Full-automatic multi-focus ophthalmic biological parameter measuring system and measuring method

Abstract

The invention discloses a full-automatic multi-focus ophthalmological biological parameter measuring system and method, and relates to the ophthalmological biological parameter measuring technology, and the system comprises an optical fiber assembly which comprises a measuring light path and a scale light path which are independently arranged; the measuring assembly comprises a collimator connected with the first coupler, a multi-focus lens, a dichroscope and an illumination target ring, an eyeball imaging module is arranged on a reflection path of the dichroscope, and the multi-focus lens enables measuring light entering the multi-focus lens to be focused on different surfaces of all tissue structures of the eyeball; the delay line assembly is used for changing the optical path and / or measuring the variable quantity of the optical path; the control assembly is respectively connected with the optical fiber assembly, the measuring assembly and the delay line assembly; and the computer is connected with the control assembly and is used for acquiring ophthalmologic biological parameters according to the acquired interference peaks of different reflecting surfaces of the eyeballs and the eyeball images. The multi-focus lens is adopted, the intensity of crystal surface and retina surface detection signals is improved, signals of tissue interfaces of eyeballs of a patient are easily detected, and the system has the advantages of being simple in structure, small in human eye optical power, convenient to install and adjust, compact, high in precision and the like.

Description

Technical Field

[0001] The present invention relates to an ophthalmic biological parameter measurement technology, and in particular to a full-automatic multi-focal ophthalmic biological parameter measurement system and a measurement method. Background Art

[0002] Ophthalmic biological parameters include axial length, corneal thickness, anterior chamber depth, lens thickness, vitreous thickness, corneal curvature and pupil size. Axial length refers to the distance from the anterior surface of the cornea to the retinal pigment epithelial cell layer. These parameters can provide a scientific basis for the diagnosis of a variety of eye diseases such as refractive error, glaucoma, cataract, strabismus, amblyopia and macular edema. The problem of refractive error in the eyes of Chinese teenagers is becoming increasingly serious, with axial myopia accounting for the vast majority, and myopia is positively correlated with axial length growth. Compared with normal human eyes, angle-closure glaucoma has a thin anterior chamber, thick lens, thin vitreous body and a shorter axial length. Therefore, accurate measurement of ophthalmic biological parameters is particularly important, and its industrialization prospects are very huge.

[0003] At present, the main methods for measuring axial length are ultrasonic measurement and optical measurement. The traditional method for measuring axial length mainly uses ultrasonic measurement, which receives ultrasonic echo signals from different layers of the eyeball structure to obtain the depth information of the eyeball. The measurement accuracy is only 100μm to 200μm, and it is necessary to contact the cornea and anesthetize the corneal surface, and it is easy to damage and infect the cornea. Optical axial length measurement uses optical coherence technology to measure axial length, which has the advantages of non-contact, high accuracy, and simple operation. However, this measurement method usually uses an ordinary single-focus lens to converge the light entering the human eye at the cornea, and detect its low-coherence signal through reflection at the interface of various tissues in the eye. At this time, the energy of the light spot at the cornea is relatively concentrated, and the energy is more divergent as it is further back. For example, the light spot at the lens and retina is relatively large, which will cause the signal intensity detected by the reflection on the surface of the lens and the retina to be relatively weak.

[0004] In order to improve the intensity of the detection signal on the lens surface and retinal surface, the existing methods mainly include: 1) Increasing the optical power entering the human eye, but it is easy to increase the risk of human eye safety power; 2) Using a dual optical path channel method, such as Chinese patent CN118370512A discloses an ophthalmic biological parameter measurement system and method, and U.S. Patent US6806963B1 discloses a method and device for measuring the optical properties of at least two regions located at a distance from one another in a transparent and / or diffuse object. Both methods use a beam splitter to split the light into two paths, which converge to the anterior segment of the eye and the posterior segment of the eye respectively. However, this increases the complexity of the system structure and requires that the two optical paths be equal or compensated. 3) Using a dual-focus combined lens method, such as Chinese patent CN104013383A discloses a dual-focus anterior and posterior segment synchronous imaging system and imaging method, which mechanically nests two lenses together. Since the light spot entering the human eye is small, with a diameter of 1-4 mm, the light spot needs to be expanded and then contracted, which increases the complexity of the system structure and the difficulty of system adjustment, which is not conducive to the compactness of the system; 4) Using a time-sharing single-channel method, such as U.S. Patent US8049899B2, which discloses a device and method for measuring the geometric values ​​of an object (Method and Apparatus for Determination of Geometric Values ​​on an Object), which alternately changes the elements in the optical path so that the anterior and posterior segments of the eye are alternately focused at different time periods. However, the signal collection is not synchronized, and eye tremors or slight movements of the head will cause large errors, affecting the measurement accuracy.

[0005] 5) Using a continuous zoom method, such as U.S. Patent US7695137B2 discloses a short-coherence interferometer measurement device for measuring the axial length of the eye (Short-Coherence Interferometeric Measurement of Length on the Eye), which drives the zoom module to move by a motor to change the focal position in the eyeball, and its system structure is complex.

[0006] These methods have the characteristics of high optical power entering the human eye, complex system structure, complex installation and adjustment, non-compact system and low accuracy.

[0007] In view of the above problems, it is necessary to provide a new type of fully automatic multifocal ophthalmic biological parameter measurement system to solve the above problems, improve the intensity of the detection signal on the lens surface and the retinal surface, facilitate the detection of signals at the interfaces of various tissues of the patient's eye, meet the needs of medical personnel to examine various patients, and have the characteristics of simple structure, low human eye light power, easy installation and adjustment, compact system, and high precision. Summary of the invention

[0008] In view of the deficiencies in the prior art, the object of the present invention is to provide a fully automatic multifocal ophthalmic biological parameter measurement system and a measurement method.

[0009] To achieve the above object, the present invention provides the following technical solutions: A fully automatic multifocal ophthalmic biological parameter measurement system, comprising: The optical fiber assembly includes a measuring optical path and a scale optical path which are independently arranged. The measuring optical path includes a measuring light source for providing measuring light, a first coupler for dividing the measuring light into two beams of light, a polarizing device for changing the polarization state of light in the optical fiber, and a first detector for receiving the reflected measuring light, wherein one beam of light enters the measuring component as a signal light for detecting the positions of different reflection surfaces of the eyeball, and the other beam of light enters the delay line component as a reference light for accurately locating the positions of different reflection surfaces of the eyeball through scanning, and forms a low-coherence interference peak with the signal light. The scale light path includes a scale light source for providing scale light, a second coupler for dividing the scale light into two beams of light, and a second detector for receiving the reflected scale light, wherein one beam of light enters the optical fiber end face reflector, and the other beam of light is coupled with the reference light of the measurement light source and enters the delay line component via a wavelength division multiplexer, and the two beams of light form a high coherence interference peak, and the optical path change is measured by the number of the scale light interference peaks; A measuring assembly, comprising a collimator connected to a first coupler, a multi-focal lens, a dichroic mirror for beam splitting, and an illumination target ring for providing an eyeball illumination light source, which are sequentially arranged along an optical path, and an eyeball imaging module is arranged on a reflection path of the dichroic mirror, and the multi-focal lens focuses the measurement light incident therein on different surfaces of various tissue structures of the eyeball; A delay line component, connected to the optical fiber component, used to change the optical path and / or measure the change in the optical path; A control component is connected with the optical fiber component, the measuring component and the delay line component respectively; The computer is connected with the control component and acquires ophthalmic biological parameters according to the interference peaks of different reflection surfaces of the eyeball and the eyeball image collected.

[0010] The multi-focal lens is a composite curved lens, which is divided into an inner ring lens of the spot irradiation part and an outer ring lens of the non-spot irradiation part from the inside to the outside, wherein the inner ring lens of the spot irradiation part is composed of a plurality of sub-lenses with different focal lengths.

[0011] The inner circle lens of the light spot irradiation part is divided into a plurality of areas, and each area corresponds to an inner circle lens.

[0012] The light transmission area of ​​each inner circle lens is 0.5 to 1.5 times the average light transmission area of ​​all inner circle lenses.

[0013] The focal points of the inner circle lens are located at different surfaces of the cornea, lens and retina respectively, and the light spot energy distributed on the retina or lens is greater than the focal point energy distributed on the cornea.

[0014] The sub-lens is any one of a spherical lens, an aspherical lens, a microlens array sub-lens and a plano-convex lens.

[0015] The focal length of each sub-lens satisfies:

[0016] in The sub-lens focuses on the eyeball k The focal length of the surface, k =1~5 surfaces are the anterior surface of the cornea, the posterior surface of the cornea, the anterior surface of the lens, the posterior surface of the lens and the retina; For the i The object distance of the surface, ; For the eye i The radius of curvature of the surface; and Eyeball i Surface and i +1 The distance between the surfaces and the refractive index, .

[0017] The deviation between the thickness of each sub-lens and the center thickness of the outer ring lens is calculated according to Compensation, including is the refractive index of the sub-lens, is the sub-lens center thickness deviation.

[0018] The composite curved lens is formed by direct integral processing, direct mold forming, or by combining thin sheets with different curvatures pasted on a single-focus lens.

[0019] A measurement method based on the fully automatic multifocal ophthalmic biological parameter measurement system comprises the following steps: 1 The operator inputs the subject's eye information, drives the pupil automatic positioning component according to the left and right eyes, and moves the host left and right to achieve rough left and right pupil positioning; 2. Rough positioning of pupil: The subject rests his head on the chin rest, and the eye imaging module records the pupil image at this time. The computer analyzes the pupil offset and transmits the obtained pupil offset to the control component. The control component drives the chin rest motion component to move up and down, thereby achieving rough positioning of pupil; 3. Detailed three-dimensional positioning of pupil: First, the position of the signal light spot in the eye imaging camera is calibrated in the software, and the center point of the pupil image is analyzed in real time by the software; then, the offset between the center point of the pupil and the center point of the signal light spot is analyzed by the software, so that the offset can be calculated; finally, the three-dimensional motion mechanism of the host is driven to move according to the offset, and the pupil is adjusted to the correct position, thereby realizing real-time and precise positioning of the pupil; 4. Data collection and analysis: By collecting the interference peaks of different reflective surfaces of the eyeball, the axial parameters of the eyeball are obtained, including the axial length, corneal thickness, anterior chamber depth, and lens thickness. The near-infrared light source and visible light source are controlled to be turned on and off in sequence through the lighting source control module to obtain the corneal curvature radius, axial angle, pupil size, and white-to-white parameters.

[0020] The beneficial effects of the present invention are as follows: the design is ingenious and unique, and a new multi-focal lens is used to improve the intensity of detection signals on the surface of the crystal and the retina, making it easy to detect signals at the interfaces of various tissues of the patient's eyeball, and it has the characteristics of simple structure, low optical power of the human eye, convenient installation and adjustment, compact system, and high precision. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] Figure 1 It is a structural schematic diagram of the fully automatic multifocal ophthalmic biological parameter measurement system of the present invention.

[0022] Figure 2 It is a schematic structural diagram of the multifocal lens of the present invention.

[0023] Figure 3 It is a schematic diagram of the structure of a single sub-lens of the present invention.

[0024] Figure 4 It is a schematic structural diagram of three specific embodiments of the multifocal lens of the present invention in which four regions are divided in different ways.

[0025] Figure 5 It is a structural schematic diagram of a specific embodiment of the multi-focal lens ray tracing of the system of the present invention.

[0026] Figure 6 It is a schematic structural diagram of a specific embodiment of the six-focus lens of the system of the present invention.

[0027] Figure 7It is a schematic structural diagram of a specific embodiment of the five-focus lens of the system of the present invention.

[0028] Figure 8 It is a schematic structural diagram of a specific embodiment of the system four-focus lens of the present invention.

[0029] Fig. 9 It is a schematic structural diagram of a specific embodiment of the trifocal lens of the system of the present invention.

[0030] Fig.10 It is a block diagram of the system control assembly and related important components of the present invention.

[0031] In the figure, 1 is an optical fiber assembly, 11 is a measuring light source, 12 is a detector, 13 is a coupler, 14 is a polarizer, 15 is a scale light source, 16 is a detector, 17 is a coupler, 18 is a wavelength division multiplexer, and 19 is an optical fiber end face reflector; 2 is a measuring assembly, 21 is a collimator, 22 is a multi-focus lens, 23 is a dichroic mirror, 24 is an illumination target ring, and 25 is an eye imaging module; 3 is a delay line assembly; 4 is a control assembly; 5 is a computer, 41 is an image processing module, 42 is a detector control module, 43 is an illumination light source control module, 44 is a jaw rest movement control module, 45 is an automatic pupil positioning control module, 6 is a jaw rest movement assembly, 7 is an automatic pupil positioning assembly, 223 is a sub-lens, 221 is an inner ring lens of the spot irradiation part, 222 is an outer ring lens of the non-spot irradiation part, 2213 is an inner ring lens, and 2223 is an outer ring lens. DETAILED DESCRIPTION

[0032] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0033] It should be noted that all directional indications in the embodiments of the present invention (such as up, down, left, right, front, back, etc.) are only used to explain the relative position relationship, movement status, etc. between the components under a certain specific posture (as shown in the accompanying drawings). If the specific posture changes, the directional indication will also change accordingly.

[0034] like Figure 1 As shown, the present invention provides a fully automatic multifocal ophthalmic biological parameter measurement system, which includes an optical fiber component 1, a measurement component 2, a delay line component 3, a control component 4 and a computer 5.

[0035] The optical fiber assembly 1 includes a measuring optical path and a scale optical path which are independently arranged.

[0036] The measuring optical path includes a measuring light source 11 for providing measuring light, a first coupler 13 for dividing the measuring light into two beams of light, a polarizing device 14 for changing the polarization state of light in the optical fiber, and a first detector 12 for receiving the reflected measuring light, wherein one beam of light enters the measuring component as a signal light for detecting the positions of different reflective surfaces of the eyeball, and the other beam of light enters the delay line component 3 as a reference light, which accurately locates the positions of different reflective surfaces of the eyeball by scanning, and forms a low coherence interference peak with the signal light.

[0037] The scale optical path includes a scale light source 15 for providing scale light, a second coupler 17 for dividing the scale light into two beams of light, and a second detector 16 for receiving the reflected scale light, wherein one beam of light enters the optical fiber end face reflector 19, and the other beam of light is coupled with the reference light of the measurement light source and enters the delay line component 3 via the wavelength division multiplexer 18, and the two beams of light form a high coherence interference peak, and the optical path change is measured by the number of the scale light interference peaks.

[0038] The optical fiber component 1 is connected to the measurement component 2 and the delay line component 3 respectively through the first coupler 13 .

[0039] The fiber end reflector 19 refers to a plane reflector with a certain reflectivity fixed at the end face of the optical fiber. The scale light source 15 divides the scale light into two beams of light through the second coupler 17. One beam enters the fiber end reflector 19, and the other beam is coupled with the reference light of the measurement light source 11 and enters the delay line component 3. The two beams of light form a high-coherence interference peak. The optical path change is measured by the number of scale light interference peaks, with higher accuracy.

[0040] The measuring light source 11 may preferably be a near-infrared superluminescent diode light source, the central wavelength of which may be 760-900 nm, and the scale light source 15 may preferably be a near-infrared high-coherence laser light source.

[0041] The measuring component 2 comprises a collimator 21 connected to a first coupler, a multi-focal lens, a dichroic mirror for beam splitting and an illumination target ring for providing an eyeball illumination light source, which are sequentially arranged along the optical path, and an eyeball imaging module is arranged on the reflection path of the dichroic mirror. The multi-focal lens focuses the measurement light incident therein on different surfaces of various tissue structures of the eyeball.

[0042] The collimator 21 is connected to one end of the first coupler 13. The illumination target ring 24 is an eyeball illumination light source, and the eyeball illumination light source includes a near-infrared light source and a visible light source. The near-infrared light source is used for pupil illumination, and the visible light source is used for iris illumination. Preferably, the near-infrared light source can use a 900-1000nm LED, and the visible light can use white light or green light. The eyeball illumination light and the signal light are beam-split by the dichroic mirror 23, and the dichroic mirror 23 transmits and reflects the signal light and the eyeball illumination light respectively, and its signal light transmittance and illumination light reflectance are both greater than 0.95. The eyeball imaging module 25 includes a camera, an imaging objective lens and a protective glass, and the imaging objective lens can use a double-cemented lens or a double telecentric lens.

[0043] The delay line component 3 is connected to the optical fiber component and is used to change the optical path and / or measure the change in the optical path; the delay line component 3 can adopt any suitable structure, and may include a motor, a linear guide or a turntable, and a reflector. The reflector is located on the linear guide or the turntable, and changes the optical path of the reference light return as the guide or the turntable moves. At the same time, the change in the optical path can also be measured by the rotation amount of the motor.

[0044] A control component 4 is connected to the optical fiber component, the measuring component and the delay line component respectively; The computer 5 is connected to the control component 4, and acquires ophthalmic biological parameters based on the interference peaks of different reflective surfaces of the eyeball and the eyeball image. The interference peaks of different reflective surfaces of the eyeball can be used to acquire the axial parameters of the eyeball, including axial length, corneal thickness, anterior chamber depth, and lens thickness. The corneal curvature radius, axial angle, pupil size, and white-to-white parameters can be acquired using the eyeball image.

[0045] like Figure 2 As shown, the multifocal lens 22 is a composite curved lens, which is composed of sub-lenses 223 with different focal lengths and certain shapes with a certain center thickness. The center thickness refers to the center thickness of the complete lens where the sub-lenses 223 are located. Figure 3 It is divided from the inside to the outside into an inner ring lens 221 of the spot irradiation part and an outer ring lens 222 of the non-spot irradiation part, wherein the inner ring lens 221 of the spot irradiation part is composed of a plurality of sub-lenses 223 with different focal lengths.

[0046] The light spot irradiation portion of the inner circle lens 221 is divided into a plurality of regions, and each region corresponds to an inner circle lens 2213 .

[0047] The inner lens 221 of the light spot irradiation part is divided into a plurality of regions according to a certain division method, and the division method can be divided according to a certain area and a certain shape; in the specific embodiment of the four-region division method of the present invention, as Figure 4 As shown, the shape may be one or more of a circle, a square, a triangle or an irregular shape.

[0048] The area has 2 to 5 areas, preferably 3 areas, and each area corresponds to an inner circle lens 2213. The light transmission area of ​​each inner circle lens 2213 is 0.5 to 1.5 times the average light transmission area of ​​the inner circle lens.

[0049] Preferably, the focal points of the inner circle lens 2213 are located at different surfaces of various eyeball tissue structures such as the cornea, lens and retina, so that the signal light is focused on different surfaces of various eyeball tissue structures, and the light spot energy distributed on the retina or lens is preferably greater than the focus energy distributed on the cornea. The outer circle lens 222 of the non-light spot irradiation part is an outer circle lens 2223 with a focus located at any position in the eye, preferably an outer circle lens 2223 with a focus located at the cornea. The sub-lens 223 can be a spherical lens or an aspherical lens, or a microlens array sub-lens, preferably a plano-convex lens.

[0050] See also Figure 5 , the focal length of each sub-lens 223 satisfies:

[0051] in The sub-lens focuses on the eyeball k The focal length of the surface, k =1~5 surfaces are the anterior surface of the cornea, the posterior surface of the cornea, the anterior surface of the lens, the posterior surface of the lens and the retina; For the i The object distance of the surface, ; For the eye i The radius of curvature of the surface; and Eyeball i Surface and i +1 The distance between the surfaces and the refractive index, .

[0052] The deviation between the center thickness of each sub-lens 223 and the center thickness of the outer ring lens 2222 is calculated according to Compensation, including is the refractive index of the sub-lens 223, is the central thickness deviation of the sub-lens 223. Preferably, the central thickness of each sub-lens 223 is equal.

[0053] The composite curved lens 22 can be formed by direct integral processing, by direct mold forming, or by pasting thin sheets with different curvatures on a single-focus lens. In a preferred solution, the rear surface of each sub-lens 223 is of the same surface type, and the front surface of each sub-lens 223 is of a different surface type. The rear surface of the composite curved lens 22 is a common curved surface, such as a spherical surface or a plane, and the front surface of the composite curved lens 22 is a composite curved surface composed of multiple curved surfaces.

[0054] Example 1, see Figure 6 As shown, the division method can be a concentric circle division method, from the inside to the outside, there are circular sub-lenses, annular sub-lenses, etc.; the sub-lenses can be plano-convex lenses; the compound curved surface lens can be a six-focus lens, that is, composed of six sub-lenses 223; each of the sub-lenses 223 has focal points located from the inside to the outside on the anterior surface of the cornea, the posterior surface of the cornea, the anterior surface of the lens, the posterior surface of the lens, the retina and the anterior surface of the cornea (outer circle lens 2223), and the outer diameters of the six sub-lenses 223 are 0.07 D ~0.3 D , 0.27 D ~0.5 D , 0.47 D ~0.7 D , 0.67 D ~0.9 D , 1.0 D and>1.0 D ( D is the spot diameter).

[0055] Example 2, see Figure 7 As shown, the division method can be a concentric circle division method, from the inside to the outside, there are circular sub-lenses, annular sub-lenses, etc.; the sub-lenses can be plano-convex lenses; the focal length of the outermost inner circle lens 2213 can be the same as that of the outer circle lens 2223, and can be combined into one sub-lens, and the composite curved lens can be a five-focus lens; the focal points of each sub-lens 223 from the inside to the outside are respectively located on the retina, the anterior surface of the lens, the posterior surface of the lens, the anterior surface of the cornea and the posterior surface of the cornea, and the outer diameters of the light-clearance apertures of the sub-lenses 223 are 0.07 D ~0.3 D , 0.27 D ~0.5 D , 0.47 D ~0.7 D , 0.67D ~0.9 D and ≥1.0 D ( D is the spot diameter).

[0056] Example 3, see Figure 8 As shown, the division method can be a concentric circle division method, from the inside to the outside, there are circular sub-lenses, annular sub-lenses, etc.; the sub-lenses can be plano-convex lenses; the compound curved lens can be a four-focus lens; each sub-lens 223 has focal points located on the front surface of the cornea, the front surface of the lens, the retina and the front surface of the cornea from the inside to the outside (outer circle lens 2223), and the outer diameter of the light aperture of the sub-lens 223 is 0.17 D ~0.5 D , 0.3 D ~0.77 D , 1.0 D and>1.0 D ( D is the spot diameter).

[0057] The best solution is Fig. 9 The division method can be a concentric circle division method, from the inside to the outside, there are circular sub-lenses, annular sub-lenses, etc.; the sub-lenses can be plano-convex lenses; the focal length of the outermost inner circle lens 2213 can be the same as that of the outer circle lens 2223, and can be combined into one sub-lens, and the composite curved lens can be a trifocal lens; the focal points of each sub-lens 223 from the inside to the outside are respectively located on the retina, the front surface of the lens and the front surface of the cornea, and the outer diameters of the light-clearance apertures of the sub-lenses 223 are 0.17 D ~0.5 D , 0.3 D ~0.77 D and ≥1.0 D ( D is the spot diameter).

[0058] The fully automatic multifocal ophthalmic bio-parameter measurement system also includes a jaw rest motion component 6 and an automatic pupil positioning component 7. The jaw rest motion component 6 includes a one-dimensional motion mechanism and a jaw rest. The one-dimensional motion mechanism can adopt a stepper motor slider rail combination structure that moves up and down. The jaw rest is located on the up and down motion mechanism. The one-dimensional motion mechanism enables the jaw rest to move freely up and down to achieve preliminary up and down positioning of the pupil. The automatic pupil positioning component 7 is a three-dimensional motion mechanism of the host. The three-dimensional motion mechanism of the host can adopt a stepper motor slider rail combination structure that moves left and right, front and back, and up and down. The automatic pupil positioning is achieved by moving the host left and right, front and back, and up and down.

[0059] The control component 4 includes an image processing module 41 , a detector control module 42 , an illumination source control module 43 , a jaw support movement control module 44 and an automatic pupil positioning control module 45 . The control component 4 is connected to the computer 5 .

[0060] The image processing module 41 is used for eyeball image processing, the detector control module 42 is used for signal processing received by the detector, the lighting source control module 43 is used to control the on and off of the lighting source, the jaw rest movement control module 44 is used for jaw rest movement control, and the pupil automatic positioning control module 45 is used for movement control of the pupil automatic positioning component 7.

[0061] The present invention also provides a measurement method based on the fully automatic multifocal ophthalmic biological parameter measurement system, which comprises the following steps: 1 The operator inputs the eye information of the subject, and according to the left and right eyes, the pupil automatic positioning component 7 is driven to move the host left and right to achieve the rough positioning of the pupil left and right; 2. Rough positioning of pupil: The subject puts his head on the chin rest, and the eyeball imaging module records the pupil image at this time. The computer analyzes the pupil offset and transmits the obtained pupil offset to the control component. The control component drives the chin rest motion component 6 to move up and down, thereby achieving rough positioning of pupil; 3. Detailed three-dimensional positioning of pupil: First, the position of the signal light spot in the eye imaging camera is calibrated in the software, and the center point of the pupil image is analyzed in real time by the software; then, the offset between the center point of the pupil and the center point of the signal light spot is analyzed by the software, so that the offset can be calculated; finally, the three-dimensional motion mechanism of the host is driven to move according to the offset, and the pupil is adjusted to the correct position, thereby realizing real-time and precise positioning of the pupil; 4. Data collection and analysis: By collecting the interference peaks of different reflective surfaces of the eyeball, the axial parameters of the eyeball are obtained, including the axial length, corneal thickness, anterior chamber depth, and lens thickness. The near-infrared light source and visible light source are controlled to be turned on and off in sequence through the lighting source control module to obtain the corneal curvature radius, axial angle, pupil size, and white-to-white parameters.

[0062] The embodiments should not be regarded as limiting the present invention, but any improvements made based on the spirit of the present invention should be within the protection scope of the present invention.

Claims

1. A fully automatic multifocal ophthalmic biological parameter measurement system, characterized in that: It includes: An optical fiber assembly (1) comprises a measuring optical path and a scale optical path which are independently arranged. The measuring optical path comprises a measuring light source (11) for providing measuring light, a first coupler (13) for dividing the measuring light into two beams of light, a polarizing device (14) for changing the polarization state of light in the optical fiber, and a first detector (12) for receiving the reflected measuring light, wherein one beam of light enters the measuring component as signal light for detecting the positions of different reflection surfaces of the eyeball, and the other beam of light enters the delay line component (3) as reference light for accurately locating the positions of different reflection surfaces of the eyeball through scanning, thereby forming a low-coherence interference peak with the signal light. The scale light path comprises a scale light source (15) for providing scale light, a second coupler (17) for dividing the scale light into two beams of light, and a second detector (16) for receiving the reflected scale light, wherein one beam of light enters the optical fiber end face reflector (19), and the other beam of light is coupled with the reference light of the measurement light source and enters the delay line component (3) via a wavelength division multiplexer (18), the two beams of light form a high coherence interference peak, and the optical path change is measured by the number of the scale light interference peaks; A measuring assembly (2), comprising a collimator (21) connected to a first coupler, a multi-focal lens (22), a dichroic mirror (23) for beam splitting, and an illumination target ring (24) for providing an eyeball illumination light source, which are sequentially arranged along an optical path, and an eyeball imaging module (25) is arranged on a reflection path of the dichroic mirror (23), and the multi-focal lens (22) focuses the measurement light incident therein onto different surfaces of various tissue structures of the eyeball; A delay line component (3), connected to the optical fiber component, used to change the optical path and / or measure the amount of change in the optical path; A control component (4) connected to the optical fiber component, the measuring component and the delay line component respectively; The computer (5) is connected to the control component (4) and acquires ophthalmic biological parameters based on the collected interference peaks of different reflective surfaces of the eyeball and the eyeball image.

2. The fully automatic multifocal ophthalmic biological parameter measurement system according to claim 1, characterized in that: The multi-focal lens (22) is a composite curved lens, which is divided from the inside to the outside into an inner ring lens (221) of a spot illumination part and an outer ring lens (222) of a non-spot illumination part, wherein the inner ring lens (221) of the spot illumination part is composed of a plurality of sub-lenses (223) of different focal lengths spliced ​​together.

3. The fully automatic multifocal ophthalmic biological parameter measurement system according to claim 2, characterized in that: The inner circle lens (221) of the light spot irradiation portion is divided into a plurality of regions, and each region corresponds to an inner circle lens (2213).

4. The fully automatic multifocal ophthalmic biological parameter measurement system according to claim 3, characterized in that: The light transmission area of ​​each inner circle lens (2213) is 0.5 to 1.5 times the average light transmission area of ​​all inner circle lenses.

5. The fully automatic multifocal ophthalmic biological parameter measurement system according to claim 3, characterized in that: The focal points of the inner circle lens (2213) are located on different surfaces of the cornea, the lens and the retina, respectively, and the light spot energy distributed on the retina or the lens is greater than the focal point energy distributed on the cornea.

6. The fully automatic multifocal ophthalmic biological parameter measurement system according to claim 3, characterized in that: The sub-lens (223) is any one of a spherical lens, an aspherical lens, a microlens array sub-lens and a plano-convex lens.

7. A fully automatic multifocal ophthalmic biological parameter measurement system according to any one of claims 2 to 6, characterized in that: The focal length of each sub-lens (223) satisfies: in The sub-lens focuses on the eyeball k The focal length of the surface, k =1~5 surfaces are the anterior surface of the cornea, the posterior surface of the cornea, the anterior surface of the lens, the posterior surface of the lens and the retina; For the i The object distance of the surface, ; For the eye i The radius of curvature of the surface; and Eyeball i Surface and i +1 The distance between the surfaces and the refractive index, .

8. A fully automatic multifocal ophthalmic biological parameter measurement system according to any one of claims 2 to 6, characterized in that: The deviation between the center thickness of each sub-lens (223) and the outer ring lens (2223) is calculated according to Compensation, including is the refractive index of the sub-lens (223), is the central thickness deviation of the sub-lens (223).

9. A fully automatic multifocal ophthalmic biological parameter measurement system according to any one of claims 2 to 6, characterized in that: The composite curved lens is formed by direct integral processing, direct mold forming, or by combining thin sheets with different curvatures pasted on a single-focus lens.

10. A measurement method based on the fully automatic multifocal ophthalmic biological parameter measurement system according to any one of claims 1 to 9, characterized in that: It includes the following steps: 1) The operator inputs the subject's eye information, and according to the left and right eyes, the pupil automatic positioning component (7) is driven, and the host moves left and right to achieve rough left and right positioning of the pupil; 2) Rough positioning of the pupil: The subject rests his head on the chin rest, and the eye imaging module records the pupil image at this time. The computer analyzes the pupil offset and transmits the obtained pupil offset to the control component. The control component drives the chin rest motion component (6) to move up and down, thereby achieving rough positioning of the pupil; 3) 3D pupil positioning: First, the position of the signal light spot in the eye imaging camera is calibrated in the software, and the center point of the pupil image is analyzed in real time by the software; then, the offset between the center point of the pupil and the center point of the signal light spot is analyzed by the software, so that the offset can be calculated; finally, the host 3D motion mechanism is driven to move according to the offset, and the pupil is adjusted to the correct position, thereby realizing real-time and accurate pupil positioning; 4) Data collection and analysis: By collecting the interference peaks of different reflective surfaces of the eyeball, the axial parameters of the eyeball are obtained, including axial length, corneal thickness, anterior chamber depth, and lens thickness. The near-infrared light source and visible light source are controlled to be turned on and off in sequence through the lighting source control module to obtain the corneal curvature radius, axial angle, pupil size, and white-to-white parameters.

Images