Ophthalmic examination measuring system and control method thereof

Abstract

The invention discloses an ophthalmic examination measurement system and a control method thereof. The ophthalmic examination measurement system comprises a biological measurement system, a refraction measurement system and a light path propagation system, the light path propagation system comprises an eyepiece with an annular lamp panel and a transmission reflector capable of transmitting light and reflecting light. The biological transverse parameters, the biological longitudinal parameters and the diopter of the eyes can be measured by adopting one set of system; the emission system of the refraction measurement system is provided with a checkerboard light spot generation module which is used for generating checkerboard light spots irradiating eyes, so that the problem of poor resolution of annular light spots in the prior art can be avoided, and the speed of judging the refraction state can be improved by comparing the checkerboard light spots formed before and after, so that the measurement accuracy is improved. And the accuracy of the inspection result is also improved.

Description

Technical Field

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

[0002] In the field of ophthalmic examination, optometrists are often used to measure the refractive power of the eye, and biometers are used to measure the biological parameters of the eye.

[0003] Refractive power includes spherical refractive power, cylindrical refractive power, astigmatism axis, etc. Refractive power measurement generally uses a light source to illuminate the eye, forming a ring-shaped light spot on the retina around the macula in the fundus, and then photographs the ring-shaped light spot reflected back from the retina to calculate the refractive power.

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

[0005] In the prior art, a Chinese invention patent with publication number CN113440099A discloses a comprehensive human eye vision examination device, which is composed of an optical path component and a three-dimensional motion platform. The optical path component is fixed to the upper end of the three-dimensional motion platform, and the alignment with the human eye is completed by the movement of the three-dimensional motion platform in the X, Y, and Z directions. The optical path component is composed of a biometric system, a refractive measurement system, and a curvature measurement system. The biometric system is used to measure biological parameters of the human eye; the refractive measurement system is used to measure the diopter of the human eye; and the curvature measurement system is used to measure the curvature of the human cornea.

[0006] According to the characteristics of the biometric system and the refractive measurement system, the two systems are cleverly integrated by using a middle-aperture reflector. The sample arm of the biometric system is actually also the projection optical path of the refractive measurement system, and the light source is also unified as one light source. The projection optical path is the same as the sample arm optical path of the biometric system, including the optical fiber head, condenser, middle-aperture reflector, second beam splitter, eyepiece and first beam splitter. Among them, the part after the middle-aperture reflector is shared with the refractive measurement optical path. The refractive measurement optical path includes the first beam splitter, eyepiece, second beam splitter, middle-aperture reflector, annular diaphragm, conical mirror, refractive measurement objective lens and refractive measurement camera. The middle-aperture reflector is used for the projection optical path, and its function is to transmit the light emitted by the refractive measurement light source; it is used for the refractive measurement optical path, and its function is to reflect the light reflected back from the fundus into the refractive measurement camera. Since the small hole in the central area cannot reflect light, the light reflected back from the fundus will become a halo after reflection, instead of a light spot. Its function is to collect the light reflected by the human eye at the convergent spot of the fundus, and through the action of the cone mirror and the refractive measurement objective lens, form a halo on the refractive measurement camera to intercept the light emitted by the refractive measurement light source reflected by the central area of ​​the human cornea (macular area). By analyzing the halo morphology, the refractive power information of the measured human eye can be obtained.

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

[0008] First: a weak coherent light source is used, which is emitted from the optical fiber head, then focused by a condenser, and then passes through the hole of the middle hole reflector, and then passes through the second beam splitter, the eyepiece and the first beam splitter in sequence to the eye. The light reflected from the retina is then formed into a halo by the middle hole reflector and the annular diaphragm, and finally forms a halo on the refractive measurement camera. The halo is formed on the light path after the retina is reflected, that is, the halo is formed on the receiving light path of the camera, and is determined by the structure and arrangement of the middle hole reflector and the annular diaphragm. There may be inaccuracies in intercepting the reflected light in the macular area, such as offset, which may cause distortion in the reaction of the annular light spot of the retina, affecting the inspection results. The above-mentioned prior art completely relies on the image of the annular light spot formed by the later interception to judge the refractive state of the eye, and the deformation judgment of the annular light spot is not so obvious. The speed of judging the refractive state is relatively slow, and the accuracy of the results needs to be improved.

[0009] Second: Determined by the characteristics of the optical fiber and the weakly coherent light source, the light spot emitted from the optical fiber is a Gaussian distribution spot, and its light intensity cross section is brightest in the center and decreases around the periphery. Therefore, the illumination distribution of the light spot when it reaches the fundus of the eye is also Gaussian distribution. Therefore, the brightness distribution of the light spot returning from the human eye to the middle hole reflector and the annular aperture is also Gaussian distribution. Then the light that can be reflected by the middle hole reflector and pass through the annular aperture is affected by the Gaussian distribution. Since the refractive power of different users' eyes 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 of the invention

[0010] The purpose of the present invention is to overcome the deficiencies of the prior art and provide an ophthalmic examination measurement system and a control method thereof, which are configured with a biological measurement system and a refractive measurement system, and can measure the biological transverse parameters, biological longitudinal parameters and refractive power of the eye with one set of systems; the transmitting system of the refractive measurement system is configured with a checkerboard light spot generation module, which is used to generate a checkerboard light spot for irradiating the eye, and the deformation judgment of the checkerboard light spot is much faster and more accurate than the deformation judgment of the annular light spot, which improves the speed of judging the refractive state and the accuracy of the inspection results. The brightness of the light spot emitted by the checkerboard light spot generation module is uniform and will not be Gaussian distributed. The annular aperture is no longer set on the receiving optical path of the receiving system. The captured images of human eyes with different refractive powers are roughly the same in brightness and signal-to-noise ratio, which is more convenient to process and improves the calculation accuracy.

[0011] The technical solution of the present invention provides an ophthalmic examination and measurement system, including a biological measurement system, a refractive measurement system and an optical path propagation system;

[0012] The optical path propagation system includes an eyepiece with an annular light plate and a transmissive reflector capable of transmitting and reflecting light;

[0013] The biometric system comprises a biometric module, an imaging lens arranged between the biometric module and the eyepiece, and an optical path interference system having a first collimating lens;

[0014] The biological measurement module, the imaging lens and the eyepiece are located on the main optical path and are used to measure the biological lateral parameters of the eye;

[0015] The first collimating lens is aligned with the transmission reflector, and light path propagation is achieved through the transmission reflector and the main light path, and the light path interference system is connected to the biological measurement module signal to measure the biological longitudinal parameters of the eye;

[0016] The refractive measurement system comprises a transmitting system having a checkerboard light spot generating module, a receiving system having a refractive measurement module and a fixation-fog vision system having a display unit;

[0017] The image information emitted by the display unit and the checkerboard light spots generated by the checkerboard light spot generation module can be transmitted to the eyes of the person to be measured via the optical path propagation system and the main optical path; the checkerboard light spots formed by retinal reflection can be transmitted to the refractive measurement module via the main optical path and the optical path propagation system, and the refractive measurement module measures the refractive power of the eye according to the deformation of the checkerboard light spots.

[0018] In one of the optional technical solutions, the optical path propagation system includes a first beam splitter disposed between the imaging lens and the eyepiece and tilted toward the eyepiece side;

[0019] The transmission reflector is located directly below the first beam splitter and is arranged in parallel with the first beam splitter;

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

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

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

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

[0024] The periscope has a high-position lens and a low-position lens that are relatively arranged, 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 under the imaging lens.

[0026] In one of the optional technical solutions, the optical path propagation system includes a first reflector, which is arranged directly below the transmission reflector and parallel to the transmission reflector;

[0027] The reflection light path of the first reflection mirror includes a vertical reflection light path and a horizontal reflection light path, and the refraction measurement system is located at the rear side of the first reflection mirror and above the horizontal reflection light path;

[0028] The receiving system, the transmitting system and the fixed vision-fog vision system are arranged in a spaced manner from back to front, and a second reflector, a second beam splitter and a third beam splitter are provided on the horizontal reflection light path accordingly;

[0029] The third beam splitter is used to reflect the image information emitted by the display unit toward the first reflector, and the second beam splitter is used to reflect the checkerboard light spot toward the first reflector;

[0030] The reflected checkerboard light spot can pass through the third beam splitter and the second beam splitter, and be reflected by the second reflector toward the refraction measurement module.

[0031] In one of the optional technical solutions, the fixed vision-fog vision system includes a focusing lens and a third reflecting mirror;

[0032] The focusing lens is adjustably arranged between the third reflecting mirror and the display unit, and the third reflecting mirror is used to reflect the image information emitted by the display unit toward the optical path propagation system.

[0033] In one of the optional technical solutions, the checkerboard light spot generating module is connected to the focusing lens via a first linkage structure, and the checkerboard light spot generating module maintains linkage with the focusing lens.

[0034] In one of the optional technical solutions, the checkerboard spot generation module includes an infrared light source, a third collimating lens and a checkerboard aperture arranged in sequence, and the checkerboard aperture is used to form the checkerboard spot. In one of the optional technical solutions, a relay lens assembly is provided on the optical path of the refractive measurement module, and the relay lens assembly is linked with the focusing lens to achieve focusing.

[0035] In one of the optional technical solutions, the relay lens assembly includes a first relay lens and a second relay lens that are fixedly arranged, and a third relay lens that is slidably arranged between the first relay lens and the second relay lens;

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

[0037] The technical solution of the present invention also provides a control method of an ophthalmic examination and measurement system, including a biological measurement step and a refractive measurement step;

[0038] The biological measurement step includes a biological transverse parameter measurement step and a biological longitudinal parameter measurement step;

[0039] The biological lateral parameter measurement step includes:

[0040] The annular light panel emits light toward the eyes of the subject to be measured, the imaging lens captures and obtains imaging data, and transmits the imaging data to the biological measurement module to obtain biological lateral parameters of the eyes;

[0041] The steps for measuring biological longitudinal parameters include:

[0042] The optical path interference system is turned on, and the first collimating lens emits a laser signal, and the laser signal is transmitted to the eyes of the subject 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 the optical path interference system interferes to generate an interference oscillation signal;

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

[0045] The refraction measurement step comprises:

[0046] Turning on the display unit for viewing by the subject;

[0047] The checkerboard light spot generated by the checkerboard light spot generating module illuminates the eyes of the subject through the light path propagation system and the main light path;

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

[0049] The refraction measurement module measures the refraction of the eye according to the deformation of the chessboard light spot.

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

[0051] The ophthalmological examination measurement system and control method thereof provided by the present invention 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, biological longitudinal parameters and refractive power of the eye can be measured by using one system, thereby improving work efficiency.

[0052] The transmitting system of the refractive measurement system is equipped with a checkerboard light spot generating module, which is used to generate a checkerboard light spot and transmit it to the eyes of the user to be tested. The checkerboard light spot is reflected by the retina to the refractive measurement module, and the refractive measurement module measures the refractive power of the eye according to the deformation of the checkerboard light spot. Since the checkerboard light spot is composed of multiple light spot units, one light spot is divided into multiple small diamond-shaped light spots as a whole, and has multiple intersections, which can be used as reference points for comparison and judgment, so that the change and deformation of the checkerboard light spot can be quickly judged, so as to quickly calculate the refractive power, which greatly improves the accuracy of the inspection results.

[0053] When judging the refractive state, compared with the method of emitting light spots from optical fibers in the prior art, the checkerboard light spots emitted by the checkerboard light spot generation module in the present invention have uniform brightness and will not be Gaussian distributed. The receiving optical path of the receiving system is no longer provided with an annular aperture. The images captured by human eyes with different refractive powers are roughly of equivalent brightness and equivalent signal-to-noise ratio, which is more convenient to process and improves the calculation accuracy. In the ophthalmic examination and measurement system provided by the present invention, the optical path for measuring biological transverse parameters coincides with the main optical path, and the optical path for measuring biological transverse parameters and the refractive measurement optical path are integrated in the optical path propagation system, and the light propagation is realized by conducting the optical path propagation system with the main optical path, respectively. The optical path reuse rate is high, and the optical path components are saved, which is conducive to saving costs and reducing the volume of the product. BRIEF DESCRIPTION OF THE DRAWINGS

[0054] The disclosure of the present invention will become more easily understood with reference to the accompanying drawings. It should be understood that these drawings are only for illustrative purposes and are not intended to limit the scope of protection of the present invention. In the drawings:

[0055] Figure 1 A schematic diagram of an ophthalmic examination measurement system provided by an embodiment of the present invention;

[0056] Figure 2 It is a schematic diagram of the optical path interference system;

[0057] Figure 3 is a schematic diagram of the structure of a transflective mirror;

[0058] Figure 4 is a schematic diagram of a refractive measurement system;

[0059] Figure 5 is a schematic diagram of a periscope provided between the imaging lens and the first beam splitter;

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

[0061] Figure 7 Schematic diagram of the initial image of the checkerboard light spot;

[0062] Figure 8 It is a schematic diagram of the shape of the checkerboard light spots reflected back from the retina when the diopter is not zero;

[0063] Fig. 9 is another schematic diagram of the checkerboard light spots reflected back from the retina when the diopter is not zero;

[0064] Fig.10 Schematic diagram of marking a checkerboard light spot, where the initial image of the checkerboard light spot is a square;

[0065] Fig.11This is a schematic diagram for marking the checkerboard light spots reflected back from the retina, wherein the image of the checkerboard light spots reflected back from the retina is non-square. DETAILED DESCRIPTION

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

[0067] like Figure 1-2 , Figure 4 and Figure 6-11 As shown, an ophthalmic examination measurement system provided by an embodiment of the present invention includes a biological measurement system 1, a refractive measurement system 2 and an optical path propagation system 4. The optical path propagation system 4 includes an eyepiece 3 having an annular light plate 31 and a transmissive reflector 41 capable of transmitting and reflecting light. The biological measurement system 1 includes a biological measurement module 11, an imaging lens 12 arranged between the biological measurement module 11 and the eyepiece 3, and an optical path interference system 13 having a first collimating lens 136.

[0068] The biological measurement module 11 , the imaging lens 12 and the 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 reflector 41 , and realizes light path propagation with the main light path 5 through the transmission reflector 41 . The light path interference system 13 is signal-connected with the biological measurement module 11 for measuring the biological longitudinal parameters of the eye 6 .

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

[0071] The image information sent by the display unit 231 and the checkerboard light spot generated by the checkerboard light spot generating 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 the retina reflection can be transmitted to the refraction measurement module 221 through the main optical path 5 and the optical path propagation system 4, and the refraction measurement module 221 measures the refraction of the eye 6 according to the deformation of the checkerboard light spot.

[0072] The ophthalmic examination and measurement system provided by the present invention is used to measure the diopter and biological parameters of the eye 6, and includes a biological measurement system 1, a refractive measurement system 2, an eyepiece 3, an optical path propagation system 4, and a main optical path 5. The biological measurement system 1, the refractive measurement system 2, the eyepiece 3, the optical path propagation system 4, and the main optical path 5 can be integrated in one or more shells and placed on an existing three-dimensional motion platform. The three-dimensional motion platform can realize three-dimensional motion of front and back, left and right, and up and down, so that the main optical path 5 can automatically move to the eye 6 of the person to be measured. For the working principle of the three-dimensional motion platform, reference can be made to the contents in the prior art, which will not be repeated here.

[0073] The ophthalmic examination and measurement system provided by the present invention is equipped with a main control unit, such as a control circuit board, a control chip, etc., which is used to control the operation of electrical instruments and can also be used to measure refractive power and biological parameters based on the obtained image data, signal data, etc.

[0074] The biometric system 1 is used to measure or detect biometric parameters of the eye 6, including biometric transverse parameters and biometric longitudinal parameters.

[0075] The biometric system 1 includes a biometric module 11 , an imaging lens 12 , an optical path interference system 13 , and the like.

[0076] The biometric module 11 can measure the biometric parameters of the eye 6 through the obtained image data, signal data, etc. The biometric module 11 can use CMOS, specifically a component with an integrated circuit chip and a photosensitive element / camera lens. The biometric module 11 can measure the biometric parameters. The biometric module 11 is connected to the main control unit for communication, and the main control unit can also measure the biometric parameters.

[0077] The imaging lens 12 is an infrared camera, which is arranged in front of the biometric measurement module 11 and at the rear of the eyepiece 3, and the three are on the main optical path 5. The eyepiece 3 is used to align with the eye 6 of the subject to be measured. A ring light board 31 is arranged around the eyepiece 3, and a plurality of light sources are arranged at intervals along the circumferential direction on the front side of the ring light board 31, and the light sources include infrared light sources, visible light sources, etc., which are used to illuminate the glasses 6 of the subject to be measured.

[0078] The biological measurement module 11, the imaging lens 12 and the eyepiece 3 are located on the main optical path 5, and are used to measure the biological lateral parameters of the eye 6. The general operation is as follows: the light source of the ring light panel 31 is turned on, and the light is emitted toward the eye 6 of the person to be measured. The imaging lens 12 captures the imaging data, and transmits the imaging data to the biological measurement module 11, and obtains the biological lateral parameters of the eye 6.

[0079] According to different biological horizontal parameters, it is divided into:

[0080] Corneal curvature radius measurement: An infrared light source is used to illuminate the eye 6. After the infrared light is projected onto the cornea, it is reflected by the cornea to form a primary image. The primary image is reflected to the imaging lens 12 via the main light path 5. The imaging lens 12 takes a secondary image and transmits the imaging data to the biometrics module 11. The curvature radius of the human cornea can be obtained by calculating according to the existing algorithm based on the acquired image data.

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

[0082] The algorithms for the corneal curvature radius, the white-white distance, and the pupil diameter are already known in the prior art and will not be described in detail here.

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

[0084] The optical path propagation system 4 has a transmission reflector 41, the center of which can reflect light, while the periphery can transmit light. Therefore, the transmission reflector 41 can allow the checkerboard light spots transmitted from the refractive measurement system 2 and the checkerboard light spots reflected by the retina to pass through. The transmission reflector 41 can also reflect the laser emitted from the first collimating lens 136 toward the main optical path 5, and can also reflect the light transmitted from the main optical path 5 toward the first collimating lens 136.

[0085] The measurement method of the biological longitudinal parameters is as follows: the optical 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 subject through the transmission reflector 41, the optical path propagation system 4 and the main optical path 5. The laser signal reflected by the eye 6 returns to the optical path interference system 13 along the original path, and the optical path interference system 13 interferes to generate an interference oscillation signal. The interference oscillation signal is transmitted to the biological measurement module 11 to obtain the biological longitudinal parameters of the eye 6.

[0086] like Figure 6 As shown, the axial length is the distance ae, the corneal thickness is the distance ab, the anterior chamber depth is the distance bc, and the lens thickness is the distance cd.

[0087] Specifically, the optical path interference system 13 includes an SLD light source 131 (broadband laser), an upper arm optical fiber flange 132, a lower arm optical 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 measuring reflector 139. The SLD light source 131 is connected to the coupler 134, and the coupler 134 is also connected to the upper arm optical fiber flange 132, the lower arm optical fiber flange 133, and the detector 135. The SLD light source 131 emits laser light, which is split by the coupler 134 to form a first path of laser light and a second path of laser light. The first path of laser light is incident on the transmission reflector 41 through the upper arm optical fiber flange 132 and the first collimating lens 136 for reflection, and then propagates to the eye 6 of the subject through the optical path propagation system 4 and the main optical path 5. The eye 6 reflects the laser signal and returns along the original path and passes through the coupler 134. The second laser beam is injected into the optical path changing device 138 through the lower arm optical fiber flange 133 and the second collimating lens 137. The optical path changing device 138 is a device that rotates periodically to change the optical path. The second laser beam is returned to the coupler 134 through the measuring reflector 139 to form interference, which plays a role in enhancing the optical signal and is easier to be detected by the detector 135. The detector 135 is connected to the biological measurement module 11 for communication. The detector 135 converts the interference oscillation signal into photoelectric conversion and then transmits it to the biological measurement module 11. After decoding, the signal can be obtained as follows: Figure 6 The interlayer interference pattern of the glasses 6 is shown.

[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 optical path of the refractive measurement system 2 is connected to the main optical path 5 through the optical path propagation system 4 to transmit the optical signal.

[0089] The refraction measurement system 2 includes a transmitting system 21 , a receiving system 22 and a fixation-fog system 23 .

[0090] The emission system 21 has a checkerboard light spot generation module 211, which can generate a relatively regular checkerboard light spot. As shown in 7-9, the checkerboard light spot is composed of a plurality of light spot units. A relatively regular checkerboard light spot or a checkerboard light spot in the initial state is composed of a plurality of square light spot units. After being reflected by the retina, the light spot unit changes into a rhombus or parallelogram without right angles. Then, the checkerboard light spot formed after the retina is reflected is composed of a plurality of rhombus light spot units or parallelogram light spot units without right angles.

[0091] The checkerboard light spot can enter the main light path 5 through the refractive measurement light path and the light path propagation system 4, and then be emitted to the eye 6. The receiving system 22 has a refractive measurement module 221, which is used to receive the checkerboard light spot reflected by the retina. Due to the different refractive states of the eye 6 (including spherical refractive power, cylindrical refractive power, and astigmatism axis), the checkerboard 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, there is a difference between the checkerboard light spot reflected by the retina and the checkerboard light spot formed by the checkerboard light spot generation module 211, and this difference will reflect the refractive state of the eye 6. The checkerboard light spot reflected by the retina will enter the refractive measurement module 221 along the main light path 5, the light path propagation system 4, and the refractive measurement light path. After receiving the checkerboard light spots reflected by the retina, the refractive measurement module 221 compares the checkerboard light spots reflected by the retina with the checkerboard light spots formed by the checkerboard light spot generating module 211. If the checkerboard light spots formed by the checkerboard light spot generating module 211 are not deformed, it indicates that the refractive state of the user's eyes is good; if the checkerboard light spots formed by the checkerboard light spot generating module 211 are deformed, it indicates that there are certain problems with the refractive state of the user's eyes, such as myopia, hyperopia, astigmatism and other problems, and further measures each refractive state.

[0092] Since the checkerboard light spot is composed of multiple light spot units, one light spot is divided into multiple small diamond-shaped light spots as a whole, and has multiple intersections, which can be used as reference points for comparison and judgment, so that the change and deformation of the checkerboard light spot can be quickly judged, and the refractive power can be quickly calculated, which greatly improves the accuracy of the inspection results.

[0093] How to calculate the refractive state will be discussed in detail in the following section.

[0094] The refractive measurement module 221 may be a CMOS, specifically a component having an integrated circuit chip and a photosensitive element / camera lens. The refractive measurement module 221 may measure biological parameters. The refractive measurement module 221 is connected to the main control unit for communication, and the main control unit may also measure biological parameters.

[0095] The fixation-fog system 23 has a display unit 231 for displaying icons, pictures, videos, etc., for locating the sight line of the eye 6. Fixation means that the eye 6 stares at a target, such as an icon, and fixes the sight line. Fog means that the eye 6 is in a relaxed state, such as watching a video, a picture, etc., which can provide more reference standards and help improve the accuracy of the measurement results. The image signal mentioned in the present invention includes a video signal, a text signal, a logo signal, a picture signal, etc.

[0096] The method of refraction measurement is: turn on the display unit 231 for the eyes of the person to be measured to see.

[0097] The checkerboard light spot generating module 211 works and generates a checkerboard light spot, and the checkerboard light spot illuminates the eye 6 of the subject through the light path propagation system 4 and the main light path 5 .

[0098] The checkerboard light spot is reflected by the retina to form a checkerboard light spot, and the checkerboard light spot is transmitted to the refractive measurement module 221 through the main optical path 5 and the optical path transmission system 4. The refractive measurement module 221 measures the refractive power of the eye 6 according to the deformation of the checkerboard light spot.

[0099] In summary, the ophthalmic examination and measurement system provided by the present invention is configured with a biological measurement system 1 and a 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, biological longitudinal parameters and refractive power of the eye 6 can be measured by using one system, thereby improving work efficiency.

[0100] The transmitting system 21 of the refractive measurement system 2 is configured with a checkerboard light spot generating module 211, which is used to generate a checkerboard light spot and transmit it to the user's eye 6. 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 of the checkerboard light spot. Since the checkerboard light spot is composed of a plurality of light spot units, one light spot as a whole is divided into a plurality of small diamond-shaped light spots and has a plurality of intersections, which can be used as reference points for comparison and judgment, so that the change and deformation of the checkerboard light spot can be quickly judged, so as to quickly calculate the refractive power, thereby greatly improving the accuracy of the inspection results.

[0101] When judging the refractive state, compared with the method of emitting light spots from optical fibers in the prior art, the checkerboard light spots emitted by the checkerboard light spot generating module 211 in the present invention have uniform brightness and are not Gaussian distributed. An annular aperture is no longer provided on the receiving optical path of the receiving system. The images captured by human eyes with different refractive powers have roughly the same brightness and signal-to-noise ratio, which makes processing more convenient and improves calculation accuracy.

[0102] In the ophthalmic examination and measurement system provided by the present invention, the optical path for measuring biological lateral parameters coincides with the main optical path 5, and the optical path for measuring biological lateral parameters and the optical path for refractive measurement are integrated in the optical path propagation system 4. The optical path propagation system 4 and the main optical path 5 are respectively connected to realize light propagation. The optical path reuse rate is high, which saves optical path components, is beneficial to saving costs and reducing the volume of products.

[0103] In one embodiment, if Figure 1 and Figure 3-4 As shown, the optical path propagation system 4 includes a first beam splitter 42 disposed between the imaging lens 12 and the eyepiece 3 and tilted toward the eyepiece 3 side.

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

[0105] The central area of ​​the top surface of the transflective mirror 41 has a reflective surface 411 , and the peripheral area of ​​the reflective surface 411 is a light-transmitting portion 412 .

[0106] The first collimating lens 136 is aligned with the reflecting surface 411 . The light emitted from the first collimating lens 136 is reflected by the reflecting surface 411 to the first beam splitter 42 . The light reflected from the central area of ​​the first beam splitter 42 is reflected by the reflecting surface 411 to the first collimating lens 136 .

[0107] The image information, the checkerboard light spots and the checkerboard light spots are transmitted through the light-transmitting portion 412 respectively.

[0108] In this embodiment, the optical path propagation system 4 includes a first beam splitter 42, which is disposed between the imaging lens 12 and the eyepiece 3, is located on the main optical path 5 and is tilted toward the eyepiece 3. The first beam splitter 42 reflects the light transmitted from the transmission reflector 41 toward the eye 6, and is also used to reflect the light reflected back from the eye 6 toward the transmission reflector 41.

[0109] The transflector 41 is located directly below the first beam splitter 42 , and the two are arranged substantially in parallel. The central area of ​​the top surface of the transflector 41 has a reflective surface 411 , and the peripheral area of ​​the reflective surface 411 is a light-transmitting portion 412 .

[0110] The first collimating lens 136 is aligned with the reflecting surface 411, so the light emitted from the first collimating lens 136 is reflected by the reflecting surface 411 and then emitted to the first beam splitter 42, and then the first beam splitter 42 reflects the light toward the eye 6. The light reflected by the eye 6 reaches the central area of ​​the first beam splitter 42, and the light reflected by this part is emitted to the reflecting surface 411, and then reflected back to the first collimating lens 136 by the reflecting surface 411.

[0111] The image information generated by the refractive measurement system 2, the checkerboard light spots generated by the checkerboard light spot generation module 211 and the checkerboard light spots reflected by the retina are respectively transmitted through the light-transmitting portion 412. A small part of the image information and the checkerboard light spots will be blocked by the reflective surface 411, but it will not affect the viewing of the eye 6.

[0112] In one embodiment, if Figure 1 and Figure 5 As shown, a periscope 14 is provided between the imaging lens 12 and the first beam splitter 42 .

[0113] The periscope 14 has a high-position lens 141 and a low-position lens 142 that are arranged relatively to each other. 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 under the imaging lens 12 .

[0115] In this embodiment, a periscope 14 is provided 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 under the imaging lens 12, which is beneficial to improving the integration of the system and reducing the height size of the product.

[0116] In one embodiment, if Figure 1 and Figure 4 As shown, the optical path propagation system 4 includes a first reflector 43 , which is disposed directly below the transmission reflector 41 and parallel to the transmission reflector 41 .

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

[0118] The receiving system 22 , the transmitting system 21 and the fixation-fog system 23 are arranged in a spaced relationship from the back to the front, and a second reflector 44 , a second beam splitter 45 and a third beam splitter 46 are provided on the horizontal reflection light path 432 .

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

[0120] The reflected checkerboard light spots can pass through the third beam splitter 46 and the second beam splitter 45 , and are reflected by the second reflector 44 toward the refraction measurement module 221 .

[0121] In this embodiment, the optical path propagation system 4 is equipped with a first reflector 43 for realizing vertical and horizontal optical path conduction. The first reflector 43 is arranged directly below the transmission reflector 41 and is arranged parallel to the transmission reflector 41. The reflection optical path of the first reflector 43 is divided into a vertical reflection optical path 431 and a horizontal reflection optical path 432. The transmission reflector 41 and the first beam splitter 42 are on the vertical reflection optical path 431.

[0122] The refractive measurement system 2 is arranged on the rear side of the first reflector 43 and above the horizontal reflective optical path 432. Specifically, the receiving system 22, the transmitting system 21 and the fixation-fog system 23 are arranged on the rear side of the imaging lens 12 and are arranged in sequence from the back to the front. Such an arrangement can reduce the height of the product.

[0123] In order to realize the conduction between the optical paths of the receiving system 22 , the transmitting system 21 and the fixation-fog vision system 23 and the horizontal reflection optical path 432 , a second reflector 44 , a second beam splitter 45 and a third beam splitter 46 are provided on the horizontal reflection optical path 432 accordingly.

[0124] The third beam splitter 46 is disposed directly below the light output end of the fixed vision-fog vision 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 toward the first reflector 43.

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

[0126] The second reflector 44 is disposed directly below the light incident end of the receiving system 22 to achieve optical path conjugation. The reflected checkerboard light spots can pass through the third beam splitter 46 and the second beam splitter 45 and are reflected by the second reflector 44 toward the refraction measurement module 221 .

[0127] In one embodiment, if Figure 4 As shown, an emission light path relay lens 212 is disposed at the light output end of the checkerboard light spot generating module 211 to improve the quality of the image signal.

[0128] In one of the embodiments, the checkerboard light spot generating module 211 can be moved and adjusted relative to the emission light path relay lens 212, so that the size of the checkerboard light spot can be adjusted to adapt to the eyes of different users.

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

[0130] The focusing lens 232 is adjustably 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 toward the optical path propagation system 4 .

[0131] In this embodiment, the fixed vision-fog vision system 23 also includes a focusing lens 232 and a third reflector 233. The display unit 231 is arranged above the imaging lens 12 and arranged backward. The focusing lens 232 and the third reflector 233 are sequentially arranged on the rear side of the display unit 231 to form a horizontal light path. The focusing lens 232 is adjustably arranged between the third reflector 233 and the display unit 231 to play a focusing role. The third reflector 233 is used to reflect the image information emitted by the display unit 231 toward the light path propagation system 4, for example, toward the third beam splitter 46.

[0132] In one embodiment, if Figure 4 As shown, a fixed vision-fog vision optical path relay lens 234 is provided between the focusing lens 232 and the display unit 231 and / or between the third reflector 233 and the third beam splitter 46 to improve the quality of the image signal.

[0133] In one embodiment, if Figure 4 As shown, the checkerboard light spot generating module 211 is connected to the focusing lens 232 through the first linkage structure 24, and the checkerboard light spot generating module 211 and the focusing lens 232 are kept in linkage. When the focusing lens 232 is focusing, the checkerboard light spot generating module 211 slides accordingly, thereby changing the distance between the checkerboard light spot generating module 211 and the transmitting light path relay lens 212, and adjusting the size of the checkerboard light spot accordingly. The corresponding light path can be pre-designed, and after the focusing lens 232 completes focusing, the checkerboard light spot generating module 211 reaches a suitable position at the same time.

[0134] The first linkage structure 24 can be a combination of a connecting rod, a pull rope and a fixed pulley.

[0135] like Figure 4 As shown, 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 checkerboard spot generation module 211 and the focusing lens 232. The pull rope 241 connects the checkerboard spot generation module 211 and the focusing lens 232 and turns through the fixed pulley 242. The pull rope 241 can reduce interference with surrounding parts.

[0136] In one embodiment, if Figure 1 and Figure 4 As shown, the checkerboard light spot generating module 211 includes an infrared light source 2111, a third collimating lens 2112 and a checkerboard aperture 2113 which are arranged in sequence. The checkerboard aperture 2113 cooperates with the conical lens 2113 to form a checkerboard light spot.

[0137] In this embodiment, a checkerboard aperture 2113 is used to form a checkerboard light spot. The checkerboard aperture 2113 is in a mesh shape, and each small unit thereof is a square structure. The infrared light source 2111 is an infrared LED light source, and the light emitted by the infrared light source is collimated by the third collimating lens 2112 and then incident on the checkerboard aperture 2113, and then a checkerboard light spot is formed. In one embodiment, as Figure 1 and Figure 4 As shown, a relay lens assembly 222 is provided on the optical path of the refractive measurement module 221 , and the relay lens assembly 222 is linked with the focusing lens 232 to achieve focusing.

[0138] In this embodiment, the light input end of the refractive measurement module 221 is provided with a relay lens assembly 222 for improving the quality of the light spot, and the relay lens assembly 222 can also be slidably adjusted relative to the refractive measurement module 221, thereby playing a focusing role. The movement amount or focusing amount of the relay lens assembly 222 is achieved by the movement of the focusing lens 232. The corresponding optical path can be pre-designed, and after the focusing lens 232 completes the focusing, the relay lens assembly 222 reaches a suitable position at the same time.

[0139] In one embodiment, if Figure 1 and Figure 4 As shown, the relay lens assembly 222 includes a first relay lens 2221 and a second relay lens 2222 that are fixedly arranged, and a third relay lens 2223 that is slidably arranged between the first relay lens 2221 and the second relay lens 2222 .

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

[0141] In this embodiment, the relay lens assembly 222 is a combination of a first relay lens 2221, a second relay lens 2222, and a 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 to the focusing lens 232 or the checkerboard light spot generating module 211 through the second linkage structure 25, so as to realize linkage focusing.

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

[0143] Combination Figure 1-11 As shown, a control method for an ophthalmic examination measurement system provided by an embodiment of the present invention includes a biological measurement step and a refractive measurement step.

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

[0145] The biological lateral parameter measurement step includes:

[0146] The annular light panel 31 emits light toward the eye 6 of the subject to be measured, and the imaging lens 12 captures and obtains imaging data, and transmits the imaging data to the biological measurement module 11 to obtain biological lateral parameters of the eye 6 .

[0147] The steps for measuring biological longitudinal parameters include:

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

[0149] The laser signal reflected by the eye 6 returns to the optical path interference system 13 along the original path, and is interfered by the optical path interference system 13 to generate an interference oscillation signal.

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

[0151] The steps of refraction measurement include:

[0152] The display unit 231 is turned on for viewing by the eyes of the subject.

[0153] The checkerboard light spot generating module 211 works and generates a checkerboard light spot, and the checkerboard light spot illuminates 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 the retina reflection is transmitted to the refractive measurement module 221 through the main optical path 5 and the optical path transmission system 4. The refractive measurement module 221 measures the refractive power of the eye 6 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 light panel is lit and the switching of each component can be carried out as needed.

[0156] The diopter measurement is calculated as follows:

[0157] The checkerboard light spot generation module 211 can be moved and adjusted on the optical 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 many experiments, it can be determined that the checkerboard light spot generation module 211 and the refractive power have a linear correspondence: S = kc × j + e; wherein S represents the refractive power, j and e represent the adjustment parameters, and kc represents the linear function coefficient. The position of the checkerboard light spot generation module 211 is directly substituted into P, j and e in the above formula and determined experimentally, thereby obtaining the refractive power (spherical refractive power) measurement result of the eye to be tested.

[0158] like Figure 7 The checkerboard light spot shown is composed of a number of small square light spot units of equal size. Compared with conventional circular or ring-shaped light spots, checkerboard light spots are easier to achieve orthodontics and can improve the accuracy of diopter measurement results.

[0159] The checkerboard spot generation module 211 projects a checkerboard spot square image. After being reflected by the retina, the fundus imaging image is obtained in the refraction measurement module 221. At this time, if the refractive power is zero, the fundus imaging image remains as a checkerboard spot. Otherwise, it will be deformed. After stretching and tilting, the image is obtained as follows Figure 8 or Fig. 9 The parallelogram shape shown in the figure makes it easier to determine whether the checkerboard spot is deformed and the amount of deformation. For example, by counting the pixels, the Figure 8-9 The deflection amount of the deflected corner points at the four corners of the chessboard light spot is calculated, thereby calculating the deformation amount of the chessboard light spot.

[0160] The j, e and kc in the above function can be obtained by fitting multiple sets of data through experiments. Specifically, the j value is determined by the following method:

[0161] like Fig.10 As shown, at least one square area is selected from the initial checkerboard light spot, and one of the square areas is used as the initial square. The four vertices of the initial square are marked as A1, B1, C1 and D1, respectively, A1B1=C1D1, B1C1=A1D1. The side length of the square is as long as possible, so this solution selects the positions of the four corner points as the four vertices of the initial square. Specifically, the intersection points of each adjacent square block of the checkerboard are identified by the checkerboard intersection recognition method, and the coordinate position of each intersection is accurately located to obtain the sub-pixel coordinate value, and the four outermost corner points are directly selected as the four vertices of the initial square.

[0162] Determine the imaging quadrilateral corresponding to the initial square in the checkerboard light spot reflected back by the retina, the four vertices of the imaging quadrilateral are A1', B1', C1' and D1', A1'B1'=C1'D1', B1'C1'=A1'D1'. When the cylindrical refractive power of the user's eye is zero, A1', B1', C1' and D1' still form a square, A1'B1'=C1'D1'=B1'C1'=A1'D1'. When the cylindrical refractive power of the eye to be tested is not zero, A1', B1', C1' and D1' form a square as follows Fig.11 The parallelogram shown.

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

[0164] For retinas with different diopters, the checkerboard spot generation module 211 is moved, and the fundus imaging image of the image retina is obtained through the refraction measurement module 221, and A1'B1', B1'C1' and c are obtained according to the above-mentioned checkerboard intersection recognition method. The c value has the following linear relationship with the lens position P: c=kpP+d. After multiple tests, the measurement results of simulated eyes with different diopters are fitted, and the coefficient kp and parameter d can be calculated. Let P=0 represent that the position of the checkerboard spot generation module 211 is at the set origin position, and the c value of different diopters when the position of the checkerboard spot generation module 211 is "0" can be calculated, represented by c0. Obviously, if P is 0, c0=j.

[0165] The diopter S has the following linear relationship with the above c0: S=kc×c0+e, that is, S=kc×j+e. After multiple tests, the measurement results of simulated eyes with different diopters are fitted to calculate the coefficient kc and the parameter e.

[0166] Obviously, using a checkerboard light spot for refractive power measurement can further simplify the calculation process.

[0167] The above-mentioned refractive power measurement method further includes:

[0168] Obtain the cylindrical diopter of the eye: C = S x (dc), where d = Max (A1'B1', B1'C1').

[0169] Obtaining the cylindrical lens axis angle α: Calculate ∠D1'A1'B1' according to the law of cosines. If A1'B1'>B1'C1', the cylindrical lens axis angle α=90°-∠D1'A1'B1'; if A1'B1'<B1'C1', α=∠D1'A1'B1'.

[0170] Through the application scheme, the deformation of the chessboard light spot can be used to directly measure the spherical mirror diopter, cylindrical mirror diopter and cylindrical mirror axis angle, which is simple to operate and requires little calculation.

[0171] The present application solution may also include a step of calibrating the diopter measurement result to avoid errors in the measurement result of a single square area due to environmental interference, etc. The calibration process is as follows:

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

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

[0174] Obtain the cylindrical diopter result corresponding to each of the auxiliary verification squares; obtain a second weighted average value of the cylindrical diopter results; if the difference between the cylindrical diopter and the second weighted average value is not within a set range, re-obtain the cylindrical diopter.

[0175] Obtain the cylindrical lens axis angle result corresponding to each of the auxiliary verification squares; obtain the third weighted average value of the cylindrical lens axis angle results; if the difference between the cylindrical lens axis angle and the third weighted average value is not within a set range, re-obtain the cylindrical lens axis angle.

[0176] The above steps refer to the calculation of the diopter (spherical lens), cylindrical lens diopter, and cylindrical lens axis angle for the auxiliary calibration square using the above steps. Afterwards, the average value is calculated based on each calculation result or the weighted average operation is performed based on the location of each square area. The average operation result is used as a judgment benchmark. If the calculation result of the original initial square does not deviate much from the benchmark, 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 scheme, it can be further ensured that the error of the diopter measurement result is within the allowable range.

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

[0178] The above are only the principles and preferred embodiments of the present invention. It should be noted that, for those skilled in the art, several other modifications can be made based on the principles of the present invention, which should also be considered as the protection scope of the present invention.

Claims

1. An ophthalmic examination measurement system, characterized in that: Including biometric system, refractive measurement system and optical path propagation system; The optical path propagation system includes an eyepiece with an annular light plate and a transmissive reflector capable of transmitting and reflecting light; The biometric system comprises a biometric module, an imaging lens arranged between the biometric module and the eyepiece, and an optical path interference system having a first collimating lens; The biological measurement module, the imaging lens and the eyepiece are located on the main optical path and are used to measure the biological lateral parameters of the eye; The first collimating lens is aligned with the transmission reflector, and light path propagation is achieved through the transmission reflector and the main light path, and the light path interference system is connected to the biological measurement module signal to measure the biological longitudinal parameters of the eye; The refractive measurement system comprises a transmitting system having a checkerboard light spot generating module, a receiving system having a refractive measurement module and a fixation-fog vision system having a display unit; The image information emitted by the display unit and the checkerboard light spots generated by the checkerboard light spot generation module can be transmitted to the eyes of the person to be measured via the optical path propagation system and the main optical path; the checkerboard light spots formed by retinal reflection can be transmitted to the refractive measurement module via the main optical path and the optical path propagation system, and the refractive measurement module measures the refractive power of the eye according to the deformation of the checkerboard light spots.

2. The ophthalmic examination measurement system according to claim 1, characterized in that: The optical path propagation system includes a first beam splitter disposed between the imaging lens and the eyepiece and tilted toward the eyepiece side; The transmission reflector is located directly below the first beam splitter and is arranged in parallel with the first beam splitter; The central area of ​​the top surface of the transmission reflector has a reflective surface, and the peripheral area of ​​the reflective surface is a light-transmitting portion; The first collimating lens is aligned with the reflecting surface, the light emitted by the first collimating lens is reflected by the reflecting surface to the first beam splitter, and the light reflected back by the central area of ​​the first beam splitter is reflected by the reflecting surface to the first collimating lens; The image information, the checkerboard light spots and the checkerboard light spots are respectively transmitted through the light-transmitting portion.

3. The ophthalmological examination measurement system according to claim 2, characterized in that: A periscope is provided between the imaging lens and the first beam splitter; The periscope has a high-position lens and a low-position lens that are relatively arranged, the imaging lens is aligned with the high-position lens, and the first beam splitter is aligned with the low-position lens; The light path of the light path propagation system passes under the imaging lens.

4. The ophthalmological examination measurement system according to claim 2, characterized in that: The optical path propagation system comprises a first reflector, which is arranged directly below the transmission reflector and parallel to the transmission reflector; The reflection light path of the first reflection mirror includes a vertical reflection light path and a horizontal reflection light path, and the refraction measurement system is located at the rear side of the first reflection mirror and above the horizontal reflection light path; The receiving system, the transmitting system and the fixed vision-fog vision system are arranged in a spaced manner from back to front, and a second reflector, a second beam splitter and a third beam splitter are provided on the horizontal reflection light path accordingly; The third beam splitter is used to reflect the image information emitted by the display unit toward the first reflector, and the second beam splitter is used to reflect the checkerboard light spot toward the first reflector; The reflected checkerboard light spot can pass through the third beam splitter and the second beam splitter, and be reflected by the second reflector toward the refraction measurement module.

5. The ophthalmic examination measurement system according to any one of claims 1 to 4, characterized in that: The fixed vision-fog vision system includes a focusing lens and a third reflecting mirror; The focusing lens is adjustably arranged between the third reflecting mirror and the display unit, and the third reflecting mirror is used to reflect the image information emitted by the display unit toward the optical path propagation system.

6. The ophthalmic examination measurement system according to claim 5, characterized in that: The chessboard light spot generating module is connected to the focusing lens via a first linkage structure, and the chessboard light spot generating module maintains linkage with the focusing lens.

7. The ophthalmic examination measurement system according to any one of claims 1 to 4, characterized in that: The checkerboard light spot generation module comprises an infrared light source, a third collimating lens and a checkerboard aperture which are arranged in sequence, and the checkerboard aperture is used to form the checkerboard light spot.

8. The ophthalmic examination measurement system according to claim 5, characterized in that: A relay lens assembly is provided on the optical path of the refractive measurement module, and the relay lens assembly is linked with the focusing lens to achieve focusing.

9. The ophthalmic examination measurement system according to claim 8, characterized in that: The relay lens assembly includes a first relay lens and a second relay lens which are fixedly arranged, and a third relay lens which is slidably arranged between the first relay lens and the second relay lens; The third relay lens is connected to the focusing lens or the chessboard light spot generating module through a second linkage structure.

10. A control method for an ophthalmic examination measurement system according to any one of claims 1 to 9, characterized in that: It includes a biometric measurement step and a refractive measurement step; The biological measurement step includes a biological transverse parameter measurement step and a biological longitudinal parameter measurement step; The biological lateral parameter measurement step includes: The annular light panel emits light toward the eyes of the subject to be measured, the imaging lens captures and obtains imaging data, and transmits the imaging data to the biological measurement module to obtain biological lateral parameters of the eyes; The steps for measuring biological longitudinal parameters include: The optical path interference system is turned on, and the first collimating lens emits a laser signal, and the laser signal is transmitted to the eyes of the subject through the optical path propagation system and the main optical path; The laser signal reflected by the eye returns to the optical path interference system along the original path, and the optical path interference system interferes to generate an interference oscillation signal; The interference oscillation signal is transmitted to the biological measurement module to obtain biological longitudinal parameters of the eye; The refraction measurement step comprises: Turning on the display unit for viewing by the subject; The checkerboard light spot generated by the checkerboard light spot generating module illuminates the eyes of the subject through the light path propagation system and the main light path; The checkerboard light spot formed by retinal reflection is propagated to the refraction measurement module through the main light path and the light path propagation system; The refraction measurement module measures the refraction of the eye according to the deformation of the chessboard light spot.

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