Computer optometry unit

Abstract

The utility model discloses a computer optometry unit which comprises a shell, a measuring light source light path, a diopter measuring light path, a corneal curvature measuring light path and a fixation light path, wherein the measuring light source light path, the diopter measuring light path, the corneal curvature measuring light path and the fixation light path are arranged in the shell. The measurement light source light path provides first light source light; the diopter measurement light path obtains incident measurement light from the first light source light, outputs the incident measurement light to human eyes, and receives first reflection measurement light reflected back by the human eyes; performing image acquisition on the first reflection measurement light to obtain a first image for measuring the diopter; the corneal curvature measuring light path provides second light source light for human eyes; second reflection measurement light reflected back by the human eyes is obtained; performing image acquisition on the second reflection measurement light to obtain a second image for measuring the corneal curvature; the fixation optical path provides sighting marks for human eyes. The diopter and the corneal curvature of the human eye can be measured at the same time, the measurement accuracy is high, ophthalmic examination is more comprehensive, and practicability is higher.

Description

Technical Field

[0001] The utility model relates to the technical field of ophthalmic equipment, in particular to a computer optometry instrument. Background Art

[0002] Computer ophthalmometer is an electronic objective ophthalmometer, which is the product of the combination of refractive examination technology and electronic computer technology. At present, computer ophthalmometer mainly adopts objective measurement method, projects infrared image to the fundus of human eye, produces scattered image on the retina of human eye, and objectively calculates the refractive power of eye by analyzing the measured image collected by CCD.

[0003] However, current computer ophthalmometers are mostly used to measure the refractive power of the human eye, without simultaneous measurement of corneal curvature, resulting in incomplete eye examinations. Utility Model Content

[0004] In view of this, the utility model provides a computer ophthalmometer to solve the problem that the existing ophthalmometer cannot detect the diopter and corneal curvature of the human eye at the same time and the detection is not comprehensive enough.

[0005] The utility model provides a computer ophthalmometer, comprising a housing and a measuring light source optical path, a diopter measuring optical path, a corneal curvature measuring optical path and a fixation optical path arranged in the housing;

[0006] The measuring light source optical path is used to provide the first light source light required for measuring the diopter;

[0007] The diopter measurement optical path is arranged on the output optical path of the measurement light source optical path, and is used to obtain incident measurement light from the first light source, output the incident measurement light to the human eye, and receive the first reflected measurement light reflected by the human eye; perform image acquisition on the first reflected measurement light to obtain a first image for measuring the diopter;

[0008] The corneal curvature measurement optical path is arranged near the human eye, and is used to provide the human eye with a second light source light required for measuring the corneal curvature; and obtain the second reflected measurement light reflected by the human eye; and perform image acquisition on the second reflected measurement light to obtain a second image for measuring the corneal curvature;

[0009] The fixation optical path is used to provide a sight mark to the human eye when the refractive power measurement optical path acquires the first reflected measurement light and when the corneal curvature measurement optical path acquires the second reflected measurement light.

[0010] Optionally, the measuring light source optical path includes a laser lamp, a light homogenizer, a collimating lens and a first beam splitter prism arranged in sequence;

[0011] The laser lamp, the light homogenizer and the collimating lens are arranged on the same optical axis, and the incident surface of the first beam splitter prism is arranged at an angle of 45° to the main optical axis of the collimating lens;

[0012] The laser lamp is used to provide a laser light source;

[0013] The light homogenizing sheet is used to homogenize the laser light source;

[0014] The collimating lens is used to focus the homogenized laser light source;

[0015] The first surface of the first beam splitter prism is used to split the focused laser light source to obtain the first light source light and output it to the diopter measurement optical path.

[0016] Optionally, the refractive power measurement optical path includes a second beam splitter prism, a first beam splitter, a microlens array and a first image sensor;

[0017] The second beam splitter prism is arranged on the output light path of the first beam splitter prism, and the incident surface of the second beam splitter prism is parallel to the incident surface of the first beam splitter prism; the first beam splitter is arranged on the side of the second beam splitter prism close to the human eye, and the first surface of the first beam splitter is at an angle of 90° to the incident surface of the second beam splitter prism; the microlens array and the first image sensor are arranged in sequence on the side of the second beam splitter prism away from the human eye, the microlens array and the first image sensor are arranged on the same optical axis, and the main optical axis of the microlens array is at an angle of 45° to the incident surface of the second beam splitter prism;

[0018] The second beam splitter prism is used to split the light of the first light source output by the first beam splitter prism;

[0019] The first surface of the first beam splitter is used to split the light output by the second beam splitter prism, and use the first transmission component obtained by the splitting as the incident measurement light, and output it to the human eye; the second surface of the first beam splitter is used to receive the first reflected measurement light reflected by the human eye when the incident measurement light irradiates the human eye, split the first reflected measurement light, and obtain the second transmission component through the splitting in sequence through the second beam splitter prism and the microlens array to obtain dot matrix light and output it to the first image sensor;

[0020] The first image sensor is used to collect the dot matrix light to obtain the first image used to measure the refractive power.

[0021] Optionally, the diopter measurement optical path further includes a pair of relay lens modules disposed between the second beam splitter prism and the microlens array, and the pair of relay lens modules are both disposed on the same optical axis as the second beam splitter prism and the microlens array;

[0022] The pair of relay lens modules is used to process the second transmission component output by the second beam splitter prism to adjust the light beam wavefront of the second transmission component.

[0023] Optionally, the corneal curvature measurement optical path includes a second beam splitter, a pupil alignment module, a ring light module, an imaging lens module, a first eyepiece and a second image sensor;

[0024] The circular light module is arranged near the human eye and is used to provide the second light source light to the human eye;

[0025] The pupil alignment module is arranged near the human eye and is used for calibrating the pupil when the ring light module provides the second light source light;

[0026] The second surface of the first beam splitter is also used to receive the second reflected measurement light reflected by the human eye when the second light source irradiates the human eye, split the second reflected measurement light, and output the first reflected component obtained by the splitting to the second beam splitter through the first eyepiece;

[0027] The first eyepiece and the second beam splitter are sequentially arranged on the reflected light path of the second surface of the first beam splitter, and the first eyepiece and the second surface of the first beam splitter form an angle of 45°, and the second beam splitter is arranged in parallel with the first beam splitter; the first surface of the second beam splitter is used to split the first reflected component output by the first beam splitter, and output the second reflected component obtained by the splitting to the second image sensor through the imaging lens module;

[0028] The imaging lens module and the second image sensor are sequentially arranged on the reflected light path of the first surface of the second beam splitter, and the imaging lens module and the second image sensor are arranged on the same optical axis, and the main optical axis of the imaging lens module forms an angle of 45° with the first surface of the second beam splitter; the second image sensor is used to collect the second reflected component to obtain the second image for measuring the corneal curvature.

[0029] Optionally, the corneal curvature measurement optical path further includes a dustproof glass sheet for blocking external dust, and the dustproof glass sheet is arranged on a side of the first beam splitter close to the human eye.

[0030] Optionally, the first eyepiece is a positive lens.

[0031] Optionally, the fixation optical path includes an object-image module, a reflector and a second eyepiece;

[0032] The object image module is used to generate a sight mark light corresponding to the sight mark when the first reflected measurement light is acquired in the diopter measurement optical path, and when the second reflected measurement light is acquired in the corneal curvature measurement optical path, and transmit the sight mark light to the reflector;

[0033] The reflector is arranged on the output optical path of the object-image module, the reflector forms an angle of 45° with the main optical axis of the object-image module, and is arranged parallel to the second beam splitter; the reflector is used to reflect the sight mark light to the second eyepiece;

[0034] The second eyepiece is arranged between the reflector and the second beam splitter and forms an angle of 45° with the reflector; the second eyepiece is used to process the sight mark light to magnify the sight mark, and transmit the processed sight mark light to the human eye through the second beam splitter, the first eyepiece and the first beam splitter in sequence.

[0035] Optionally, the second eyepiece is a positive lens.

[0036] Optionally, the fixation optical path further includes a focusing lens disposed between the object image module and the reflector;

[0037] The focusing lens is arranged on the same optical axis as the object-image module, and is used for processing the sight mark light generated by the object-image module to focus the sight mark, and transmit the processed sight mark light to the reflector.

[0038] The beneficial effects of the utility model are as follows: the measuring light source optical path outputs the first light source light to the diopter measuring optical path, the diopter measuring optical path first obtains the incident measuring light therefrom, and outputs the incident measuring light to the human eye, and by collecting the first image corresponding to the first reflected measuring light reflected by the human eye, the diopter measurement can be realized; the corneal curvature measuring optical path is arranged at the human eye, the optical path provides the second light source light to the human eye, and outputs the second light source light to the human eye, and by collecting the second image corresponding to the second reflected measuring light reflected by the human eye, the corneal curvature measurement can be realized; in the above-mentioned process of measuring diopter and corneal curvature, the visual mark is provided to the human eye through the fixation optical path, which can play a fixation role, and ensure the accuracy of measuring diopter and corneal curvature at the same time;

[0039] The computer ophthalmometer of the utility model can measure the diopter and corneal curvature of the human eye at the same time, and the measurement accuracy is high, and the ophthalmological examination is more comprehensive and more practical. BRIEF DESCRIPTION OF THE DRAWINGS

[0040] The features and advantages of the present invention will be more clearly understood by referring to the accompanying drawings, which are schematic and should not be construed as limiting the present invention in any way. In the accompanying drawings:

[0041] Figure 1 The structure diagram of a computer ophthalmometer in an embodiment of the utility model is shown;

[0042] Figure 2 It shows the optical path structure diagram of the measuring light source optical path and the diopter measuring optical path in the computer optometry in the embodiment of the utility model;

[0043] Figure 3 It shows the optical path structure diagram of the corneal curvature measurement optical path of the computer optometry instrument in the embodiment of the utility model;

[0044] Figure 4 The optical path structure diagram of the fixation optical path in the computer optometry instrument in the embodiment of the utility model is shown.

[0045] Description of reference numerals:

[0046] 1. Measuring light source optical path, 2. Refractive power measuring optical path, 3. Corneal curvature measuring optical path, 4. Fixation optical path, 11. Laser light, 12. Light homogenizer, 13. Collimating lens, 14. First beam splitter prism, 21. Second beam splitter prism, 22. First beam splitter, 23. Microlens array, 24. First image sensor, 25. Relay lens module, 31. Second beam splitter, 32. Pupil alignment module, 33. Ring light module, 34. Imaging lens module, 35. First eyepiece, 36. Second image sensor, 37. Dust-proof glass sheet, 41. Object-image module, 42. Reflector, 43. Second eyepiece, 44. Focusing lens. DETAILED DESCRIPTION

[0047] In order to make the purpose, technical solution and advantages of the embodiment of the utility model clearer, the technical solution in the embodiment of the utility model will be clearly and completely described below in conjunction with the drawings in the embodiment of the utility model. Obviously, the described embodiment is a part of the embodiment of the utility model, not all the embodiments. Based on the embodiment of the utility model, all other embodiments obtained by those skilled in the art without creative work are within the scope of protection of the utility model.

[0048] Example

[0049] A computer ophthalmometer, such as Figure 1 to Figure 4 As shown, it includes a housing and a measuring light source optical path 1, a diopter measuring optical path 2, a corneal curvature measuring optical path 3 and a fixation optical path 4 arranged in the housing;

[0050] The measuring light source optical path 1 is used to provide the first light source light required for measuring the diopter;

[0051] The diopter measurement optical path 2 is arranged on the output optical path of the measurement light source optical path 1, and is used to obtain incident measurement light from the first light source, output the incident measurement light to the human eye 5, and receive the first reflected measurement light reflected by the human eye 5; perform image acquisition on the first reflected measurement light to obtain a first image for measuring the diopter;

[0052] The corneal curvature measurement optical path 3 is arranged near the human eye 5, and is used to provide the human eye 5 with a second light source light required for measuring the corneal curvature; and obtain the second reflected measurement light reflected by the human eye 5; and perform image acquisition on the second reflected measurement light to obtain a second image for measuring the corneal curvature;

[0053] The fixation optical path 4 is used to provide a sight mark to the human eye 5 when the diopter measurement optical path 2 acquires the first reflected measurement light and when the corneal curvature measurement optical path 3 acquires the second reflected measurement light.

[0054] In this embodiment, the measuring light source optical path outputs the first light source light to the diopter measuring optical path, the diopter measuring optical path first obtains the incident measuring light therefrom, and outputs the incident measuring light to the human eye, and by collecting the first image corresponding to the first reflected measuring light reflected back by the human eye, the measurement of diopter can be achieved; the corneal curvature measuring optical path is arranged at the human eye, the optical path provides the second light source light to the human eye, and outputs the second light source light to the human eye, and by collecting the second image corresponding to the second reflected measuring light reflected back by the human eye, the measurement of corneal curvature can be achieved; in the above-mentioned process of measuring diopter and corneal curvature, providing the sight mark to the human eye through the fixation optical path can play a fixation role, thereby ensuring the accuracy of simultaneous measurement of diopter and corneal curvature.

[0055] The computer ophthalmometer of this embodiment can measure the diopter and corneal curvature of the human eye at the same time, and the measurement accuracy is high, and the ophthalmic examination is more comprehensive and more practical.

[0056] It should be noted that the utility model only improves the optical path structure of the computer ophthalmometer and does not involve improvements to the computer program. The analysis of the refractive power based on the first image and the analysis of the corneal curvature based on the second image both adopt the existing image analysis technology. The computer programs related to the image analysis technology are pre-stored in the analysis system of the computer ophthalmometer. The specific details of the image analysis technology are not the invention points of the utility model and will not be repeated here.

[0057] Preferably, if Figure 1 to Figure 4 As shown, the measuring light source optical path 1 includes a laser lamp 11, a light homogenizer 12, a collimating lens 13 and a first beam splitter prism 14 which are arranged in sequence;

[0058] The laser lamp 11, the light homogenizer 12 and the collimating lens 13 are arranged on the same optical axis, and the incident surface of the first beam splitter prism 14 is arranged at an angle of 45° to the main optical axis of the collimating lens 13;

[0059] The laser lamp 11 is used to provide a laser light source;

[0060] The light homogenizing sheet 12 is used to homogenize the laser light source;

[0061] The collimating lens 13 is used to focus the homogenized laser light source;

[0062] The first surface of the first beam splitter prism 14 is used to split the focused laser light source to obtain the first light source light and output it to the diopter measurement optical path 2 .

[0063] Using laser light as a light source for measuring refractive power has the advantages of high brightness, high stability and easy adjustment, which can greatly improve the accuracy and efficiency of measuring refractive power and enhance user experience; using a light homogenizer to homogenize the laser light source can make the uneven laser light source uniform, improve the optical path, and improve the accuracy and stability of measurement; focusing the homogenized laser light source through a collimating lens can accurately direct the homogenized laser light source to ensure that the light can enter the subsequent optical path at a specific angle and direction, and can also play a focusing role to improve the accuracy and stability of subsequent splitting; connecting the first beam splitter prism to the collimating lens can split the incident non-polarized light into two beams of vertical linear polarized light, so as to more accurately measure the refractive power later.

[0064] Preferably, if Figure 1 to Figure 4 As shown, the refractive power measurement optical path 2 includes a second beam splitter prism 21, a first beam splitter 22, a microlens array 23 and a first image sensor 24;

[0065] The second beam splitter prism 21 is arranged on the output light path of the first beam splitter prism 14, and the incident surface of the second beam splitter prism 21 is parallel to the incident surface of the first beam splitter prism 14; the first beam splitter plate 22 is arranged on the side of the second beam splitter prism 21 close to the human eye 5, and the first surface of the first beam splitter plate 22 and the incident surface of the second beam splitter prism 21 form an angle of 90°; the microlens array 23 and the first image sensor 24 are arranged in sequence on the side of the second beam splitter prism 21 away from the human eye 5, the microlens array 23 and the first image sensor 24 are arranged on the same optical axis, and the main optical axis of the microlens array 23 and the incident surface of the second beam splitter prism 21 form an angle of 45°;

[0066] The second beam splitter prism 21 is used to split the first light source light output by the first beam splitter prism 14;

[0067] The first surface of the first beam splitter 22 is used to split the light output by the second beam splitter prism 21, and use the first transmission component obtained by the splitting as the incident measurement light, and output it to the human eye 5; the second surface of the first beam splitter 22 is used to receive the first reflected measurement light reflected by the human eye 5 when the incident measurement light irradiates the human eye 5, split the first reflected measurement light, and obtain the second transmission component through the splitting in turn through the second beam splitter prism 21 and the microlens array 23 to obtain dot matrix light and output it to the first image sensor 24;

[0068] The first image sensor 24 is used to collect the dot matrix light to obtain the first image used to measure the refractive power.

[0069] Connecting a second beam splitter prism to the output optical path of the first beam splitter prism can, on the one hand, split the incident non-polarized light into two beams of perpendicular linear polarized light, so as to more accurately measure the diopter later; on the other hand, it can also transmit the main optical path for measuring the diopter in the desired direction, thereby realizing a more compact optical path layout; connecting a first beam splitter to the output optical path of the second beam splitter prism can absorb the linear polarized light of a specific band, and transmit the linear polarized light of the specified band (such as 840nm wavelength) to the human eye, thereby reducing unnecessary glare and reflection in the diopter measurement, improving the user experience, and standardizing the measurement conditions, thereby improving the repeatability and comparability of the measurement; the microlens array can splice the fields of view of multiple microlenses together to create a larger field of view, wherein each microlens can focus light into a small area, so that the first image sensor of the subsequent stage can detect finer signals, thereby improving the measurement resolution and sensitivity.

[0070] The microlens array of this embodiment is composed of a plurality of microlenses, and the light outputted is point-pin light.

[0071] Preferably, if Figure 1 As shown, the diopter measurement optical path 2 further includes a pair of relay lens modules 25 disposed between the second beam splitter prism 21 and the microlens array 23, and the pair of relay lens modules 25 are both disposed on the same optical axis as the second beam splitter prism 21 and the microlens array 23;

[0072] The pair of relay lens modules 25 is used to process the second transmission component output by the second beam splitter prism 21 to adjust the beam wavefront of the second transmission component.

[0073] Adding a pair of relay lens modules in front of the microlens array can adjust the light beam wavefront of the second transmitted component. Specifically, by reducing the light beam wavefront, the refractive power detection range can be increased, making it easier for the subsequent first image sensor to capture the first image, thereby improving the accuracy and reliability of the refractive power measurement.

[0074] In each relay lens module of the present embodiment, the relay lens module is formed by gluing a group of lenses together.

[0075] The optical path structures of the light source measurement optical path and the diopter measurement optical path in this embodiment are as follows: Figure 2 shown.

[0076] Preferably, if Figure 1 to Figure 4 As shown, the corneal curvature measurement optical path 3 includes a second beam splitter 31, a pupil alignment module 32, a ring light module 33, an imaging lens module 34, a first eyepiece 35 and a second image sensor 36;

[0077] The annular light module 33 is disposed near the human eye 5 and is used to provide the second light source light to the human eye 5;

[0078] The pupil alignment module 32 is disposed near the human eye 5 and is used to calibrate the pupil when the ring light module 33 provides the second light source light;

[0079] The second surface of the first beam splitter 22 is also used to receive the second reflected measurement light reflected by the human eye 5 when the second light source irradiates the human eye 5, split the second reflected measurement light, and output the first reflected component obtained by the splitting to the second beam splitter 31 through the first eyepiece 35;

[0080] The first eyepiece 35 and the second beam splitter 31 are sequentially arranged on the reflected light path of the second surface of the first beam splitter 22, and the first eyepiece 35 and the second surface of the first beam splitter 22 form an angle of 45°, and the second beam splitter 31 is arranged parallel to the first beam splitter 22; the first surface of the second beam splitter 31 is used to split the first reflected component output by the first beam splitter 22, and output the second reflected component obtained by the splitting to the second image sensor 36 through the imaging lens module 34;

[0081] The imaging lens module 34 and the second image sensor 36 are sequentially arranged on the reflected light path of the first surface of the second beam splitter 31, and the imaging lens module 34 and the second image sensor 36 are arranged on the same optical axis, and the main optical axis of the imaging lens module 34 forms an angle of 45° with the first surface of the second beam splitter 31; the second image sensor 36 is used to collect the second reflected component to obtain the second image for measuring the corneal curvature.

[0082] The circular light module arranged at the human eye can provide light source to the human eye to achieve the effect of fill light and provide necessary light source conditions for corneal curvature measurement; the pupil alignment module is also arranged at the human eye to achieve the purpose of pupil calibration, and can quickly locate the user's pupil position at the human eye, maintain the alignment state between the optical system and the pupil, which helps to reduce the measurement error caused by pupil movement, and finally transmit it to the imaging lens module through the first beam splitter, the first eyepiece and the second beam splitter in turn, which can improve the accuracy of corneal curvature measurement; before the second image sensor collects the second image, the light can be optically processed and corrected through the imaging lens module to improve the image quality, so as to better adapt to the collection of the second image sensor and provide a better image basis for the measurement of corneal curvature.

[0083] In this embodiment, both the first image sensor and the second image sensor are CMOS sensors.

[0084] Preferably, if Figure 1 to Figure 4 As shown, the corneal curvature measurement optical path 3 further includes a dustproof glass sheet 37 for blocking external dust, and the dustproof glass sheet 37 is arranged on a side of the first beam splitter 22 close to the human eye 5.

[0085] The dust-proof glass can effectively prevent external dust from entering the internal optical path structure of the entire computer ophthalmometer, avoiding the impact on the optical path and ensuring the reliability of the measurement.

[0086] In this embodiment, the first eyepiece 35 is a positive lens.

[0087] The positive lens can play a focusing role while ensuring that the light is transmitted to the subsequent optical path.

[0088] The optical path structure of the corneal curvature measurement optical path in this embodiment is as follows: Figure 3 shown.

[0089] Preferably, if Figure 1 to Figure 4 As shown, the fixation optical path 4 includes an object-image module 41, a reflector 42 and a second eyepiece 43;

[0090] The object image module 41 is used to generate a sight mark light corresponding to the sight mark when the first reflected measurement light is acquired in the diopter measurement optical path 2 and when the second reflected measurement light is acquired in the corneal curvature measurement optical path 3, and transmit the sight mark light to the reflector 42;

[0091] The reflector 42 is arranged on the output optical path of the object-image module 41, the reflector 42 forms an angle of 45° with the main optical axis of the object-image module 41, and is arranged parallel to the second beam splitter 31; the reflector 42 is used to reflect the sight mark light to the second eyepiece 43;

[0092] The second eyepiece 43 is arranged between the reflector 42 and the second beam splitter 31, and forms an angle of 45° with the reflector 42; the second eyepiece 43 is used to process the sight mark light to magnify the sight mark, and transmit the processed sight mark light to the human eye 5 through the second beam splitter 31, the first eyepiece 35 and the first beam splitter 22 in sequence.

[0093] The object-image module generates sight mark light that can form a sight mark image, and transmits the sight mark light to the subsequent stage, so that the user at the human eye can observe the sight mark, which plays a role in fixation, avoids the influence of the movement of the user's pupil on the measurement, and improves the accuracy and reliability of the measurement; a reflector is connected after the object-image module, and the direction of the optical path can be changed without affecting the sight mark light, so that the sight mark light can be transmitted along the required path, thereby making the layout of the entire ophthalmometer more compact, facilitating the miniaturization design of the ophthalmometer and reducing the manufacturing cost; the sight mark can be magnified through the second eyepiece, making it easier for the user at the human eye to see a clearer and more natural sight mark, which plays a better role in fixation; finally, it is transmitted to the human eye through the second beam splitter, the first eyepiece and the first beam splitter in turn, which can effectively ensure the fixation effect without increasing the optical path structure, thereby ensuring the accuracy of the refractive power measurement and the corneal curvature measurement.

[0094] Specifically, the second eyepiece 43 of this embodiment is a positive lens.

[0095] Similarly, a positive lens can play a focusing role while ensuring that the light is transmitted to the subsequent optical path.

[0096] Preferably, if Figure 1 to Figure 4 As shown, the fixation optical path 4 further includes a focusing lens 44 disposed between the object image module 41 and the reflector 42;

[0097] The focusing lens 44 is disposed on the same optical axis as the object-image module 41 , and is used to process the sight mark light generated by the object-image module 41 to focus the sight mark, and transmit the processed sight mark light to the reflector 42 .

[0098] By processing the light of the sight mark through the focusing lens, the sight mark can be focused on the basis of fixation, so as to achieve fine adjustment and calibration of the sight mark, ensure that different users can see clean and accurate sight marks, adapt to the visual needs and adjustment status of different users, and improve the accuracy and repeatability of refractive power measurement and corneal curvature measurement.

[0099] The optical path structure of the fixation optical path in this embodiment is as follows: Figure 4 shown.

[0100] The optical elements such as the lenses, modules, lamps and image sensors of this embodiment can all be products of suitable specifications or models on the market according to actual conditions, and the specific details are not listed here.

[0101] Although the embodiments of the present invention are described in conjunction with the accompanying drawings, those skilled in the art may make various modifications and variations without departing from the spirit and scope of the present invention, and such modifications and variations are all within the scope defined by the appended claims.

Claims

1. A computer ophthalmometer, characterized in that: It comprises a housing and a measuring light source optical path, a diopter measuring optical path, a corneal curvature measuring optical path and a fixation optical path arranged in the housing; The measuring light source optical path is used to provide the first light source light required for measuring the diopter; The diopter measurement optical path is arranged on the output optical path of the measurement light source optical path, and is used to obtain incident measurement light from the first light source, output the incident measurement light to the human eye, and receive the first reflected measurement light reflected by the human eye; perform image acquisition on the first reflected measurement light to obtain a first image for measuring the diopter; The corneal curvature measurement optical path is arranged near the human eye, and is used to provide the human eye with a second light source light required for measuring the corneal curvature; and obtain the second reflected measurement light reflected by the human eye; and perform image acquisition on the second reflected measurement light to obtain a second image for measuring the corneal curvature; The fixation optical path is used to provide a sight mark to the human eye when the refractive power measurement optical path acquires the first reflected measurement light and when the corneal curvature measurement optical path acquires the second reflected measurement light.

2. The computer ophthalmometer according to claim 1, characterized in that: The measuring light source optical path comprises a laser lamp, a light homogenizer, a collimating lens and a first beam splitter prism arranged in sequence; The laser lamp, the light homogenizer and the collimating lens are arranged on the same optical axis, and the incident surface of the first beam splitter prism is arranged at an angle of 45° to the main optical axis of the collimating lens; The laser lamp is used to provide a laser light source; The light homogenizing sheet is used to homogenize the laser light source; The collimating lens is used to focus the homogenized laser light source; The first surface of the first beam splitter prism is used to split the focused laser light source to obtain the first light source light and output it to the diopter measurement optical path.

3. The computer ophthalmometer according to claim 2, characterized in that: The refractive power measurement optical path includes a second beam splitter prism, a first beam splitter, a microlens array and a first image sensor; The second beam splitter prism is arranged on the output light path of the first beam splitter prism, and the incident surface of the second beam splitter prism is parallel to the incident surface of the first beam splitter prism; the first beam splitter is arranged on the side of the second beam splitter prism close to the human eye, and the first surface of the first beam splitter is at an angle of 90° to the incident surface of the second beam splitter prism; the microlens array and the first image sensor are arranged in sequence on the side of the second beam splitter prism away from the human eye, the microlens array and the first image sensor are arranged on the same optical axis, and the main optical axis of the microlens array is at an angle of 45° to the incident surface of the second beam splitter prism; The second beam splitter prism is used to split the light of the first light source output by the first beam splitter prism; The first surface of the first beam splitter is used to split the light output by the second beam splitter prism, and use the first transmission component obtained by the splitting as the incident measurement light, and output it to the human eye; the second surface of the first beam splitter is used to receive the first reflected measurement light reflected by the human eye when the incident measurement light irradiates the human eye, split the first reflected measurement light, and obtain the second transmission component through the splitting in sequence through the second beam splitter prism and the microlens array to obtain dot matrix light and output it to the first image sensor; The first image sensor is used to collect the dot matrix light to obtain the first image used to measure the refractive power.

4. The computer ophthalmometer according to claim 3, characterized in that: The refractive power measurement optical path further includes a pair of relay lens modules disposed between the second beam splitter prism and the microlens array, wherein the pair of relay lens modules are both disposed on the same optical axis as the second beam splitter prism and the microlens array; The pair of relay lens modules is used to process the second transmission component output by the second beam splitter prism to adjust the light beam wavefront of the second transmission component.

5. The computer ophthalmometer according to claim 3, characterized in that: The keratometer optical path includes a second beam splitter, a pupil alignment module, a ring light module, an imaging lens module, a first eyepiece, and a second image sensor; The circular light module is arranged near the human eye and is used to provide the second light source light to the human eye; The pupil alignment module is arranged near the human eye and is used for calibrating the pupil when the ring light module provides the second light source light; The second surface of the first beam splitter is also used to receive the second reflected measurement light reflected by the human eye when the second light source irradiates the human eye, split the second reflected measurement light, and output the first reflected component obtained by the splitting to the second beam splitter through the first eyepiece; The first eyepiece and the second beam splitter are sequentially arranged on the reflected light path of the second surface of the first beam splitter, and the first eyepiece and the second surface of the first beam splitter form an angle of 45°, and the second beam splitter is arranged in parallel with the first beam splitter; the first surface of the second beam splitter is used to split the first reflected component output by the first beam splitter, and output the second reflected component obtained by the splitting to the second image sensor through the imaging lens module; The imaging lens module and the second image sensor are sequentially arranged on the reflected light path of the first surface of the second beam splitter, and the imaging lens module and the second image sensor are arranged on the same optical axis, and the main optical axis of the imaging lens module forms an angle of 45° with the first surface of the second beam splitter; the second image sensor is used to collect the second reflected component to obtain the second image for measuring the corneal curvature.

6. The computer ophthalmometer according to claim 5, characterized in that: The corneal curvature measurement optical path also includes a dustproof glass sheet for blocking external dust, and the dustproof glass sheet is arranged on a side of the first beam splitter close to the human eye.

7. The computer ophthalmometer according to claim 5, characterized in that: The first eyepiece is a positive lens.

8. The computer ophthalmometer according to claim 5, characterized in that: The fixation optical path includes an object-image module, a reflector and a second eyepiece; The object image module is used to generate a sight mark light corresponding to the sight mark when the first reflected measurement light is acquired in the diopter measurement optical path, and when the second reflected measurement light is acquired in the corneal curvature measurement optical path, and transmit the sight mark light to the reflector; The reflector is arranged on the output optical path of the object-image module, the reflector forms an angle of 45° with the main optical axis of the object-image module, and is arranged parallel to the second beam splitter; the reflector is used to reflect the sight mark light to the second eyepiece; The second eyepiece is arranged between the reflector and the second beam splitter and forms an angle of 45° with the reflector; the second eyepiece is used to process the sight mark light to magnify the sight mark, and transmit the processed sight mark light to the human eye through the second beam splitter, the first eyepiece and the first beam splitter in sequence.

9. The computer ophthalmometer according to claim 8, characterized in that: The second eyepiece is a positive lens.

10. The computer ophthalmometer according to claim 8, characterized in that: The fixation optical path further comprises a focusing lens disposed between the object image module and the reflector; The focusing lens is arranged on the same optical axis as the object-image module, and is used for processing the sight mark light generated by the object-image module to focus the sight mark, and transmit the processed sight mark light to the reflector.

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