A universal method and device for detecting the focal length of human eye objects based on the ciliary body

Abstract

This invention relates to the field of optical detection, specifically to a universal method and device for detecting the focal length of a human eye based on the ciliary body. The method includes: obtaining the focal length of a sample group at different standard focal lengths f1 to f2. m The OCT light signal set of the ciliary body region was collected, and each different site M1 to M2 was extracted from the OCT light signal set. n Points P1 to P2 in different layers i The sample light reflectance coefficients, after normalization transformation, are used to obtain different standard focal lengths f1 to f2. m The invention obtains the "feature point-sample mean light reflectance coefficient curve" and the "feature point-measured light reflectance coefficient curve" for any focal length of the subject, and fits it with the "feature point-sample mean light reflectance coefficient curve" to obtain the measured focal length value of the subject. This invention achieves universal detection of the human eye's actual focal length based on the ciliary body, avoiding eye discomfort caused by laser irradiation of the lens, allowing the subject to enjoy a better testing experience with less eye stimulation, and further making focal length detection more accurate.

Description

Technical Field

[0001] This invention relates to the field of optical detection, specifically to a method and apparatus for universal detection of the focal length of a human eye object based on the ciliary body. Background Technology

[0002] Optical coherence tomography (OCT) is a high-resolution, non-contact imaging technique for biological tissues, similar to ultrasound but using light instead of sound waves to generate images. It measures the scattering and propagation delay of light pulses within a sample, processing this data to create high-resolution, deep images that analyze the microstructure of living tissues without physical contact. Lateral scanning can rapidly acquire clear, non-invasive two-dimensional and three-dimensional images.

[0003] Since its introduction into ophthalmology, OCT has emerged as a new non-contact, non-invasive ophthalmic imaging diagnostic technology. It uses the different light reflection, absorption, and scattering abilities of various ocular tissues to perform tomographic imaging of tissues, so as to clearly distinguish the various tissue structures of the eye. Its resolution is as high as 5μm, making it a common ophthalmic imaging diagnostic technology.

[0004] Traditionally, when using OCT to detect the focal length of the human eye, it is necessary to use a laser with a wavelength >1µm to illuminate the lens of the eye. Because this method directly illuminates the transparent lens, and the lens itself has a unique lensing effect, in some special cases, such as when the incident light is focused on a tiny area by impurities or lesions on the surface of the conjunctiva of the eyeball, causing conjunctival cell necrosis to form scars or nodular degeneration, which can lead to microlenses, the laser light passing through these microlenses can suddenly increase the energy of the laser beam concentrated at a single point in a short period of time. This can potentially cause photostimulation to the outermost cone and rod cells of the retina behind the lens. When the photostimulation energy reaches or exceeds the upper limit that the cells can withstand, it may cause discomfort, and in severe cases, it may lead to cell burns or death, resulting in the risk of local visual loss or decline. Summary of the Invention

[0005] In existing technologies for object focus detection, when laser light is irradiated onto the lens of the eye, due to the lens effect inherent in the lens itself, under certain circumstances, the energy of the laser light concentrated at a single point may suddenly increase, potentially causing photostimulation to the outermost cone and rod cells of the retina behind the lens. When the photostimulation energy reaches or exceeds the upper limit that the cells can withstand, it may cause discomfort, and in severe cases, lead to cell burns or death, resulting in the risk of localized visual loss or decline.

[0006] A universal method for detecting the focal length of human objects based on the ciliary body is proposed, including:

[0007] S1: Obtain the sample population focused at different standard focal lengths f1 to f2. m The OCT light signal set of the ciliary body region was collected, and each different site M1 to M2 was extracted from the OCT light signal set. n Points P1 to P2 in different layers i The sample light reflectance coefficients, after normalization transformation, are used to obtain different standard focal lengths f1 to f2. m The "feature point-sample mean light reflectance coefficient curve" below;

[0008] S2: Obtain the focal length f of the subject at any given focal length. x The measured OCT light signal set of the ciliary body region was used to extract M1 to M2 from each different site calibrated in the measured OCT light signal set. n Points P1 to P2 in different layers i The measured light reflectance coefficient, after normalization transformation, is used to obtain the focal length f. x The "feature point-measured light reflectance coefficient curve" is obtained and fitted with the "feature point-sample mean light reflectance coefficient curve" to obtain the measured focal length f of the current person being measured. x The value of .

[0009] Preferably, S1 specifically includes:

[0010] S11: Obtain sample OCT light signal sets for y samples of y×m ciliary body sites at m different focal lengths from y sample individuals;

[0011] S12: Extract samples from y×m ciliary body sites into an OCT optical signal set. Each signal set contains n ciliary body site locations M1~M2. n At each site, there are i layer points P1 to P2. i The light reflectance coefficients of y×m×n×i samples;

[0012] S13: Average the light reflectance coefficients with the same focal point among the obtained y×m×n×i sample light reflectance coefficients to obtain the average light reflectance coefficients of m×n×i samples.

[0013] S14: Normalize the mean light reflectance coefficients of the m×n×i samples to generate m "feature point-sample mean light reflectance coefficient relationship curves", where the abscissa of the curves in the m "feature point-sample mean light reflectance coefficient relationship curves" is the feature point P1~P i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points.

[0014] Preferably, S12 specifically includes:

[0015] S121: Mark n sites M1~M on the sagittal surface of the ciliary body. n;

[0016] S122: At n sites M1~M n Sampling points P1 to P2 are taken at intervals along the laser axis of the ciliary body tissue region at each site. i ;

[0017] S123: Traverse the sample OCT light signal sets of y×m ciliary body regions, and extract the M1~M values ​​calibrated in each sample OCT light signal set. n The set of light reflectance coefficients for n sample sites within a given location;

[0018] S124: Extract the light reflectance coefficients of n sample sites and assign different layer points P1 to P2 to each site. i The light reflectance coefficients of n×i sample layer points.

[0019] Preferably, S2 specifically includes:

[0020] S21: Obtain the focal length f of the subject at any given focal length. x Measured OCT light signal set of the ciliary body region below;

[0021] S22: Extract each site M1 to M from the measured OCT optical signal and calibrate it. n The set of light reflectance coefficients at n measured sites;

[0022] S23: Extract the light reflectance coefficients of n×i measured layer points P1~Pi at each site calibrated by the measured OCT optical signal;

[0023] S24: Based on n ciliary body sites M1~M n At each site, there are i layer points P1 to P2. i The measured light reflectance coefficient is normalized to generate a "feature point-measured light reflectance coefficient relationship curve", where the abscissa of the curve is the feature point P1 to P2. i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points;

[0024] S25: Fit the obtained "feature point-measured light reflectance coefficient relationship curve" to m "feature point-sample mean light reflectance coefficient curves" respectively, select the focal length corresponding to the curve with the best fit among the sample mean curves as the near-optimal focal length, and obtain the measured focal length f of the current person being tested. x The value of .

[0025] Preferably, the midpoint of S22 can be selected from M1 to M2. n A subset of the site set.

[0026] Preferably, the different layer points P1 to P2 are...i In the case of i, i ≥ 1.

[0027] A detection device for a universal method of detecting the focal length of a human eye based on the ciliary body, characterized in that it comprises:

[0028] General module: Used to obtain the focal length of the sample population at different standard focal lengths f1 to f2. m The OCT light signal set of the ciliary body region was collected, and each different site M1 to M2 was extracted from the OCT light signal set. n Points P1 to P2 in different layers i The sample light reflectance coefficients, after normalization transformation, are used to obtain different standard focal lengths f1 to f2. m The "feature point-sample mean light reflectance coefficient curve" below;

[0029] The actual measurement module is used to obtain the focal length f of the person being tested. x The measured OCT light signal set of the ciliary body region was used to extract M1 to M2 from each different site calibrated in the measured OCT light signal set. n Points P1 to P2 in different layers i The measured light reflectance coefficient, after normalization transformation, is used to obtain the focal length f. x The "feature point-measured light reflectance coefficient curve" is obtained and fitted with the "feature point-sample mean light reflectance coefficient curve" to obtain the measured focal length f of the current person being measured. x The value of .

[0030] Preferably, the measured reference module includes:

[0031] First data acquisition unit: used to obtain sample OCT light signal sets of y×m ciliary body parts of y sample personnel with m different focal lengths;

[0032] Data extraction unit: used to extract samples from y×m ciliary body sites from the OCT optical signal set. Each signal set contains n ciliary body site sites M1 to M2. n At each site, there are i layer points P1 to P2. i The light reflectance coefficients of y×m×n×i samples;

[0033] Data mean unit: used to average the light reflectance coefficients with the same focal point among the obtained y×m×n×i sample light reflectance coefficients, to obtain the mean light reflectance coefficients of m×n×i samples;

[0034] The first normalization unit is used to normalize the mean light reflectance coefficients of m×n×i samples, generating m "feature point-sample mean light reflectance coefficient relationship curves", where the abscissa of the curves in the m "feature point-sample mean light reflectance coefficient relationship curves" is the feature point P1 to P2.i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points.

[0035] Preferably, the data extraction unit includes:

[0036] First calibration subunit: used to calibrate n sites M1 to M2 on the sagittal surface of the ciliary body. n ;

[0037] Second calibration subunit: used for calibration at n sites M1~M n Sampling points P1 to P2 are taken at intervals along the laser axis of the ciliary body tissue region at each site. i ;

[0038] The first analysis subunit is used to traverse the sample OCT light signal sets of y×m ciliary body regions and extract the M1~M values ​​calibrated in each sample OCT light signal set. n The set of light reflectance coefficients for n sample sites within a given location;

[0039] The second analysis subunit is used to extract the light reflectance coefficients of n sample sites, with different layer points P1 to P2 labeled at each site. i The light reflectance coefficients of n×i sample layer points.

[0040] Preferably, the actual measurement and testing module includes:

[0041] Second data acquisition unit: used to obtain the focal length f of the person being tested. x Measured OCT light signal set of the ciliary body region below;

[0042] The third analysis unit is used to extract each site M1 to M from the measured OCT optical signal calibration. n The set of light reflectance coefficients at n measured sites;

[0043] The fourth analysis unit is used to extract the light reflectance coefficients of n × i measured layer points P1 to Pi at each site calibrated by the measured OCT optical signal.

[0044] Second normalization unit: used to normalize based on n ciliary body sites M1~M n At each site, there are i layer points P1 to P2. i The measured light reflectance coefficient is normalized to generate a "feature point-measured light reflectance coefficient relationship curve", where the abscissa of the curve is the feature point P1 to P2. i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points;

[0045] Output Unit: The obtained "feature point-measured light reflectance coefficient relationship curve" is fitted to m "feature point-sample mean light reflectance coefficient curves" respectively. The focal length corresponding to the curve with the best fit among the sample mean curves is selected as the near-optimal focal length, and the measured focal length f of the current person being measured is obtained. x The value of .

[0046] This invention discloses a universal method for detecting the focal length of real objects in the human eye based on the ciliary body. When the human eye focuses on viewing real objects with different focal lengths, relevant state data of the selected ciliary body are recorded. By exploring the relationship between this data and the focal length, the focal length of real objects in the human eye based on the ciliary body can be detected. Compared with the traditional method based on the lens, this method avoids the discomfort caused by the light passing through the lens and ultimately falling on the retina when the laser irradiates the lens for detection. The visual cells are stimulated by the strong light beam, which can cause eye discomfort. This invention can provide a better testing experience for the test subject and avoid further problems in the accuracy of focal length detection caused by changes in the human eye's focus due to avoiding stimulation. Attached Figure Description

[0047] The accompanying drawings, which are included to provide a further understanding of the embodiments of the present invention and form part of this application, are not intended to limit the embodiments of the present invention.

[0048] Figure 1 This is a flowchart of the universal method for detecting the focal length of the human eye based on the ciliary body according to the first embodiment of the present invention.

[0049] Figure 2 This is a flowchart of the method for obtaining the "feature point-sample mean light reflectance coefficient relationship curve" in the first embodiment of the present invention;

[0050] Figure 3 This is a flowchart of the method for obtaining the light reflectance coefficient of a sample according to the first embodiment of the present invention;

[0051] Figure 4 This is a flowchart of the method for obtaining the measured focal length of the current test subject according to the first embodiment of the present invention;

[0052] Figures 5-6 A flowchart for generating the "feature point-sample mean light reflectance coefficient curve" data processing method in the first embodiment of the present invention;

[0053] Figure 7 This is a flowchart illustrating the process of obtaining the measured focal length data of the current test subject according to the first embodiment of the present invention.

[0054] Figure 8 This is a schematic diagram of site selection in the ciliary body region according to the first embodiment of the present invention;

[0055] Figure 9This is a schematic diagram of the light transmission point of the ciliary body region in the first embodiment of the present invention;

[0056] Figure 10 This is a schematic diagram of the lower layer feature points of the ciliary body region in the first embodiment of the present invention;

[0057] Figure 11 To obtain different standard focal lengths f1 to f2 using the normalized transformation of the light reflection coefficients of characteristic points in the ciliary body region of the first embodiment of the present invention. m The following is a schematic diagram of the "feature point-measured reference light reflectance coefficient curve";

[0058] Figure 12 A schematic diagram of the state of the lens and ciliary body when the human eye focuses on observing a real object;

[0059] Figure 13 This is a schematic diagram of the detection device structure of the human eye object focal length detection method based on the ciliary body according to the second embodiment of the present invention. Detailed Implementation

[0060] The technical solutions of the embodiments of this disclosure will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of this disclosure, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this disclosure.

[0061] The following explains some of the terms mentioned in the embodiments of this disclosure.

[0062] The lens and ciliary body mentioned in this disclosure are parts of the human eye. The human eye is shaped like a small ball and is commonly referred to as the eyeball. The eyeball has a special refractive system that allows visible light entering the eye to converge onto the retina. The retina contains photoreceptor rod cells and cone cells. These photoreceptor cells transmit the received color light signals to ganglion cells, and then from the optic nerve to the visual cortex in the occipital lobe of the brain, producing color perception.

[0063] Eye imaging is an important application of lens imaging. Cameras and eyes have similar structures. The cornea and lens in the eyeball work together to form a "convex lens," while the retina acts like the film in a camera. Light rays emitted from an object are focused by the lens, causing the light beam to converge onto the retina, which is rich in cone and rod cells, forming an inverted, reduced real image. The optic nerve cells on the retina are stimulated by the light, transmitting this signal to the brain. After processing, the brain can see an upright image of the object.

[0064] Unlike camera lenses, the lens is more like a convex lens that automatically adjusts its focus. Because a convex lens controls the focal length by adjusting its surface curvature, the lens's radius of curvature decreases when viewing near objects and increases when viewing distant objects. This ensures that the object's image is precisely focused on the retina, allowing us to see it clearly. This change in the lens's surface curvature is achieved through the ciliary body. The ciliary muscle in the ciliary body, via suspensory ligaments, pulls the lens to change its surface curvature, thus adjusting the focus of near and far objects onto the retina. Figure 11 As shown, when the ciliary muscle contracts, the lens is stretched, thinned, and its radius of curvature increases, allowing us to see distant objects. When the ciliary muscle relaxes, the lens thickens and its radius of curvature decreases, allowing us to see nearby objects. It also relaxes when we are resting. Therefore, the lens is directly related to the actual focal length of the human eye, while the ciliary body is indirectly related. Traditionally, when the eye is focused on an object, a laser is directly used to illuminate the lens, which is directly related to focal length adjustment. The standard focal length of the eye is then determined by observing the lens's data. However, due to the inherent characteristics of laser light, the energy it carries, after passing through the transparent lens, will fall onto the retina via the equally transparent vitreous humor. Since the entire optical path is a light refraction system, under certain conditions, this can cause light energy stimulation to the retina and photoreceptor cells. This invention uses laser to irradiate the ciliary body, which is indirectly related to focal length adjustment. By observing the relevant data of the ciliary body, the standard focal length of the human eye can be detected. Since it does not pass through the lens, the focal length will not fall on the retina during the detection, thus avoiding stimulation of visual cells and discomfort to the human eye.

[0065] Example 1

[0066] like Figure 1 As shown, a universal method for detecting the focal length of a real object in the human eye based on the ciliary body is proposed. This method includes the following steps:

[0067] S1: Obtain the sample population focused at different standard focal lengths f1 to f2. m The OCT light signal set of the ciliary body region was collected, and each different site M1 to M2 was extracted from the OCT light signal set. n Points P1 to P2 in different layers i The sample light reflectance coefficients, after normalization transformation, are used to obtain different standard focal lengths f1 to f2. m The "feature point-sample mean light reflectance coefficient curve" below;

[0068] S2: Obtain the focal length f of the subject at any given focal length. xThe measured OCT light signal set of the ciliary body region was used to extract M1 to M2 from each different site calibrated in the measured OCT light signal set. n Points P1 to P2 in different layers i The measured light reflectance coefficient, after normalization transformation, is used to obtain the focal length f. x The "feature point-measured light reflectance coefficient curve" is obtained and fitted with the "feature point-sample mean light reflectance coefficient curve" to obtain the measured focal length f of the current person being measured. x The value of .

[0069] It is important to understand that the "feature point-sample mean light reflectance coefficient curve" obtained from the sample population in S1 of this embodiment is a general curve. S1 can be used as a preliminary step. After obtaining the "feature point-sample mean light reflectance coefficient curve," it can be built into the computer as a "reference standard." When subsequently detecting the focal length of the tested person, S2 can be executed directly. At this point, only the measured light reflectance coefficient of the tested person needs to be obtained. By fitting the obtained measured light reflectance coefficient with the "reference standard," the focal length of the tested person can be obtained. The method of this invention is suitable for detecting the focal length of a large number of tested persons in a relatively short period of time.

[0070] Specifically, such as Figure 2 As shown, S1 specifically includes:

[0071] S11: Obtain sample OCT light signal sets for y samples of y×m ciliary body sites at m different focal lengths from y sample individuals;

[0072] It's important to understand that while each convex lens has a fixed focal length, called its standard focal length, the human eye's lens is a "variable convex lens." Each time it transforms into a different "convex lens," a different standard focal length is obtained. The change in the lens's surface curvature is due to the eye's automatic adjustment of its thickness—autofocus—to see objects at different distances. Therefore, when the eye's position is fixed, by placing objects at different distances from the eye, different standard focal lengths of lens surface curvature can be obtained when the eye focuses on each object. Since the change in lens surface curvature is achieved through the contraction and relaxation of the ciliary muscle in the ciliary body, different lens surface curvature states correspond to different standard focal lengths. This means that different states of light reflectivity in the ciliary tissue—tension and relaxation—correspond to different standard focal lengths. Thus, by having the subject focus on objects at different positions, the OCT light signal sets of the ciliary body region under different standard focal lengths can be obtained.

[0073] S12: Extract samples from y×m ciliary body sites into an OCT optical signal set. Each signal set contains n ciliary body site locations M1~M2.n At each site, there are i layer points P1 to P2. i The light reflectance coefficients of y×m×n×i samples;

[0074] It is important to understand that each sample OCT optical signal set contains a large amount of ciliary body state information. When processing, it is necessary to select several calibrated feature points on the ciliary body and observe the changes in the ciliary body state information at these feature points.

[0075] S13: Average the light reflectance coefficients with the same focal length among the obtained y×m×n×i sample light reflectance coefficients to obtain the average light reflectance coefficients of m×n×i samples.

[0076] It is important to understand that due to individual differences, when observing objects with the same focal length, the state information of the same feature points of the ciliary body of each person in the sample population will be slightly different. In order to obtain a more objective and meaningful relationship between feature points and light reflectance coefficients, it is necessary to average the light reflectance coefficients of each feature point with the same focal length among the obtained y×m×n×i sample light reflectance coefficients to obtain m×n×i sample average light reflectance coefficients.

[0077] S14: Normalize the mean light reflectance coefficients of the m×n×i samples to generate m "feature point-sample mean light reflectance coefficient relationship curves", where the abscissa of the curves in the m "feature point-sample mean light reflectance coefficient relationship curves" is the feature point P1~P i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points.

[0078] It's important to understand that, at the same focal length, the "feature point-sample mean light reflectance coefficient relationship curve" is obtained at point M1, at point M2, and so on. Each point yields its own "feature point-sample mean light reflectance coefficient relationship curve." Since these curves represent light reflectance coefficients obtained at different depths during a single laser irradiation, the goal is to efficiently acquire as much optical signal data as possible. Therefore, by analyzing curves from M1 to M2... n The n "feature point-sample mean light reflectance coefficient relationship curves" corresponding to each site are normalized to obtain a more accurate "feature point-sample mean light reflectance coefficient relationship curve" at that focal length. There are m focal lengths, so there are m "feature point-sample mean light reflectance coefficient relationship curves".

[0079] Specifically, such as Figure 3 As shown, S12 specifically includes:

[0080] S121: Mark n sites M1~M on the sagittal surface of the ciliary body. n ;

[0081] S122: At n sites M1~M n Sampling points P1 to P2 are taken at intervals along the laser axis of the ciliary body tissue region at each site. i ;

[0082] S123: Traverse the sample OCT light signal sets of y×m ciliary body regions, and extract the M1~M values ​​calibrated in each sample OCT light signal set. n The set of light reflectance coefficients for n sample sites within a given location;

[0083] S124: Extract the light reflectance coefficients of n sample sites and assign different layer points P1 to P2 to each site. i The light reflectance coefficients of n×i sample layer points.

[0084] Specifically, such as Figure 4 As shown, S2 specifically includes:

[0085] S21: Obtain the focal length f of the subject at any given focal length. x Measured OCT light signal set of the ciliary body region below;

[0086] S22: Extract each site M1 to M from the measured OCT optical signal and calibrate it. n The set of light reflectance coefficients at n measured sites;

[0087] S23: Extract the light reflectance coefficients of n×i measured layer points P1~Pi at each site calibrated by the measured OCT optical signal;

[0088] S24: Based on n ciliary body sites M1~M n At each site, there are i layer points P1 to P2. i The measured light reflectance coefficient is normalized to generate a "feature point-measured light reflectance coefficient relationship curve", where the abscissa of the curve is the feature point P1 to P2. i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points;

[0089] S25: Fit the obtained "feature point-measured light reflectance coefficient relationship curve" to m "feature point-sample mean light reflectance coefficient curves" respectively, select the focal length corresponding to the curve with the best fit among the sample mean curves as the near-optimal focal length, and obtain the measured focal length f of the current person being tested. x The value of .

[0090] It is important to understand that, based on the obtained "feature point-sample mean light reflectance coefficient relationship curve," we obtain a "reference standard" for the standard focal length corresponding to each ciliary body state. After obtaining the measured OCT light signal set, we repeat the same generation route as the "feature point-measured reference light reflectance coefficient relationship curve," which also requires processing the obtained n ciliary body sites M1 to M2. n At each site, there are i layer points P1 to P2. i The measured reflectance coefficient is normalized to generate a "feature point-measured reflectance coefficient relationship curve". After obtaining this relationship curve, it is fitted with m "feature point-measured reference reflectance coefficient relationship curves". The "feature point-measured reference reflectance coefficient relationship curve" with the highest fit is selected. The focal length corresponding to this measured reference curve is the closest suitable focal length to the actual focal length of the person being tested. It can be considered as the measured focal length of the person being tested at this time. The focal length value corresponding to this measured reference curve is F. x The value of .

[0091] Specifically, the sites in S22 can be selected from M1 to M2. n A subset of the site set.

[0092] It is important to understand that after obtaining the measured reference data of the test subjects, the "characteristic point-measured reference light reflectance coefficient relationship curve" obtained by the test subjects is our reference standard. When conducting actual tests on the test subjects, the characteristic points of the ciliary body of the test subjects are selected. At this time, a subset of the characteristic points of the ciliary body selected in the measured reference data of the test subjects can be selected.

[0093] Specifically, the different layer points P1 to P... i In the case of i, i ≥ 1.

[0094] like Figure 5 , Figure 6 As shown in the example, when y = 2, m = 4, n = 5, and i = 3, the method of the present invention can be implemented through the following embodiments:

[0095] When there are four focal lengths f1, f2, f3, and f4, five different sites are selected on the sagittal surface of the ciliary body of the first sample person, such as... Figure 8 , Figure 9 As shown, the points are sequentially labeled as M1, M2, M3, M4, and M5, and represented as points a, b, c, d, and e in the diagram. At each point, points in the first, second, and third layers are sampled at intervals along the laser axis (vertical direction in the diagram), as follows: Figure 10 As shown, the first layer point below the first point is denoted as P. 11The second point below the first point is denoted as P. 12 The third point below the first point is denoted as P. 13 Similarly, the layer points below the second point are denoted as P. 21 P 22 P 23 The sub-layers below the third site are denoted as P. 31 P 32 P 33 The sub-layers below the fourth site are denoted as P. 41 P 42 P 43 The sub-layers below the fifth site are denoted as P. 51 P 52 P 53 When the first sample person is focusing on viewing the first focal length object, the ciliary body is illuminated with a laser, and the OCT light signal set H of the ciliary body at focal length f1 is obtained. 1-1 To obtain the set F of light reflectance coefficients at different sites in the ciliary body. 1-1 = {M1, M2, M3, M4, M5}, then we obtain the relevant data F of the second sample person. 2-1 ={M1, M2, M3, M4, M5}, the light reflectance coefficients of the ciliary body feature points of the second sample person are averaged with the light reflectance coefficients of the same feature points of the ciliary body of the first sample person, that is, F 1-1 M1 and F 2-1 Calculate the average value of M1 in F, and then... 1-1 M2 and F 2-1 The average value of M2 is calculated, and so on, to obtain the set of mean light reflectance coefficients F at different sites in the ciliary body under f1. f1 ={M1, M2, M3, M4, M5}, where the set of light reflectance coefficients of different sites M1 to M5 and different layer points P1 to P3 in the ciliary body is M1 = {U P11 U P12 U P13}, M2={U P21 U P22 U P23}, M3={U P31 U P32 U P33}, M4={U P41 U P42 U P43}, M5={U P51 U P52 U P53}, where U P11The meaning represented is the light reflectance coefficient of the first layer point below the first point, U. P53 This indicates the light reflectance coefficient at the third layer point below the fifth position. For example... Figure 11 As shown, for M1 = {U} at focal length f1 P11 U P12 U P13}, which yields the corresponding feature point-light reflectance coefficient discrete data L M1 The vertical axis represents the light reflectance coefficient, and the horizontal axis represents the feature point (P). 11 P 12 P 13 For M2 = {U} at focal length f1 P21 U P22 U P23}, which yields the corresponding feature point-light reflectance coefficient discrete data L M2 The vertical axis represents the light reflectance coefficient, and the horizontal axis represents the feature point (P). 21 P 22 P 23 Similarly, L is obtained sequentially. M3 L M4 L M5 Because the first layer points P corresponding to sites M1, M2, M3, M4, and M5 11 P 12 P 13 P 14 P 15 They are extremely similar, P 11 P 12 P 13 P 14 P 15 After normalization, a relative ratio value of P1 for the first layer is obtained at focal length f1. Similarly, the relative ratio value of P2 for the second layer of 5 sites is obtained by normalization, and the relative ratio value of P3 for the third layer of 5 sites is obtained by normalization. A "feature point-light reflectance coefficient curve L" is constructed at focal length f1, with P1, P2, and P3 as the x-axis and the corresponding relative ratios of P1, P2, and P3 as the y-axis. F1 Similarly, L is obtained sequentially. F2 L F3 L F4 .

[0096] like Figure 7 As shown, when the subject is focusing on viewing any focal length f x When measuring an object, the OCT light signal set H of the ciliary body region of the subject is obtained. x The set of light reflectance coefficients at different sites in the ciliary body F x= {M1, M2, M3, M4, M5}, the set F of light reflectance coefficients x It is the optical signal set H x After analog-to-digital conversion, the set of light reflectance coefficients at different layer points P1-P3 of different sites M1-M5 in the ciliary body is M1={U P11 U P12 U P13}, M2={U P21 U P22 U P23}, M3={U P31 U P32 U P33}, M4={U P41 U P42 U P43}, M5={U P51 U P52 U P53 After normalization, the "feature point-light reflectance coefficient curve L" is obtained. Fx The vertical axis represents the relative ratios of P1, P2, and P3, and the horizontal axis represents P1, P2, and P3. Let L... Fx With L F1 L F2 L F3 L F4 Fit each curve separately, and select the curve with the highest fit. If L Fx With L F1 The best fit is achieved by f. x =f1, from which the current focal length of the person being measured can be obtained.

[0097] Example 2

[0098] A detection device based on a universal method for detecting the focal length of a real human eye using the ciliary body, such as... Figure 13 As shown, it includes:

[0099] General module: Used to obtain the focal length of the sample population at different standard focal lengths f1 to f2. m The OCT light signal set of the ciliary body region was collected, and each different site M1 to M2 was extracted from the OCT light signal set. n Points P1 to P2 in different layers i The sample light reflectance coefficients, after normalization transformation, are used to obtain different standard focal lengths f1 to f2. m The "feature point-sample mean light reflectance coefficient curve" below;

[0100] The actual measurement module is used to obtain the focal length f of the person being tested. xThe measured OCT light signal set of the ciliary body region was used to extract M1 to M2 from each different site calibrated in the measured OCT light signal set. n Points P1 to P2 in different layers i The measured light reflectance coefficient, after normalization transformation, is used to obtain the focal length f. x The "feature point-measured light reflectance coefficient curve" is obtained and fitted with the "feature point-sample mean light reflectance coefficient curve" to obtain the measured focal length f of the current person being measured. x The value of .

[0101] Specifically, the measured reference module includes:

[0102] First data acquisition unit: used to obtain sample OCT light signal sets of y×m ciliary body parts of y sample personnel with m different focal lengths;

[0103] Data extraction unit: used to extract samples from y×m ciliary body sites from the OCT optical signal set. Each signal set contains n ciliary body site sites M1 to M2. n At each site, there are i layer points P1 to P2. i The light reflectance coefficients of y×m×n×i samples;

[0104] Data mean unit: used to average the light reflectance coefficients with the same focal point among the obtained y×m×n×i sample light reflectance coefficients, to obtain the mean light reflectance coefficients of m×n×i samples;

[0105] The first normalization unit is used to normalize the mean light reflectance coefficients of m×n×i samples, generating m "feature point-sample mean light reflectance coefficient relationship curves", where the abscissa of the curves in the m "feature point-sample mean light reflectance coefficient relationship curves" is the feature point P1 to P2. i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points.

[0106] Specifically, the data extraction unit includes:

[0107] First calibration subunit: used to calibrate n sites M1 to M2 on the sagittal surface of the ciliary body. n ;

[0108] Second calibration subunit: used for calibration at n sites M1~M n Sampling points P1 to P2 are taken at intervals along the laser axis of the ciliary body tissue region at each site. i ;

[0109] The first analysis subunit is used to traverse the sample OCT light signal sets of y×m ciliary body regions and extract the M1~M values ​​calibrated in each sample OCT light signal set. nThe set of light reflectance coefficients for n sample sites within a given location;

[0110] The second analysis subunit is used to extract the light reflectance coefficients of n sample sites, with different layer points P1 to P2 labeled at each site. i The light reflectance coefficients of n×i sample layer points.

[0111] Specifically, the actual measurement and testing module includes:

[0112] Second data acquisition unit: used to obtain the focal length f of the person being tested. x Measured OCT light signal set of the ciliary body region below;

[0113] The third analysis unit is used to extract each site M1 to M from the measured OCT optical signal calibration. n The set of light reflectance coefficients at n measured sites;

[0114] The fourth analysis unit is used to extract the light reflectance coefficients of n × i measured layer points P1 to Pi at each site calibrated by the measured OCT optical signal.

[0115] Second normalization unit: used to normalize based on n ciliary body sites M1~M n At each site, there are i layer points P1 to P2. i The measured light reflectance coefficient is normalized to generate a "feature point-measured light reflectance coefficient relationship curve", where the abscissa of the curve is the feature point P1 to P2. i The vertical axis of the curve represents the relative ratio of the light reflectance coefficients at the characteristic points;

[0116] Output Unit: The obtained "feature point-measured light reflectance coefficient relationship curve" is fitted to m "feature point-sample mean light reflectance coefficient curves" respectively. The focal length corresponding to the curve with the best fit among the sample mean curves is selected as the near-optimal focal length, and the measured focal length f of the current person being measured is obtained. x The value of .

[0117] It is understood that the above embodiments are merely exemplary embodiments used to illustrate the principles of the present invention, and the present invention is not limited thereto. For those skilled in the art, various modifications and improvements can be made without departing from the spirit and essence of the present invention, and these modifications and improvements are also considered to be within the scope of protection of the present invention.

Claims

1. A general method for detecting the real focal length of a human eye based on the ciliary body, characterized in that, Comprising: S1: Obtain the sample population focused at different standard focal lengths f1 to f2. m The OCT light signal set of the ciliary body region was collected, and each different site M1 to M2 was extracted from the OCT light signal set. n Points P1 to P2 in different layers i The sample light reflectance coefficients, after normalization transformation, are used to obtain different standard focal lengths f1 to f2. m The "feature point-sample mean light reflectance coefficient curve" below; S1 specifically comprises: S11: obtaining a sample OCT light signal set of yx m ciliary body parts of y sample persons about m different focal lengths; S12: extract y x m sample OCT light signal sets each of which has n ciliary body site points M1~M n in each of the y x m sample OCT light signal sets i y x m x n x i sample light reflection coefficients S13: Among the obtained y×m×n×i sample light reflectance coefficients, n ciliary body sites M1~M1 with the same focal length are selected. n At each site, there are i layer points P1 to P2. i The light reflectance coefficients are averaged to obtain the average light reflectance coefficients of m×n×i samples. S14: normalizing the m*n*i sample mean light reflection coefficients to generate m "feature point-sample mean light reflection coefficient relationship curves", wherein the horizontal coordinates of the m "feature point-sample mean light reflection coefficient relationship curves" are feature points P1-Pm, and the vertical coordinates are feature point light reflection coefficient relative ratios. i , the horizontal coordinates of the m "feature point-sample mean light reflection coefficient relationship curves" are feature points P1-Pm, and the vertical coordinates are feature point light reflection coefficient relative ratios. S2: Obtain the focal length f of the subject at any given focal length. x The measured OCT light signal set of the ciliary body region was used to extract each different site M1 to M from the measured OCT light signal set. n Points P1 to P2 in different layers i The measured light reflectance coefficient, after normalization transformation, is used to obtain the focal length f. x The "feature point-measured light reflectance coefficient curve" is obtained and fitted with the "feature point-sample mean light reflectance coefficient curve" to obtain the measured focal length f of the current person being measured. x The value of .

2. The ciliary body based human eye real focal length universal probing method according to claim 1, characterized in that, S12 specifically comprises: S121: calibrate n points M1-Mn on the sagittal plane surface in the ciliary body part n ; S122: The ciliary body tissue region at each of the n sites M1~Mn along the laser axis direction is sampled at the interval of the layer points P1~Pn. n i ;​ S123: traversing the sample OCT light signal set of y x m ciliary body sites, extracting the set of n sample light reflection coefficients of the n sample sites in the calibrated M1~Mm ciliary body site in each sample OCT light signal set n site S124: Extracting the different layer points P1~Pn of each site index in the n sample site light reflection coefficient set i nx i sample layer point light reflection coefficients.

3. The ciliary body based human eye real focal length universal probing method according to claim 1, characterized in that, S2 specifically comprises: S21: obtaining a measured OCT light signal set of the ciliary body part of the person under test focusing on any focal length f x S21: obtaining a measured OCT light signal set of the ciliary body part of the person under test focusing on any focal length f S22: extracting each site M1~Mn of the measured OCT light signal set for calibration n n measured site light reflection coefficient set S23: extracting the different layer point P1~Pn of each site under the calibration of the measured OCT light signal set i n×i measured layer point light reflection coefficients; S24: The n ciliary body part site points M1~Mn are divided into i layer points P1~Pi in each site according to the ciliary body part site point division method of S23. n i The measured light reflection coefficient of each layer point is normalized to generate a "feature point-measured light reflection coefficient relationship curve", in which the curve abscissa is the feature point P1~Pi i , and the curve ordinate is the relative ratio of the feature point light reflection coefficient.​ S25: The obtained "feature point-actual light reflection coefficient relationship curve" is respectively fitted with m "feature point-sample mean light reflection coefficient curves", and the focal length corresponding to the curve with the optimal fitting degree in the sample mean curve is selected as the near focal length, to obtain the value of the actual focal length f of the current measured person. x of the value.

4. The ciliary body based human eye real focal length universal probing method according to claim 3, characterized in that, The S22 midpoints can be selected from M1 to M n subset of the set of sites.

5. The ciliary body based, human eye real focal length universal probing method according to claim 1, wherein, The different layer points P1-P i where i > 1.

6. A ciliary body based in-vivo focal length universal probing method for probing the human eye, characterized by, Comprising: General module: used for obtaining sample OCT light signal set focused on different standard focal length f1~f m under different standard focal length f1~f n under different standard focal length f1~f i under different standard focal length f1~f m "feature point-sample average light reflection coefficient curve" The general module comprises: A first data acquisition unit: configured to obtain a sample OCT light signal set of yx m ciliary body parts of y sample persons about m different focal lengths; a data extraction unit for extracting y x m sample OCT light signals of n ciliary body sites M1~Mn in each of the signal sets of y x m ciliary body sites; n i layer points P1~Pi in each of the sites; i y x m x n x i sample light reflection coefficients; A data mean unit: configured to perform mean value processing on the light reflection coefficients with the same focal point in the obtained yx mx n x i sample light reflection coefficients, to obtain mx n x i sample mean light reflection coefficients; The first normalization unit is used for normalizing the m*n*i sample mean light reflection coefficients to generate m "feature point-sample mean light reflection coefficient relationship curves", wherein the horizontal coordinates of the m "feature point-sample mean light reflection coefficient relationship curves" are feature points P1-Pm, and the vertical coordinates are feature point light reflection coefficient relative ratios. i , the horizontal coordinates of the m "feature point-sample mean light reflection coefficient relationship curves" are feature points P1-Pm, and the vertical coordinates are feature point light reflection coefficient relative ratios. The measured module is used to obtain a set of measured OCT light signals of the ciliary body part of the measured person focusing on any focal length f x The measured OCT light signals in the set are extracted to obtain the measured light reflection coefficients of each different point M1-M n P1-P i of the different layers in the set, and the measured light reflection coefficients are normalized to obtain the "feature point-measured light reflection coefficient curve" at the focal length f x The "feature point-measured light reflection coefficient curve" is fitted with the "feature point-sample mean light reflection coefficient curve" to obtain the value of the measured focal length f x of the current measured person.

7. The ciliary body based human eye real focal length universal probing method's probing device according to claim 6, characterized in that, The data extraction unit comprises: The first calibration subunit is used for calibrating n points M1-Mn on the sagittal plane surface in the ciliary body part. n ; The second calibration subunit is used for sampling the points P1-Pn in the ciliary body tissue region at each of the n sites M1-Mn along the direction of the laser axis. n i ;​ The first analysis subunit is used for traversing the sample OCT light signal set of y x m ciliary body sites, extracting the calibrated M1~Mn sample light reflection coefficient set in each sample OCT light signal set, and calculating the mean value of the sample light reflection coefficient set of each sample OCT light signal set to obtain the mean light reflection coefficient set of each sample OCT light signal set. n The first analysis subunit is used for traversing the sample OCT light signal set of y x m ciliary body sites, extracting the calibrated M1~Mn sample light reflection coefficient set in each sample OCT light signal set, and calculating the mean value of the sample The second analysis subunit is used to extract the different layer points P1~P i of the n×i sample layer points light reflection coefficients.

8. The ciliary body based human eye real focal length universal probing method's probing device according to claim 6, characterized in that, The actual measurement module comprises: Second data acquisition unit: for obtaining the measured OCT light signal set of the ciliary body part of the measured person focusing on any focal length f x ; The third analysis unit is used for extracting each site M1-M n of the n measured site light reflection coefficient set; The fourth analysis unit is used for extracting the different layer points P1~Pn of each site under the calibration of the measured OCT light signal set i The n×i measured layer point light reflection coefficients second normalization unit: for normalizing the measured light reflection coefficients of the i layer points P1-Pi at each of the n ciliary body part sites M1-Mn to generate a "feature point-measured light reflection coefficient relationship curve" in which the curve abscissa is the feature point P1-Pi and the curve ordinate is the feature point light reflection coefficient relative ratio; n second normalization unit: for normalizing the measured light reflection coefficients of the i layer points P1-Pi at each of the n ciliary body part sites M1-Mn to generate a "feature point-measured light reflection coefficient relationship curve" in which the curve abscissa is the feature point P1-Pi and the curve ordinate is the feature point light reflection coefficient relative ratio; i second normalization unit: for normalizing the measured light reflection coefficients of the i layer points P1-Pi at each of the n ciliary body part sites M1-Mn to generate a "feature point-measured light reflection coefficient relationship curve" in which the curve abscissa is the feature point P1-Pi and the curve ordinate is the feature point light reflection coefficient relative ratio; i second normalization unit: for normalizing the measured light reflection coefficients of the i layer points P1-Pi at The output unit: the obtained "feature point-actual light reflection coefficient relationship curve" is respectively fitted with m "feature point-sample mean light reflection coefficient curve", and the focal length corresponding to the curve with the optimal fitting degree in the sample mean curve is selected as the near focal length, to obtain the value of the actual focal length f of the current measured person. x of the value.

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