scattered light reflected at the different reflecting surfaces and the reference light returned by the reference arm 530 interfere at the coupler 520 to form interference light. The interference light meets the envelope surface modulation of Gaussian distribution from the image, and the interference positions of different reflecting surfaces can be obtained by resolution through the envelope surface modulation of Gaussian distribution.

Then, the interference light enters the grating 552 after being collimated by the third collimating lens 551, the grating 552 separates the interference light with different wavelengths, the separated interference light enters the photoelectric sensor 554 by the third collimating lens 553, the data processor 555 reconstructs an image according to the interference light collected by the photoelectric sensor 554, and the eye axis length of the measured human eye 400 is calculated according to the reconstructed image.

In some embodiments of the present invention, referring to fig. 6, fig. 6 is a block diagram of a refractive detection assembly provided in an embodiment of the present invention, in the refractive detection assembly 600, a refractive incident light path 610 includes a coaxially disposed second light source 611 and a second stop 612, and a refractive acquisition light path 630 includes a coaxially disposed refractive acquisition module 631 and a focusing light path 632. The second diaphragm 612 is located between the fourth half lens 620 and the second light source 611, the focusing light path 632 is located between the fourth half lens 620 and the refractive acquisition module 631, the axis of the refractive incident light path 610 is perpendicular to the axis of the refractive acquisition light path 630, and the refractive acquisition light path 630, the fourth half lens 620 and the second working position are coaxial.

Alternatively, the second light source 611 may be a halogen lamp, but may also be other visible light sources, which is not particularly limited in the present invention.

Further, the focus light path 632 includes at least three coaxially disposed focus lenses.

It should be noted that, in the embodiment of the present invention, the focusing optical path 632 includes three focusing lenses disposed coaxially, but in other embodiments of the present invention, the focusing optical path 632 may further include more than three focusing lenses disposed coaxially according to the actual requirement of the focusing effect, which is not limited in this invention.

In the embodiment of the present invention, the principle and process of implementing the detection of refractive parameters by the refractive detection assembly 600 are as follows:

first, the second half lens 300 is cut into the second working position, the first half lens 200 is cut out from the first working position, the second light source 611 is controlled to be turned on, the visible light emitted by the second light source 611 is incident on the second diaphragm 612, the imaging annular light with stray light eliminated by the second diaphragm 612 is obtained, and the fourth half lens 620 reflects the imaging annular light to the second half lens 300 located at the second working position. Then, the second half lens 300 reflects the annular light for imaging to the human eye 400 to be tested, the third scattered light formed after being scattered by the human eye 400 to be tested is reflected to the fourth half lens 620 through the second half lens 300, the fourth half lens 620 transmits the third scattered light to the focusing light path 632, the position of the focusing lens in the focusing light path 632 is adjusted according to the quality of refractive imaging, and then Qu Guangcheng image points are obtained. Finally, the third scattered light enters the refraction acquisition module 631 through the focusing light path 632, and the refraction acquisition module 631 obtains refraction parameters by calculating an optimal imaging point.

In some embodiments of the present invention, referring to fig. 1 and 7, fig. 7 is another block diagram of a myopia detection system according to embodiments of the present invention. The myopia detection system provided by the embodiment of the invention can further comprise:

an adjustment device 700;

the motion control module 800 is connected with the first stepper motor, the second stepper motor, the third stepper motor, the fourth stepper motor, the fifth stepper motor and the sixth stepper motor, and is connected with the first light source 111, the second light source 611 and the OCT light source 510;

the main control unit 900 is connected with the motion control module 800 and is respectively connected with the refraction acquisition module 631, the data processing module 550 and the imaging acquisition module 132.

Alternatively, the main control unit 900 is communicatively connected to the motion control module 800 through an RS232 serial port, and those skilled in the art will understand that other serial interface standards, such as RS422 and RS485, are also applicable besides RS232 serial port communication, which is not particularly limited in the present invention.

It should be noted that, RS232, also called as a serial binary data exchange interface technical standard between a data terminal device and a data communication device, is defined as a single-ended communication method for increasing a communication distance in low-rate serial communication, which adopts an unbalanced transmission manner, that is, it is a so-called single-ended communication.

Further, the adjustment device 700 may include, but is not limited to, the following components:

a myopia detection stage 710 for mounting optical components other than the first light source 111, the second light source 611, and the OCT light source 510;

the first lens moving device 720 includes a first moving bracket and a first stepper motor, one end of the first moving bracket is fixed with the first half lens 200, and the other end is connected with the first stepper motor;

the second lens moving device 730, including a second moving bracket and a second stepping motor, one end of the second moving bracket is fixed with the second half lens 300, and the other end is connected with the second stepping motor;

the focusing moving device 740 comprises a third moving bracket and a third stepping motor, wherein one end of the third moving bracket is fixed with the imaging objective 131 or the imaging acquisition module 132, and the other end of the third moving bracket is connected with the third stepping motor;

a chin rest 750 for providing a patient with a chin to be held.

The bracket moving device 760 includes a fourth moving bracket and a fourth stepping motor, one end of the fourth moving bracket is connected with the chin bracket 750, and the other end thereof is connected with the fourth stepping motor;

the detection stage moving device 770 includes a fifth stepping motor and a sixth stepping motor, which are respectively connected with the myopia detection stage 710;

In an embodiment of the present invention, the motion control module 800 is configured to control the first light source 111, the second light source 611, and the OCT light source 510 to operate.

The motion control module 800 is further configured to control the first stepper motor to operate, where the first stepper motor drives the first moving support to move, so that the first half lens 200 is cut into or out of the first working position.

The motion control module 800 is further configured to control the second stepper motor to operate, and the second stepper motor drives the second moving support to move when operating, so that the second half lens 300 is cut into the second working position or out of the second working position.

The motion control module 800 is further configured to control the third stepper motor to operate, where the third stepper motor drives the third moving bracket to move when operating, so as to move the imaging objective 131 or the imaging acquisition module 132, so as to change the distance between the imaging objective 131 and the imaging acquisition module 132.

The motion control module 800 is further configured to control the fourth stepper motor to operate, and the fourth stepper motor drives the fourth moving bracket to move when operating, so that the chin rest 750 moves in the vertical direction, and the height of the chin rest 750 is adjusted.

The motion control module 800 is further configured to control the fifth stepper motor and the sixth stepper motor to operate, and the fifth stepper motor and the sixth stepper motor operate to drive the myopia detection stage 710 to move, so as to adjust the relative vertical distance and the relative distance between the tested human eye 400 and the fundus imaging assembly 100, the OCT detection assembly 500, and the refraction detection assembly 600.

Optionally, the motion control module 800 receives an instruction of the main control unit 900, and performs the above-described configured operation or behavior according to the instruction sent by the main control unit 900.

Next, one implementation step of the myopia detection method according to the embodiments of the present invention will be described in detail below.

The method in the embodiment of the invention can be applied to the terminal, the server, software running in the terminal or the server and the like. The terminal may be, but is not limited to, a tablet computer, a notebook computer, a desktop computer, etc. The server may be an independent physical server, a server cluster or a distributed system formed by a plurality of physical servers, or a cloud server providing cloud services, cloud databases, cloud computing, cloud functions, cloud storage, network services, cloud communication, middleware services, domain name services, security services, CDNs, basic cloud computing services such as big data and artificial intelligent platforms.

Referring to fig. 1 and 7 and fig. 8, fig. 8 is a flowchart of a myopia detection method according to an embodiment of the present invention, which may include, but is not limited to, the following steps:

s101, cutting the first half lens 200 into the first working position.

In this step, the motion control module 800 controls the first stepping motor and the second stepping motor to operate, so that the first half lens 200 is moved to the first working position, and the second half lens 300 is cut out of the second working position.

S102, controlling the OCT detection assembly and the fundus imaging assembly to work, performing fundus OCT scanning on the detected human eye through the OCT detection assembly to obtain the axial length of the detected human eye, and acquiring fundus images of the detected human eye through the fundus imaging assembly to obtain the fundus images of the detected human eye.

S103, the first half lens 200 is moved out of the first working position, and the second half lens 300 is cut into the second working position.

In this step, the motion control module 800 controls the first stepper motor and the second stepper motor to operate, so that the second half lens 300 is moved to the second working position, and the first half lens 200 is cut out of the first working position.

S104, controlling the refraction detection assembly to work, and carrying out refraction measurement on the measured human eye through the refraction detection assembly to obtain the refraction parameters of the measured human eye.

S105, obtaining a myopia detection result of the human eye to be detected according to the axial length of the human eye to be detected, the fundus image and the refraction parameters.

In the embodiment of the present invention, the detection of myopia parameters of multiple modes of the tested human eye 400 is achieved by controlling multiple stepper motors and multiple light sources through the main control unit and the motion control module 800. Specifically, first, the first half lens 200 is cut into the first working position, and the second half lens 300 is cut out of the second working position, so that the simultaneous acquisition of the fundus image and the axial length of the eye 400 of the tested human eye is realized by controlling the OCT detection assembly 500 and the fundus imaging assembly 100 to work together; then, the second half lens 300 is cut into the second working position, and the first half lens 200 is cut out of the first working position, so that the refractive parameters of the tested human eye 400 are measured by the refraction detection assembly 500, and the detection of myopia parameters of multiple modes of the tested human eye 400 is further realized.

Optionally, before step S101, the myopia detection method may further include the steps of:

the height of the chin rest 750 is controlled by the motion control module 800, and the relative distances between the eye 400 to be measured and the fundus imaging assembly 100, the OCT detection assembly 500, and the refraction detection assembly 500 are adjusted by the motion control module 800 controlling the fifth and sixth stepper motors.

In some embodiments of the present invention, referring to fig. 4, in step S102, the fundus image acquisition of the tested human eye 400 by the fundus imaging assembly 100, the implementation process of obtaining the fundus image of the tested human eye 400 may include, but is not limited to, the following steps:

first, the first light source 111 is controlled to be turned on, light emitted by the first light source 111 is collimated by the first lens group and forms first annular light with the first diaphragm 112, the first annular light is reflected to the first focusing lens 114 by the first reflecting mirror 113, and the first annular light is focused to the third half lens 120 by the first focusing lens 114.

The first annular light is then reflected by the third lens half 120 to the web objective 140, and is transmitted through the web objective 140 to the first lens half 200 in the first operating position.

Then, the first annular light is projected to the tested human eye 400 through the first half lens 200 located at the first working position, and the first scattered light formed after being scattered by the tested human eye 400 sequentially passes through the first half lens 200, the net film objective lens 140, the third half lens 120 and the imaging objective lens 131 to enter the imaging acquisition module 132.

Finally, a fundus image of the tested human eye 400 is generated based on the first scattered light by the imaging acquisition module 132.

Optionally, in step S102, the fundus image acquisition of the tested human eye 400 by the fundus imaging assembly 100 may further include the following steps:

the position of the imaging acquisition module 132 or the imaging objective 131 in the horizontal direction is changed by controlling the third stepping motor so that the distance between the imaging acquisition module 132 and the imaging objective 131 is changed.

In this step, the imaging focal length is adjusted by changing the position of the imaging acquisition module 132 or the imaging objective 131 in the horizontal direction, so that the fundus imaging quality is better and the fundus imaging efficiency is improved.

In some embodiments of the present invention, referring to fig. 5, in step S102, the implementation process of performing fundus OCT scanning on the measured human eye 400 by the OCT detection assembly 500 to obtain the eye axis length of the measured human eye 400 may include, but is not limited to, the following steps:

first, the OCT light source 510 is controlled to be turned on, and the light emitted from the OCT light source 510 is decomposed into reference light and sample light by the coupler 520, the reference light is incident on the reference arm 530, and the sample light is incident on the sample arm 540.

In the reference arm 530, the reference light is collimated by the second collimating lens 531 and then enters the second focusing lens 532, the reference light is focused by the second focusing lens 532 to the second reflecting mirror 533, and the reference light is reflected by the second reflecting mirror 533 so that the reference light is returned to the coupler 520.

In the sample arm 540, the sample light is collimated to the scanning galvanometer 542 by the first collimating lens 541, the scanning galvanometer 542 is controlled to vibrate in the horizontal direction and the vertical direction, the sample light is reflected to the second lens group by the scanning galvanometer 542, the sample light is focused to the first half lens 200 located at the first working position by the sample objective lens 543 and the sample eyepiece 544, the sample light is reflected to the human eye 400 to be measured by the first half lens 200 located at the first working position, and the second scattered light formed after being scattered by the human eye 400 to be measured returns to the coupler 520 by the sample arm 540.

Thereafter, the second scattered light interferes with the reference light returned by the reference arm 530 through the coupler 520 to form interference light.

Finally, the data processing module 550 performs image reconstruction on the interference light, and calculates the axial length of the tested human eye 400 according to the reconstructed image.

More specifically, the step of reconstructing an image of the interference light by the data processing module 550 and calculating the axial length of the measured human eye 400 according to the reconstructed image mainly includes:

the first step, according to the relation between the pixel points of the photoelectric sensor and the wavelength, the illumination intensity received by each pixel point of the photoelectric sensor is integrated to form an initial spectrogram.

In this step, the relationship between the pixel points of the photoelectric sensor 554 from left to right and the wavelength is positive, which is used as the relationship between the pixel points of the photoelectric sensor 554 and the wavelength, and the light intensities received by the pixel points are integrated to obtain a relationship graph between the wavelength and the light intensity, i.e. a spectrogram.

And step two, performing wavelength-wave number conversion on the initial spectrogram to generate a wave number domain spectrogram.

In the step, wavelength information in the initial spectrogram is converted into wave number information through a conversion relation between wavelength and wave number, so that a wave number domain spectrogram is obtained.

Thirdly, performing cubic spline interpolation, hanning window addition, dispersion compensation and fast Fourier transformation on the wave number domain spectrogram to obtain the relation between the refractive index and the depth corresponding to the wave number domain spectrogram.

It should be noted that, the cubic spline interpolation refers to a process of obtaining a curve function set by solving a three-bending moment equation set mathematically through a smooth curve of a series of shape value points. The hanning window is one of the window functions, which is a special case of a raised cosine window, and can be seen as the sum of the spectra of three rectangular time windows. Dispersion compensation refers to the control of the overall dispersion of a system by incorporating appropriate optical elements into the system.

In this step, first, cubic spline interpolation is performed on the wavenumber domain spectrogram, and the unevenly sampled wavenumber domain spectrogram is converted into an evenly sampled wavenumber domain spectrogram. And then, adding a hanning window to the wave number domain spectrogram after the interpolation processing to realize convolution processing on the wave number domain spectrogram frequency domain, thereby being beneficial to enhancing the frequency domain characteristics of the wave number domain spectrogram and reducing the frequency spectrum energy leakage. And then, carrying out dispersion compensation on the wavenumber domain spectrogram processed by the window function, wherein the dispersion compensation can avoid the broadening of the wavenumber domain spectrogram in the time domain or the distortion of signals. And finally, calculating the wave number domain spectrogram after dispersion compensation through fast Fourier transform to obtain the refractive index-depth relation corresponding to the wave number domain spectrogram, namely the A-SCAN data.

Alternatively, the refractive index-depth relationship measurements for various areas of the fundus can be made by varying the deflection angle of scanning galvanometer 542 in OCT detection assembly 500.

Fourth, according to the relation between the refractive index and the depth, the axial length of the measured human eye 400 is calculated.

It should be noted that, in this step, the calculation of the eye axis length belongs to the prior art, and the embodiment of the present invention will not be repeated.

In some embodiments of the present invention, referring to fig. 6, in step S104, the implementation process of obtaining the refractive parameter of the measured human eye 400 by performing the refractive measurement on the measured human eye 400 by the refractive detection component 500 may include, but is not limited to, the following steps:

controlling the second light source 611 to be turned on, and forming second annular light through the refraction incident light path 610;

the second annular light is reflected to the second half lens 300 located at the second working position through the fourth half lens 620, the second annular light is reflected to the tested human eye 400 through the second half lens 300 located at the second working position, and the third scattered light formed after being scattered by the tested human eye 400 sequentially passes through the second half lens 300, the fourth half lens 620 and the focusing light path 632 to enter the refraction acquisition module 631;

the refractive parameters of the human eye 400 to be measured are calculated by the refractive acquisition module 631 based on the third scattered light.

Referring to fig. 1 to 7 again, an example will be described below to illustrate and explain the application of the myopia detection system and the detection method according to the embodiments of the present invention.

First, the chin of the patient is placed on the chin rest 750, and the fourth stepping motor is operated by the motion control module 800 so that the chin rest 750 is raised to an appropriate height. Meanwhile, the motion control module 800 controls the fifth stepping motor and the sixth stepping motor to work, and the positions of the myopia detection table in the directions of the x axis, the y axis and the z axis are adjusted. The eye optical axis of the patient is made coaxial with the fundus imaging optical path 130 of the fundus imaging assembly 100 by the above adjustment.

Then, the first and second stepper motors are controlled to operate by the motion control module 800 so that the first half lens 200 is cut into the first working position and the second half lens 300 is cut out of the second working position.

Then, the first light source 111 is controlled to be turned on, the fundus of the tested human eye 400 is illuminated through the fundus incidence light path 110 of the fundus imaging assembly 100, a fundus image is acquired through the fundus imaging light path 130, a focusing index is detected through the fundus image, namely whether blood vessels on the retina are imaged clearly is judged, and the third stepping motor is controlled according to the detected focusing index, so that the distance between the imaging objective lens 131 and the imaging acquisition module 132 is adjusted, and a clear fundus image is obtained. At the same time, the OCT light source 510 is controlled to be turned on, and the axial length of the eye 400 is detected by the OCT detection assembly 500.

Thereafter, the first and second stepper motors are controlled to operate by the motion control module 800 such that the first half lens 200 is cut out of the first operating position and the second half lens 300 is cut into the second operating position. The second light source 611 is controlled to be turned on, and the refractive parameters of the human eye 400 to be measured are detected by the refractive detection assembly 500.

Finally, according to the detected axial length, refractive parameters and fundus image of the detected human eye 400, a myopia detection result of the patient is obtained.

In summary, the myopia detection system and the detection method provided by the embodiment of the invention integrate the OCT detection component, the refraction detection component and the fundus imaging component into the detection system. For a myopia detection method, the embodiment of the invention realizes the switching of different detection light paths by changing the working positions of the first half lens and the second half lens, and when the first half lens is positioned at the first working position and the second half lens is positioned outside the second working position, the OCT detection component is used for detecting the axial length of the eye of the detected human eye and the fundus imaging component is used for detecting the fundus image of the detected human eye; and when the first semi-transparent lens is positioned outside the first working position and the second semi-transparent lens is positioned in the second working position, the refraction parameter of the tested human eye is measured through the refraction detection assembly.

On one hand, the embodiment of the invention effectively reduces the volume of the special optical equipment for myopia detection and reduces the cost for myopia detection. On the other hand, the embodiment of the invention realizes simultaneous measurement of refractive parameters, ocular axial length and fundus images in the single myopia detection process, can monitor changes of fundus morphology of human eyes while measuring myopia parameters, improves the detection efficiency and detection precision of myopia detection by simultaneously collecting and analyzing myopia parameters of a plurality of modes, effectively reduces the probability of missed diagnosis and the probability of misdiagnosis of myopia, is beneficial to further medical treatment of myopes and prevention and control of myopia, and has high availability.

The embodiment of the present invention also provides a computer-readable storage medium in which a processor-executable program is stored, which when executed by a processor is for performing the myopia detection method described above.

The content in the method embodiment is applicable to the storage medium embodiment, and functions specifically implemented by the storage medium embodiment are the same as those of the method embodiment, and the achieved beneficial effects are the same as those of the method embodiment.

In some alternative embodiments, the functions/acts noted in the block diagrams may occur out of the order noted in the operational illustrations. For example, two blocks shown in succession may in fact be executed substantially concurrently or the blocks may sometimes be executed in the reverse order, depending upon the functionality/acts involved. Furthermore, the embodiments presented and described in the flowcharts of the present invention are provided by way of example in order to provide a more thorough understanding of the technology. The disclosed methods are not limited to the operations and logic flows presented herein. Alternative embodiments are contemplated in which the order of various operations is changed, and in which sub-operations described as part of a larger operation are performed independently.

Furthermore, while the invention is described in the context of functional modules, it should be appreciated that, unless otherwise indicated, one or more of the functions and/or features may be integrated in a single physical device and/or software module or may be implemented in separate physical devices or software modules. It will also be appreciated that a detailed discussion of the actual implementation of each module is not necessary to an understanding of the present invention. Rather, the actual implementation of the various functional modules in the apparatus disclosed herein will be apparent to those skilled in the art from consideration of their attributes, functions and internal relationships. Accordingly, one of ordinary skill in the art can implement the invention as set forth in the claims without undue experimentation. It is also to be understood that the specific concepts disclosed are merely illustrative and are not intended to be limiting upon the scope of the invention, which is to be defined in the appended claims and their full scope of equivalents.

The functions, if implemented in the form of software functional units and sold or used as a stand-alone product, may be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present invention may be embodied essentially or in a part contributing to the prior art or in the form of a software product stored in a storage medium, including several programs for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the method according to the embodiments of the present invention. And the aforementioned storage medium includes: a U-disk, a removable hard disk, a Read-Only Memory (ROM), a random access Memory (RAM, random Access Memory), a magnetic disk, or an optical disk, or other various media capable of storing program codes.

Logic and/or steps represented in the flowcharts or otherwise described herein, e.g., a ordered listing of executable programs for implementing logical functions, can be embodied in any computer-readable medium for use by or in connection with a program execution system, apparatus, or device, such as a computer-based system, processor-containing system, or other system that can fetch the programs from the program execution system, apparatus, or device and execute the programs. For the purposes of this description, a "computer-readable medium" can be any means that can contain, store, communicate, propagate, or transport the program for use by or in connection with the program execution system, apparatus, or device.

More specific examples (a non-exhaustive list) of the computer-readable medium would include the following: an electrical connection (electronic device) having one or more wires, a portable computer diskette (magnetic device), a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber device, and a portable compact disc read-only memory (CDROM). In addition, the computer readable medium may even be paper or other suitable medium on which the program is printed, as the program may be electronically captured, via, for instance, optical scanning of the paper or other medium, then compiled, interpreted or otherwise processed in a suitable manner, if necessary, and then stored in a computer memory.

It is to be understood that portions of the present invention may be implemented in hardware, software, firmware, or a combination thereof. In the above embodiments, the various steps or methods may be implemented in software or firmware stored in a memory and executed by a suitable program execution system. For example, if implemented in hardware, as in another embodiment, may be implemented using any one or combination of the following techniques, as is well known in the art: discrete logic circuits having logic gates for implementing logic functions on data signals, application specific integrated circuits having suitable combinational logic gates, programmable Gate Arrays (PGAs), field Programmable Gate Arrays (FPGAs), and the like.

In the foregoing description of the present specification, reference has been made to the terms "one embodiment/example", "another embodiment/example", "certain embodiments/examples", and the like, 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 invention. 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 invention 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 invention, the scope of which is defined by the claims and their equivalents.

While the preferred embodiment of the present invention has been described in detail, the present invention is not limited to the embodiments described above, and various equivalent modifications and substitutions can be made by those skilled in the art without departing from the spirit of the present invention, and these equivalent modifications and substitutions are intended to be included in the scope of the present invention as defined in the appended claims.

Claims

1. A myopia detection system, comprising:

2. The myopia detection system according to claim 1, wherein the fundus imaging assembly further comprises a omentum objective lens disposed between the second working position and the third semi-transparent lens, the fundus incident light path comprising a first light source, a first lens group, a first stop, a first mirror, and a first focusing lens, the fundus imaging light path comprising an imaging objective lens and an imaging acquisition module disposed coaxially; the first light source, the first lens group, the first diaphragm and the first reflecting mirror are coaxial, the first reflecting mirror, the first focusing lens and the third semi-transparent mirror are coaxial, and the axes of the first focusing lens and the third semi-transparent lens are perpendicular to the axes of the first light source and the first diaphragm.

3. The myopia detection system according to claim 1, wherein the sample arm comprises a first collimating lens, a scanning galvanometer, and a second lens group, and the reference arm comprises a coaxially disposed second collimating lens, a second focusing lens, and a second reflecting mirror; the axes of the first collimating lens and the scanning galvanometer are perpendicular to the axes of the second lens group and the scanning galvanometer, and the second lens group is coaxial with the first working position.

4. A myopia detection system according to claim 3, wherein the refractive incident light path comprises a coaxially disposed second light source and second stop, the refractive acquisition light path comprising a coaxially disposed refractive acquisition module and a focusing light path; the second diaphragm is located between the fourth half lens and the second light source, the focusing light path is located between the fourth half lens and the refraction acquisition module, the axis of the refraction incident light path is perpendicular to the axis of the refraction acquisition light path, and the refraction acquisition light path, the fourth half lens and the second working position are coaxial.

5. A myopia detection system according to claim 4, wherein the focusing optical path comprises at least three coaxially disposed focusing lenses.

6. A myopia detection method, characterized in that it is applied to a myopia detection system according to any one of claims 1-5, comprising the steps of:

cutting the first half lens to a first working position;

7. A myopia detection method according to claim 6, wherein the acquiring the fundus image of the eye to be detected by the fundus imaging assembly, to obtain the fundus image of the eye to be detected, comprises:

8. The myopia detection method according to claim 6, wherein the performing fundus OCT scanning on the human eye to be detected by the OCT detection component to obtain an axial length of the human eye to be detected comprises:

9. The myopia detection method according to claim 8, wherein the data processing module comprises a photoelectric sensor, wherein the image reconstruction of the interference light by the data processing module is performed, and the eye axis length of the human eye to be detected is calculated according to the reconstructed image, and the method comprises:

10. A method of myopia according to claim 6, wherein the step of obtaining refractive parameters of the measured eye by refractive measurement of the measured eye by the refractive detection assembly comprises: