CN112155512A - Optical coherence tomography imaging equipment and control method thereof - Google Patents
Optical coherence tomography imaging equipment and control method thereof Download PDFInfo
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Abstract
The invention discloses an optical coherence tomography imaging device and a control method thereof, wherein the optical coherence tomography imaging device comprises an interference system, an eyeball tracking system, a focusing system, a first half-lens and a control system, wherein the control system is respectively connected with the interference system, the eyeball tracking system and the focusing system; an eye tracking system for reconstructing a fundus map; the control system is used for acquiring the fundus map from the eyeball tracking system and determining a target area from the fundus map; an interference system for generating a tomographic image; and the control system is also used for processing the tomographic image. The structure of the existing OCT equipment is changed, the OCT equipment is integrated, the size of the OCT equipment is better reduced, in addition, the scanning area can be automatically determined, automatic calibration is realized, the operation flow and the operation time of the OCT equipment are simplified, and the working efficiency is improved.
Description
Technical Field
The invention relates to the technical field of optical coherence tomography, in particular to an optical coherence tomography device and a control method thereof.
Background
The imaging principle of Optical Coherence Tomography (OCT) is to extract the depth information of semitransparent substances by using the characteristics of optical coherence and interference, and the OCT technology has high application value in clinical medicine due to the imaging characteristics of high resolution and no wound and loss. In order to make OCT imaging devices have better clinical applications, OCT technology development is continuously dedicated to improving its performance, such as imaging quality, system resolution, etc. In order to diagnose vascular diseases, researchers have developed angiographic imaging (OCTA) based on OCT, enabling visualization of vascular morphology. However, with the continuous development of computer technology and embedded technology, the development of medical instruments and devices towards miniaturization and high integration becomes the mainstream trend of instrument development nowadays.
The existing OCT equipment is generally large in size, mainly comprises a host (an optical device) and a computer, and the computer is large in size, so that the placement of instruments has certain requirements on space. At present, an embedded system is added into OCT equipment for development, but most of the OCT equipment is a semi-embedded system and still depends on a computer system. The embedded development is only responsible for the sequential control and the motor control of the galvanometer and the camera, and the data processing part is still completed by a computer, so that the good volume reduction effect cannot be achieved.
In addition, OCT has become an important examination apparatus for ophthalmology. However, how to automatically determine the scanning area and how to automatically calibrate and acquire a good tomogram belongs to the problem to be solved.
Disclosure of Invention
The present invention provides an optical coherence tomography apparatus and a control method thereof, which solves one or more technical problems in the prior art and provides at least one useful choice or creation condition.
In a first aspect, an embodiment of the present invention provides an optical coherence tomography apparatus, including an interference system, an eyeball tracking system, a focusing system, a first half-mirror and a control system, where the control system is connected to the interference system, the eyeball tracking system and the focusing system respectively;
the eyeball tracking system is used for generating a first light beam, receiving first reflected light reflected by the detected eye and generating a fundus map according to the first reflected light; the first light beam sequentially passes through the first half-reflecting mirror and the focusing system to reach the detected eye, and first reflected light reflected from the detected eye is reflected back to the eyeball tracking system through the focusing system and the first half-reflecting mirror;
the control system is used for acquiring the fundus map from the eyeball tracking system and determining a target area from the fundus map;
the interference system is used for generating a second light beam, enabling the second light beam to reach the target area of the detected eye under the control of the control system, receiving second reflected light reflected from the target area of the detected eye, and generating a tomographic image according to the interference of the second reflected light and the reference light, wherein the second light beam sequentially passes through the first half mirror and the focusing system to reach the detected eye, and the second reflected light reflected from the detected eye is reflected back to the interference system through the focusing system and the first half mirror;
the control system is also used for processing the tomographic image.
Further, the eye tracking system comprises: first light source, first collimation lens, slit, first scanning galvanometer, cylindrical mirror, the semi-transparent half of second return mirror, focusing lens and imaging element, the light that first light source sent forms the parallel light through first collimation lens, the parallel light becomes the line light behind the slit, the line light is gathered together by cylindrical lens, kick into through the semi-transparent half of second return mirror, first semi-transparent half return mirror, focusing system in proper order and is detected the eye, follow the light that is detected the eye and returns does first reverberation, first reverberation is reflected at the semi-transparent half of second return mirror, and the light that the semi-transparent half of second return mirror reflected is according to on the imaging element is reachd through focusing lens to generate the fundus map.
Further, the interferometry system comprises: the optical fiber coupling device comprises a second light source, a circulator, an optical fiber coupler, a reference arm, a sample arm, a reflector and a spectrometer, wherein the second light source generates a second light beam, the second light beam passes through the circulator to reach the optical fiber coupler, the optical fiber coupler is provided with two output light paths, one light path passes through the reference arm to reach the reflector, the light reflected back by the reflector is the reference light, the other light path sequentially passes through the sample arm, a first semi-transparent return mirror and a focusing system to reach a detected eye, the light reflected back by the detected eye is second reflected light, the reference light and the second reflected light are in interference of the optical fiber coupler, the interference light is received by the spectrometer, and a fault image is generated.
Further, the sample arm includes polarizer, second collimating lens, second scanning mirror and the third scanning mirror that shakes that sets gradually, the polarizer sets up fiber coupler another way light path, control system is connected with polarizer, second scanning mirror and third scanning mirror that shakes respectively.
Further, the optical coherence tomography imaging device further comprises a first motor translation stage, and the control system is connected with the first motor translation stage and controls the first motor translation stage to move so as to adjust the position of the detected eyeball.
Furthermore, the interference system further comprises a second motor translation stage, the control system is connected with the second motor translation stage and controls the second motor translation stage to move so as to calibrate the optical path of the interference system.
Further, the focusing system comprises a third motor translation stage, the control system is connected with the third translation stage and controls the third motor translation stage to move so as to adjust the distance between the focusing system and the measured eye.
In a second aspect, an embodiment of the present invention further provides a control method for an optical coherence tomography apparatus, including the following steps:
the control system controls the movement of the first motor translation stage to enable the pupil of the detected eye to be aligned with the center of the video;
the eyeball tracking system generates a fundus image of the detected eye;
the control system acquires the fundus image from the eyeball tracking system and determines a target area scanned by the interference system from the fundus image;
the control system controls the deflection of the polarizer in the interference system, so that the scanning position of the detected eye is the target area;
the control system controls the interference system to carry out automatic calibration, wherein the automatic calibration comprises calibration of an optical path, a focal length and polarization so as to obtain a tomogram of the detected eye meeting preset conditions;
and the control system acquires the tomogram from the interference system and processes the tomogram.
Further, the control system controlling the movement of the first motor translation stage so that the pupil of the detected eye is aligned with the center of the video comprises:
acquiring a shot pupil image, and identifying a pupil in the image;
respectively calculating the distance between the pupil and the transverse coordinate and the distance between the pupil and the longitudinal coordinate of the video center;
calculating the moving distance of the first motor translation stage according to the calculated distance;
the control system controls the movement of the first motor translation stage according to the movement distance of the first motor translation stage, so that the pupil is aligned with the center of the video.
Further, the control system controls the interference system to perform automatic calibration, the automatic calibration includes calibration of optical path, focal length and polarization, and acquiring a tomogram of the detected eye meeting preset conditions includes:
the control system controls the movement of a second motor translation stage in the interference system to enable the optical distances of a reference arm and a sample arm in the interference system to be equal;
the control system controls the movement of a third motor translation stage in the focusing system, so that the detected eye is placed at the focus of the focusing system;
a control system controls the deflection of the polarizer in the interference system to obtain a tomogram of the eye to be examined having the greatest intensity value of the image
The optical coherence tomography imaging equipment and the control method thereof in the embodiment of the invention have at least the following beneficial effects: the structure of the existing OCT equipment is changed, the OCT equipment is integrated, the size of the OCT equipment is better reduced, the OCT equipment is convenient to transport and place, certain space pressure is reduced for a user, in addition, a scanning area can be automatically determined, automatic calibration is realized, the operation flow and the operation time of the OCT equipment are simplified, and the work efficiency is improved.
Drawings
The accompanying drawings are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the example serve to explain the principles of the invention and not to limit the invention.
Fig. 1 is a schematic structural diagram of an OCT apparatus according to an embodiment of the present invention.
Fig. 2 is a schematic diagram of an eye tracking system according to an embodiment of the present invention.
FIG. 3 is a schematic diagram of an interferometric system provided in accordance with an embodiment of the invention.
Fig. 4 is a control method of an OCT apparatus according to an embodiment of the present invention.
Description of reference numerals: 100-control system, 200-eyeball tracking system, 300-interference system, 400-first half-transmission half-returning mirror, 500-focusing system, 600-eye to be detected, 201-first light source, 202-first collimating lens, 203-slit, 204-first scanning mirror, 205-cylindrical mirror, 206-second half-transmission half-returning mirror, 207-focusing lens, 208-imaging unit, 301-second light source, 302-circulator, 303-fiber coupler, 304-reference arm, 305-reflector, 306-sample arm, 307-spectrometer, 3041-second collimating lens, 3042-third lens, 3061-polarizer, 3062-third collimating lens, 3063-second scanning oscillating mirror, 3064-third scanning oscillating mirror, 3071-grating, 3041-focusing system, 3072-fourth lens, 3073-linear camera, 308-fourth collimating lens, 501-first lens, 502-second lens.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
It should be noted that although functional block divisions are provided in the system drawings and logical orders are shown in the flowcharts, in some cases, the steps shown and described may be performed in different orders than the block divisions in the systems or in the flowcharts. The terms first, second and the like in the description and in the claims, and the drawings described above, are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order.
As shown in fig. 1, the OCT apparatus includes a control system 100, an eyeball tracking system 200, an interference system 300, a first half mirror 400, and a focusing system 500, wherein the control system 100 is connected to the interference system 200, the eyeball tracking system 300, and the focusing system 500, respectively;
an eye tracking system 200 for generating the first light beam, receiving a first reflected light reflected from the detected eye 600, and generating a fundus map according to the first reflected light; the first light beam sequentially passes through the first half mirror 500 and the focusing system 400 to reach the detected eye 600, and a first reflected light reflected from the detected eye 600 is reflected back to the eyeball tracking system 200 through the focusing system 500 and the first half mirror 400;
a control system 100, configured to acquire the fundus map from the eyeball tracking system 200, and determine a target area according to the fundus map;
the interference system 300 is configured to generate the second light beam, enable the second light beam to reach the target area of the detected eye under the control of the control system 100, receive second reflected light reflected from the target area of the detected eye, and generate a tomographic image according to interference between the second reflected light and the reference light, where the second light beam sequentially passes through the first half mirror 400 and the focusing system 500 to reach the detected eye 600, and the second reflected light reflected from the detected eye 600 is reflected back to the interference system 300 through the focusing system 500 and the first half mirror 400;
the control system 100 is further configured to process the tomographic image.
As shown in fig. 2, the eyeball tracking system 200 includes a first light source 201, a first collimating lens 202, a slit 203, a first scanning galvanometer 204, a cylindrical lens 205, a second half-returning half-mirror 206, a focusing lens 207, and an imaging unit 208, wherein a first light beam emitted by the first light source 201 forms parallel light through the first collimating lens 202, the parallel light becomes linear light after passing through the slit 203, the linear light is converged by the cylindrical lens 204, and is sequentially emitted into a detected eye through the second half-returning half-mirror 205, the first half-returning half-mirror 400 (not shown in fig. 2), and the focusing system 500, a first reflected light returned by the detected eye is reflected by the focusing system 500 and the first half-returning half-mirror 400 (not shown in fig. 2) and then reflected by the second half-returning half-mirror 400, and the light reflected by the second half-returning mirror 400 reaches the imaging unit 208 through the focusing lens 207, so as to generate an eye fundus map.
In one embodiment, the focusing system 500 is a 4F focusing system, comprising a first lens 501 and a second lens 502.
In one embodiment, the imaging unit 208 includes a first camera, which is coupled to the control system 100. The first camera is an area array camera and is connected and communicated with the control system through a USB interface.
As shown in FIG. 3, an interferometric system 300 includes: the optical fiber coupler comprises a second light source 301, a circulator 302, an optical fiber coupler 303, a reference arm 304, a reflector 305, a sample arm 306 and a spectrometer 307, wherein the second light source 302 generates a second light beam, the second light beam reaches the optical fiber coupler 303 through the circulator 302, the optical fiber coupler 303 has two output light paths, one light path reaches the reflector 305 through the reference arm 304, the light reflected from the reflector 305 is reference light, the other light path reaches the detected eye 600 through the sample arm 306, a first semi-transparent semi-return mirror 400 (not shown in fig. 3) and a focusing system 500 in sequence, the light reflected from the detected eye 600 is the second reflected light, the reference light and the second reflected light interfere in the optical fiber coupler 303, and the interference light is received by the spectrometer 306 to generate the tomographic image.
The reference arm 304 includes a second collimating lens 3041 and a third lens 3042, and one optical path output by the fiber coupler 303 reaches the reflector 305 through the second collimating lens 3041 and the third lens 3042.
The sample arm 306 comprises a polarizer 3061, a third collimating lens 3062, a second scanning galvanometer 3063 and a third scanning galvanometer 3064 which are arranged in sequence, and the other light path output by the optical fiber coupler 303 passes through the polarizer 3061, the third collimating lens 3062, the second scanning galvanometer 3063 and the third scanning galvanometer 3064 in sequence to reach the focusing system 500.
In one embodiment, the spectrometer 307 includes a grating 3071, a fourth lens 3072, and a line camera 3073, the line camera 3073 generating a tomogram of the eye to be examined, the line camera 3073 being connected to the control system 100 for transmitting the tomogram to the control system 100.
In one embodiment, the interference system 300 further includes a fourth collimating lens 308, and the fourth collimating lens 308 is disposed between the circulator 302 and the grating 3071, and converts the interference light into parallel light and inputs the parallel light to the grating 3071.
In an embodiment, the OCT apparatus further includes a first motor translation stage, and the control system 100 is connected to the first motor translation stage and controls movement of the first motor translation stage to adjust the position of the detected eyeball.
The interferometry system 300 further includes a second motor translation stage, and the control system 100 is coupled to the second motor translation stage and controls movement of the second motor translation stage to calibrate the optical path of the interferometry system 300.
The focusing system 500 further comprises a third motor translation stage, and the control system 100 is connected with the third motor translation stage and controls the movement of the third motor translation stage to adjust the distance between the focusing system 500 and the detected eye 600.
In one embodiment, the first motor stage, the second motor stage, and the third motor stage each include a stepper drive motor and a translation stage, and the control system 100 is connected to the stepper motors of each motor stage.
In an embodiment, the OCT apparatus is a touch screen OCT apparatus, which includes a touch screen connected to the control system 100, and the touch screen is configured to obtain an input instruction of a user, and the control system 100 controls the OCT apparatus according to the input instruction. The touch screen of the OCT equipment with the extremely simple operation type comprises only 4 steps of selecting an acquisition position, selecting an acquisition mode, starting acquisition and exporting an automatically generated inspection report. Wherein, the collecting position can be selected from anterior segment of eye and posterior segment of eye, the anterior segment of eye can be selected from cornea, angle of chamber and iris, and the posterior segment of eye can be selected from papilla of sight or macula lutea area. The acquisition mode depends on a galvanometer scanning mode, and can be selected from three-dimensional scanning, circular scanning, raster scanning, line scanning, radioactive ray scanning and blood flow scanning. The examination report includes results such as a scan target structure image, a blood flow image, and a thickness analysis. Export the generated check report into a specified file path in the mobile storage through the device USB interface.
In an embodiment, the OCT apparatus is an embedded OCT apparatus, and the control system 100 includes an embedded development board system, the embedded development board system selects NVIDIA Jeston Xavier NX as an upper computer of the control system, wherein the data processing portion is completed by the embedded development board system. The embedded development board system comprises a GPU and a CPU, and can be used for extracting structural information and blood vessel information in signals acquired by the linear camera and displaying the structural information and the blood vessel information in the form of images. The USB serial port of the embedded development board system is connected with the touch screen, an operation interface of OCT system software is displayed on the touch screen, the software compiling is realized based on C + + language, and the operation system is Linux.
The control system further comprises a single chip microcomputer, the single chip microcomputer is connected with the NVIDIA Jeston Xavier NX, the single chip microcomputer is respectively connected with the first motor platform, the second motor platform and the third motor platform, and the single chip microcomputer is connected with the first quick scanning galvanometer 3043 and the second quick scanning galvanometer 3044. The single chip microcomputer is connected with the first camera and the linear camera respectively, or the single chip microcomputer is connected with the first camera and the linear camera through NVIDIAjeston Xavier NX.
Fig. 4 is a control method of an OCT apparatus for controlling the OCT apparatus described above, including the steps of:
s41, the control system controls the movement of the first motor translation stage, so that the pupil of the detected eye is aligned with the center of the video; wherein the video center refers to the center of the pupil image display;
s42, generating a fundus image of the detected eye by an eyeball tracking system;
s43, acquiring the fundus image from the eyeball tracking system by the control system, and determining a target area scanned by the interference system from the fundus image;
s44, controlling the deflection of a polarizer in the interference system by the control system, so that the scanning position of the detected eye is the target area;
s45, controlling the interference system to perform automatic calibration by the control system, wherein the automatic calibration comprises calibration of optical path, focal length and polarization so as to obtain a tomogram of the detected eye meeting preset conditions;
and S46, the control system acquires the tomogram from the interference system and processes the tomogram.
Wherein, step 41 comprises the following steps:
acquiring a shot pupil image, and identifying a pupil in the image;
respectively calculating the distance between the pupil and the transverse coordinate and the distance between the pupil and the longitudinal coordinate of the video center;
calculating the moving distance of the first motor translation stage according to the calculated distance;
the control system controls the movement of the first motor translation stage according to the movement distance of the first motor translation stage, so that the pupil is aligned with the center of the video.
Specifically, pupil identification is performed on the acquired image by using a computer vision method for matching identification, the eyeball position is detected, and the distance between the eyeball position and the test mark center in the X and Y directions is calculated. The movement of the first motor translation stage is completed by the single chip microcomputer, the upper computer sends the distance information of X and Y to the single chip microcomputer through USB serial port communication, and the single chip microcomputer controls the movement of the first motor translation stage.
The eye fundus image of the eye being examined is generated in step 42 using the eye tracking system of fig. 2.
In steps S43 and S44, determining from the fundus image that the target area scanned by the interference system includes identifying automatically from the fundus image the target area based on the acquisition position selected by the user from the touch screen, controlling the deflection of the polarizer in the interference system so as to control the superposition of the scan line of the interference system to the center of the target area of the fundus image.
Step 45 comprises:
the control system controls the movement of a second motor translation stage in the interference system to enable the optical distances of a reference arm and a sample arm in the interference system to be equal;
the control system controls the movement of a third motor translation stage in the focusing system, so that the detected eye is placed at the focus of the focusing system;
a control system controls the deflection of the polarizer in the interference system to obtain a tomogram of the eye under examination with the maximum intensity value of the image.
Specifically, the calibration of the optical path, the focal length and the polarization is sequentially realized by the automatic calibration function, and the optical path calibration function is realized by controlling the second motor translation stage of the interference optical path to move back and forth. The focus calibration function is completed by the forward and backward movement of a third motor translation stage of the focusing system. The alignment of the polarization is done by the swinging of the polarizer. Firstly, adjusting the optical path to enable the optical paths of the reference arm and the sample arm to be equal, acquiring an interference image, then placing an imaging tissue on the focus of a focusing lens of an optical device to enhance the tissue imaging intensity, and finally adjusting the polarization state of the optical path to optimize the image. The automatic calibration function of the invention takes the image intensity as a reference, controls the second motor translation stage of the interference light path to move 20mm forwards and backwards by taking the starting position as an origin, acquires the image intensity during the comparison period, and stops moving when the intensity is maximum. And controlling a third motor translation table of the focusing system to move 10mm forwards and backwards by taking the starting position as an origin, acquiring the image intensity during comparison, and stopping moving when the intensity is maximum. The polarizer controlling the polarization of the light path swings 180 degrees left and right with the start position as the origin, acquires the image intensity during the comparison, and stops swinging at the maximum value of the intensity.
The generation of the tomogram is done by the linear camera of the interferometric system, the data acquisition of which is done by the image acquisition card, and the processing of said tomogram in step 56 comprises data processing such as fourier transformation, phase extraction, background filtering, etc. The image acquisition card can be acquired by the singlechip and forwarded to the embedded development system, or the image acquisition card is connected with the embedded development board system through a USB interface, and the CPU and the GPU in the development board are utilized to perform data processing.
Before step 41, the method further comprises initializing the system, selecting an acquisition position and an acquisition mode by a user through a touch screen, and starting acquisition. After step 46, the control system is also included to derive an automatically generated report.
The optical coherence tomography imaging equipment and the control method thereof in the embodiment of the invention have at least the following beneficial effects: the structure of the existing OCT equipment is changed, the OCT equipment is integrated, the size of the OCT equipment is better reduced, the OCT equipment is convenient to transport and place, certain space pressure is reduced for a user, in addition, the scanning area can be automatically determined through simple operation of a touch screen, automatic calibration is realized, the operation flow and the operation time of the OCT equipment are simplified, and the work efficiency is improved.
One of ordinary skill in the art will appreciate that all or some of the steps, systems, and methods disclosed above may be implemented as software, firmware, hardware, and suitable combinations thereof. Some or all of the physical components may be implemented as software executed by a processor, such as a central processing unit, digital signal processor, or microprocessor, or as hardware, or as an integrated circuit, such as an application specific integrated circuit. Such software may be distributed on computer readable media, which may include computer storage media (or non-transitory media) and communication media (or transitory media). The term computer storage media includes volatile and nonvolatile, removable and non-removable media implemented in any method or technology for storage of information such as computer readable instructions, data structures, program modules or other data, as is well known to those of ordinary skill in the art. Computer storage media includes, but is not limited to, RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, Digital Versatile Disks (DVD) or other optical disk storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store the desired information and which can accessed by a computer. In addition, communication media typically embodies computer readable instructions, data structures, program modules or other data in a modulated data signal such as a carrier wave or other transport mechanism and includes any information delivery media as known to those skilled in the art.
While the preferred embodiments of the present invention have been described in detail, it will be understood by those skilled in the art that the foregoing and various other changes, omissions and deviations in the form and detail thereof may be made without departing from the scope of this invention.
Claims (10)
1. An optical coherence tomography imaging device is characterized by comprising an interference system, an eyeball tracking system, a focusing system, a first half-lens and a control system, wherein the control system is respectively connected with the interference system, the eyeball tracking system and the focusing system;
the eyeball tracking system is used for generating a first light beam, receiving first reflected light reflected by the detected eye and generating a fundus map according to the first reflected light; the first light beam sequentially passes through the first half-reflecting mirror and the focusing system to reach the detected eye, and first reflected light reflected from the detected eye is reflected back to the eyeball tracking system through the focusing system and the first half-reflecting mirror;
the control system is used for acquiring the fundus map from the eyeball tracking system and determining a target area from the fundus map;
the interference system is used for generating a second light beam, enabling the second light beam to reach the target area of the detected eye under the control of the control system, receiving second reflected light reflected from the target area of the detected eye, and generating a tomographic image according to the interference of the second reflected light and the reference light, wherein the second light beam sequentially passes through the first half mirror and the focusing system to reach the detected eye, and the second reflected light reflected from the detected eye is reflected back to the interference system through the focusing system and the first half mirror;
the control system is also used for processing the tomographic image.
2. The optical coherence tomography instrument of claim 1, wherein the eye tracking system comprises: first light source, first collimation lens, slit, first scanning galvanometer, cylindrical mirror, the semi-transparent half of second return mirror, focusing lens and imaging element, the light that first light source sent forms the parallel light through first collimation lens, the parallel light becomes the line light behind the slit, the line light is gathered together by cylindrical lens, kick into through the semi-transparent half of second return mirror, first semi-transparent half return mirror, focusing system in proper order and is detected the eye, follow the light that is detected the eye and returns does first reverberation, first reverberation is reflected at the semi-transparent half of second return mirror, and the light that the semi-transparent half of second return mirror reflected is according to on the imaging element is reachd through focusing lens to generate the fundus map.
3. The optical coherence tomography instrument of claim 1, wherein the interference system comprises: the optical fiber coupling device comprises a second light source, a circulator, an optical fiber coupler, a reference arm, a sample arm, a reflector and a spectrometer, wherein the second light source generates a second light beam, the second light beam passes through the circulator to reach the optical fiber coupler, the optical fiber coupler is provided with two output light paths, one light path passes through the reference arm to reach the reflector, the light reflected back by the reflector is the reference light, the other light path sequentially passes through the sample arm, a first semi-transparent return mirror and a focusing system to reach a detected eye, the light reflected back by the detected eye is second reflected light, the reference light and the second reflected light are in interference of the optical fiber coupler, the interference light is received by the spectrometer, and a fault image is generated.
4. The optical coherence tomography imaging apparatus of claim 3, wherein the sample arm comprises a polarizer, a second collimating lens, a second scanning galvanometer and a third scanning galvanometer, which are sequentially arranged, the polarizer is arranged on the other optical path of the fiber coupler, and the control system is respectively connected with the polarizer, the second scanning galvanometer and the third scanning galvanometer.
5. The optical coherence tomography instrument of claim 4, further comprising a first motor translation stage, wherein the control system is connected to the first motor translation stage and controls movement of the first motor translation stage to adjust the position of the detected eye.
6. The optical coherence tomography instrument of claim 5, wherein the interferometric system further comprises a second motor translation stage, the control system coupled to the second motor translation stage to control movement of the second motor translation stage to calibrate the optical path length of the interferometric system.
7. The optical coherence tomography instrument of claim 1, wherein the focusing system comprises a third motor translation stage, and the control system is connected to the third translation stage and controls movement of the third motor translation stage to adjust the distance of the focusing system from the eye under test.
8. A control method of an optical coherence tomographic imaging apparatus, characterized by comprising the steps of:
the control system controls the movement of the first motor translation stage to enable the pupil of the detected eye to be aligned with the center of the video;
the eyeball tracking system generates a fundus image of the detected eye;
the control system acquires the fundus image from the eyeball tracking system and determines a target area scanned by the interference system from the fundus image;
the control system controls the deflection of the polarizer in the interference system, so that the scanning position of the detected eye is the target area;
the control system controls the interference system to carry out automatic calibration, wherein the automatic calibration comprises calibration of an optical path, a focal length and polarization so as to obtain a tomogram of the detected eye meeting preset conditions;
and the control system acquires the tomogram from the interference system and processes the tomogram.
9. The control method of claim 8, wherein the controlling system controlling the movement of the first motor translation stage such that the pupil of the detected eye is aligned with the center of the video comprises:
acquiring a shot pupil image, and identifying a pupil in the image;
respectively calculating the distance between the pupil and the transverse coordinate and the distance between the pupil and the longitudinal coordinate of the video center;
calculating the moving distance of the first motor translation stage according to the calculated distance;
the control system controls the movement of the first motor translation stage according to the movement distance of the first motor translation stage, so that the pupil is aligned with the center of the video.
10. The control method according to claim 8, wherein the control system controls the interference system to perform automatic calibration including calibration of optical length, focal length and polarization, so as to acquire the tomogram of the detected eye satisfying preset conditions comprises:
the control system controls the movement of a second motor translation stage in the interference system to enable the optical distances of a reference arm and a sample arm in the interference system to be equal;
the control system controls the movement of a third motor translation stage in the focusing system, so that the detected eye is placed at the focus of the focusing system;
a control system controls the deflection of the polarizer in the interference system to obtain a tomogram of the eye under examination with the maximum intensity value of the image.
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