CN112244756B

CN112244756B - Multifunctional full-automatic ophthalmic measurement method and system

Info

Publication number: CN112244756B
Application number: CN202011119620.9A
Authority: CN
Inventors: 何卫红; 李鹏; 蔡守东; 冉东梅
Original assignee: Shenzhen Certainn Technology Co Ltd
Current assignee: Shenzhen Certainn Technology Co Ltd
Priority date: 2020-10-19
Filing date: 2020-10-19
Publication date: 2024-03-15
Anticipated expiration: 2040-10-19
Also published as: CN112244756A

Abstract

The invention discloses a multifunctional ophthalmic full-automatic measurement method and a system, wherein the method comprises the following steps: after the eye to be detected is monitored to be positioned right in front of the eye-receiving objective lens, the three-dimensional movement control unit is regulated so as to automatically regulate the probe assembly; the control device in the main body module drives the first mobile control unit to control the insertion lens of the anterior ocular segment OCT to be inserted into the light path or removed out of the light path and adjust the light path adjusting device, the measuring light provided by the main body module enters the eye to be measured and is focused in the anterior ocular segment or the fundus of the eye to be measured to return an anterior ocular segment light signal or a posterior ocular segment light signal to be transmitted to the main body module, and the main body module provides reference light and can utilize the reference light to interfere with the anterior ocular segment light signal or the posterior ocular segment light signal and collect anterior ocular segment interference light signals or posterior ocular segment interference light signals obtained through interference so as to respectively collect and obtain an anterior ocular segment OCT image or a posterior ocular segment OCT image of the eye to be measured. The invention not only can improve the convenience of measurement, but also can improve the accuracy of measurement.

Description

Multifunctional full-automatic ophthalmic measurement method and system

Technical Field

The invention relates to the technical field of photoelectrons, in particular to a multifunctional ophthalmic full-automatic measurement method and system.

Background

The ophthalmic examination includes visual examination and ophthalmic disease examination, both of which require detection of an eye to be examined by an ophthalmic detection apparatus, and then output related data, which is then judged or diagnosed by a doctor. The relevant data includes sphere power, cylinder power, axial position, eye axial length, anterior and posterior surface curvature of cornea, cornea thickness, anterior chamber depth, lens thickness, anterior and posterior surface curvature of lens, white-to-white distance, pupil diameter, etc. When the eye diseases are required to be treated, more data are often required to assist in calculating a better treatment formula. At this time, a doctor is required to operate the detection device for multiple times to perform multiple times of detection, and the detection stage can be started only by relying on manual adjustment of the doctor to find the detection position of the eye to be detected, and multiple times of manual adjustment are required to find the detection position of the eye to be detected, and the speed of manual adjustment depends on the operation experience of the doctor and the proficiency of the detection device, so that the whole detection process is complicated and inconvenient.

In addition, today, the elderly suffering from cataract eye diseases are more and more, and the transplantation of intraocular lenses is an effective scheme for treating cataract which is widely used at present. However, the parameters required for calculation of the intraocular lens are more demanding, such as cornea anterior and posterior surface curvature, cornea thickness, anterior chamber depth, lens thickness, lens anterior and posterior surface curvature, eye axis length, white-to-white distance, pupil diameter, etc. The measured parameters are more, but a plurality of medical devices are often needed to detect the measured parameters, so that the complete data can be obtained.

Optical coherence tomography (OCT, optical Coherence Tomography) is an emerging optical imaging technique, and compared with the traditional clinical imaging means, has the advantages of high resolution, high imaging speed, no radiation damage, moderate price, compact structure and the like, and is an important potential tool for basic medical research and clinical diagnosis application. Currently, among a variety of ophthalmic apparatuses using optical instruments, OCT apparatuses for ophthalmic examination and treatment have become an ophthalmic apparatus indispensable for diagnosis of ophthalmic diseases. However, the current OCT apparatus is complicated in specialized operation, doctors need specialized training to operate, and the operation process is complicated and has a great influence on the detection quality and feasibility if the operation process is not adjusted in the initial stage.

The foregoing background is only for the purpose of facilitating an understanding of the principles and concepts of the invention and is not necessarily in the prior art to the present application and is not intended to be used as an admission that such background is not entitled to antedate such novelty and creativity by the present application without undue evidence prior to the present application.

Disclosure of Invention

In order to solve the technical problems, the invention provides a multifunctional full-automatic ophthalmic measuring method and system, which can automatically obtain a plurality of data to be measured by only one device, and can improve the convenience and the accuracy of measurement for the detection of patients.

In order to achieve the above purpose, the present invention adopts the following technical scheme:

one embodiment of the invention discloses a multifunctional ophthalmic full-automatic measurement method, which adopts a multifunctional full-automatic measurement system to perform measurement, wherein the multifunctional full-automatic measurement system comprises a main body module, a probe assembly and a three-dimensional movement control unit, the main body module comprises a control device, the probe assembly is arranged on the three-dimensional movement control unit to adjust the three-dimensional position of the probe assembly through the three-dimensional movement control unit, the probe assembly comprises an optical path adjusting device, an optical path scanning device (1109), a posterior segment OCT field lens (1301), an anterior segment OCT insertion lens (1501), a prepositive dichroic mirror (1303), an eye objective lens (1305) and a first movement control unit, and the anterior segment OCT insertion lens (1501) is arranged on the first movement control unit so that the anterior segment OCT insertion lens (1501) can be inserted into an optical path or removed out of the optical path; the multifunctional ophthalmic full-automatic measurement method comprises the following steps: s1: after the eye to be detected is monitored to be positioned right in front of the eye-receiving objective lens (1305), a control device in the main body module adjusts the three-dimensional movement control unit according to the position of the eye to be detected so as to automatically adjust the probe assembly; s2: the control device in the main body module drives the first movement control unit to control the insertion of the anterior ocular segment OCT insertion mirror (1501) into a light path and adjust the light path adjusting device, measurement light provided by the main body module passes through the light path adjusting device, the light path scanning device (1109) reflects the measurement light and then passes through the posterior ocular segment OCT field mirror (1301) and the anterior ocular segment OCT insertion mirror (1501), the measurement light is reflected by the anterior dichroic mirror (1303) to the eye objective lens (1305) to enter an eye (E) to be measured and is focused in the anterior ocular segment to be measured so as to return an anterior ocular segment light signal to be transmitted to the main body module, and the main body module provides reference light and can utilize the reference light to interfere with the anterior ocular segment light signal and collect an anterior ocular segment interference light signal obtained through interference so as to acquire an anterior ocular segment OCT image of the eye (E) to be measured; s4: the control device in the main body module drives the first movement control unit to control the OCT insertion lens (1501) to move out of a light path and adjust the light path adjusting device, measuring light provided by the main body module passes through the light path adjusting device, passes through the OCT field lens (1301) after being reflected by the light path scanning device (1109), then is reflected to the eye objective lens (1305) by the front dichroic mirror (1303) to enter an eye to be detected (E) and is focused in the eye fundus (Er) to be detected so as to return an optical signal of the eye back section to be transmitted to the main body module, and the main body module can utilize the reference light and the optical signal of the eye back section to interfere and collect the interference optical signal of the eye back section obtained by interference so as to collect and obtain an OCT image of the eye to be detected (E).

Another embodiment of the invention discloses a multifunctional ophthalmic full-automatic measurement system, comprising a main body module, a probe assembly and a three-dimensional movement control unit, wherein the probe assembly is installed on the three-dimensional movement control unit to adjust the three-dimensional position of the probe assembly through the three-dimensional movement control unit, wherein: the probe assembly comprises an optical path adjusting device, an optical path scanning device (1109), a posterior segment OCT field lens (1301), an anterior segment OCT insertion lens (1501), a front dichroic mirror (1303), an eye objective lens (1305) and a first movement control unit, wherein the anterior segment OCT insertion lens (1501) is arranged on the first movement control unit so that the anterior segment OCT insertion lens (1501) can be inserted into an optical path or removed out of the optical path; when the first movement control unit controls the insertion of the anterior ocular segment OCT insertion mirror (1501) into an optical path, measuring light provided by the main body module passes through the optical path adjusting device, passes through the posterior ocular segment OCT field mirror (1301) after being reflected by the optical path scanning device (1109), and the anterior ocular segment OCT insertion mirror (1501), and then is reflected by the prepositive dichroic mirror (1303) to the eye objective lens (1305) to enter an eye (E) to be tested and focus in the anterior ocular segment to be tested so as to return an anterior ocular segment light signal to be transmitted to the main body module, and the main body module provides reference light and can utilize the reference light to interfere with the anterior ocular segment light signal and collect an anterior ocular segment interference light signal obtained through interference so as to obtain an anterior ocular segment OCT image of the eye (E) to be tested; when the first movement control unit controls the OCT insertion mirror (1501) to move out of the optical path, the measuring light provided by the main body module passes through the optical path adjusting device, passes through the OCT field mirror (1301) after being reflected by the optical path scanning device (1109), then is reflected by the front dichroic mirror (1303) to the eye objective (1305) to enter the eye (E) to be tested and is focused in the fundus (Er) of the eye to be tested so as to return an optical posterior segment light signal to be transmitted to the main body module, and the main body module can utilize the reference light to interfere with the optical posterior segment light signal and collect the optical posterior segment interference light signal obtained through interference so as to obtain an optical posterior segment OCT image of the eye (E) to be tested.

Compared with the prior art, the invention has the beneficial effects that: the multifunctional ophthalmic full-automatic measurement system disclosed by the invention is provided with the anterior ocular segment OCT insertion mirror, the anterior ocular segment OCT insertion mirror is arranged on the first mobile control unit, and the first mobile control unit can be driven by the control device in the main body module to quickly control whether the anterior ocular segment OCT insertion mirror is inserted into a light path, so that the switching of an anterior ocular segment OCT imaging system and a posterior ocular segment OCT imaging system can be quickly realized, the improvement of the anterior ocular segment OCT imaging quality is facilitated, and the rapid switching of anterior ocular segments and posterior ocular segments can be realized only by adopting one mobile control unit, so that the cost is low; the optical constant path surface is positioned on the retina of the human eye during OCT imaging of the posterior segment of the eye, and the optical constant path surface is positioned on the anterior segment of the human eye during OCT imaging of the anterior segment of the eye, so that OCT imaging of different parts can be realized without adjusting the optical path of a reference arm, and a plurality of data needing to be measured can be rapidly and accurately measured.

In a further scheme, the invention has the following beneficial effects:

(1) The oblique angle anterior ocular segment camera module is arranged below the eye objective lens, so that the anterior ocular segment camera module can assist in positioning of the eye to be measured, and the iris or pupil position can be searched preliminarily by means of the oblique angle anterior ocular segment camera module, so that the influence of eye movement is avoided, and the measurement result of the eye data to be measured is more accurate.

(2) An iris shooting module is also arranged in the measurement system, and can be combined with an iris automatic recognition technology for controlling the movement of the probe assembly so as to realize the detection of eyes to be detected; the obtained iris image can measure parameters such as pupil diameter, white-to-white distance and the like.

(3) The measuring system is also provided with a fixation optical module, so that a fixation optical path of eyes can be realized to meet the fixation of left and right eyes.

(4) The eye receiving objective lens and the oblique angle anterior segment photographing module are relatively and fixedly arranged on the second movement control module and can move along the direction of the optical path from the measuring light to the eye to be measured, so that refraction compensation can be carried out on eyes with different eyesight, and eye imaging of different parts is realized. Further, the diopter adjusting device is shared by the fixation optical module and the OCT imaging of the posterior segment of the eye, so that moving parts of the fixation optical path are reduced, confocal of the fixation optical path and the OCT optical path of the posterior segment of the eye is realized, and fixation of the eye of a person to be tested and acquisition of OCT images of the posterior segment of the eye are facilitated.

(5) The refraction measuring module is further arranged in the measuring system, so that the refraction of the eye to be measured can be measured by combining the refraction measuring technology, and the refraction measuring module is used for guiding OCT imaging of the posterior segment of the eye or refraction adjustment of a fixation optical path, and therefore the signal-to-noise ratio of OCT images of the posterior segment of the eye and the definition of fixation marks are improved.

(6) On the basis of the multifunctional ophthalmic full-automatic measurement system, on one hand, the rapid switching function can be realized, the measurement of different depths of the eye to be measured is realized, the detection range (front and rear section imaging) of the OCT system is improved, the switching system is stable, the positioning is accurate, and the signal to noise ratio of the system is not influenced; on the other hand, the optical beams can be focused at different positions respectively, high-quality OCT imaging of different positions can be realized for eyes with different eyesight, and the optical imaging device has higher transverse resolution. Numerous parameter data of the human eye, such as cornea curvature, cornea thickness, anterior chamber depth, lens thickness, lens surface curvature, white-to-white distance, pupil diameter, etc., can be obtained by rapidly switching the anterior-posterior segment imaging OCT system. Further, the automatic detection of the instrument can be assisted by combining the anterior ocular segment photographing and automatic identification technology. The diopter of the eye to be measured can be measured by combining with a diopter measurement technology, and the diopter adjustment in the OCT acquisition process of the posterior segment of the eye is guided, so that a stronger and better OCT image of the posterior segment of the eye is obtained. The full-automatic detection of the system is realized through the iris recognition technology, the automatic refraction measuring technology, the anterior segment OCT image automatic recognition technology, the posterior segment OCT image automatic recognition technology and the like.

(7) The invention discloses a multifunctional ophthalmic full-automatic measurement method, which comprises the steps of automatically sensing an eye to be measured by detection equipment and judging whether the eye to be measured is positioned on a detection station; the position of the eye to be measured is automatically judged by the detection equipment based on the settings of the first mobile control unit, the OCT insertion mirror for the anterior ocular segment, the oblique anterior ocular segment camera module, the iris camera module, the refraction measuring module and the like; the automatic adjusting system automatically adjusts the position of the eye to be detected and/or at least one part of the detecting equipment according to the position of the eye to be detected by the detecting equipment so that the eye to be detected is automatically matched with the detecting system of the detecting equipment, and the eye to be detected is in a detecting state; and then entering a detection stage, namely automatically starting a detection system of the detection equipment to automatically detect the eye to be detected, so that the whole detection flow is realized through automation, and the method is quick and convenient. The automatic matching of the eyes to be detected and the monitoring equipment is automatically completed by automatically detecting whether the eyes to be detected arrive at the station, so that the detection flow is simplified, accurate data of a plurality of important human eye parameters can be obtained, and the clinical diagnosis requirement of doctors is met. The OCT ophthalmic device can be made possible to be applied to more application scenarios (such as community, telemedicine).

(8) The multifunctional ophthalmic full-automatic measurement system is used for full-automatic measurement, can collect images of front and rear sections in one measurement, is beneficial to doctor operation, improves diagnosis speed and improves doctor-patient interaction experience. Has the advantages of low cost, high speed, high precision, multifunction and the like.

(9) Compared with a time domain system, the scheme of the invention adopts a frequency domain optical coherence tomography technology, has high scanning imaging speed and imaging resolution, but has shallow detection depth; compared with the scanning frequency domain optical coherence tomography, the scanning speed, the resolution and the like are equivalent, the cost is much lower, but the detection depth is shallow.

Drawings

FIG. 1 is a schematic structural view of a multifunctional ophthalmic fully automatic measurement system according to a preferred embodiment of the present invention;

FIG. 2 is a schematic diagram of the structure of an OCT imaging system for the posterior segment of the eye;

FIG. 3 is a schematic diagram of the structure of an anterior ocular segment OCT imaging system;

FIG. 4 is a schematic diagram of the structure of the diopter measurement system;

FIG. 5a is a front view of the iris camera module configuration;

FIG. 5b is a top view of the optical path structure of the iris camera module;

FIG. 6 is a schematic view of the structure of an oblique anterior ocular segment camera module;

FIG. 7 is a schematic view of a fixation optical module;

FIG. 8 is a partial flow diagram of a multi-functional ophthalmic fully automated measurement method according to a preferred embodiment of the present invention;

FIG. 9 is a block diagram of an implementation of a multi-functional ophthalmic full-automatic measurement method;

FIG. 10 is a block diagram of a specific architecture of an implementation of a multi-functional ophthalmic fully automated measurement method;

FIG. 11 is a block diagram of an implementation of automatic sensing of an eye under test;

FIG. 12 is a schematic flow chart of an automatic sensing eye to be tested;

FIG. 13 is a flow chart of eye adjustment to be measured;

FIG. 14 is a flow diagram of a back-and-forth adjustment of a probe assembly;

fig. 15 is a flow chart of pupil centering;

FIG. 16 is a schematic flow chart of controlling the movement of the motors up, down, left and right;

fig. 17 is a flow chart of the centralized monitoring.

Detailed Description

The invention will be described in further detail with reference to the following detailed description and with reference to the accompanying drawings. Wherein like reference numerals refer to like parts throughout unless otherwise specified. It should be emphasized that the following description is merely exemplary in nature and is in no way intended to limit the scope of the invention or its applications.

The invention will be better understood by the following detailed description of specific embodiments with reference to the accompanying drawings, but the following examples do not limit the scope of the invention. In addition, it should be noted that the illustrations provided in the following embodiments merely illustrate the basic concept of the present invention by way of illustration, and only the components related to the present invention are shown in the drawings rather than being drawn according to the number, shape and size of the components in actual implementation, and the shapes, numbers and proportions of the components in actual implementation may be arbitrarily changed, and the layout of the components may be more complicated.

It is to be understood that the terms "upper," "lower," "front," "rear," "inner," "outer," "left," "right," and the like indicate or are based on the orientation or positional relationship shown in the drawings, merely to facilitate describing embodiments of the present invention and to simplify the description, and do not indicate or imply that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and thus should not be construed as limiting the present invention.

As shown in fig. 1, the preferred embodiment of the present invention discloses a multifunctional ophthalmic full-automatic measurement system, which comprises a main body module, a probe assembly 10 and a three-dimensional movement control unit (not shown in the figure), wherein the probe assembly 10 is mounted on the three-dimensional movement control unit to adjust the three-dimensional position of the X/Y/Z axis of the probe assembly by the three-dimensional movement control unit, wherein the X axis is defined as an axis perpendicular to the paper surface, the Y axis is defined as an axis parallel to the paper surface in the up-down direction, and the Z axis is defined as an axis parallel to the paper surface in the left-right direction, that is, the X axis and the Y axis directions refer to the horizontal axis and the vertical axis direction on a plane parallel to the outer surface of an eye (E) to be measured, respectively, and the Z axis direction refers to a direction perpendicular to a plane parallel to the outer surface of the eye (E) to be measured.

The main body module comprises an OCT light source 1101, a fiber coupler 1103, a detector 1141, a computer 1143, a polarization controller 1105, and a reference arm module comprising a reference arm optical path lens 1121 and a reference arm mirror 1123; the computer 1143 is not a PC computer in a conventional sense, but is a control device capable of performing a set of functions such as operation, control, storage, display, and the like.

The probe assembly 10 includes an optical path adjusting device, an optical path scanning device 1109, an optical path scanning device 1301, an optical path scanning device 1109, an optical path scanning device 1501, a front-eye OCT insertion lens 1501, a front dichroic mirror 1303, an objective lens 1305, an oblique anterior-eye imaging module, an iris imaging module, a fixation optical module, a refraction measuring module, a first movement control unit (not shown), a second movement control unit (not shown), a third movement control unit (not shown), and a rotation control unit (not shown), wherein the optical path scanning device 1109 adopts a two-dimensional scanning mechanism, and is composed of an X-axis direction scanning device 11091 and a Y-axis direction scanning device 11093.

The optical path adjusting device comprises an optical fiber collimating lens 1107 and an optical fiber head (not shown in the figure), the oblique anterior ocular segment imaging module comprises an oblique anterior ocular segment imaging lens 1801 and an oblique anterior ocular segment imaging device 1803, the iris imaging module comprises an illumination light source 1901, an iris fixation relay lens 1903, an iris fixation spectroscope 1905, an iris imaging lens 1907 and an iris imaging device 1909, the fixation optical module comprises a fixation light source 1701 and a fixation optical path lens 1703, and the refraction measuring module comprises a refraction spectroscope 1401, a first refraction lens 1403, a second refraction lens 1405, a micro-lens array element 1407 and a refraction imaging device 1409; the first movement control unit is connected with the anterior ocular segment OCT insertion mirror 1501 to control the anterior ocular segment OCT insertion mirror 1501 to be inserted into or removed out of the optical path, the objective lens 1305 and the oblique anterior ocular segment camera module are relatively fixed to form a combined module 18 together, and the second movement control unit is connected with the combined module 18 to control the combined module to be capable of moving along the Z-axis direction so as to realize refractive adjustment; the third movement control unit is connected with the optical fiber collimating mirror 1107 to control the optical fiber collimating mirror 1107 to move along the direction of the optical path so as to change the optical path of the sample arm; the rotation control unit is connected to the refractive beam splitter 1401 to control the refractive beam splitter 1401 to be capable of rotating into the optical path between the optical path scanning device 1109 and the posterior segment OCT field lens 1301 or moving out of the optical path between the optical path scanning device 1109 and the posterior segment OCT field lens 1301.

The first movement control unit is controlled by the computer 1143 to drive the insertion or removal of the optical anterior segment OCT insertion mirror 1501 into or out of the optical path, and the third movement control unit is controlled to drive the optical fiber collimating mirror 1107 to translate along the optical axis, so that optical path switching and OCT imaging of different parts of the eye to be detected are realized. The OCT light source 1101 adopts a weak coherent light source, and outputs near infrared light with a wavelength, and specifically, an infrared light source with a certain bandwidth, such as a superluminescent diode SLED, with a center wavelength of 840nm, or an infrared light source with a certain bandwidth, such as a sweep light source, with a center wavelength of 1050nm, can be selected. Measurement light from the OCT light source 1101 provides light through the fiber coupler 1103 to the reference arm module and sample arm module, which has a known length and reflects the light back into the fiber coupler 1103 through the reference arm mirror 1123. The sample arm module provides light for the eye to be tested E, the light scattered back from the eye to be tested E is interfered in the optical fiber coupler 1103 by the light reflected back from the sample arm, the polarization controller 1105 and the reference arm module, the interfered light is detected by the detector 1141, and then the interfered light is processed by the computer 1143, and finally an OCT image of the eye to be tested E is displayed; wherein the eye E to be measured is scanned by the optical path scanning device 1109, so as to realize the tomographic imaging of OCT.

As shown in fig. 2, the multifunctional ophthalmic fully automatic measurement system according to the preferred embodiment of the present invention can be used as an OCT imaging system for the posterior segment of the eye, where the optical fiber collimator 1107, the optical path scanning device 1109, the OCT field lens 1301, the front dichroic mirror 1303, and the objective lens 1305 together form an OCT sample arm module for the posterior segment of the eye. The optical path scanning device 1109 may be a one-dimensional optical path switching scanning device, or may be two-dimensional or even three-dimensional, that is, the optical path scanning device 1109 may realize one-dimensional to multi-dimensional scanning of the eye E to be measured. The fiber collimator 1107 is connected to the sample arm fiber, and the whole is driven by a third motion control unit, which may be a motor, and can translate along the optical axis thereof, so as to change the optical path of the sample arm optical path. When performing posterior ocular segment OCT imaging, light output by the OCT light source 1101 supplies light to the sample arm module and the reference arm module via the fiber coupler 1103. Wherein the light transmitted by the OCT sample arm module of the anterior ocular segment is emitted by the optical fiber collimating mirror 1107 and reflected by the optical path scanning device 1109; at this time, the optical path scanning device 1109 is controlled by the computer 1143, and the light beam passes through the optical path scanning device 1109, then passes through the optical coherence tomography field lens 1301, then passes through the front dichroic mirror 1303, and finally passes through the eye E, and finally is converged to the eye fundus Er. The detection light beam of the OCT imaging light path system of the posterior segment of the eye meets the requirement that the central line of the scanning light beam is converged near the pupil of the human eye, and the OCT light beam is focused on the fundus Er of the human eye at any moment. For different eyes (with different diopters), the second movement control unit is used for adjusting the eye objective 1305, so that OCT light beams can be converged on the eye fundus Er of the eyes, namely, the light beams are focused on the retina, and the signal-to-noise ratio and the transverse resolution of OCT images can be effectively improved during retina measurement. The front dichroic mirror 1303 reflects the signal light emitted from the OCT light source 1101, transmits the fixation light emitted from the fixation light source 1701 in the fixation optical module 170, and also transmits the illumination light emitted from the illumination light source 1901 in the iris imaging module. The anterior ocular segment OCT insertion mirror 1501 is controlled by the computer 1143 to switch out the posterior ocular segment OCT imaging optical path. In addition, the refraction spectroscope 1401 is controlled by the computer 1143 to switch out the OCT imaging light path of the posterior segment of the eye. When measuring the fundus, scanning by the scanning devices 11091 and 11093; the optical path matching for the eyeground of different eyes is realized by combining the integral translation of the sample arm optical fiber head (not shown) through the optical fiber collimating lens 1107; the eye objective 1305 translates along the optical axis to adjust and bend for different eyes; finally, the acquisition of OCT images of the posterior segment of the eye is realized, so that important parameters of human eye structures such as retina thickness and the like are obtained.

As shown in fig. 3, the multifunctional ophthalmic fully automatic measurement system according to the preferred embodiment of the present invention can be used as an anterior segment OCT imaging system, where an optical fiber collimator 1107, an optical path scanning device 1109, a posterior segment OCT field lens 1301, an anterior segment OCT insertion lens 1501, a front dichroic mirror 1303, and an eye objective 1305 together form an anterior segment OCT sample arm module. When performing anterior ocular segment OCT imaging, light output by the OCT light source 1101 supplies light to the sample arm module and the reference arm module via the fiber coupler 1103. The light transmitted through the anterior ocular segment OCT sample arm module is emitted through the optical fiber collimator 1107, reflected through the optical path scanning device 1109, transmitted through the posterior ocular segment OCT field 1301, the anterior ocular segment OCT insertion mirror 1501, reflected through the anterior dichroic mirror 1303, transmitted through the objective lens 1305, and finally converged to the anterior ocular segment through the human eye E. The detection beam of the OCT imaging optical path system of the anterior ocular segment meets the requirement that the OCT beam is focused on the anterior ocular segment of a human eye. At this time, the computer 1143 controls the first movement control unit to start inserting the anterior ocular segment OCT insertion mirror 1501 into the optical path. And the refraction spectroscope 1401 is controlled by the computer 1143 to start the rotation control unit to switch out the OCT imaging light path of the anterior segment of the eye. When the front and back surfaces of the cornea and the crystalline lens are measured, the OCT light beam is focused on the middle area of the anterior segment of the eye, and the signal to noise ratio and the transverse resolution of OCT images can be effectively improved when the front and back surfaces of the cornea and the crystalline lens are measured. When measuring the OCT image of the anterior ocular segment, scanning by an optical path scanning device 1109; the optical path matching required by OCT measurement is realized by combining the integral translation of a sample arm optical fiber head (not shown) through an optical fiber collimator 1107; focusing is achieved by translation of the objective 1305 along the optical axis. The anterior segment sample arm module can obtain OCT images of the front and back surfaces of cornea and lens, so that important parameters of the structure of human eye such as the curvature of the front and back surfaces of cornea, the thickness of cornea, the depth of anterior chamber, the thickness of lens, the curvature of the front and back surfaces of lens and the like can be obtained.

As shown in fig. 4, the multifunctional ophthalmic full-automatic measurement system according to the preferred embodiment of the present invention can be used as a refractive power measurement system, wherein the refractive spectroscope 1401, the first refractive lens 1403, the second refractive lens 1405, the microlens array element 1407 and the refractive image pickup device 1409 together form a refractive power measurement module, and the refractive spectroscope 1401 in the refractive power measurement module is inserted into the optical path between the optical path scanning device 1109 and the posterior segment OCT field lens 1301 in the posterior segment OCT imaging system through the rotation control unit, thereby forming the refractive power measurement system. Wherein the refractive beam splitter 1401 is controlled by the computer 1143 to rotate the control unit to switch into the refractive measuring light path. Light from the OCT light source 1101 is split by the fiber coupler 1103, and part of the light enters the sample arm optical path, and the polarization state is adjusted by the polarization controller 1105, and the light path is reflected by the optical path scanning device 1109. The light then passes through a refractive beam splitter 1401, which is partially reflected and partially transmitted. Part of the light transmitted through the optical coherence tomography field lens 1301 passes through the front dichroic mirror 1303, is reflected to the objective lens 1305, and finally enters the fundus Er of the human eye through the human eye E. After the fundus reflects the light, the light returns along the original path, passes through the eye E and the objective lens 1305, is reflected by the front dichroic mirror 1303, passes through the optical coherence tomography field 1301, and enters the refractive beam splitter 1401. At this time, the return light is split by the refractive beam splitter 1401, and a part of the reflected light is diverted to the first refractive lens 1403, passes through the first refractive lens 1403, the third refractive lens 1405, and the microlens array element 1407, and is captured by the refractive imaging device 1409. The computer 1143 calculates the diopter of the eye to be measured from the photographed fundus reflex image. The calculated refraction principle adopts the SHACK-HARTMANN wave-front measuring principle. The diopter measurement module 140 utilizes the OCT light source 1101 as a light source, saves the cost of the light source, and simplifies the light path structure. When the refraction measuring module 140 works, the optical path scanning device 1109 needs to be in a set working position, so that the light of the OCT light source 1101 of the optical path scanning device 1109 is along the upper graph optical axis. The refractive beam splitter 1401 is cut into the optical path by a shutter switching device (not shown) for splitting. The refractive beam splitter 1401 may employ a partial beam splitter design or a polarizing beam splitter design. The objective 1305 needs to be moved to a set working position when the diopter measurement is performed, for example, the working position when the diopter adjustment state is 0 diopter.

Fig. 5a and 5b show an iris imaging module, wherein an illumination light source 1901, an iris gaze relay lens 1903, an iris gaze spectroscope 1905, an iris imaging lens 1907 and an iris imaging device 1909 together form the iris imaging module. The module can be used for iris preview so as to guide doctors to operate instruments and lead the probe light path to be aligned with eyes to be detected; or automatically identifying the center position of the iris for guiding the probe assembly 10 to automatically perform three-dimensional movement, so as to realize the alignment of pupils of eyes to be detected, thereby realizing the detection of the eyes to be detected. The light emitted from the illumination light source 1901 (infrared light) irradiates the anterior chamber of the eye E to be measured, the light is reflected by the tissue of the anterior chamber, and the reflected light passes through the objective lens 1305 and the front dichroic mirror 1303, passes through the iris fixation relay lens 1903, is transmitted through the iris fixation spectroscope 1905, passes through the iris imaging mirror 1907, and is finally imaged by the iris imaging device 1909. The examinee uses a chin rest (not shown) to fix the examinee's head and to fix the eye of the examinee by fixing the fixation mark of the eye fixation system. Then, the detector controls the movement of the chin rest apparatus, the probe assembly 10, etc. by the joystick while observing the display screen of the computer 1143, so that the iris of the eye E to be measured enters the iris imaging apparatus 1909, and the anterior ocular segment is presented in the display screen of the computer 1143. Or automatically identifying the center position of the iris for guiding the probe assembly 10 to automatically perform three-dimensional movement, so as to realize the alignment of pupils of eyes to be detected, thereby realizing the detection of the eyes to be detected. The iris camera module can obtain important parameters of human eye structures such as white-to-white distance, pupil diameter and the like. The distribution of the illumination sources 1901 in fig. 5b is only shown, and other distribution methods can be adopted, only the illumination sources 1901 illuminate the anterior segment of the eye to be measured, and the number can be 1 or more.

As shown in fig. 6, an oblique anterior ocular segment image capturing module is illustrated, where the oblique anterior ocular segment image capturing lens 1801 and the oblique anterior ocular segment image capturing device 1803 together form an oblique anterior ocular segment image capturing module, and the oblique anterior ocular segment image capturing module is relatively fixed to the objective lens 1305, that is, the objective lens 1305 and the oblique anterior ocular segment image capturing module together form a combined module 18. The combination module 18 is driven by a second motion control unit, which may be a motor, capable of moving in the Z-axis direction to achieve refractive adjustment. The light emitted from the illumination light source 1901 (infrared light) is irradiated to the anterior chamber of the eye E to be measured, and the light is reflected by the tissue of the anterior chamber. The reflected light passes through the oblique anterior ocular segment imaging lens 1801 and is finally captured by the oblique anterior ocular segment imaging device 1803. The oblique anterior ocular segment imaging module is disposed below the objective lens 1305, for example, the oblique anterior ocular segment imaging module may be disposed at the left lower side, the right lower side or directly below the objective lens 1305, preferably directly below, if disposed at the left/right side of the X direction of the probe assembly 10, it is unfavorable for the use of both eyes together, and if disposed above the objective lens 1305, it is easily shielded by eyelid. Specifically, the optical path formed by the eye to be tested E to the oblique anterior segment image pickup device 1803 forms a preset angle, for example, 45 ° with the optical path between the eye to be tested E and the objective lens. The oblique anterior ocular segment camera module has larger shooting range and depth of field compared with the iris camera module, but has slightly poorer imaging resolution compared with the iris camera module. In contrast, the iris imaging module adopts a coaxial design, but its imaging range is limited by other optical paths in the probe assembly 10, especially the working distance, so that its imaging range is small. In addition, the iris imaging module is also used for measuring data such as iris diameter, pupil diameter and the like, so that the iris imaging module is required to have higher imaging quality, the resolution is improved, and the depth of field is limited to a certain extent. When the probe assembly 10 moves in a large range back and forth along the Z-axis direction, the multifunctional ophthalmic full-automatic measurement system of the preferred embodiment of the present invention introduces an oblique anterior ocular segment imaging module because the anterior ocular segment imaged by the probe assembly is not clear enough and the iris or pupil position anomaly is easily identified automatically. Therefore, the system can initially search the iris or pupil position by means of the images shot by the oblique anterior ocular segment shooting module, but accurately positions the center of the iris or pupil, adopts the iris shooting module, and can avoid the problems of limited depth of field of the iris shooting module or insufficient definition of shot anterior ocular segment shooting and the like by combining the iris shooting module and the oblique anterior ocular segment shooting module. Because the lens is in oblique angle distribution, the oblique angle anterior segment photographing module can further judge the Z-axis direction position of the eye E to be detected by combining with the iris photographing module, and the auxiliary probe assembly 10 adjusts the working position of the eye E to be detected.

Fig. 7 shows a fixation optical module, in which a fixation light source 1701 and a fixation optical path lens 1703 together constitute the fixation optical module. The fixation light source 1701 in the fixation optical module 170 is used for fixation marks (internal fixation marks) for fixation of the eye E to be measured. Light from the fixation light source 1701 is reflected by the iris fixation beam splitter 1905 through the fixation light path lens 1703, transmitted through the iris fixation relay mirror 1903 and the front dichroic mirror 1303, and then enters the eye E to be inspected through the objective lens 1305; finally, the internal fixation index is projected onto the fundus Er of the human eye E to be inspected. The fixation light source 1701 may employ a single point LED, or an LCD screen, an OLED screen, or an LED array screen, or the like. When fundus OCT imaging is carried out, when different eyes observe the fixation point, the definition degree of the fixation point is different, which causes discomfort to a tested person in fixation, and is inconvenient for fixation and fixation of the tested eye. In the preferred embodiment of the invention, the fundus OCT optical path can be focused on the fundus retina Er after being adjusted and bent by the eye objective 1305, namely, the human eye can see clear scanning lines; and because the OCT optical path and the fixation optical path of the posterior segment share the eye objective 1305, the fixation target can be seen clearly for different eyes.

The invention adopts the OCT system with rapid switching of front and rear segments, combines the technology of photographing and automatic identification of front segments of eyes and the technology of refraction measurement, and can solve the detection of numerous optical parameters of human eyes, thereby meeting the measurement requirements of different parts, obtaining accurate data of numerous important parameters of human eyes and meeting the clinical diagnosis requirements of doctors. The full-automatic detection of the system is realized through the iris recognition technology, the automatic refraction measuring technology, the anterior segment OCT image automatic recognition technology, the posterior segment OCT image automatic recognition technology and the like. By adopting the automatic detection method, the detection operation can be simplified, the detection time can be reduced, and the detection quality and feasibility can be improved. Therefore, the multifunctional ophthalmic full-automatic measurement system disclosed by the preferred embodiment of the invention can realize a multifunctional ophthalmic full-automatic measurement method, and a specific full-automatic detection scheme is as follows.

As shown in fig. 8, the multifunctional ophthalmic full-automatic measurement method includes: automatic sensing eye to be detected 001, motor reset 002, eye to be detected adjustment 003, probe assembly front-back adjustment 004, pupil centering 005, pupil monitoring 006 and automatic scanning detection 007. As shown in fig. 9, the multifunctional full-automatic ophthalmic measurement method is implemented by an electronic control component C01, an automatic control unit C02 and an automatic detection program C03, wherein the electronic control component C01 is a hardware module and comprises a pressure sensor, a three-dimensional movement control unit (comprising an up-down motor, a left-right motor and a front-back motor), a first movement control unit (comprising a front-back electricity-saving magnet), a second movement control unit (comprising a diopter motor), a third movement control unit (comprising an optical path motor) and a polarization motor. The automatic control unit C02 is a micro control unit MCU, the automatic control unit C02 is connected with and communicated with the hardware module C01, and the automatic control unit C02 sends instructions to the hardware module C01 or reads the hardware state. The automatic control unit C02 is connected to a program host, and the automatic detection program C03 runs on the program host. The automatic control unit C02 and the program host are part of the computer 1143, and the automatic detection program C03 is a program running in the computer 1143. As shown in fig. 10, the automatic detection program C03 includes: acquisition program C04, automatic control program C05. The automatic control program C05 comprises an automatic sensing eye to be tested 001 and an automatic control module. The automatic control module comprises a motor reset 002, eye adjustment 003 to be detected, front and back adjustment 004 of a probe assembly, pupil centering 005, pupil monitoring 006 and automatic scanning detection 007, and the automatic scanning detection will not be withdrawn until all detection of the eye to be detected is completed. Further, the multifunctional ophthalmic full-automatic measurement method is realized through an acquisition unit C07, an acquisition program C04, an automatic control unit C02 and an automatic control program C05. The automatic control unit C02 and the acquisition unit C07 are both connected with a program host, and an automatic control program C05 and an acquisition program C04 are operated in the program host. The acquisition program C04 mainly controls the acquisition unit C07 to acquire acquisition images such as front and back section OCT images and iris images (images shot by an iris shooting module); the acquisition unit C07 is a hardware structure part of the multifunctional ophthalmic full-automatic measurement system in the preferred embodiment of the invention. The automatic control program C05 mainly communicates with the automatic control unit C02, and controls the electronic control unit C01. The electronic control component C01 is embedded in the acquisition unit C07, and the electronic control component C01 is electrically connected with the automatic control unit C02 and is used for controlling the automatic operation of the acquisition unit C07.

As shown in fig. 11, the auto-sensing eye 001 to be measured includes: a pressure sensor 0010, an automatic control unit 0011, and an automatic sensing module 0012. The pressure sensor 0010 is a pressure sensitive and force sensitive sensor, and the sensor is above 10 megaohms when no pressure exists, which is equivalent to open circuit; the application of different magnitudes of pressure to the sensor produces a change in resistance which is further translated into a change in voltage which is connected as an output voltage to the automatic control unit C02 via Vout. Vout of the pressure sensor 0010 is connected to an external interrupt IO port of the auto-induction control unit 0011. The connection mode between the auto-induction control unit 0011 and the external IO port of the program host can be serial ports, USB and the like. The auto-induction control module 0012 runs on a program host, and can continuously read the state of the pressure sensor through an interface of the auto-induction control unit 0011. The pressure sensor state comprises two states, namely, a non-pressure state is a non-eye state to be detected, and a pressure state is a state with pressure, namely, a state with an eye to be detected. Referring to fig. 12, the auto-sensing module 0012 starts to run when the detection system is started, and does not exit until the auto-detection program C03 ends. If the state of the pressure sensor is that the eye to be detected exists, judging whether the automatic control program C05 runs, if the automatic control program C05 does not run in a stop state, starting the automatic control module, and then entering a motor reset 002 flow. If the automatic control module is started, the eye to be detected still needs to be called to automatically sense the state of the pressure sensor read by the eye 001 to be detected, and whether the eye to be detected leaves or not is monitored. If it is detected that the eye to be tested has left, the automatic control module should be exited.

The motor reset 002 includes: left-right motor reset, up-down motor reset, front-back motor reset (i.e., three-dimensional movement control unit reset), qu Guangdian machine reset (i.e., second movement control unit reset), optical path motor reset (i.e., third movement control unit reset), polarization motor reset (i.e., control motor of polarization controller 1105 in the main body module), front-back electromagnet reset (i.e., first movement control unit reset). Wherein the motor reset 002 is that each motor moves to the program preset position. When the motor is reset, the automatic control program C04 reads the preset position of the configuration file, and calls the interface to send a motor moving instruction to the automatic control unit C02. The front and back power saving magnets can drive the eye front section OCT insertion mirror 1501 to draw out or insert the optical path, and when the automatic control module is started, the front and back power saving magnets reset the eye front section OCT insertion mirror to insert the optical path for detecting the eye front section. The polarization motor reset is to move the polarization controller 1105 to obtain an optimal polarization direction, so that the reflected light of the measuring light reflected and the reference light can generate strongest interference light, namely strongest OCT signal. The optical path motor is reset, namely the optical fiber probe and the focusing lens are horizontally moved to the position farthest from the eye to be detected, and the front section OCT signal is detected when the detection system starts. The reset of Qu Guangdian is that the diopter motor drives the diopter adjusting element (namely the combined module 18 formed by the eye objective 1305 and the oblique angle anterior segment shooting module which are fixed relatively) to move, and the Qu Guangdian machine is reset to the 0D position when the automatic control module is started. The 0D position is the default refraction degree set by the automatic control module, and the refraction adjusting element is moved to the actual refraction degree of the eye to be measured through the refraction adjusting process in the subsequent flow. In this embodiment, the diopter electro-optical machine can also be reset to the diopter position input by the user, and the automatic control module does not include the diopter adjustment flow control. The three motors are positioned below the probe assembly 10, and the three motors can move the whole probe assembly 10, so that the position of the probe assembly relative to the eye to be measured is controlled; the measuring probe is the position of the objective lens in the light path diagram. The left and right eyes are reset to independent empirical positions. The motor reset 002 is that the probe assembly is reset to the right eye measuring position of the eye to be measured. Therefore, the left motor and the right motor are reset to the right end of the device, the upper motor and the lower motor are reset to the middle position of the upper motor and the lower motor, and the front motor and the rear motor are reset to the position farthest from the eye to be measured in order to find signals from back to front in the process of analog measurement. Wherein the upper motor, the lower motor, the left motor, the right motor, the front motor, the back motor, the refractive motor, the optical path motor and the polarization motor are stepping motors which are electrically connected with the automatic control unit C02. When the motor is reset, the automatic control module calls the interface to send an instruction to the automatic control unit C02, and the automatic control unit C02 controls the motor to move. As shown in fig. 12, the start-up detection program includes: waiting for the upper eye of the eye to be tested; reading the state of the pressure sensor, judging whether an eye to be detected exists, if so, judging whether the automatic control module operates, and if not, returning to wait for the eye to be detected to go up; executing motor reset 002 when the automatic control module is judged not to be running; and when the automatic control module is operated, reading the state of the pressure sensor, judging whether an eye to be detected exists, if so, continuously reading the state of the pressure sensor, judging whether the eye to be detected exists, if not, judging whether the eye to be detected leaves, if so, exiting the automatic control module, and returning to the step of waiting for the eye to be detected to go up.

Specifically, each motor is reset and moved to a corresponding starting operating position. Wherein the motor reset contains: the control motor (polarization motor) of the polarization controller 1105, the X/Y/Z three-dimensional movement control motor (left-right motor, up-down motor, front-back motor) of the probe assembly 10, the combination module 18 adjusts the bending control motor (Qu Guangdian machine), the optical fiber collimator 1107 adjusts the optical fiber control motor (optical path motor), the refractive spectroscope 1401 switches the control motor, the front-back power saving magnet (driving the eye front section OCT insertion mirror 1501 to move, i.e., the first movement control unit), and the like. The set initial working positions are respectively as follows: the control motor of the polarization controller 1105 causes the sample arm polarization state to be adjusted to a position such that the polarization state of the return signal light substantially coincides with the polarization state of the reference arm; the X/Y/Z three-dimensional movement of the probe assembly 10 assembly controls the motor to move to a working position from the left/right eye of the person under test if directed against the eye. The combination module 18 adjusts the flexion control motor to move to a position where the refractive state is substantially at 0D; the position of 0D is also the position of the combining module 18 when the probe light exiting the objective 1305 is collimated light. An optical path adjusting control motor of the optical fiber collimating mirror 1107 moves to a position for measuring the optical path length of the sample arm required by the OCT of the anterior segment of the eye; the shutter of the optical splitter 1401 is switched to control the motor so that the optical splitter 1401 switches out the OCT optical path of the anterior segment of the eye. The front and rear power saving magnets enable the anterior ocular segment OCT insertion mirror 1501 to be inserted into the anterior ocular segment OCT optical path. The computer 1143 controls the optical path scanning device 1109 to perform scanning, and controls the light emission of the OCT light source 1101, the fixation light source 1701, the illumination light source 1901, and the like, in preparation for acquisition.

The multifunctional ophthalmic full-automatic measurement system of the preferred embodiment of the invention is arranged on a platform, and the system also comprises a head supporting device and a pressure sensor, wherein the head supporting device comprises two cheek supports, a forehead support and two forehead support struts, the forehead support struts are fixedly arranged on the platform, and the two forehead support struts and the forehead support tail are connected into an inverted U-shaped structure; the cheek support is located in the middle of the U-shaped structure, and the lower surface of the cheek support is parallel to the forehead support. Under the detection working condition, the cheek of the detected person is supported on the cheek support, the forehead is abutted against the forehead support, at the moment, the pressure sensor can sense that the head of the detected person is arranged on the head support device, namely, the eye to be detected is arranged right in front of the eye contact objective 1305, and the oblique angle eye front section shooting module is arranged below the main lens (namely, the eye contact objective 1305) of the probe of the measurement system. The distance between the oblique anterior ocular segment camera module and the eye objective 1305 in the vertical direction is recorded as Ly, the horizontal distance between the human eye and the main lens of the probe when the detection probe extends to the forefront is recorded as Lz, and the inclination angle between the oblique anterior ocular segment camera module and the horizontal table is recorded as theta0. Radial distortion possibly exists when the oblique anterior ocular segment camera module images, and the distortion correction coefficients k1 and k2 of the oblique anterior ocular segment camera module are calculated by adopting a Zhang calibration method or other equivalent effect calibration methods. Wherein Ly, lz, theta, k1, k2 are all configured in the parameter file as parameters, each device is somewhat different, and the program is read by the automatic control module when being started. Referring to fig. 8, after the motor reset 002 is completed, the eye adjustment 003 to be measured is started. As shown in fig. 13, which is a flowchart of the eye adjustment 003, the eye adjustment 003 does not move the position of the eye, and the eye only needs to abut against the forehead support and the cheek support respectively, and then moves the pupil to the main lens imaging range of the probe of the detection device by moving the motors up, down, left and right. When the eye E to be measured is placed right in front of the objective lens 1305 (i.e. the main lens of the probe), the illumination light source 1901 projects to the eye E to be measured to form a white bright ring, and the eye to be measured adjusts 003 to move the pupil into the light spot range, so that the iris image acquired by the subsequent pupil centering 005 can be ensured to have an iris, and the success of the whole automatic control flow is ensured. The eye adjustment 003 step to be measured includes: firstly, connecting and initializing a 45-degree upward-looking camera (namely an oblique-angle anterior ocular segment shooting module), and then acquiring an imaging image of the 45-degree camera (namely the oblique-angle anterior ocular segment shooting module), wherein the imaging image is a color image; identifying pupil coordinates xy in the 45-degree camera imaging map; the 45-degree upward-looking camera (namely the oblique-angle anterior ocular segment shooting module) imaging image has radial distortion, so that the true coordinate x0 and y0 are required to be calculated through distortion correction; and then calculating motor movement offset Hx and Hy, controlling the motors to move up, down, left and right, judging whether the pupil enters a light spot or not, if so, exiting the step 003 of eye adjustment to be detected, and if not, returning to the step of obtaining an imaging image of a 45-degree camera (namely an oblique angle anterior segment imaging module).

And step 004, the front and back adjustment of the probe assembly is to move the front and back motor according to the definition of the iris image and adjust the front and back positions of the probe relative to the eye to be measured. The iris image is an eye front section image to be detected, which is acquired by the iris camera module. The iris shooting module is used for shooting images required by parameters such as pupil diameter, white-to-white distance and the like of the eye E to be detected, for example, iris images of the eye E to be detected. The iris camera module is electrically connected with the computer 1143, and the computer 1143 collects iris images of the imaging images of the anterior segment of the eye to be detected. After the acquisition procedure C04 is started, the acquired iris image is continuously read from the computer 1143. As shown in fig. 14, when the front-back adjustment 004 of the probe assembly is started, the front-back motor is started to move forward first, the iris image is continuously acquired while the front-back motor moves forward, one iris image is acquired each time, the image definition is calculated, and whether the probe adjustment is finished is judged according to the image definition. If the image is not clear enough, and the exit adjustment condition is not met, judging whether the real-time position pos of the motor reaches the empirical position stopval, and if the real-time position pos reaches the empirical position, exiting the probe assembly and adjusting 004 front and back. If the empirical position is not reached, a further iris image is obtained and sharpness calculated until it is sufficiently sharp or the empirical position is reached. In the front-back adjustment 004 of the probe assembly, the definition judgment standard of the iris image which is withdrawn from the adjustment is that the iris image can see the pupil image, so that the pupil centering 005 can be smoothly carried out when the iris image enters after the front-back adjustment 004 of the probe assembly is withdrawn. In the process of adjusting the probe assembly back and forth 004, before each iris image is acquired, whether the iris image needs to be withdrawn is judged, and if the iris image needs to be withdrawn, the probe assembly back and forth adjustment 004 is stopped directly. The need to exit includes many situations such as automatically sensing that the eye 001 under test has been detected as leaving, the user clicking a "cancel" operation in the acquisition procedure, etc. The front-back adjustment 004 of the probe assembly runs in parallel with the eye adjustment 003 to be detected, and the front-back motor is started to move forwards by the front-back adjustment 004 of the probe assembly, and meanwhile, the 45-degree upward camera is connected and initialized; and in the forward and backward movement process of the front camera and the rear camera, the imaging image of the 45-degree upward-looking camera is continuously acquired, the movement offsets Hx and Hy of the upper motor, the lower motor, the left motor and the right motor are calculated, and the upper motor, the lower motor, the left motor and the right motor are controlled to move the pupil to the imaging range of the main lens of the probe of the detection equipment.

Pupil centering 005 is to use an iris camera module to acquire an iris image and calculate offset coordinates X and Y of the pupil center and the imaging center of the iris imaging module, and guide an XY motor to move and adjust the relative up-down and left-right positions of a detection probe and an eye to be detected. As shown in fig. 15, in the process of the pupil centering 005, before an iris image is acquired, it needs to be determined whether to exit the pupil centering 005, because if the auto-sensing to-be-detected eye 001 monitors that the to-be-detected eye has left or the acquisition software C04 is clicked by the user to click a "cancel" button, the user should exit the pupil centering 005, and after exiting the pupil centering 005, the user should exit the auto-control module C07, so as to end the detection of the to-be-detected eye; then after an iris image is obtained, firstly judging whether an iris exists, if so, calculating offset coordinates X and Y of the pupil center in the iris image and the center of the iris imaging module; the center of the iris camera module is an image center point of an iris image, and the iris image center point is also the center of the eye objective lens; the aim of controlling the movement of the XY motor is to align the pupil center point with the iris image center point, essentially align the eye center point to be detected with the center of the objective lens, and the objective lens is the detection probe of the detection equipment; if the probe assembly is adjusted back and forth 004, the iris image is compared with a fuzzy algorithm to judge that no iris exists, so that a front motor and a back motor are required to be moved forward for Step pulses, and then an image is continuously acquired to judge whether the iris exists or not; if the eye position to be detected is not well placed, for example, the iris camera module shoots upper and lower eyelid, and the iris can not be found when the front and rear motors move to the forefront; in order to prevent the detection probe from being perforated, the automatic control module C07 configures a safety distance, and determines that a perforation is made once the safety distance is smaller than the safety distance; if the drilling voice prompts the eye to be measured to adjust a position, the front motor and the rear motor are retracted to the position at which the front motor and the rear motor of the probe assembly are retracted 004, namely, the pupil centering 005 is restarted; if the eye to be tested has left, the pupil will be centered in infinite loop, and the automatic detection procedure C03 will also appear as a seizing phenomenon. In order to avoid the occurrence of the accident, the automatic control module configures the maximum iris-free times max, and when the iris-centered iris image continuously cannot find the iris times more than max, the pupil centering 005 is exited, the acquisition program C04 is exited after the pupil centering 005 is exited, and the detection of the detection equipment on the eye to be detected is ended. As shown in fig. 16, the motors are controlled to move up, down, left and right, firstly, xyflag=flag is set, pupil misalignment is set by default when centering is started, and XYflag indicates whether pupil alignment is performed; for the case of misalignment xyflag=false, the alignment is calculated with smaller deviation, otherwise, the upper, lower, left and right motors are moved, and whether the alignment is performed is always judged according to the standard; after pupil alignment, xyflag=true, pupil tracking is required; after pupil alignment, the pupil centering tracking process finds that the offset is larger and the moveflag=flag, marks as the moving eye moveflag=true, waits for a period of time of about 0.5 seconds, recalculates, and if the offset is not so large, ignores the last moving eye and does not move the motor; for the aligned state, the deviation is found to be greater than a threshold value in the pupil centering tracking process and the eyes are moved (moveflag=true), which indicates that after waiting for 0.5 seconds, the eyes do not return, the current deviation is the second deviation, the mark is not aligned, and the motors are moved up, down, left and right; the upper, lower, left and right motors are electrically connected with the automatic control unit C02, and when the automatic control module needs to move the upper, lower, left and right motors, an instruction is sent to the automatic control unit C02, and the automatic control unit C02 controls the upper, lower, left and right motors to move the specified offset.

After pupil centering 005 is finished, the eye to be tested and the detection equipment probe all enter the correct position, the eye to be tested enters the detection state, the centering monitoring 006 process is started when entering the detection state, when the eye to be tested detects, the eye to be tested and the detection equipment must be in the correct position, and the function of the centering monitoring 006 process is to ensure that the eye to be tested and the detection equipment probe are in the correct position. After entering the detection stage, the detection system of the detection equipment automatically detects the eye to be detected, wherein the automatic detection comprises anterior segment OCT scanning, refractive measurement and posterior segment OCT scanning, and the automatic detection is sequentially carried out according to the time sequence; the automatic detection needs to be performed while the centering monitoring 006 is performed, and the centering monitoring 006 needs to wait until the automatic detection is completed and then exit. Because the automatic control module has been exited when the pupil centering 005 encounters an accident (the iris image has no pupil), the centering monitoring 006 does not need to consider the iris image having no pupil; but the centering monitor 006 needs to determine whether to exit the centering monitor 006, if the auto-sensing eye 001 detects that the eye has left or the collection software C04 is clicked by the user to "cancel" the button, all should exit the centering monitor 006. So as shown in fig. 17, the centered monitoring 006 process includes: and taking an iris image, calculating the pupil center and the camera center offset XY, controlling the XY motor to move, judging whether to exit centering monitoring, if so, exiting centering monitoring, and if not, returning to take the iris image.

The eye adjustment 003, the front-back adjustment 004, the pupil centering 005 and the centering monitoring 006 to be measured in the steps can be summarized as follows: after the head of the patient is fixed and the eyes of the patient are fixed. The oblique anterior ocular segment image pickup module collects oblique anterior ocular segment images, such as images containing iris and pupil of eye to be detected. The computer 1143 recognizes the iris outline or the iris center or recognizes the pupil outline or the pupil center in real time to determine the position of the eye to be measured. The reference for determining the position of the eye to be measured may be various multidimensional indexes, such as iris outline or iris center, pupil outline or pupil center, or sharpness or the like of the iris imaging of the eye to be measured (the image acquired by the oblique anterior segment of the eye imaging module 180), or others. Hereinafter collectively referred to as determination of the position of the eye to be measured. The computer 1143 also needs to determine whether the eye to be tested blinks, and perform corresponding data removal processing. The computer 1143 determines the position of the eye to be measured, and drives the X/Y/Z three-dimensional movement control motor of the probe assembly 10, so that the main optical axis L1 of the system optical path (i.e. the main optical axis of the optical path of the eye to be measured) is aligned with the pupil center of the eye E to be measured. The computer 1143 drives the X/Y/Z three-dimensional motion control motor of the probe assembly 10 assembly according to the definition, or sharpness, etc. of the E-iris image of the eye to be measured, so that the definition is optimized, or the sharpness is maximized. Because the oblique anterior segment of the eye makes a video recording the module and compares in the iris and makes a video recording the module, the oblique anterior segment of the eye makes a video recording the module and makes a video recording the scope bigger, the depth of field is bigger, but the imaging resolution ratio is slightly worse than the iris makes a video recording the module. Therefore, the system can initially search the iris or pupil position by means of the image shot by the oblique anterior ocular segment shooting module, but accurately positions the center of the iris or pupil, and adopts the iris shooting module. The iris camera module works together and collects iris images of the eye to be detected E, such as images containing the iris and pupil of the eye to be detected. After the working position of the eye E to be measured is initially positioned by the image collected by the oblique anterior ocular segment camera module, the computer 1143 determines the working position of the eye E precisely according to the iris camera module, and drives the X/Y/Z three-dimensional movement control motor of the probe assembly 10 assembly, so that the main optical axis L1 of the system optical path (i.e. the main optical axis of the optical path of the eye to be measured) is aligned to the pupil center of the eye E to be measured. The computer 1143 drives the X/Y/Z three-dimensional movement control motor of the probe assembly 10 according to the indexes such as definition, sharpness, etc. of the E-iris image (the image collected by the iris imaging module) of the eye to be detected, so that the definition is optimal, or the sharpness is highest. In the subsequent collection work, the computer 1143 needs to track the position of the eye to be detected in real time according to the iris image of the eye to be detected E collected by the iris imaging module, and drive the X/Y/Z three-dimensional movement control motor of the probe assembly 10 assembly to perform corresponding movement, so that the main optical axis L1 of the system optical path (i.e. the main optical axis of the optical path of the eye to be detected) is aligned to the pupil center of the eye to be detected E. The computer 1143 drives the X/Y/Z three-dimensional movement control motor of the probe assembly 10 assembly according to the indexes such as definition, sharpness, etc. of the E-iris imaging (the image collected by the iris imaging module) of the eye to be detected in real time, so that the definition is optimal, or the sharpness is highest.

The automatic scan detection 007 specifically includes the following steps in order: the method comprises the steps of OCT acquisition of anterior ocular segment, refraction measurement, OCT acquisition of posterior ocular segment and rapid switching of OCT acquisition of anterior ocular segment, wherein the steps are executed while the step of centering monitoring 006 is also carried out.

The OCT acquisition step of the anterior ocular segment specifically comprises the following steps: the computer 1143 controls the optical path scanning device 1109 to scan, controls the OCT light source 1101 to emit light, and the combination module 18 adjusts the refraction control motor to move to a position where the refraction state is substantially at 0D; the optical fiber collimator 1107 controls the motor to move to a position for measuring the optical path length of the sample arm required by the OCT of the anterior segment of the eye; the shutter of the optical splitter 1401 is switched to control the motor so that the optical splitter 1401 switches out the OCT optical path of the anterior ocular segment; the front-rear power saving magnet causes the anterior ocular segment OCT insertion mirror 1501 to be inserted into the anterior ocular segment OCT optical path, as in the state shown in fig. 3. The computer 1143 controls the OCT sample arm module of the anterior ocular segment to perform OCT scanning on the anterior ocular segment to be detected, the computer 1143 drives the Z-axis movement control motor of the probe assembly 10 to perform Z-axis movement (optical path adjustment for the anterior ocular segment OCT acquisition), and real-time judgment is performed to find an OCT image of the cornea of the eye to be detected; after the OCT image of the cornea is found, the computer drives the X/Y/Z three-dimensional movement control motor of the probe assembly 10 to conduct fine adjustment, so that the OCT image of the cornea is positioned at a proper position of a display screen, such as centering or leaning upwards, and the OCT image signal of the cornea is strongest; when the main optical axis L1 of the system optical path is opposite to the pupil center, or the corneal vertex, the corneal OCT image signal at this time tends to be strongest. Since the basic principle of the OCT system is a michelson interferometer, the computer 1143 can precisely determine the position of the corneal vertex from the OCT image of the anterior segment of the eye according to the optical path matching. When the computer 1143 controls the optical path scanning device 1109 to perform radiation scanning on the anterior ocular segment, such as 6-line scanning. The computer 1143 can judge the intensity of the OCT signal of the anterior segment of the eye and determine the position of the strong reflection column of the OCT signal of the cornea according to the two orthogonal OCT images of the anterior segment of the eye in the scanning mode, and precisely drive the X/Y/Z three-dimensional movement control motor of the probe assembly 10, so that the main optical axis L1 of the system optical path is opposite to the pupil center and the cornea vertex. Therefore, the accuracy of judging the working position of the eye E to be detected is continuously improved, the oblique angle anterior ocular segment image acquired by the oblique angle anterior ocular segment image pickup module is subjected to rough positioning, the iris image acquired by the iris image pickup module is subjected to further positioning, and the OCT image of the anterior ocular segment is subjected to accurate positioning. Therefore, the oblique angle anterior ocular segment camera module is actually an auxiliary function, so that the oblique angle anterior ocular segment camera module is unnecessary, but the addition of the module can be beneficial to judging the working position of the eye to be detected.

The refraction measuring step comprises the following steps: after the working position of the eye E to be measured is located and the OCT image of the anterior segment of the eye is acquired, the computer 1143 controls the refractive module to perform refractive measurement. The computer 1143 controls the light path scanning device 1109 to stop scanning, controls the OCT light source 1101 to emit light, and the combination module 18 adjusts the refraction control motor to move to a position where the refraction state is substantially at 0D; wherein the refractive spectroscope 1401 is controlled by the computer 1143 to switch into the refractive measuring light path; the optical path scanning device 1109 needs to be in a set working position so that the OCT light source 1101 that exits the optical path scanning device 1109 is directed along the main optical axis shown in fig. 4. The front-back power saving magnet causes the anterior ocular segment OCT insertion mirror 1501 to leave the Qu Guangce-amount optical path, as shown in fig. 4. At this time, the computer 1143 calculates the diopter of the eye to be measured based on the photographed fundus reflex image.

The OCT acquisition of the posterior segment of the eye is specifically as follows: the computer 1143 controls the optical path scanning device 1109 to scan, and the combination module 18 adjusts the refraction control motor to move to the refraction position corresponding to the refraction measured by the refraction measuring module 140; in order to keep the working distance from the probe assembly 10 to the eye E to be tested unchanged, when the combination module 18 moves in a bending manner, if the combination module 18 moves along the Z direction close to the eye E to be tested, the Z-axis control motor of the probe assembly 10 needs to be correspondingly compensated, i.e. the probe assembly 10 is controlled to move along the Z direction away from the eye E to be tested, and vice versa; the anterior ocular segment OCT insertion mirror 1501 is controlled by the computer 1143 to switch out the posterior ocular segment OCT imaging light path; in addition, the refraction spectroscope 1401 is controlled by the computer 1143 to switch out the OCT imaging light path of the posterior segment of the eye, as shown in the state of fig. 2; when measuring the fundus, scanning is performed by the scanning devices 11091 and 11093; the optical path matching for the eyeground of different eyes is realized by combining the integral translation of the sample arm optical fiber head (not shown) through the optical fiber collimating lens 1107; when the posterior segment OCT signal is found by the translation of the optical path module, the computer 1143 controls the fiber collimator 1107 to fine tune the anterior-posterior segment so that the posterior segment OCT image is in the proper position on the screen (e.g., centered). At this time, the optical path matching adjustment for the eye E to be measured is realized. Then, the computer 1143 controls the objective lens 1305 to translate along the optical axis according to the strength of the OCT signal of the posterior segment of the eye to accurately adjust and bend the refractive states of different eyes so as to improve the signal intensity of the OCT image of the posterior segment of the eye, and finally, the acquisition of the OCT image of the posterior segment of the eye is realized, thereby obtaining important parameters of the eye structure such as retina thickness and the like. In this process, when the combination module 18 is adjusted to bend, in order to keep the working distance between the probe assembly 10 and the eye E to be measured unchanged, when the combination module 18 is adjusted to bend and move, if the combination module 18 moves along the Z direction close to the eye E to be measured, the Z-axis control motor of the probe assembly 10 needs to be correspondingly compensated, that is, the probe assembly 10 is controlled to move along the Z direction away from the eye E to be measured, and vice versa. If the adjustment stroke is larger, for example, exceeds 0.5mm, the optical collimator 1107 needs to be matched with the optical path compensation, so that the OCT image of the posterior segment of the eye is always in a proper position (for example, centered) on the screen. Since the computer 1143 can determine whether the refractive state of the combination module 18 is adjusted to the optimal position according to the strength of the OCT signal of the posterior segment of the eye during the OCT acquisition, the above refractive measuring module is not a necessary module for the OCT acquisition of the posterior segment of the eye. However, if the refractive condition deviation is large, the OCT signal of the posterior segment is weak, which affects the recognition of the OCT image of the posterior segment, and the refractive adjustment speed and success rate can be improved by using the refractive measurement module.

The fast switching anterior ocular segment OCT acquisitions are specifically as follows: the shutter of the refractive spectroscope 1401 is switched to control the motor so that the refractive spectroscope 1401 switches out the optical path of the anterior ocular segment OCT, and the anterior-posterior power saving magnet causes the anterior ocular segment OCT insertion mirror 1501 to be inserted into the optical path of the anterior ocular segment OCT, as shown in fig. 3. Because the diopter is adjusted for different eyes E to be measured during the OCT acquisition, that is, the combination module 18 performs the diopter adjustment movement, and the probe assembly 10 performs the corresponding compensation, the working distance of the eye E to be measured is kept unchanged, so that the optical path length of the OCT sample arm module 150 of the anterior segment of the eye is changed; therefore, the optical fiber collimator 1107 adjusts the optical path control motor to move to the position of the original optical path length of the sample arm required by the OCT of the anterior segment of the eye, and then adjusts the bending movement amount according to the combination module 18 to perform corresponding optical path compensation. If the combining module 18 needs to be moved close to the eye to be tested, the probe assembly 10 needs to be moved away from the whole human eye, so as to keep the relative distance between the eye to be tested E and the objective lens 1305 unchanged. At this time, the optical path length of the anterior ocular segment OCT sample arm module 150 is increased, so when the optical fiber collimator 1107 measures the anterior ocular segment OCT, the optical fiber collimator needs to be close to the optical path scanning device 1109, so that the optical path length of the anterior ocular segment OCT sample arm module 150 remains unchanged, i.e., the optical path length of the sample arm required for measuring the anterior ocular segment OCT is satisfied; i.e. the test eye E is still at the working distance required for OCT acquisition of the anterior segment of the eye, while its optical path is matched. The computer 1143 controls the anterior ocular segment OCT sample arm module 150 to perform OCT scanning on the anterior ocular segment to be detected and collect an anterior ocular segment OCT image; the OCT imaging module 110 then stops acquisition and the system enters the data analysis stage. Because the OCT image of the anterior segment and the OCT image of the posterior segment are acquired, the computer 1143 can calculate corresponding eye data to be measured according to the data of the corresponding optical path matching. So the operation of 'fast switching anterior segment OCT acquisition' is not necessary. However, in this embodiment, in order to improve the accuracy of the test data, this step is introduced, so that the OCT image acquisition of the anterior segment of the eye is quickly realized after the OCT acquisition of the posterior segment of the eye, the acquisition interval time of the two modes is short, and the influence of eye movement during the measurement at different moments before and after is avoided, so that the more accurate eye data to be measured is measured.

After all the steps of automatically measuring the eye to be measured are executed, entering a data analysis stage: when the acquisition is completed, the computer 1143 controls the system to stop the acquisition and enter a data analysis stage. The collected OCT image of anterior segment, OCT image of posterior segment, image of anterior segment, refractive measurement fundus image, etc. are processed to obtain various data such as anterior and posterior surface curvature of cornea, cornea thickness, anterior chamber depth, lens thickness, anterior and posterior surface curvature of lens, white-to-white distance, pupil diameter, etc. The doctor can also judge the morphology according to the collected OCT image of the anterior segment of the eye and the OCT image of the posterior segment of the eye, and determine whether the eye E to be detected has related diseases and the like. The multifunctional full-automatic ophthalmic measuring method is mainly used for automatic measurement of relevant optical parameters of eyes of patients, is used for screening vision of teenagers and glaucoma, and can specifically measure various ophthalmic relevant parameters such as cornea front and back surface curvature, cornea thickness, anterior chamber depth, lens thickness, lens front and back surface curvature, white-to-white distance, pupil diameter, sphere power, cylinder power, axial position, anterior and posterior section OCT images, macular region eye fundus images, ILM-RPE nine-region thickness images, ILM-RPE thickness topographic maps, ILM-RPE curve thickness images, GCC eight-region thickness images, GCC thickness topographic maps, GCC curve thickness images and the like.

In summary, in the multifunctional ophthalmic full-automatic measurement method according to the preferred embodiment of the present invention, the inspection apparatus first determines whether the eye to be inspected is on the inspection station; if the eye to be detected is at the correct position of the detection station, adjusting the position of a probe of the detection equipment relative to the eye to be detected, wherein the relative positions comprise front and back, left and right, up and down; after the probe of the detection equipment moves to the correct position, the detection system of the detection equipment is successfully matched with the eye to be detected, and the eye to be detected enters a detection state; entering a detection stage, namely automatically starting a detection system of the detection equipment to automatically detect the eye to be detected, so that the whole detection flow is realized through automation, and the method is quick and convenient. The specific summary is as follows: 1) Whether the eye to be detected is on the detection station is sensed, the forehead above the eye to be detected is automatically sensed through a sensor arranged on the forehead support, and the sensor is fed back to a control module (computer) of the detection equipment to judge whether the eye to be detected is on the detection station. 2) The motor resets, and the motor that resets includes controlling, about, refraction, optical path, polarization motor etc. need carry out the motor reset after the eye that awaits measuring gets into the detection station. 3) The position of the eye to be measured is adjusted by moving the probe left and right and up and down according to the picture shot by the 45-degree camera (the oblique angle anterior segment shooting module), and moving the pupil of the eye to be measured to the imaging range of the iris shooting module. 4) And adjusting the position of the probe back and forth while adjusting the position of the eye to be measured. 5) The probe position is adjusted and the pupil is centered. 6) After pupil centering is completed, the eye to be detected and the detection equipment probe enter the correct position, the eye to be detected enters the detection state, a centering monitoring flow is started when the eye to be detected enters the detection state, the eye to be detected and the detection equipment must be positioned at the correct position when the eye to be detected is detected, and the function of the centering monitoring flow is to ensure that the eye to be detected and the detection equipment probe are positioned at the correct position. 7) After entering the detection stage, the detection system of the detection equipment automatically detects the eye to be detected, wherein the automatic detection comprises front section OCT scanning, refraction measurement, rear section OCT scanning and rapid switching of the front section OCT scanning, and the automatic detection is sequentially carried out according to time sequence; the automatic detection is performed while the centering monitoring is required to be performed, and the centering monitoring is required to be stopped after the automatic detection is completed.

The multifunctional full-automatic ophthalmic measuring method can simultaneously carry out multiple detection, refraction measurement, anterior segment OCT and posterior segment OCT on the eye to be measured, and can obtain data such as sphere power, cylinder power, axial position, front and back surface curvature of cornea, cornea thickness, anterior chamber depth, lens thickness, front and back surface curvature of lens, white-to-white distance, pupil diameter and the like through one-time detection, and the whole detection process does not need manual intervention at all, so that unattended operation is truly realized; in each flow of the full-automatic process, intelligent voice broadcasting can be achieved through a computer, so that a user can automatically detect eyes without any help of any person.

The foregoing is a further detailed description of the invention in connection with the preferred embodiments, and it is not intended that the invention be limited to the specific embodiments described. It will be apparent to those skilled in the art that several equivalent substitutions and obvious modifications can be made without departing from the spirit of the invention, and the same should be considered to be within the scope of the invention.

Claims

1. The multifunctional full-automatic ophthalmic measurement method is characterized by adopting a multifunctional full-automatic measurement system to perform measurement, wherein the multifunctional full-automatic measurement system comprises a main body module, a probe assembly and a three-dimensional movement control unit, the main body module comprises a control device, the probe assembly is arranged on the three-dimensional movement control unit to adjust the three-dimensional position of the probe assembly through the three-dimensional movement control unit, the probe assembly comprises an optical path adjusting device, an optical path scanning device (1109), an eye posterior segment OCT field lens (1301), an eye anterior segment OCT insertion lens (1501), a front dichroic mirror (1303), an eye objective lens (1305), a first movement control unit, an illumination light source and an oblique angle eye anterior segment photographing module, and the eye anterior segment OCT insertion lens (1501) is arranged on the first movement control unit so that the eye anterior segment OCT insertion lens (1501) can be inserted into an optical path or removed out of the optical path; the oblique anterior ocular segment imaging module is arranged below the eye objective lens (1305), and comprises an oblique anterior ocular segment imaging lens (1801) and an oblique anterior ocular segment imaging device (1803), light emitted by the illumination light source irradiates the eye (E) to be tested and can sequentially pass through the oblique anterior ocular segment imaging lens (1801) and the oblique anterior ocular segment imaging device (1803) after being reflected so as to obtain oblique anterior ocular segment images, wherein an optical path formed from the eye (E) to be tested to the oblique anterior ocular segment imaging device (1803) and an optical path formed from measuring light to the eye (E) to be tested form a preset angle;

The multifunctional ophthalmic full-automatic measurement method comprises the following steps:

s1: after the eye to be detected is monitored to be positioned right in front of the eye-receiving objective lens (1305), a control device in the main body module adjusts the three-dimensional movement control unit according to the position of the eye to be detected so as to automatically adjust the probe assembly; the three-dimensional movement control unit adjusts the probe assembly according to the position of the eye to be detected (E) so as to adjust the eye to be detected (E) to a proper position;

s2: the control device in the main body module drives the first movement control unit to control the insertion of the anterior ocular segment OCT insertion mirror (1501) into a light path and adjust the light path adjusting device, measurement light provided by the main body module passes through the light path adjusting device, the light path scanning device (1109) reflects the measurement light and then passes through the posterior ocular segment OCT field mirror (1301) and the anterior ocular segment OCT insertion mirror (1501), the measurement light is reflected by the anterior dichroic mirror (1303) to the eye objective lens (1305) to enter an eye (E) to be measured and is focused in the anterior ocular segment to be measured so as to return an anterior ocular segment light signal to be transmitted to the main body module, and the main body module provides reference light and can utilize the reference light to interfere with the anterior ocular segment light signal and collect an anterior ocular segment interference light signal obtained through interference so as to acquire an anterior ocular segment OCT image of the eye (E) to be measured;

S4: the control device in the main body module drives the first movement control unit to control the OCT insertion lens (1501) to move out of a light path and adjust the light path adjusting device, measuring light provided by the main body module passes through the light path adjusting device, passes through the OCT field lens (1301) after being reflected by the light path scanning device (1109), then is reflected to the eye objective lens (1305) by the front dichroic mirror (1303) to enter an eye to be detected (E) and is focused in the eye fundus (Er) to be detected so as to return an optical signal of the eye back section to be transmitted to the main body module, and the main body module can utilize the reference light and the optical signal of the eye back section to interfere and collect the interference optical signal of the eye back section obtained by interference so as to collect and obtain an OCT image of the eye to be detected (E).

2. The method for multifunctional ophthalmic full-automatic measurement according to claim 1, wherein,

the probe assembly further comprises a rotation control unit and a refraction measuring module, the refraction measuring module comprises a refraction spectroscope (1401), a first refraction lens (1403), a second refraction lens (1405), a micro lens array element (1407) and a refraction imaging device (1409), the refraction spectroscope (1401) is arranged between the light path scanning device (1109) and the back-eye section OCT field lens (1301) and is arranged in the rotation control unit, so that the refraction spectroscope (1401) can rotate into a light path between the light path scanning device (1109) and the back-eye section OCT field lens (1301) or move out of the light path between the light path scanning device (1109) and the back-eye section OCT field lens (1301), when the rotation control unit controls the refraction spectroscope to rotate into the light path between the light path scanning device (1109) and the back-eye section OCT field lens (1301), measurement light provided by the main body module enters into a to-be-measured eye (E), passes through the back-eye section OCT field lens (1301), passes through the second refraction imaging device (1407) and passes through the back-eye section OCT field lens (1301) and then passes through the second refraction imaging device (1409) in turn;

The method further comprises a step S3: the control device in the main body module drives the rotation control unit to control the refraction spectroscope (1401) to rotate into a light path between the light path scanning device (1109) and the posterior ocular segment OCT field lens (1301) so as to shoot and obtain the fundus reflection image.

3. The method according to claim 2, wherein the step S4 further comprises, before acquiring the posterior segment OCT image of the eye (E) to be measured: the refractive state of the ocular objective (1305) is adjusted according to the fundus reflection image.

4. The method for multifunctional ophthalmic full-automatic measurement according to claim 1, further comprising step S5: the control device in the main body module drives the first mobile control unit again to control the insertion of the anterior ocular segment OCT insertion mirror (1501) into an optical path, and adjusts the optical path adjusting device to acquire an anterior ocular segment OCT image of the eye (E) to be detected.

5. The multifunctional ophthalmologic full-automatic measurement method according to claim 1, further comprising a head support device and a pressure sensor provided on the head support device, wherein the monitoring of the placement of the eye to be measured in front of the objective lens (1305) in step S1 determines and monitors whether there is the placement of the eye to be measured in front of the objective lens (1305) specifically according to the reading state of the pressure sensor.

6. The method for multifunctional ophthalmic full-automatic measurement according to claim 1, wherein,

the probe assembly further comprises an illumination light source and an iris shooting module, wherein the iris shooting module comprises an iris fixation relay lens (1903), an iris fixation spectroscope (1905), an iris shooting lens (1907) and an iris shooting device (1909), and light emitted by the illumination light source can pass through the eye objective lens (1305), the front dichroic mirror (1303), the iris fixation relay lens (1903), the iris fixation spectroscope (1905), the iris shooting lens (1907) and the iris shooting device (1909) after being reflected in the eye to be detected (E) so as to shoot and obtain iris images;

the step S1 comprises the following steps: according to the iris image shot by the iris shooting module, calculating the relative position of the eye (E) to be detected relative to the center of the optical path, and the three-dimensional movement control unit adjusts the probe assembly according to the relative position of the eye (E) to be detected relative to the center of the optical path so as to adjust the eye (E) to be detected to a proper position.

7. The method according to claim 1, wherein the control device in the main body module in step S1 adjusts the three-dimensional movement control unit according to the position of the eye to be measured to automatically adjust the probe assembly includes adjusting the eye to be measured, wherein the adjusting the eye to be measured includes the steps of:

A1: adopting an oblique anterior ocular segment imaging module to shoot oblique anterior ocular segment images;

a2: calculating the center coordinates of the pupils of the eyes to be detected according to the oblique angle anterior segment images;

a3: performing distortion correction on the oblique angle anterior segment image to calculate the real coordinates of the pupil of the eye to be detected;

a4: calculating the offset of the X-axis and Y-axis movement of the three-dimensional movement control unit according to the center coordinates of the pupils of the eyes to be detected and the real coordinates of the pupils of the eyes to be detected; wherein the X-axis and Y-axis directions refer to the directions of a transverse axis and a longitudinal axis on a plane parallel to the eye to be measured respectively;

a5: controlling the three-dimensional movement control unit to move the position of the probe assembly in the X-axis and Y-axis directions through the control device of the main body module according to the offset of the X-axis and Y-axis movement in the step A4;

a6: judging whether the pupil center of the eye to be detected is positioned on a main optical axis of an optical path, if so, executing the step A7; if not, returning to the step A1;

a7: and (3) exiting the step of adjusting the eye to be measured.

8. The method according to claim 6, wherein the step S1 of adjusting the three-dimensional movement control unit by the control device in the main body module according to the position of the eye to be measured to automatically adjust the probe assembly includes adjusting the probe assembly back and forth, wherein the step of adjusting the probe assembly back and forth includes the steps of:

B1: the control device of the main body module controls the three-dimensional movement control unit to drive the probe assembly to move forwards, and steps B2-B7 are executed in the process of moving the probe assembly forwards, wherein the forward movement is directed to move in a direction close to the eye to be detected;

b2: judging whether to exit, if yes, executing the step B8, and if not, executing the step B3;

b3: taking an iris image obtained by shooting by the iris shooting module;

b4: calculating the definition of the iris image shot by the iris shooting module;

b5: judging whether the front and rear positions of the probe assembly can be stopped to be adjusted according to the definition, if so, executing the step B8, and if not, executing the step B6;

b6: acquiring a real-time position of the three-dimensional movement control unit in the Z-axis direction, wherein the Z-axis direction is a direction perpendicular to a plane parallel to the eye to be detected;

b7: judging whether the real-time position of the three-dimensional mobile control unit in the Z-axis direction exceeds an empirical value, if so, executing the step B8, and if not, returning to the step B3;

b8: and stopping the three-dimensional movement control unit, and finishing adjustment.

9. The method according to claim 6, wherein the control device in the main body module in step S1 adjusts the three-dimensional movement control unit according to the position of the eye to be measured to automatically adjust the probe assembly includes pupil centering, wherein pupil centering includes the steps of:

C1: judging whether to exit, if yes, executing the step C11, and if not, executing the step C2;

c2: taking an iris image obtained by shooting by the iris shooting module;

and C3: judging whether the iris image has the iris of the eye to be detected, if so, executing the step C4, and if not, executing the step C7;

and C4: calculating the X-axis and Y-axis offset between the pupil center of the eye to be detected and the center of the iris camera module, wherein the X-axis and Y-axis directions refer to the transverse axis and longitudinal axis directions on a plane parallel to the eye to be detected respectively;

c5: controlling the three-dimensional movement control unit to move the position of the probe assembly in the X-axis and Y-axis directions by the control device of the main body module according to the X-axis and Y-axis offset of the step C4;

c6: judging whether the pupil of the eye to be detected is centered, if so, executing the step C11, and if not, returning to the step C1;

c7: judging whether the number of times of the iris of the eye to be detected in the iris image exceeds a preset value, if so, executing the step C11, and if not, executing the step C8;

and C8: judging whether the distance between the probe assembly and the eye to be detected is smaller than a safety distance, if so, executing a step C9, and if not, executing a step C10;

C9: c1, controlling the three-dimensional movement control unit to drive the probe assembly to move backwards to a preset position through a control device of the main body module, and returning to the step C1;

c10: c1, controlling the three-dimensional movement control unit to drive the probe assembly to move forwards through a control device of the main body module, and returning to the step C1;

c11: and exiting the pupil centering step.

10. The method according to claim 6, 8 or 9, wherein the steps S2, S4 are performed simultaneously with the pupil centering monitoring step, wherein the pupil centering monitoring comprises the steps of:

d1: taking an iris image obtained by shooting by the iris shooting module;

d2: calculating the X-axis and Y-axis offset between the pupil center of the eye to be detected and the center of the iris camera module, wherein the X-axis and Y-axis directions refer to the transverse axis and longitudinal axis directions on a plane parallel to the eye to be detected respectively;

d3: controlling the three-dimensional movement control unit to move the position of the probe assembly in the X-axis and Y-axis directions by the control device of the main body module according to the X-axis and Y-axis offset of the step D2;

d4: judging whether to exit the pupil centering monitoring step, if so, executing a step D5, and if not, returning to the step D1;

D5: and exiting the pupil centering monitoring step.

11. The method for multifunctional ophthalmic full-automatic measurement according to claim 2, wherein,

in performing step S3, a pupil centering monitoring step is also performed synchronously, wherein the pupil centering monitoring comprises the steps of:

d1: taking an iris image obtained by shooting by the iris shooting module;

d5: and exiting the pupil centering monitoring step.

12. The method for multifunctional ophthalmic full-automatic measurement according to claim 4, wherein,

in performing step S5, a pupil centering monitoring step is also performed synchronously, wherein the pupil centering monitoring comprises the steps of:

D1: taking an iris image obtained by shooting by the iris shooting module;

d5: and exiting the pupil centering monitoring step.

13. The utility model provides a full-automatic measurement system of multi-functional ophthalmology, its characterized in that includes main body module, probe subassembly, three-dimensional removal control unit, the probe subassembly is installed on the three-dimensional removal control unit in order to pass through three-dimensional removal control unit adjusts the three-dimensional position of probe subassembly, wherein:

the probe assembly comprises an optical path adjusting device, an optical path scanning device (1109), a posterior segment OCT field lens (1301), an anterior segment OCT insertion lens (1501), a front dichroic mirror (1303), an eye objective lens (1305), a first movement control unit, an illumination light source and an oblique angle anterior segment photographing module, wherein the anterior segment OCT insertion lens (1501) is arranged on the first movement control unit so that the anterior segment OCT insertion lens (1501) can be inserted into an optical path or removed out of the optical path; the oblique anterior ocular segment imaging module is arranged below the eye objective lens (1305), and comprises an oblique anterior ocular segment imaging lens (1801) and an oblique anterior ocular segment imaging device (1803), light emitted by the illumination light source irradiates the eye (E) to be tested and can sequentially pass through the oblique anterior ocular segment imaging lens (1801) and the oblique anterior ocular segment imaging device (1803) after being reflected so as to obtain oblique anterior ocular segment images, wherein an optical path formed from the eye (E) to be tested to the oblique anterior ocular segment imaging device (1803) and an optical path formed from the eye (E) to be tested to the eye objective lens (1305) form a preset angle;

When the first movement control unit controls the insertion of the anterior ocular segment OCT insertion mirror (1501) into an optical path, measuring light provided by the main body module passes through the optical path adjusting device, passes through the posterior ocular segment OCT field mirror (1301) after being reflected by the optical path scanning device (1109), and the anterior ocular segment OCT insertion mirror (1501), and then is reflected by the prepositive dichroic mirror (1303) to the eye objective lens (1305) to enter an eye (E) to be tested and focus in the anterior ocular segment to be tested so as to return an anterior ocular segment light signal to be transmitted to the main body module, and the main body module provides reference light and can utilize the reference light to interfere with the anterior ocular segment light signal and collect an anterior ocular segment interference light signal obtained through interference so as to obtain an anterior ocular segment OCT image of the eye (E) to be tested;

when the first movement control unit controls the OCT insertion mirror (1501) to move out of the optical path, the measuring light provided by the main body module passes through the optical path adjusting device, passes through the OCT field mirror (1301) after being reflected by the optical path scanning device (1109), then is reflected by the front dichroic mirror (1303) to the eye objective (1305) to enter the eye (E) to be tested and is focused in the fundus (Er) of the eye to be tested so as to return an optical posterior segment light signal to be transmitted to the main body module, and the main body module can utilize the reference light to interfere with the optical posterior segment light signal and collect the optical posterior segment interference light signal obtained through interference so as to obtain an optical posterior segment OCT image of the eye (E) to be tested.

14. The system of claim 13, wherein the probe assembly further comprises a second motion control unit, the objective lens (1305) and the oblique anterior ocular segment camera module being relatively fixedly mounted to the second motion control unit such that the objective lens (1305) and the oblique anterior ocular segment camera module are movable along a direction of an optical path formed by the measuring light to the eye to be measured.

15. The system according to claim 13, wherein the probe assembly further comprises an illumination light source and an iris imaging module, the iris imaging module comprises an iris fixation relay lens (1903), an iris fixation spectroscope (1905), an iris imaging lens (1907) and an iris imaging device (1909), and the light emitted by the illumination light source can pass through the objective lens (1305), the front dichroic mirror (1303), the iris fixation relay lens (1903), the iris fixation spectroscope (1905), the iris imaging lens (1907) and the iris imaging device (1909) after being reflected by the eye to be measured (E) so as to obtain an iris image.

16. The system according to claim 15, wherein the probe assembly further comprises a fixation optical module, the fixation optical module comprises a fixation light source (1701) and a fixation optical path lens (1703), and the light emitted by the fixation light source (1701) passes through the fixation optical path lens (1703), is reflected by the iris fixation spectroscope (1905), and sequentially passes through the iris fixation relay lens (1903), the front dichroic mirror (1303) and the eye objective lens (1305) to enter the eye to be tested (E) to form a fixation target for fixation of the eye to be tested (E).

17. The system according to claim 13, wherein the probe assembly further comprises a rotation control unit and a refractive measuring module, the refractive measuring module comprises a refractive spectroscope (1401), a first refractive lens (1403), a second refractive lens (1405), a micro lens array element (1407) and a refractive imaging device (1409), the refractive spectroscope (1401) is arranged between the optical scanning device (1109) and the retroocular OCT field lens (1301) and the refractive spectroscope (1401) is mounted in the rotation control unit so that the refractive spectroscope (1401) can rotate into an optical path between the optical scanning device (1109) and the retroocular field lens (1301) or move out of an optical path between the optical scanning device (1109) and the retroocular field lens (1301), and when the rotation control unit controls the spectroscope to rotate into an optical path between the optical scanning device (1109) and the retroocular field lens (1301), the refractive spectroscope (1407) is provided to enter a refractive imaging device (1405) and a second refractive imaging device (1403) to sequentially pass through the refractive optical scanning device (1407) and the refractive imaging device (1301).