Optical ophthalmology tomography imaging system and tomography imaging method thereof

Abstract

The invention discloses an optical ophthalmology tomography imaging system which comprises an optical fiber coupler, and one end of the optical fiber coupler is connected with an OCT spectrometer camera and an OCT light source light path through a polarization control system and a power monitoring system; the other end of the optical fiber coupler is respectively connected with the reflector, the eyepiece and the SLO camera through a power adjusting system and a dispersion compensation system; an optical signal emitted by the OCT light source passes through the power monitoring system, passes through the optical fiber coupler and the power adjusting system and reaches the eyepiece, and images a human eye right facing one side of the eyepiece; after an optical signal of the fundus is collected, the optical signal is transmitted to the OCT spectrograph camera through the polarization control system, and a human eye tomography image is collected. The invention discloses an optical ophthalmology tomography imaging system and a tomography imaging method thereof. The optical system is compact in structure, high in imaging quality, beneficial to processing and adjustment, and capable of realizing broadband focusing.

Description

Technical Field

[0001] The present invention relates to the field of optical technology, and in particular to an optical ophthalmic tomography system, and in particular to an optical ophthalmic tomography imaging system and a tomography imaging method thereof. Background Art

[0002] Optical Coherence Tomography (OCT) is an interference-based optical imaging technology that has the advantages of non-contact, radiation-free, non-invasive, deep imaging, and high-resolution imaging, providing strong support for ophthalmology. OCT can perform high-resolution imaging of structures such as the retina, optic disc, and cornea, and can more accurately detect some early lesions, such as macular degeneration and retinopathy.

[0003] With the development of theories such as image processing and laser technology, OCT technology has made major breakthroughs in imaging speed and imaging resolution, and has derived a variety of functional technologies. One of them is a non-invasive, high-resolution, and safe new fundus blood flow angiography technology based on OCT, OCTA (Optical Coherence Tomography Angiography), which has been widely recognized and applied in the prevention and diagnosis of ophthalmic diseases. OCTA can provide high-resolution blood flow dynamic information to help doctors diagnose and monitor a variety of fundus diseases, such as diabetic retinopathy, macular degeneration, and retinal vein occlusion. Compared with traditional fluorescent angiography, OCTA does not require the injection of contrast agents, reducing user discomfort and potential risks. In addition, the OCTA examination process is fast and painless, and requires less cooperation from the user, making it an important tool for screening and diagnosis of fundus diseases.

[0004] Scanning Laser Ophthalmoscope (SLO) is an advanced ophthalmic examination technology, mainly used to observe and diagnose fundus lesions. The fundus is scanned and imaged by a weak laser beam to capture detailed images of the fundus. It is mainly used to examine diseases of the optic nerve head, retina, and macula. Doctors can observe three-dimensional imaging of blood vessels in the fundus, as well as subtle lesions of the retina and choroid. Its advantage is that the SLO examination process is painless and non-invasive, and is suitable for users who cannot undergo fundus fluorescein angiography. Compared with traditional ophthalmoscopy or fundus photography, SLO provides clearer images, which helps doctors detect subtle fundus lesions at an early stage. Summary of the invention

[0005] The present invention overcomes the shortcomings of the prior art and provides an optical ophthalmic tomography imaging system and a tomography imaging method thereof; the system has a compact structure, high imaging quality, is easy to process and assemble, and can achieve wide-band focusing.

[0006] To achieve the above object, the technical solution adopted by the present invention is: an optical ophthalmic tomography imaging system, comprising: a fiber coupler, one end of which is connected to an OCT spectrometer camera and an OCT light source optical path through a polarization control system and a power monitoring system respectively; The other end of the fiber coupler is connected to the reflector, the eyepiece and the SLO camera optical path respectively through the power adjustment system and the dispersion compensation system; The optical signal emitted by the OCT light source passes through the power monitoring system, the fiber coupler and the power adjustment system to reach the eyepiece, forming an image of the human eye on one side of the eyepiece; after collecting the optical signal from the fundus, the optical signal is sent to the OCT spectrometer camera through the polarization control system to collect a tomographic image of the human eye.

[0007] In a preferred embodiment of the present invention, the polarization control system establishes an optical path with an OCT spectrometer camera via a grating; The reflector is connected to the optical path of the fiber coupler via a reference arm assembly; The eyepiece establishes an optical path between the fiber coupler and the SLO camera through a dichroic mirror.

[0008] In a preferred embodiment of the present invention, a collimator and an XY galvanometer are provided between the fiber coupler and the dichroic mirror, and an optical path between the fiber coupler and the dichroic mirror is constructed by the collimator and the XY galvanometer; A Y galvanometer and a beam splitter are provided between the dichroic mirror and the SLO camera, and an optical path is established with the SLO light source and the internal fixation through the beam splitter; The SLO light source passes through a beam splitter, a Y galvanometer, a dichroic mirror, and an eyepiece to the human eye; after collecting the human eye information, the optical signal is reversibly transmitted to the SLO camera, and the SLO camera converts the optical signal into an electrical signal for processing to obtain a fundus image.

[0009] In a preferred embodiment of the present invention, the SLO light source and the Y galvanometer are located on the same side of the beam splitter; And / or, the SLO light source and the SLO camera are on different sides of the Y galvanometer; and / or, the SLO camera and the internal fixation are located on the same side of the beam splitter; and / or, the XY galvanometer and the eyepiece are located on the same side of the dichroic mirror; and / or, the XY galvanometer and the Y galvanometer are located on different sides of the dichroic mirror; And / or, the imaging angle of the XY galvanometer or the Y galvanometer includes y=4.5x, where y is the imaging angle; x is the rotation angle of the XY galvanometer or the Y galvanometer; And / or, in response to different structural layers of the human eye fundus, the light source is selected to be 700nm-1400nm; And / or, the Y galvanometer can be a one-dimensional galvanometer or a MEMS galvanometer.

[0010] In a preferred embodiment of the present invention, the XY galvanometer and the Y galvanometer synchronously receive a trigger signal to achieve synchronization, and the OCT spectrometer camera and the SLO fundus image of the SLO camera are synchronously displayed; The power monitoring system comprises a light detector, one end of which is a light source interface connected to the OCT light source, and the other end of the light detector is butt-jointed with one end of the optical fiber coupler.

[0011] In a preferred embodiment of the present invention, the power regulation system includes an attenuator, one end of the attenuator is connected to the optical fiber coupler through the optical fiber coupler input interface, the other end of the attenuator is connected to the reference arm assembly through the optical fiber reflector, and the reference arm assembly is connected to the reflector optical path; In a preferred embodiment of the present invention, a power regulation system is coupled into the optical fiber coupler, one end of the optical fiber coupler is respectively connected to the optical fiber coupler input interface and the optical fiber coupler input end, the other end of the optical fiber coupler is respectively connected to the optical fiber coupler output end and the polarization controller, and the polarization controller is connected to the optical fiber reflector through an attenuator.

[0012] In a preferred embodiment of the present invention, the polarization control system includes a device card slot for loading an optical fiber, the device card slot is connected to a motor drive, and the rotation of the motor drives the optical fiber on the device card slot to swing, thereby adjusting the polarization state of the light transmitted by the optical fiber; And / or, the grating is one of a volume holographic grating, a transmission relief grating, and a reflection relief grating.

[0013] In a preferred embodiment of the present invention, the eyepiece includes a pupil positioning component, and the pupil positioning component is one of a monocular pupil positioning component, a binocular pupil positioning component, and a trinocular pupil positioning component; The monocular pupil positioning assembly includes an iris camera arranged below the eyepiece; the binocular pupil positioning assembly includes two iris cameras arranged on the left and right sides of the eyepiece; the trinocular pupil positioning assembly includes three iris cameras arranged on the left and right sides of the eyepiece and below the eyepiece; And / or, the reference arm assembly adopts a movable reference arm; the movable reference arm includes: a collimator head, a dove prism, and a corner cube prism connected in an optical path, and the dove prism and the corner cube prism can be relatively displaced to adjust the spacing between the dove prism and the corner cube prism; And / or, the reference arm assembly adopts a fixed reference arm; the fixed reference arm includes: a collimation head, a Dove prism, and a corner cube prism connected in the optical path; and / or, the eyepiece is arranged on one side of the dichroic mirror by adjusting the collimation mechanism, and the adjustable collimation mechanism includes a movable collimating lens group and a fixed lens group arranged on one side of the dichroic mirror; the collimating lens group is moved by a collimation drive device, thereby changing the collimation state of the light beam.

[0014] In a preferred embodiment of the present invention, a tomographic imaging method of an optical ophthalmic tomographic imaging system is implemented by using an optical ophthalmic tomographic imaging system, and comprises the following steps: The optical signal emitted by the OCT light source reaches the eyepiece through the power monitoring system, the fiber coupler and the power adjustment system, and forms an image of the human eye on the side facing the eyepiece; after collecting the optical signal of the fundus, the optical signal is sent to the OCT spectrometer camera through the polarization control system to collect the tomographic image of the human eye; The SLO light source passes through a beam splitter, a Y galvanometer, a dichroic mirror, and the eyepiece to the human eye; after collecting the human eye information, the optical signal is reversibly transmitted to the SLO camera, and the SLO camera converts the optical signal into an electrical signal for processing to obtain a fundus image.

[0015] Compared with the prior art, the present invention has the following beneficial effects: The present invention discloses an optical ophthalmic tomography imaging system and a tomography imaging method thereof, which have a compact structure, high imaging quality, are easy to process and adjust, and can achieve wide-band focusing. The present invention enriches the perfection and imaging quality of the system and reduces the probability of system imaging failure caused by poor patient cooperation.

[0016] 1. The optical ophthalmic coherence tomography scanner system of the present invention adopts an achromatic optical design with a wide wavelength band, and is compatible with the light sources required for a variety of applications (different wavelengths for different applications).

[0017] 2. The optical ophthalmic coherence tomography scanner system of the present invention is equipped with a polarization control system, a power regulation system, a dispersion compensation system, and a power monitoring system to improve imaging quality.

[0018] 3. The optical ophthalmic coherence tomography system of the present invention simultaneously images the fundus of the human eye and the tomography of the human eye. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] The present invention is further described below in conjunction with the accompanying drawings and embodiments.

[0020] Figure 1 A layout diagram of an optical ophthalmic coherence tomography scanner system provided for an embodiment of the present invention; Figure 2 A schematic diagram of a power monitoring device provided for an embodiment of the present invention; Figure 3 A schematic diagram of a power regulating device provided for an embodiment of the present invention; Figure 4 A schematic diagram of coupling a power regulating device provided in an embodiment of the present invention into a fiber coupler; Figure 5 A schematic diagram of a polarization adjustment device provided in an embodiment of the present invention; Figure 6 A schematic diagram of a volume holographic grating provided in an embodiment of the present invention; Figure 7 A schematic diagram of a reflective relief grating provided in an embodiment of the present invention; Figure 8 A schematic diagram of a transmissive relief grating provided in an embodiment of the present invention; Fig. 9 A schematic diagram of a monocular positioning device provided for an embodiment of the present invention; Fig.10 A schematic diagram of a binocular positioning device provided for an embodiment of the present invention; Fig.11 A schematic diagram of a three-eye positioning device provided for an embodiment of the present invention; Fig.12 A schematic diagram of a movable reference arm device provided for an embodiment of the present invention; Fig.13 A schematic diagram of a fixed reference arm device provided for an embodiment of the present invention; Fig.14 A schematic diagram of an optical fiber reference arm in a fixed reference arm provided in an embodiment of the present invention; Fig.15 A schematic diagram of a refractive adjustment device for adjusting a collimation mechanism provided in an embodiment of the present invention; Fig.16 A schematic diagram of a refractive adjustment device for a movable eyepiece mechanism provided in an embodiment of the present invention; Fig.17 A schematic diagram of OCTA imaging provided for an embodiment of the present invention; Fig.18 A schematic diagram of a dispersion compensation device provided in an embodiment of the present invention; Fig.19 A schematic diagram of the dispersion compensation effect provided by the embodiment of the present invention; Fig. 20 A schematic diagram of a fundus image provided for an embodiment of the present invention; Among them, 100-OCT light source, 101-collimator, 102-XY galvanometer, 103-dichroic mirror, 104-eyepiece, 105-human eye, 106-fiber coupler, 107-grating, 108-OCT spectrometer camera, 109-reference arm assembly, 110-reflector, 111-SLO light source, 112-beam splitter, 113-Y galvanometer, 114-SLO camera, 20-power monitoring system, 30-power adjustment system, 40-polarization control system, 50-dispersion compensation system, 60-endofin fixation; 200-light detector, 201-light source interface; 300 - fiber coupler input interface, 301 - attenuator, 302 - fiber reflector, 303 - polarization controller, 304 - fiber coupler input end, 305 - fiber coupler output end; 400-motor, 401-device slot; 500-Dispersion compensation components; 601-iris camera; 700-optical system, 701-slide rail, 702-driving device; 800-fixed lens group, 801-movable collimating lens group, 802-collimating drive device; 901-collimation head, 902-Dove prism, 903-corner cube prism 1, 904-corner cube prism 2; 1000-Volume holographic grating diffraction layer. DETAILED DESCRIPTION

[0021] The technical solution of the present invention is described in detail below through the accompanying drawings and specific embodiments. It should be understood that the embodiments of the present invention and the specific features in the embodiments are detailed descriptions of the technical solution of the present invention, rather than limitations on the technical solution of the present invention. The embodiments of the present invention and the technical features in the embodiments may be combined with each other unless there is a conflict.

[0022] The term "and / or" is only a description of the association relationship between related objects, indicating that there can be three relationships. For example, A and / or B can mean: A exists alone, A and B exist at the same time, and B exists alone. In addition, the character " / " generally indicates that the related objects are in an "or" relationship. Embodiment 1

[0023] An optical ophthalmic tomography imaging system includes: a fiber coupler 106, one end of the fiber coupler 106 is optically connected to an OCT spectrometer camera 108 and an OCT light source 100 through a polarization control system 40 and a power monitoring system 20. The other end of the fiber coupler 106 is optically connected to a reflector 110, an eyepiece 104 and an SLO camera 114 through a power adjustment system 30 and a dispersion compensation system 50.

[0024] Specifically, the polarization control system 40 establishes an optical path with the OCT spectrometer camera 108 through the grating 107. The reflector 110 is connected to the optical path of the fiber coupler 106 through the reference arm assembly 109. The eyepiece 104 establishes an optical path between the fiber coupler 106 and the SLO camera 114 through the dichroic mirror 103. A collimator 101 and an XY galvanometer 102 are arranged between the fiber coupler 106 and the dichroic mirror 103, and the optical path between the fiber coupler 106 and the dichroic mirror 103 is constructed through the collimator 101 and the XY galvanometer 102; a Y galvanometer 113 and a beam splitter 112 are arranged between the dichroic mirror 103 and the SLO camera 114, and an optical path is established with the SLO light source 111 and the internal fixation 60 through the beam splitter 112.

[0025] Furthermore, in response to different structural layers of the fundus of the human eye 105, the light source is selected to be 700nm-1400nm; the Y galvanometer 113 can be one of a reflector device, a one-dimensional galvanometer, and a MEMS galvanometer.

[0026] Working principle: The optical signal emitted by the OCT light source 100 passes through the power monitoring system 20, the fiber coupler 106 and the power regulation system 30 to reach the eyepiece 104, and images the human eye 105 on the side facing the eyepiece 104; after collecting the optical signal of the fundus, the optical signal passes through the polarization control system 40 to the OCT spectrometer camera 108, and collects the tomographic image of the human eye 105. The SLO light source 111 passes through the beam splitter 112, the Y galvanometer 113, the dichroic mirror 103, the eyepiece 104 to the human eye 105; after collecting the human eye information, the optical signal is reversibly sent to the SLO camera 114, and the SLO camera 114 converts the optical signal into an electrical signal for processing to obtain the fundus image.

[0027] This embodiment realizes high-resolution tomographic imaging and vascular imaging of eye tissues, as well as fundus reflection imaging; among them, tomographic imaging can observe the morphology of each layer of the retina; blood flow imaging can use a layered algorithm to view blood flow images at different structural levels, thereby clearly showing the level and location of the lesion; fundus reflection imaging can provide us with the fundus situation near the retinal layer. Compared with tomography and vascular imaging, which are more based on algorithms and projected to present fundus images, reflective fundus imaging based on the direct optical bottom principle has a higher resolution. See Attachment Figure 1 , which is the optical path layout diagram of the optical ophthalmic coherence tomography system provided in this embodiment. The light emitted by the OCT light source 100 reaches the collimator 101 and the XY galvanometer 102 after passing through the fiber coupler 106, and forms an image of the human eye 105 through the dichroic mirror 103 and the eyepiece 104. After collecting the fundus information, since the optical path is reversible, the optical signal passes through the grating 107 to the OCT spectrometer camera 108. It is the tomographic image of the human eye 105 collected by the OCT system. Embodiment 2

[0028] On the basis of the first embodiment, the SLO light source 111 and the Y galvanometer 113 are located on the same side of the beam splitter 112; the SLO light source 111 and the SLO camera 114 are on different sides of the Y galvanometer 113; the SLO camera 114 and the internal fixation 60 are located on the same side of the beam splitter 112; the XY galvanometer 102 and the eyepiece 104 are located on the same side of the dichroic mirror 103; the XY galvanometer 102 and the Y galvanometer 113 are located on different sides of the dichroic mirror 103. The imaging angle of the XY galvanometer 102 or the Y galvanometer 113 includes y=4.5x, where y is the imaging angle; and x is the rotation angle of the XY galvanometer 102 or the Y galvanometer 113. The XY galvanometer 102 or the Y galvanometer 113 has different angles with the eyepiece 104 to achieve imaging of different fundus ranges. Embodiment 3

[0029] On the basis of the first embodiment, the eyepiece 104 is at the human eye 105; after collecting the human eye information, the optical signal can be reversibly sent to the SLO camera 114, and the optical signal is converted into an electrical signal by the camera for processing, and then the fundus image is presented, which is the fundus image collected by the SLO system. In response to the different structural layers of the fundus of the human eye 105, the light source can be selected from 700nm-1400nm. The XY galvanometer 102 and the Y galvanometer 113 are synchronized by signals to synchronize the SLO fundus images of the OCT spectrometer camera 108 and the SLO camera 114. Specifically, the SLO camera 114 can be used for eye tracking, and its imaging optical resolution is less than 8μm; it performs tracking 100 times or more per second, and has a tracking accuracy greater than 8 microns and a success rate of more than 97%, which can significantly reduce artifacts caused by eye drift and micro-saccades. Embodiment 4

[0030] Based on the third embodiment, Figure 2 As shown, the power monitoring system 20 includes a light detector 200, one end of which is a light source interface 201 connected to the OCT light source 100, and the other end of the light detector 200 is connected to one end of the fiber coupler 106. Specifically, the trigger signals of the XY galvanometer 102 and the Y galvanometer 113 are ensured to be triggered simultaneously, that is, the two Y galvanometer periods are the same and the phase difference is equal.

[0031] Specifically, the optical detector 200 can detect light of 400nm-1400nm; the light source interface 201 can be adapted according to the interface of the incident light of the OCT light source 100, such as using an FC / APC interface, an FC / PC / interface, or an SMA interface. The light emitted by the OCT light source 100 is incident on the optical detector 200 through the power monitoring system 20 to monitor the power, and the power monitoring error is <0.3%. When the device is running, the power monitoring system 20 monitors the power through the optical detector 200 to ensure that it is within the safety threshold of the human eye 105 to ensure the safety of the diagnostic process. The power monitoring system 20 can help detect abnormal conditions in the system, including circuit overload or short circuit, so as to take measures to avoid system crash or unstable operation. At the same time, the power monitoring of the power monitoring system 20 can also be used for later equipment fault diagnosis to facilitate early detection of equipment failures. Embodiment 5

[0032] Based on the third embodiment, in laser applications, the control of optical power is very important. Laser is a beam with high directionality and high energy density, which is widely used in medical, manufacturing, scientific research and other fields. In the medical field, such as ophthalmic OCT, the optical power is adjusted according to different conditions and the age of the user to achieve the effect of accurate diagnosis and treatment.

[0033] like Figure 3 As shown, the power regulation system 30 includes an attenuator 301, one end of the attenuator 301 is connected to the fiber coupler 106 through the fiber coupler input interface 300, and the other end of the attenuator 301 is connected to the reference arm assembly 109 through the fiber reflector 302, and the reference arm assembly 109 is optically connected to the reflector 110.

[0034] In other embodiments, Figure 4 As shown, the power regulation system 30 is coupled into the optical fiber coupler 106, one end of the optical fiber coupler 106 is respectively connected to the optical fiber coupler input interface 300 and the optical fiber coupler input end 304, the other end of the optical fiber coupler 106 is respectively connected to the optical fiber coupler output end 305 and the polarization controller 303, and the polarization controller 303 is connected to the optical fiber reflector 302 through the attenuator 301. Embodiment 6

[0035] Based on the third embodiment, the polarization control system 50 includes a device slot 401 for loading optical fiber, which is connected to the motor 400. The rotation of the motor 400 drives the optical fiber on the device slot 401 to swing, thereby adjusting the polarization state of the light transmitted by the optical fiber. Embodiment 7

[0036] On the basis of the third embodiment, the grating 107 adopts one of the volume holographic grating, the transmission relief grating and the reflection relief grating. The processes of the volume holographic grating, the transmission relief grating and the reflection relief grating are different. The volume holography is based on the change of the refractive index in the medium, and is modulated by adjusting the thickness and refractive index of the medium. The surfaces of the transmission and reflection relief gratings are both relief medium structures, and dispersion is achieved through this structure. One of them transmits light and the other reflects light. The grating 107 used in ophthalmic equipment based on the interference principle generally adopts a volume holographic grating, see the attached Figure 6 The volume holographic grating diffraction layer 1000 is where the light source is incident to achieve spectral dispersion of the light source, so that the dispersed spectrum is received by the spectrometer, and finally the fundus section can be seen clearly after algorithm processing; the product has a long production period and is expensive. Therefore, by modifying the optical path of the spectrometer, the transmission volume holographic grating is changed to a relief grating, which is cheaper. See the attached Figure 7 It is a reflective relief grating, see the attached Figure 8 It is a transmissive relief grating. Embodiment 8

[0037] On the basis of the third embodiment, the eyepiece 104 includes a pupil positioning component, and the pupil positioning component adopts one of a monocular pupil positioning component, a binocular pupil positioning component, and a trinocular pupil positioning component.

[0038] First, the monocular pupil positioning component includes an iris camera 601 disposed below the eyepiece 104; specifically, the monocular positioning component is as follows: Fig. 9 As shown, only one iris camera 601 located at the nose wing is used, and the ocular surface camera inside the device is used for auxiliary positioning. The user aligns his eyes with the eyepiece 104, and the iris camera 601 at the nose wing captures images to preliminarily determine the approximate area of ​​the pupil. The ocular surface camera further captures ocular surface images, and the system accurately determines the position of the pupil through image processing algorithms. According to the image data from the ocular surface camera, the platform position is adjusted so that the pupil is accurately located within the scanning area. The system performs secondary focusing to ensure the accuracy of the scan. Monocular positioning: When only one iris camera 601 is used, the pupil can still be accurately positioned with the assistance of the ocular surface camera, which is suitable for scenarios with limited device space.

[0039] Secondly, the binocular pupil positioning component includes two iris cameras 601 arranged on the left and right sides of the eyepiece 104; specifically, the binocular positioning component is as follows: Fig.10The system shown includes two iris cameras 601 located on the left and right sides of the eyepiece 104. The fields of view of the two iris cameras 601 intersect to form a focal point. When the pupil of the user's eye enters the approximate range, the movement state of the platform is adjusted in real time according to the image collected by the iris camera 601, so that the pupil reaches the vicinity of the focal point as soon as possible. Subsequently, the system performs secondary focusing to ensure that the pupil is accurately located in the scanning area. The user aligns his eyes with the eyepiece 104, and the iris cameras 601 on the left and right sides begin to collect images. The system preliminarily determines the position of the pupil through an image processing algorithm. The platform is adjusted according to the position of the pupil so that the pupil is close to the focal point. The system performs secondary focusing to ensure that the pupil is accurately located in the scanning area. Binocular positioning: The pupil can be quickly and preliminarily located through the intersecting fields of view of the two iris cameras 601, and accurate locking can be achieved by adjusting the secondary focusing.

[0040] Third, the trinocular pupil positioning assembly includes three iris cameras 601 arranged on the left and right sides of the eyepiece 104 and below the eyepiece 104; specifically, the trinocular pupil positioning assembly is as follows: Fig.11 As shown, on the basis of binocular positioning, a third iris camera 601 located at the nose wing is added. The three iris cameras 601 work together to more accurately lock the spatial position of the pupil. According to the calculated position, the platform is quickly adjusted so that the pupil is accurately located in the scanning area. The system performs secondary focusing to ensure the accuracy of the scan. Trinocular positioning: adding an iris camera 601 at the nose wing can more accurately lock the three-dimensional spatial position of the pupil, improving the positioning speed and accuracy. Embodiment 9

[0041] Based on the third embodiment, two reference arm solutions are proposed. One uses a reflector 110 to fold the optical path to reduce the volume; the other uses a pure optical fiber method to allow light to propagate in the optical fiber, which has a smaller volume.

[0042] See attached Fig.12 , the reference arm assembly 109 adopts a movable reference arm; the movable reference arm includes: a collimator 901, a dove prism 902, and a corner cube prism 903. The collimator 901, the dove prism 902, and the corner cube prism 903 are connected by an optical path, and the dove prism 902 and the corner cube prism 903 can be relatively displaced to adjust the distance between the dove prism 902 and the corner cube prism 903; specifically, the light is incident from the collimator 901 to the dove prism 902, and the light path is folded by the dove prism 902 to reduce the volume, and the light is finally reflected by the corner cube prism 903 and returned to the original path, and the distance between the corner cube prism 903 and the dove prism 902 is moved to change the optical path of the reference arm to match the optical path of the sample arm. That is, the light is incident from the collimator 901, refracted by the dove prism 902, and finally reflected back by the corner cube prism 903.

[0043] See attached Fig.13 , the reference arm assembly 109 adopts a fixed reference arm; the fixed reference arm includes: a collimator head 901 and a corner cube prism 903. The collimator head 901 and the corner cube prism 903 are optically connected. Specifically, the collimator head 901 and the corner cube prism 903 are located on the reference arm, and the light is directly incident on the corner cube prism 903 by the collimator head 901, and returns to the original path after being reflected by the corner cube prism 903, and the position between the two is fixed. That is, the light is incident by the collimator head 901 and reflected back by the corner cube prism 903. But it is not limited to this. Another corner cube prism 904 is combined with the collimator head 901 and is located in the sample arm. The optical path difference between the sample arm and the reference arm is matched by adjusting the distance between the collimator head 901 and the corner cube prism 904 on the sample arm. The distance between the two is moved to adjust the optical path difference between the sample arm and the reference arm, so that the two interfere. Fig.13 The reference arm in the can also be replaced as a whole with a pure optical fiber, such as Fig.14 As shown, the light propagates in the optical fiber, and is finally reflected back by the optical fiber reflector 302 . Embodiment 10

[0044] The conventional method of adjusting the refraction is to move the eyepiece mechanism. Since the working distance between the laser diagnostic instrument and the human eye 105 is often short, the refraction is generally adjusted by moving all the systems in front of the eyepiece 104, that is, changing the relative distance to the eyepiece 104. This solution requires the entire system to be moved during adjustment, which is complicated and bulky.

[0045] In this embodiment, based on the third embodiment, the eyepiece 104 is arranged on one side of the dichroic mirror 103 by adjusting the collimation mechanism, and the adjustable collimation mechanism includes a movable collimating lens group 801 and a fixed lens group 800 arranged on one side of the dichroic mirror 103; the collimating lens group 801 is moved by the collimation driving device 802, thereby changing the collimation state of the light beam.

[0046] The difference between the two refractive options: Solution 1: Move the eyepiece mechanism such as Fig.15As shown, the eyepiece mechanism includes: the eyepiece 104 is connected to the other parts of the optical system 700 through a slide rail 701, allowing the eyepiece mechanism to move along the optical axis. The driving device 702 is used to accurately control the moving distance of the eyepiece mechanism. When the refraction needs to be adjusted, the system moves the eyepiece 104 through the driving device 702 to change the relative distance between the eyepiece 104 and the human eye 105. The focusing state of the light beam incident on the eye can be changed, thereby realizing the refraction adjustment. The refraction adjustment range is usually large, and the specific range depends on the moving distance of the eyepiece 104 and the design of the optical system 700. Specific adjustment steps: After the system is started, the required refraction adjustment amount is calculated according to the user's refraction state. The driving device 702 moves the eyepiece 104 mechanism according to the calculation result to change the distance between it and the eye. The system monitors the focusing state of the light beam in real time and ensures the accuracy of the refraction adjustment through feedback control. After the adjustment is completed, the system locks the position of the eyepiece 104 to ensure the stability of the refraction state during the scanning process. The refraction adjustment is realized by moving the eyepiece 104, and the principle is simple and easy to understand and operate. It is applicable to various optical systems 700 and devices and has certain versatility. The entire eyepiece mechanism needs to be moved, which increases the complexity and weight of the system. Due to the short working distance, the eyepiece 104 needs to move a large distance to achieve diopter adjustment. The mechanical movement speed is slow, and it is difficult to achieve rapid adjustment.

[0047] Solution 2: Adjust the collimation mechanism as follows Fig.16The system shown includes a movable collimating lens group 801 and a fixed lens group 800. The collimating lens group is precisely moved by the collimating drive device 802, thereby changing the collimation state of the light beam. The fixed lens group is used to maintain the basic propagation direction of the light beam. When the refraction needs to be adjusted, the system changes the focusing state of the light beam incident on the eye by controlling the position of the collimating lens group 801. By adjusting the distance between the collimating lens group 801 and the fixed lens group 800, the convergence or divergence of the light beam can be achieved, thereby adjusting the diopter. The refraction adjustment range can reach more than ±25D, meeting the refraction needs of different users. Adjusting the refraction relative to the eyepiece mechanism based on the collimating mechanism can achieve the goal through a smaller moving stroke. At the same time, the collimating mechanism is generally relatively light in weight, simple in structure, fast in speed and high in precision when moving. Specific adjustment steps: After the system is started, the required refraction adjustment amount is calculated according to the refraction state of the user. The collimating drive device 802 drives the collimating lens group 801 to move and changes the distance between it and the fixed lens group 800. The system monitors the focusing state of the light beam in real time and ensures the accuracy of the refractive adjustment through feedback control. After the adjustment is completed, the system locks the position of the collimating lens group 801 to ensure the stability of the refractive state during the scanning process. Solution 2 achieves refractive adjustment by adjusting the collimating mechanism, avoiding the complexity of moving the entire optical system 700. The number of mechanical moving parts is reduced, and the weight of the system is reduced. The refractive adjustment range can reach more than ±25D, which is suitable for a wide range of refractive states. Precise control is achieved through the collimating drive device 802 to ensure the accuracy of the refractive adjustment. Embodiment 11

[0048] A tomographic imaging method of an optical ophthalmic tomographic imaging system is implemented by using an optical ophthalmic tomographic imaging system of embodiment 1, and comprises the following steps: The optical signal emitted by the OCT light source 100 passes through the power monitoring system 20, the optical fiber coupler 106 and the power regulation system 30 to reach the eyepiece 104, and forms an image of the human eye 105 facing the eyepiece 104. After collecting the optical signal of the fundus, the optical signal passes through the polarization control system 40 to the OCT spectrometer camera 108, and a tomographic image of the human eye 105 is collected. The SLO light source 111 passes through the beam splitter 112, the Y galvanometer 113, the dichroic mirror 103, the eyepiece 104 to the human eye 105; after collecting the human eye information, the optical signal is reversibly transmitted to the SLO camera 114, and the SLO camera 114 converts the optical signal into an electrical signal for processing to obtain a fundus image. Embodiment 12

[0049] A method for acquiring optical coherence tomography blood flow imaging (OCTA) in an optical ophthalmic coherence tomography scanner. Based on the system described in Example 2 and Example 3, a spectrometer camera is used to repeatedly collect K OCT image B-scans (B-scan, i.e., brightness scan) at the same position along the X-axis direction to form a B-scan group with blood flow differences. After the acquisition is completed, the scanning angle of the Y galvanometer 113 is adjusted to continue collecting B-scan groups at different positions along the Y-axis direction to form OCTA volume data. After obtaining the OCTA volume data, a difference analysis is performed on the B-scan group in the volume data to obtain a blood flow image. I Flow ; I Flow The calculation formula is as follows: ; in, A i Represents the amplitude of each B-scan in the B-scan. After obtaining the blood flow images of all B-scan groups, firstly, all blood flow images are statistically decorrelated to remove noise signals, and then the denoised blood flow signals are projected to the maximum value to generate OCTA images. The generated images are as follows: Fig.17 shown. Embodiment 13

[0050] Provides a dispersion compensation function in an optical ophthalmic coherence tomography scanner. Since frequency domain OCT uses a broadband light source, when the dispersion between the sample arm and the reference arm does not match, the broadband light source will cause the group velocity dispersion effect. The dispersion effect will cause the broadening of the axial signal of the tomogram, reduce the axial resolution of the tomogram, and seriously affect the imaging quality of frequency domain OCT. See Appendix Fig.18 The dispersion compensation component 500 in the dispersion compensation system 50 adjusts the optical path and the dispersion of the reference arm and the sample arm through the dispersion compensation component 500 to improve the image quality. Fig.19 , the left side is before dispersion compensation, and the right side is after dispersion compensation.

[0051] Working principle: The optical ophthalmic tomography system provided by the patent of this invention can achieve clear imaging within the visible and near-infrared wavelength range; at the same time, by utilizing the variable magnification design principle, it can realize continuous change of the linear field of view and clear imaging; by utilizing the focusing device, clear imaging at different object distances can be achieved; the entire system uses spherical mirrors, which have a compact structure, high imaging quality, and are conducive to processing and assembly; it can be used in the medical industry to diagnose various ophthalmic diseases such as dry eyes.

[0052] The present invention is based on the principles of geometric optics, physical optics, fiber optics, etc., and utilizes optical coherence tomography, reflection imaging, etc. to achieve high-resolution tomographic imaging of eye tissues, blood flow imaging, and reflective fundus imaging. The patented product of the present invention can realize fully automatic diagnosis, and at the same time, multiple functions are added to the system, such as power adjustment, polarization control, power monitoring, dispersion compensation, etc.; at the same time, optimization is made in refractive adjustment, positioning method, and reference arm assembly; the combination of reflection imaging and tomographic imaging can realize eye tracking. At the same time, the patented design of the present invention has a large tolerance, a wide applicable band, low processing and manufacturing costs, good thermal adaptability, and easy installation and detection. These greatly enrich the perfection and imaging quality of the system, reduce the probability of system imaging failure due to poor patient cooperation, and can be applied to the diagnosis of ophthalmic diseases in the medical field.

[0053] Based on the ideal embodiment of the present invention, through the above description, relevant personnel can make various changes and modifications without departing from the technical concept of the present invention. The technical scope of the present invention is not limited to the content in the specification, and the technical scope must be determined according to the scope of the claims.

Claims

1. An optical ophthalmic tomography imaging system, characterized in that: include: A fiber coupler, one end of which is connected to an OCT spectrometer camera and an OCT light source optical path through a polarization control system and a power monitoring system respectively; The other end of the fiber coupler is connected to the reflector, the eyepiece and the SLO camera optical path respectively through the power adjustment system and the dispersion compensation system; The optical signal emitted by the OCT light source passes through the power monitoring system, the fiber coupler and the power adjustment system to reach the eyepiece, forming an image of the human eye on one side of the eyepiece; after collecting the optical signal from the fundus, the optical signal is sent to the OCT spectrometer camera through the polarization control system to collect a tomographic image of the human eye.

2. The optical ophthalmic tomography imaging system according to claim 1, characterized in that: The polarization control system establishes an optical path with the OCT spectrometer camera through a grating; The reflector is connected to the optical path of the fiber coupler via a reference arm assembly; The eyepiece establishes an optical path between the fiber coupler and the SLO camera through a dichroic mirror.

3. The optical ophthalmic tomography imaging system according to claim 2, characterized in that: A collimator and an XY galvanometer are provided between the fiber coupler and the dichroic mirror, and an optical path between the fiber coupler and the dichroic mirror is constructed by the collimator and the XY galvanometer; A Y galvanometer and a beam splitter are provided between the dichroic mirror and the SLO camera, and an optical path is established with the SLO light source and the internal fixation through the beam splitter; The SLO light source passes through a beam splitter, a Y galvanometer, a dichroic mirror, and an eyepiece to the human eye; after collecting the human eye information, the optical signal is reversibly transmitted to the SLO camera, and the SLO camera converts the optical signal into an electrical signal for processing to obtain a fundus image.

4. The optical ophthalmic tomography imaging system according to claim 3, characterized in that: The SLO light source and the Y galvanometer are located on the same side of the beam splitter; And / or, the SLO light source and the SLO camera are on different sides of the Y galvanometer; and / or, the SLO camera and the internal fixation are located on the same side of the beam splitter; and / or, the XY galvanometer and the eyepiece are located on the same side of the dichroic mirror; and / or, the XY galvanometer and the Y galvanometer are located on different sides of the dichroic mirror; And / or, the imaging angle of the XY galvanometer or the Y galvanometer includes y=4.5x, where y is the imaging angle; x is the rotation angle of the XY galvanometer or the Y galvanometer; And / or, in response to different structural layers of the human eye fundus, the light source is selected to be 700nm-1400nm; And / or, the Y galvanometer can be a one-dimensional galvanometer or a MEMS galvanometer.

5. The optical ophthalmic tomography imaging system according to claim 4, characterized in that: The XY galvanometer and the Y galvanometer receive the trigger signal synchronously to achieve synchronization, and the OCT spectrometer camera and the SLO camera's SLO fundus image are displayed synchronously; The power monitoring system comprises a light detector, one end of which is a light source interface connected to the OCT light source, and the other end of the light detector is butt-jointed with one end of the optical fiber coupler.

6. The optical ophthalmic tomography imaging system according to claim 5, characterized in that: The power regulation system comprises an attenuator, one end of which is connected to the optical fiber coupler through the optical fiber coupler input interface, and the other end of which is connected to the reference arm assembly through the optical fiber reflector, and the reference arm assembly is connected to the reflector optical path.

7. The optical ophthalmic tomography imaging system according to claim 6, characterized in that: The power regulation system is coupled into the optical fiber coupler, one end of the optical fiber coupler is respectively connected to the optical fiber coupler input interface and the optical fiber coupler input end, the other end of the optical fiber coupler is respectively connected to the optical fiber coupler output end and the polarization controller, and the polarization controller is connected to the optical fiber reflector through an attenuator.

8. The optical ophthalmic tomography imaging system according to claim 7, characterized in that: The polarization control system includes a device card slot for loading optical fibers, the device card slot is connected to a motor drive, and the rotation of the motor drives the optical fiber on the device card slot to swing, thereby adjusting the polarization state of light transmitted by the optical fiber; And / or, the grating is one of a volume holographic grating, a transmission relief grating, and a reflection relief grating.

9. The optical ophthalmic tomography imaging system according to claim 8, characterized in that: The eyepiece includes a pupil positioning component, and the pupil positioning component adopts one of a monocular pupil positioning component, a binocular pupil positioning component, and a trinocular pupil positioning component; the monocular pupil positioning component includes an iris camera arranged below the eyepiece; the binocular pupil positioning component includes two iris cameras arranged on the left and right sides of the eyepiece; the trinocular pupil positioning component includes three iris cameras arranged on the left and right sides of the eyepiece and below the eyepiece; And / or, the reference arm assembly adopts a movable reference arm; the movable reference arm includes: a collimator head, a dove prism, and a corner cube prism connected in an optical path, and the dove prism and the corner cube prism can be relatively displaced to adjust the spacing between the dove prism and the corner cube prism; And / or, the reference arm assembly adopts a fixed reference arm; the fixed reference arm includes: a collimator head, a dove prism, and a corner cube prism connected to the optical path; And / or, the eyepiece is arranged on one side of the dichroic mirror by adjusting the collimation mechanism, and the adjustable collimation mechanism includes a movable collimation lens group and a fixed lens group arranged on one side of the dichroic mirror; the collimation lens group is moved by the collimation drive device, thereby changing the collimation state of the light beam.

10. A tomographic imaging method of an optical ophthalmic tomographic imaging system, characterized in that: The optical ophthalmic tomography imaging system of claim 9 is used to implement the method, comprising the following steps: The optical signal emitted by the OCT light source reaches the eyepiece through the power monitoring system, the fiber coupler and the power adjustment system, and forms an image of the human eye on the side facing the eyepiece; after collecting the optical signal of the fundus, the optical signal is sent to the OCT spectrometer camera through the polarization control system to collect the tomographic image of the human eye; The SLO light source passes through a beam splitter, a Y galvanometer, a dichroic mirror, and the eyepiece to the human eye; after collecting the human eye information, the optical signal is reversibly transmitted to the SLO camera, and the SLO camera converts the optical signal into an electrical signal for processing to obtain a fundus image.

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