CN119666087A - All-in-one eyeball comprehensive parameter measuring instrument and method for measuring eyeball parameters using the same - Google Patents
All-in-one eyeball comprehensive parameter measuring instrument and method for measuring eyeball parameters using the same Download PDFInfo
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Abstract
本发明公开了一种多合一眼球综合参数测量仪及利用其测量眼球参数的方法，该测量仪包括信号光源、信号光源样品臂、信号光源参考臂、标尺光源、标尺光源样品臂、标尺光源参考臂、环形光源、远心镜头、变焦镜组等器件，该仪器能同时实现对人眼生物参数信息，角膜曲率以及眼球屈光度进行测量。本发明设计和科学合理，具有能够在非接触、无创的条件下一次性同时测量人眼的曲率、屈光度和生物学参数的优点。
The present invention discloses an all-in-one eyeball comprehensive parameter measuring instrument and a method for measuring eyeball parameters using the same. The measuring instrument includes a signal light source, a signal light source sample arm, a signal light source reference arm, a scale light source, a scale light source sample arm, a scale light source reference arm, a ring light source, a telecentric lens, a zoom lens group and other devices. The instrument can simultaneously measure the biological parameter information of the human eye, the corneal curvature and the diopter of the eyeball. The present invention is scientifically and reasonably designed, and has the advantages of being able to simultaneously measure the curvature, diopter and biological parameters of the human eye at one time under non-contact and non-invasive conditions.
Description
Technical Field
The application relates to the technical field of optical measurement, in particular to an all-in-one eyeball comprehensive parameter measuring instrument and a method for measuring eyeball parameters by using the same.
Background
Along with the development of ophthalmic technology, the technology for preventing and treating eye diseases is well expanded, such as myopia correction by laser operation, cataract extraction combined with intraocular lens implantation operation for cataract treatment, and cornea refractive operation for near-far vision, astigmatism and the like. Biometric technology of the eyeball is also receiving increasing attention from a vast number of clinicians.
The biological measurement of the eyeball is to measure the structural parameters of the eyeball, such as cornea thickness, anterior chamber depth, lens thickness, vitreous cavity length, axial length of the eyeball and the like by using various related examination methods, including the detection of cornea curvature and eyeball diopter, and provides basis for the diagnosis and treatment of eye diseases. How to obtain accurate parameters of each component of the eyeball is always the direction of research, and any small error can lead the perfect operation not to obtain ideal effects.
The biological measuring instrument of the eyeball length commonly used at present is ultrasonic measurement, such as A ultrasonic, and the principle is that emitted ultrasonic waves are reflected at the interface of each tissue through human eyes, and the position information of each tissue is determined by utilizing the amplitude of echo pulse.
The traditional ultrasonic A ultrasonic measurement has the problems of contact cornea (cross infection), uncertain alignment (affected by the manipulation of operators), pressing of the anterior chamber, low precision on specific eyes (high myopia, posterior scleral grape swelling and deformation of the posterior wall of the eyeball) and the like in the measurement time sequence.
Clinically, the eye vision inspection is commonly used as an optometry instrument, and the diopter of eyes can be inspected, but the optometry instrument cannot prevent myopia, and has limited myopia prevention and control for teenagers. With the development of medicine, researchers find that tracking changes in ocular axis length and cornea curvature ratio and diopter compensation can make a degree of risk prediction for teenager myopia, and measurement equipment of these biological parameters has become a research hotspot and development trend in the field.
In recent years, a measuring instrument that applies OCT technology to biological eyeball parameter information has appeared. Compared with the traditional ultrasonic A ultrasonic, the instrument adopting the optical interference technology has the advantages of non-contact measurement, high measurement precision (10 um, ultrasonic 100 um), automatic alignment and the like, if the partial coherence interference technology (Partial Coherence Interferometer, PCI) and the weak coherence reflection technology (Low Coherence Reflectometry, LCR) are adopted. However, the functions of the measuring instrument are often single, and with the maturation of optical measurement technology, the technical innovation needs to integrate more technologies, the functions are more fully integrated, and the intelligent and automatic equipment provides the development direction. The comprehensive system capable of measuring various eyeball parameters has the advantages of complete functions, compact structure and precise measurement, however, the multifunctional eyeball parameter measurement system has higher requirements on design and use, the integration of the multifunctional modules needs to consider fusion compatibility of more technologies, and meanwhile, the calibration maintenance of the equipment is more complicated and time-consuming, so that the close cooperative work of software and hardware needs to be designed and debugged more carefully in order to ensure the accuracy and the reliability. In addition, precision instruments also add to the complexity and difficulty of operation for the operator.
Disclosure of Invention
The invention aims to provide an all-in-one eyeball comprehensive parameter measuring instrument and a method for measuring eyeball parameters by using the same, so as to solve the problems of single functional structure, low integration level and the like of the traditional equipment, and can simultaneously measure the curvature, diopter and biological parameters of human eyes at one time under the non-contact and non-invasive conditions, thereby achieving the purposes of more intelligentization and practicability.
In order to achieve the above purpose, the invention adopts the following technical scheme:
the first aspect provides an all-in-one eyeball comprehensive parameter measuring instrument, which comprises a signal light source module, a scale light source module, a dichroic mirror, a wavelength division multiplexer, an optical delay line, an annular light source, an illumination imaging module, a sighting target illumination module, a sighting target imaging module, a second spectroscope, a third spectroscope, a data acquisition card and a data processing unit;
The signal light source module sends out two light beams, one light beam is transmitted to the dichroic mirror, after being reflected by the dichroic mirror, the light beam enters an eyeball to be detected, after being reflected by the eyeball, the light beam returns to the original return signal light source module;
the scale light source module emits two light beams, one light beam is reflected and then returns to the scale light source module, the other light beam enters the wavelength division multiplexer and is transmitted to the optical delay line, and the other light beam is reflected and then returns to the scale light source module, and the two return light beams interfere at the scale light source module;
The visual target illumination module is used for imaging visual target images through illumination, the visual target images are imaged on eyeground after passing through a third spectroscope and a second spectroscope, and the visual target images of the eyeground are transmitted to the visual target imaging module for clear imaging;
The signal light source module and the scale light source module are both connected with the data acquisition card, the data acquisition card is connected with the data processing unit, and the data processing unit is connected with the optical delay line.
Optionally, the signal light source module includes a signal light source, an optical fiber circulator, a photoelectric balance detector, a first optical fiber coupler, a signal light source sample arm, and a signal light source reference arm;
The signal light source emits light rays which pass through the optical fiber circulator and enter the first optical fiber coupler from the optical fiber circulator, the first optical fiber coupler is split into two beams, the two beams enter the signal light source sample arm and the signal light source reference arm respectively, the light of the signal light source sample arm deflects in a light path through a dichroic mirror and is transmitted to a measuring eyeball for reflection, the return light reenters a third port of the first optical fiber coupler, the signal light source reference arm is connected with a wavelength division multiplexer and an optical delay line, the light of the signal light source reference arm reenters a fourth port of the first optical fiber coupler after being reflected by the optical delay line, the two paths of return light entering the first optical fiber coupler are respectively input into the optical fiber circulator and the photoelectric balance detector from a first port and a second port of the first optical fiber coupler after being interfered, the optical fiber circulator is connected with the photoelectric balance detector, and the photoelectric balance detector amplifies the two paths and converts the two paths into electric signals, and the electric signals are transmitted to the data acquisition card.
Optionally, the signal light source sample arm comprises a first optical fiber collimator, a first spectroscope, a signal light source test arm, a signal light source zero point arm and a first polarization controller, wherein the signal light source reference arm is provided with a second polarization controller;
The light of the signal light source sample arm passes through the first optical fiber collimator and then enters the first spectroscope, and is divided into two beams of light to enter the signal light source test arm and the signal light source zero point arm respectively, wherein the signal light source test arm and the signal light source zero point arm can reflect the light, and the returned light beam is combined to enter the third port of the first optical fiber coupler again;
The first polarization controller is used for controlling the polarization state of the returned light of the signal light source sample arm, and the second polarization controller is used for controlling the polarization state of the returned light of the signal light source reference arm.
Optionally, the scale light source module includes a scale light source, a photoelectric unit detector, a second optical fiber coupler, a scale light source sample arm, a scale light source reference arm, and an optical fiber reflector;
The light emitted by the scale light source is divided into two beams of light through the second optical fiber coupler, the two beams of light enter the scale light source sample arm and the scale light source reference arm respectively, the scale light source sample arm is connected with the optical fiber reflector, the light is reflected by the optical fiber reflector, the return light enters the third port of the second optical fiber coupler, the light of the scale light source reference arm is transmitted to the optical delay line from the wavelength division multiplexer, the return light enters the fourth port of the second optical fiber coupler after being reflected by the optical delay line, and the two paths of return light entering the second optical fiber coupler interfere and then come out from the first port and the second port of the second optical fiber coupler respectively, the two paths of return light are respectively input into the scale light source and the photoelectric unit detector, the photoelectric unit detector converts an optical signal into an electric signal, and the electric signal is transmitted to the data acquisition card.
Optionally, the optical delay line comprises a second optical fiber collimator, a voice coil motor, a right angle prism, a hollow roof prism, a fifth plane reflector, a sixth plane reflector and a cementing lens, wherein the hollow roof prism is arranged in front of the voice coil motor, the right angle prism is fixedly arranged right in front of a hollow roof of the hollow roof prism, the fifth plane reflector and the sixth plane reflector are arranged on the left side and the right side of the right angle prism, the cementing lens is arranged in front of the sixth plane reflector, light is collimated by the second optical fiber collimator and then transmitted to the fifth reflector, after being deflected, is transmitted back and forth between the right angle prism and the hollow roof prism, is focused and reflected by the sixth reflector after being converged by the cementing lens, and is coupled into the second optical fiber collimator again after being transmitted by the original path of the light path.
Optionally, the illumination imaging module includes a telecentric lens and a first camera;
Light from the annular light source is reflected at the cornea and, after the reflected light passes through the dichroic mirror, the second beam splitter and the telecentric lens, imaged at the first camera.
Optionally, the optotype lighting module includes an optotype light source, an optotype, a first lens, a reflector, and a second lens;
The sighting target light source illuminates the sighting target, illumination light is focused through a first lens, deflected through a reflecting mirror, focused into parallel light through a second lens, transmitted through the third spectroscope and reflected by the second spectroscope, transmitted through the dichroic mirror and imaged on retina.
Optionally, the optotype imaging module comprises a zoom lens group and a second camera;
the target image returns in the original path after being reflected, is transmitted through a dichroic mirror, enters the zoom lens group after being reflected by the second spectroscope and the third spectroscope, and is finally imaged on the second camera.
Optionally, a movable lens is disposed on the zoom lens group, the focal length of the system is changed by the movable lens, so that the second camera forms clear images, and the diopter of the eyeball can be measured by the position of the movable lens on the zoom lens group.
In a second aspect, there is provided a measurement method using the integrated eyeball integrated parameter measurement instrument of the first aspect, the method including the steps of:
step S1, adjusting the distance between the annular light source and the cornea of the model eye to enable the imaging on the illumination imaging module to be clear, and calculating the cornea curvature by calculating the mass center and the diameter of the inner ring and the outer ring;
s2, adjusting a sighting target imaging module to enable an image on the sighting target imaging module to be clear, and further obtaining the diopter of an eyeball;
Step S3, dynamically adjusting the distance between the annular light source and the cornea of the eye to enable the illumination imaging module to form clear images, adjusting the normal incidence of detection light on the eyeball, and simultaneously adjusting the optical path from the signal light source module to the cornea, wherein the data acquisition card dynamically acquires interference signal measurement data of the signal light source module;
s4, carrying out mean value reduction, band-pass and smooth filtering treatment on the interference signal measurement data, and then carrying out cross correlation to obtain a signal waveform with prominent peak value signals;
S5, carrying out peak searching by using the processed signal waveform, and finding out the position information of the signal peak;
Step S6, synchronously acquiring interference peaks of the scale light source module closest to the position information obtained in the step S5 by utilizing the same optical delay line shared by the scale light source module and the signal light source module;
And S7, utilizing the interference wave crest of the scale light source module as an endogenous position scale, and utilizing the number of interference waveforms of the scale light source module to calculate the corresponding peak position information interval distance obtained in the step S6, so as to calculate the data of each human eye tissue structure.
The beneficial effects of the invention are as follows:
The invention combines an all-in-one eyeball comprehensive parameter measuring instrument, adopts a low-coherence light measuring technology and an imaging technology, designs a signal light source module, a scale light source module, an illumination imaging module, a sighting target illumination module, a sighting target imaging module, an optical delay line and other modules, wherein the signal light source module is used for measuring eyeball biological parameters, the scale light source module is used for calculating eyeball biological parameter distances, an annular light source and a telecentric lens in the illumination imaging module can measure cornea curvature through imaging of the annular light source, a zoom lens group of the sighting target imaging module can measure eyeball diopter through refraction compensation of the annular light source, and the reasonable spatial layout of various devices is adopted to realize simultaneous measurement of various functions, so that the problems of single function and low integration level of the traditional equipment are overcome, the measuring precision is high, and the measuring effect is obvious.
The invention utilizes the method that the comprehensive parameter measuring apparatu of the many unification eyeballs measures the eyeball parameter, start the measuring apparatu to lighten each light source and start the voice coil motor first, then carry on the light source imaging of the lighting plate, eyeground optotype imaging sequentially to obtain eyeball diopter, then obtain the interference wave dynamically, confirm the annular light source and distance of cornea of eye accurately, then demodulate the signal light source interference signal, seek peak to obtain the position information, obtain the staff light source interference peak synchronously, finally utilize staff light source relevant information to calculate each organization structure data of human eye, wherein the processing of the signal of low signal-to-noise ratio is through carrying on the bandpass filter processing to the signal, then turn over the mean value, process with the mean value smoothing filter algorithm, through carrying on the cross correlation algorithm comparison to each measuring result, keep the cross correlation result greater than the measuring data of the settlement threshold value, can remove noise and white noise etc. of the signal channel that the mechanical vibration brings through this method effectively, especially because of the irregular change of the signal height that the eyeball moves.
It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the application as claimed.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the application and together with the description, serve to explain the principles of the application.
Fig. 1 is a schematic diagram of the overall structure of an integrated eyeball integrated parameter measurement instrument according to an embodiment of the present invention.
Fig. 2 is a schematic structural diagram of an optical delay line according to an embodiment of the present invention.
Fig. 3 is a schematic structural diagram of a zoom lens set according to an embodiment of the present invention.
Fig. 4 is a signal processing flow chart provided in an embodiment of the present invention.
Fig. 5 is a flowchart of a mean smoothing filtering algorithm according to an embodiment of the present invention.
Fig. 6 is a flowchart of a peak searching process according to an embodiment of the present invention.
Fig. 7 is a diagram of signal data to be processed according to an embodiment of the present invention.
Fig. 8 is processed signal data provided by an embodiment of the present invention.
In the figure, 1, a signal light source; 2, an optical fiber circulator; 3, a photoelectric balance detector; a first optical fiber coupler, a first polarization controller, a second polarization controller, a first optical fiber collimator, a first optical fiber coupler, a second optical fiber coupler, a third optical fiber coupler, a fourth optical fiber coupler, a fifth optical fiber coupler, a fourth optical fiber mirror, a fourth optical fiber coupler, a fourth optical fiber mirror, a fifth optical coupler, a fourth optical fiber coupler, a fourth optical fiber coupler, a fourth optical coupler, fourth, a fifth optical coupler, fourth, a fourth lens, fourth lens fifth lens, fourth polarizing lens fourth lens fifth lens mirror, fourth lens mirror fifth lens mirror, fourth lens mirror blue, 23 fourth lens mirror lens fifth lens mirror lens 23 fifth lens 23 respective 23 respective fifth polarizing lens 23 mirror lens mirror lens respectively 24 mirror respectively 24, respectively, respectively,.
Detailed Description
The embodiments of the present invention will be described in further detail below with reference to the accompanying drawings, and it should be emphasized that the examples of embodiments of the present invention are illustrative, not limiting, and thus the present invention is not limited to the examples of embodiments described in the detailed description.
Referring to fig. 1-3, an embodiment of the present invention provides an integrated eyeball integrated parameter measurement apparatus, which includes a signal light source module 46, a scale light source module 50, a dichroic mirror 18, a wavelength division multiplexer 29, an optical delay line 35, an annular light source 19, an illumination imaging module 47, a optotype imaging module 48, an optotype illumination module 49, a second beam splitter 17, a third beam splitter 23, a data acquisition card 36 and a data processing unit 30;
in one embodiment, the signal light source module 46 includes a signal light source 1, a fiber circulator 2, a photoelectric balance detector 3, a first fiber coupler 4, a signal light source sample arm and a signal light source reference arm, wherein the signal light source sample arm includes a first fiber collimator 7, a first spectroscope 8, a signal light source test arm, a signal light source zero point arm and a first polarization controller 5, the signal light source reference arm is provided with a second polarization controller 6, the signal light source test arm includes a first reflecting mirror 9 and a second plano-convex lens 14, the signal light source zero point arm includes a second reflecting mirror 10, a first plano-convex lens 12, a glass rod 11 and a third reflecting mirror 13. The signal light source testing arm is designed to rapidly measure human eye information, and the signal light source zero point arm is used for measuring position location.
In an embodiment, a signal light source 1 is connected to a first port of an optical fiber circulator 2, a second port of the optical fiber circulator 2 is connected to a first port of a first optical fiber coupler 4, a third port of the optical fiber circulator 2 is connected to a first signal input port of a photoelectric balance detector 3, a second signal input port of the photoelectric balance detector 3 is connected to a second port of the first optical fiber coupler 4, light emitted by the signal light source 1 passes through the optical fiber circulator 2 and is split into two beams of light through the first optical fiber coupler 4, the two beams of light enter the signal light source sample arm and the signal light source reference arm respectively, the light of the signal light source sample arm is transmitted from an optical fiber outlet, collimated by the first optical fiber collimator 7 and then transmitted to a first spectroscope 8 for 5:5 light intensity equalization, one path of light is reflected into a signal light zero point arm, and the other path of light is transmitted into a signal light source test arm. The light entering the signal light source testing arm is reflected by the third reflector, and then the light is converged by the first plano-convex lens 13, so that the light completely enters the glass rod 11 for transmission, and then is reflected by the second reflector 10, and the reflected light is transmitted to the third port of the first optical fiber coupler 4. The signal light source reference arm is connected to the wavelength division multiplexer 29 and the optical delay line 35, and the light transmission of the signal light source reference arm is transmitted from the wavelength division multiplexer 29 to the optical delay line 35, after being reflected by the optical delay line 35, the return light reenters the fourth port of the first optical fiber coupler 4, and after two paths of return light entering the first optical fiber coupler 4 interfere, the return light is respectively input to the second port of the optical fiber circulator 2 and the second port of the photoelectric balance detector 3 from the first port and the second port of the first optical fiber coupler 4.
In an embodiment, the signal light source reference arm is provided with a second polarization controller 6, the second polarization controller 6 is used for controlling the polarization state of the return light of the signal light source reference arm, the signal light source reference arm and the signal light source sample arm are in the same polarization state by adjusting the polarization state of the signal light source reference arm, at the moment, the interference signal contrast is highest and the signal intensity is highest, the first polarization controller 5 is used for controlling the polarization state of the return light of the signal light source sample arm, and the second polarization controller 6 is used for controlling the polarization state of the return light of the signal light source reference arm.
The light interference of the signal light source sample arm and the signal light source reference arm after polarization control is input into a third port of the optical fiber circulator 2 from a second port of the optical fiber circulator 2 and then is input into a first port of the photoelectric balance detector 3, the photoelectric balance detector 3 receives interference light from the signal light source sample arm and the signal light source reference arm and sends the interference light to the data acquisition card 36, and the acquisition card sends data to the data processing unit 30.
In one embodiment, the scale light source module 50 includes a scale light source 31, a photo-electric unit detector 32, a second fiber coupler 33, a scale light source sample arm, a scale light source reference arm, and a fiber optic reflector 34;
The scale light source 31 is connected with the first port of the second optical fiber coupler 33, the second port of the second optical fiber coupler 33 is connected with the photoelectric unit detector 32, the light emitted by the scale light source 31 is divided into two beams of light through the second optical fiber coupler 33, the two beams of light enter the scale light source sample arm and the scale light source reference arm respectively, the scale light source sample arm is connected with the optical fiber reflector 34, the optical fiber reflector 34 is used for the optical fiber loop of the scale light source sample arm, and the optical fiber reflector 34 can reflect the light to interfere with each other at maximum efficiency under the condition of no space optical coupling. The light is reflected by the optical fiber reflector 34, the return light enters the third port of the second optical fiber coupler 33, the light of the scale light source reference arm is transmitted from the wavelength division multiplexer 29 to the optical delay line 35, the return light enters the fourth port of the second optical fiber coupler 33 after being reflected by the optical delay line 35, the two paths of return light entering the second optical fiber coupler 33 interfere and come out from the first port and the second port of the second optical fiber coupler 33 respectively and are respectively input to the scale light source 31 and the photoelectric unit detector 32, the photoelectric unit detector 32 receives interference light from the scale light source sample arm and the scale light source reference arm and transmits the interference light to the data acquisition card 36, and the data acquisition card 36 transmits data to the data processing unit 30 for data processing and displaying.
The photoelectric balance detector 3 and the photoelectric unit detector 32 are both connected with the data acquisition card 36, the data acquisition card 36 is connected with the data processing unit 30, and the data processing unit 30 is connected with the optical delay line 35. In an embodiment, the optical delay line 35 includes a second optical fiber collimator 37, a voice coil motor 39, a right angle prism 41, a hollow roof prism 40, a fifth plane mirror 38, a sixth plane mirror 43 and a cemented lens 42, wherein the hollow roof prism 40 is installed in front of the voice coil motor 39, the right angle prism 41 is fixedly installed in front of the hollow roof prism 40, the fifth plane mirror and the sixth plane mirror are installed on the left and right sides of the right angle prism 41, the cemented lens 42 is installed in front of the sixth plane mirror, the light is collimated by the second optical fiber collimator 37 and then transferred to the fifth mirror 38, the light path is transferred back and forth between the right angle prism 41 and the hollow roof prism 40 after being converged by the cemented lens 42, and is focused and reflected by the sixth mirror 43 after being transferred, and is coupled into the second optical fiber collimator 37 again after being transferred, wherein the cemented lens 42 is significantly increased by the deflection of the hollow roof prism 40 and the right angle prism 41 to the optical path under the premise of limiting the movement distance of the hollow roof prism 40, the cemented lens 42 is used for reducing the focal distance of the measured on the premise that the distance of the limited motor 39, and the focal distance can be effectively increased, and the focal distance of the cemented lens 42 is used for reducing the focal angle of the light beam and the optical delay signal can be transferred to the optical delay line 1 when the optical delay is offset, and the optical delay angle is reduced, and the optical delay signal is transferred between the position of the optical delay mirror 1 and the optical delay line is effectively reduced.
In one embodiment, the illumination imaging module includes a telecentric lens 16 and a first camera 15, the annular light source 19 emits light, the eyeball is illuminated, the cornea of the eyeball reflects the light to pass through the hollow part of the annular light source 19, the light transmits a dichroic mirror 18 and a second dichroic mirror 17, and the light passes through the telecentric lens 16 and then is imaged on the first camera 15. The positions of the annular light source 19 and the signal light source sample arm, the signal light source reference arm, the scale light source sample arm and the scale light source reference arm are relatively fixed, the positions at the moment meet the optical path condition required by the formation of stable interference waves between the signal light source sample arm and the reference arm and between the scale light source sample arm and the reference arm and the distance condition for clear imaging of the first camera 15, the position of the measuring human eye relative to the measuring instrument is adjusted through the observation camera, and when clear imaging is observed, the measurement human eye is in the measuring range of the measuring instrument at the moment.
The optotype lighting module comprises an optotype light source 24, an optotype 25, a first lens 26, a fourth lens 27 and a second lens 25, the optotype imaging module comprises a zooming lens group 22 and a second camera 21, in one embodiment, the first lens 26, the fourth lens 27 and the second lens 25 are arranged between the optotype 25 and the third spectroscope 23 in sequence, the lighting light passes through a 4f system formed by the first positive lens 26, the fourth lens 27 and the second positive lens 28, is transmitted through the third spectroscope 23, is reflected at the second spectroscope 17, is transmitted through the dichroic mirror 18 and is formed into an optotype image on the retina, the optotype image serves as an object, is transmitted through the dichroic mirror 18 and the second spectroscope 17, is reflected into the zooming lens group 22 at the third spectroscope 23, the first lens of the zooming lens group 22 is a fixed lens 45, the second lens 44 is moved through the zooming lens group 22, and the light passes through the zooming lens group 22 to form a clear image on the second camera 21. The fourth reflecting mirror 27 is used for deflecting the light path, and the first lens 26 and the second lens 25 are used for maximally extending the light path on the premise of ensuring the parallelism of the light path.
In an embodiment, the zoom lens group 22 is provided with a movable lens 44, the focal length of the system is changed by the movable lens 44, so that the second camera 21 forms a clear image, wherein the position of the movable lens 44 on the zoom lens group 22 corresponds to the diopter compensation value of the zoom lens group 22 one by one, and the diopter compensation value of the system can be measured by moving the position of the lens 44, so as to measure the diopter of the human eye.
As can be seen from the above embodiments, the integrated multi-in-one eyeball comprehensive parameter measuring apparatus is designed according to the present application, and the integrated multi-in-one eyeball comprehensive parameter measuring apparatus comprises a signal light source module for measuring biological parameters of human eyes, a scale light source module for synchronously calculating the biological parameter information of human eyes, an annular light source 19 for measuring cornea curvature, a optotype light source 24 for measuring cornea curvature, and a zoom lens group 22 for measuring eyeball diopter. The embodiment of the application also provides a method for measuring eyeball parameters by using the all-in-one eyeball comprehensive parameter measuring instrument, which comprises the following steps:
Step S1, imaging by using an illumination plate light source, namely adjusting the distance between an annular light source and a model cornea so as to enable imaging on an illumination imaging module to be clear, and calculating the cornea curvature by calculating the mass center and the diameter of an inner ring and an outer ring;
Specifically, the measuring instrument is moved, the distance between the annular light source 19 and the cornea of the model eye is adjusted, so that the imaging on the illumination imaging module 47 is clear, and the cornea curvature can be obtained by calculating the mass center and the diameter of the inner ring and the outer ring;
In the invention, the first camera on the illumination imaging module displays an annular image, and a centroid algorithm formula can be utilized:
;
Wherein, ,For the pixel coordinates,For the intensity of the pixel light, calculating the center of mass of the circular ring, calculating the inner diameter and the outer diameter of the circular ring according to the coordinate point of the intensity of the circular ring, and calculating the cornea curvature radius, the cornea transverse diameter and the pupil diameter by using the diameter.
Step S2, eyeground optotype imaging, namely adjusting an optotype imaging module to enable an image on the optotype imaging module to be clear, and further obtaining diopter of an eyeball, wherein the step can comprise the following substeps:
s21, calibrating the refraction states of the movable lenses of the zoom lens group of the sighting mark imaging module at different positions;
s22, moving a movable lens of the zoom lens group, changing the focal length of the zoom lens group, and performing refraction compensation on the retina image;
step S23, observing the definition of the image on the second camera on the visual target imaging module in the process of moving the lens, and recording the position of the movable lens in the clearest imaging;
s24, inquiring a corresponding relation table of lens positions and diopters to obtain the diopters of the eyeballs;
in the present invention, an optical system can calculate its diopter using the formula:
Wherein, In order to be the object distance,In order to be the image distance,As focal length, according to the optical focal length definition:
Wherein: Is the incident optical power;
Since the definition of the human eye uses the incident light to define diopters, the optical power is Corresponding to the outgoing light of (a)Is the eyeball of (2);
Wherein: is the emergent focal power;
The theoretical diopter calculation formula is the product of the focal length and the object distance divided by the focal length and the object distance;
By moving the movable lens of the zoom lens group, the diopter of the eyeball can be obtained by complementing the diopter of the sighting target imaging module with the diopter of the eyeball.
Step S3, dynamically acquiring interference waves, namely dynamically adjusting the distance between the annular light source and the cornea of the eye to enable the illumination imaging module to form clear images, adjusting the normal incidence of detection light on the eyeball, and simultaneously adjusting the optical path from the signal light source module to the cornea, wherein the data acquisition card dynamically acquires interference signal measurement data of the signal light source module;
Specifically, the distance between the annular light source 19 and the cornea of the eye is dynamically adjusted to enable the first camera to image clearly, the detection light is adjusted to be normally incident on the eyeball, meanwhile, the optical path between the signal light source module and the cornea is also adjusted, and the data acquisition card dynamically acquires interference signal measurement data of the signal light source module;
In the invention, the positions of the annular light source 19, the signal light source sample arm, the signal light source reference arm, the scale light source sample arm and the scale light source reference arm are relatively fixed, and at the moment, the positions meet the distance condition of clear imaging of the first camera and the optical path condition required by the formation of stable interference waves of the signal light source sample arm, the reference arm, the scale light source sample arm and the reference arm, the interference signal waveforms comprise waveforms on the signal light source test arm, waveforms of the signal light source zero point arm and interference waveforms of the scale light source sample arm and the scale light source reference arm;
s4, carrying out mean value reduction, band-pass and smooth filtering treatment on the interference signal measurement data, and then carrying out cross correlation to obtain a signal waveform with prominent peak value signals;
Specifically, the measurement data obtained in the step S3 is utilized to firstly carry out average value reduction and turnover processing, then the zero signal and the peak signal waveform for measuring eyeball parameters are obtained after bandpass and smooth average value filtering, and then the signal waveform with prominent peak signal is obtained after low-pass filtering processing;
in the present invention, the system uses the optical delay line 35 as the linear motion driven by the voice coil motor 39, and mechanical noise is introduced due to the back and forth vibration of the voice coil motor 39, so that the signal to noise ratio of the signal is reduced, based on the situation, the present invention designs a smoothing filtering algorithm for processing the low signal to noise ratio introduced by the oversized vibration, the filtering algorithm flow refers to fig. 4, specifically, for the collected interference signal, the average value is firstly calculated to obtain Because the original data has both positive and negative values, the original data is used to realize the inversion of the negative dataAnd (3) withAnd performing difference making, and then obtaining an absolute value, so that negative value data can be turned upwards relative to the average value.
In order to find the peak value corresponding to the zero optical path difference, a useful signal is extracted, and the interference signal is subjected to smoothing filter processing, and the processing method is shown in fig. 5. Firstly, a proper filter mean value window K is set, the larger the K value is, the higher the signal smoothness is, the lower the sensitivity is, the operation speed is slower, and the smaller the n value is, the lower the signal smoothness is, the higher the sensitivity is, and the operation speed is fast. For ease of calculation, n is typically an integer power of 2, e.g., 4, 8, 16, 32, etc. And then, averaging the turned numerical values and averaging adjacent numerical values in a certain range. Each mean value is taken as a new filtered result.
Considering that the measured sample is a biological eyeball, the biological eyeball is inevitably lost due to movement in the measuring process, so the invention designs a cross-correlation algorithm for carrying out data segment comparison, and the data segment with the cross-correlation result larger than a set threshold value is reserved, and the complete sample information can be calculated by processing the measurement results for a plurality of times.
And calculating a correlation coefficient of a corresponding position of each range data segment, wherein the calculation formula is as follows:
;
Wherein, Is the standard deviation of the sample of X, and the formula is:
,;
for sample covariance, the formula is:
;
Sample of ,Data representing the range of two adjacent scans,Represents the sample mean value of the scanned data, and n is the sample data size.
Step S5, peak searching and obtaining, namely carrying out peak searching by using the processed signal waveform, and finding out the position information of the signal peak;
Specifically, referring to fig. 6, in this example, for the filtered value, the signal extremum may be obtained by obtaining the first-order derivative signal of the signal, and then judging whether the extremum is the maximum value by the second derivative, where the minimum interval between the peaks, the height threshold and the peak reference height are added to make the peak value more reasonable, considering that the filtered signal is unlikely to be completely smooth.
The invention realizes the real-time synchronization of the data acquisition and the linear movement boundary, because the linear movement is not unidirectional linear movement, the voice coil motor 39 moves back and forth, so the scanning range corresponding to the signal sample arm of the biological eyeball testing system also scans back and forth.
Step S6, synchronous information acquisition, namely synchronously acquiring interference peaks of the scale light source module nearest to the position corresponding to the step S5 by utilizing the scale light source module 50 and the signal light source module 46 to share the same optical delay line;
S7, calculating, namely calculating the corresponding peak position information interval distance obtained in the S6 by using the number of interference waveforms of the scale light source module and using the interference peaks of the scale light source module as an endogenous position scale, and calculating the data of each tissue structure of human eyes;
Specifically, the number of interference peaks of the scale light source module 50 is used as an endogenous position scale, and the corresponding peak position information interval distance obtained in step S6 is calculated by using the number of interference waveforms of the scale light source module 50, so as to calculate the data of each tissue structure of human eyes. The waveform diagram of each tissue signal of the human eye can be displayed on the data processing unit in real time, and meanwhile, each peak distance information is displayed.
Examples:
As shown in fig. 1, the signal light source 1 adopts a superradiation light emitting diode with a selected center wavelength of 840nm, a bandwidth of 40nm and an optical power of 6mw, and the scale light source 31 adopts a DFB (Distributed Feed Back) laser with a center wavelength of 1310nm, a bandwidth of 1GH and an optical power of 10 mw;
the first optical fiber coupler 4 is 2 x 2, the optical fiber device with the central wavelength and bandwidth matched with the signal light source, the optical fiber is a single-mode optical fiber, the second optical fiber coupler 33 is 2 x 2, the optical fiber device with the central wavelength and bandwidth matched with the scale light source, and the optical fiber is a single-mode optical fiber;
The first optical fiber collimator 7 and the second optical fiber collimator 37 are aspheric lenses with the center wavelength of 840nm, and the focal length is 11mm;
The focal length 12 of the first plano-convex lens is 50mm, the focal length of the second plano-convex lens 14 is 100mm, the focal length of the first positive lens 26 is 50mm, the focal length of the second positive lens 28 is 30mm, the focal length of the fixed lens 45 is 20mm, and the focal length of the movable lens 44 is 30mm;
The first polarization controller 5 and the second polarization controller 6 realize the change of the light polarization state by mechanically twisting and stretching the optical fiber;
the photoelectric balance detector 3 and the photoelectric unit detector 32 are photoelectric devices, and can convert optical signals into electric signals;
wavelength division multiplexer 29 is capable of transmitting light having a center wavelength of 840nm and reflecting light having a center wavelength of 1310 nm;
the first light splitting prism performs 5:5 light splitting on light with the center of 840nm, and the second light splitting prism and the third light splitting prism perform 5:5 light splitting on light with the center of 940 nm;
the annular light source and the vision light source LED are 940nm near infrared light sources, and the first camera is a CCD or a CMOS;
The model eye 20 is measured by the system of the present invention, and the results are shown in fig. 7 and 8, wherein fig. 7 shows the data collected by the detector, and fig. 8 shows the result of processing the signals by the design of the present invention, wherein a is the anterior surface interference peak of cornea, b is the posterior surface interference peak of cornea, c is the anterior surface interference peak of crystal, d is the posterior surface interference peak of crystal, e is the retinal interference peak, and all biological parameters of the eyeball including cornea thickness, anterior chamber depth, crystal thickness, vitreous thickness and ocular axis length can be precisely calculated once according to the positions of the respective peaks.
The technical scheme of the invention is explained in detail above with reference to the accompanying drawings, and the described embodiments are used for helping to understand the idea of the invention. The specific embodiments described herein are offered by way of example only. Those skilled in the art may make various modifications or additions to the described embodiments or substitutions in a similar manner without departing from the spirit of the invention or exceeding the scope of the invention as defined in the accompanying claims.
Claims (10)
1. The utility model provides an all-in-one eyeball comprehensive parameter measuring apparatu, includes signal light source module, scale light source module, dichroscope, wavelength division multiplexer, optical delay line, annular light source, illumination imaging module, optotype lighting module, optotype imaging module, second beam splitter, third beam splitter, data acquisition card and data processing unit;
The signal light source module sends out two light beams, one light beam is transmitted to the dichroic mirror, after being reflected by the dichroic mirror, the light beam enters an eyeball to be detected, after being reflected by the eyeball, the light beam returns to the original return signal light source module;
the scale light source module emits two light beams, one light beam is reflected and then returns to the scale light source module, the other light beam enters the wavelength division multiplexer and is transmitted to the optical delay line, and the other light beam is reflected and then returns to the scale light source module, and the two return light beams interfere at the scale light source module;
The visual target illumination module is used for imaging visual target images through illumination, the visual target images are imaged on eyeground after passing through a third spectroscope and a second spectroscope, and the visual target images of the eyeground are transmitted to the visual target imaging module for clear imaging;
The signal light source module and the scale light source module are both connected with the data acquisition card, the data acquisition card is connected with the data processing unit, and the data processing unit is connected with the optical delay line.
2. The integrated eyeball integrated parameter measurement of claim 1 wherein the signal light source module includes a signal light source, a fiber optic circulator, a photoelectric balance detector, a first fiber optic coupler, a signal light source sample arm and a signal light source reference arm;
The signal light source emits light rays which pass through the optical fiber circulator and enter the first optical fiber coupler from the optical fiber circulator, the first optical fiber coupler is split into two beams, the two beams enter the signal light source sample arm and the signal light source reference arm respectively, the light of the signal light source sample arm deflects in a light path through a dichroic mirror and is transmitted to a measuring eyeball for reflection, the return light reenters a third port of the first optical fiber coupler, the signal light source reference arm is connected with a wavelength division multiplexer and an optical delay line, the light of the signal light source reference arm reenters a fourth port of the first optical fiber coupler after being reflected by the optical delay line, the two paths of return light entering the first optical fiber coupler are respectively input into the optical fiber circulator and the photoelectric balance detector from a first port and a second port of the first optical fiber coupler after being interfered, the optical fiber circulator is connected with the photoelectric balance detector, and the photoelectric balance detector amplifies the two paths and converts the two paths into electric signals, and the electric signals are transmitted to the data acquisition card.
3. The all-in-one eyeball integrated parameter measurement instrument according to claim 2 is characterized in that the signal light source sample arm comprises a first optical fiber collimator, a first spectroscope, a signal light source test arm, a signal light source zero point arm and a first polarization controller, wherein the signal light source reference arm is provided with a second polarization controller;
The light of the signal light source sample arm passes through the first optical fiber collimator and then enters the first spectroscope, and is divided into two beams of light to enter the signal light source test arm and the signal light source zero point arm respectively, wherein the signal light source test arm and the signal light source zero point arm can reflect the light, and the returned light beam is combined to enter the third port of the first optical fiber coupler again;
The first polarization controller is used for controlling the polarization state of the returned light of the signal light source sample arm, and the second polarization controller is used for controlling the polarization state of the returned light of the signal light source reference arm.
4. The integrated eyeball integrated parameter measurement of claim 1 wherein the scale light source module includes a scale light source, a photoelectric cell detector, a second fiber coupler, a scale light source sample arm, a scale light source reference arm and a fiber mirror;
The light emitted by the scale light source is divided into two beams of light through the second optical fiber coupler, the two beams of light enter the scale light source sample arm and the scale light source reference arm respectively, the scale light source sample arm is connected with the optical fiber reflector, the light is reflected by the optical fiber reflector, the return light enters the third port of the second optical fiber coupler, the light of the scale light source reference arm is transmitted to the optical delay line from the wavelength division multiplexer, the return light enters the fourth port of the second optical fiber coupler after being reflected by the optical delay line, and the two paths of return light entering the second optical fiber coupler interfere and then come out from the first port and the second port of the second optical fiber coupler respectively, the two paths of return light are respectively input into the scale light source and the photoelectric unit detector, the photoelectric unit detector converts an optical signal into an electric signal, and the electric signal is transmitted to the data acquisition card.
5. The integrated parameter measuring instrument for the multiple-in-one eyeball according to claim 1 is characterized in that the optical delay line comprises a second optical fiber collimator, a voice coil motor, a right angle prism, a hollow roof prism, a fifth plane reflector, a sixth plane reflector and a cemented lens, wherein the hollow roof prism is arranged in front of the voice coil motor, the right angle prism is fixedly arranged in front of the hollow roof prism, the fifth plane reflector and the sixth plane reflector are arranged on the left side and the right side of the right angle prism, the cemented lens is arranged in front of the sixth plane reflector, light is collimated by the second optical fiber collimator and then transmitted to the fifth reflector, the light path is deflected and then transmitted back and forth between the right angle prism and the hollow roof prism, and is focused and reflected by the sixth reflector after being converged by the cemented lens, and the light path is coupled into the second optical fiber collimator again after being transmitted in the original path.
6. The integrated ocular parameter gauge of claim 1, wherein the illumination imaging module comprises a telecentric lens and a first camera;
Light from the annular light source is reflected at the cornea and, after the reflected light passes through the dichroic mirror, the second beam splitter and the telecentric lens, imaged at the first camera.
7. The integrated ocular parameter gauge of claim 1, wherein the optotype lighting module comprises an optotype light source, an optotype, a first lens, a reflector, and a second lens;
The sighting target light source illuminates the sighting target, illumination light is focused through a first lens, deflected through a reflecting mirror, focused into parallel light through a second lens, transmitted through the third spectroscope and reflected by the second spectroscope, transmitted through the dichroic mirror and imaged on retina.
8. The integrated ocular parameter gauge of claim 1, wherein the optotype imaging module comprises a zoom lens set and a second camera;
the target image returns in the original path after being reflected, is transmitted through a dichroic mirror, enters the zoom lens group after being reflected by the second spectroscope and the third spectroscope, and is finally imaged on the second camera.
9. The apparatus according to claim 8, wherein the zoom lens is provided with a movable lens, the focal length of the system is changed by the movable lens, the second camera is made to image clearly, and the diopter of the eyeball is measured by the position of the movable lens on the zoom lens.
10. A method of measuring using the integrated eyeball combination parameter measurement of claim 1, the method comprising the steps of:
step S1, adjusting the distance between the annular light source and the cornea of the model eye to enable the imaging on the illumination imaging module to be clear, and calculating the cornea curvature by calculating the mass center and the diameter of the inner ring and the outer ring;
s2, adjusting a sighting target imaging module to enable an image on the sighting target imaging module to be clear, and further obtaining the diopter of an eyeball;
Step S3, dynamically adjusting the distance between the annular light source and the cornea of the eye to enable the illumination imaging module to form clear images, adjusting the normal incidence of detection light on the eyeball, and simultaneously adjusting the optical path from the signal light source module to the cornea, wherein the data acquisition card dynamically acquires interference signal measurement data of the signal light source module;
s4, carrying out mean value reduction, band-pass and smooth filtering treatment on the interference signal measurement data, and then carrying out cross correlation to obtain a signal waveform with prominent peak value signals;
S5, carrying out peak searching by using the processed signal waveform, and finding out the position information of the signal peak;
Step S6, synchronously acquiring interference peaks of the scale light source module closest to the position information obtained in the step S5 by utilizing the same optical delay line shared by the scale light source module and the signal light source module;
And S7, utilizing the interference wave crest of the scale light source module as an endogenous position scale, and utilizing the number of interference waveforms of the scale light source module to calculate the corresponding peak position information interval distance obtained in the step S6, so as to calculate the data of each human eye tissue structure.
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN120167881A (en) * | 2025-05-23 | 2025-06-20 | 中国科学院苏州生物医学工程技术研究所 | OCT reference arm with adjustable integrate in operation microscope |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102525402A (en) * | 2012-03-01 | 2012-07-04 | 浙江工业大学 | Optical system and optometry method of computer optometer |
| 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 |
| CN206920338U (en) * | 2017-07-05 | 2018-01-23 | 广东欧谱曼迪科技有限公司 | An optical coherent confocal endoscopic microscope system |
| CN113397476A (en) * | 2021-06-16 | 2021-09-17 | 浙大宁波理工学院 | Method for full-automatic measurement of eyeball parameters |
-
2025
- 2025-02-20 CN CN202510188484.5A patent/CN119666087A/en active Pending
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102525402A (en) * | 2012-03-01 | 2012-07-04 | 浙江工业大学 | Optical system and optometry method of computer optometer |
| 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 |
| CN206920338U (en) * | 2017-07-05 | 2018-01-23 | 广东欧谱曼迪科技有限公司 | An optical coherent confocal endoscopic microscope system |
| CN113397476A (en) * | 2021-06-16 | 2021-09-17 | 浙大宁波理工学院 | Method for full-automatic measurement of eyeball parameters |
Non-Patent Citations (1)
| Title |
|---|
| 李坤成: "严重急性呼吸综合征的影像诊断研究", 28 February 2005, 科学技术文献出版社, pages: 139 - 141 * |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN120167881A (en) * | 2025-05-23 | 2025-06-20 | 中国科学院苏州生物医学工程技术研究所 | OCT reference arm with adjustable integrate in operation microscope |
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