CN210204688U - Fundus multi-mode synchronous imaging system - Google Patents
Fundus multi-mode synchronous imaging system Download PDFInfo
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- CN210204688U CN210204688U CN201920290913.XU CN201920290913U CN210204688U CN 210204688 U CN210204688 U CN 210204688U CN 201920290913 U CN201920290913 U CN 201920290913U CN 210204688 U CN210204688 U CN 210204688U
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Abstract
The utility model discloses a synchronous imaging system of fundus multi-modality, include: the optical coherence tomography scanning system comprises an optical coherence tomography module, a slow axis scanning module, an imaging module, a middle reflecting dichroic mirror, a line scanning confocal illumination module, a fast axis scanning module and a flat field lens. The utility model provides a synchronous imaging system of eye ground multimode has realized the effective utilization of optical coherence tomography and the confocal scanning speed of line, has reached the purpose of the quick face formation of image and the tomography of eye ground retina. The utility model discloses with "middle transmission among the prior art, the slit reflecting mirror of both sides reflection" is revised as "middle reflection", and the well anti-dichroscope of both sides transmission can not influence OCT's light and pass in the middle of the anti-dichroscope of well. The utility model improves the imaging resolution of line confocal, has better ghost suppression effect and has no influence on the imaging of OCT; the problem that the imaging resolution of the line confocal imaging technology is affected by the width of the slit in the slit reflector in the prior art is solved.
Description
Technical Field
The utility model relates to an optical imaging technical field, in particular to synchronous imaging system of fundus multi-modality.
Background
The clinical fundus imaging technology mainly comprises a fundus camera, Optical Coherence Tomography (OCT) and confocal scanning imaging, and has advantages and disadvantages in imaging speed, imaging field of view and imaging mode. The fundus camera adopts scintillation exposure, so that the imaging is simple, but the continuous imaging cannot be realized; optical coherence tomography is a tomographic imaging technique, with the deepest imaging depth; the confocal imaging technology is transverse imaging, and the signal-to-noise ratio of an image is high.
Compared with the confocal scanning imaging technology, the transverse imaging speed is high, and the confocal scanning imaging technology is often used as auxiliary imaging of optical coherence tomography. Confocal imaging is further divided into point confocal imaging and line confocal imaging. The imaging quality of the line confocal is slightly reduced, but the imaging speed is greatly improved.
The confocal imaging technology and the optical coherence tomography technology are combined to form a set of multi-mode system (namely, a plurality of imaging technologies are combined), so that the advantages of all the imaging technologies are combined, and multi-directional rapid imaging is realized.
In the literature, "Real-time eye movement correction in phase-resolved OCTangiograph with tracking SLO" reports that a point confocal technology (SLO) and an optical coherence tomography are coupled at the front end of an eye by a dichroic mirror, and the images are respectively imaged without mutual influence, but the imaging synchronization cannot be realized, and the complexity of the system cannot be reduced (see accessories in the literature).
In the documents "Noise analysis of a combined optical coherence tomography and confocal scanning optical system" and "two-dimensional confocal imaging using an OCT light source and scanning optics" there are reports of collecting part of the returned light from an OCT sample as point-confocal imaging light, and using the imaging of the excess light from OCT, the energy utilization is improved, but OCT and point-confocal imaging directions are different, the point-confocal imaging speed is reduced by two orders of magnitude, and the speed is greatly limited (see the attached documents).
The patent of the earlier application of the present applicant discloses a fundus multi-modal simultaneous imaging system (application No. 201810297538.1), which combines line scanning confocal imaging technology with Optical Coherence Tomography (OCT), and uses a resonant mirror to perform synchronous scanning, and uses a slit mirror to perform optical path coupling, wherein the slit mirror can reduce the vertical reflection light of the cornea and the front mirror from entering a line confocal detection camera, thereby reducing the existence of ghost, and OCT can pass through the slit, thereby imaging the fundus. Most of line confocal optical devices are shared in a sample imaging optical path of OCT, the optical paths of the two systems can be always coaxial in one dimension, and therefore synchronous scanning is achieved. And under the condition of reducing hardware overhead, the respective imaging speed is not influenced.
A problem still remains in the above patent is that the width of the slit in the slit mirror will affect the imaging resolution of the line confocal imaging technique. Too small, resolution decreases; too large, the energy utilization is not sufficient. The imaging resolution and ghost suppression effect of line confocal still need to be further improved.
SUMMERY OF THE UTILITY MODEL
The utility model aims to solve the technical problem that to the not enough among the above-mentioned prior art, provide a synchronous imaging system of fundus multimode.
The present application mainly aims at further improvement of the patent (application number 201810297538.1) that the applicant has applied earlier, and changes the slit mirror of the middle transmission and two-side reflection into the middle reflection and two-side transmission middle reflecting dichroic mirror, so that the light that does not affect the OCT passes through the middle of the middle reflecting dichroic mirror. The utility model improves the imaging resolution of line confocal, has better ghost suppression effect and has no influence on the imaging of OCT; the problem that the imaging resolution of the line confocal imaging technology is affected by the width of the slit in the slit reflector in the prior art is solved.
The utility model adopts the technical proposal that: a fundus multi-mode synchronous imaging system comprises an optical coherence tomography module, a slow axis scanning module, an imaging module, a middle reflecting dichroic mirror, a line scanning confocal lighting module, a fast axis scanning module and a flat field lens;
the optical coherence tomography module is used for forming sample light of optical coherence tomography, the slow axis scanning module comprises a slow axis scanning galvanometer and a slow axis focusing lens, the fast axis scanning module comprises a fast axis scanning galvanometer and a fast axis focusing lens, the imaging module comprises an imaging lens, a spectroscope and a detector, and the line scanning confocal illumination module comprises a laser, a collimating lens and a cylindrical lens; the two sides of the middle reflecting dichroic mirror are light-transmitting parts, the middle part is a reflecting part, and the reflecting part in the middle reflects light beams emitted by the line scanning confocal illumination module and transmits light beams emitted by the optical coherence tomography module; wherein:
after the sample light enters the slow-axis scanning galvanometer, the sample light is focused by the slow-axis focusing lens, reflected by the beam splitter and transmitted through the middle part of the middle reflecting dichroic mirror after passing through the imaging lens in sequence and reaches the fast-axis scanning galvanometer;
the laser beam emitted by the laser device is collimated by the collimating lens and focused by the cylindrical lens to form a line beam for line confocal scanning, the line beam is reflected to the fast axis scanning galvanometer by the middle reflection part of the middle reflecting dichroic mirror and is combined with the sample light passing through the middle reflecting dichroic mirror to form combined light;
the combined light passes through the fast axis scanning galvanometer, the fast axis focusing lens and the flat field lens and then synchronously illuminates and images the eyeground, and the combined light returns to the middle reflecting dichroic mirror after being reflected by the eyeground and then sequentially passes through the flat field lens, the fast axis focusing lens and the fast axis scanning galvanometer; part of the line light beam passes through light-transmitting parts on two sides of the middle reflecting dichroic mirror to reach the imaging lens, and then passes through the spectroscope to reach the detector for imaging; the sample light passes through the middle part of the middle reflecting dichroic mirror to reach the imaging lens, and after being reflected by the spectroscope, the sample light passes through the slow-axis focusing lens and the slow-axis scanning mirror in sequence and is subjected to interference imaging in the optical coherence tomography module.
Preferably, the intermediate reflecting dichroic mirror is a flat sheet with a middle plated narrow-band dichroic film.
Preferably, the middle-reflecting dichroic mirror includes a flat sheet and a dichroic prism disposed in the middle of the flat sheet.
Preferably, the optical coherence tomography module is a swept-source optical coherence tomography module or a spectral-domain optical coherence tomography module or a time-domain optical coherence tomography module.
Preferably, the slow axis focusing lens in the slow axis scanning module and the imaging lens in the imaging module form a 4f system, and the slow axis scanning galvanometer and the fast axis scanning galvanometer are respectively located at focal positions of two lenses of the 4f system.
Preferably, the spectroscope is a spectroscope flat sheet or a spectroscope prism or a spectroscope film.
The utility model has the advantages that:
the utility model provides a synchronous imaging system of eye ground multimode, through combining together line scanning quick imaging technique and optical coherence tomography imaging technique, adopt common light path resonance mirror synchronous scanning imaging method effectively to reduce system hardware, and do not influence the scanning of optical coherence tomography when adopting the cavity slit speculum to solve lens and cornea reflection bright speckles, realized the effective utilization of optical coherence tomography and the confocal scanning speed of line, reached the purpose of the quick face formation of image and the tomography of eye ground retina. The utility model discloses with "middle transmission among the prior art, the slit reflecting mirror of both sides reflection" is revised as "middle reflection", and the well anti-dichroscope of both sides transmission can not influence OCT's light and pass in the middle of the anti-dichroscope of well. The utility model improves the imaging resolution of line confocal, has better ghost suppression effect and has no influence on the imaging of OCT; the problem that the imaging resolution of the line confocal imaging technology is affected by the width of the slit in the slit reflector in the prior art is solved.
Drawings
Fig. 1 is a schematic structural view of the fundus multi-modality synchronous imaging system of the present invention;
fig. 2 is a schematic structural diagram of a middle reflecting dichroic mirror in an embodiment of the present invention;
fig. 3 is a schematic structural diagram of a middle reflecting dichroic mirror in another embodiment of the present invention;
fig. 4 is a schematic optical path diagram of a middle reflecting dichroic mirror in an embodiment of the present invention;
fig. 5 is a schematic optical path diagram of a middle reflecting dichroic mirror in another embodiment of the present invention;
fig. 6 is a schematic structural view of an fundus multi-modality simultaneous imaging system according to embodiment 1 of the present invention;
fig. 7 is a schematic structural view of an fundus multi-modality simultaneous imaging system according to embodiment 2 of the present invention.
Detailed Description
The present invention is further described in detail below with reference to examples so that those skilled in the art can implement the invention with reference to the description.
It will be understood that terms such as "having," "including," and "comprising," as used herein, do not preclude the presence or addition of one or more other elements or groups thereof.
As shown in fig. 1, the fundus multi-modal synchronous imaging system of the present embodiment includes an optical coherence tomography module 3, a slow-axis scanning module 2, an imaging module 6, a middle-reflective dichroic mirror 5, a line-scanning confocal illumination module 1, a fast-axis scanning module 4, and a flat-field lens 7.
The optical coherence tomography module 3 is used for forming sample light for optical coherence tomography, the slow axis scanning module 2 comprises a slow axis scanning galvanometer 21 and a slow axis focusing lens 22, the fast axis scanning module 4 comprises a fast axis scanning galvanometer 41 and a fast axis focusing lens 42, the imaging module 6 comprises an imaging lens 61, a spectroscope 62 and a detector 63, and the line scanning confocal illumination module 1 comprises a laser 11, a collimating lens 12 and a cylindrical lens 13; the two sides of the middle reflecting dichroic mirror 5 are light-transmitting parts, the middle part is a reflecting part, and the reflecting part in the middle reflects the light beam emitted by the line scanning confocal illumination module 1 and transmits the light beam emitted by the optical coherence tomography module 3; wherein:
the light path is as follows:
after the sample light enters the slow axis scanning galvanometer 21, the sample light is focused by the slow axis focusing lens 22, reflected by the spectroscope 62 and transmitted through the middle part of the middle reflecting dichroic mirror 5 after passing through the imaging lens 61 in sequence and reaches the fast axis scanning galvanometer 41;
the laser beam emitted by the laser 11 is collimated by the collimating lens 12 and focused by the cylindrical lens 13 to form a line beam for line confocal scanning, the line beam is reflected to the fast axis scanning galvanometer 41 by the middle reflection part of the middle reflecting dichroic mirror 5 and is combined with the sample light passing through the middle reflecting dichroic mirror 5 to form combined light;
the combined light passes through the fast axis scanning galvanometer 41, the fast axis focusing lens 42 and the flat field lens 7 to synchronously illuminate and image the fundus, and after being reflected by the fundus, the combined light returns to the middle reflecting dichroic mirror 5 after sequentially passing through the flat field lens 7, the fast axis focusing lens 42 and the fast axis scanning galvanometer 41; part of the line light beam passes through light-transmitting parts at two sides of the middle reflecting dichroic mirror 5 to reach the imaging lens 61, and then reaches the detector 63 through the transmission spectroscope 62 for imaging; the sample light passes through the middle part of the middle reflecting dichroic mirror 5 to reach the imaging lens 61, and after being reflected by the spectroscope 62, the sample light passes through the slow-axis focusing lens 22 and the slow-axis scanning galvanometer 21 in sequence and is subjected to interference imaging in the optical coherence tomography module 3. 7
The optical coherence tomography module 3 is a swept-source optical coherence tomography module, a spectral domain optical coherence tomography module or a time domain optical coherence tomography module.
The slow-axis focusing lens 22 in the slow-axis scanning module 2 and the imaging lens 61 in the imaging module 6 form a 4f system, and the slow-axis scanning galvanometer 21 and the fast-axis scanning galvanometer 41 are respectively located at focal positions of the two lenses of the 4f system.
The beam splitter 62 is a beam splitter plate 51, a beam splitter prism or a beam splitter film.
Referring to fig. 2, in a preferred embodiment, the intermediate reflecting dichroic mirror 5 is a flat sheet 51 with a narrow band dichroic film 52 in the middle. The dichroic film 52 reflects the line beam from the line scanning confocal illumination module 1 and transmits the sample light from the optical coherence tomography module 3. Fig. 4 is a schematic optical path diagram of the middle reflecting dichroic mirror 5, in which the left side represents reflection of the line beam and the right side represents transmission of the sample light.
Referring to fig. 3, in another preferred embodiment, the intermediate counter-dichroic mirror 5 includes a flat sheet 51 and a dichroic prism 53 disposed in the middle of the flat sheet 51. The dichroic prism 53 reflects the line beam emitted from the line scanning confocal illumination module 1 and transmits the sample light emitted from the optical coherence tomography module 3. Fig. 5 is a schematic optical path diagram of the middle reflecting dichroic mirror 5, in which the left side represents reflection of the line beam and the right side represents transmission of the sample light.
The utility model provides a synchronous imaging system of eye ground multimode, through combining together line scanning quick imaging technique and optical coherence tomography imaging technique, adopt common light path resonance mirror synchronous scanning imaging method effectively to reduce system hardware, and do not influence the scanning of optical coherence tomography when adopting the cavity slit speculum to solve lens and cornea reflection bright speckles, realized the effective utilization of optical coherence tomography and the confocal scanning speed of line, reached the purpose of the quick face formation of image and the tomography of eye ground retina. The utility model discloses with "middle transmission among the prior art, the slit reflecting mirror of both sides reflection" is revised as "middle reflection", and the well anti-dichroscope of both sides transmission can not influence OCT's light and pass in the middle of the anti-dichroscope of well. The utility model improves the imaging resolution of line confocal, has better ghost suppression effect and has no influence on the imaging of OCT; the problem that the imaging resolution of the line confocal imaging technology is affected by the width of the slit in the slit reflector in the prior art is solved.
The following 2 specific examples are provided to further illustrate the present invention.
Example 1
Referring to fig. 6, it is a schematic structural diagram of an fundus multi-modality synchronous imaging system provided in embodiment 1 of the present invention. In this embodiment, the optical coherence tomography module 3 is a swept-source optical coherence tomography unit, and includes: a light source 311, a first coupler 312, a second collimator 313, a compensating mirror 316, a right-angle reflecting prism 317, a third collimator 315, a second coupler 318, and a balanced detector 319.
Specifically, light emitted by the light source 311 for optical coherence tomography is split into two light beams after passing through the first coupler 312, wherein one light beam is emitted through the collimator 314, passes through the compensating mirror 316 and the right-angle reflecting prism 317, is received by the collimator 316, and reaches the second coupler 318 as reference light; the other part of the light reaches the collimator 313 from the first coupler 312 as sample light for optical coherence tomography, and is emitted from the collimator 313 and then enters the slow axis scanning galvanometer 21, and then enters the spectroscope 62 after passing through the slow axis focusing lens 22, and the sample light reflected by the spectroscope 62 is focused by the imaging lens 61 and then passes through the middle part of the middle reflecting dichroic mirror 5 to reach the fast axis scanning galvanometer 41.
The laser beam emitted by the laser 11 sequentially passes through the collimating lens 12 and the cylindrical lens 13 to form a line beam for line confocal scanning, the line beam is reflected to the fast axis scanning galvanometer 41 by the middle reflection part of the middle reflecting dichroic mirror 5, and is combined with the sample light passing through the middle reflecting dichroic mirror 5 to form combined light;
the combined light passes through the fast axis scanning galvanometer 41, the fast axis focusing lens 42 and the flat field lens 7 and then synchronously illuminates and images the fundus, and the combined light returns to the middle reflecting dichroic mirror 5 after sequentially passing through the flat field lens 7, the fast axis focusing lens 42 and the fast axis scanning galvanometer 41 after being reflected by a fundus retina 8; part of the line light beam passes through light-transmitting parts on two sides of the middle reflecting dichroic mirror 5 to reach the imaging lens 61, and then passes through the spectroscope 62 to reach the detector 63 for imaging; the sample light passes through the middle part of the middle reflecting dichroic mirror 5 to reach the imaging lens 61, and after being reflected by the spectroscope 62, the sample light passes through the slow-axis focusing lens 22 and the slow-axis scanning galvanometer 21 in sequence and is subjected to interference imaging in the optical coherence tomography module 3. The sample light entering the optical coherence tomography module 3 is received by the collimator 313, coupled by the first coupler 312, and most of the light enters the second coupler 318, interferes with the reference light to be imaged, and is finally received and imaged by the balanced detector 319.
In a further preferred embodiment, the model of the swept-source optical coherence tomography module 3 is santec-HSL-10, the sweep speed is 100kHz, and the center wavelength is 1060 nm. It can be understood that the model of the swept-source optical coherence tomography module 3, the sweep speed, and the center wavelength are not limited to the above settings, and can be adjusted in practice according to practical situations.
It can be understood that, after the light emitted from the swept-source 311 passes through the first coupler 312 of the coupler 322, 80% of the light passes through the second collimator 313, the compensating mirror 316 and the right-angle reflecting prism 317 and is received by the third collimator 315 again, and the other 20% of the light reaches the collimator 313 as the sample light.
In a further preferred embodiment, the fast axis scanning galvanometer 41 has a scanning speed of 200Hz and a mirror size of 10mmX15 mm. It can be understood that, in practice, the scanning speed and the mirror size of the fast axis scanning galvanometer 41 can be adjusted according to practical situations.
The scanning speed set by the slow axis scanning galvanometer 21 is 0.5Hz, the model is the same as that of the fast axis scanning galvanometer 41, the models are Cambridge 6220H, and the scanning axes are vertical to each other. It is understood that the model of the slow axis scanning galvanometer 21 is not limited to the above model, and may be adjusted in practice according to practical situations.
In a further preferred embodiment, the slow-axis focusing lens 22 and the imaging lens 61 form a 4f system, and the slow-axis scanning galvanometer 21 and the fast-axis scanning galvanometer 41 are both located at the focal point of the lens of the 4f system.
In a further preferred embodiment, the laser 11 of the line scanning confocal illumination module 1 emits 650nm light, which passes through the collimator 142 and becomes a parallel light spot with a diameter of 20mm, and is converged into a line beam by the cylindrical lens 13 with a focal length of 50mm again, the line beam is reflected by the middle of the middle reflecting dichroic mirror 5 during illumination, and the line beam reaches the imaging lens 61 through the light-transmitting parts at the two sides of the middle reflecting dichroic mirror 5 during imaging.
In a preferred embodiment, the beam splitter 62 is a beam splitter plate, a beam splitter prism or a beam splitter film.
In a preferred embodiment, the intermediate reflecting dichroic mirror 5 is a flat sheet 51 with a narrow band dichroic film 52 in the middle. The dichroic film 52 reflects the line beam from the line scanning confocal illumination module 1 and transmits the sample light from the optical coherence tomography module 3.
In another preferred embodiment, the middle-reflecting dichroic mirror 5 includes a flat sheet 51 and a dichroic prism 53 disposed in the middle of the flat sheet. The dichroic prism 53 reflects the line beam emitted from the line scanning confocal illumination module 1 and transmits the sample light emitted from the optical coherence tomography module 3.
In some preferred embodiments, the beam splitter 62 is a beam splitter plate, a beam splitter prism, or a beam splitter film. Preferably, the beam splitter is a thorlabdmsp 805, short pass, cut to wavelength 805 nm.
In some preferred embodiments, the detector 63 is model E2V-EM4, pixel size 512pixels, maximum sampling rate 210 kHz.
Example 2
Referring to fig. 7, a schematic structural diagram of an fundus multi-modality synchronous imaging system according to embodiment 2 of the present invention is shown.
In the present embodiment, the optical coherence tomography module 3 is a spectral domain optical coherence tomography unit, and includes a semiconductor laser 321, a coupler 322, a collimator 328, a compensation mirror 325, a plane mirror 326, a collimator 327, a collimator 328, a grating 329, a focusing lens 330, and a line camera 331.
The light source of the spectral domain optical coherence tomography unit is a semiconductor laser 321 with the model of SLD-351, the central wavelength is 830nm, and the bandwidth is 80 nm.
After light emitted by the semiconductor laser 321 passes through the coupler 322, 80% of the light passes through the collimator 324 and the compensating mirror 325, is reflected by the plane mirror 326, and is received by the collimator 324 again; in addition, 20% of the light reaches the collimator 323 as sample light, and is emitted from the collimator 323 and then enters the slow-axis scanning galvanometer 21, and then enters the spectroscope 62 after passing through the slow-axis focusing lens 22, and the sample light reflected by the spectroscope 62 is focused by the imaging lens 61 and then passes through the middle part of the middle reflecting dichroic mirror 5 to reach the fast-axis scanning galvanometer 41.
The laser beam emitted by the laser 11 sequentially passes through the collimator 12 and the cylindrical lens 13 to form a line beam for line confocal scanning, the line beam is reflected to the fast axis scanning galvanometer 41 by the middle reflection part of the middle reflecting dichroic mirror 5, and is combined with the sample light passing through the middle reflecting dichroic mirror 5 to form combined light;
the combined light passes through the fast axis scanning galvanometer 41, the fast axis focusing lens 42 and the flat field lens 7 and then synchronously illuminates and images the fundus, and the combined light returns to the middle reflecting dichroic mirror 5 after sequentially passing through the flat field lens 7, the fast axis focusing lens 42 and the fast axis scanning galvanometer 41 after being reflected by a fundus retina 8; part of the line light beam passes through light-transmitting parts on two sides of the middle reflecting dichroic mirror 5 to reach the imaging lens 61, and then passes through the spectroscope 62 to reach the detector 63 for imaging; the sample light passes through the middle part of the middle reflecting dichroic mirror 5 to reach the imaging lens 61, and after being reflected by the spectroscope 62, the sample light passes through the slow-axis focusing lens 22 and the slow-axis scanning galvanometer 21 in sequence and is subjected to interference imaging in the optical coherence tomography module 3.
The sample light entering the optical coherence tomography module 3 is received by the collimator 323, enters the coupler 322 to generate interference imaging with the reference light, enters the collimator 327, is collimated into parallel beams by the collimating mirror 328, is separated by the grating 329 from each spectrum, is focused by the focusing lens 330, and is finally received by the line camera 331.
In a preferred embodiment, the intermediate reflecting dichroic mirror 5 is a flat sheet 51 with a narrow band dichroic film 52 in the middle. The dichroic film 52 reflects the line beam from the line scanning confocal illumination module 1 and transmits the sample light from the optical coherence tomography module 3.
In another preferred embodiment, the middle-reflecting dichroic mirror 5 includes a flat sheet 51 and a dichroic prism 53 disposed in the middle of the flat sheet. The dichroic prism 53 reflects the line beam emitted from the line scanning confocal illumination module 1 and transmits the sample light emitted from the optical coherence tomography module 3.
While the embodiments of the invention have been disclosed above, it is not limited to the applications listed in the description and the embodiments, which are fully applicable in all kinds of fields where the invention is suitable, and further modifications may readily be made by those skilled in the art, and the invention is therefore not limited to the specific details without departing from the general concept defined by the claims and the scope of equivalents.
Claims (6)
1. A fundus multi-mode synchronous imaging system is characterized by comprising an optical coherence tomography module, a slow axis scanning module, an imaging module, a middle reverse dichroic mirror, a line scanning confocal illumination module, a fast axis scanning module and a flat field lens;
the optical coherence tomography module is used for forming sample light of optical coherence tomography, the slow axis scanning module comprises a slow axis scanning galvanometer and a slow axis focusing lens, the fast axis scanning module comprises a fast axis scanning galvanometer and a fast axis focusing lens, the imaging module comprises an imaging lens, a spectroscope and a detector, and the line scanning confocal illumination module comprises a laser, a collimating lens and a cylindrical lens; the two sides of the middle reflecting dichroic mirror are light-transmitting parts, the middle part is a reflecting part, and the reflecting part in the middle reflects light beams emitted by the line scanning confocal illumination module and transmits light beams emitted by the optical coherence tomography module; wherein:
after the sample light enters the slow-axis scanning galvanometer, the sample light is focused by the slow-axis focusing lens, reflected by the beam splitter and transmitted through the middle part of the middle reflecting dichroic mirror after passing through the imaging lens in sequence and reaches the fast-axis scanning galvanometer;
the laser beam emitted by the laser device is collimated by the collimating lens and focused by the cylindrical lens to form a line beam for line confocal scanning, the line beam is reflected to the fast axis scanning galvanometer by the middle reflection part of the middle reflecting dichroic mirror and is combined with the sample light passing through the middle reflecting dichroic mirror to form combined light;
the combined light passes through the fast axis scanning galvanometer, the fast axis focusing lens and the flat field lens and then synchronously illuminates and images the eyeground, and the combined light returns to the middle reflecting dichroic mirror after being reflected by the eyeground and then sequentially passes through the flat field lens, the fast axis focusing lens and the fast axis scanning galvanometer; part of the line light beam passes through light-transmitting parts on two sides of the middle reflecting dichroic mirror to reach the imaging lens, and then passes through the spectroscope to reach the detector for imaging; the sample light passes through the middle part of the middle reflecting dichroic mirror to reach the imaging lens, and after being reflected by the spectroscope, the sample light passes through the slow-axis focusing lens and the slow-axis scanning mirror in sequence and is subjected to interference imaging in the optical coherence tomography module.
2. An fundus multi-modal synchronized imaging system according to claim 1, wherein said intermediate anti-dichroic mirror is a flat sheet with a middle plated narrow band dichroic film.
3. An fundus multi-modality simultaneous imaging system according to claim 1, wherein said intermediate-reflection dichroic mirror comprises a flat sheet and a dichroic prism disposed in the middle of said flat sheet.
4. An fundus multi-modal simultaneous imaging system according to claim 2 or 3, wherein said optical coherence tomography module is a swept source optical coherence tomography module or a spectral domain optical coherence tomography module or a time domain optical coherence tomography module.
5. An eyeground multi-mode synchronous imaging system as claimed in claim 2 or 3, characterized in that the slow axis focusing lens in the slow axis scanning module and the imaging lens in the imaging module form a 4f system, and the slow axis scanning galvanometer and the fast axis scanning galvanometer are respectively located at the focal positions of the two lenses of the 4f system.
6. An fundus multi-modal simultaneous imaging system according to claim 1, wherein said beam splitter is a beam splitter plate or a beam splitter prism or a beam splitter film.
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