CN118000655A

CN118000655A - Ophthalmic measurement system

Info

Publication number: CN118000655A
Application number: CN202410223165.9A
Authority: CN
Inventors: 蔡守东; 吴蕾; 王辉; 郭曙光
Original assignee: Shenzhen Moting Medical Technology Co ltd
Current assignee: Shenzhen Moting Medical Technology Co ltd
Priority date: 2024-02-28
Filing date: 2024-02-28
Publication date: 2024-05-10

Abstract

The invention provides an ophthalmic measurement system, which comprises an OCT imaging module, wherein the OCT imaging module comprises an OCT light source, a reference arm module, an OCT sample arm module, an optical fiber coupler and a detector; the OCT sample arm module comprises an optical fiber light splitting device, an optical path scanning device, an optical path of an OCT sample arm of a posterior segment and an optical path of an OCT sample arm of an anterior segment, wherein the optical fiber light splitting device, the optical path scanning device and the optical path of the OCT sample arm of the posterior segment form the OCT sample arm module of the posterior segment, the optical path scanning device and the optical path of the OCT sample arm of the anterior segment form the OCT sample arm module of the anterior segment, and rear-segment detection light and front-segment detection light are split by the optical fiber light splitting device and respectively enter the optical path of the OCT sample arm of the posterior segment and the optical path of the OCT sample arm of the anterior segment after being reflected by different areas of the optical path scanning device, so that quick, accurate and high-degree-of-freedom ophthalmic measurement is realized.

Description

Ophthalmic measurement system

Technical Field

The invention relates to the technical field of ophthalmic measurement, in particular to an ophthalmic measurement system.

Background

Nowadays, more and more old people suffering from cataract eye diseases are transplanted with artificial lenses, and the artificial lenses are an effective scheme for treating cataract widely used at present. However, the parameters required for calculation of the intraocular lens are more demanding, such as cornea anterior and posterior surface curvature, cornea thickness, anterior chamber depth, lens thickness, lens anterior and posterior surface curvature, eye axis length, white-to-white distance, pupil diameter, etc. The measured parameters are more, but a plurality of medical devices are often needed to detect the measured parameters, so that the complete data can be obtained. Thus, if one device can be realized, the medical device can obtain the data, and for the detection of a patient, the convenience of measurement can be improved, and the accuracy of measurement can be improved.

Optical coherence tomography (OCT, optical Coherence Tomography) is an emerging optical imaging technique, and compared with the traditional clinical imaging means, the Optical Coherence Tomography (OCT) has the advantages of high resolution, high imaging speed, no radiation damage, moderate price, compact structure and the like, and is an important potential tool for basic medical research and clinical diagnosis application. Currently, among a variety of ophthalmic apparatuses using optical instruments, OCT apparatuses for ophthalmic examination and treatment have become an ophthalmic apparatus indispensable for diagnosis of ophthalmic diseases.

The prior art adopts a time domain tomography technology to measure the axial length, and has low speed and low measurement accuracy.

Patent document 200710020707.9 discloses a measurement method for measuring the eye axial length by OCT. Although this method can achieve measurement of the eye axis length of the human eye and various animal living bodies, the method has the following two disadvantages: 1, a moving probe of a stepping motor is adopted to realize the adjustment of the optical path, thereby realizing the imaging of cornea and fundus. The motor needs a certain time to move forwards and backwards, the front section and the rear section can not be switched rapidly and imaged in real time, and the eyes of the measured object shake, so that the length of the measured eye axis is inaccurate, and the error is large; 2. because of the different structures of cornea and fundus, the same probe cannot be focused at both positions, resulting in poor imaging quality, which is an unavoidable disadvantage of this approach.

The prior patent ' an ophthalmic optical coherence tomography system ' has the application number 201290000031.1 ' and adopts a plurality of switching mechanisms, so that the instrument cost is higher.

The prior patent ' an OCT system and method for measuring an optical path value of an eye axis ' application number 201410214827.2 ' introduces a cornea position alignment technique without switching anterior and posterior segments, but without anterior segment measurement function, and a cornea curvature measurement function (or not mentioned). The cornea is measured an additional time. Rapid diagnosis of the patient cannot be achieved.

The prior patents "ophthalmic measurement system and method," application number 201810130278.9 "and" ophthalmic measurement system, "application number 201910116857.2". The scanning device needs to scan and switch, and a certain time interval exists between front and back section measurement. And limited by the multipurpose use of the scanning device, the degree of freedom of the system light path design is not high enough.

The prior art patent "an OCT-based ocular axis measurement method and apparatus, application number 202110916582.8", uses a beam splitter 10 to split the sample arm light and the reference arm light (see paragraph 0074). It can't carry out the optical path according to the different eye axial length of people's eye in anterior and posterior festival and adjust. In addition, after the light emitted by the SLD light source 1 is split by the optical fiber coupler 2, the first OCT light beam and the second OCT light beam are generated by the first optical fiber collimating lens 3 and the second optical fiber collimating lens 4 and respectively enter the left side and the right side of the rotation shaft of the scanning vibrating lens 15, and the layout of the optical path structure can also be seen that the first OCT light beam and the second OCT light beam need to be distributed by adopting the left side and the right side of the rotation shaft of the scanning vibrating lens 15, but the structural distribution not only increases the lens width of the scanning vibrating lens 15, thereby reducing the vibration speed, but also introduces doppler frequency shift, thereby weakening the imaging signal intensity.

Disclosure of Invention

The invention aims to provide an ophthalmic measurement system, which can solve the problems of low switching speed, low measurement precision and insufficient degree of freedom of the front and rear section measurement in the existing ophthalmic measurement technology.

In order to achieve the above purpose, the present invention adopts the following technical scheme:

The OCT imaging module comprises an OCT light source, a reference arm module, an OCT sample arm module, an optical fiber coupler and a detector, wherein the OCT sample arm module comprises an optical fiber light splitting device, an optical path scanning device, an OCT sample arm optical path of a posterior segment of the eye and an OCT sample arm optical path of a anterior segment of the eye, the optical fiber light splitting device, the optical path scanning device and the OCT sample arm optical path of the posterior segment of the eye form the OCT sample arm module, the optical fiber light splitting device, the optical path scanning device and the OCT sample arm optical path of the anterior segment of the eye form the OCT sample arm module of the anterior segment of the eye, and posterior segment detection light and anterior segment detection light are split by the optical fiber light splitting device and then respectively enter the OCT sample arm optical path of the posterior segment of the eye and the OCT sample arm optical path of the anterior segment of the eye after being reflected by different areas of the optical path scanning device.

In some embodiments, the optical fiber splitting device adopts an optical switch or an optical fiber coupler or an optical filter or a wavelength division multiplexer to split the rear section detection light and the front section detection light.

In some embodiments, the optical path scanning device includes a single-surface reflective scanning lens, when the scanning lens rotates, light incident on the scanning lens is folded to scan, the back section detection light and the front section detection light are both incident on a rotation axis of the scanning lens, and along the rotation axis direction, the back section detection light and the front section detection light are spatially separated, so as to respectively enter the optical path of the posterior section OCT sample arm and the optical path of the anterior section OCT sample arm.

In some embodiments, the optical path scanning device includes a scanning lens with two reflection surfaces, when the scanning lens rotates, light incident on the scanning lens is folded to scan, the back section detection light and the front section detection light are respectively incident on the back surface and the front surface of the scanning lens, and after reflection, the light enters the optical path of the OCT sample arm of the posterior segment and the optical path of the OCT sample arm of the anterior segment respectively.

In some embodiments, the optical path of the post-ocular segment OCT sample arm sequentially includes a first post-ocular segment OCT optical path mirror, a post-ocular segment and gaze spectroscope, a diopter adjustment device, a third post-ocular segment OCT optical path mirror, a front post-ocular segment OCT spectroscope, a front spectroscope, and an eye objective lens, where the post-ocular segment probe light is reflected by the optical path scanning device, reflected by the first post-ocular segment OCT optical path mirror, reflected by the post-ocular segment and gaze spectroscope, reflected by the third post-ocular segment OCT optical path mirror and the front post-ocular segment OCT spectroscope, reflected by the front spectroscope to the eye objective lens, and finally converged by the eye of the human eye to the fundus.

In some embodiments, the optical path of the post-ocular segment OCT sample arm sequentially includes a first post-ocular segment OCT optical path mirror, a second post-ocular segment OCT optical path mirror, a post-ocular segment and fixation spectroscope, a refractive adjustment device, a front post-ocular segment OCT spectroscope, a front spectroscope, and an objective lens, wherein the post-ocular segment probe light is reflected by the optical path scanning device, reflected by the first post-ocular segment OCT optical path mirror and the second post-ocular segment OCT optical path mirror, reflected by the post-ocular segment and fixation spectroscope, passed through the refractive adjustment device, reflected by the front post-ocular segment OCT spectroscope, reflected by the front post-ocular spectroscope, and finally converged by the eye to the eye fundus of the human eye; the second back section OCT optical path reflecting mirror, the back eye section and the fixation spectroscope are integrally arranged to be translatable, so that the optical path length of the optical path of the back eye section OCT sample arm is adjustable.

In some embodiments, the optical path of the optical sample arm for the OCT of the posterior segment of the eye includes, in order, a posterior segment of the eye and a gaze spectroscope, a refractive adjustment device, a third posterior segment OCT optical path mirror, a front and a posterior segment OCT spectroscope, a front spectroscope, and an objective lens, and the posterior segment probe light is reflected by the optical path scanning device, reflected by the posterior segment of the eye and the gaze spectroscope, passes through the refractive adjustment device, reflected by the third posterior segment OCT optical path mirror and the front and the posterior segment OCT spectroscope, reflected by the front spectroscope, and then reflected by the front spectroscope to the objective lens, and finally converged to the fundus of the eye.

In some embodiments, a back section OCT optical fiber collimating lens is further disposed between the optical fiber splitting device and the optical path scanning device, and the back section OCT optical fiber collimating lens and the back section OCT sample arm optical fiber head are disposed to be translatable integrally along a main optical axis of the back section OCT optical fiber collimating lens, so that an optical path length of an optical path of the back section OCT sample arm is adjustable.

In some embodiments, the optical path of the anterior segment OCT sample arm includes a first lens, a third lens, an anterior-posterior segment OCT beam splitter, a front beam splitter, and an objective lens, and the anterior segment probe light is reflected by the optical path scanning device, sequentially transmitted through the first lens, the third lens, and the anterior-posterior segment OCT beam splitter, reflected by the front beam splitter to the objective lens, and finally converged by the human eye to the anterior segment of the human eye.

In some embodiments, a front section OCT fiber collimator is further disposed between the fiber optic splitting device and the optical path scanning device.

In some embodiments, a fixation optical module is further included, the fixation optical module including a fixation light source for providing a fixation mark for fixation of the eye of the person under examination.

In some embodiments, the eye anterior segment imaging module further comprises an illumination light source and an imaging device, wherein the illumination light source is used for irradiating light emitted to the eye anterior chamber of the detected human eye, reflecting through the tissue of the eye anterior chamber and finally imaging by the imaging device.

The invention has the following beneficial effects:

According to the invention, the optical fiber beam splitting device is matched with the OCT sample arm light path of the posterior segment and the OCT sample arm light path of the anterior segment of the eye, which are arranged by the OCT sample arm module, so that the rapid and accurate switching and the accurate measurement of the anterior segment and the posterior segment are realized by fewer moving mechanisms, and the anterior segment and the posterior segment can be measured simultaneously. Specifically, important parameters of human eye structures such as retina thickness and the like are obtained through an OCT sample arm module of the posterior segment of the eye; OCT images of the front and back surfaces of the cornea and the crystalline lens are obtained through an OCT sample arm module of the anterior segment of the eye, so that important parameters of human eye structures such as the curvature of the front and back surfaces of the cornea, the thickness of the cornea, the depth of the anterior chamber, the thickness of the crystalline lens, the curvature of the front and back surfaces of the crystalline lens and the like can be obtained; the eye structure important parameters such as the eye axial length can be obtained by matching the eye anterior segment OCT sample arm module with the eye posterior segment OCT sample arm module; important parameters of human eye structures such as white-to-white distance, pupil diameter and the like are obtained through the anterior ocular segment camera module, so that integral measurement is realized, and the measurement speed is improved.

According to the technical scheme, the rapid switching scanning or simultaneous scanning of the front section and the rear section can be realized, the rapid OCT imaging of different depths of different parts of the human eye is realized, the detection range of the imaging of the front section and the rear section of the OCT system is improved, the switching system is stable, the positioning is accurate, the signal to noise ratio of the system is not influenced, the scanning of tens of images can be realized in almost quasi-real time per second, the speed is high, and the influence of irregular movement of the human eye can be avoided. The human eye axial length can be accurately measured. Because the light beams can be focused at different positions respectively, OCT imaging of different positions with high quality can be realized for eyes with different eyesight, and the transverse resolution is higher.

In general, the invention not only realizes the rapid and stable switching of the measuring light paths of the front section and the rear section, but also realizes the accurate scanning of the front section and the rear section, and can simultaneously measure the front section and the rear section by utilizing the measuring light paths of the front section and the rear section, thereby being capable of rapidly and accurately obtaining the OCT images of the front section and the rear section, the optical path adjustment quantity and other parameters, thereby obtaining a plurality of optical parameters of human eyes.

In some embodiments of the invention, the fixation light source of the fixation optical module and the optical path of the OCT sample arm of the posterior segment of the eye share the refraction adjusting device, so that the moving part of the fixation light source is reduced, the confocal between the fixation light source and the optical path of the OCT of the posterior segment of the eye is realized, and the fixation of the eye to be measured and the acquisition of the fundus OCT image are facilitated.

Other advantages of embodiments of the present invention are further described below.

Drawings

FIG. 1 is a schematic diagram of an ophthalmic measurement system of example 1 of the present invention;

FIG. 2 is a schematic diagram of an ophthalmic measurement system of example 2 of the present invention;

Fig. 3 is a schematic diagram of an ophthalmic measurement system of example 2 of the present invention.

The reference numerals are as follows:

The OCT optical system comprises an OCT light source 1101, a fiber coupler 1103, a reference arm module 1120, a detector 1141, a fiber splitting device 1105, a computer 1143, a third back-section OCT light path reflecting mirror 1306, a front-section OCT light path reflecting mirror 1307, a front-section OCT light path reflecting mirror 1309, an objective lens 1311, a first lens 1503, a third lens 1509, a fifth lens 1703, an illumination light source 1901, a seventh lens 1905, an imaging device 1911, a back-section OCT fiber collimating mirror 11073, a second back-section OCT light path reflecting mirror 2302, a main optical axis L1 and a human eye E;

Rear-section OCT optical fiber collimator 11073, 31073, front-section OCT optical fiber collimator 11075, 31075, scanning lenses 11091, 31091, optical path scanning devices 1109, 3109, fixation light sources 1701, 2701, posterior and fixation beamsplitters 1303, 2303, refraction adjustment devices 1305, 2305, fifth lenses 1703, 2703, first rear-section OCT optical path mirrors 1301, 2301, posterior and fixation beamsplitters 1303, 2303.

Detailed Description

The following describes embodiments of the present invention in detail. It should be emphasized that the following description is merely exemplary in nature and is in no way intended to limit the scope of the invention or its applications.

It will be understood that when an element is referred to as being "mounted" or "disposed" on another element, it can be directly on the other element or be indirectly on the other element. When an element is referred to as being "connected to" another element, it can be directly connected to the other element or be indirectly connected to the other element. In addition, the connection may be for both a fixing action and a coupling or communication action.

It is to be understood that the terms "length," "width," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," and the like are merely for convenience in describing embodiments of the invention and to simplify the description by referring to the figures, rather than to indicate or imply that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and thus are not to be construed as limiting the invention.

Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In the description of the embodiments of the present invention, the meaning of "plurality" is two or more, unless explicitly defined otherwise.

The OCT imaging of different parts of the human eye adopts different scanning modes and focusing positions, so that the optical paths adopted by measurement are different. When fundus OCT imaging is carried out, the central line of a scanning beam is required to be converged on the pupil of human eyes, and OCT beams at any moment are required to be parallel to the human eyes; in the case of imaging the anterior segment of the eye, the scanning beam is required to be incident on the human eye with its center line parallel to the center line, and the OCT beam at any time is required to be focused on the anterior segment of the human eye. The aplanatic surface is positioned on the retina of a human eye during fundus OCT imaging, the aplanatic surface is positioned on the cornea during cornea imaging, the aplanatic surface is positioned on the front surface of the lens during lens front surface imaging, and the aplanatic surface is positioned on the rear surface of the lens during lens rear surface imaging.

The ophthalmic measurement system comprises an OCT imaging module, wherein the OCT imaging module comprises an OCT light source 1101, a reference arm module 1120, an OCT sample arm module, an optical fiber coupler 1103 and a detector 1141, wherein detection light emitted by the OCT light source 1101 is transmitted to the reference arm module 1120 after passing through the optical fiber coupler 1103, one part of detection light is transmitted to the optical fiber coupler 1103, the other part of detection light is input into the OCT sample arm module, and signal light returned to the optical fiber coupler 1103 from the OCT sample arm module interferes with reference light returned by the reference arm module 1120 and is detected by the detector 1141; the OCT sample arm module comprises an optical fiber beam splitting device 1105, an optical path scanning device, an optical path of an OCT sample arm for the posterior segment of the eye and an optical path of an OCT sample arm for the anterior segment of the eye, wherein the optical fiber beam splitting device 1105, the optical path scanning devices 1109 and 3109 and the optical path of the OCT sample arm for the posterior segment of the eye form the OCT sample arm module for the posterior segment of the eye, the optical path scanning devices 1109 and 3109 and the optical path of the OCT sample arm for the anterior segment of the eye form the OCT sample arm module for the anterior segment of the eye, and rear-segment detection light and front-segment detection light are split by the optical fiber beam splitting device 1105, reflected by different areas of the optical path scanning devices 1109 and 3109 and respectively enter the optical path of the OCT sample arm for the posterior segment of the eye and the OCT sample arm for the anterior segment of the eye.

The ophthalmology measuring system provided by the embodiment of the invention is mainly used for measuring relevant optical parameters of eyes of patients, is used for guiding the selection of artificial lens parameters and the examination of eyes of patients, can measure a plurality of relevant ophthalmology parameters such as the axial length, the cornea curvature, the anterior chamber depth, the white-to-white distance and the like of eyes, and can solve the detection of a plurality of optical parameters of eyes by matching with an optical fiber spectroscopic device, so that the measuring requirements of different parts are met, the accurate data of a plurality of important parameters of eyes can be obtained, and the clinical diagnosis requirements of doctors are met. The embodiment of the invention is beneficial to correction of OCT images of the front and rear surfaces of cornea and crystalline lens.

The embodiment of the invention is mainly based on the optical coherence tomography technology. The optical coherence tomography technology combines the rapid switching scanning of front and rear sections to realize the measurement of various optical parameters of human eyes such as human eye axial length, anterior chamber depth, crystal thickness, cornea thickness and the like.

According to the invention, the optical path scanning device is matched with the optical fiber beam splitting device, the optical path of the OCT sample arm of the anterior segment of the eye and the optical path of the OCT sample arm of the anterior segment of the eye, so that the rapid switching of the optical paths of the anterior segment and the posterior segment is realized, the scanning of the anterior segment and the posterior segment is realized, and a plurality of optical parameters of the eye are obtained by obtaining the OCT images of the anterior segment and the posterior segment, the optical path adjustment quantity and other parameters.

The invention can realize rapid switching scanning of front and rear sections, measurement of different depths of human eyes, rapid OCT imaging of different parts of human eyes, and improves the detection range (including front and rear section imaging) of an OCT system. Therefore, the axial length of human eyes can be accurately measured, on the other hand, the light beams can be respectively focused at different positions, high-quality OCT imaging of different positions can be realized for human eyes with different eyesight, and the transverse resolution is higher. The OCT system can rapidly acquire numerous parameter data of human eyes, such as cornea curvature, cornea thickness, anterior chamber depth, lens thickness, lens surface curvature, eye axial length, white-to-white distance, pupil diameter and the like, by rapidly switching front and rear sections, rapid switching of the front and rear sections is not needed, fewer movement mechanisms are provided, and the cost is low.

The system of the invention can acquire the front and back section images by one-time quick measurement, is beneficial to the operation of doctors, improves the diagnosis speed and improves the interaction experience of doctors and patients. In addition, the detection of a plurality of human eye key parameters such as cornea, anterior chamber depth, eye axial length, cornea curvature, white-to-white and the like can be realized by one-time measurement, and the method has a plurality of advantages such as cost, speed, precision, multifunction and the like.

The anterior ocular segment imaging optical path of the invention discards traditional fundus imaging optical paths (such as a color fundus camera, an LSLO, etc.), can be used for guiding doctors to operate instruments, and can be used for measuring pupil diameters and white-to-white distances. The invention does not need to adjust the optical path of the reference arm to realize OCT imaging of different parts.

In addition, the preferred embodiment of the invention can also carry out refraction compensation aiming at eyes with different vision so as to realize the imaging of eyes at different positions. The preferred embodiments of the present invention may also provide a light path for fixation of the human eye to satisfy the fixation of the left and right eyes. According to the optical fiber OCT shared diopter adjusting device for the eye posterior segment, disclosed by the preferred embodiment of the invention, the moving parts of the optical fiber OCT are reduced, the confocal effect of the optical fiber OCT is realized, and the optical fiber OCT is beneficial to the fixation of the eye to be measured and the acquisition of fundus OCT images.

Example 1

A schematic diagram of an ophthalmic measurement system of embodiment 1 of the present invention is fig. 1, comprising: OCT imaging module, fixation optical module and anterior segment of the eye camera module.

OCT imaging module

The OCT imaging module includes an OCT light source 1101, a fiber coupler 1103, a reference arm module 1120, a probe 1141, and an OCT sample arm module. After passing through the optical fiber coupler 1103, a part of detection light emitted by the OCT light source 1101 is transmitted to the reference arm module 1120 and then transmitted to the optical fiber coupler 1103, and the other part of detection light is input to the OCT sample arm module, and signal light returned from the OCT sample arm module to the optical fiber coupler 1103 interferes with reference light returned from the reference arm module 1120 and is detected by the detector 1141.

The OCT sample arm module comprises a posterior segment OCT sample arm module and an anterior segment OCT sample arm module, an optical fiber beam splitting device 1105 and an optical path scanning device 1109, and the optical path scanning device 1109 and the optical fiber beam splitting device 1105 are controlled by a computer 1143 to realize optical path switching, so that OCT imaging of different parts of human eyes is realized. The optical fiber beam splitting device 1105, the optical path scanning device 1109 and the optical path of the optical fiber OCT sample arm form an optical fiber OCT sample arm module of the back section, the optical fiber beam splitting device 1105, the optical path scanning device 1109 and the optical path of the optical fiber OCT sample arm form an optical fiber OCT sample arm module of the front section, and the back section detection light and the front section detection light are split by the optical fiber beam splitting device 1105, reflected by different areas of the optical path scanning device 1109 and respectively enter the optical path of the optical fiber OCT sample arm of the back section and the optical path of the optical fiber OCT sample arm of the front section.

The OCT imaging module optical path includes an OCT light source 1101, which is a weak coherent light source, and the probe light output by the OCT imaging module optical path provides light to the sample arm module and the reference arm module 1120 through the optical fiber coupler 1103, and a part of the probe light is transmitted to the reference arm module 1120 and then transmitted to the optical fiber coupler 1103, and another part of the probe light is input to the OCT sample arm module, and the signal light returned from the OCT sample arm module to the optical fiber coupler 1103 interferes with the reference light returned from the reference arm module 1120 and is detected by the detector 1141.

Specifically, the reference arm module 1120 has a known length that returns the reference light into the fiber coupler 1103. The OCT sample arm module provides light for the detected human eye E, the light returned by the signal light scattered by the sample through the sample arm and the reference arm module 1120 is interfered in the optical fiber coupler 1103, the interference light is detected by the detector 1141, and then the interference light is processed by the computer 1143, and finally the OCT image of the detected sample is displayed. The sample is scanned by the optical path scanning device 1109, and tomographic imaging of OCT is realized.

The computer 1143 is not a PC computer in a conventional sense, but is a circuit control and processing system capable of performing operations, control, storage, display, and other functions.

OCT sample arm module for posterior segment of eye

The eye posterior segment OCT sample arm module can obtain important parameters of human eye structures such as retina thickness, and the like, and comprises an optical fiber beam splitting device 1105, an optical path scanning device 1109 and an eye posterior segment OCT sample arm optical path.

For different eye axial lengths of eyes to be measured, a back section OCT optical fiber collimator 11073 is further disposed between the optical fiber spectroscopic device 1105 and the optical path scanning device 1109 in this embodiment 1, and a back section OCT sample arm optical fiber head (not shown) is integrally disposed along a main optical axis L1 of the back section OCT optical fiber collimator 11073 by using the back section OCT optical fiber collimator 11073, so that the optical path length of the optical path of the back section OCT sample arm is adjustable, so as to meet the requirement of measuring OCT images at different positions when measuring different eye axial lengths.

The optical path of the post-ocular OCT sample arm sequentially includes a first post-ocular OCT optical path mirror 1301, a post-ocular and fixation beam splitter 1303 (first beam splitter 1303), a refractive adjustment device 1305, a third post-ocular OCT optical path mirror 1306, a front post-ocular OCT beam splitter 1307 (third beam splitter 1307), a front beam splitter 1309 (fifth beam splitter 1309), and an objective lens 1311.

When performing posterior ocular segment OCT imaging, light from OCT light source 1101 enters the OCT sample arm module via fiber coupler 1103. After passing through the optical fiber splitting device 1105, the sample light enters the rear section OCT optical fiber collimator 11073 and is reflected by the scanning lens 11091. At this time, the optical path scanning device 1109 is controlled by the computer 1143, and the rear-section probe light is reflected by the optical path scanning device 1109, reflected by the first rear-section OCT optical path mirror 1301, reflected by the eye rear-section and gaze beam splitter 1303 (first beam splitter 1303), passed through the diopter adjusting device 1305, reflected by the third rear-section OCT optical path mirror 1306 and the front-section OCT beam splitter 1307 (third beam splitter 1307), reflected by the front-section beam splitter 1309 (fifth beam splitter 1309), reflected by the front-section OCT beam splitter 1307, and finally converged by the human eye E to the fundus to be measured. The detection light beam of the OCT imaging light path of the posterior segment of the eye meets the requirement that the central line of the scanning light beam is converged near the pupil of the human eye, and the OCT light beam is focused on the fundus of the human eye E at any moment.

The optical path scanning device 1109 of embodiment 1 of the present invention includes a single-surface reflective scanning lens, and the optical path scanning device 1109 drives the scanning lens 11091 to rotate, and when the scanning lens 11091 rotates, the light incident on the scanning lens 11091 is folded to perform scanning. In this embodiment, the back section detection light emitted from the back section OCT optical fiber collimator 11073 and the front section detection light emitted from the front section OCT optical fiber collimator 11075 are both incident on the rotation axis of the scan mirror 11091, but are spatially separated along the rotation axis direction, so that the back section detection light is reflected by the scan mirror 11091 and enters the optical path of the back section OCT sample arm, and the front section detection light is reflected by the scan mirror 11091 and enters the optical path of the front section OCT sample arm. By making the rear-section detection light and the front-section detection light incident on the rotation axis, the Doppler shift phenomenon caused by that the detection light is not incident on the axis is avoided.

The optical fiber beam splitting device 1105 adopts an optical switch or an optical fiber coupler or an optical filter or a wavelength division multiplexer to split the rear section detection light and the front section detection light, so that the front section detection light and the rear section detection light are emitted through different optical fibers. In contrast, the optical switch is adopted to perform front-back section measurement, the switching time is required, but the optical path switching speed is faster than that of the traditional galvanometer, and the optical fiber coupler and the wavelength division multiplexer can be adopted to image simultaneously, but the imaging quality is poorer than that of the optical switch. Wherein the different areas of the scanning device reflect, may be different areas of a single reflective surface, or the front and back sides of the scanning mirror. The front and back sides of the scanning lens are designed to reflect, so that the front and back sides of the scanning lens can be utilized, the size of the lens can be reduced, and the vibration speed and the scanning speed are improved. The optical path adjusting device also has different implementation schemes.

The back section detection light and the front section detection light are split by the optical fiber splitting device, reflected by different areas of the optical path scanning device and respectively enter the optical path of the OCT sample arm of the back section and the optical path of the OCT sample arm of the front section of the eye.

In some embodiments, optical fiber splitting device 1105 employs an optical switch. The optical switch is capable of selectively transmitting the probe light to the posterior segment OCT sample arm optical path or the anterior segment OCT sample arm optical path. When performing OCT imaging of the posterior segment of the eye, the OCT imaging device is controlled by the computer 1143, so that the sample light from the fiber coupler 1103 enters the optical path of the OCT sample arm of the posterior segment of the eye after passing through the fiber spectroscopic device 1105. When performing OCT imaging of the anterior segment of the eye, the OCT imaging device is controlled by the computer 1143, so that the sample light from the fiber coupler 1103 enters the optical path of the OCT sample arm of the anterior segment of the eye after passing through the fiber spectroscopic device 1105.

In other embodiments, the fiber optic splitter 1105 employs a fiber optic coupler 1103, and the splitting effect (split according to different light energy ratios) of the fiber optic coupler 1103 results in a decrease in signal-to-noise ratio of the OCT imaging of the posterior segment and the OCT imaging of the anterior segment, which affects the imaging effect of the OCT imaging of the anterior segment and the posterior segment. But the cost of the fiber coupler is much lower than that of the optical switch.

In still other embodiments, the optical fiber splitting device 1105 includes a filter, which may be a high-pass filter or a low-pass filter, or other filters that meet the requirements, or a wavelength division multiplexer, to sort the light of different wavelength bands, so that the light of different wavelength bands enters the optical path of the OCT sample arm of the posterior segment and the optical path of the OCT sample arm of the anterior segment of the eye.

The diopter adjustment device 1305 focuses for different eyes (with different diopters), and as shown in the above figure, the diopter adjustment device 1305 can translate along the main optical axis where it is located, so that the OCT light beam can be focused on the eye E to be measured. That is, the light beam is focused on the retina, so that the signal-to-noise ratio and the transverse resolution of OCT images can be effectively improved during retina measurement.

The first spectroscope 1303 can transmit the fixation light (wavelength 550 nm) emitted from the fixation light source 1701 in the fixation optical module; the OCT light source 1101 output light may be reflected.

In some embodiments, the front and back section OCT beam splitters 1307 (third beam splitter 1307) employ partial beam splitters (split at different light energy ratios) that partially reflect the back section detection light incident on the front and back section OCT beam splitters 1307 and partially transmit the front section detection light incident on the front and back section OCT beam splitters 1307.

In still other embodiments, the front and back section OCT beam splitters 1307 utilize high pass filters or low pass filters to sort light of different wavelength bands, thereby allowing the back section detection light incident on the front and back section OCT beam splitters 1307 to be totally reflected and the front section detection light incident on the front and back section OCT beam splitters 1307 to be totally transmitted.

The pre-beam splitter 1309 (fifth beam splitter 1309) can reflect the signal light emitted from the OCT light source 1101 and reflect the fixation light emitted from the fixation light source 1701 in the fixation optical module. But also transmits illumination light from the illumination light source 1901 in the anterior segment imaging module.

OCT sample arm module for anterior ocular segment

The anterior ocular segment OCT sample arm module includes an optical fiber spectroscopic device 1105, an optical path scanning device 1109, and an anterior ocular segment OCT sample arm optical path. OCT images of the front and back surfaces of the cornea and the crystalline lens can be obtained, so that important parameters of human eye structures such as the front and back surface curvature of the cornea, the thickness of the cornea, the depth of the anterior chamber, the thickness of the crystalline lens, the front and back surface curvature of the crystalline lens and the like can be obtained, and the important parameters of human eye structures such as the axial length of the eye and the like can be obtained by matching the OCT sample arm module of the anterior segment with the OCT sample arm module of the posterior segment of the eye.

A front section OCT optical fiber collimator 11075 is also provided between the optical fiber spectroscopic device and the optical path scanning device.

The anterior ocular segment OCT sample arm optical path includes a first lens 1503, a third lens 1509, an anterior posterior segment OCT beam splitter 1307 (third beam splitter 1307), a pre-beam splitter 1309 (fifth beam splitter 1309), and an objective lens 1311.

When performing anterior ocular segment OCT imaging, light from the OCT light source 1101 enters the OCT sample arm module via the fiber coupler 1103. After passing through the optical fiber splitting device 1105, the sample light enters the front section OCT optical fiber collimator 11075 and is reflected by the scanning lens 11091. At this time, the optical path scanning device 1109 is controlled by the computer 1143, and after the front section detection light is reflected by the optical path scanning device 1109, the front section detection light sequentially transmits the first lens 1503, the third lens 1509, the front-rear section OCT spectroscope 1307 (the third spectroscope 1307), and then is reflected by the front spectroscope 1309 (the fifth spectroscope 1309) to the objective lens 1311, and finally is converged to the front section of the human eye by the human eye E. The detection light beam of the OCT imaging light path system of the anterior ocular segment meets the requirement that the central line of the scanning light beam is parallel to the main optical axis L1 of the light path system and is incident to the human eye, and the OCT light beam is focused on the anterior ocular segment at any moment.

When the front and back surfaces of the cornea and the crystalline lens are measured, the OCT light beam is focused on the middle area of the anterior segment of the eye, and the signal to noise ratio and the transverse resolution of OCT images can be effectively improved when the front and back surfaces of the cornea and the crystalline lens are measured. And the scanning beam central line is parallel to the main optical axis L1 of the optical path system and is incident to the human eye, which is favorable for the refraction correction of the front and back surfaces of the cornea and the crystalline lens, thereby obtaining accurate curvatures of the front and back surfaces of the cornea and the crystalline lens.

The ophthalmic measurement system of embodiment 1 of the present invention further includes a fixation optical module including a fixation light source 1701 for fixation of the subject's eye E (internal fixation). Light from the fixation light source 1701 passes through the fifth lens 1703, passes through the posterior segment of the eye and the gaze spectroscope (first spectroscope) 1303, adjusts diopter by the diopter adjusting device 1305, reflects by the third posterior segment OCT optical path reflecting mirror 1306 and the anterior and posterior segment OCT spectroscope 1307 (third spectroscope 1307), and reflects to the eye objective 1311 by the pre-spectroscope 1309 (fifth spectroscope 1309), and the light passes through the eye objective 1311 and then enters the eye E to be inspected. Finally, the internal fixation index is projected onto the fundus of the eye to be inspected.

The fixation light source 1701 may employ a single point LED, or an LCD screen, an OLED screen, or an LED array screen, or the like.

When fundus OCT imaging is carried out, when different eyes observe the fixation point, the definition degree of the fixation point is different, which causes discomfort to a tested person in fixation, and is inconvenient for fixation and fixation of the tested eye. Since the fundus OCT optical path is adjusted by the diopter adjuster 1305, it can be focused on the fundus retina E. Since the optical OCT optical path and the fixation optical path are shared by the diopter adjustment device 1305, the fixation target can be seen clearly for different eyes.

The ophthalmologic measurement system of the embodiment 1 of the invention further comprises an anterior ocular segment photographing module, which can obtain important parameters of human eye structures such as white-to-white distance, pupil diameter and the like, and comprises an illumination light source 1901 and a photographing device, wherein the photographing device is a photographing device 1911, the illumination light source is used for irradiating light emitted by the illumination light source to an anterior ocular segment of a detected human eye, reflected by tissue of the anterior ocular segment, and finally photographed by the photographing device, and can be used for photographing and previewing anterior ocular segments so as to guide a doctor to operate an instrument, and a probe light path is aligned to the human eye to be detected.

The illumination light source 1901, which in the present embodiment is 940nm infrared light, irradiates the anterior chamber of the eye E to be inspected, and reflects the light through the anterior chamber tissue. The reflected light passes through the objective lens 1311, the front beam splitter 1309 (fifth beam splitter 1309), the seventh lens 1905, and the ninth lens 1909, and is finally captured by the imaging device 1911.

The examinee uses a chin rest (not shown) to fix the examinee's head and to fix the eye of the examinee by fixing the fixation mark of the eye fixation system. Then, the detector controls the movement of the chin rest apparatus, the probe, and the like by the lever while observing the display screen of the computer 1143 so that the anterior ocular segment of the eye E to be inspected enters the imaging device 1911, and an anterior ocular segment image is presented in the display screen of the computer 1143.

Example 2

Example 2 differs from example 1 mainly in the posterior segment OCT sample arm module and fixation optics module, as shown in fig. 2.

Wherein the posterior ocular segment OCT sample arm module differs from example 1 primarily in the posterior ocular segment OCT sample arm optical path.

OCT sample arm module for posterior segment of eye

The posterior segment OCT sample arm module comprises an optical fiber beam splitting device 1105, an optical path scanning device 1109 and an optical path of the posterior segment OCT sample arm.

A back section OCT optical fiber collimator 11073 is further disposed between the optical fiber spectroscopic device 1105 and the optical path scanning device 1109, and the back section OCT optical fiber collimator 11073 is integrally disposed along the main optical axis L1 of the back section OCT optical fiber collimator 11073 together with the optical fiber head of the back section OCT sample arm, so that the optical path length of the optical path of the back section OCT sample arm can be adjusted.

The posterior segment OCT sample arm optical path sequentially includes a first posterior segment OCT optical path mirror 2301, a second posterior segment OCT optical path mirror 2302, a posterior segment and fixation beam splitter 2303, a refractive adjustment device 2305, an anterior and posterior segment OCT beam splitter 1307 (third beam splitter 1307), a pre-beam splitter 1309 (fifth beam splitter 1309), and an objective lens 1311.

When performing posterior ocular segment OCT imaging, probe light from OCT light source 1101 enters the OCT sample arm module via fiber coupler 1103. After the detection light is split by the optical fiber splitting device 1105, the detection light enters the rear section OCT optical fiber collimator 11073, and the rear section detection light is reflected by the scanning lens 11091. At this time, the optical path scanning device 1109 is controlled by the computer 1143, and the rear-section probe light is reflected by the optical path scanning device 1109, reflected by the first rear-section OCT optical path mirror 2301 and the second rear-section OCT optical path mirror 2302, reflected by the rear-eye section and the gaze spectroscope 2303, reflected by the diopter adjustment device 2305, reflected by the front-back section OCT spectroscope 1307 (the third spectroscope 1307), reflected by the front-stage spectroscope 1309 (the fifth spectroscope 1309), and finally converged by the human eye E to the fundus of the eye to be tested. The detection light beam of the OCT imaging light path system of the posterior segment of the eye meets the requirement that the central line of the scanning light beam is converged near the pupil of the human eye, and the OCT light beam is focused on the fundus of the human eye E at any moment.

The optical path scanning device 1109 of embodiment 2 of the present invention includes a single-surface reflective scanning lens, and the optical path scanning device 1109 drives the scanning lens 11091 to rotate, and when the scanning lens 11091 rotates, the light incident on the scanning lens 11091 is folded to perform scanning. In this embodiment 2, the back section detection light exiting the back section OCT optical fiber collimator 11073 and the front section detection light exiting the front section OCT optical fiber collimator 11075 are both incident on the rotation axis of the scan mirror 11091, but are spatially separated along the rotation axis direction, so that the back section detection light is reflected by the scan mirror 11091 and enters the optical path of the back section OCT sample arm, and the front section detection light is reflected by the scan mirror 11091 and enters the optical path of the front section OCT sample arm.

The optical fiber beam splitting device 1105 adopts an optical switch or an optical fiber coupler or an optical filter or a wavelength division multiplexer to split the rear section detection light and the front section detection light, so that the front section detection light and the rear section detection light are emitted through different optical fibers. Wherein the different areas of the scanning device reflect, may be different areas of a single reflective surface, or the front and back sides of the scanning mirror. The optical path adjusting device also has different implementation schemes.

In some embodiments, optical fiber splitting device 1105 employs an optical switch. The optical switch is capable of selectively transmitting the probe light to the posterior segment OCT sample arm optical path or the anterior segment OCT sample arm optical path. When performing OCT imaging of the posterior segment of the eye, the OCT imaging device is controlled by the computer 1143, so that the sample light from the fiber coupler 1103 enters the optical path of the OCT sample arm of the posterior segment of the eye after passing through the optical switch 1105. When performing the anterior ocular segment OCT imaging, it is controlled by the computer 1143, so that the sample light from the fiber coupler 1103 enters the anterior ocular segment OCT sample arm optical path after passing through the optical switch 1105.

The diopter adjustment device 2305 focuses on different eyes (with different diopters), and as shown in the above figure, the diopter adjustment device 2305 can translate along the main optical axis where it is located, so that the OCT beam can be focused on the fundus of the eye E to be measured. That is, the light beam is focused on the retina, so that the signal-to-noise ratio and the transverse resolution of OCT images can be effectively improved during retina measurement.

The posterior segment and fixation beam splitter 2303 may transmit fixation light (550 nm wavelength) from fixation light source 2701 in the fixation optical module; the OCT light source 1101 output light may be reflected.

The pre-beam splitter 1309 (fifth beam splitter 1309) can reflect the signal light emitted from the OCT light source 1101 and reflect the fixation light emitted from the fixation light source 2701 in the fixation optical module. But also transmits illumination light from the illumination light source 1901 in the anterior segment imaging module.

For different eye axial lengths of eyes to be measured, in this embodiment, the whole body of the optical fiber head (not shown) of the optical fiber sample arm of the back section OCT is translated along the main optical axis L1 of the optical fiber collimator 11073 of the back section OCT by using the optical fiber collimator 11073 of the back section OCT, so as to change the optical path length of the optical path of the optical fiber sample arm of the back section OCT, so as to meet the requirement of measuring OCT images at different positions when measuring different eye axial lengths.

In other embodiments, the optical path length of the optical path of the OCT sample arm of the posterior segment of the eye can be changed by using the integral translation of the second posterior segment OCT optical path mirror 2302 and the posterior segment of the eye and gaze spectroscope 2303, so as to meet the requirement of measuring OCT images at different positions when measuring different axial lengths of the eye.

The fixation optical module of this embodiment 2 is also different from embodiment 1.

Specifically, the fixation optical module of embodiment 2 of the present invention includes a fixation light source 2701 for fixation of a fixation target (internal fixation target) of the eye E. Light from the fixation light source 2701 passes through the fifth lens 2703, passes through the posterior segment of the eye and the fixation beam splitter (first beam splitter) 2303, adjusts diopter by the diopter adjustment device 2305, reflects by the anterior-posterior segment OCT beam splitter 1307 (third beam splitter 1307), and reflects by the anterior beam splitter 1309 (fifth beam splitter 1309) to the eye objective 1311, and the light is incident on the eye to be inspected E through the eye objective 1311. Finally, the internal fixation index is projected onto the fundus of the eye to be inspected.

The fixation light source 2701 may employ a single point LED, or an LCD screen, an OLED screen, or an LED array screen, or the like.

When fundus OCT imaging is carried out, when different eyes observe the fixation point, the definition degree of the fixation point is different, which causes discomfort to a tested person in fixation, and is inconvenient for fixation and fixation of the tested eye. Since the fundus OCT optical path is adjusted by the diopter adjustment device 2305, it can be focused on the fundus retina E. Because the OCT optical path and the fixation optical path of the posterior segment of the eye share the diopter adjusting device 2305, the fixation target can be seen clearly for different eyes.

Example 3

Example 3 differs from example 1 mainly in the posterior segment OCT sample arm module and the anterior segment OCT sample arm module, and includes: OCT imaging module, posterior segment OCT sample arm module, anterior segment OCT sample arm module, fixation optical module and anterior segment camera module

OCT sample arm module for posterior segment of eye

The posterior segment OCT sample arm module comprises an optical fiber beam splitting device 1105, an optical path scanning device 3109 and an optical path of the posterior segment OCT sample arm.

For different eye axial lengths of eyes to be measured, a back section OCT optical fiber collimator 31073 is further disposed between the optical fiber spectroscopic device 1105 and the optical path scanning device 3109 in this embodiment 1, and a back section OCT sample arm optical fiber head (not shown) connected with the back section OCT optical fiber collimator 31073 is configured to be translatable integrally along a main optical axis of the back section OCT optical fiber collimator 31073, so that an optical path length of an optical path of the back section OCT sample arm is adjustable, so as to meet a requirement of measuring OCT images at different positions when measuring different eye axial lengths.

The optical path of the post-ocular section OCT sample arm sequentially includes a post-ocular section and gaze beamsplitter 1303 (first beamsplitter 1303), a refractive adjustment device 1305, a third post-ocular section OCT optical path reflecting mirror 1306, a front-posterior section OCT beamsplitter 1307 (third beamsplitter 1307), a front-mounted beamsplitter 1309 (fifth beamsplitter 1309), and an objective lens 1311.

When performing posterior ocular segment OCT imaging, probe light from OCT light source 1101 enters the OCT sample arm module via fiber coupler 1103. After passing through the optical fiber spectroscopic device 1105, the probe light enters the rear-section OCT optical fiber collimator 31073 and is reflected by the back surface of the scanning mirror 31091. At this time, the optical path scanning device 3109 is controlled by the computer 1143, and the rear-section detection light is reflected by the optical path scanning device 3109, reflected by the eye rear-section and gaze beam splitter 1303 (first beam splitter 1303), passes through the diopter adjusting device 1305, reflected by the third rear-section OCT optical path reflecting mirror 1306 and the front-section OCT beam splitter 1307 (third beam splitter 1307), reflected by the front-section beam splitter 1309 (fifth beam splitter 1309) to the eye-receiving objective lens 1311, and finally converged to the fundus of the eye to be measured by the human eye E. The detection light beam of the OCT imaging light path of the posterior segment of the eye meets the requirement that the central line of the scanning light beam is converged near the pupil of the human eye, and the OCT light beam is focused on the fundus of the human eye E at any moment.

The optical path scanning device 3109 includes a scanning mirror that reflects on both sides, and is capable of driving the scanning mirror 31091 to rotate, and when the scanning mirror 31091 rotates, light incident on the scanning mirror is folded to perform scanning. In this embodiment 3, the back-section detection light of the back-section OCT optical fiber collimator 31073 and the front-section detection light of the front-section OCT optical fiber collimator 31075 are emitted to the back surface and the front surface of the scanning mirror 31091, respectively, so that the back-section detection light is reflected by the scanning mirror 31091 and enters the optical path of the back-section OCT sample arm, and the front-section detection light is reflected by the scanning mirror 31091 and enters the optical path of the front-section OCT sample arm. The front and back sides of the scanning lens can be utilized, so that the size of the lens can be reduced, and the vibration speed and the scanning speed are improved.

The optical fiber beam splitting device 1105 adopts an optical switch or an optical fiber coupler 1103 or an optical filter or a wavelength division multiplexer to split the rear section detection light and the front section detection light, so that the front section detection light and the rear section detection light are emitted through different optical fibers. Wherein the different areas of the scanning device reflect, may be different areas of a single reflective surface, or the front and back sides of the scanning mirror. The optical path adjusting device also has different implementation schemes.

The back section detection light and the front section detection light are split by the optical fiber splitting device, reflected by different areas of the optical path scanning device 3109 and respectively enter the optical path of the OCT sample arm of the back section of the eye and the optical path of the OCT sample arm of the front section of the eye.

In other embodiments, the fiber optic splitter 1105 employs a fiber optic coupler 1103, and the splitting effect (split according to different light energy ratios) of the fiber optic coupler 1103 results in a decrease in signal-to-noise ratio of the OCT imaging of the posterior segment and the OCT imaging of the anterior segment, which affects the imaging effect of the OCT imaging of the anterior segment and the posterior segment. The fiber coupler 1103 is much less costly than an optical switch.

The diopter adjustment device 1305 focuses for different eyes (with different diopters), and as shown in the above figure, the diopter adjustment device 1305 can translate along the main optical axis where it is located, so that the OCT light beam can be focused on the fundus of the eye E to be tested. That is, the light beam is focused on the retina, so that the signal-to-noise ratio and the transverse resolution of OCT images can be effectively improved during retina measurement.

Aiming at the difference of different eye axial lengths of eyes to be measured, in the embodiment, the whole body of the rear section OCT sample arm optical fiber head (not shown) is translated along the main optical axis L1 of the rear section OCT optical fiber collimating lens 31073 by utilizing the rear section OCT optical fiber collimating lens 31073, so that the optical path length of an optical path of the rear section OCT sample arm is changed, and the requirement of measuring OCT images at different positions when measuring different eye axial lengths is met.

OCT sample arm module for anterior ocular segment

The anterior ocular segment OCT sample arm module includes an optical fiber spectroscopic device 1105, an optical path scanning device 3109, and an anterior ocular segment OCT sample arm optical path.

A front-section OCT optical fiber collimator 31075 is further provided between the optical fiber spectroscopic device 1105 and the optical path scanning device 3109.

When performing anterior ocular segment OCT imaging, light from the OCT light source 1101 enters the sample arm via the fiber coupler 1103. After passing through the optical fiber splitting device 1105, the sample light enters the front section OCT optical fiber collimator 31075 and is reflected by the front surface of the scanning lens 31091. At this time, the optical path scanning device 3109 is controlled by the computer 1143, after the light beam is reflected by the optical path scanning device 3109, the light beam transmits through the first lens 1503 and the third lens 1509, then transmits through the front and rear section OCT beam splitter 1307 (the third beam splitter 1307), then reflects through the front beam splitter 1309 (the fifth beam splitter 1309) to the objective lens 1311, and finally converges through the human eye E to the front section of the human eye. The detection light beam of the OCT imaging light path system of the anterior ocular segment meets the requirement that the central line of the scanning light beam is parallel to the main optical axis L1 of the light path system and is incident to the human eye, and the OCT light beam is focused on the anterior ocular segment at any moment.

The solid-state optical module and the anterior ocular segment imaging module are the same as in embodiment 1.

The foregoing is a further detailed description of the invention in connection with specific/preferred embodiments, and it is not intended that the invention be limited to such description. It will be apparent to those skilled in the art that several alternatives or modifications can be made to the described embodiments without departing from the spirit of the invention, and these alternatives or modifications should be considered to be within the scope of the invention. In the description of the present specification, reference to the terms "one embodiment," "some embodiments," "preferred embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, schematic representations of the above terms are not necessarily directed to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Those skilled in the art may combine and combine the features of the different embodiments or examples described in this specification and of the different embodiments or examples without contradiction. Although embodiments of the present invention and their advantages have been described in detail, it should be understood that various changes, substitutions and alterations can be made herein without departing from the scope of the invention as defined by the appended claims.

Claims

1. The OCT imaging module comprises an OCT light source, a reference arm module, an OCT sample arm module, an optical fiber coupler and a detector, and is characterized in that the OCT sample arm module comprises an optical fiber beam splitting device, an optical path scanning device, an optical path of an OCT sample arm of a posterior segment of the eye and an optical path of an OCT sample arm of an anterior segment of the eye, the optical fiber beam splitting device, the optical path scanning device and the optical path of the OCT sample arm of the posterior segment of the eye form the OCT sample arm module of the posterior segment of the eye, the optical path scanning device and the optical path of the OCT sample arm of the anterior segment of the eye form the OCT sample arm module of the anterior segment of the eye, and posterior segment detection light and anterior segment detection light are split by the optical fiber beam splitting device and respectively enter the OCT sample arm optical path of the posterior segment of the eye and the OCT sample arm optical path of the anterior segment of the eye after being reflected by different areas of the optical path scanning device.

2. The ophthalmic measurement system of claim 1, wherein the fiber optic spectroscopy apparatus employs an optical switch or fiber coupler or filter or wavelength division multiplexer to effect the spectroscopy of the posterior detection light and the anterior detection light.

3. The ophthalmic measurement system of claim 1, wherein the optical path scanning device comprises a single-sided reflective scanning mirror that rotates to fold light incident on the scanning mirror for scanning, wherein the posterior detection light and the anterior detection light are both incident on a rotational axis of the scanning mirror, and wherein the posterior detection light and the anterior detection light are spatially separated along the rotational axis direction so as to enter the posterior eye OCT sample arm optical path and the anterior eye OCT sample arm optical path, respectively.

4. The ophthalmic measurement system of claim 1, wherein the optical path scanning device comprises a scanning lens with two-sided reflection, the scanning lens rotates to cause light incident on the scanning lens to be folded for scanning, the posterior segment detection light and the anterior segment detection light respectively enter the posterior segment OCT sample arm optical path and the anterior segment OCT sample arm optical path after being reflected respectively on the back surface and the front surface of the scanning lens.

5. The ophthalmic measurement system of any one of claims 1 to 4, wherein the posterior segment OCT sample arm optical path sequentially comprises a first posterior segment OCT optical path mirror, a posterior segment and fixation beam splitter, a refractive adjustment device, a third posterior segment OCT optical path mirror, a anterior-posterior segment OCT beam splitter, a front beam splitter, and an objective lens, wherein the posterior segment probe light is reflected by the optical path scanning device, reflected by the first posterior segment OCT optical path mirror, reflected by the posterior segment and fixation beam splitter, reflected by the refractive adjustment device, reflected by the third posterior segment OCT optical path mirror and the anterior-posterior segment OCT beam splitter, reflected by the front beam splitter, and finally converged by the human eye to the fundus of the human eye.

6. The ophthalmic measurement system of claim 3, wherein the posterior segment OCT sample arm optical path sequentially comprises a first posterior segment OCT optical path mirror, a second posterior segment OCT optical path mirror, an posterior segment and gaze spectroscope, a refractive adjustment device, a anterior posterior segment OCT spectroscope, a anterior spectroscope, and an ocular objective lens, wherein the posterior segment probe light is reflected by the optical path scanning device, reflected by the first posterior segment OCT optical path mirror and the second posterior segment OCT optical path mirror, reflected by the posterior segment and gaze spectroscope, passed through the refractive adjustment device, reflected by the anterior posterior segment OCT spectroscope, reflected by the anterior spectroscope, passed through the anterior spectroscope, and finally converged by the human eye to the ocular fundus; the second back section OCT optical path reflecting mirror, the back eye section and the fixation spectroscope are integrally arranged to be translatable, so that the optical path length of the optical path of the back eye section OCT sample arm is adjustable.

7. The ophthalmic measurement system of claim 4, wherein the posterior segment OCT sample arm optical path comprises, in order, a posterior segment and gaze beamsplitter, a refractive adjustment device, a third posterior segment OCT optical path mirror, a anterior and posterior segment OCT beamsplitter, a pre-beamsplitter, and an ocular objective, wherein the posterior segment probe light is reflected by the optical path scanning device, reflected by the posterior segment and gaze beamsplitter, passed through the refractive adjustment device, reflected by the third posterior segment OCT optical path mirror and the anterior and posterior segment OCT beamsplitter, reflected by the pre-beamsplitter, and then reflected by the pre-beamsplitter to the ocular objective, and finally converged by the human eye to the ocular fundus.

8. An ophthalmic measurement system according to claim 5 or claim 7, wherein a posterior OCT optical fiber collimator is further provided between the optical fiber spectroscopic device and the optical path scanning device, the posterior OCT optical fiber collimator being arranged with a posterior OCT sample arm fiber head to be translatable integrally along a main optical axis of the posterior OCT optical fiber collimator, thereby enabling an optical path length of the optical path of the posterior OCT sample arm to be adjustable.

9. The ophthalmic measurement system of any one of claims 1 to 4, wherein the anterior segment OCT sample arm optical path comprises a first lens, a third lens, an anterior-posterior segment OCT beam splitter, a front beam splitter, and an objective lens, and the anterior segment probe light is reflected by the optical path scanning device, sequentially transmitted through the first lens, the third lens, and the anterior-posterior segment OCT beam splitter, reflected by the front beam splitter to the objective lens, and finally converged by the human eye to the anterior segment of the human eye.

10. The ophthalmic measurement system of claim 9, wherein a front section OCT fiber collimator is further disposed between the fiber optic spectroscopic device and the optical path scanning device.

11. The ophthalmic measurement system of any one of claims 1 to 4, further comprising a fixation optical module comprising a fixation light source for providing a fixation index for fixation of the eye of the subject.

12. The ophthalmic measurement system of any one of claims 1 to 4, further comprising an anterior ocular segment camera module comprising an illumination source and a camera device, the illumination source being configured to illuminate the anterior ocular segment of the subject's eye, reflect off anterior ocular segment tissue, and be imaged by the camera device.