WO2021046975A1 - 共光路光束扫描的大视场自适应光学视网膜成像系统和方法 - Google Patents

共光路光束扫描的大视场自适应光学视网膜成像系统和方法 Download PDF

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WO2021046975A1
WO2021046975A1 PCT/CN2019/112687 CN2019112687W WO2021046975A1 WO 2021046975 A1 WO2021046975 A1 WO 2021046975A1 CN 2019112687 W CN2019112687 W CN 2019112687W WO 2021046975 A1 WO2021046975 A1 WO 2021046975A1
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module
scanning
imaging
light
field
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PCT/CN2019/112687
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English (en)
French (fr)
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史国华
何益
高峰
孔文
邢利娜
李婉越
张欣
王晶
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中国科学院苏州生物医学工程技术研究所
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Priority to US16/977,192 priority Critical patent/US12004813B2/en
Priority to JP2020551385A priority patent/JP7077507B2/ja
Priority to EP19917523.3A priority patent/EP3818923A4/en
Priority to KR1020207028523A priority patent/KR102449173B1/ko
Publication of WO2021046975A1 publication Critical patent/WO2021046975A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/14—Arrangements specially adapted for eye photography
    • A61B3/15—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing
    • A61B3/152—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing for aligning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/0008—Apparatus for testing the eyes; Instruments for examining the eyes provided with illuminating means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/0016—Operational features thereof
    • A61B3/0025—Operational features thereof characterised by electronic signal processing, e.g. eye models
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/1015—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for wavefront analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/1025—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for confocal scanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/113—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining or recording eye movement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A61B3/1225—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes using coherent radiation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A61B3/1241—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes specially adapted for observation of ocular blood flow, e.g. by fluorescein angiography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/14—Arrangements specially adapted for eye photography
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N23/00—Cameras or camera modules comprising electronic image sensors; Control thereof
    • H04N23/58—Means for changing the camera field of view without moving the camera body, e.g. nutating or panning of optics or image sensors

Definitions

  • This application relates to the field of optical imaging technology, and in particular to a large field of view adaptive optical retinal imaging system and method with common optical path beam scanning.
  • Patent number ZL201010197028.0 proposes a retinal imaging device based on adaptive optics technology.
  • the device uses two independent scanning galvanometers to achieve two-dimensional synchronous scanning of the retinal plane to achieve confocal scanning imaging, which can achieve high resolution. Rate imaging function.
  • this device can only achieve high-resolution imaging with a maximum field of view of 3 degrees of the human eye.
  • the halo zone such as adaptive optics aberration correction, adaptive optics often compromises the imaging field of view while achieving high-resolution imaging, and can only achieve small field of view imaging within 3°.
  • the existing laser confocal scanning ophthalmoscope has a large imaging field, but the resolution is not sufficient to observe the fine structure of the retina; the laser confocal scanning ophthalmoscope combined with adaptive optics can observe the fine structure of the retina, but the imaging vision The field is small, and it is impossible to observe the lesions with a larger field of view.
  • the technical problem to be solved by this application is to provide a large field of view adaptive optical retinal imaging system with common optical path beam scanning in view of the above-mentioned shortcomings in the prior art.
  • the existing laser confocal scanning ophthalmoscope has a large imaging field, but the resolution is not enough to observe the fine structure of the retina; the laser confocal scanning ophthalmoscope combined with adaptive optics can observe the fine structure of the retina, but the imaging field is small and cannot Observe the condition of the lesion with a larger field of view.
  • this application proposes a common optical path beam scanning large field of view adaptive optical retinal imaging system based on the basic principles of adaptive optics combined with confocal scanning technology.
  • the two scanning mirrors share the optical path structure, and the two scanning mirrors are configured in different scanning modes, which can perform large-field imaging of more than 20 degrees on the retina for observing the focal area of retinal diseases; it can also perform no more than 5 on the retina.
  • High-degree small field of view scanning imaging in the case of adaptive optics correcting aberrations, to achieve small field of view high-resolution imaging to observe the microstructure and pathological changes of the lesion, and further set up a second scanning mirror to realize the light beam in each area of the retina to sequentially tilt and illuminate, Then through image splicing, high-resolution imaging with a large field of view over 15 degrees of the retina can be obtained at one time.
  • a common optical path beam scanning large field of view adaptive optics retinal imaging system including: a light source module, an adaptive optics module, a beam scanning module, a defocus compensation module, an optotype module, and pupil monitoring Module, detection module, control module and output module;
  • the light source module emits parallel light beams, and then passes through the adaptive optics module, the beam scanning module, and the defocus compensation module to illuminate the human eyes.
  • the imaging light scattered by the human eyes and carrying human eye aberration information and light intensity information follows the original path Return and transmit to the adaptive optics module and detection module;
  • the adaptive optics module is used for receiving imaging light containing human eye aberration information, and realizing real-time measurement and correction of human eye aberration;
  • the beam scanning module is controlled by the control module and can be configured into different scanning modes to realize different scanning imaging functions, including at least: large field of view imaging function, small field of view high-resolution imaging function, and large field of view high-resolution imaging function. Resolution imaging function;
  • the defocus compensation module is used for realizing compensation for the refractive error of human eyes
  • the optotype module is used to realize the guidance and fixation of different areas of the retina of the human eye;
  • the pupil monitoring module is used to realize the alignment and monitoring of the pupil of the human eye
  • the detection module is used to obtain the returned human eye imaging light, convert it into an electrical signal and transmit it to the control module;
  • the output module is connected with the control module and is used for displaying and storing human eye imaging images.
  • the light source module, the adaptive optics module, the beam scanning module, the visual target module, the defocus compensation module, and the pupil monitoring module are arranged in sequence along the incident light path;
  • the light source module is configured as a light source, a collimator, and a first beam splitter arranged in sequence along the incident light path, which outputs parallel light beams to the adaptive optics module; the light emitted by the light source is partially transmitted through the collimator The first beam splitter enters the adaptive optics module;
  • the adaptive optics module is configured as a second beam splitter, a wavefront corrector, a transmissive or reflective telescope, and a wavefront sensor, which are sequentially arranged along the incident light path, and are connected to the beam scanning module for realizing wavefront imaging.
  • the parallel beam output by the light source module partially transmits through the second beam splitter and then is reflected by the wavefront corrector to the transmissive or reflective telescope, and enters the beam scanning module;
  • the imaging light carrying human eye aberration information and light intensity information exits the transmissive or reflective telescope through the beam scanning module, and then is reflected by the wavefront corrector to the second beam splitter, and part of the imaging light Reflected by the second beam splitter to the wavefront sensor to achieve wavefront aberration measurement, the remaining imaging light is transmitted through the second beam splitter and continues to propagate;
  • the wavefront sensor After the wavefront sensor receives the imaging light beam containing human eye aberration information, it is transmitted to the control module for wavefront calculation, and the wavefront control voltage is obtained and output to the wavefront corrector to realize the correction of the wavefront aberration. Detection and correction.
  • the detection module is configured to collect a lens, a confocal pinhole, and a high-sensitivity detector, and the part of the returned imaging light that transmits through the second beam splitter of the adaptive optics module reaches the first beam splitter. Part of the imaging light is then reflected by the first beam splitter to the collecting lens, focused and then passed through the confocal pinhole and then reaches the high-sensitivity detector, undergoes photoelectric conversion to obtain an electrical signal, and then outputs it to the control The module performs processing to obtain the retinal imaging image, and finally outputs it to the output module for display and storage;
  • the confocal pinhole is arranged at the focal point of the collecting lens.
  • the beam scanning module is configured as a first scanning mirror and a second scanning mirror, and the two scanning mirrors are connected by a transmission or reflection telescope to achieve pupil-plane matching;
  • the first scanning mirror realizes the alignment of the retinal plane
  • the second scanning mirror realizes the vertical scanning of the retinal plane under the driving of periodic voltage, and the second scanning mirror can generate a certain horizontal and vertical tilt angle under the driving of the DC voltage.
  • the second scanning The mirror produces lateral and longitudinal tilt angles driven by a DC voltage, and at the same time can realize a horizontal and vertical two-dimensional scanning of the retinal plane under a periodic voltage drive;
  • the front and rear positions of the first scanning mirror and the second scanning mirror can be interchanged;
  • the beam scanning module is controlled by the output voltage signal of the control module, and can be configured into different scanning modes to realize different imaging functions, including: large field of view imaging function, small field of view high resolution imaging function, and large field of view high resolution Rate imaging function.
  • the defocus compensation module is configured as a scanning objective lens, a flat field objective lens, and a guide rail that are sequentially arranged along the incident light path, and the emitted light beam of the beam scanning module propagates to the pupil monitoring module through the defocus compensation module, and
  • the plan objective lens can reciprocate along the central axis of the plan objective lens on the guide rail, so as to realize the compensation of the refractive error of the human eye.
  • the visual target module is configured as an LED array, a lens, and a first dichroic beam splitter, and the light emitted from any lamp bead in the LED array being lit by the control module passes through the lens After propagation, it is reflected by the first dichroic beam splitter into the defocus compensation module and finally enters the human eye.
  • the human eye looks at the luminous LED lamp bead to achieve fixation; the beam emitted by the beam scanning module passes through the The first dichroic beam splitter of the visual target module enters the defocus compensation module and continues to propagate after being transmitted.
  • the pupil monitoring module is configured as a ring-shaped LED array, a second dichroic beam splitter, an imaging lens, and an area array detector.
  • the light emitted by the ring-shaped LED array illuminates the pupil of the human eye and passes through the pupil after being reflected by the pupil of the human eye.
  • the hollow part of the annular LED array is completely reflected by the second dichroic beam splitter and then focused by the imaging lens to the area array detector.
  • the area array detector converts optical signals into electrical signals and outputs them to The control module obtains the pupil imaging image, and finally outputs it to the output module for display and storage.
  • control module controls the first scanning mirror and the second scanning mirror in the beam scanning module through an output voltage signal, so as to realize different scanning and imaging functions;
  • the realization method of the large field of view imaging function is:
  • the adaptive optics module is in a shutdown state, or a startup state that is not working;
  • the first scanning mirror is driven by a periodic voltage signal to realize the lateral scanning of the retinal plane;
  • the second scanning mirror is driven by a periodic voltage signal to realize the longitudinal scanning of the retinal plane.
  • the retina scanning angle of the first scanning mirror and the second scanning mirror driven by a periodic voltage signal is not less than 20 degrees;
  • the detection module converts the acquired retinal light signal of the fundus into an electrical signal, the periodic driving voltage signal of the first scanning mirror and the second scanning mirror is synchronized by the control module, and the control module resamples the electrical signal Constructing an imaging image of the retina with a large field of view, and outputting it to the output module for display and storage;
  • the realization method of the small field of view high-resolution imaging function is:
  • the adaptive optics module is in a power-on working state to realize the measurement and correction of wavefront aberration
  • the first scanning mirror is driven by a periodic voltage signal to realize the horizontal scanning of the retinal plane;
  • the second scanning mirror can be driven by a DC voltage signal to generate a certain horizontal and vertical tilt angle for illuminating the fundus retina
  • the beam is positioned at the position of interest, and then driven by the periodic voltage signal to realize the longitudinal scanning of the retinal plane;
  • the retina scanning angle of the first scanning mirror and the second scanning mirror driven by the periodic voltage signal is not greater than 5 degrees;
  • the DC voltage signal is calculated by the control module according to the coordinate position of the fundus retina
  • the detection module converts the acquired retinal light signal of the fundus into an electrical signal, the periodic driving voltage signal of the first scanning mirror and the second scanning mirror is synchronized by the control module, and the control module resamples the electrical signal
  • a high-resolution imaging image of the small field of view of the retina is constructed, and the coordinate position of the retina of the fundus is marked in the imaging image; the high-resolution imaging image of the small field of view is output to the output module through the control module for display and storage ;
  • the realization method of the large-field-of-view high-resolution imaging function is:
  • the adaptive optics module is in a power-on working state to realize the measurement and correction of wavefront aberration
  • the first scanning mirror is driven by a periodic voltage signal to realize the horizontal scanning of the retinal plane;
  • the second scanning mirror is driven by a periodic voltage signal to realize the longitudinal scanning of the retinal plane;
  • the first scanning mirror The retina scanning angle of the second scanning mirror driven by the periodic voltage signal is not more than 5 degrees;
  • the second scanning mirror can generate a certain horizontal and vertical tilt angle under the drive of the DC voltage signal, and the light beam is tilted to illuminate each area of the fundus retina in turn.
  • the single horizontal and vertical tilt angle of the second scanning mirror is not greater than 3 degrees, the maximum lateral and longitudinal tilt angles of the retina of the second scanning mirror driven by a DC voltage signal are not more than 15 degrees; the DC voltage signal is calculated by the control module according to the coordinate position of the fundus retina;
  • the control module can obtain high-resolution imaging images of each area of the retina, and the control module stitches each image according to the position coordinates of the fundus retina of the high-resolution imaging images of each area To obtain a high-resolution image of the fundus retina with a large field of view, and then output to the output module for display and storage.
  • the light source module may include multiple light sources, and the multiple light sources may be coupled into the collimator through a fiber coupler to be collimated into parallel light beams; multiple light sources may also be collimated into parallel light beams by respective collimators. After the light beam is coupled into the optical path through the dichroic beam splitter;
  • the collimator may be a single lens, an achromatic lens, an apochromatic lens or a parabolic mirror, which is used to collimate the light beam emitted by the light source into a parallel light beam;
  • the first beam splitter is a wide-band beam splitter, 20% of the parallel beam emitted by the collimator passes through the beam splitter and continues to propagate into the adaptive optics module, and the emergent imaging beam 80 returned by the adaptive optics module % Is reflected by the first beam splitter and enters the detection module.
  • the wavefront sensor included in the adaptive optics module is one of a microprism array Hartmann wavefront sensor, a microlens array Hartmann wavefront sensor, a quadrangular pyramid sensor, and a curvature sensor.
  • the wavefront corrector is one of deformable mirrors, liquid crystal spatial light modulators, micro-machined thin-film deformable mirrors, micro-electromechanical deformable mirrors, bi-piezoelectric ceramic deformable mirrors, and liquid deformable mirrors.
  • 95% of the parallel light beam output by the light source module is transmitted through the second beam splitter to the wavefront corrector; the returned imaging beam is reflected by the wavefront corrector to the second beam splitter for splitting, wherein 5% of the light energy is It is reflected into the wavefront sensor to achieve wavefront aberration measurement; the remaining 95% of the light energy is transmitted to the first beam splitter and continues to propagate.
  • a common optical path beam scanning large-field adaptive optics retinal imaging method which adopts the above-mentioned system for imaging, and includes the following steps:
  • Step S1 Turn on and start the system
  • Step S2 The subject’s head is placed on the headrest, the pupil monitoring module is turned on, and the three-dimensional translation of the headrest is automatically adjusted by manual adjustment or the control module, so that the pupil is imaged in the middle area of the field of view;
  • Step S3 Manually slide the plan objective lens to move along the center of the optical axis, or use the control module to drive the motor to move the position of the plan objective lens on the guide rail to realize the compensation and correction of the refractive error of the human eye;
  • Step S4 illuminate a lamp bead in the LED array, and the subject will stare at the light spot to achieve fixation;
  • Step S5 The adaptive optics module is turned off or turned on and not working, the beam scanning module is set to the large field of view scanning mode, and the control module controls the beam scanning module to complete the large field of view scanning, realizes the retina large field of view imaging and outputs to the output module;
  • Step S6 The adaptive optics module is in power-on operation to realize wavefront aberration measurement and correction, and the control module controls the beam scanning module to perform small field of view scanning, which may include two small field of view scanning modes S61 and S62;
  • Step S61 the control module controls the beam scanning module to complete the small field of view high-resolution imaging image output to the output module 10;
  • Step S62 the control module controls the beam scanning module to complete the large field of view high-resolution imaging image and output it to the output module.
  • step S5 and step S6 can be reversed.
  • Step S61 and step S62 have no sequence relationship and can be selected according to requirements.
  • This application proposes a common optical path beam scanning large field of view adaptive optics retinal imaging system and method.
  • the system of the present application uses two scanning mirrors to form a common optical path beam scanning structure, and the first scanning mirror realizes the lateral scanning of the retina.
  • the second scanning mirror realizes the vertical scanning of the retina, and the second scanning mirror can also realize the horizontal and vertical tilt under the direct current voltage drive, so as to realize the positioning of the illumination beam to the area of interest of the retina.
  • different scanning imaging functions can be realized, including the large field of view scanning imaging function, which can obtain imaging images of the retina; the small field of view high-resolution imaging function can achieve arbitrary retina Small field of view high-resolution imaging observation at the position of interest; large field of view high-resolution imaging function, according to the fundus retina position coordinates of the high-resolution imaging images of each area, stitching each image, can get the large field of view and high resolution of the fundus retina Rate imaging images.
  • the large-field adaptive optics retinal imaging system and method with common optical path beam scanning can obtain large-field-of-field imaging images of the fundus retina, small-field high-resolution imaging images of any region of interest, and large-field high-resolution imaging Rate imaging images, and the three types of imaging images are acquired by the common optical path structure, so the three types of imaging images have good consistency and are easy to process and operate.
  • the system is simple in structure, and the common optical path structure can obtain three types of retinal imaging images: By switching between different synchronous scanning modes, both large field of view imaging can be used to observe the retinal disease focus area, and small field of view high-resolution imaging can be used to observe the focus Fine structure.
  • Large-field imaging images can observe features such as structures and lesions in a large area of the retina
  • small-field high-resolution imaging images can observe the fine structure of any region of interest
  • large-field high-resolution imaging images can observe the retina in a large area Fine structure.
  • a variety of imaging images are acquired through common optical path beam scanning to meet the needs of different application scenarios and greatly increase the application range of retinal imaging.
  • FIG. 1 is a schematic block diagram of a large field of view adaptive optics retinal imaging system with common optical path beam scanning of the present application;
  • FIG. 2 is a schematic diagram of the optical path structure of the large-field adaptive optics retinal imaging system with common optical path beam scanning of the application;
  • FIG. 3 is a schematic diagram of the working process of the large-field adaptive optics retinal imaging system with common optical path beam scanning of the present application;
  • a common optical path beam scanning large field of view adaptive optics retinal imaging system of this embodiment includes: a light source module 1, an adaptive optics module 2, a beam scanning module 3, and a defocus compensation module 4.
  • the light source module 1 emits a parallel light beam, and then passes through the adaptive optics module 2, the beam scanning module 3, and the defocus compensation module 4 to illuminate the human eye 5.
  • the imaging light scattered by the human eye 5 carries human eye aberration information and light intensity information. Return to the original path and transmit to the adaptive optics module 2 and the detection module 8;
  • the adaptive optics module 2 is used to receive the imaging light containing human eye aberration information, and realize the real-time measurement and correction of human eye aberration;
  • the beam scanning module 3 is controlled by the control module 9 and can be configured into different scanning modes to realize different scanning imaging functions, including at least: large field of view imaging function, small field of view high resolution imaging function, and large field of view high resolution imaging function Imaging function;
  • the defocus compensation module 4 is used for realizing compensation for the refractive error of the human eye
  • the optotype module 6 is used to realize the guidance and fixation of different areas of the retina of the human eye;
  • the pupil monitoring module 7 is used to realize the alignment and monitoring of the pupil of the human eye
  • the detection module 8 is used to obtain the returned human eye imaging light, convert it into an electrical signal, and transmit it to the control module 9;
  • the output module 10 is connected to the control module 9 for displaying and storing human eye imaging images (fundus retinal imaging images and pupil imaging images).
  • the light source module 1, the adaptive optics module 2, the beam scanning module 3, the visual target module 6, the defocus compensation module 4, and the pupil monitoring module 7 are arranged in sequence along the incident light path;
  • the light source module 1 is configured as a light source arranged in sequence along the incident light path 101, a collimator 102, and a first beam splitter 103, which output parallel light beams to the adaptive optics module 2;
  • the light emitted by the light source 101 is partially transmitted through the first beam splitter 103 after the collimator 102 and enters the adaptive optics module 2.
  • the light source module 1 may include multiple light sources 101.
  • the multiple light sources 101 may be coupled into the collimator 102 through a fiber coupler to be collimated into parallel beams; the multiple light sources 101 may also be collimated into parallel beams by their respective collimators 102.
  • the light beams are coupled into the optical path through a dichroic beam splitter; the multiple light sources 101 may include typical fundus imaging illumination wavelengths, such as 488nm, 515nm, 650nm, 680nm, 780nm, 830nm and other characteristic wavelengths.
  • the collimator 102 may be a single lens, an achromatic lens, an apochromatic lens or a parabolic mirror, and is used to collimate the light beam emitted from the light source 101 into a parallel light beam.
  • the reflective collimator 102RC12FC-P01 from Thorlabs is selected.
  • the first beam splitter 103 is a wide-band beam splitter, and its transmittance and reflectance ratio is 20:80. 20% of the parallel beam emitted by the collimator 102 passes through the first beam splitter 103 and continues to propagate into the adaptive optics module 2, and 80% of the imaging beam returned by the adaptive optics module 2 is reflected by the first beam splitter 103 and enters the detection module 8 .
  • the first dichroic beam splitter 603 has a transmission effect on all wavelengths included in the light source 101
  • the second dichroic beam splitter 702 has a transmission effect on all wavelengths included in the light source 101.
  • the adaptive optics module 2 is configured as a second beam splitter 201, a wavefront corrector 202, a transmissive or reflective telescope 203, and a wavefront sensor 204 arranged in sequence along the incident light path, which are connected to the beam scanning module 3 for Realize wavefront aberration detection and correction;
  • the parallel beam output by the light source module 1 partially transmits through the second beam splitter 201 and then is reflected by the wavefront corrector 202 to the transmissive or reflective telescope 203, and enters the beam scanning module 3;
  • the imaging light with human eye aberration information and light intensity information exits through the beam scanning module 3 into the transmissive or reflective telescope 203, and then is reflected by the wavefront corrector 202 to the second beam splitter 201, and part of the imaged light is by the second beam splitter 201 is reflected to the wavefront sensor 204 to achieve wavefront aberration measurement, and the rest of the imaging light is transmitted through the second beam splitter 201 to continue to propagate;
  • the wavefront aberration detected by the wavefront sensor 204 is processed by the control module 9 to obtain a wavefront control voltage and output to the wavefront corrector 202 to realize the correction of the wavefront aberration.
  • the wavefront sensor 204 included in the adaptive optics module 2 is one of a microprism array Hartmann wavefront sensor, a microlens array Hartmann wavefront sensor, a quadrangular pyramid sensor, and a curvature sensor.
  • the wavefront corrector 202 is a deformation sensor.
  • the second beam splitter 201 is a wide-band beam splitter with a transmittance and reflectance ratio of 95:5.
  • 95% of the parallel beam output by the light source module 1 is transmitted through the second beam splitter 201 to the wavefront corrector 202; the returned imaging beam is reflected by the wavefront corrector 202 to the second beam splitter 201 for splitting, of which 5% of the light energy is reflected into
  • the wavefront sensor 204 realizes wavefront aberration measurement; the remaining 95% of the light energy is transmitted to the first beam splitter 103 and continues to propagate.
  • the detection module 8 is configured as a collection lens 801, a confocal pinhole 802 and a high-sensitivity detector 803.
  • the returned imaging beam is transmitted through the second beam splitter 201 of the adaptive optics module 2, and reaches the first beam splitter 103, and is then
  • the first beam splitter 103 is reflected to the collection lens 801, focused through the confocal pinhole 802, and then reaches the high-sensitivity detector 803, undergoes photoelectric conversion to obtain electrical signals, and then outputs them to the control module 9 for processing to obtain retinal imaging images, which are finally output to
  • the output module 10 performs display and storage; the confocal pinhole 802 is arranged at the focal point of the collecting lens 801.
  • the collecting lens 801 may be an achromatic lens, or an apochromatic lens, or a combination of lenses, and its focal length is not less than 100 mm.
  • the confocal pinhole 802 is 50 microns, and its size can be changed according to the light energy efficiency, and does not exceed 200 microns.
  • the high-sensitivity detector 803 may be a photomultiplier tube or an avalanche diode.
  • the beam scanning module 3 is configured as a first scanning mirror 301 and a second scanning mirror 303.
  • the two scanning mirrors are connected through a transmission type telescope or a reflection type telescope 302 to achieve pupil-plane matching; the first scanning mirror 301 achieves alignment to the retinal plane
  • the second scanning mirror 303 realizes the vertical scanning of the retinal plane under the driving of periodic voltage.
  • the second scanning mirror 303 can generate a certain horizontal and vertical tilt angle under the driving of the DC voltage.
  • the second scanning mirror 303 is driven by the DC voltage.
  • the horizontal and vertical tilt angles are generated under voltage drive, and the horizontal and vertical two-dimensional scanning of the retinal plane can be realized under the periodic voltage drive;
  • the front and rear positions of the first scanning mirror 301 and the second scanning mirror 303 can be interchanged, without affecting the imaging effect;
  • the beam scanning module 3 is controlled by the output voltage signal of the control module 9, and can be configured into different scanning modes to achieve different imaging functions, including: large field of view imaging function, small field of view high resolution imaging function and large field of view high resolution imaging Features.
  • the first scanning mirror 301 is a resonant galvanometer 6SC08KA040-02Y from Cambrige Company
  • the second scanning mirror 303 is a fast mirror MR-30-15-G-25 ⁇ 25D from Optotune Company.
  • the defocus compensation module 4 is configured as a scanning objective lens 401, a plan objective lens 402, and a guide 403 which are sequentially arranged along the incident light path.
  • the exit beam of the beam scanning module 3 propagates through the defocus compensation module 4 to the pupil monitoring module 7, and the plan objective lens
  • the 402 can reciprocate along the central axis of the plan objective lens 402 on the guide rail 403 to realize the compensation for the refractive error of the human eye.
  • the extending direction of the guide rail 403 is consistent with the direction of the central axis of the plan objective lens 402, and the plan objective lens 402 is slidably arranged on the guide rail 403.
  • the plan objective lens 402 is connected to the guide rail 403 through a motor, and the plan objective lens 402 can be controlled to move back and forth along its central axis through the control module 9 to realize the compensation for the refractive error of the human eye.
  • the scanning objective lens 401 is an achromatic lens, or an apochromatic lens, or an aspheric lens, or a combination of lenses, and the field of view angle is greater than 30 degrees, and the plan objective lens 402 may be an achromatic lens or an apochromatic lens. Or an aspheric lens or a combination of lenses to achieve a flat field effect on the fundus retina.
  • the visual standard module 6 is configured as an LED array 601, a lens 602, and a first dichroic beam splitter 603.
  • the light emitted by any lamp bead in the LED array 601 after being lit by the control module 9 is transmitted by the lens 602
  • the first dichroic beam splitter 603 reflects into the defocus compensation module 4 and finally enters the human eye 5.
  • the human eye 5 looks at the luminous LED lamp bead to achieve fixation; the beam emitted by the beam scanning module 3 passes through the target module 6
  • the first dichroic beam splitter 603 enters the defocus compensation module 4 and continues to propagate after being transmitted.
  • the LED lamp beads of the LED array 601 select a certain characteristic wavelength in the range of 500nm-600nm.
  • the selected wavelength of the LED array 601 cannot be the same as the wavelength contained in the light source 101, and it must have a wavelength difference of more than 30nm to ensure the first dichroic separation.
  • the mirror 603 has a reflection function for the wavelength selected by the LED array 601, and at the same time has a transmission function for the wavelength selected by the light source 101.
  • the pupil monitoring module 7 is configured as a ring-shaped LED array 701, a second dichroic beam splitter 702, an imaging lens 703, and an area detector 704.
  • the light emitted by the ring-shaped LED array 701 illuminates the 5 pupils of the human eye and passes through the 5 pupils of the human eye. After being reflected, it passes through the hollow part of the annular LED array 701, is completely reflected by the second dichroic beam splitter 702, and is focused by the imaging lens 703 to the area array detector 704.
  • the area array detector 704 converts the optical signal into an electrical signal and outputs it To the control module 9, the pupil imaging image is obtained, and finally output to the output module 10 for display and storage.
  • the LED lamp beads of the annular LED array 701 can be selected at a near-infrared wavelength of 900 nm or above, and the second dichroic beam splitter 702 has a reflection effect on the emission wavelength of the annular LED array 701 lamp beads.
  • the transmission light path is: the light emitted by the light source 101 can be approximated as a point light source 101, collimated into a parallel beam by the collimator 102, and split by the first beam splitter 103, 20% of the light energy is transmitted into the second beam splitter 201 Spectroscopy; 95% of the incident light reaching the second beam splitter 201 is transmitted and reflected by the wavefront corrector 202.
  • the parallel beam continues to pass through the transmissive or reflective telescope 203 to achieve pupil diameter matching, and the first After a scanning mirror 301 is reflected, the pupil diameter is matched by a transmissive or reflective telescope 302, and after reaching the second scanning mirror 303, it is reflected, transmitted by the first dichroic beam splitter 603, and then sequentially passed through the scanning objective lens 401 and the flat field
  • the objective lens 402 transmits, then passes through the second dichroic beam splitter 702 and then passes through the hollow part of the annular LED array 701 to reach the human eye 5, and the light beam is focused to a point on the fundus retina through the optical system of the human eye 5;
  • the human eye fundus has a scattering effect on the incident light.
  • the scattered imaging light carries the aberration information of the human eye and the light intensity information of the fundus. It returns to the second beam splitter 201 along the original path, and the second beam splitter 201 affects this part.
  • the scattered light is split again: 5% of the light energy enters the wavefront sensor 204 through reflection; the remaining 95% of light energy is transmitted to the first beam splitter 103 through transmission.
  • the first beam splitter 103 reflects 80% of the light energy into the collection lens 801, passes through the confocal pinhole 802, and then reaches the high-sensitivity detector 803.
  • the high-sensitivity detector 803 performs photoelectric conversion to obtain an electrical signal, and then outputs it to the control module 9 for processing. After processing, the retinal imaging image is obtained, and finally output to the output module 10 for display and storage.
  • Subject's related process mainly including pupil alignment and monitoring, refractive error compensation and correction, visual target guidance and fixation.
  • the pupil monitoring module 7 includes a ring-shaped LED array 701, a second dichroic beam splitter 702, an imaging lens 703, and an area detector 704.
  • the ring-shaped LED array 701 includes at least three LED lamp beads, which are arranged in a ring at equal intervals and are hollow. The light transmission aperture of the part is not less than the imaging beam aperture.
  • the emitted light of the annular LED array 701 reaches the pupil of the human eye 5, and the light beam reflected by the pupil of the human eye 5 passes through the hollow part of the annular LED array 701 and passes through the second dichroic beam splitter. After 702 is reflected, it is focused on the area array detector 704 by the imaging lens 703.
  • the area array detector 704 converts the optical signal into an electrical signal, outputs it to the control module 9 to obtain the pupil imaging image, and outputs it to the output module 10 for display, storage, and Processing and other functions.
  • the subject’s head is located on the headrest, and the headrest has a three-dimensional translation adjustment function.
  • the three-dimensional translation guide of the headrest can be adjusted manually, or it can be configured as a motor-driven three-dimensional translation of the headrest.
  • the guide rail is automatically adjusted by the motor driven by the control module 9 so that the pupil is imaged in the middle area of the field of view.
  • the defocus compensation module 4 includes a scanning objective lens 401, a plan objective lens 402, and a guide rail 403.
  • the extension direction of the guide rail 403 is consistent with the direction of the central axis of the plan objective lens 402.
  • the plan objective lens 402 is slidably arranged on the guide rail 403. After the incident light exits from the beam scanning module 3, it sequentially passes through the scanning objective lens 401 and the flat field objective lens 402, and the flat field objective lens 402 is controlled to move back and forth along its central axis through the control module 9 to realize the compensation for the refractive error of the human eye.
  • the visual standard module 6 includes an LED array 601, a lens 602, and a first dichroic beam splitter 603.
  • One LED lamp bead in the LED array 601 is lit by the control module 9, and the light emitted by the LED lamp bead reaches the first dichroic lens 602 through the lens 602.
  • the dichroic beam splitter 603 is reflected by the first dichroic beam splitter 603, enters the plan objective lens 402 and propagates, passes through the scanning objective lens 401, the plan objective lens 402, and the second dichroic beam splitter 702 in turn, and then passes through the annular LED array
  • the hollow part of 701 reaches the human eye and is focused on the fundus retina through the optical system of the human eye.
  • the human eye looks at the LED luminous point to achieve fixation.
  • control module 9 illuminating the lamp beads at different positions on the LED array 601, different areas of the fundus retina will be guided into imaging areas.
  • the returned imaging light carrying human eye aberration information and light intensity information passes through the beam scanning module 3 and enters the transmissive or reflective telescope 203, and then is reflected by the wavefront corrector 202 to the second beam splitter 201.
  • Part of the imaging light is
  • the two beam splitter 201 is reflected to the wavefront sensor 204 to achieve wavefront aberration measurement, and the remaining imaging light is transmitted through the second beam splitter 201 to continue to propagate; after the wavefront sensor receives the light beam containing human eye aberration information, it is transmitted to the control module 9.
  • the control module 9 obtains the wavefront correction voltage through wavefront calculation and outputs it to the wavefront corrector 202, and the wavefront corrector 202 realizes real-time correction of human eye aberrations.
  • the beam scanning module 3 includes a first scanning mirror 301 and a second scanning mirror 303, and the two scanning mirrors are connected by a transmissive telescope or a reflective telescope 302 to achieve pupil surface matching.
  • the front and rear positions of the first scanning mirror 301 and the second scanning mirror 303 can be interchanged without affecting the imaging effect.
  • the first scanning mirror 301 and the second scanning mirror 303 are controlled by the output voltage signal of the control module 9 and can be configured in different scanning modes to realize different imaging functions.
  • the adaptive optics module 2 is in the shutdown state, or the startup is not working;
  • the first scanning mirror 301 is driven by a periodic voltage signal to realize the lateral scanning of the retinal plane; the second scanning mirror 303 is driven by a periodic voltage signal to realize the longitudinal scanning of the retinal plane.
  • the retina scanning angle of the first scanning mirror 301 and the second scanning mirror 303 driven by the periodic voltage signal is not less than 20 degrees;
  • the detection module 8 converts the acquired light signal of the fundus retina into electrical signals.
  • the control module 9 synchronizes the periodic driving voltage signals of the first scanning mirror 301 and the second scanning mirror 303, and the control module 9 samples the electrical signals to reconstruct the retina.
  • the large-field imaging image is output to the output module 10 for display, storage, and processing functions.
  • the adaptive optics module 2 is in the power-on working state to realize the measurement and correction of wavefront aberration
  • the first scanning mirror 301 is driven by a periodic voltage signal to realize the horizontal scanning of the retinal plane; the second scanning mirror 303 can generate a certain horizontal and vertical inclination angle under the driving of a DC voltage signal, which is used to illuminate the light beam that illuminates the fundus retina. Locate at the position of interest, and then realize the longitudinal scanning of the retinal plane under the drive of the periodic voltage signal; the scanning angle of the retina under the drive of the periodic voltage signal of the first scanning mirror 301 and the second scanning mirror 303 is not greater than 5 degrees ;
  • the DC voltage signal is calculated by the control module 9 according to the coordinate position of the fundus retina
  • the detection module 8 converts the acquired light signal of the fundus retina into electrical signals.
  • the control module 9 synchronizes the periodic driving voltage signals of the first scanning mirror 301 and the second scanning mirror 303, and the control module 9 samples the electrical signals to reconstruct the retina.
  • the adaptive optics module 2 is in the power-on working state to realize the measurement and correction of wavefront aberration
  • the first scanning mirror 301 is driven by the periodic voltage signal to realize the horizontal scanning of the retinal plane;
  • the second scanning mirror 303 is driven by the periodic voltage signal to realize the longitudinal scanning of the retinal plane;
  • the first scanning mirror 301, the second The scanning angle of the retina of the scanning mirror 303 driven by the periodic voltage signal is not greater than 5 degrees;
  • the second scanning mirror 303 can generate a certain horizontal and vertical tilt angle under the driving of the DC voltage signal, and tilt the light beam to illuminate each area of the fundus retina in turn.
  • the single horizontal and vertical tilt angle of the second scanning mirror 303 is not more than 3 degrees.
  • the maximum lateral and longitudinal tilt angle of the retina of the second scanning mirror 303 driven by the DC voltage signal is not greater than 15 degrees; the DC voltage signal is calculated by the control module 9 according to the coordinate position of the fundus retina;
  • the control module 9 can obtain high-resolution imaging images of each area of the retina.
  • the control module 9 stitches each image according to the position coordinates of the fundus retina of the high-resolution imaging images of each area to obtain The large field of view high-resolution image of the fundus retina is then output to the output module 10 for display, storage, processing and other functions.
  • the present application also provides a common optical path beam scanning large-field adaptive optics retinal imaging method, which adopts the above system for imaging, referring to FIG. 3, which includes the following steps:
  • Step S1 Turn on and start the system
  • Step S2 The subject’s head is placed on the headrest, the pupil monitoring module 7 is turned on, and the three-dimensional translation of the headrest is automatically adjusted by manual adjustment or the control module 9 so that the pupil is imaged in the middle area of the field of view;
  • Step S3 Manually slide the plan objective lens 402 to move along the center of the optical axis, or move the position of the plan objective lens 402 on the guide rail 403 through the control module 9 to drive the motor to realize the compensation and correction of the refractive error of the human eye;
  • Step S4 Turn on a lamp bead in the LED array 601, and the subject will look at the light spot to achieve fixation;
  • Step S5 The adaptive optics module 2 is turned off or turned on and not working, the beam scanning module 3 is set to the large field of view scanning mode, and the control module 9 controls the beam scanning module 3 to complete the large field of view scanning, and realizes the retina large field of view imaging and output To output module 10;
  • Step S6 The adaptive optics module 2 is in power-on operation to realize wavefront aberration measurement and correction, and the control module 9 controls the beam scanning module 3 to perform small field of view scanning;
  • Step S61 the control module 9 controls the beam scanning module 3 to complete the small field of view high-resolution imaging image output to the output module 1010;
  • Step S62 the control module 9 controls the beam scanning module 3 to complete a large field of view high-resolution imaging image and output it to the output module 10.
  • step S5 and step S6 can be reversed.
  • step S61 and step S62 can be selected according to actual needs.
  • the existing laser confocal scanning ophthalmoscope has a large imaging field, but the resolution is not enough to observe the fine structure of the retina; the laser confocal scanning ophthalmoscope combined with adaptive optics can observe the fine structure of the retina, but the imaging field is small and cannot Observe the condition of the lesion with a larger field of view.
  • this application proposes a common optical path beam scanning large field of view adaptive optical retinal imaging system based on the basic principles of adaptive optics combined with confocal scanning technology.
  • the common optical path structure of the two scanning mirrors allows the two scanning mirrors to be configured in different scanning imaging modes, which can image the retina with a large field of view of more than 20 degrees for observing the focal area of retinal diseases; Scanning imaging with a small field of view over 5 degrees, under the condition of adaptive optics to correct aberrations, realize small field of view high-resolution imaging to observe the fine structure and pathological changes of the lesion, and further set up a second scanning mirror 302 to realize the light beam in each area of the retina.
  • Oblique illumination, and then through image stitching can obtain high-resolution imaging of the retina with a large field of view over 15 degrees at a time.
  • This application proposes a large field of view adaptive optical retinal imaging system with common optical path beam scanning, which uses two scanning mirrors to form a common optical path beam scanning structure.
  • the first scanning mirror 301 realizes the horizontal scanning of the retina
  • the second scanning mirror 303 realizes the vertical scanning of the retina.
  • the second scanning mirror 303 can also realize the horizontal and vertical tilt under the direct current voltage drive, so as to realize the positioning of the illumination beam to the retina. Region of interest.
  • the first scanning mirror 301 is registered for horizontal scanning, and the second scanning mirror 303 is configured for vertical scanning.
  • the scanning angle of the retina of the two scanning mirrors is not less than 20 degrees.
  • the adaptive optics correction function fails, and it is turned off or not working. State, obtain the large-field imaging image of retina.
  • the first scanning mirror 301 is registered for horizontal scanning, and the second scanning mirror 303 is configured for vertical scanning.
  • the scanning angle of the retina of the two scanning mirrors is not more than 5 degrees.
  • the adaptive optics completes the aberration measurement and correction function to obtain the image A high-resolution image of the retina with a small field of view after correction.
  • the second scanning mirror 303 can also generate lateral and longitudinal tilt under the drive of a DC voltage signal, which is used to position the light beam illuminating the fundus retina at a position of interest, so as to realize a small field of view and high-resolution imaging observation of any interested position of the retina.
  • the first scanning mirror 301 is registered for horizontal scanning, and the second scanning mirror 303 is configured for vertical scanning.
  • the scanning angle of the retina of the two scanning mirrors is not more than 5 degrees.
  • the adaptive optics completes the aberration measurement and correction function to obtain the image A high-resolution image of the retina with a small field of view after correction.
  • the second scanning mirror 303 can also be driven by a DC voltage signal to generate lateral and longitudinal tilts, position the light beam illuminating the fundus retina at a position of interest, and is configured to tilt the light beam to illuminate each area of the fundus retina in turn.
  • the second scanning mirror 303 is single The secondary lateral and longitudinal tilt angles are not greater than 3 degrees, and the maximum lateral and longitudinal tilt angles of the retina of the second scanning mirror 303 driven by a direct current voltage are not greater than 15 degrees.
  • control module 9 stitches each image according to the position coordinates of the fundus retina of the high-resolution imaging images of each area to obtain the fundus retina. High-resolution imaging images with a large field of view.
  • the large-field adaptive optics retinal imaging system and method with common optical path beam scanning can obtain large-field-of-field imaging images of the fundus retina, small-field high-resolution imaging images of any region of interest, and large-field high-resolution imaging Rate imaging images, and the three types of imaging images are acquired by the common optical path structure, so the three types of imaging images have good consistency and are easy to process and operate.
  • the system is simple in structure, and the common optical path structure can obtain three types of retinal imaging images: By switching between different synchronous scanning modes, both large field of view imaging can be used to observe the retinal disease focus area, and small field of view high-resolution imaging can be used to observe the focus Fine structure.
  • Large-field imaging images can observe features such as structures and lesions in a large area of the retina
  • small-field high-resolution imaging images can observe the fine structure of any region of interest
  • large-field high-resolution imaging images can observe the retina in a large area Fine structure.
  • a variety of imaging images are acquired through common optical path beam scanning to meet the needs of different application scenarios and greatly increase the application range of retinal imaging.

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Abstract

一种共光路光束扫描的大视场自适应光学视网膜成像系统和方法，该系统包括：光源模块（1）、自适应光学模块（2）、光束扫描模块（3）、离焦补偿模块（4）、视标模块（6）、瞳孔监测模块（7）、探测模块（8）、控制模块（9）和输出模块（10）。其中，光束扫描模块（3）可配置为不同的扫描模式，以实现不同的扫描成像功能，包括：大视场成像图像、小视场高分辨率成像图像以及大视场高分辨率成像图像。该系统结构简单，共光路结构可以获取三种类型的视网膜成像图像，满足不同的应用场景需求，提高了视网膜成像的应用范围。

Description

共光路光束扫描的大视场自适应光学视网膜成像系统和方法
交叉引用
本申请要求在2019年9月9日提交中国专利局、申请号为201910864687.6、申请名称为“共光路光束扫描的大视场自适应光学视网膜成像系统和方法”的中国专利申请的优先权，其全部内容通过引用结合在本申请中。
技术领域
本申请涉及光学成像技术领域，特别涉及一种共光路光束扫描的大视场自适应光学视网膜成像系统和方法。
背景技术
传统的共焦扫描技术，在1987年发展成为成熟的激光共焦扫描成像设备(Webb R，Hughes G，Delori F.Confocal scanning laser ophthalmoscope.Applied optics.1987；26(8)：1492-9)，并且广泛应用于视网膜成像，可以实现大视场的眼底视网膜活体成像。但是，眼球是一个复杂的光学系统，即使是无屈光不正的眼睛也不可避免地存在光学像差，尤其是为了获得大数值孔径下的高分辨率图像，大瞳孔下根据光学理论可以得到衍射极限的更高分辨率，但大瞳孔带来更多的人眼像差极大地限制了实际分辨率，传统的激光共焦扫描检眼镜通常可以获取眼底10度以上大视场成像图像，但是很难分辨20微米以下的血管，更谈不上观察视细胞等微细结构。
十九世纪九十年代，随着自适应光学技术被引入眼底视网膜成像中，利用自适应光学变形镜等校正器件可以很好地校正人眼像差，从而获取衍射极限的高分辨率，首次实现活体观察视网膜微细血管和视细胞。专利号为ZL201010197028.0的申请专利提出基于自适应光学技术的视网膜成像装置，该装置通过两个独立的扫描振镜实现视网膜平面二维同步扫描，用以实现共焦扫描成像，可实现高分辨率成像功能。但是，该装置只能实现人眼最大3度视场的高分辨率成像。受自适应光学像差校正等晕区的限制，自适应光学在实现高分辨率成像的同时，往往在成像视场上作出了妥协，只能实现3°以内的小视场成像。
综上所述可知，现有的激光共焦扫描检眼镜成像视场大，但是分辨率不足以观察视网膜微细结构；结合自适应光学的激光共焦扫描检眼镜可以观察视网膜微细结构，但是成像视场小，无法观察较大视场的病灶情况。
申请内容
本申请所要解决的技术问题在于针对上述现有技术中的不足，提供一种共光路光束扫描的大视场自适应光学视网膜成像系统。
众所周知，现有的激光共焦扫描检眼镜成像视场大，但是分辨率不足以观察视网膜微细结构；结合自适应光学的激光共焦扫描检眼镜可以观察视网膜微细结构，但是成像视场小，无法观察较大视场的病灶情况。
对比国内外在激光共焦扫描成像领域的技术成果，本申请在自适应光学结合共焦扫描技术的基本原理基础上，提出一种共光路光束扫描的大视场自适应光学视网膜成像系统，采用两块扫描镜共光路结构，将两块扫描镜配置为不同的扫描方式，既可以对视网膜完成超过20度的大视场成像，用于观察视网膜疾病病灶区域；也可以对视网膜完成不超过5度的小视场扫描成像，在自适应光学校正像差的情况下，实现小视场高分辨率成像观察病灶微细结构和病理改变，进一步地设置第二扫描镜实现光束在视网膜各个区域依次倾斜照明，然后通过图像拼接，可以一次获取视网膜超过15度的大视场高分辨率成像。
本申请采用的技术方案是：一种共光路光束扫描的大视场自适应光学视网膜成像系统，包括：光源模块、自适应光学模块、光束扫描模块、离焦补偿模块、视标模块、瞳孔监测模块、探测模块、控制模块和输出模块；
所述光源模块出射平行光束，依次经过所述自适应光学模块、光束扫描模块、离焦补偿模块照射到人眼，人眼散射的携带人眼像差信息和光强信息的成像光沿原路返回，并传输到所述自适应光学模块和探测模块；
所述自适应光学模块用于接收含人眼像差信息的成像光，并实现人眼像差的实时测量和校正；
所述光束扫描模块由所述控制模块控制，可配置为不同的扫描模式，用于实现不同的扫描成像功能，至少包括：大视场成像功能、小视场高分辨率成像功能和大视场高分辨率成像功能；
所述离焦补偿模块用于实现对人眼屈光不正的补偿；
所述视标模块用于实现对人眼视网膜不同区域的引导与固视；
所述瞳孔监测模块用于实现对人眼瞳孔的对准与监测；
所述探测模块用于获取返回的人眼成像光，并转换为电信号后传输至所述控制模块；
所述输出模块与所述控制模块连接，用于对人眼成像图像进行显示和存储。
优选的是，所述光源模块、自适应光学模块、光束扫描模块、视标模块、离焦补偿模块、瞳孔监测模块沿入射光路依次设置；
所述光源模块配置为沿入射光路依次设置的光源、准直器以及第一分光镜，其输出平行光束至所述自适应光学模块；所述光源发出的光经所述准直器后部分透射所述第一分光镜，进入所述自适应光学模块；
所述自适应光学模块配置为沿入射光路依次设置的第二分光镜、波前校正器、透射式或反射式望远镜以及波前传感器，其与所述光束扫描模块连接，用于实现波前像差探测与校正；所述光源模块输出的平行光束部分透射所述第二分光镜后再由所述波前校正器反射至所述透射式或反射式望远镜，进入所述光束扫描模块；返回的携带人眼像差信息和光强信息的成像光经过所述光束扫描模块出射进入所述透射式或反射式望远镜，再由所述波前校正器反射至所述第二分光镜，部分成像光被所述第二分光镜反射至所述波前传感器，实现波前像差测量，其余成像光透射所述第二分光镜继续传播；
所述波前传感器接收到含有人眼像差信息的成像光束后传输至所述控制模块进行波前计算，得到波前控制电压并输出给所述波前校正器，实现对波前像差的探测与校正。
优选的是，所述探测模块配置为收集透镜、共焦针孔和高灵敏度探测器，返回的成像光中透射所述自适应光学模块的第二分光镜的部分，到达所述第一分光镜，其中的部分成像光再被所述第一分光镜反射到收集透镜，聚焦再经过所述共焦针孔后到达所述高灵敏 度探测器，进行光电转换得到电信号，然后输出给所述控制模块进行处理，得到视网膜成像图像，最终输出至所述输出模块进行显示、存储；
所述共焦针孔设置在所述收集透镜的焦点处。
优选的是，所述光束扫描模块配置为第一扫描镜和第二扫描镜，两片扫描镜通过透射式或反射式望远镜连接用以实现瞳面匹配；所述第一扫描镜实现对视网膜平面的横向扫描，所述第二扫描镜在周期性电压驱动下实现对视网膜平面的纵向扫描，所述第二扫描镜在直流电压驱动下可以产生一定的横向和纵向倾斜角度，所述第二扫描镜在直流电压驱动下产生横向和纵向倾斜角度同时还能在周期性电压驱动下实现对视网膜平面的横向和纵向二维扫描；
所述第一扫描镜和第二扫描镜前后位置可以互换；
所述光束扫描模块由所述控制模块输出电压信号控制，可以配置为不同的扫描模式，实现不同的成像功能，包括：大视场成像功能、小视场高分辨率成像功能和大视场高分辨率成像功能。
优选的是，所述离焦补偿模块配置为沿入射光路依次设置的扫描物镜、平场物镜以及导轨，所述光束扫描模块的出射光束经离焦补偿模块传播至所述瞳孔监测模块，所述平场物镜能够在所述导轨上沿该平场物镜的中心轴线往复移动，实现对人眼屈光不正的补偿。
优选的是，所述视标模块配置为LED阵列、透镜和第一二向色分光镜，所述LED阵列中的任意一个灯珠被所述控制模块点亮后发出的光，经过所述透镜传播后由所述第一二向色分光镜反射进入所述离焦补偿模块并最终进入人眼，人眼注视该发光的LED灯珠，实现固视；所述光束扫描模块出射的光束经所述视标模块的第一二向色分光镜透射后进入所述离焦补偿模块继续传播。
所述瞳孔监测模块配置为环形LED阵列、第二二向色分光镜和成像透镜、面阵探测器，所述环形LED阵列发出的光照明人眼瞳孔，经人眼瞳孔反射后穿过所述环形LED阵列的中空部位，由所述第二二向色分光镜全部反射后被所述成像透镜聚焦到所述面阵探测器，所述面阵探测器将光信号转换成电信号后输出至所述控制模块，得到瞳孔成像图像，最后输出至所述输出模块进行显示、存储。
优选的是，所述控制模块通过输出电压信号对所述光束扫描模块中的所述第一扫描镜和第二扫描镜进行控制，用于实现不同的扫描成像功能；
其中，所述大视场成像功能的实现方法为：
所述自适应光学模块处于关机状态，或开机不工作状态；
所述第一扫描镜在周期性电压信号驱动下，实现对视网膜平面的横向扫描；所述第二扫描镜在周期性电压信号驱动下，实现对视网膜平面的纵向扫描。所述第一扫描镜、第二扫描镜在周期性电压信号驱动下的视网膜扫描角度不小于20度；
所述探测模块将获取的眼底视网膜光信号转换为电信号，经所述控制模块将第一扫描镜和第二扫描镜的周期性驱动电压信号同步，所述控制模块将所述电信号采样重构得到视网膜大视场成像图像，并输出至所述输出模块进行显示、存储；
其中，所述小视场高分辨率成像功能的实现方法为：
所述自适应光学模块处于开机工作状态，实现对波前像差的测量与校正；
所述第一扫描镜在周期性电压信号驱动下，实现对视网膜平面的横向扫描；所述第二扫描镜在直流电压信号驱动下可以产生一定的横向和纵向倾斜角度，用于将照明眼底视网膜的光束定位在感兴趣的位置，随后在周期性电压信号驱动下，实现对视网膜平面的纵向扫描；所述第一扫描镜、第二扫描镜在周期性电压信号驱动下的视网膜扫描角度不大于5度；
所述直流电压信号由所述控制模块根据眼底视网膜坐标位置计算得到；
所述探测模块将获取的眼底视网膜光信号转换为电信号，经所述控制模块将第一扫描镜和第二扫描镜的周期性驱动电压信号同步，所述控制模块将所述电信号采样重构得到视网膜小视场高分辨率成像图像，同时将眼底视网膜坐标位置并标记在所述成像图像中；所述小视场高分辨率成像图像经所述控制模块输出至所述输出模块进行显示、存储；
其中，所述大视场高分辨率成像功能的实现方法为:
所述自适应光学模块处于开机工作状态，实现对波前像差的测量与校正；
所述第一扫描镜在周期性电压信号驱动下，实现对视网膜平面的横向扫描；所述第二扫描镜在周期性电压信号驱动下，实现对视网膜平面的纵向扫描；所述第一扫描镜、第二扫描镜在周期性电压信号驱动下的视网膜扫描角度不大于5度；
此时，所述第二扫描镜在直流电压信号驱动下可以产生一定的横向和纵向倾斜角度，将光束依次倾斜照明眼底视网膜各个区域，所述第二扫描镜单次横向和纵向倾斜角度不大于3度，所述第二扫描镜在直流电压信号驱动下的视网膜最大横向和纵向倾斜角度不大于15度；所述直流电压信号由所述控制模块根据眼底视网膜坐标位置计算得到；
当眼底视网膜各个区域依次被光束照明时，所述控制模块可以获取得到视网膜各个区域的高分辨率成像图像，所述控制模块根据各个区域高分辨率成像图像的眼底视网膜位置坐标将各个图像进行拼接，得到眼底视网膜的大视场高分辨率图像，然后输出至所述输出模块进行显示、存储。
优选的是，所述光源模块可以包括多个光源，多个光源可以通过光纤耦合器耦合进入准直器被准直为平行光束；多个光源也可以分别经各自的准直器准直为平行光束后经二向色分光镜耦合进入光路中；
所述准直器可以是单透镜、消色差透镜、复消色差透镜或抛物面反射镜，用于将光源出射的光束准直为平行光束；
所述第一分光镜为宽波段分光镜，所述准直器出射的平行光束20％透过所述分光镜继续传播进入所述自适应光学模块，经自适应光学模块返回的出射成像光束80％经所述第一分光镜反射进入所述探测模块。
优选的是，所述自适应光学模块包含的所述波前传感器为微棱镜阵列哈特曼波前传感器、微透镜阵列哈特曼波前传感器、四棱锥传感器和曲率传感器中的一种，所述波前校正器为变形反射镜、液晶空间光调制器、微加工薄膜变形镜、微机电变形镜、双压电陶瓷变形镜、液体变形镜中的一种。
所述光源模块输出的平行光束95％经所述第二分光镜透射至波前校正器；返回的成像光束经所述波前校正器反射至所述第二分光镜分光，其中5％光能被反射进入所述波前传感器，实现波前像差测量；其余95％光能被透射至所述第一分光镜继续传播。
一种共光路光束扫描的大视场自适应光学视网膜成像方法，其采用如上所述的系统进行成像，其包括以下步骤：
步骤S1：开机，启动系统；
步骤S2：被试者头部置于托头架上，开启所述瞳孔监测模块，通过手动调节或控制模块自动调节托头架三维平移，使得瞳孔成像在视场中间区域；
步骤S3：手动滑动平场物镜沿光轴中心移动，或通过控制模块驱动电机移动平场物镜在导轨上的位置，实现对人眼屈光不正的补偿与校正；
步骤S4：点亮LED阵列中的一个灯珠，受试者注视该光点，实现固视；
步骤S5：自适应光学模块处于关机或开机不工作状态，光束扫描模块设置为大视场扫描模式，控制模块控制光束扫描模块完成大视场扫描，实现视网膜大视场成像并输出至输出模块；
步骤S6：自适应光学模块处于开机工作，用于实现波前像差测量与校正，控制模块控制光束扫描模块进行小视场扫描，可以包含两种小视场扫描模式S61和S62；
步骤S61：控制模块控制光束扫描模块完成小视场高分辨率成像图像输出至输出模块10；
步骤S62：控制模块控制光束扫描模块完成大视场高分辨率成像图像并输出至输出模块。
其中，步骤S5和步骤S6顺序可以对调。步骤S61和步骤S62无顺序关系，可根据需求选取。
本申请的有益效果是：
本申请提出了一种共光路光束扫描的大视场自适应光学视网膜成像系统和方法，本申请的系统采用两块扫描镜组成共光路的光束扫描结构，第一扫描镜实现对视网膜的横向扫描，第二扫描镜实现对视网膜的纵向扫描，同时第二扫描镜还可以在直流电压驱动下实现横向和纵向倾斜，实现将照明光束定位至视网膜感兴趣区域。通过控制两块扫描镜处于不同的扫描方式，可以实现不同的扫描成像功能，包括大视场扫描成像功能，能获取视网膜大视场成像图像；小视场高分辨率成像功能，能实现对视网膜任意感兴趣位置的小视场高分辨率成像观察；大视场高分辨率成像功能，根据各个区域高分辨率成像图像的眼底视网膜位置坐标将各个图像进行拼接，能得到眼底视网膜的大视场高分辨率成像图像。
本申请提供的共光路光束扫描的大视场自适应光学视网膜成像系统和方法，可以获取眼底视网膜大视场成像图像、任意感兴趣区域的小视场高分辨率成像图像、以及大视场高分辨率成像图像，并且三类成像图像由共光路结构采集获得，因此三类成像图像特征一致性好，便于进行处理和操作。同时，该系统结构简单，共光路结构可以获取三种类型的视网膜成像图像：通过切换不同的同步扫描模式，既可以大视场成像观察视网膜疾病病灶区域，也可以小视场高分辨率成像观察病灶微细结构。大视场成像图像可以观察视网膜大范围内的结构和病灶等特征，小视场高分辨率成像图像可以观察任意感兴趣区域的微细结构，大视场高分辨率成像图像可以观察大范围内的视网膜微细结构。多种成像图像通过共光路光束扫描获取，满足不同的应用场景需求，极大地提高了视网膜成像的应用范围。
附图说明
图1为本申请的共光路光束扫描的大视场自适应光学视网膜成像系统的原理框图；
图2为本申请的共光路光束扫描的大视场自适应光学视网膜成像系统的光路结构示意图；
图3为本申请的共光路光束扫描的大视场自适应光学视网膜成像系统的工作流程示意图；
附图标记说明：
1—光源模块；2—自适应光学模块；3—光束扫描模块；4—离焦补偿模块；5—人眼；6—视标模块；7—瞳孔监测模块；8—探测模块；9—控制模块；10—输出模块；101—光源；102—准直器；103—第一分光镜；201—第二分光镜；202—波前校正器；203—透射式望远镜或反射式望远；204—波前传感器；301—第一扫描镜；302—透射式望远镜或反射式望远镜；303—第二扫描镜；401—扫描物镜；402—平场物镜；403—导轨；601—LED阵列；602—透镜；603—第一二向色分光镜；701—环形LED阵列；702—第二二向色分光镜；703—成像透镜；704—面阵探测器；801—收集透镜；802—共焦针孔；803—高灵敏度探测器。
具体实施方式
下面结合实施例对本申请做进一步的详细说明，以令本领域技术人员参照说明书文字能够据以实施。
应当理解，本文所使用的诸如“具有”、“包含”以及“包括”术语并不排除一个或多个其它元件或其组合的存在或添加。
如图1-2所示，本实施例的一种共光路光束扫描的大视场自适应光学视网膜成像系统，包括：光源模块1、自适应光学模块2、光束扫描模块3、离焦补偿模块4、视标模块6、瞳孔监测模块7、探测模块8、控制模块9和输出模块10；
光源模块1出射平行光束，依次经过自适应光学模块2、光束扫描模块3、离焦补偿模块4照射到人眼5，人眼5散射的携带人眼像差信息和光强信息的成像光沿原路返回，并传输到自适应光学模块2和探测模块8；
自适应光学模块2用于接收含人眼像差信息的成像光，并实现人眼像差的实时测量和校正；
光束扫描模块3由控制模块9控制，可配置为不同的扫描模式，用于实现不同的扫描成像功能，至少包括：大视场成像功能、小视场高分辨率成像功能和大视场高分辨率成像功能；
离焦补偿模块4用于实现对人眼屈光不正的补偿；
视标模块6用于实现对人眼视网膜不同区域的引导与固视；
瞳孔监测模块7用于实现对人眼瞳孔的对准与监测；
探测模块8用于获取返回的人眼成像光，并转换为电信号后传输至控制模块9；
输出模块10与控制模块9连接，用于对人眼成像图像(眼底视网膜成像图像和瞳孔成像图像)进行显示、存储。
其中，光源模块1、自适应光学模块2、光束扫描模块3、视标模块6、离焦补偿模 块4、瞳孔监测模块7沿入射光路依次设置；光源模块1配置为沿入射光路依次设置的光源101、准直器102以及第一分光镜103，其输出平行光束至自适应光学模块2；光源101发出的光经准直器102后部分透射第一分光镜103，进入自适应光学模块2。
光源模块1可以包括多个光源101，多个光源101可以通过光纤耦合器耦合进入准直器102被准直为平行光束；多个光源101也可以分别经各自的准直器102准直为平行光束后经二向色分光镜耦合进入光路中；多个光源101可以包含典型的眼底成像照明波长，例如488nm、515nm、650nm、680nm、780nm、830nm等特征波长。
准直器102可以是单透镜、消色差透镜、复消色差透镜或抛物面反射镜，用于将光源101出射的光束准直为平行光束。本实施例中选取thorlabs公司的反射式准直器102RC12FC-P01。
在本实施例中，第一分光镜103为宽波段分光镜，其透射反射比为20:80。准直器102出射的平行光束20％透过第一分光镜103继续传播进入自适应光学模块2，经自适应光学模块2返回出射的成像光束80％经第一分光镜103反射进入探测模块8。
第一二向色分光镜603对光源101包含的所有波长为透射作用，第二二向色分光镜702对光源101包含的所有波长为透射作用。
其中，自适应光学模块2配置为沿入射光路依次设置的第二分光镜201、波前校正器202、透射式或反射式望远镜203以及波前传感器204，其与光束扫描模块3连接，用于实现波前像差探测与校正；光源模块1输出的平行光束部分透射第二分光镜201后再由波前校正器202反射至透射式或反射式望远镜203，进入光束扫描模块3；返回的携带人眼像差信息和光强信息的成像光经过光束扫描模块3出射进入透射式或反射式望远镜203，再由波前校正器202反射至第二分光镜201，部分成像光被第二分光镜201反射至波前传感器204，实现波前像差测量，其余成像光透射第二分光镜201继续传播；
波前传感器204探测得到的波前像差经控制模块9处理，得到波前控制电压并输出给波前校正器202，实现对波前像差的校正。
自适应光学模块2包含的波前传感器204为微棱镜阵列哈特曼波前传感器、微透镜阵列哈特曼波前传感器、四棱锥传感器和曲率传感器中的一种，波前校正器202为变形反射镜、液晶空间光调制器、微加工薄膜变形镜、微机电变形镜、双压电陶瓷变形镜、液体变形镜中的一种。
在本实施例中，第二分光镜201为宽波段分光镜，其透射反射比为95:5。光源模块1输出的平行光束95％经第二分光镜201透射至波前校正器202；返回的成像光束经波前校正器202反射至第二分光镜201分光，其中5％光能被反射进入波前传感器204，实现波前像差测量；其余95％光能被透射至第一分光镜103继续传播。
其中，探测模块8配置为收集透镜801、共焦针孔802和高灵敏度探测器803，返回的成像光束经自适应光学模块2的第二分光镜201透射，到达第一分光镜103，再被第一分光镜103反射到收集透镜801，聚焦经过共焦针孔802后到达高灵敏度探测器803，进行光电转换得到电信号，然后输出给控制模块9进行处理，得到视网膜成像图像，最终输出至输出模块10进行显示、存储；共焦针孔802设置在收集透镜801的焦点处。
收集透镜801可以是消色差透镜、或复消色差透镜、或透镜组合，其焦距不小于100mm。在优选的实施例中，共焦针孔802为50微米，其大小可根据光能效率更换，不超过200微米。高灵敏度探测器803可以是光电倍增管、或雪崩二极管。
其中，光束扫描模块3配置为第一扫描镜301和第二扫描镜303，两片扫描镜通过透射式望远镜或反射式望远镜302连接用以实现瞳面匹配；第一扫描镜301实现对视网膜平面的横向扫描，第二扫描镜303在周期性电压驱动下实现对视网膜平面的纵向扫描，第二扫描镜303在直流电压驱动下可以产生一定的横向和纵向倾斜角度，第二扫描镜303在直流电压驱动下产生横向和纵向倾斜角度同时还能在周期性电压驱动下实现对视网膜平面的横向和纵向二维扫描；
第一扫描镜301和第二扫描镜303前后位置可以互换，不影响成像效果；
光束扫描模块3由控制模块9输出电压信号控制，可以配置为不同的扫描模式，实现不同的成像功能，包括：大视场成像功能、小视场高分辨率成像功能和大视场高分辨率成像功能。
本实施例中，第一扫描镜301为Cambrige公司的共振振镜6SC08KA040-02Y，第二扫描镜303为Optotune公司的快速反射镜MR-30-15-G-25×25D。
其中，离焦补偿模块4配置为沿入射光路依次设置的扫描物镜401、平场物镜402以及导轨403，光束扫描模块3的出射光束经离焦补偿模块4传播至瞳孔监测模块7，平场物镜402能够在导轨403上沿该平场物镜402的中心轴线往复移动，实现对人眼屈光不正的补偿。
导轨403的延伸方向与平场物镜402的中心轴线方向一致，平场物镜402可滑动地设置在导轨403上。
在优选的实施例中，平场物镜402通过电机连接在导轨403上，通过控制模块9能够控制平场物镜402沿其中心轴线往复移动，实现对人眼屈光不正的补偿。进一步优选的，扫描物镜401为消色差透镜、或复消色差透镜、或非球面透镜、或透镜组合，视场角度大于30度，平场物镜402可以是消色差透镜、或复消色差透镜、或非球面透镜、或透镜组合，实现对眼底视网膜平场作用。
其中，视标模块6配置为LED阵列601、透镜602和第一二向色分光镜603，LED阵列601中的任意一个灯珠被控制模块9点亮后发出的光，经过透镜602传播后由第一二向色分光镜603反射进入离焦补偿模块4并最终进入人眼5，人眼5注视该发光的LED灯珠，实现固视；光束扫描模块3出射的光束经视标模块6的第一二向色分光镜603透射后进入离焦补偿模块4继续传播。
LED阵列601的LED灯珠选取500nm-600nm范围内的某种特征波长，LED阵列601所选波长与光源101所含波长不能相同，需具有30nm以上的波长差异，以保证第一二向色分光镜603对LED阵列601所选波长具有反射功能，同时对光源101所选波长具有透射功能。通过控制模块9点亮LED阵列601上不同位置的灯珠，眼底视网膜不同的区域将被引导成为成像区域。
其中，瞳孔监测模块7配置为环形LED阵列701、第二二向色分光镜702和成像透镜703、面阵探测器704，环形LED阵列701发出的光照明人眼5瞳孔，经人眼5瞳孔反射后穿过环形LED阵列701的中空部位，由第二二向色分光镜702全部反射后被成像透镜 703聚焦到面阵探测器704，面阵探测器704将光信号转换成电信号后输出至控制模块9，得到瞳孔成像图像，最后输出至输出模块10进行显示、存储。
环形LED阵列701的LED灯珠可选取900nm或以上近红外波长，第二二向色分光镜702对环形LED阵列701灯珠出射波长为反射作用。
成像系统工作中存在多个过程，包括主光路传输过程、受试者相关过程、自适应光学像差测量与校正过程、扫描成像过程。
1、光路传输过程
传输光路为：光源101发出的光可以近似看作点光源101，经过准直器102准直为平行光束，并由第一分光镜103分光，20％的光能被透射进入第二分光镜201分光；到达第二分光镜201的入射光中，95％的光能被透射后经波前校正器202反射，该平行光束继续经过透射式或反射式望远镜203实现光瞳口径匹配，并由第一扫描镜301反射后，经透射式或反射式望远镜302实现光瞳口径匹配，并到达第二扫描镜303后反射，经第一二向色分光镜603透射后依次经扫描物镜401、平场物镜402透射，接着经第二二向色分光镜702透射后穿过环形LED阵列701的中空部位后到达人眼5，并通过人眼5的光学系统将光束聚焦到眼底视网膜上的一点；
人眼眼底对入射光有散射作用，散射的成像光携带着人眼的像差信息和眼底该点的光强信息，沿原路返回到第二分光镜201，第二分光镜201对这部分散射光再次分光：5％的光能经反射进入波前传感器204；剩余95％的光能经透射传播至第一分光镜103。第一分光镜103将80％的光能反射进入收集透镜801，经过共焦针孔802后到达高灵敏度探测器803，高灵敏度探测器803进行光电转换得到电信号，然后输出给控制模块9进行处理，得到视网膜成像图像，最终输出至输出模块10进行显示、存储。
2、受试者相关过程，主要包括瞳孔对准与监测、屈光不正补偿与校正、视标引导与固视。
(1)瞳孔对准与监测
瞳孔监测模块7包括环形LED阵列701、第二二向色分光镜702、成像透镜703、以及面阵探测器704，环形LED阵列701包含至少三颗LED灯珠，为环形等间距排布，中空部位透光口径不小于成像光束口径，环形LED阵列701的出射光到达人眼5瞳孔，经人眼5瞳孔反射回的光束穿过环形LED阵列701的中空部位，经第二二向色分光镜702反射后，经成像透镜703聚焦到面阵探测器704，面阵探测器704将光信号转换成电信号，输出至控制模块9获取瞳孔成像图像，并输出给输出模块10实现显示、存储、处理等功能。
本申请的系统工作时，受试者头部位于托头架，托头架具有三维平移调节功能，可以通过手动调节托头架的三维平移导轨，也可以配置为电机驱动托头架的三维平移导轨，由控制模块9驱动电机实现自动调节，使得瞳孔成像在视场中间区域。
(2)屈光不正补偿与校正
离焦补偿模块4包括扫描物镜401、平场物镜402以及导轨403，导轨403的延伸方向与平场物镜402的中心轴线方向一致，平场物镜402可滑动地设置在导轨403上。入射光从光束扫描模块3出射后，依次经过扫描物镜401和平场物镜402，通过控制模块9控制平场物镜402沿其中心轴线往复移动，实现对人眼屈光不正的补偿。
(3)视标引导与固视
视标模块6包括LED阵列601、透镜602、第一二向色分光镜603，通过控制模块9点亮LED阵列601中的一个LED灯珠，该LED灯珠发出的光经透镜602到达第一二向色分光镜603，由第一二向色分光镜603反射进入平场物镜402传播，依次经扫描物镜401、平场物镜402、第二二向色分光镜702透射后穿过环形LED阵列701的中空部位后到达人眼，并经人眼的光学系统聚焦到眼底视网膜。
人眼注视该LED发光点，实现固视。
通过控制模块9点亮LED阵列601上不同位置的灯珠，眼底视网膜不同的区域将被引导成为成像区域。
3、自适应光学像差测量与校正过程
返回的携带人眼像差信息和光强信息的成像光经过光束扫描模块3出射进入透射式或反射式望远镜203，再由波前校正器202反射至第二分光镜201，部分成像光被第二分光镜201反射至波前传感器204，实现波前像差测量，其余成像光透射第二分光镜201继续传播；波前传感接收到含有人眼像差信息的光束后，传递给控制模块9，控制模块9通过波前计算，得到波前校正电压并输出给波前校正器202，波前校正器202实现对人眼像差的实时校正。
4、扫描成像过程
光束扫描模块3包括第一扫描镜301和第二扫描镜303，两片扫描镜通过透射式望远镜或反射式望远镜302连接用以实现瞳面匹配。第一扫描镜301和第二扫描镜303前后位置可以互换，不影响成像效果。第一扫描镜301和第二扫描镜303由控制模块9输出电压信号控制，可以配置为不同的扫描模式，实现不同的成像功能。
(1)大视场成像功能，实现方法为：
自适应光学模块2处于关机状态，或开机不工作状态；
第一扫描镜301在周期性电压信号驱动下，实现对视网膜平面的横向扫描；第二扫描镜303在周期性电压信号驱动下，实现对视网膜平面的纵向扫描。第一扫描镜301、第二扫描镜303在周期性电压信号驱动下的视网膜扫描角度不小于20度；
探测模块8将获取的眼底视网膜光信号转换为电信号，经控制模块9将第一扫描镜301和第二扫描镜303的周期性驱动电压信号同步，控制模块9将电信号采样重构得到视网膜大视场成像图像，并输出至输出模块10进行显示、存储、处理等功能。
(2)小视场高分辨率成像功能，实现方法为：
自适应光学模块2处于开机工作状态，实现对波前像差的测量与校正；
第一扫描镜301在周期性电压信号驱动下，实现对视网膜平面的横向扫描；第二扫描镜303在直流电压信号驱动下可以产生一定的横向和纵向倾斜角度，用于将照明眼底视网膜的光束定位在感兴趣的位置，随后在周期性电压信号驱动下，实现对视网膜平面的纵向扫描；第一扫描镜301、第二扫描镜303在周期性电压信号驱动下的视网膜扫描角度不大于5度；
直流电压信号由控制模块9根据眼底视网膜坐标位置计算得到；
探测模块8将获取的眼底视网膜光信号转换为电信号，经控制模块9将第一扫描镜301和第二扫描镜303的周期性驱动电压信号同步，控制模块9将电信号采样重构得到视网膜小视场高分辨率成像图像，同时将眼底视网膜坐标位置并标记在成像图像中；小视场 高分辨率成像图像经控制模块9输出至输出模块10进行显示、存储、处理等功能。
(3)大视场高分辨率成像功能，实现方法为:
自适应光学模块2处于开机工作状态，实现对波前像差的测量与校正；
第一扫描镜301在周期性电压信号驱动下，实现对视网膜平面的横向扫描；第二扫描镜303在周期性电压信号驱动下，实现对视网膜平面的纵向扫描；第一扫描镜301、第二扫描镜303在周期性电压信号驱动下的视网膜扫描角度不大于5度；
此时，第二扫描镜303在直流电压信号驱动下可以产生一定的横向和纵向倾斜角度，将光束依次倾斜照明眼底视网膜各个区域，第二扫描镜303单次横向和纵向倾斜角度不大于3度，第二扫描镜303在直流电压信号驱动下的视网膜最大横向和纵向倾斜角度不大于15度；直流电压信号由控制模块9根据眼底视网膜坐标位置计算得到；
当眼底视网膜各个区域依次被光束照明时，控制模块9可以获取得到视网膜各个区域的高分辨率成像图像，控制模块9根据各个区域高分辨率成像图像的眼底视网膜位置坐标将各个图像进行拼接，得到眼底视网膜的大视场高分辨率图像，然后输出至输出模块10进行显示、存储、处理等功能。
本申请还提供一种共光路光束扫描的大视场自适应光学视网膜成像方法，其采用如上的系统进行成像，参照图3，其包括以下步骤：
步骤S1：开机，启动系统；
步骤S2：被试者头部置于托头架上，开启瞳孔监测模块7，通过手动调节或控制模块9自动调节托头架三维平移，使得瞳孔成像在视场中间区域；
步骤S3：手动滑动平场物镜402沿光轴中心移动，或通过控制模块9驱动电机移动平场物镜402在导轨403上的位置，实现对人眼屈光不正的补偿与校正；
步骤S4：点亮LED阵列601中的一个灯珠，受试者注视该光点，实现固视；
步骤S5：自适应光学模块2处于关机或开机不工作状态，光束扫描模块3设置为大视场扫描模式，控制模块9控制光束扫描模块3完成大视场扫描，实现视网膜大视场成像并输出至输出模块10；
步骤S6：自适应光学模块2处于开机工作，用于实现波前像差测量与校正，控制模块9控制光束扫描模块3进行小视场扫描；
步骤S61：控制模块9控制光束扫描模块3完成小视场高分辨率成像图像输出至输出模块1010；
步骤S62：控制模块9控制光束扫描模块3完成大视场高分辨率成像图像并输出至输出模块10。
其中，步骤S5和步骤S6顺序可以对调。
当完成步骤S6的操作后，步骤S61和步骤S62可根据实际需要进行选择操作。
众所周知，现有的激光共焦扫描检眼镜成像视场大，但是分辨率不足以观察视网膜微细结构；结合自适应光学的激光共焦扫描检眼镜可以观察视网膜微细结构，但是成像视场小，无法观察较大视场的病灶情况。
对比国内外在激光共焦扫描成像领域的技术成果，本申请在自适应光学结合共焦扫描技术的基本原理基础上，提出一种共光路光束扫描的大视场自适应光学视网膜成像系统，采用两块扫描镜的共光路结构，将两块扫描镜配置为不同的扫描成像方式，既可以对视网膜完成超过20度的大视场成像，用于观察视网膜疾病病灶区域；也可以对视网膜完成不超过5度的小视场扫描成像，在自适应光学校正像差的情况下，实现小视场高分辨率成像观察病灶微细结构和病理改变，进一步地设置第二扫描镜302实现光束在视网膜各个区域依次倾斜照明，然后通过图像拼接，可以一次获取视网膜超过15度的大视场高分辨率成像。
本申请提出了一种共光路光束扫描的大视场自适应光学视网膜成像系统，采用两块扫描镜组成共光路的光束扫描结构。第一扫描镜301实现对视网膜的横向扫描，第二扫描镜303实现对视网膜的纵向扫描，同时第二扫描镜303还可以在直流电压驱动下实现横向和纵向倾斜，实现将照明光束定位至视网膜感兴趣区域。
通过控制两块扫描镜处于不同的扫描方式，可以实现不同的扫描成像功能。
(1)大视场扫描成像
第一扫描镜301配准为横向扫描，第二扫描镜303配置为纵向扫描，两块扫描镜的视网膜扫描角度不小于20度，此时，自适应光学校正功能失效，处于关机或开机不工作状态，获取视网膜大视场成像图像。
(2)小视场高分辨率成像
第一扫描镜301配准为横向扫描，第二扫描镜303配置为纵向扫描，两块扫描镜的视网膜扫描角度不大于5度，此时，自适应光学完成像差测量与校正功能，获取像差校正后的视网膜小视场高分辨率成像图像。第二扫描镜303还可以在直流电压信号驱动下产生横向和纵向倾斜，用于将照明眼底视网膜的光束定位在感兴趣的位置，实现对视网膜任意感兴趣位置的小视场高分辨率成像观察。
(3)大视场高分辨率成像
第一扫描镜301配准为横向扫描，第二扫描镜303配置为纵向扫描，两块扫描镜的视网膜扫描角度不大于5度，此时，自适应光学完成像差测量与校正功能，获取像差校正后的视网膜小视场高分辨率成像图像。第二扫描镜303还可以在直流电压信号驱动下产生横向和纵向倾斜，将照明眼底视网膜的光束定位在感兴趣的位置，配置为将光束依次倾斜照明眼底视网膜各个区域，第二扫描镜303单次横向和纵向倾斜角度不大于3度，第二扫描镜303在直流电压驱动下的视网膜最大横向和纵向倾斜角度不大于15度。
当眼底视网膜各个区域依次被光束照明时，可以获取得到视网膜各个区域的高分辨率成像图像，控制模块9根据各个区域高分辨率成像图像的眼底视网膜位置坐标将各个图像进行拼接，得到眼底视网膜的大视场高分辨率成像图像。
本申请提供的共光路光束扫描的大视场自适应光学视网膜成像系统和方法，可以获取眼底视网膜大视场成像图像、任意感兴趣区域的小视场高分辨率成像图像、以及大视场高分辨率成像图像，并且三类成像图像由共光路结构采集获得，因此三类成像图像特征一致性好，便于进行处理和操作。同时，该系统结构简单，共光路结构可以获取三种类型的视网膜成像图像：通过切换不同的同步扫描模式，既可以大视场成像观察视网膜疾病病灶区域，也可以小视场高分辨率成像观察病灶微细结构。大视场成像图像可以观察视网膜大范围内的结构和病灶等特征，小视场高分辨率成像图像可以观察任意感兴趣区域的微细结构，大视场高分辨率成像图像可以观察大范围内的视网膜微细结构。多种成像图像通过共 光路光束扫描获取，满足不同的应用场景需求，极大地提高了视网膜成像的应用范围。
尽管本申请的实施方案已公开如上，但其并不仅仅限于说明书和实施方式中所列运用，它完全可以被适用于各种适合本申请的领域，对于熟悉本领域的人员而言，可容易地实现另外的修改，因此在不背离权利要求及等同范围所限定的一般概念下，本申请并不限于特定的细节。

Claims (10)

  1. 一种共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，包括：光源模块、自适应光学模块、光束扫描模块、离焦补偿模块、视标模块、瞳孔监测模块、探测模块、控制模块和输出模块；
    所述光源模块出射平行光束，依次经过所述自适应光学模块、光束扫描模块、离焦补偿模块照射到人眼，人眼散射的携带人眼像差信息和光强信息的成像光沿原路返回，并传输到所述自适应光学模块和探测模块；
    所述自适应光学模块用于接收含人眼像差信息的成像光，并实现人眼像差的实时测量和校正；
    所述光束扫描模块由所述控制模块控制，可配置为不同的扫描模式，用于实现不同的扫描成像功能，至少包括：大视场成像功能、小视场高分辨率成像功能和大视场高分辨率成像功能；
    所述离焦补偿模块用于实现对人眼屈光不正的补偿；
    所述视标模块用于实现对人眼视网膜不同区域的引导与固视；
    所述瞳孔监测模块用于实现对人眼瞳孔的对准与监测；
    所述探测模块用于获取返回的人眼成像光，并转换为电信号后传输至所述控制模块；
    所述输出模块与所述控制模块连接，用于对人眼成像图像进行显示和存储。
  2. 根据权利要求1所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述光源模块、自适应光学模块、光束扫描模块、视标模块、离焦补偿模块、瞳孔监测模块沿入射光路依次设置；
    所述光源模块配置为沿入射光路依次设置的光源、准直器以及第一分光镜，其输出平行光束至所述自适应光学模块；所述光源发出的光经所述准直器后部分透射所述第一分光镜，进入所述自适应光学模块；
    所述自适应光学模块配置为沿入射光路依次设置的第二分光镜、波前校正器、透射式或反射式望远镜以及波前传感器，其与所述光束扫描模块连接，用于实现波前像差探测与校正；所述光源模块输出的平行光束部分透射所述第二分光镜后再由所述波前校正器反射至所述透射式或反射式望远镜，进入所述光束扫描模块；返回的携带人眼像差信息和光强信息的成像光经过所述光束扫描模块出射进入所述透射式或反射式望远镜，再由所述波前校正器反射至所述第二分光镜，部分成像光被所述第二分光镜反射至所述波前传感器， 实现波前像差测量，其余成像光透射所述第二分光镜继续传播；
    所述波前传感器接收到含有人眼像差信息的成像光束后传输至所述控制模块进行波前计算，得到波前控制电压并输出给所述波前校正器，实现对波前像差的探测与校正。
  3. 根据权利要求2所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述探测模块配置为收集透镜、共焦针孔和高灵敏度探测器，返回的成像光中透射所述自适应光学模块的第二分光镜的部分，到达所述第一分光镜，其中的部分成像光再被所述第一分光镜反射到收集透镜，聚焦再经过所述共焦针孔后到达所述高灵敏度探测器，进行光电转换得到电信号，然后输出给所述控制模块进行处理，得到视网膜成像图像，最终输出至所述输出模块进行显示、存储；
    所述共焦针孔设置在所述收集透镜的焦点处。
  4. 根据权利要求3所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述光束扫描模块配置为第一扫描镜和第二扫描镜，两片扫描镜通过透射式或反射式望远镜连接用以实现瞳面匹配；所述第一扫描镜实现对视网膜平面的横向扫描，所述第二扫描镜在周期性电压驱动下实现对视网膜平面的纵向扫描，所述第二扫描镜在直流电压驱动下可以产生一定的横向和纵向倾斜角度，所述第二扫描镜在直流电压驱动下产生横向和纵向倾斜角度同时还能在周期性电压驱动下实现对视网膜平面的横向和纵向二维扫描；
    所述第一扫描镜和第二扫描镜前后位置可以互换；
    所述光束扫描模块由所述控制模块输出电压信号控制，可以配置为不同的扫描模式，实现不同的成像功能，包括：大视场成像功能、小视场高分辨率成像功能和大视场高分辨率成像功能。
  5. 根据权利要求2所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述离焦补偿模块配置为沿入射光路依次设置的扫描物镜、平场物镜以及导轨，所述光束扫描模块的出射光束经离焦补偿模块传播至所述瞳孔监测模块，所述平场物镜能够在所述导轨上沿该平场物镜的中心轴线往复移动，实现对人眼屈光不正的补偿。
  6. 根据权利要求2所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述视标模块配置为LED阵列、透镜和第一二向色分光镜，所述LED阵列中的任意一个灯珠被所述控制模块点亮后发出的光，经过所述透镜传播后由所述第一二向色分光镜反射进入所述离焦补偿模块并最终进入人眼，人眼注视该发光的LED灯珠，实现固视； 所述光束扫描模块出射的光束经所述视标模块的第一二向色分光镜透射后进入所述离焦补偿模块继续传播；
    所述瞳孔监测模块配置为环形LED阵列、第二二向色分光镜和成像透镜、面阵探测器，所述环形LED阵列发出的光照明人眼瞳孔，经人眼瞳孔反射后穿过所述环形LED阵列的中空部位，由所述第二二向色分光镜全部反射后被所述成像透镜聚焦到所述面阵探测器，所述面阵探测器将光信号转换成电信号后输出至所述控制模块，得到瞳孔成像图像，最后输出至所述输出模块进行显示、存储。
  7. 根据权利要求4所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述控制模块通过输出电压信号对所述光束扫描模块中的所述第一扫描镜和第二扫描镜进行控制，用于实现不同的扫描成像功能；
    其中，所述大视场成像功能的实现方法为：
    所述自适应光学模块处于关机状态，或开机不工作状态；
    所述第一扫描镜在周期性电压信号驱动下，实现对视网膜平面的横向扫描；所述第二扫描镜在周期性电压信号驱动下，实现对视网膜平面的纵向扫描。所述第一扫描镜、第二扫描镜在周期性电压信号驱动下的视网膜扫描角度不小于20度；
    所述探测模块将获取的眼底视网膜光信号转换为电信号，经所述控制模块将第一扫描镜和第二扫描镜的周期性驱动电压信号同步，所述控制模块将所述电信号采样重构得到视网膜大视场成像图像，并输出至所述输出模块进行显示、存储；
    其中，所述小视场高分辨率成像功能的实现方法为：
    所述自适应光学模块处于开机工作状态，实现对波前像差的测量与校正；
    所述第一扫描镜在周期性电压信号驱动下，实现对视网膜平面的横向扫描；所述第二扫描镜在直流电压信号驱动下可以产生一定的横向和纵向倾斜角度，用于将照明眼底视网膜的光束定位在感兴趣的位置，随后在周期性电压信号驱动下，实现对视网膜平面的纵向扫描；所述第一扫描镜、第二扫描镜在周期性电压信号驱动下的视网膜扫描角度不大于5度；
    所述直流电压信号由所述控制模块根据眼底视网膜坐标位置计算得到；
    所述探测模块将获取的眼底视网膜光信号转换为电信号，经所述控制模块将第一扫描镜和第二扫描镜的周期性驱动电压信号同步，所述控制模块将所述电信号采样重构得到视网膜小视场高分辨率成像图像，同时将眼底视网膜坐标位置标记在所述成像图像中；所 述小视场高分辨率成像图像经所述控制模块输出至所述输出模块进行显示、存储；
    其中，所述大视场高分辨率成像功能的实现方法为:
    所述自适应光学模块处于开机工作状态，实现对波前像差的测量与校正；
    所述第一扫描镜在周期性电压信号驱动下，实现对视网膜平面的横向扫描；所述第二扫描镜在周期性电压信号驱动下，实现对视网膜平面的纵向扫描；所述第一扫描镜、第二扫描镜在周期性电压信号驱动下的视网膜扫描角度不大于5度；
    此时，所述第二扫描镜在直流电压信号驱动下可以产生一定的横向和纵向倾斜角度，将光束依次倾斜照明眼底视网膜各个区域，所述第二扫描镜单次横向和纵向倾斜角度不大于3度，所述第二扫描镜在直流电压信号驱动下的视网膜最大横向和纵向倾斜角度不大于15度；所述直流电压信号由所述控制模块根据眼底视网膜坐标位置计算得到；
    当眼底视网膜各个区域依次被光束照明时，所述控制模块可以获取得到视网膜各个区域的高分辨率成像图像，所述控制模块根据各个区域高分辨率成像图像的眼底视网膜位置坐标将各个图像进行拼接，得到眼底视网膜的大视场高分辨率图像，然后输出至所述输出模块进行显示、存储。
  8. 根据权利要求7所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述光源模块可以包括多个光源，多个光源可以通过光纤耦合器耦合进入准直器被准直为平行光束；多个光源也可以分别经各自的准直器准直为平行光束后经二向色分光镜耦合进入光路中；
    所述准直器可以是单透镜、消色差透镜、复消色差透镜或抛物面反射镜，用于将光源出射的光束准直为平行光束；
    所述第一分光镜为宽波段分光镜，所述准直器出射的平行光束20％透过所述分光镜继续传播进入所述自适应光学模块，经自适应光学模块返回的出射成像光束80％经所述第一分光镜反射进入所述探测模块。
  9. 根据权利要求2所述的共光路光束扫描的大视场自适应光学视网膜成像系统，其特征在于，所述自适应光学模块包含的所述波前传感器为微棱镜阵列哈特曼波前传感器、微透镜阵列哈特曼波前传感器、四棱锥传感器和曲率传感器中的一种，所述波前校正器为变形反射镜、液晶空间光调制器、微加工薄膜变形镜、微机电变形镜、双压电陶瓷变形镜、液体变形镜中的一种；
    所述光源模块输出的平行光束95％经所述第二分光镜透射至波前校正器；返回的成像 光束经所述波前校正器反射至所述第二分光镜分光，其中5％光能被反射进入所述波前传感器，实现波前像差测量；其余95％光能被透射至所述第一分光镜继续传播。
  10. 一种共光路光束扫描的大视场自适应光学视网膜成像方法，其特征在于，其采用如权利要求1-9中任意一项所述的系统进行成像，其包括以下步骤：
    步骤S1：开机，启动系统；
    步骤S2：被试者头部置于托头架上，开启所述瞳孔监测模块，通过手动调节或控制模块自动调节托头架三维平移，使得瞳孔成像在视场中间区域；
    步骤S3：手动滑动平场物镜沿光轴中心移动，或通过控制模块驱动电机移动平场物镜在导轨上的位置，实现对人眼屈光不正的补偿与校正；
    步骤S4：点亮所述视标模块中的LED阵列中的一个灯珠，受试者注视该光点，实现固视；
    步骤S5：自适应光学模块处于关机或开机不工作状态，光束扫描模块设置为大视场扫描模式，控制模块控制光束扫描模块完成大视场扫描，实现视网膜大视场成像并输出至输出模块；
    步骤S6：自适应光学模块处于开机工作，用于实现波前像差测量与校正，控制模块控制光束扫描模块进行小视场扫描，包含两种小视场扫描模式S61和S62；
    步骤S61：控制模块控制光束扫描模块完成小视场高分辨率成像图像输出至输出模块10；
    步骤S62：控制模块控制光束扫描模块完成大视场高分辨率成像图像并输出至输出模块；
    其中，步骤S5和步骤S6顺序可以对调，步骤S61和步骤S62无顺序关系，根据需求选取。
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