CN119453912B - A fully automatic multifocal ophthalmic biological parameter measurement system and measurement method - Google Patents
A fully automatic multifocal ophthalmic biological parameter measurement system and measurement method Download PDFInfo
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- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/107—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining the shape or measuring the curvature of the cornea
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Abstract
一种全自动多焦点眼科生物参数测量系统及测量方法，涉及眼科生物参数测量技术，其包括：光纤组件，其包括相互独立设置的测量光路及标尺光路；测量组件，其包括与第一耦合器连接的准直器、多焦点透镜、二向色镜及照明靶环，且二向色镜的反射路径上设有眼球成像模块，多焦点透镜使入射其内的测量光聚焦在眼球各组织结构的不同表面处；延迟线组件，用于改变光程和/或度量光程变化量；控制组件，分别与光纤组件、测量组件及延迟线组件连接；计算机，与所述控制组件连接，依据采集到眼球不同反射面的干涉峰和眼球图像，获取眼科生物参数。采用多焦点透镜，提高了晶体表面和视网膜表面探测信号的强度，易于探测患者眼球各组织界面的信号，具有结构简单、人眼光功率小、装调方便、系统紧凑、精度高等特点。
A fully automatic multi-focal ophthalmic biological parameter measurement system and method, which relates to ophthalmic biological parameter measurement technology, includes: an optical fiber component, which includes a measurement optical path and a scale optical path that are independently set; a measurement component, which includes a collimator connected to a first coupler, a multi-focal lens, a dichroic mirror and an illumination target ring, and an eyeball imaging module is provided on the 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, which is used to change the optical path and/or measure the optical path change; a control component, which is respectively connected to the optical fiber component, the measurement component and the delay line component; a computer, which is connected to the control component, and obtains ophthalmic biological parameters based on the interference peaks and eyeball images collected from different reflection surfaces of the eyeball. The use of a multi-focal lens improves the intensity of the detection signal on the surface of the crystal and the retina, and is easy to detect the signals of the interfaces of various tissues of the patient's eyeball, and has the characteristics of simple structure, low light power of the human eye, convenient installation and adjustment, compact system, high precision, etc.
Description
Technical Field
The invention relates to an ophthalmic biological parameter measurement technology, in particular to a full-automatic multifocal ophthalmic biological parameter measurement system and a full-automatic multifocal ophthalmic biological parameter measurement method.
Background
The ophthalmic biological parameters include an eye axis length, a cornea thickness, an anterior chamber depth, a crystal thickness, a vitreous body thickness, a cornea curvature, a pupil size and the like, wherein the eye axis length refers to a distance from the anterior surface of the cornea to a retinal pigment epithelial cell layer, and the parameters can provide scientific judgment basis for various eye diseases such as ametropia, glaucoma, cataract, strabismus, amblyopia, macular edema and the like. Angle closure glaucoma is thin in the anterior chamber, thick in the lens, thin in the vitreous body and short in the axial length of the eye relative to normal human eyes. Therefore, the accurate measurement of ophthalmic biological parameters is particularly important, and the industrialization prospect is very great.
Currently, the eye axis length measurement method mainly comprises ultrasonic measurement and optical measurement. The traditional eye axis length measurement method mainly adopts ultrasonic measurement, obtains depth information of the eyeball by receiving ultrasonic echo signals of different layer structures of the eyeball, has measurement accuracy of only 100-200 mu m, needs to contact the cornea and the surface of the anesthetized cornea, and is easy to damage and infect the cornea. The optical eye axis measurement is to measure the length of the eye axis by utilizing an optical coherence technology, and has the advantages of non-contact, high precision, simple operation and the like, however, the measurement method generally adopts a common single focus lens, light rays entering the human eye are converged at the cornea, and the light rays are reflected by each tissue interface in the eye to detect low coherence signals, so that the light spot energy at the cornea is concentrated, the light spot energy at the cornea is dispersed more later, for example, the light spot at the crystal and the retina is larger, and the signal intensity detected by the reflection of the crystal surface and the retina surface is relatively weaker.
In order to increase the intensity of the detection signals of the surface of the crystal and the surface of the retina, the existing methods mainly comprise:
1) The optical power entering human eyes is improved, but the risk of human eye safety power is easily increased;
2) As disclosed in chinese patent CN118370512a, US6806963B1 discloses a system and a method for measuring ophthalmic biological parameters, and US6806963B1 discloses a device and a method （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）, for measuring optical characteristics of at least two regions of a transparent and/or diffuse object that are at a distance from each other, wherein both the device and the method are characterized in that light is split into two paths of light by a beam splitter and is converged to anterior and posterior segments of the eye respectively, but the complexity of the system structure is increased, and the two paths of light are required to be equal or compensated;
3) By adopting a double-focus combined lens mode, as disclosed in China patent CN104013383A, a double-focus front and rear eye section synchronous imaging system and an imaging method are adopted, two lenses are nested and combined together in a mechanical mode, and as the light spot entering human eyes is smaller and has the diameter of 1-4mm, the light spot needs to be expanded and contracted, but the complexity of the system structure and the difficulty of system adjustment are increased, and the compactness of the system is not facilitated;
4) A device and method (Method and Apparatus for Determination of Geometric Values on an Object) for measuring the geometry of an object using a time-sharing single channel approach, such as that disclosed in US8049899B2, is provided that alternately focuses on the anterior and posterior segments of the eye during different time periods by alternately changing the elements in the optical path, but the signal acquisition is not synchronized, and both tremor or head micro-movements cause large errors, affecting the measurement accuracy.
5) A Short coherence interferometry device (Short-Coherence Interferometeric Measurement of Length on the Eye) for measuring the length of an eye axis is disclosed in US7695137B2, which adopts a continuous zooming mode, and a motor is used to drive a zooming module to move so as to change the focusing position in the eyeball, so that the system structure is complex.
The methods have the characteristics of high optical power entering human eyes, complex system structure, complex installation and adjustment, non-compact system, low precision and the like.
In view of the above problems, it is necessary to provide a novel full-automatic multi-focus ophthalmic biological parameter measurement system to solve the above problems, improve the strength of detection signals on the surface of the crystal and the surface of the retina, easily detect signals on the interfaces of various tissues of the eyeballs of patients, meet the requirements of medical staff for checking various patients, and have the characteristics of simple structure, small optical power of the eyes, convenient assembly and adjustment, compact system, high precision and the like.
Disclosure of Invention
Aiming at the defects existing in the prior art, the invention aims to provide a full-automatic multifocal ophthalmic biological parameter measurement system and a measurement method.
In order to achieve the above purpose, the present invention provides the following technical solutions:
A fully automatic multifocal ophthalmic biometric parameter measurement system, comprising:
An optical fiber component comprises a measuring light path and a scale light path which are mutually independent,
The measuring light path comprises a measuring light source for providing measuring light, a first coupler for dividing the measuring light into two beams of light, a polarization device for changing the polarization state of the light in the optical fiber and a first detector for receiving the reflected measuring light, wherein one beam of light enters the measuring assembly as signal light for detecting the positions of different reflecting surfaces of the eyeball, the other beam of light enters the delay line assembly as reference light, the positions of the different reflecting surfaces of the eyeball are precisely positioned through scanning, a low coherence interference peak is formed with the signal light,
The optical path of the staff gauge comprises a staff gauge light source for providing staff gauge light, a second coupler for dividing the staff gauge light into two beams of light and a second detector for receiving the reflected staff gauge light, wherein one beam of light enters an optical fiber end surface reflecting mirror, the other beam of light and a reference light of the measuring light source are coupled together and enter a delay line component through a wavelength division multiplexer, the two beams of light form high-coherence interference peaks, and the optical path variation is measured through the number of the interference peaks of the staff gauge light;
The measuring assembly comprises a collimator, a multi-focus lens, a dichroic mirror and an illumination target ring, wherein the collimator is connected with the first coupler, the multi-focus lens is sequentially arranged along a light path, the dichroic mirror is used for splitting beams, the illumination target ring is used for providing an eyeball illumination light source, an eyeball imaging module is arranged on a reflection path of the dichroic mirror, and the multi-focus lens focuses measuring light incident into the multi-focus lens on different surfaces of each tissue structure of an eyeball;
a delay line component connected with the optical fiber component and used for changing the optical path and/or measuring the optical path variation;
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 acquires ophthalmic biological parameters according to the acquired interference peaks and eyeball images of different reflecting surfaces of the eyeballs.
The multi-focus lens is a compound curved lens and is divided into a spot irradiation part inner ring lens and a non-spot irradiation part outer ring lens from inside to outside, wherein the spot irradiation part inner ring lens is formed by splicing a plurality of sub lenses with different focal lengths.
The light spot irradiation part inner ring lens is divided into a plurality of areas, and each area corresponds to one inner ring sub lens.
The light transmission area of each inner ring sub-lens is 0.5-1.5 times of the average light transmission area of all the inner ring sub-lenses.
The focuses of the inner ring sub-lenses are respectively positioned on different surfaces of the cornea, the crystalline lens and the retina, and the energy of the light spots distributed on the retina or the crystalline lens is larger than the energy of the focuses distributed on the cornea.
The sub-lenses are any one of spherical lenses, aspherical lenses, micro-lens array sub-lenses and plano-convex lenses.
The focal length of each sub-lens satisfies:
Wherein the method comprises the steps of For focusing the sub-lens on the focal length of the kth surface of the eyeball, the kth=1 to 5 surfaces are the front surface of the cornea, the rear surface of the cornea, the front surface of the crystalline lens, the rear surface of the crystalline lens and the retina respectively; For the object distance of the i-th plane, ;The curvature radius of the ith surface of the eyeball; And The distance and the refractive index between the ith surface and the (i+1) th surface of the eyeball are respectively,。
The deviation between the center thickness of each sub-lens and the outer ring sub-lens is as followsCompensation in whichFor the refractive index of the sub-lenses in question,Is the center thickness deviation of the sub-lens.
The compound curved lens is formed by a direct integral processing mode, a direct forming mode by a mould or a combination mode of sticking different curvature surface type sheets on a single focus lens.
A measurement method based on the fully automatic multifocal ophthalmic biological parameter measurement system, comprising the following steps:
1, an operator inputs eye information of a photographed person, drives a pupil automatic positioning component according to left and right eyes, and achieves left and right coarse positioning of the pupil through left and right movement of a host;
2 coarse positioning the pupil up and down, namely enabling a photographer to lean against the head on the jaw support, recording pupil images at the moment by the eyeball imaging module, analyzing the pupil offset by a computer, transmitting the obtained pupil offset to the control assembly, and driving the jaw support moving assembly to move up and down by the control assembly so as to realize coarse positioning of the pupil up and down;
3 pupil three-dimensional fine positioning, namely, firstly, determining the position of a signal light spot in an eyeball imaging camera according to software, and analyzing the central point of an exit pupil image in real time through the software, then, analyzing the offset between the central point of the exit pupil and the central point of the signal light spot through the software, so as to calculate the offset;
And 4, data acquisition and analysis, namely acquiring interference peaks of different reflecting surfaces of the eyeball to obtain axial parameters of the eyeball, including the length of the eye axis, the thickness of the cornea, the depth of the anterior chamber and the thickness of the crystal, and respectively controlling a near infrared light source and a visible light source to be sequentially turned on and off by a lighting source control module to obtain the cornea curvature radius, the axial angle, the pupil size and the white-to-white parameters.
The invention has the beneficial effects that the design is ingenious and unique, the strength of detection signals of the crystal surface and the retina surface is improved by adopting the novel multifocal lens, the signals of each tissue interface of the eyeball of a patient are easy to detect, and the invention has the characteristics of simple structure, small optical power of human eyes, convenient assembly and adjustment, compact system, high precision and the like.
Drawings
FIG. 1 is a schematic diagram of the architecture of a fully automated multifocal ophthalmic biometric parameter measurement system of the present invention.
Fig. 2 is a schematic structural view of the multifocal lens of the present invention.
Fig. 3 is a schematic view of the structure of a single sub-lens of the present invention.
Fig. 4 is a schematic structural diagram of three embodiments of four different divisions of a multifocal lens of the present invention.
Fig. 5 is a schematic diagram of a system for multi-focal lens ray tracing according to an embodiment of the invention.
Fig. 6 is a schematic diagram of a six-focal-point lens system according to an embodiment of the present invention.
Fig. 7 is a schematic diagram of a configuration of a five-focus lens according to an embodiment of the present invention.
Fig. 8 is a schematic diagram of a four-focal lens system according to an embodiment of the present invention.
Fig. 9 is a schematic structural view of an embodiment of the trifocal lens of the present invention.
Fig. 10 is a block diagram of the system control assembly and related essential components of the present invention.
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 polarizing device, 15 is a scale light source, 16 is a detector, 17 is a coupler, 18 is a wavelength division multiplexer, 19 is an optical fiber end surface reflecting mirror, 2 is a measuring assembly, 21 is a collimator, 22 is a multifocal lens, 23 is a dichroic mirror, 24 is an illumination target ring, 25 is an eyeball 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 motion control module, 45 is an automatic pupil positioning control module, 6 is a jaw motion assembly, 7 is an automatic pupil positioning assembly, 223 is a sub-lens, 221 is an inner ring lens of a light spot illumination part, 222 is an outer ring lens of a non-light spot illumination part, 2213 is an inner ring sub-lens, 2223 is an outer ring sub-lens.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
It should be noted that all directional indicators (such as up, down, left, right, front, and rear are used in the embodiments of the present invention) are merely for explaining the relative positional relationship, movement conditions, and the like between the components in a certain specific posture (as shown in the drawings), and if the specific posture is changed, the directional indicators are changed accordingly.
As shown in fig. 1, the present invention provides a fully automatic multi-focal ophthalmic bio-parameter measurement system, which includes an optical fiber assembly 1, a measurement assembly 2, a delay line assembly 3, a control assembly 4, and a computer 5.
Wherein the optical fiber component 1 comprises a measuring light path and a scale light path which are mutually independent.
The measuring light 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 polarization 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 assembly as signal light for detecting the positions of different reflecting surfaces of the eyeball, and the other beam of light enters the delay line assembly 3 as reference light, and forms a low-coherence interference peak with the signal light by scanning and precisely positioning the positions of the different reflecting surfaces of the eyeball.
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 an optical fiber end surface reflector 19, the other beam of light is coupled with reference light of the measuring light source together to enter the delay line component 3 through a wavelength division multiplexer 18, the two beams of light form high-coherence interference peaks, and the optical path variation is measured through the number of the interference peaks of the scale light.
The optical fiber assembly 1 is connected with the measuring assembly 2 and the delay line assembly 3 through the first coupler 13 respectively.
The optical fiber end surface reflector 19 is a plane reflector with a certain reflectivity fixed at the optical fiber end surface, the scale light source 15 divides the scale light into two beams of light through the second coupler 17, one beam enters the optical fiber end surface reflector 19, the other beam is optically coupled with the reference light of the measuring light source 11 and enters the delay line component 3, the two beams of light form high coherence interference peaks, the optical path variation is measured through the number of the scale light interference peaks, and the accuracy is higher.
The measuring light source 11 can preferably adopt a near infrared super-radiation light-emitting diode light source, the central wavelength of the measuring light source can be 760-900 nm, and the scale light source 15 can preferably adopt a near infrared high-coherence laser light source.
The measuring component 2 comprises a collimator 21, a multi-focus lens, a dichroic mirror and an illumination target ring, wherein the collimator 21 is connected with the first coupler, the multi-focus lens is used for splitting beams, the illumination target ring is used for providing an eyeball illumination light source, an eyeball imaging module is arranged on the reflecting path of the dichroic mirror, and the multi-focus lens focuses measuring light incident into the multi-focus lens on different surfaces of each organization structure of an eyeball.
The collimator 21 is connected to one end of the first coupler 13. The illumination target ring 24 is an eyeball illumination light source, the eyeball illumination light source comprises a near infrared light source and a visible light source, the near infrared light source is used for pupil illumination, the visible light source is used for iris illumination, preferably, the near infrared light source can adopt 900-1000 nm LEDs, and the visible light can adopt white light or green light. The eyeball illumination light and the signal light are split by the dichroic mirror 23, the dichroic mirror 23 transmits and reflects the signal light and the eyeball illumination light respectively, and the signal light transmittance and the illumination light reflectance are both greater than 0.95. The eyeball imaging module 25 comprises a camera, an imaging objective lens and protective glass, wherein the imaging objective lens can adopt a double-cemented lens or a double-telecentric lens.
The delay line component 3 is connected with the optical fiber component and used for changing the optical path and/or measuring the optical path change quantity, the delay line component 3 can adopt any suitable structure and can comprise a motor, a linear guide rail or a rotary table and a reflecting mirror, the reflecting mirror is positioned on the linear guide rail or the rotary table, the optical path returned by the reference light is changed along with the movement of the guide rail or the rotary table, and meanwhile, the optical path change quantity can be measured through the rotation quantity of the motor.
The control component 4 is respectively connected with the optical fiber component, the measuring component and the delay line component;
And the computer 5 is connected with the control assembly 4 and acquires ophthalmic biological parameters according to the acquired interference peaks and eyeball images of different reflecting surfaces of the eyeball, wherein the axial parameters of the eyeball, including the length of the axis of the eye, the thickness of the cornea, the depth of the anterior chamber and the thickness of the crystal, can be acquired by utilizing the interference peaks of different reflecting surfaces of the eyeball, and the radius of curvature of the cornea, the axial angle, the pupil size and the white-to-white parameters can be acquired by utilizing the eyeball images.
As shown in fig. 2, the multifocal lens 22 is a compound curved lens, the compound curved lens 22 is formed by splicing sub-lenses 223 with a certain central thickness and a certain shape and different focal lengths, and the central thickness refers to the central thickness of the complete lens where the sub-lenses 223 are located, as shown in fig. 3. The lens is divided into a spot irradiation part inner ring lens 221 and a non-spot irradiation part outer ring lens 222 from inside to outside, wherein the spot irradiation part inner ring lens 221 is formed by splicing a plurality of sub lenses 223 with different focal lengths.
The spot irradiation part inner ring lens 221 is divided into a plurality of areas, and each area corresponds to one inner ring sub-lens 2213.
In the four-area dividing method embodiment of the present invention, as shown in fig. 4, the shape may be one or more of a circle, a square, a triangle, an irregular pattern, and the like.
The number of the regions is 2-5, preferably 3, and each region corresponds to one inner ring sub-lens 2213. The light-passing area of each inner ring sub-lens 2213 is 0.5-1.5 times of the average light-passing area of the inner ring sub-lens.
Preferably, the focal points of the inner ring sub-lens 2213 are respectively located at different surfaces of each of the eye tissue structures such as cornea, crystalline lens and retina, so that the signal light is respectively focused at different surfaces of each of the eye tissue structures, and the energy of the light spot distributed on the retina or crystalline lens is preferably larger than the energy of the focal point distributed on the cornea. The non-spot illuminating portion outer ring lens 222 is an outer ring sub-lens 2223 with a focus at any position in the eye, and preferably an outer ring sub-lens 2223 with a focus at the cornea is used. The sub-lenses 223 may be spherical or aspherical lenses, or may be microlens array sub-lenses, and preferably plano-convex lenses may be used.
Referring to fig. 5, the focal length of each sub-lens 223 satisfies:
Wherein the method comprises the steps of For focusing the sub-lens on the focal length of the kth surface of the eyeball, the kth=1 to 5 surfaces are the front surface of the cornea, the rear surface of the cornea, the front surface of the crystalline lens, the rear surface of the crystalline lens and the retina respectively; For the object distance of the i-th plane, ;The curvature radius of the ith surface of the eyeball; And The distance and the refractive index between the ith surface and the (i+1) th surface of the eyeball are respectively,。
The amount of deviation between the center thickness of each sub-lens 223 and the center thickness of the outer ring sub-lens 2223 is in accordance withCompensation in whichFor the refractive index of the sub-lenses 223,Is the amount of center thickness deviation of the sub-lenses 223. Preferably, the center thickness of each of the sub-lenses 223 is equal.
The compound curved lens 22 can be formed by a direct integral processing mode, can be formed by a direct molding mode of a mould, and can also be formed by a mode of sticking different curvature surface type sheets on a single focus lens in a combined mode. Preferably, the rear surface of each sub-lens 223 is the same surface type, and the front surface of each sub-lens 223 is different surface types, so that the rear surface of the compound curved lens 22 is a common curved surface, such as a spherical surface and a plane, and the front surface of the compound curved lens 22 is a compound curved surface formed by combining multiple sections of curved surfaces.
In embodiment 1, please refer to fig. 6, the dividing manner may be a concentric dividing manner, and the dividing manner may be a circular sub-lens, an annular sub-lens, etc. from inside to outside, the sub-lenses may be plano-convex lenses, the compound curved lens may be a six-focal lens, that is, it is composed of six sub-lenses 223, each of the sub-lenses 223 is located at the front surface of cornea, the rear surface of cornea, the front surface of lens, the rear surface of lens, the retina and the front surface of cornea (outer ring sub-lens 2223), and the diameter of the outer circle of the light-transmitting aperture of the six sub-lenses 223 is 0.07D to 0.3D, 0.27D to 0.5D, 0.47D to 0.7D, 0.67D to 0.9D, 1.0D and >1.0D (D is the diameter of light spot).
In embodiment 2, please refer to fig. 7, the dividing manner may be a concentric dividing manner, and the dividing manner may be a circular sub-lens, an annular sub-lens, etc. from inside to outside, the sub-lenses may be plano-convex lenses, the focal length of the outermost inner ring sub-lens 2213 may be the same as that of the outer ring sub-lens 2223, and may be combined into one sub-lens, the compound curved lens may be a five-focus lens, the focal point of each sub-lens 223 from inside to outside is located on the retina, front lens surface, rear lens surface, front cornea surface and rear cornea surface, respectively, and the diameter of the outer circle of the light-transmitting aperture of the sub-lens 223 is 0.07D to 0.3D, 0.27D to 0.5D, 0.47D to 0.7D, 0.67D to 0.9D, and ≡1.0D (D is the diameter of light spot).
In embodiment 3, as shown in fig. 8, the division manner may be a concentric division manner, and the division manner may be a circular sub-lens, an annular sub-lens, etc. from inside to outside, the sub-lenses may be plano-convex lenses, the compound curved lens may be a four-focus lens, the focal point of each sub-lens 223 from inside to outside is located on the front surface of the cornea, the front surface of the lens, the retina and the front surface of the cornea (outer ring sub-lens 2223), and the diameter of the outer circle of the aperture of the sub-lens 223 is 0.17D to 0.5D, 0.3D to 0.77D, 1.0D and >1.0D (D is the diameter of the light spot).
Referring to fig. 9, the division mode may be a concentric division mode, namely, a circular sub-lens, an annular sub-lens and the like from inside to outside, the sub-lenses may be plano-convex lenses, the focal length of the inner ring sub-lens 2213 at the outermost layer may be the same as that of the outer ring sub-lens 2223, and may be combined into one sub-lens, the compound curved lens may be a trifocal lens, the inner focal point of each sub-lens 223 is located at the front surface of retina, lens and front surface of cornea, the diameter of the outer circle of the light-transmitting aperture of each sub-lens 223 is 0.17D-0.5D, 0.3D-0.77D and 1.0D (D is the diameter of the light spot).
The full-automatic multifocal ophthalmic biological parameter measurement system also comprises a jaw motion assembly 6 and a pupil automatic positioning assembly 7. The jaw support moving assembly 6 comprises a one-dimensional moving mechanism and a jaw support, wherein the one-dimensional moving mechanism can adopt a stepping motor sliding block guide rail combination structure capable of moving up and down, the jaw support is positioned on the up-and-down moving mechanism, free movement of the jaw support in the up-and-down direction is realized through the one-dimensional moving mechanism, and preliminary up-and-down positioning of pupils is realized. The automatic pupil positioning assembly 7 is a host three-dimensional movement mechanism, and the host three-dimensional movement mechanism can adopt a stepping motor slide block guide rail combination structure which moves left and right, front and back and up and down, and realizes automatic pupil positioning by moving left and right, front and back and up and down of the host.
The control assembly 4 comprises an image processing module 41, a detector control module 42, an illumination light source control module 43, a jaw movement control module 44 and a pupil automatic positioning control module 45, and the control assembly 4 is connected with the computer 5.
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 illumination light source control module 43 is used for controlling the on and off of the illumination light source, the jaw support movement control module 44 is used for jaw support movement control, and the pupil automatic positioning control module 45 is used for pupil automatic positioning component 7 movement control.
The invention also provides a measuring method based on the full-automatic multifocal ophthalmic biological parameter measuring system, which comprises the following steps:
1, an operator inputs eye information of a photographed person, drives an automatic pupil positioning assembly 7 according to left and right eyes, and achieves left and right rough pupil positioning through left and right movement of a host;
2 coarse positioning the pupil up and down, namely enabling a photographer to lean against the head on the jaw support, recording pupil images at the moment by the eyeball imaging module, analyzing the pupil offset by a computer, transmitting the obtained pupil offset to the control assembly, and driving the jaw support moving assembly 6 to move up and down by the control assembly so as to realize coarse positioning of the pupil up and down;
3 pupil three-dimensional fine positioning, namely, firstly, determining the position of a signal light spot in an eyeball imaging camera according to software, and analyzing the central point of an exit pupil image in real time through the software, then, analyzing the offset between the central point of the exit pupil and the central point of the signal light spot through the software, so as to calculate the offset;
And 4, data acquisition and analysis, namely acquiring interference peaks of different reflecting surfaces of the eyeball to obtain axial parameters of the eyeball, including the length of the eye axis, the thickness of the cornea, the depth of the anterior chamber and the thickness of the crystal, and respectively controlling a near infrared light source and a visible light source to be sequentially turned on and off by a lighting source control module to obtain the cornea curvature radius, the axial angle, the pupil size and the white-to-white parameters.
The examples should not be construed as limiting the invention, but any modifications based on the spirit of the invention should be within the scope of the invention.
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| JPH01254141A (en) * | 1988-04-01 | 1989-10-11 | Canon Inc | Ophthalmoscopic checking equipment |
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| CN101703389A (en) * | 2009-11-03 | 2010-05-12 | 南开大学 | Method for improving focal depth range of optical coherence tomography system |
| CN217902220U (en) * | 2022-09-14 | 2022-11-25 | 深圳迈塔兰斯科技有限公司 | Tomography system based on superlens |
| DE102022133951A1 (en) * | 2022-12-19 | 2024-06-20 | Heidelberg Engineering Gmbh | Device for measuring eye length |
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| JPH01212536A (en) * | 1988-02-19 | 1989-08-25 | Canon Inc | ophthalmological examination equipment |
| CN102727172A (en) * | 2012-06-19 | 2012-10-17 | 天津市索维电子技术有限公司 | System and method for measuring eyeball parameters by using weak coherent technology |
| CN107928624A (en) * | 2017-12-22 | 2018-04-20 | 温州医科大学附属眼视光医院 | A kind of adaptive optics scanning laser eyeground imaging system and its imaging method based on pupil automatic positioning focusing |
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