Apparatus and method for high-precision full-eyeball diopter map detection

Abstract

The present invention relates to an apparatus and method for high-precision full-eyeball diopter map detection. The apparatus comprises: a light-emitting assembly for illuminating a fundus, a beam shaping module for converging a light beam, a reflection assembly for reflecting a light beam, an eyepiece for transmission imaging, an eye fixation position for providing an eye detection position, an imaging module for imaging, and a data processing assembly for processing image data. The eye fixation position, the eyepiece, the reflection assembly, and the imaging module are sequentially arranged on the same horizontal line. The data processing assembly is connected to the imaging module by means of a connecting wire and is configured for receiving imaging data from the imaging module and processing the imaging data. The light-emitting assembly, the beam shaping module, and the reflection assembly are located on the same vertical line. According to the present invention, the full-eyeball diopter can be calculated precisely to give a full-eyeball diopter map, achieving targeted fitting of defocus spectacle lenses and contact lenses, and improving the effect of myopia prevention and control.

Description

A high-precision whole-eye diopter detection device and method Technical Field

[0001] This invention relates to the field of vision measurement technology, and more specifically, to a high-precision whole-eye vision measurement device and method. Background Technology

[0002] Research indicates that abnormal axial elongation is a major factor in the occurrence and development of myopia. Currently, defocus eyeglasses and contact lenses used clinically primarily utilize the principle of eliminating or reversing peripheral hyperopic defocus, resulting in a myopic defocus state for peripheral retinal images, to effectively inhibit axial elongation and myopia progression, thereby achieving myopia control. However, these lenses determine fitting parameters based solely on macular disorientation. While the same peripheral retinal defocus parameters are used for individuals with the same macular disorientation, the complex structure of the human eye and individual developmental differences mean that the morphology of the peripheral retina and the axial length of the eyeball vary even among individuals with the same disorientation. Therefore, current peripheral retinal defocus effects are difficult to personalize, impacting myopia control effectiveness. To achieve ideal peripheral retinal defocus, it is essential to understand the overall visual acuity of the entire eye. Accurate fitting and defocusing can only be performed based on a complete visual acuity chart. Furthermore, as one of the primary organs for acquiring external information, the human eye, in addition to the macula, also has a peripheral retina that functions for vision. Therefore, obtaining the visual acuity maps of different people and making targeted eyeglass fittings can make full use of the function of the human retina, provide better visual quality, and improve the effectiveness of myopia prevention and control.

[0003] Given the above issues, obtaining a full-field (full-range) diopter map and fitting targeted defocus eyeglasses and contact lenses can improve myopia control. Currently, the commonly used refraction devices in clinical practice are automated refractometers, which utilize the eye's focusing principle to examine macular diopter. However, due to the visual characteristics of the human eye and the rectilinear propagation of light, the light emitted by an automated refractometer enters the eye through the pupil, only detecting macular diopter; peripheral retinal diopter data cannot be detected. Currently, there are two main publicly available methods for retinal refractive topography (CN112263216A, CN114587268A). The first (CN112263216A, MRT) refractive topography instrument primarily detects different defocus positions when light of different wavelengths converges on the retina and uses defocus compensation to simulate and calculate the retinal refractive topography. However, it requires a multispectral light source, increasing costs. The second (CN114587268A) refractive topography instrument projects patterns such as black and white checkerboards onto the retina. By stepping forward and backward, the clarity of the projected pattern is observed to calculate the retinal diopter. Although this detection method is simple, its accuracy is limited by the size and number of tables, as well as the amount of movement during stepping forward and backward.

[0004] Therefore, in order to address the shortcomings of existing technologies in vision detection, this invention provides a high-precision whole-eye vision map detection device and method to detect the whole-eye vision of different human eye features, including the macula and peripheral retina, and obtain the whole-eye vision status.

[0005] Summary of the Invention

[0006] The present invention aims to overcome at least one of the defects (deficiencies) of the prior art and provide a high-precision whole-eye diopter map detection device and method for detecting the whole-eye diopter, including the macula and peripheral retina, of different human eye characteristics, accurately calculating the whole-eye diopter, and obtaining a whole-eye diopter map, thereby enabling targeted adaptation of defocused eyeglasses and contact lenses, and improving the effect of myopia prevention and control.

[0007] The technical solution adopted by the present invention is a high-precision whole-eye diopter map detection device, the device comprising: a light-emitting component for illuminating the fundus, a beam-shaping module for converging the light beam, a reflective component for reflecting the light beam, an eyepiece for transmission imaging, an eye fixation position for providing the eye detection position, an imaging module for imaging, and a data processing component for processing the image data.

[0008] The eye gaze position, eyepiece, reflector, and imaging module are arranged sequentially on the same horizontal line; the data processing component is connected to the imaging module via a connecting line to receive and process the imaging data from the imaging module; and the light-emitting component, beam shaping module, and reflector are on the same vertical line.

[0009] When using the device of the present invention, the user's eye and / or artificial eye are kept in the eye fixation position and on the same water surface as the eyepiece. The light source emitted by the light-emitting component is processed by the beam shaping module, and then reflected by the reflection component into the eyepiece. The eyepiece transmits the image in front of the pupil of the eye, and then, after being transmitted through the cornea and lens of the user's eye and / or artificial eye, it is uniformly illuminated on the retina of the fundus. After being reflected by the retina, it is emitted from the pupil, focused by the eyepiece, and then passes through the reflection component into the imaging module for imaging. Finally, the data processing component processes the image data to obtain a full-eye diopter map.

[0010] Compared to traditional optometry equipment, this invention's device is applicable to different human eye characteristics. It can detect not only the visual acuity of the macula but also the visual acuity of the entire eye, including the peripheral retina, obtaining a complete visual acuity map and precise optometry data. This allows for a more accurate determination of the eye's refractive error and visual correction needs, making eyeglass prescriptions more personalized and precise. Furthermore, by detecting the visual acuity of the entire eye, it can comprehensively and regularly monitor and quantify the progression of myopia. By comparing changes in eye structure and retinal layers at different time points, it can detect the worsening trend of myopia early, enabling effective prevention and control measures to be taken. This allows ophthalmologists to intervene and manage myopia earlier, reducing its adverse effects on visual health.

[0011] Preferably, the imaging module includes an internal lens for imaging, an image receiver for receiving the image, and an objective lens moving assembly for front and rear focusing; the objective lens moving assembly and the image receiver are respectively connected to the data processing assembly via connecting lines; the objective lens moving assembly moves the position of the internal lens to achieve precise focusing on all areas of the fundus, and receives the clearest image obtained through the image receiver.

[0012] By moving the objective lens relative position using the objective lens moving component, scanning the objective lens diopter, and adjusting the optical path length, the focal length of the imaging system is changed, enabling precise focusing on different areas of the fundus, ensuring image clarity and accuracy, and recording fundus images acquired at each location, thus ensuring high-quality, high-resolution eye imaging and data acquisition.

[0013] Preferably, the objective lens moving assembly is a manual or electric adjustment assembly, and has an automated measurement component capable of recording the focusing position data of the fundus image acquired at each position.

[0014] In this device, the objective lens movement assembly can be set to manual or electric to adjust the objective lens, enabling precise focusing and obtaining clear fundus images. It is also equipped with an automated measurement component that can be connected to the data processing component to measure the distance the objective lens moves and the changes in imaging. It can monitor changes in the focal position in real time and provide accurate image distance measurement results.

[0015] Preferably, the middle part of the reflective component is set as an open area, which is used for the light source reflected back through the fundus, and the unopened area is used to reflect the light source focused by the beam shaping module in the direction of the eyepiece.

[0016] By setting a reflective component with an opening in the middle, it is possible to guide and control the light path, directing light from the light source to the eye structure to be examined. Through precise control of the reflection angle and position, it is ensured that the light enters and leaves the eyeball along a predetermined optical path, thereby obtaining stable and accurate imaging. It also allows the light source reflected back from the fundus to pass through the reflective component and reach the imaging module for imaging.

[0017] On the other hand, the present invention also provides a high-precision whole-eye vision detection method based on the high-precision whole-eye vision detection device described above, the method comprising:

[0018] S1: Acquire fundus images taken by the device at different focusing positions;

[0019] S2: Record the focusing position data corresponding to the fundus image;

[0020] S3: Divide the fundus image into regions and obtain the clarity of each image region of the fundus image;

[0021] S4: For each image region, select the fundus image with the highest clarity in each image region as the target fundus image;

[0022] S5: Obtain the focusing position data corresponding to the target fundus image as the target focusing position data;

[0023] S6: For each image region, based on the target fundus image and the target focusing position data, calculate the visual acuity of each image region, thereby obtaining the visual acuity of each region in the entire fundus image.

[0024] In this invention, the method acquires target fundus images and target focusing position data for each region in a fundus image. By calculating the correspondence between the two, the diopter of the fundus image region is accurately calculated, thereby obtaining a diopter map of the entire eyeball. This allows for a more accurate determination of the eye's refractive power and visual correction needs, making eyeglass prescriptions more personalized and precise. The detailed data for each region of the entire eyeball obtained through calculation also allows ophthalmologists or ophthalmologists to regularly monitor and quantify the progression of myopia. By comparing changes in eyeball structure and retinal layers at different time points, the worsening trend of myopia can be detected early, enabling the implementation of effective prevention and control measures, the development of personalized myopia prevention and control strategies, and the improvement of myopia prevention and control effectiveness.

[0025] Preferably, in steps S1 to S2, the fundus images at different focusing positions are captured by adjusting the objective lens moving component in the imaging module of the device, and the corresponding focusing position data are recorded according to the automated measurement component, thereby achieving precise focusing to obtain clear fundus images, and being able to monitor changes in the focus position in real time to provide accurate image distance measurement results.

[0026] Preferably, step S3 specifically includes: dividing the fundus image into regions according to a set size area, establishing a sharpness evaluation formula by calculating the maximum gray level difference between adjacent pixels in the fundus image and introducing a threshold to distinguish edge points and non-edge points, thereby calculating the sharpness of each image region in each fundus image.

[0027] By dividing the fundus image into regions and calculating the sharpness of each region, the local quality of the fundus image can be evaluated more precisely. Different regions may have different levels of sharpness. Regional evaluation helps to determine the availability and information richness of specific parts in the fundus image. Furthermore, the sharpness of the image is quantified by calculating the maximum gray-level difference. At the same time, a threshold is introduced to distinguish between edge points and non-edge points for edge detection and segmentation, thereby improving the overall quality of the fundus image. A sharpness evaluation formula is established to realize the automated evaluation of fundus image sharpness.

[0028] Preferably, the sharpness evaluation formula is:

[0029] Where: V(I) represents the normalized sharpness evaluation function value. The larger the value of V(I), the higher the sharpness of each image region; M and N represent the length and width of each image region of the fundus image, respectively; x and y represent the horizontal and vertical coordinates of the pixels in each image region, respectively; G″(x,y) represents the gradient image of each image region after removing false edges.

[0030] By setting specific formulas, the clarity level of different regions of the fundus image can be numerically evaluated, providing objective evaluation indicators. This provides objective and accurate data for subsequent calculation of the whole-eye diopter map, which helps to obtain a more accurate whole-eye diopter map.

[0031] Preferably, step S4 specifically involves: selecting the fundus image corresponding to the largest V(I) value in each image region from the V(I) values ​​calculated in step S3 as the target fundus image, thereby obtaining the target fundus image corresponding to each region in the fundus image.

[0032] By using the fundus image corresponding to the largest V(I) value in the image region as the target fundus image, the focus position data corresponding to the target fundus image can be quickly determined in step S5, thereby obtaining the target focus position data.

[0033] Preferably, in step S6, the formula for calculating the viewpoint of the image region is:

[0034] in, D represents the diopter of the target fundus image region; f3 represents the target focusing position data; l1, l2, and l3 are known fixed parameters, where l1 is the distance from the user's eye and / or artificial eye to the eyepiece, l2 is the distance from the eyepiece to the imaging module, and l3 is the distance from the lens inside the imaging module to the film of the image receiver; f1 is the focal length of the eyepiece; and f2 is the equivalent focal length of the lens and cornea of ​​the user's eye and / or artificial eye.

[0035] According to the aforementioned diopter formula, the diopter of the fundus image region can be accurately calculated simply by obtaining the corresponding target focusing position data, thereby constructing a whole-eye diopter map. This provides a fast and effective method for detecting the diopter status of the whole eye, including the macula and peripheral retina.

[0036] Compared with existing technologies, the beneficial effects of this invention are as follows: By providing a high-precision whole-eye diopter map detection device and method, this invention solves the problems of existing technologies that use multispectral light source defocus compensation to calculate diopter, where the accuracy of the calculated result is limited by the type and number of light sources and the wavelength of specific colors of light, resulting in poor accuracy and high cost. Furthermore, existing technologies that calculate retinal diopter by observing the clarity of the black and white checkerboard pattern projected onto the retina through stepping and back-stepping are also limited by the clarity of the table itself during projection, the size and number of the table, and the amount of stepping and back-stepping movement, leading to numerous influencing factors and low accuracy. Directly analyzing the clarity of fundus images obtained by arbitrarily changing the focal length yields higher diopter accuracy, is less affected by objective factors, and significantly reduces costs. This invention also addresses the problem that traditional vision measurement primarily targets the macula, failing to detect vision data in the peripheral retina, resulting in poor myopia control. By directly capturing fundus images and dividing them into regions, the invention calculates the overall vision of the entire eye, including the macula and peripheral retina, based on the obtained target fundus images and target focus position data. Furthermore, the divided image regions are not limited by size or shape and can be modified as needed, enabling precise and personalized calculation of the entire eye's vision. This allows for personalized and targeted adaptation of defocus eyeglasses and contact lenses, improving myopia control and visual quality. Attached Figure Description

[0037] Figure 1 is a schematic diagram of the high-precision whole-eye diopter detection device of the present invention.

[0038] Figure 2 is a schematic diagram of the overall process of the high-precision whole-eye vision map detection device of the present invention.

[0039] Figure 3 is a schematic diagram of the optical path process by which the high-precision whole-eye diopter detection device of the present invention illuminates the retina at the fundus.

[0040] Figure 4 is a schematic diagram of the image imaging process performed by the high-precision whole-eye vision map detection device of the present invention.

[0041] Figure 5 is a flowchart illustrating the high-precision whole-eye diopter map detection method of the present invention.

[0042] Figure 6 is a schematic diagram illustrating the calculation of the visual acuity of a certain fundus image region using the high-precision whole-eye visual acuity map detection method of the present invention.

[0043] Figure description: 1. Light-emitting component; 2. Beam shaping module; 3. Eye gaze position; 4. Eyepiece; 5. Reflection component; 6. Imaging module; 7. Image receiver; 8. Objective lens movement component; 9. Data processing component. Detailed Implementation

[0044] The accompanying drawings are for illustrative purposes only and should not be construed as limiting the invention. To better illustrate the following embodiments, some components in the drawings may be omitted, enlarged, or reduced, and do not represent the actual product dimensions; it is understandable to those skilled in the art that some well-known structures and their descriptions may be omitted in the drawings.

[0045] Example 1

[0046] As shown in Figure 1, this embodiment provides a high-precision full-eye diopter map detection device. The device includes: a light-emitting component 1 for illuminating the fundus, a beam shaping module 2 for converging the light beam, a reflective component 5 for reflecting the light beam, an eyepiece 4 for transmission imaging, an eye fixation position 3 for providing the eye detection position, an imaging module 6 for imaging, and a data processing component 9 for processing image data.

[0047] The eye gaze position 3, eyepiece 4, reflector 5, and imaging module 6 are arranged sequentially on the same horizontal line; the data processing component 9 is connected to the imaging module via a connecting line and is used to receive and process the imaging data of the imaging module 6; the light emission component 1, beam shaping module 2, and reflector 5 are on the same vertical line.

[0048] Preferably, in this embodiment, the light-emitting component 1 can be an LED, a light bulb, a laser, or other light-emitting devices to illuminate the fundus of the target user; the beam shaping module 2 includes lenses, mirrors, and diffraction light source elements, which converge the light beam emitted by the light-emitting component 1 so that it can be focused onto the reflective component 5; the eyepiece 4 can be a transmissive or reflective optical system, and the specifications of the eyepiece 4 meet the requirements of power-sensory fundus imaging; the image receiver 7 can be an optical conversion device such as a CCD or CMOS, which can receive the fundus retinal imaging image obtained after each focusing of the imaging module 6; the data processing component 9 can be a communication, control, and data processing unit composed of a high-performance microcomputer, used for various data processing, including the displacement of the imaging component, the switching of the light source, and the data reception and processing of the image receiver 7.

[0049] Preferably, the imaging module 6 can be a high-resolution fundus camera optical system that meets the technical requirements of full fundus optical imaging. The imaging module 6 includes an internal lens for imaging, an image receiver 7 for receiving the image, and an objective lens moving assembly 8 for front and rear focusing. The objective lens moving assembly 8 and the image receiver 7 are respectively connected to the data processing assembly 9 via connecting lines. The objective lens moving assembly 8 moves the position of the internal lens to achieve precise focusing on all areas of the fundus, and receives the clearest image obtained through the image receiver 7.

[0050] The objective lens is moved relative to the objective lens by the objective lens moving component 8, the objective lens diopter is scanned, the optical path length is adjusted, and the focal length of the imaging system is changed to achieve precise focusing on different areas of the fundus, ensuring the clarity and accuracy of the image, and recording the fundus image acquired at each position, thus ensuring high-quality, high-resolution eye imaging and data acquisition.

[0051] More preferably, the objective lens moving assembly 8 is a manual or electric adjustment assembly, and has an automated measurement component capable of recording the focusing position data of the fundus image acquired at each position.

[0052] In this device, the objective lens moving assembly 8 can be set to manual or electric to adjust the objective lens, which can achieve precise focusing and obtain a clear fundus image. It is also equipped with an automated measurement component that can be connected to the data processing assembly 9 to measure the distance of objective lens movement and image changes. It can monitor the changes in the focal position in real time and provide accurate image distance measurement results.

[0053] Preferably, the middle part of the reflective component 5 is set as an open area, which is used for the light source reflected back through the fundus, and the unopened area is used to reflect the light source focused by the beam shaping module 2 to the direction of the eyepiece.

[0054] By setting a reflective component with an opening in the middle, it is possible to guide and control the light path, directing light from the light source to the eye structure to be examined. Through precise control of the reflection angle and position, it is ensured that the light enters and leaves the eyeball along a predetermined optical path, thereby obtaining stable and accurate imaging. It also allows the light source reflected back from the fundus to pass through the reflective component and reach the imaging module for imaging.

[0055] As shown in Figure 2, which is a schematic diagram of the overall process of the high-precision whole-eye diopter map detection device according to an embodiment of the present invention, and as can be seen from Figure 1, when using the device, the user's eye and / or artificial eye are kept at eye fixation position 3 and at the same water level as the eyepiece 4. The light source emitted by the light-emitting component 1 is processed by the beam shaping module 2, and then reflected by the reflection component 1 into the eyepiece 4. The eyepiece 4 transmits the image to the pupil of the eye, and then, after being transmitted through the cornea and lens of the user's eye and / or artificial eye, it is uniformly illuminated on the retina of the fundus. After being reflected by the retina, it is emitted from the pupil, focused by the eyepiece 4, and then passes through the reflection component 5 to the imaging module 6 for imaging by the calibrated fundus imaging optical system. The corresponding focusing position data is obtained by the objective lens moving component 8, and finally the image data is processed by the data processing component 9 to obtain the whole-eye diopter map.

[0056] As shown in Figure 3, which is a schematic diagram of the optical path process by which the high-precision whole-eye diopter map detection device illuminates the retina of the fundus in this embodiment, the transmission process of the eyepiece 4 can be expressed by the following formula based on the lens formula of classical optical theory:

[0057] In the formula: u1 and u2 represent the distances from the two light sources of the reflective component 5 to the eyepiece 4; v1 and v2 represent the distances from the image of the light source transmitted through the eyepiece 4 to the eyepiece 4; f1 represents the focal length of the eyepiece 4; and f2 represents the equivalent focal length of the lens and cornea of ​​the user's eye and / or the artificial eye.

[0058] Referring to Figure 4, which is a schematic diagram of the image imaging process of the high-precision whole-eye diopter detection device in this embodiment, it can be seen from the figure that after the light source illuminates the fundus retina, according to the law of reflection of light, the light is reflected from the fundus retina and then transmitted through the lens and cornea of ​​the eye to the eyepiece 4, and then transmitted from the eyepiece 4 to the imaging module 6, thus realizing the imaging of the fundus retina image.

[0059] Therefore, the device of this invention can not only detect the visual acuity of the macula, but also the visual acuity of the entire eye, including the peripheral retina, to obtain a complete visual acuity map and precise refraction data. This allows for a more accurate determination of the eye's refractive error and visual correction needs, making eyeglass prescriptions more personalized and precise. Furthermore, by detecting the visual acuity of the entire eye, the progression of myopia can be comprehensively and regularly monitored and quantified. By comparing changes in eye structure and retinal layers at different time points, the worsening trend of myopia can be detected early, allowing for effective prevention and control measures. This enables ophthalmologists to intervene and manage myopia earlier, reducing its adverse effects on visual health.

[0060] Example 2

[0061] As shown in Figure 5, this embodiment also provides a high-precision whole-eye vision detection method based on the high-precision whole-eye vision detection device described in Embodiment 1, the method comprising:

[0062] S1: Acquire fundus images taken by the device at different focusing positions;

[0063] S2: Record the focusing position data corresponding to the fundus image;

[0064] S3: Divide the fundus image into regions and obtain the clarity of each image region of the fundus image;

[0065] S4: For each image region, select the fundus image with the highest clarity in each image region as the target fundus image;

[0066] S5: Obtain the focusing position data corresponding to the target fundus image as the target focusing position data;

[0067] S6: For each image region, based on the target fundus image and the target focusing position data, calculate the visual acuity of each image region, thereby obtaining the visual acuity of each region in the entire fundus image.

[0068] In Embodiment 2 of the present invention, the method acquires target fundus images and target focusing position data for each region in the fundus image. By calculating the correspondence between the two, the diopter of the fundus image region is accurately calculated, thereby obtaining a diopter map of the entire eyeball. This allows for a more accurate determination of the eye's refractive power and visual correction needs, making eyeglass prescriptions more personalized and precise. The detailed data of each region of the entire eyeball obtained through calculation also allows ophthalmologists or ophthalmologists to regularly monitor and quantify the development of myopia. By comparing changes in eyeball structure and retinal layers at different time points, the worsening trend of myopia can be detected early, thereby taking effective prevention and control measures, formulating personalized myopia prevention and control strategies, and improving the effectiveness of myopia prevention and control.

[0069] Preferably, in steps S1 to S2, the fundus images at different focusing positions are captured by adjusting the objective lens moving component 8 in the imaging module 6 of the device. Then, a corresponding fundus image is obtained for each focusing position, and the corresponding focusing position data is recorded according to the automatic measurement component, thereby achieving accurate focusing to obtain a clear fundus image, and being able to monitor the change of focus position in real time to provide accurate image distance measurement results.

[0070] More preferably, in addition to setting up automated measurement components to record focusing position data, focusing position data can also be obtained through visual inspection, differential measurement, optical interferometry, and other measurement methods. The differential measurement method can use a differential measuring device (such as a micrometer eye or the longitudinal axis at the bottom of the microscope) to accurately measure the distance the objective lens has moved. The exact distance is determined by reading the scale or digital display, and this method is more accurate than visual inspection. Secondly, in some advanced microscope systems, optical interferometry can use optical interferometers (such as a Michelson interferometer) to measure the distance between the objective lens and the imaging plane. This method uses the movement of interference fringes to determine the distance the objective lens has moved, typically providing very accurate distance measurements. Those skilled in the art can choose appropriate methods as needed, and are not limited to the methods mentioned above.

[0071] Preferably, step S3 specifically includes: dividing the fundus image into regions according to a set size area, establishing a sharpness evaluation formula by calculating the maximum gray level difference between adjacent pixels in the fundus image and introducing a threshold to distinguish edge points and non-edge points, thereby calculating the sharpness of each image region in each fundus image.

[0072] For the division of fundus image regions, grid partitioning can be performed according to a fixed size, uniformly dividing the fundus image into grids of a fixed size. For example, the image can be divided into small blocks of 10x10 pixels, or larger blocks of 100x100 pixels, to allow for local analysis within each block; alternatively, region partitioning can be based on anatomical structures, dividing according to the size and location of ocular anatomical structures. For example, the optic disc region can be divided into a circular or elliptical region, and the macula region can also be divided according to its specific size and location; or adaptive partitioning can be performed, using adaptive methods to divide regions based on the specific characteristics of the fundus image and the analysis requirements. For example, the partitioning size can be adjusted according to the contrast or grayscale level changes of different parts of the image. Those skilled in the art can choose from the fundus image region partitioning methods mentioned above according to actual needs, and are not limited to the methods mentioned above. Furthermore, in practical applications, the size standard for region partitioning is usually set according to the needs and resolution requirements of medical image analysis. Smaller region partitioning can provide more refined local analysis, but it will also increase computational complexity and processing time. Therefore, choosing an appropriate region size when performing region segmentation requires a balance between the accuracy requirements of image analysis, processing efficiency, and computational resources.

[0073] By dividing fundus images into regions of a specific size and calculating the sharpness of each region, the local quality of fundus images can be evaluated more precisely. Different regions may have different levels of sharpness, and regional evaluation helps to determine the availability and information richness of specific parts in the fundus image. Furthermore, the sharpness of the image is quantified by calculating the maximum gray-level difference. At the same time, a threshold is introduced to distinguish between edge points and non-edge points for edge detection and segmentation, thereby improving the overall quality of fundus images. A sharpness evaluation formula is established to achieve automated evaluation of fundus image sharpness.

[0074] Preferably, the sharpness evaluation formula is:

[0075] Where: V(I) represents the normalized sharpness evaluation function value. The larger the value of V(I), the higher the sharpness of each image region; M and N represent the length and width of each image region of the fundus image, respectively; x and y represent the horizontal and vertical coordinates of the pixels in each image region, respectively; G″(x,y) represents the gradient image of each image region after removing false edges.

[0076] By setting specific formulas, the clarity level of different regions of the fundus image can be numerically evaluated, providing objective evaluation indicators. This provides objective and accurate data for subsequent calculation of the whole-eye diopter map, which helps to obtain a more accurate whole-eye diopter map.

[0077] Preferably, step S4 specifically involves: selecting the fundus image corresponding to the largest V(I) value in each image region from the V(I) values ​​calculated in step S3 as the target fundus image, thereby obtaining the target fundus image corresponding to each region in the fundus image.

[0078] By using the fundus image corresponding to the largest V(I) value in the image region as the target fundus image, the focus position data corresponding to the target fundus image can be quickly determined in step S5, thereby obtaining the target focus position data.

[0079] As shown in Figure 6, Figure 6 is a specific schematic diagram of the high-precision whole-eye vision map detection method of this embodiment for calculating the vision of a certain fundus image region. For the fundus image region, Figure 6 shows a specific schematic diagram for calculating the vision of the fundus image region based on the correspondence between the target fundus image and the target focusing position data. In Figure 6, l1, l2, and l3 are known fixed parameters: l1 is the distance from the user's eye and / or artificial eye 3 to the eyepiece 4; l2 is the distance from the eyepiece 4 to the imaging module 6; l3 is the distance from the internal lens of the imaging module 6 to the film of the image receiver 7; f1 is the focal length of the eyepiece 4; f2 is the equivalent focal length of the lens and cornea of ​​the user's eye and / or artificial eye 3; f3 is the focal length of the imaging module 6, i.e., the target focusing position data; v e v t v p Figure 6 shows the image distances of the user's eye and / or artificial eye 3, eyepiece 4, and imaging module 6, respectively. As can be seen from Figure 6, v p It equals l3.

[0080] The relationship between the focal length f2 of the user's eye and / or the artificial eye 3 and the visual acuity D of the target image region can be expressed by the following formula:

[0081] Furthermore, based on the lens formula of classical optics theory, and referring to Figure 6, the following relationship can be obtained:

[0082] Combining the graphical relationships shown in Figure 6, we can obtain the following relationship:

[0083] Preferably, by combining the above formulas (1), (2), and (3), the relationship between the visibility D of the target image region and the target focusing position data f3 can be obtained. The formula for calculating the visibility of the image region is as follows:

[0084] in, D represents the diopter of the target fundus image region; f3 represents the target focusing position data; l1, l2, and l3 are known fixed parameters, where l1 is the distance from the user's eye and / or artificial eye to the eyepiece, l2 is the distance from the eyepiece to the imaging module, and l3 is the distance from the lens inside the imaging module to the film of the image receiver 7; f1 is the focal length of the eyepiece; and f2 is the equivalent focal length of the lens and cornea of ​​the user's eye and / or artificial eye.

[0085] Using the aforementioned diopter formula, the diopter of the fundus image region can be accurately calculated simply by obtaining the corresponding target focusing position data f3, thereby constructing a whole-eye diopter map. This provides a fast and effective method for detecting the diopter status of the whole eye, including the macula and peripheral retina.

[0086] Obviously, the above embodiments of the present invention are merely examples for clearly illustrating the technical solution of the present invention, and are not intended to limit the specific implementation of the present invention. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the claims of the present invention should be included within the protection scope of the claims of the present invention.

Claims

1. A high-precision whole-eye diopter map detection device, characterized in that, The device includes: a light-emitting component for illuminating the fundus, a beam-shaping module for converging the light beam, a reflective component for reflecting the light beam, an eyepiece for transmission imaging, an eye gaze position for providing the eye detection position, an imaging module for imaging, and a data processing component for processing the image data. The eye gaze position, eyepiece, reflector, and imaging module are arranged sequentially on the same horizontal line; the data processing component is connected to the imaging module via a connecting line to receive and process the imaging data from the imaging module; and the light-emitting component, beam shaping module, and reflector are on the same vertical line.

2. The high-precision whole-eye diopter map detection device according to claim 1, characterized in that, The imaging module includes an internal lens for imaging, an image receiver for receiving the image, and an objective lens moving assembly for front and rear focusing. The objective lens moving assembly and the image receiver are respectively connected to the data processing assembly via connecting lines. The objective lens moving assembly moves the position of the internal lens to achieve precise focusing on all areas of the fundus, and receives the clearest image obtained through the image receiver.

3. The high-precision whole-eye diopter map detection device according to claim 2, characterized in that, The objective lens movement assembly is a manual or electric adjustment assembly, and has an automated measurement component that can record the focusing position data of the fundus images acquired at each position.

4. The high-precision whole-eye diopter map detection device according to any one of claims 1-3, characterized in that, The middle part of the reflective component is set as an open area, which is used for the light source reflected back through the fundus, while the unopened area is used to reflect the light source focused by the beam shaping module toward the direction of the eyepiece.

5. A high-precision whole-eye vision detection method based on the high-precision whole-eye vision detection device according to any one of claims 1-4, characterized in that, The method includes: S1: Acquire fundus images taken by the device at different focusing positions; S2: Record the focusing position data corresponding to the fundus image; S3: Divide the fundus image into regions and obtain the clarity of each image region of the fundus image; S4: For each image region, select the fundus image with the highest clarity in each image region as the target fundus image; S5: Obtain the focusing position data corresponding to the target fundus image as the target focusing position data; S6: For each image region, based on the target fundus image and the target focusing position data, calculate the visual acuity of each image region, thereby obtaining the visual acuity of each region in the entire fundus image.

6. The high-precision whole-eye diopter map detection method according to claim 5, characterized in that, In steps S1 to S2, fundus images at different focusing positions are captured by adjusting the objective lens moving component in the imaging module of the device, and the corresponding focusing position data are recorded by the automated measurement component.

7. The high-precision whole-eye diopter map detection method according to claim 5, characterized in that, In step S3, the specific steps include: dividing the fundus image into regions according to a set size area; establishing a sharpness evaluation formula by calculating the maximum gray level difference between adjacent pixels in the fundus image and introducing a threshold to distinguish edge points and non-edge points; thereby calculating the sharpness of each image region in each fundus image.

8. The high-precision whole-eye diopter map detection method according to claim 7, characterized in that, The formula for evaluating sharpness is: Where: V(I) represents the normalized sharpness evaluation function value. The larger the value of V(I), the higher the sharpness of each image region; M and N represent the length and width of each image region of the fundus image, respectively; x and y represent the horizontal and vertical coordinates of the pixels in each image region, respectively; G″(x,y) represents the gradient image of each image region after removing false edges.

9. The high-precision whole-eye diopter map detection method according to claim 8, characterized in that, Step S4 includes: selecting the fundus image corresponding to the largest V(I) value in each image region from the V(I) values ​​calculated in step S3 as the target fundus image, thereby obtaining the target fundus image corresponding to each region in the fundus image.

10. The high-precision whole-eye diopter map detection method according to claim 9, characterized in that, In step S6, the formula for calculating the viewpoint of the image region is: in, D represents the diopter of the target fundus image region; f3 represents the target focusing position data; l1, l2, and l3 are known fixed parameters, where l1 is the distance from the user's eye and / or artificial eye to the eyepiece, l2 is the distance from the eyepiece to the imaging module, and l3 is the distance from the lens inside the imaging module to the film of the image receiver; f1 is the focal length of the eyepiece; and f2 is the equivalent focal length of the lens and cornea of ​​the user's eye and / or artificial eye.

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