Ophthalmic examination measurement system and method of controlling the same

Abstract

The application discloses an ophthalmic examination and measurement system and a control method thereof, comprising a biological measurement system, a refractive measurement system and an optical path propagation system; the optical path propagation system comprises an eyepiece with a ring-shaped light plate and a transmission mirror capable of transmitting and reflecting light. The biological transverse parameter, the biological longitudinal parameter and the refractive power of the eye can be measured by using a set of systems; the emission system of the refractive measurement system is configured with a checkered light spot generation module for generating a checkered light spot for irradiating the eye, so that the problem of poor resolution of the ring-shaped light spot in the prior art can be avoided, and the speed of judging the refractive state can be improved by comparing the checkered light spots formed in front and back, and the accuracy of the examination result is also improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of ophthalmic instruments, in particular to an ophthalmic examination and measurement system and a control method thereof. BACKGROUND

[0002] In the field of ophthalmic examination, optometry examination instruments are often used to measure the diopter of the eye, and biometry instruments are used to measure the biological parameters of the eye.

[0003] The diopter includes spherical diopter, cylindrical diopter, and astigmatism axis. The diopter measurement generally uses a light source to irradiate the eye, forms a ring-shaped light spot on the peripheral retina of the macular area of the fundus, and then photographs the ring-shaped light spot reflected by the retina, which is used to calculate the diopter.

[0004] The biological parameters include biological horizontal parameters and biological vertical parameters. The biological horizontal parameters include corneal curvature or radius, white-to-white distance, pupil diameter, etc., and the biological vertical parameters include corneal thickness, anterior chamber depth, lens thickness, and axial length. The biological parameter measurement uses a combination of a light plate, a camera, and an interference light path to photograph the images of the cornea and the pupil to calculate the biological horizontal parameters, and uses laser interference to calculate the biological vertical parameters.

[0005] In the prior art, a Chinese invention patent with publication number CN113440099A discloses a human eye vision comprehensive examination device, which is composed of a light path assembly and a three-dimensional motion platform. The light path assembly is fixed to the upper end of the three-dimensional motion platform and is aligned with the human eye through the movement of the three-dimensional motion platform in the X, Y, and Z directions. The light path assembly is composed of a biometry system, a diopter measurement system, and a curvature measurement system. The biometry system is used to measure the biological parameters of the human eye. The diopter measurement system is used to measure the diopter of the human eye. The curvature measurement system is used to measure the curvature of the cornea of the human eye.

[0006] According to the characteristics of the biometry system and the refractive measurement system, the two systems are ingeniously fused by using a middle-hole mirror. The sample arm of the biometry system is actually also the projection light path of the refractive measurement system, and the light source is also unified as one light source. The projection light path and the sample arm light path of the biometry system are the same light path, including the optical fiber head, the condenser lens, the middle-hole mirror, the second beam splitter, the eyepiece, and the first beam splitter. Among them, the part after the middle-hole mirror is shared with the refractive measurement light path. The refractive measurement light path includes the first beam splitter, the eyepiece, the second beam splitter, the middle-hole mirror, the annular diaphragm, the conical mirror, the refractive measurement objective lens, and the refractive measurement camera. The middle-hole mirror is used for the projection light path, and its role is to pass through the light emitted by the refractive measurement light source; it is used for the refractive measurement light path, and its role is to reflect the light reflected from the fundus into the refractive measurement camera. Since the small hole in the central region cannot reflect light, the light reflected from the fundus after reflection will become a light ring, rather than a light spot. Its role is to collect the light reflected by the human eye at the converging light spot on the fundus, and through the action of the conical mirror and the refractive measurement objective lens, a light ring is formed on the refractive measurement camera, and the light emitted by the refractive measurement light source reflected by the central region (macular region) of the cornea of the human eye is intercepted. Through analysis of the shape of the light ring, the refractive information of the measured human eye is obtained.

[0007] The above prior art has the following defects:

[0008] Firstly, a weak coherent light source is used, which is emitted from the optical fiber head, then converges through the condenser lens, then passes through the hole of the middle-hole mirror, then successively passes through the second beam splitter, the eyepiece, and the first beam splitter, and then is emitted to the eye. The light reflected by the retina forms a light ring through the joint action of the middle-hole mirror and the annular diaphragm, and finally forms a light ring on the refractive measurement camera. The light ring is formed on the light path after reflection of the retina, that is, the light ring is formed on the receiving light path of the camera, and is determined by the structure and arrangement of the middle-hole mirror and the annular diaphragm. In terms of intercepting the reflected light of the macular region, there may be inaccurate phenomena such as deviation, which may cause distortion in the reaction of the retinal ring-shaped light spot, affecting the test results. The above prior art completely relies on the pattern of the ring-shaped light spot formed by the post-interception to judge the refractive state of the eye, and the deformation judgment of the ring-shaped light spot is not so obvious. In terms of judging the refractive state, the speed is relatively slow, and the accuracy of the result needs to be improved.

[0009] Second: determined by the characteristics of the optical fiber and the weak coherent light source, the light spot emitted from the optical fiber is a Gaussian distribution light spot, and the light intensity section is the brightest in the center and decreases periphery. Therefore, the illumination distribution of the light spot when reaching the fundus of the eye is also Gaussian distribution, so the brightness distribution of the light spot returned from the human eye to the central hole mirror and the annular diaphragm is also Gaussian distribution. Then, the light that can be reflected by the central hole mirror and can pass through the annular diaphragm is affected by Gaussian distribution. Because the refractive power of the eyes of different users is different, the brightness of the reflected annular pattern is different. When the brightness of the reflected light is dark, the signal-to-noise ratio is poor, resulting in reduced accuracy. SUMMARY

[0010] The purpose of the present application is to overcome the shortcomings of the prior art, provide an ophthalmic examination and measurement system and a control method thereof, which is provided with a biometric measurement system and a refractive measurement system, and can measure the biometric transverse parameters, biometric longitudinal parameters and refractive power of the eye by using a set of system; the emission system of the refractive measurement system is provided with a chessboard light spot generation module for generating a chessboard light spot for irradiating the eye. The deformation judgment of the chessboard light spot is much faster and more accurate than that of the annular light spot, which improves the speed of judging the refractive state and the accuracy of the examination result. The light spot emitted by the chessboard light spot generation module is uniform in brightness and does not show Gaussian distribution. The annular diaphragm is no longer arranged on the receiving light path of the receiving system. The brightness and signal-to-noise ratio of the photographed images of the eyes of people with different refractive powers are comparable, which is more convenient for processing and improves the calculation accuracy.

[0011] The technical scheme of the present application provides an ophthalmic examination and measurement system, which comprises a biometric measurement system, a refractive measurement system and a light path propagation system;

[0012] The light path propagation system comprises an ocular lens with an annular lamp plate and a transmissive mirror capable of transmitting and reflecting light;

[0013] The biometric measurement system comprises a biometric measurement module, an imaging lens arranged between the biometric measurement module and the ocular lens, and a light path interference system with a first collimating lens;

[0014] The biometric measurement module, the imaging lens and the ocular lens are on the main light path and are used for measuring the biometric transverse parameters of the eye;

[0015] The first collimating lens is aligned with the transmissive mirror, and the light path propagation is realized through the transmissive mirror and the main light path. The light path interference system is signal connected with the biometric measurement module and is used for measuring the biometric longitudinal parameters of the eye;

[0016] The refractive measurement system comprises an emission system with a chessboard light spot generation module, a receiving system with a refractive measurement module, and a fixation-veiling system with a display unit;

[0017] The image information emitted by the display unit and the checkerboard light spot generated by the checkerboard light spot generating module can be transmitted to the eye of the subject to be measured through the light path propagation system and the main light path, and the checkerboard light spot formed by the retina reflection can be transmitted to the refractive measurement module through the main light path and the light path propagation system, and the refractive measurement module measures the refractive power of the eye according to the deformation of the checkerboard light spot.

[0018] In one of the optional technical solutions, the light path propagation system comprises a first beam splitter arranged between the imaging lens and the eyepiece and inclined towards the eyepiece side;

[0019] The transmission mirror is arranged in parallel with the first beam splitter below the first beam splitter;

[0020] The central area of the top surface of the transmission mirror has a reflective surface, and the peripheral area of the reflective surface is a light-transmitting part;

[0021] The first collimating lens is aligned with the reflective surface, and the light emitted by the first collimating lens is reflected to the first beam splitter through the reflective surface, and the light reflected by the central area of the first beam splitter is reflected to the first collimating lens through the reflective surface;

[0022] The image information, the checkerboard light spot and the checkerboard light spot are transmitted through the light-transmitting part respectively.

[0023] In one of the optional technical solutions, a periscope is arranged between the imaging lens and the first beam splitter;

[0024] The periscope has a high-position lens and a low-position lens arranged oppositely, the imaging lens is aligned with the high-position lens, and the first beam splitter is aligned with the low-position lens;

[0025] The light path of the light path propagation system passes below the imaging lens.

[0026] In one of the optional technical solutions, the light path propagation system comprises a first mirror arranged below the transmission mirror and arranged in parallel with the transmission mirror;

[0027] The reflected light path of the first mirror comprises a vertical reflected light path and a horizontal reflected light path, and the refractive measurement system is arranged at the rear side of the first mirror and above the horizontal reflected light path;

[0028] The receiving system, the emitting system and the fixation-vergence system are arranged in a rear-to-front direction, and the horizontal reflected light path is respectively provided with a second mirror, a second beam splitter and a third beam splitter;

[0029] The third beam splitter is used for reflecting the image information emitted by the display unit to the first reflector, and the second beam splitter is used for reflecting the chessboard light spot to the first reflector.

[0030] The reflected chessboard light spot can pass through the third beam splitter and the second beam splitter and is reflected by the second reflector to the refraction measurement module.

[0031] In one of the optional technical solutions, the fixation-fogging system comprises a focusing lens and a third reflector.

[0032] The focusing lens is adjustably arranged between the third reflector and the display unit, and the third reflector is used for reflecting the image information emitted by the display unit to the light path propagation system.

[0033] In one of the optional technical solutions, the chessboard light spot generation module and the focusing lens are connected through a first linkage structure, and the chessboard light spot generation module and the focusing lens are kept in linkage.

[0034] In one of the optional technical solutions, the chessboard light spot generation module comprises an infrared light source, a third collimating lens and a chessboard diaphragm arranged in sequence, and the chessboard diaphragm is used for forming the chessboard light spot. In one of the optional technical solutions, a relay lens assembly is arranged on the light path of the refraction measurement module, and the relay lens assembly keeps linkage with the focusing lens to realize focusing.

[0035] In one of the optional technical solutions, the relay lens assembly comprises a first relay lens and a second relay lens fixedly arranged and a third relay lens slidably arranged between the first relay lens and the second relay lens.

[0036] The third relay lens is connected with the focusing lens or the chessboard light spot generation module through a second linkage structure.

[0037] The technical scheme of the present application also provides a control method of an ophthalmic examination and measurement system, comprising a biometric measurement step and a refraction measurement step.

[0038] The biometric measurement step comprises a biometric transverse parameter measurement step and a biometric longitudinal parameter measurement step.

[0039] The biometric transverse parameter measurement step comprises:

[0040] The annular light plate emits light towards the eye of the person to be measured, the imaging lens captures imaging data, and the imaging data is transmitted to the biometric measurement module to obtain the biometric transverse parameter of the eye.

[0041] The biological longitudinal parameter measurement step comprises:

[0042] The optical path interference system is started, the first collimating lens emits a laser signal, the laser signal is propagated to the eye of the to-be-measured person through the optical path propagation system and the main optical path;

[0043] The laser signal reflected by the eye returns to the optical path interference system along the original path, and an interference oscillation signal is generated by interference of the optical path interference system;

[0044] The interference oscillation signal is transmitted to the biological measurement module to obtain the biological longitudinal parameter of the eye;

[0045] The refractive measurement step comprises:

[0046] The display unit is started to be used for the eye of the to-be-measured person to view;

[0047] The checkerboard light spot generated by the checkerboard light spot generation module irradiates the eye of the to-be-measured person through the optical path propagation system and the main optical path;

[0048] The checkerboard light spot formed by the retina reflection is propagated to the refractive measurement module through the main optical path and the optical path propagation system;

[0049] The refractive measurement module measures the refractive power of the eye according to the deformation amount of the checkerboard light spot.

[0050] The above technical scheme has the following beneficial effects:

[0051] The ophthalmic examination and measurement system and the control method thereof provided by the application are configured with a biological measurement system and a refractive measurement system. The biological measurement system can measure biological transverse parameters and biological longitudinal parameters. The refractive measurement system can measure the refractive power of the eye. The biological transverse parameters, the biological longitudinal parameters and the refractive power of the eye can be measured by using one set of system, and the work efficiency is improved.

[0052] The emission system of the refractive measurement system is configured with a checkerboard light spot generation module, which is used to generate a checkerboard light spot to propagate to the eye of the to-be-measured user. The checkerboard light spot reflected by the retina is reflected to the refractive measurement module. The refractive measurement module measures the refractive power of the eye according to the deformation amount of the checkerboard light spot. Since the checkerboard light spot is composed of a plurality of light spot units, one light spot is divided into a plurality of small diamond-shaped light spots, and has a plurality of intersection points, which can be used as reference points when comparison and judgment are performed. Therefore, the change and deformation amount of the checkerboard light spot can be quickly judged, the refractive power can be quickly calculated, and the accuracy of the examination result is greatly improved.

[0053] Compared with the existing technology of emitting light spots by optical fibers, the chessboard light spot emitted by the chessboard light spot generation module is uniform in brightness and does not present Gaussian distribution, and the annular diaphragm is no longer arranged on the receiving light path of the receiving system, so that the images of the eyes of people with different refractive powers are substantially equivalent in brightness and signal-to-noise ratio, the processing is more convenient, and the calculation accuracy is improved. The ophthalmic examination and measurement system provided by the application has the advantages that the light path for measuring the biological transverse parameter coincides with the main light path, the light path for measuring the biological transverse parameter and the refractive measurement light path are integrated in the light path propagation system, the light propagation is realized by the light path propagation system and the main light path respectively, the light path utilization rate is high, the components of the light path are saved, and the cost and the volume of the product are reduced. BRIEF DESCRIPTION OF DRAWINGS

[0054] The disclosure of the application will become more apparent with reference to the drawings. It should be understood that these drawings are only for the purpose of illustration and are not intended to limit the scope of protection of the application. In the drawings:

[0055] Figure 1 The schematic diagram of the ophthalmic examination and measurement system provided by an embodiment of the application;

[0056] Figure 2 The schematic diagram of the light path interference system;

[0057] Figure 3 The structural schematic diagram of the transmission mirror;

[0058] Figure 4 The schematic diagram of the refractive measurement system;

[0059] Figure 5 The schematic diagram of the periscope arranged between the imaging lens and the first beam splitter;

[0060] Figure 6 The schematic diagram of the interlayer interference pattern of the eye;

[0061] Figure 7 The initial image schematic diagram of the chessboard light spot;

[0062] Figure 8 The schematic diagram of the chessboard light spot reflected by the retina when the refractive power is not zero;

[0063] Figure 9 The schematic diagram of the chessboard light spot reflected by the retina when the refractive power is not zero;

[0064] Figure 10 The schematic diagram of marking the chessboard light spot, wherein the initial image of the chessboard light spot is a square;

[0065] Figure 11This is a schematic diagram of marking a checkerboard pattern of light reflected from the retina, where the image of the checkerboard pattern reflected from the retina is not square. Detailed Implementation

[0066] The specific embodiments of the present invention will be further described below with reference to the accompanying drawings. Identical components are indicated by the same reference numerals. It should be noted that the terms "front," "rear," "left," "right," "up," and "down" used in the following description refer to directions in the accompanying drawings, while the terms "inner" and "outer" refer to directions toward or away from the geometric center of a specific component, respectively.

[0067] like Figures 1-2 , Figure 4 and Figures 6-11 As shown, an embodiment of the present invention provides an ophthalmic examination measurement system, including a biometry system 1, a refractive measurement system 2, and an optical path propagation system 4. The optical path propagation system 4 includes an eyepiece 3 with a ring-shaped lamp plate 31 and a transmissive and reflective mirror 41 that is both light-transmitting and light-reflecting. The biometry system 1 includes a biometry module 11, an imaging lens 12 disposed between the biometry module 11 and the eyepiece 3, and an optical path interference system 13 with a first collimating lens 136.

[0068] The biometry module 11, imaging lens 12, and eyepiece 3 are located on the main optical path 5 and are used to measure the biological lateral parameters of the eye 6.

[0069] The first collimating lens 136 is aligned with the transmission and reflection mirror 41, and the light path is propagated through the transmission and reflection mirror 41 and the main light path 5. The light path interference system 13 is connected to the bio-measurement module 11 for signal measurement of the biological longitudinal parameters of the eye 6.

[0070] The refractive measurement system 2 includes a transmitting system 21 with a checkerboard light spot generation module 211, a receiving system 22 with a refractive measurement module 221, and a fixation-fogging system 23 with a display unit 231.

[0071] The image information emitted by the display unit 231 and the checkerboard light spot generated by the checkerboard light spot generation module 211 can be transmitted to the eye 6 of the subject through the optical path propagation system 4 and the main optical path 5. The checkerboard light spot formed by retinal reflection can be transmitted to the refractive measurement module 221 through the main optical path 5 and the optical path propagation system 4. The refractive measurement module 221 measures the refractive power of the eye 6 based on the deformation of the checkerboard light spot.

[0072] The ophthalmic examination and measurement system for measuring the diopter and biological parameters of the eye 6 comprises a biological measurement system 1, a diopter measurement system 2, an ocular lens 3, a light path propagation system 4, a main light path 5 and the like. The biological measurement system 1, the diopter measurement system 2, the ocular lens 3, the light path propagation system 4 and the main light path 5 and the like can be integrated in one or several housings and placed on an existing three-dimensional motion platform capable of realizing front-back, left-right and up-down three-way motion to realize that the main light path 5 can automatically aim at the eye 6 of the person to be measured. The working principle of the three-dimensional motion platform can refer to the content in the prior art, and will not be described here.

[0073] The ophthalmic examination and measurement system provided by the application is configured with a master control unit such as a control circuit board, a control chip and the like for controlling the operation of the electrical instrument and can also be used to measure the diopter and biological parameters according to the obtained image data, signal data and the like.

[0074] The biological measurement system 1 is used for measuring or detecting the biological parameters of the eye 6, including biological transverse parameters and biological longitudinal parameters.

[0075] The biological measurement system 1 comprises a biological measurement module 11, an imaging lens 12 and a light path interference system 13 and the like.

[0076] The biological measurement module 11 can measure the biological parameters of the eye 6 through the obtained image data, signal data and the like. The biological measurement module 11 can adopt CMOS, specifically a component with an integrated circuit chip and a photosensitive element / camera lens. The biological measurement module 11 can measure the biological parameters. The biological measurement module 11 is in communication connection with the master control unit, and the master control unit can also be used to measure the biological parameters.

[0077] The imaging lens 12 is an infrared camera which is arranged at the front side of the biological measurement module 11 and at the rear side of the ocular lens 3, and the three are located on the main light path 5. The ocular lens 3 is used for aiming at the eye 6 of the person to be measured. A ring-shaped lamp plate 31 is arranged around the ocular lens 3, and a plurality of light sources are arranged at the front side of the ring-shaped lamp plate 31 along the circumferential direction at intervals, including infrared light sources, visible light sources and the like, for illuminating the eye 6 of the person to be measured.

[0078] The biological measurement module 11, the imaging lens 12 and the ocular lens 3 are located on the main light path 5 and are used for measuring the biological transverse parameters of the eye 6. The general operation is that the light sources of the ring-shaped lamp plate 31 are turned on and emit light towards the eye 6 of the person to be measured. The imaging lens 12 shoots imaging data and transmits the imaging data to the biological measurement module 11 to obtain the biological transverse parameters of the eye 6.

[0079] According to the different biological transverse parameters, the specific division is as follows:

[0080] Corneal radius of curvature measurement: infrared light source is used to illuminate the eye 6, and the infrared light is reflected once on the cornea to form an image, and the image is reflected to the imaging lens 12 through the main light path 5, and the imaging lens 12 takes a second image and transmits the imaging data to the biometric measurement module 11. According to the acquired image data, the existing algorithm is calculated, and the corneal radius of curvature of the human eye can be obtained.

[0081] White-white distance, pupil diameter measurement: visible light source is used for illumination, and the visible light illuminates the ocular surface of the eye 6, and the imaging lens 12 takes an image once, and the imaging data is transmitted to the biometric measurement module 11. According to the acquired image data and the existing algorithm calculation, the white-white distance and the pupil diameter can be obtained.

[0082] The algorithm for the radius of curvature of the cornea, the algorithm for the white-white distance, and the algorithm for the pupil diameter are contents in the prior art, and will not be described here.

[0083] The light path interference system 13 is used for the measurement of the biological longitudinal parameters, and plays a role in increasing the optical path. The light path interference system 13 includes a first collimating lens 136. The first collimating lens 136 is connected with the main light path 5 through the light path transmission system 4 to realize light path transmission. The light path interference system 13 is signal connected with the biometric measurement module 11, and is used for measuring the biological longitudinal parameters of the eye 6.

[0084] The light path transmission system 4 has a transmissive mirror 41, the center of which can reflect light, and the periphery of which can transmit light. Therefore, the transmissive mirror 41 can allow the chessboard light spot transmitted by the refractive measurement system 2 and the chessboard light spot reflected by the retina to pass through. The transmissive mirror 41 can also reflect the laser emitted by the first collimating lens 136 to the main light path 5, and can also reflect the light transmitted by the main light path 5 to the first collimating lens 136.

[0085] The measurement method of the biological longitudinal parameters is as follows: the light path interference system 13 is turned on, the first collimating lens emits a laser signal, and the laser signal is transmitted to the eye 6 of the to-be-measured person through the transmissive mirror 41, the light path transmission system 4 and the main light path 5. The laser signal reflected by the eye 6 returns to the light path interference system 13 along the original path, and the light path interference system 13 generates an interference oscillation signal by interference. The interference oscillation signal is transmitted to the biometric measurement module 11 to obtain the biological longitudinal parameters of the eye 6.

[0086] As shown in Figure 6 , the axial length is the distance a-e, the corneal thickness is the distance a-b, the anterior chamber depth is the distance b-c, and the lens thickness is the distance c-d.

[0087] Specifically, the optical path interference system 13 comprises an SLD light source 131 (a broadband laser), an upper arm fiber flange 132, a lower arm fiber flange 133, a coupler 134, a detector 135, a first collimating lens 136, a second collimating lens 137, an optical path changing device 138, and a measurement mirror 139. The SLD light source 131 is connected with the coupler 134, and the coupler 134 is further connected with the upper arm fiber flange 132, the lower arm fiber flange 133, and the detector 135. The SLD light source 131 emits laser light which is split into a first laser light and a second laser light by the coupler 134. The first laser light passes through the upper arm fiber flange 132 and the first collimating lens 136, is reflected by the transmission mirror 41, and then propagates to the eye 6 of the to-be-measured person through the optical path propagation system 4 and the main optical path 5. The reflected laser signal of the eye 6 returns along the original path and passes through the coupler 134. The second laser light passes through the lower arm fiber flange 133 and the second collimating lens 137, enters the optical path changing device 138, and returns to the coupler 134 through the measurement mirror 139 to form interference, thereby enhancing the light signal and making it easier for the detector 135 to monitor the light signal. The detector 135 is in communication connection with the biological measurement module 11. The detector 135 performs photoelectric conversion on the interference oscillation signal and then transmits the signal to the biological measurement module 11. After decoding, the interlaminar interference pattern of the glasses 6 shown in FIG. 9 can be obtained. Figure 6

[0088] The refractive measurement system 2 is used to measure the refractive power of the eye, for example, hyperopia, myopia, and astigmatism. The refractive measurement light path of the refractive measurement system 2 is connected and propagates the light signal through the optical path propagation system 4 and the main optical path 5.

[0089] The refractive measurement system 2 comprises an emission system 21, a receiving system 22, and a fixation-veiling system 23.

[0090] The emission system 21 has a chessboard light spot generation module 211 which can generate a relatively regular chessboard light spot. As shown in FIGS. 7-9, the chessboard light spot is composed of a plurality of light spot units. The relatively regular chessboard light spot or the initial state chessboard light spot is composed of a plurality of square light spot units. After being reflected by the retina, the light spot units change to rhombuses or parallelograms without right angles, and then the chessboard light spot formed after being reflected by the retina is composed of a plurality of rhombus light spot units or parallelogram light spot units without right angles.

[0091] ​The chessboard light spot can enter the main light path 5 through the refraction measurement light path, the light path propagation system 4, and then be shot to the eye 6. The receiving system 22 has a refraction measurement module 221 for receiving the retinal reflection of the chessboard light spot. Due to the different refraction states of the eye 6 (including spherical refraction, cylindrical refraction, and astigmatism axis), the chessboard light spot reaching the fundus of the eye 6 will change, which is specifically reflected in the shape and angle of the light spot unit. Therefore, the chessboard light spot reflected by the retina is different from the chessboard light spot formed by the chessboard light spot forming module 211, and the difference will reflect the refraction state of the eye 6. The chessboard light spot reflected by the retina will enter the refraction measurement module 221 along the main light path 5, the light path propagation system 4, and the refraction measurement light path. After the refraction measurement module 221 receives the chessboard light spot reflected by the retina, the chessboard light spot reflected by the retina is compared with the chessboard light spot formed by the chessboard light spot forming module 211. If the chessboard light spot formed by the chessboard light spot forming module 211 is not deformed, it indicates that the refraction state of the user's eye is good; if the chessboard light spot formed by the chessboard light spot forming module 211 is deformed, it indicates that the refraction state of the user's eye has certain problems, such as myopia, hyperopia, astigmatism, etc., and further measures each refraction state.

[0092] Since the chessboard light spot is composed of multiple light spot units, one light spot is divided into multiple small diamond-shaped light spots, and has multiple intersection points, which can be used as reference points for comparison and judgment, so that the change and deformation of the chessboard light spot can be quickly judged, and the refraction can be quickly calculated, greatly improving the accuracy of the test results.

[0093] How to calculate the refraction state will be discussed in detail in the following part.

[0094] The refraction measurement module 221 can adopt CMOS, specifically a component with an integrated circuit chip and a photosensitive element / camera lens. The refraction measurement module 221 can measure biological parameters. The refraction measurement module 221 is in communication connection with the main control unit, and the biological parameters can also be measured by the main control unit.

[0095] The fixation-veiling system 23 has a display unit 231 for displaying icons, pictures, videos, etc., for positioning the line of sight of the eye 6. Fixation refers to the eye 6 staring at the target, such as an icon, and fixing the line of sight. Veiling refers to the eye 6 in a relaxed state, such as watching videos, pictures, etc., which can provide more reference standards and help improve the accuracy of the measurement results. The image signal mentioned in the present application includes video signals, text signals, icon signals, picture signals, etc.

[0096] The refraction measurement method is to turn on the display unit 231 for the eye of the person to be tested to watch.

[0097] The checkerboard light spot generation module 211 works and generates a checkerboard light spot, and the checkerboard light spot irradiates the eye 6 of the to-be-measured person through the light path propagation system 4 and the main light path 5.

[0098] The checkerboard light spot is formed by retinal reflection, and the checkerboard light spot propagates to the refractive measurement module 221 through the main light path 5 and the light path propagation system 4, and the refractive measurement module 221 measures the refractive power of the eye 6 according to the deformation amount of the checkerboard light spot.

[0099] In summary, the ophthalmic examination and measurement system provided by the application is configured with the biological measurement system 1 and the refractive measurement system 2. The biological measurement system 1 can measure biological transverse parameters and biological longitudinal parameters. The refractive measurement system 2 can measure the refractive power of the eye 6. The biological transverse parameters, the biological longitudinal parameters and the refractive power of the eye 6 can be measured by using a set of system, and the work efficiency is improved.

[0100] The emission system 21 of the refractive measurement system 2 is configured with the checkerboard light spot generation module 211, which is used to generate the checkerboard light spot to propagate to the eye 6 of the user, and the checkerboard light spot is reflected by the retina to the refractive measurement module 221. The refractive measurement module 221 measures the refractive power of the eye according to the deformation amount of the checkerboard light spot. Since the checkerboard light spot is composed of a plurality of light spot units, one light spot is divided into a plurality of small diamond-shaped light spots as a whole, and has a plurality of intersection points, which can be used as a reference point for comparison and judgment, so that the change and deformation amount of the checkerboard light spot can be quickly judged, and the refractive power can be quickly calculated, and the accuracy of the examination result is greatly improved.

[0101] In the judgment of the refractive state, compared with the light spot emission mode of the prior art, the checkerboard light spot emitted by the checkerboard light spot generation module 211 in the application has uniform brightness and does not have Gaussian distribution. The receiving light path of the receiving system no longer has an annular diaphragm. The brightness and signal-to-noise ratio of the photographed images of the eyes of people with different refractive powers are roughly equivalent, which is more convenient for processing and improves the calculation accuracy.

[0102] The ophthalmic examination and measurement system provided by the application has the following advantages. The light path for measuring the biological transverse parameters coincides with the main light path 5, and the light path for measuring the biological transverse parameters and the refractive measurement light path are integrated in the light path propagation system 4. The light propagation is realized by the light path propagation system 4 and the main light path 5 respectively. The light path has high reutilization rate, and the components of the light path are saved, which is beneficial to saving cost and reducing the volume of the product.

[0103] In one embodiment, as shown in Figure 1 and Figures 3-4 The light path propagation system 4 includes a first light splitter 42 which is arranged between the imaging lens 12 and the eyepiece 3 and is inclined towards the eyepiece 3 side.

[0104] The transmissive mirror 41 is arranged in parallel with the first beam splitter 42 directly below the first beam splitter 42.

[0105] The central region of the top surface of the transmissive mirror 41 has a reflecting surface 411, and the peripheral region of the reflecting surface 411 is a light-transmissive portion 412.

[0106] The first collimating lens 136 is aligned with the reflecting surface 411, and the light emitted by the first collimating lens 136 is reflected by the reflecting surface 411 to the first beam splitter 42. The central region of the first beam splitter 42 reflects the light back to the first collimating lens 136 via the reflecting surface 411.

[0107] The image information, the checkerboard light spot, and the light spot reflected by the retina propagate through the light-transmissive portion 412, respectively.

[0108] In the embodiment, the optical path propagation system 4 includes the first beam splitter 42, which is arranged between the imaging lens 12 and the eyepiece 3, is located on the main optical path 5, and is inclined toward the eyepiece 3. The first beam splitter 42 reflects the light from the transmissive mirror 41 toward the eye 6, and also reflects the light reflected by the eye 6 toward the transmissive mirror 41.

[0109] The transmissive mirror 41 is arranged in parallel with the first beam splitter 42 directly below the first beam splitter 42. The central region of the top surface of the transmissive mirror 41 has a reflecting surface 411, and the peripheral region of the reflecting surface 411 is a light-transmissive portion 412.

[0110] The first collimating lens 136 is aligned with the reflecting surface 411, and the light emitted by the first collimating lens 136 is reflected by the reflecting surface 411 to the first beam splitter 42. The central region of the first beam splitter 42 reflects the light back to the first collimating lens 136 via the reflecting surface 411.

[0111] The image information generated by the refractive measurement system 2, the checkerboard light spot generated by the checkerboard light spot generation module 211, and the light spot reflected by the retina propagate through the light-transmissive portion 412, respectively. A small part of the image information and the checkerboard light spot is blocked by the reflecting surface 411, but this does not affect the view of the eye 6.

[0112] In one of the embodiments, as shown in Figure 1 and Figure 5 The imaging lens 12 and the first beam splitter 42 are arranged with a periscope 14 therebetween.

[0113] The periscope 14 has a high-position lens 141 and a low-position lens 142 arranged oppositely, the imaging lens 12 is aligned with the high-position lens 141, and the first beam splitter 42 is aligned with the low-position lens 142.

[0114] The light path of the light path propagation system 4 passes below the imaging lens 12.

[0115] In this embodiment, the periscope 14 is arranged between the imaging lens 12 and the first beam splitter 42 to raise the imaging lens 12, so that the light path of the light path propagation system 4 passes below the imaging lens 12, which is beneficial to improving the integration of the system and reducing the height of the product.

[0116] In one of the embodiments, as shown in Figure 1 and Figure 4 The light path propagation system 4 includes a first mirror 43 arranged below the transmissive mirror 41 and parallel to the transmissive mirror 41.

[0117] The reflected light path of the first mirror 43 includes a vertical reflected light path 431 and a horizontal reflected light path 432. The refractive measurement system 2 is arranged on the rear side of the first mirror 43 and above the horizontal reflected light path 432.

[0118] The receiving system 22, the emitting system 21 and the fixation-fogging system 23 are arranged in sequence along the direction from the rear to the front. The second mirror 44, the second beam splitter 45 and the third beam splitter 46 are arranged on the horizontal reflected light path 432 correspondingly.

[0119] The third beam splitter 46 is used to reflect the image information emitted by the display unit 231 to the first mirror 43, and the second beam splitter 45 is used to reflect the checkerboard light spot to the first mirror 43.

[0120] The reflected checkerboard light spot can pass through the third beam splitter 46 and the second beam splitter 45 and be reflected to the refractive measurement module 221 by the second mirror 44.

[0121] In this embodiment, the light path propagation system 4 is configured with the first mirror 43 to realize the vertical and horizontal light path conduction. The first mirror 43 is arranged below the transmissive mirror 41 and parallel to the transmissive mirror 41. The reflected light path of the first mirror 43 is divided into the vertical reflected light path 431 and the horizontal reflected light path 432. The transmissive mirror 41 and the first beam splitter 42 are arranged on the vertical reflected light path 431.

[0122] The refractive measurement system 2 is arranged on the rear side of the first mirror 43 and above the horizontal reflected light path 432. Specifically, the receiving system 22, the emitting system 21 and the fixation-fogging system 23 are arranged on the rear side of the imaging lens 12 and arranged in sequence along the direction from the rear to the front. Such arrangement can reduce the height of the product.

[0123] In order to enable the optical paths of the receiving system 22, the transmitting system 21 and the fixed-view-fog system 23 to be connected with the horizontal reflection optical path 432, a second reflecting mirror 44, a second beam splitter 45 and a third beam splitter 46 are correspondingly provided on the horizontal reflection optical path 432.

[0124] The third beam splitter 46 is positioned directly below the light-emitting end of the fixed-viewing-fogging system 23 to achieve optical path conjugation. The third beam splitter 46 is used to reflect the image information emitted by the display unit 231 back to the first reflecting mirror 43.

[0125] The second beam splitter 45 is positioned directly below the light-emitting end of the emitting system 21 to achieve optical path conjugation. The second beam splitter 45 also employs a perforated lens. The second beam splitter 45 is used to reflect the checkerboard pattern light spot toward the first reflecting mirror 43.

[0126] The second reflector 44 is positioned directly below the light-incident end of the receiving system 22, achieving optical path conjugation. The reflected checkerboard light spot can pass through the third beam splitter 46 and the second beam splitter 45, and is reflected by the second reflector 44 towards the refractive measurement module 221.

[0127] In one embodiment, such as Figure 4 As shown, a relay lens 212 for transmitting light path is configured at the light output end of the checkerboard light spot generation module 211 to improve the quality of the image signal.

[0128] In one embodiment, the checkerboard spot generation module 211 can be moved and adjusted relative to the relay lens 212 in the emitting optical path, thereby adjusting the size of the checkerboard spot to suit the eyes of different users.

[0129] In one embodiment, such as Figure 1 and Figure 4 As shown, the fixed-view fog system 23 includes a focusing lens 232 and a third reflecting mirror 233.

[0130] The focusing lens 232 is adjustablely disposed between the third reflector 233 and the display unit 231. The third reflector 233 is used to reflect the image information emitted by the display unit 231 to the optical path propagation system 4.

[0131] In this embodiment, the fixed-view-fog system 23 further includes a focusing lens 232 and a third reflecting mirror 233. The display unit 231 is positioned above the imaging lens 12 and faces rearward. The focusing lens 232 and the third reflecting mirror 233 are sequentially positioned behind the display unit 231, forming a horizontal optical path. The focusing lens 232 is adjustablely positioned between the third reflecting mirror 233 and the display unit 231, serving a focusing function. The third reflecting mirror 233 is used to reflect the image information emitted by the display unit 231 towards the optical path propagation system 4, for example, towards the third beam splitter 46.

[0132] In one of the embodiments, as shown in Figure 4 A fixation-veiling light path relay lens 234 is arranged between the focusing lens 232 and the display unit 231 and / or between the third mirror 233 and the third beam splitter 46 to improve the quality of the image signal.

[0133] In one of the embodiments, as shown in Figure 4 The chessboard light spot generating module 211 is connected with the focusing lens 232 through the first linkage structure 24, and the chessboard light spot generating module 211 is linked with the focusing lens 232. When the focusing lens 232 is focused, the chessboard light spot generating module 211 slides accordingly to change the distance between the chessboard light spot generating module 211 and the emission light path relay lens 212, and the size of the chessboard light spot is adjusted accordingly. The corresponding light path can be designed in advance, and the chessboard light spot generating module 211 reaches the appropriate position at the same time when the focusing lens 232 is focused.

[0134] The first linkage structure 24 can adopt a combination of connecting rods, pull ropes and fixed pulleys, etc.

[0135] As shown in Figure 4 The first linkage structure 24 preferably adopts a combination of a pull rope 241 and a fixed pulley 242. The fixed pulley 242 is arranged between the chessboard light spot generating module 211 and the focusing lens 232, and the pull rope 241 connects the chessboard light spot generating module 211 and the focusing lens 232 and is diverted through the fixed pulley 242. The pull rope 241 can reduce the interference with the surrounding parts.

[0136] In one of the embodiments, as shown in Figure 1 and Figure 4 The chessboard light spot generating module 211 includes an infrared light source 2111, a third collimating lens 2112 and a chessboard light diaphragm 2113 arranged in sequence. The chessboard light diaphragm 2113 cooperates with the conical lens 2113 to form a chessboard light spot.

[0137] In this embodiment, the chessboard light diaphragm 2113 is used to form a chessboard light spot. The chessboard light diaphragm 2113 is in a net shape, and each small unit is in a square structure. The infrared light source 2111 adopts an infrared LED light source. The light emitted by the infrared light source 2111 is collimated by the third collimating lens 2112 and then falls on the chessboard light diaphragm 2113 to form a chessboard light spot. In one of the embodiments, as shown in Figure 1 and Figure 4 A relay lens assembly 222 is arranged on the light path of the refractive measurement module 221, and the relay lens assembly 222 is linked with the focusing lens 232 to realize focusing.

[0138] In the embodiment, the light entrance end of the refraction measurement module 221 is configured with a relay lens assembly 222 for improving the quality of the light spot, which can also be adjusted in sliding mode relative to the refraction measurement module 221, thereby playing a focusing role. The moving amount or focusing amount of the relay lens assembly 222 is realized by the movement of the focusing lens 232. A corresponding optical path can be designed in advance, and after the focusing lens 232 completes focusing, the relay lens assembly 222 reaches the appropriate position at the same time.

[0139] In one of the embodiments, as shown in Figure 1 and Figure 4 The relay lens assembly 222 includes a first relay lens 2221 and a second relay lens 2222 fixedly arranged, and a third relay lens 2223 slidably arranged between the first relay lens 2221 and the second relay lens 2222.

[0140] The third relay lens 2223 is connected with the focusing lens 232 or the chessboard light spot generation module 211 through the second linkage structure 25.

[0141] In the embodiment, the relay lens assembly 222 adopts the combination of the first relay lens 2221, the second relay lens 2222 and the third relay lens 2223. The first relay lens 2221 and the second relay lens 2222 are fixedly arranged, and the third relay lens 2223 is slidably arranged between the first relay lens 2221 and the second relay lens 2222. The third relay lens 2223 is connected with the focusing lens 232 or the chessboard light spot generation module 211 through the second linkage structure 25, thereby realizing linkage focusing.

[0142] The second linkage structure 25 can adopt the combination of the connecting rod, the pull rope and the fixed pulley and the like.

[0143] As shown in Figures 1-11 An embodiment of the present application provides a control method of an ophthalmic examination and measurement system, which includes a biometric measurement step and a refraction measurement step.

[0144] The biometric measurement step includes a biometric transverse parameter measurement step and a biometric longitudinal parameter measurement step.

[0145] The biometric transverse parameter measurement step includes:

[0146] The annular light plate 31 emits light towards the eye 6 of the to-be-measured person, the imaging lens 12 captures imaging data, and the imaging data is transmitted to the biometric measurement module 11 to obtain the biometric transverse parameter of the eye 6.

[0147] The biometric longitudinal parameter measurement step includes:

[0148] The light path interference system 13 is turned on, and the first collimating lens emits a laser signal, which is transmitted to the eye 6 of the subject through the light path propagation system 4 and the main light path 5.

[0149] The laser signal reflected by the eye 6 returns to the light path interference system 13 along the original path, and the interference vibration signal is generated by the light path interference system 13.

[0150] The interference vibration signal is transmitted to the biometric measurement module 11 to obtain the biometric longitudinal parameters of the eye 6.

[0151] The refractive measurement step includes:

[0152] The display unit 231 is turned on for the subject's eye to view.

[0153] The checkerboard light spot generation module 211 works and generates a checkerboard light spot, which irradiates the eye 6 of the subject through the light path propagation system 4 and the main light path 5.

[0154] The checkerboard light spot formed by retinal reflection is propagated to the refractive measurement module 221 through the main light path 5 and the light path propagation system 4, and the refractive power of the eye 6 is measured according to the deformation of the checkerboard light spot.

[0155] The order of the above steps is not limited, and the number of times the ring-shaped light plate is turned on and the switching of each component can be adjusted as needed.

[0156] The measurement and calculation method of the refractive power is as follows:

[0157] The checkerboard light spot generation module 211 can be moved and adjusted on the light path to adjust the size of the image displayed in the eye. During the movement of the checkerboard light spot generation module 211, the fundus imaging image collected by the refractive measurement module 221 will change synchronously. After multiple tests, it can be determined that the checkerboard light spot generation module 211 and the refractive power have a linear correspondence: S = kc x j + e; where S represents the refractive power, j and e represent the adjustment parameters, and kc represents the linear function coefficient. Directly substitute the position of the checkerboard light spot generation module 211 into the above formula P, j and e are determined by experiment, and thus the refractive power (spherical refractive power) measurement result of the subject's eye can be obtained.

[0158] As shown in the checkerboard light spot, Figure 7 The checkerboard light spot is composed of a plurality of small square light spot units of equal size. Compared with the conventional circular or ring-shaped light spot, the checkerboard light spot is easier to implement orthodontics and can improve the accuracy of the refractive power measurement result.

[0159] The chessboard light spot generation module 211 projects a square image of the chessboard light spot. After reflection by the retina, the eye fundus imaging image is obtained by the refractive measurement module 221. At this time, if the refractive power is zero, the eye fundus imaging image remains a chessboard light spot, otherwise the eye fundus imaging image will be deformed. After stretching and tilting, a parallelogram shape as shown in Figure 8 or Figure 9 is obtained. It is easier to judge whether the chessboard light spot is deformed and the amount of deformation. For example, by calculating the pixel points, the amount of deflection of the deflection corner point among the four corners of the chessboard light spot in Figures 8-9 is calculated, so as to calculate the deformation amount of the chessboard light spot.

[0160] The j, e and kc in the above function can be obtained by fitting a plurality of data obtained by experiments. Specifically, the j value is determined as follows:

[0161] As shown in Figure 10 , at least one square region is selected in the initial chessboard light spot, and one of the square regions is taken as an initial square. The four vertices of the initial square are marked as A1 point, B1 point, C1 point and D1 point, A1B1=C1D1, B1C1=A1D1. The side length of the square is as long as possible, so the positions of the four corner points are selected as the four vertices of the initial square. Specifically, the intersection points of each adjacent square block of the chessboard are identified by the chessboard intersection point identification method, and the coordinates of each intersection point are accurately positioned to obtain sub-pixel coordinate values. The four outermost corner points are directly selected as the four vertices of the initial square.

[0162] The corresponding imaging quadrilateral of the initial square in the chessboard light spot reflected by the retina is determined. The four vertices of the imaging quadrilateral are A1' point, B1' point, C1' point and D1' point, A1'B1'=C1'D1', B1'C1'=A1'D1'. When the cylinder refractive power of the user's eye is zero, the A1' point, B1' point, C1' point and D1' point still form a square, A1'B1'=C1'D1'=B1'C1'=A1'D1'. When the cylinder refractive power of the eye to be measured is not zero, the A1' point, B1' point, C1' point and D1' point form a parallelogram as shown in Figure 11 .

[0163] The c=Min(A1'B1', B1'C1') is calculated, and the c value has the following linear relationship with the lens position: c=kpP+j.

[0164] For different diopters of the retina, the moving chessboard light spot generation module 211 obtains the fundus imaging image of the image retina through the diopter measurement module 221, and obtains A1'B1', B1'C1' and c according to the above chessboard intersection identification method. The value of c and the lens position P have the following linear relationship: c=kpP+d. After multiple tests on the measurement results of the simulated eyes with different diopters, the coefficients kp and the parameters d can be calculated. Let P=0 represent that the position of the chessboard light spot generation module 211 is at the set origin position, and the value of c when the position of the chessboard light spot generation module 211 is "0" for different diopters can be calculated, which is represented by c0. Obviously, if P is 0, then c0=j.

[0165] And the diopter S and the above c0 have the following linear relationship: S=kc×c0+e, that is, S=kc×j+e. Still after multiple tests on the measurement results of the simulated eyes with different diopters, the coefficients kc and the parameters e can be calculated.

[0166] Obviously, the diopter measurement using the chessboard light spot can further simplify the calculation process.

[0167] The above diopter measurement method further comprises:

[0168] Obtaining the cylinder diopter of the eye: C=S×(d-c), where d=Max(A1'B1', B1'C1').

[0169] Obtaining the cylinder axis angle α: calculating ∠D1'A1'B1' according to the cosine theorem, if A1'B1'>B1'C1', then the cylinder axis angle α=90°-∠D1'A1'B1'; if A1'B1'<B1'C1', then α=∠D1'A1'B1'.

[0170] Through the scheme of the present application, the spherical diopter, the cylinder diopter and the cylinder axis angle can be directly measured by using the deformation amount of the chessboard light spot, which is simple to operate and has small amount of calculation.

[0171] In the scheme of the present application, a step of calibrating the diopter measurement result can also be included to avoid errors in the measurement result of a single square region due to environmental interference and the like. The calibration process is as follows:

[0172] The selected initial square region includes two or more light spot units, and other square regions outside the initial square region are used as auxiliary verification squares. In specific implementation, different square regions can be distributed around the center block of the chessboard light spot.

[0173] Obtaining a deformation value corresponding to each of the auxiliary check squares as an auxiliary check result; obtaining a first weighted average of the auxiliary check results; if the difference between the deformation value and the first weighted average is not within a set range, then re-obtaining the deformation value.

[0174] Obtaining a cylindrical power corresponding to each of the auxiliary check squares; obtaining a second weighted average of the cylindrical powers; if the difference between the cylindrical power and the second weighted average is not within a set range, then re-obtaining the cylindrical power.

[0175] Obtaining a cylindrical axis angle corresponding to each of the auxiliary check squares; obtaining a third weighted average of the cylindrical axis angles; if the difference between the cylindrical axis angle and the third weighted average is not within a set range, then re-obtaining the cylindrical axis angle.

[0176] The above steps refer to calculating the spherical power, cylindrical power, and cylindrical axis angle for each auxiliary check square using the foregoing steps. Then, an average is calculated based on each of the calculation results or a weighted average is calculated based on the positions of the square regions. The average calculation result is used as a judgment criterion. If the calculation result of the original initial square deviates from the criterion by a small amount, then the original result is considered to be usable. Otherwise, the original result is considered to have a large error and needs to be recalculated. The above process is repeated until the calculation result of the initial square meets the error requirement. Through the present application, the error of the refractive power measurement result can be further ensured to be within an allowable range.

[0177] According to the need, the above technical solutions can be combined to achieve the best technical effect.

[0178] The above is only the principle and preferred embodiment of the present application. It should be noted that, for those skilled in the art, on the basis of the principles of the present application, several other variants can also be made, which should also be considered as the protection scope of the present application.

Claims

1. An ophthalmic examination measurement system, characterized by, The system comprises a biometry system, a refraction system and a light path propagation system; The light path propagation system comprises an eyepiece with a ring-shaped light plate and a transmissive mirror capable of transmitting and reflecting light; The biometry system comprises a biometry module, an imaging lens arranged between the biometry module and the eyepiece and a light path interference system with a first collimating lens; The biometry module, the imaging lens and the eyepiece are on a main light path for measuring biometric transverse parameters of an eye; The first collimating lens is aligned with the transmissive mirror and the light path is propagated through the transmissive mirror and the main light path, the light path interference system is signal connected with the biometry module for measuring biometric longitudinal parameters of the eye; The refraction system comprises a transmitting system with a checkerboard light spot generating module, a receiving system with a refraction measuring module and a fixation-vision system with a display unit; Image information emitted by the display unit and checkerboard light spots generated by the checkerboard light spot generating module can be propagated to an eye of a subject to be measured through the light path propagation system and the main light path; the checkerboard light spots formed by retinal reflection can be propagated to the refraction measuring module through the main light path and the light path propagation system, and the refraction measuring module measures the refractive power of the eye according to the deformation of the checkerboard light spots; The light path propagation system comprises a first beam splitter arranged between the imaging lens and the eyepiece and inclined towards the eyepiece; the transmissive mirror is arranged below the first beam splitter and parallel to the first beam splitter; the central region of the top surface of the transmissive mirror has a reflecting surface, and the peripheral region of the reflecting surface is a light-transmitting part; the first collimating lens is aligned with the reflecting surface, the light emitted by the first collimating lens is reflected to the first beam splitter through the reflecting surface, and the light reflected by the central region of the first beam splitter is reflected to the first collimating lens through the reflecting surface; the image information, the checkerboard light spots and the checkerboard light spots are propagated through the light-transmitting part respectively.

2. The ophthalmic examination measurement system of claim 1, wherein, A periscope is arranged between the imaging lens and the first beam splitter; The periscope has oppositely arranged high and low lenses, the imaging lens is aligned with the high lens, and the first beam splitter is aligned with the low lens; The light path of the light path propagation system passes below the imaging lens.

3. The ophthalmic examination measurement system of claim 1, wherein, The light path propagation system comprises a first mirror arranged below the transmissive mirror and parallel to the transmissive mirror; The reflecting light path of the first mirror comprises a vertical reflecting light path and a horizontal reflecting light path, the refraction system is arranged at the rear side of the first mirror and above the horizontal reflecting light path; The receiving system, the transmitting system and the fixation-vision system are arranged in a rear-to-front direction, and a second mirror, a second beam splitter and a third beam splitter are arranged on the horizontal reflecting light path correspondingly; The third beam splitter is used for reflecting the image information emitted by the display unit to the first mirror, and the second beam splitter is used for reflecting the checkerboard light spots to the first mirror. The reflected chessboard light spot can pass through the third beam splitter and the second beam splitter and be reflected by the second mirror to the refraction measurement module.

4. The ophthalmic examination measurement system of any one of claims 1-3, wherein, The fixation-fogging system comprises a focusing lens and a third mirror. The focusing lens is adjustably arranged between the third mirror and the display unit, and the third mirror is used for reflecting image information emitted by the display unit to the light path propagation system.

5. The ophthalmic examination measurement system of claim 4, wherein, The chessboard light spot generation module and the focusing lens are connected through a first linkage structure, and the chessboard light spot generation module and the focusing lens are kept in linkage.

6. The ophthalmic examination measurement system of any of claims 1-3, wherein, The chessboard light spot generation module comprises an infrared light source, a third collimating lens and a chessboard diaphragm arranged in sequence, and the chessboard diaphragm is used for forming the chessboard light spot.

7. The ophthalmic examination measurement system of claim 4, wherein, A relay lens assembly is arranged on the light path of the refraction measurement module, and the relay lens assembly is kept in linkage with the focusing lens to realize focusing.

8. The ophthalmic examination measurement system of claim 7, wherein, The relay lens assembly comprises a first relay lens and a second relay lens fixedly arranged and a third relay lens slidably arranged between the first relay lens and the second relay lens. The third relay lens is connected with the focusing lens or the chessboard light spot generation module through a second linkage structure.

9. A control method of an ophthalmic examination measurement system as claimed in any one of claims 1-8, characterized in that, The method comprises a biometry step and a refraction measurement step. The biometry step comprises a biometric transverse parameter measurement step and a biometric longitudinal parameter measurement step. The biometric transverse parameter measurement step comprises: The annular light board emits light towards the eye of the person to be measured, the imaging lens captures imaging data, and the imaging data is transmitted to the biometry module to obtain the biometric transverse parameter of the eye. The biometric longitudinal parameter measurement step comprises: The light path interference system is turned on, the first collimating lens emits a laser signal, and the laser signal is transmitted to the eye of the person to be measured through the light path propagation system and the main light path; The laser signal reflected by the eye returns to the light path interference system along the original path, and the light path interference system generates an interference oscillation signal by interference; The interference oscillation signal is transmitted to the biometry module to obtain the biometric longitudinal parameter of the eye; The refraction measurement step comprises: The display unit is turned on for the eye of the person to be measured to view; The chessboard light spot generated by the chessboard light spot generation module is transmitted to the eye of the person to be measured through the light path propagation system and the main light path; The chessboard light spot formed by retinal reflection is transmitted to the refraction measurement module through the main light path and the light path propagation system; The refraction measurement module measures the refractive power of the eye according to the deformation amount of the chessboard light spot.

Images