Ophthalmic optical imaging system

Abstract

An ophthalmic optical imaging system comprises an OCT light source, an imaging light source, an opening light splitting device with a light through hole and a fundus confocal scanning imaging module of a polychromatic light detection device, irradiation light of the OCT light source is split through an optical fiber coupler, and one part of irradiation light is transmitted to a reference arm module and then is transmitted to the optical fiber coupler to serve as reference light; the other part is input into the OCT sample arm module; the imaging light source generates infrared light and / or visible light to be input into the OCT sample arm module; light input into the OCT sample arm module penetrates through the light through hole to irradiate the fundus, signal light returned from the fundus is subjected to light splitting by the perforated light splitting device, and part of the signal light returns to the optical fiber coupler through the light through hole, is converged with reference light returned by the reference arm module and then is transmitted to the OCT signal acquisition module to generate an OCT image; the other part of the signal light is guided to the polychromatic light detection device by the perforated light splitting device to generate confocal scanning infrared preview imaging and / or confocal scanning visible light color imaging on the fundus; the system is simple in structure and low in cost.

Description

Technical Field

[0001] The present invention relates to the technical field of fundus imaging, and in particular to an ophthalmic optical imaging system. Background Art

[0002] Optical coherence tomography (OCT) is an emerging optical imaging technology. Compared with traditional clinical imaging methods, it has the advantages of high resolution, fast imaging speed, no radiation damage, moderate price, and compact structure. It is an important potential tool for basic medical research and clinical diagnosis applications. Currently, among the various ophthalmic devices using optical instruments, OCT devices used for ophthalmic examination and treatment have become an indispensable ophthalmic device for the diagnosis of ophthalmic diseases.

[0003] The fundus confocal scanning imaging technology can improve the optical resolution and contrast of microscopic images by using spatial pinholes to block defocused light. However, the inventors of the present invention have found in long-term research and development that in order to achieve large-scale high-definition and high-speed confocal imaging of the fundus, it is often necessary for the scanning mechanism and signal acquisition and processing system to have high-speed scanning and acquisition performance, which will complicate the system hardware and increase the cost accordingly.

[0004] Application No. 202011120798.5 “An ophthalmic measurement system and method” introduces a complex ophthalmic OCT imaging system, but it does not have the fundus preview and color imaging functions when operating the eye to be tested.

[0005] Application No. 202210493429.3 “A fundus imaging optical system” introduces a fundus imaging optical system. Although it uses a fundus color imaging solution, it does not have the OCT system function.

[0006] Application No. 201610292370.6 “A multi-color line scanning fundus imaging device and a multi-color image synthesis method” introduces a fundus imaging optical system, but it does not have the OCT system function. In addition, the imaging camera used is relatively expensive. Summary of the invention

[0007] The object of the present invention is to provide an ophthalmic optical imaging system, which can simply and reliably combine fundus confocal scanning infrared preview imaging and / or fundus confocal scanning visible light color imaging with an OCT system.

[0008] To achieve the above object, the present invention adopts the following technical solutions:

[0009] An ophthalmic optical imaging system, comprising an OCT light source, an imaging light source, a reference arm module, an OCT sample arm module, a fiber coupler, an OCT signal acquisition module and a fundus confocal scanning imaging module, wherein the fundus confocal scanning imaging module comprises an aperture spectrometer and a multicolor light detection device, the aperture spectrometer having a light-through hole; after the illumination light emitted by the OCT light source is split by the fiber coupler, a part of it is transmitted to the reference arm module and then to the fiber coupler as reference light, and the other part is input to the OCT sample arm module; the imaging light source generates a signal for confocal scanning imaging The infrared light and / or visible light is input into the OCT sample arm module; the light input into the OCT sample arm module passes through the light-through hole of the aperture spectrometer to illuminate the fundus, and the signal light returned from the fundus is split by the aperture spectrometer, a part of the signal light is returned to the fiber coupler through the light-through hole, and is combined with the reference light returned by the reference arm module and then transmitted to the OCT signal acquisition module to generate an OCT image, and the other part of the signal light is guided by the aperture spectrometer to the multi-color light detection device to realize confocal scanning infrared preview imaging and / or confocal scanning visible light color imaging of the fundus.

[0010] In some embodiments of the present invention, the light generated by the imaging light source is coupled with the light input from the OCT light source to the OCT sample arm module through a light output spectroscope after passing through a collimating lens, and then they are combined into one output; or the light generated by the imaging light source and the light output from the OCT light source are coupled through a wavelength division multiplexer, and then they are combined into one output through a fiber optic collimator.

[0011] In some embodiments of the present invention, the multi-color light detection device includes a spectrometer and a multi-color detector, and the multi-color light received by the multi-color light detection device is split by the spectrometer and then received by the multi-color detector respectively, wherein the spectrometer includes a wavelength division multiplexer.

[0012] In some embodiments of the present invention, the polychromatic light detection device includes multiple spectroscopes, a multi-path aperture and a polychromatic detector. The polychromatic light received by the polychromatic light detection device is split by the multiple spectroscopes and respectively converged on the multi-path aperture. Each color light passes through the multi-path aperture and is then respectively received by the polychromatic detector.

[0013] In some embodiments of the present invention, the open-hole spectrometer is an open-hole prism with a light hole. The light input into the OCT sample arm module passes through the light hole of the open-hole prism and then illuminates the fundus. A portion of the signal light returning from the fundus returns to the fiber coupler through the light hole of the open-hole prism, while the other portion is refracted through the peripheral area of ​​the light hole of the open-hole prism and then transmitted to the multi-color light detection device.

[0014] In some embodiments of the present invention, a compensation prism is provided between the aperture prism and the polychromatic light detection device, and the signal light refracted by the aperture prism is further refracted by the compensation prism and then received by the polychromatic light detection device.

[0015] In some embodiments of the present invention, the apertured spectroscopic device is an apertured reflector having a light-through hole, and the light input into the OCT sample arm module passes through the light-through hole of the apertured reflector and then illuminates the fundus, and a portion of the signal light returning from the fundus returns to the fiber coupler through the light-through hole of the apertured reflector, while the other portion is reflected by an area surrounding the light-through hole of the apertured reflector and then transmitted to the multi-color light detection device.

[0016] In some embodiments of the present invention, the OCT sample arm module includes an iris split-image imaging module, which includes an iris illumination light source, an iris imaging lens and an iris camera device, wherein the light emitted by the iris illumination light source is irradiated to the anterior chamber of the eye to be tested, reflected by the anterior chamber tissue, and the reflected light passes through the iris imaging lens and is captured by the iris camera device.

[0017] In some embodiments of the present invention, the OCT sample arm module includes an optical path scanning device, a field lens, a pre-beam splitter and an eyepiece objective lens. The irradiated light passing through the light hole of the open-aperture beam splitter device is reflected by the optical path scanning device, passes through the field lens, is reflected by the pre-beam splitter to the eyepiece objective lens, and converges to the fundus through the eye to be tested; the iris split-image imaging modules are distributed in pairs on the left and right sides of the eyepiece objective lens.

[0018] In some embodiments of the present invention, the OCT sample arm module further includes a fixation optical module, which includes a fixation light source for providing a fixation mark for the subject's eye to fixate; the front beam splitter transmits the fixation light from the fixation light source.

[0019] The present invention has the following beneficial effects:

[0020] The present invention proposes an ophthalmic optical imaging system, wherein an OCT light source and an imaging light source are provided. After the illumination light emitted by the OCT light source is split by an optical fiber coupler, a part of the illumination light is transmitted to a reference arm module and then to an optical fiber coupler as a reference light, and the other part is input to an OCT sample arm module; the imaging light source generates infrared light and / or white light for confocal scanning imaging and inputs the OCT sample arm module; a fundus confocal scanning imaging module is also provided, which includes an aperture spectrometer and a multicolor light detection device, the aperture spectrometer having a light through hole, the light input to the OCT sample arm module passes through the light through hole of the aperture spectrometer and then illuminates the fundus, and the signal light returned from the fundus is split by the aperture spectrometer. A portion of the signal light returns to the fiber coupler through the light hole, merges with the reference light returned by the reference arm module, and is then transmitted to the OCT signal acquisition module to generate an OCT image. The other portion of the signal light is guided by the apertured spectroscopic device to the multicolor light detection device to generate confocal scanning infrared preview imaging and / or confocal scanning visible light color imaging of the fundus. The present invention can combine the fundus confocal scanning infrared preview imaging and / or fundus confocal scanning visible light imaging with the optical path system of the OCT system, thereby reducing the cost of the fundus imaging system, which is conducive to the popularization of OCT equipment, and can also allow more patients to enjoy the fundus non-destructive detection technology, and can provide doctors with an intuitive graphical detection method for diagnosis.

[0021] In addition, in some embodiments, the following beneficial effects are also achieved:

[0022] In some embodiments of the present invention, the return light from the fundus is refracted through an aperture prism, and a compensating prism is used to eliminate chromatic aberration to achieve confocal imaging of the fundus; in addition, combining the gaze optical path and the split-image iris alignment optical path can form an ophthalmic OCT detection device that is convenient for doctors to use.

[0023] In some embodiments of the present invention, through wavelength division multiplexing, fundus OCT imaging, fundus infrared imaging and / or fundus visible light color imaging can be obtained without adding a scanning mechanism.

[0024] In some embodiments of the present invention, the working distance can be automatically adjusted according to the principle of iris split-image imaging, and the main optical axis of the probe optical path can be aligned with the pupil center of the eye to be tested; the fundus refractive adjustment can be assisted by the posterior segment OCT imaging quality; a common imaging optical path refractive adjustment mirror can be used to achieve synchronous refractive adjustment of the fixation optical path, fundus OCT imaging optical path, and fundus confocal scanning imaging optical path; and combined with technologies such as automatic recognition of posterior segment OCT imaging, fully automated detection of the system can be achieved.

[0025] Other beneficial effects of the embodiments of the present invention will be further described below. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1ais a schematic diagram of an OCT imaging module and an OCT sample arm module according to an embodiment of the present invention;

[0027] Figure 1b is a schematic diagram of a fundus confocal scanning imaging module according to an embodiment of the present invention;

[0028] Figure 1c is a schematic diagram of a fixation optical module according to an embodiment of the present invention;

[0029] Figure 1d is a schematic diagram of an iris split-image imaging module according to an embodiment of the present invention;

[0030] Figure 2a is a schematic diagram of an ophthalmic optical imaging system in Embodiment 1 of the present invention;

[0031] Figure 2b is a schematic diagram of a spectroscopic device in an ophthalmic optical imaging system in Embodiment 1 of the present invention;

[0032] Figure 3 is a schematic diagram of an ophthalmic optical imaging system in Embodiment 2 of the present invention;

[0033] Figure 4 is a schematic diagram of an ophthalmic optical imaging system in Embodiment 3 of the present invention;

[0034] Figure 5 Schematic diagram of the composition and installation of the iris split-image imaging module in Embodiment 3 of the present invention

[0035] Figure 6 is a schematic diagram of an ophthalmic optical imaging system in Example 4 of the present invention;

[0036] Figure 7a is a schematic diagram of an apertured prism in Embodiments 1-3 of the present invention;

[0037] Figure 7b is a schematic diagram of a reflector with an aperture in Embodiment 4 of the present invention;

[0038] The reference numerals are as follows:

[0039] 10 is a probe module, 110 is an OCT imaging module, 130 is an OCT sample arm module, 150 is a fundus confocal scanning imaging module, 170 is a fixation optical module, and 180 is an iris split-image imaging module;

[0040] 1101 is an OCT light source, 1103 is a fiber coupler, 1105 is a polarization controller, 1107 is a fiber collimator, and 1109 is an optical path scanning device;

[0041] 11091 is an X-direction scanning device, and 11093 is a Y-direction scanning device;

[0042] 1121 is the reference arm optical path lens, 1123 is the reference arm reflector, 1141 is the detector, and 1143 is the computer;

[0043] 1301 is the field lens, 1303 is the front beam splitter, and 1305 is the eyepiece lens;

[0044] 1500 is a multi-color light detection device, 1501 is an aperture prism, 1503 is a compensation prism, 1505 is a converging lens, 1506 is a first beam splitter, 1507 is a multi-path aperture, 1508 is a second beam splitter, 1509 is a multi-color detector, and 1510 is a third beam splitter;

[0045] 15011 is a light-through hole, and 15012 is a peripheral area of ​​the light-through hole;

[0046] 506 is a spectrometer, 1507IR is an infrared detection light path aperture, 1507R is a red light detection light path aperture, 1507G is a green light detection light path aperture, 1507B is a blue light detection light path aperture, 1509IR is an infrared detector, 1509R is a red light detector, 1509G is a green light detector, and 1509B is a blue light detector;

[0047] 1601 is an imaging light source, 1607 is a polychromatic light passing through a collimating lens, and 1609 is a light-emitting beam splitter;

[0048] 1701 is a fixation light source, 1703 is a fixation light path lens, 1705 is a fixation light path aperture, and 1707 is a fixation relay lens;

[0049] 1811 is an iris illumination light source, 1811L is a left iris illumination light source, 1811R is a right iris illumination light source, 1801L is a left iris camera device, 1801R is a right iris camera device, 1803L is a left iris imaging lens, 1803R is a right iris imaging lens, L18L is a left iris split-image optical path, and L18R is a right iris split-image optical path;

[0050] 2501 is an apertured reflector; 25011 is a light-through hole of the apertured reflector; 25012 is a peripheral area of ​​the light-through hole of the apertured reflector;

[0051] L1 is the main optical axis. DETAILED DESCRIPTION

[0052] The present invention is further described below with reference to the accompanying drawings and in combination with preferred embodiments. It should be noted that the embodiments and features in the embodiments of the present application can be combined with each other without conflict.

[0053] It should be noted that the directional terms such as left, right, up, down, top, and bottom in this embodiment are merely relative concepts or are based on the normal use status of the product, and should not be considered as restrictive.

[0054] The following embodiment of the present invention proposes an ophthalmic optical imaging system, which is an optical path system that combines fundus confocal scanning infrared preview imaging and / or fundus confocal scanning visible light color imaging with an OCT system, and is mainly used for measuring patient eye-related optical parameters and examining the patient's eyes. It can measure imaging data such as fundus infrared imaging, fundus visible light color imaging, OCT imaging, anterior segment photography, etc. of the eye to be tested, and further obtain many ophthalmological related parameters such as corneal thickness, anterior chamber depth, white-to-white distance, etc. of the eye to be tested.

[0055] The following embodiment of the present invention proposes an ophthalmic optical imaging system, including an OCT light source 1101, an imaging light source 1601, a reference arm module, an OCT sample arm module 130, a fiber coupler 1103, an OCT signal acquisition module, and a fundus confocal scanning imaging module 150, wherein the fundus confocal scanning imaging module 150 includes an aperture spectrometer (such as 1501 or 2501) and a multicolor light detection device 1500, the aperture spectrometer has a light hole 15011 (as shown in FIG. 7), the illumination light emitted by the OCT light source 1101 is split by the fiber coupler 1103, a part of which is transmitted to the reference arm module and then to the fiber coupler 1103 as a reference light, and the other part is input into the OCT sample arm module 130. ; The imaging light source 1601 generates infrared light and / or white light for confocal scanning imaging and inputs into the OCT sample arm module 130; the light input into the OCT sample arm module 130 passes through the light hole 15011 of the aperture spectrometer and illuminates the fundus, and the signal light returned from the fundus is split by the aperture spectrometer (such as 1501 or 2501), a part of the signal light returns to the fiber coupler 1103 through the light hole 15011, and is transmitted to the OCT signal acquisition module after merging with the reference light returned by the reference arm module to generate an OCT image, and the other part of the signal light is guided by the aperture spectrometer to the multi-color light detection device 1500 to realize confocal scanning infrared preview imaging and / or confocal scanning visible light color imaging of the fundus.

[0056] In a preferred embodiment, the light generated by the imaging light source 1601 is coupled with the light input from the OCT light source 1101 to the OCT sample arm module 130 through the light output spectroscope 1609 after passing through the collimating lens 1607, and then is output as one channel. Alternatively, the light generated by the imaging light source 1601 and the light output from the OCT light source are coupled through a wavelength division multiplexer, and then are output through a fiber collimator.

[0057] In a preferred embodiment, the multicolor light detection device 1500 includes a spectrometer 506 and a multicolor detector 1509. The multicolor light received by the multicolor light detection device 1500 is split by the spectrometer 506 and then received by the multicolor detector 1509 respectively. The spectrometer 506 includes a wavelength division multiplexer.

[0058] In a preferred embodiment, the polychromatic light detection device 1500 includes a plurality of spectroscopes, a multi-path aperture 1507 and a polychromatic detector 1509. The polychromatic light received by the polychromatic light detection device 1500 is split by the plurality of spectroscopes and respectively converged on the multi-path aperture 1507. Each color light passes through the multi-path aperture 1507 and is then respectively received by the polychromatic detector 1509.

[0059] In a preferred embodiment, the open-hole spectroscopic device is an open-hole prism 1501 having a light hole 15011. The light input into the OCT sample arm module 130 passes through the light hole 15011 of the open-hole prism 1501 and then illuminates the fundus. A portion of the signal light returning from the fundus returns to the fiber coupler 1103 through the light hole 15011 of the open-hole prism 1501, while the other portion is refracted through an area 15012 surrounding the light hole of the open-hole prism 1501 and then transmitted to the multi-color light detection device 1500.

[0060] In a preferred embodiment, a compensation prism 1503 is provided between the aperture prism 1501 and the polychromatic light detection device 1500 , and the signal light refracted by the aperture prism 1501 is further refracted by the compensation prism 1503 and then received by the polychromatic light detection device 1500 .

[0061] In a preferred embodiment, the open-aperture spectroscopic device is an open-aperture reflector 2501 having a light-through hole, and the light-through hole is an open-aperture reflector light-through hole 25011. The light input into the OCT sample arm module 130 passes through the open-aperture reflector light-through hole 25011 and then illuminates the fundus. A portion of the signal light returning from the fundus is returned to the fiber coupler 1103 through the open-aperture reflector light-through hole 25011, while the other portion is reflected by the peripheral area 25012 of the open-aperture reflector light-through hole and then transmitted to the multi-color light detection device 1500.

[0062] In a preferred embodiment, the OCT sample arm module 130 includes an iris split-image imaging module 180, which includes an iris illumination light source 1811, an iris imaging lens, and an iris camera device, wherein the light emitted by the iris illumination light source 1811 is irradiated to the anterior chamber of the eye to be tested, and is reflected by the anterior chamber tissue of the eye to be tested. The reflected light passes through the iris imaging lens and is captured by the iris camera device.

[0063] In a preferred embodiment, the OCT sample arm module 130 includes an optical path scanning device 1109, a field lens 1301, a pre-beam splitter and an eyepiece objective lens 1305. The irradiated light passing through the light hole of the open-aperture beam splitter device is reflected by the optical path scanning device 1109, passes through the field lens 1301, is reflected by the pre-beam splitter to the eyepiece objective lens 1305, and converges to the fundus through the eye to be tested; the iris split-image imaging modules 180 are distributed in pairs on the left and right sides of the eyepiece objective lens 1305.

[0064] In a preferred embodiment, the OCT sample arm module 130 further includes a fixation optical module 170 , which includes a fixation light source 1701 for providing a fixation mark for the subject's eye to fixate; the front beam splitter transmits the fixation light from the fixation light source 1701 .

[0065] Example 1

[0066] See also Figure 2a The present embodiment proposes an ophthalmic optical imaging system, comprising: an OCT imaging module, an OCT sample arm module 130 and a fundus confocal scanning imaging module 150. To facilitate the subject's fixation, a fixation optical module 170 is introduced. In addition, to facilitate operation, an iris split-image imaging module 180 is introduced.

[0067] The system probe module 10 is defined as comprising: an OCT sample arm module 130 and a fundus confocal scanning imaging module 150. Further, the system probe module 10 comprises a fixation optical module 170 and an iris split-image imaging module 180.

[0068] The probe module 10 as a whole can achieve X / Y / Z three-dimensional translation (transmission mechanism is not shown). In this embodiment, the X-axis is defined as an axis perpendicular to the paper. The Y-axis is defined as an axis parallel to the paper and in the up-down direction. The Z-axis is defined as an axis parallel to the paper and in the left-right direction. The above definitions are only for the convenience of description of this embodiment.

[0069] The combined module 18 is composed of the eyepiece objective lens 1305 and the iris split-image imaging module 180. The module can move along the Z direction (the transmission mechanism is not shown) to achieve diopter adjustment.

[0070] The following is a detailed description of each module in the system of this embodiment. 。

[0071] 1. OCT imaging module

[0072] See also Figure 1a The OCT imaging module 110 includes an OCT light source 1101 , a fiber coupler 1103 , a reference arm module, a detector 1141 , and a computer 1143 .

[0073] The computer 1143 in this embodiment is not a PC in the traditional sense, but a circuit control and processing system capable of performing a combination of functions such as calculation, control, storage, and display.

[0074] The reference arm module schematically includes a reference arm optical path lens 1121 and a reference arm reflector 1123 .

[0075] The optical path scanning device 1109 adopts a two-dimensional scanning mechanism, and is composed of an X-direction scanning device 11091 and a Y-direction scanning device 11093 .

[0076] The optical path of the OCT imaging module 110 includes an OCT light source 1101, whose output light provides light to the OCT sample arm module 130 and the reference arm module through the fiber coupler 1103. The reference arm module has a known length and reflects light back to the fiber coupler 1103 through the reference arm reflector 1123. The OCT sample arm module 130 provides light to the subject's eye E, and the light scattered back from the sample passes through the OCT sample arm module 130, the polarization controller 1105, and the light reflected back from the reference arm interferes in the fiber coupler 1103. The interference light is detected by the detector 1141, and then processed by the computer 1143, and finally the OCT image of the sample under test is displayed. The sample is scanned by the optical path scanning device 1109 to achieve OCT tomographic imaging.

[0077] The OCT light source 1101 outputs light of a wavelength approximately in the near infrared region.

[0078] 2. OCT Sample Arm Module

[0079] See also Figure 1a The OCT sample arm module 130 includes a fiber collimator 1107, a light output spectroscope 1609, an aperture prism 1501, an optical path scanning device 1109, a field lens 1301, a pre-beam splitter 1303 and an eyepiece objective lens 1305.

[0080] The optical path scanning device 1109 can be a one-dimensional optical path switching scanning device, or a two-dimensional or even three-dimensional optical path scanning device. The optical path scanning device 1109 realizes one-dimensional to multi-dimensional scanning of the sample to be tested.

[0081] The fiber collimator 1107 is connected to the sample arm optical fiber and driven by a motor to move along its optical axis, thereby changing the optical path of the sample arm. Similarly, the matching of the optical paths of the sample arm and the reference arm can also be achieved by changing the optical path of the reference arm.

[0082] When performing OCT imaging, the light emitted by the OCT light source 1101 passes through the optical fiber collimator 1107, passes through the light output beam splitter 1609, and then passes through the light hole 15011 of the aperture prism 1501, and is reflected by the optical path scanning device 1109. At this time, the optical path scanning device 1109 is controlled by the computer 1143. After being reflected by the optical path scanning device 1109, the light beam passes through the field lens 1301, is reflected to the eye lens 1305 through the pre-beam splitter 1303, and finally passes through the human eye E to be tested and converges to the fundus Er. The detection beam of the posterior segment OCT imaging optical path system meets the requirement that the center line of the scanning beam converges near the pupil of the human eye, and the OCT beam is focused on the fundus Er of the human eye at any time. The light returning from the fundus Er returns along the original path, still passes through the light hole 15011 of the aperture prism 1501, and converges to the optical fiber head at the sample end of the optical fiber coupler 1103 through the optical fiber collimator 1107. The return light interferes with the light reflected from the reference arm in the optical fiber coupler 1103, thereby obtaining a coherent signal of the fundus Er of the eye to be measured.

[0083] For different human eyes (with different refractive powers), the OCT beam can be converged on the human eye fundus Er by translating the eyepiece objective lens 1305 along the main optical axis L1. That is, the beam is focused on the retina, which can effectively improve the signal-to-noise ratio and lateral resolution of the OCT image during retinal measurement.

[0084] The front beam splitter 1303 can reflect the signal light emitted by the OCT light source 1101 , reflect the light of the imaging light source 1601 , and transmit the fixation light emitted by the fixation light source 1701 in the fixation optical module 170 .

[0085] When measuring the fundus, scanning is performed through the X / Y direction scanning devices 11091 and 11093; the optical path matching for the fundus of different human eyes is achieved through the fiber optic collimator 1107 combined with the overall translation of the sample arm fiber optic head (not shown); the eyepiece objective lens 1305 is translated along the main optical axis L1 to adjust the refraction for different human eyes; finally, the OCT image of the posterior segment of the eye is collected, thereby obtaining important parameters of the human eye structure such as retinal thickness.

[0086] 3. Fundus confocal scanning imaging module

[0087] See also Figure 1b The fundus confocal scanning imaging module 150 may also include fundus confocal scanning infrared preview imaging and / or fundus confocal scanning visible light color imaging. The imaging light source 1601 generates infrared light and / or visible light for confocal scanning imaging and inputs the OCT sample arm module 130. Preferably, the visible light output by the imaging light source 1601 may be white light or other colors of visible light, such as red light, green light, blue light, etc. More preferably, the visible light color imaging may be color imaging obtained using the above-mentioned various lights.

[0088] The infrared light source for fundus confocal scanning infrared preview imaging may utilize the OCT light source 1101 of the OCT imaging module 110. At this time, the imaging light source 1601 may only output visible light, and further, may only output white light.

[0089] Furthermore, the infrared light source for fundus confocal scanning infrared preview imaging can also utilize the infrared light output by the imaging light source 1601. In this case, the imaging light source 1601 can output multi-color light, including white light and infrared light, or only output infrared light. It is easy to understand that in this case, the wavelength band of the infrared light output by the imaging light source 1601 can be distinguished from the light output by the OCT light source 1101 of the OCT imaging module 110, so that the OCT light source 1101 of the OCT imaging module 110 and the imaging light source 1601 can be simultaneously utilized for fundus confocal scanning infrared preview imaging.

[0090] It can be understood that by simultaneously performing confocal imaging of the fundus with two different bands of infrared light, more data on the human eye or intraocular substances can be obtained. For example, the imaging light source 1601 and the OCT light source 1101 emit light of different bands. According to the differences in transmittance, absorption rate and reflectivity of intraocular substances for light of different bands, the solubility of different substances can be obtained by comparing indicators such as signal strength.

[0091] The visible light output by the imaging light source 1601 can also be synthesized from RGB three-color lights. For example, white light, red light, green light, blue light, etc. can be synthesized from RGB three-color lights. The specific selection can be determined according to actual conditions.

[0092] At this time, the imaging light source 1601 can use a wavelength division multiplexer to couple light sources of multiple wavelength bands into one output, or can use multiple beam splitters to couple different colors of light into one output.

[0093] When the system can use the light output by the OCT light source 1101 of the OCT imaging module 110 to perform fundus confocal scanning infrared preview imaging, the device cost can be saved.

[0094] The light outputted by the OCT light source 1101 of the OCT imaging module 110 is outputted through the fiber collimator 1107, and the multi-color light outputted by the imaging light source 1601 is outputted through the collimator lens 1607, coupled at the light output spectroscope 1609, and then combined and outputted. Similarly, the coupling here can also be realized by using a wavelength division multiplexer.

[0095] The fundus confocal scanning imaging module 150 can utilize the polychromatic light provided by the above-mentioned various solutions.

[0096] When performing fundus confocal scanning infrared preview imaging, the infrared light output by the OCT light source 1101 of the OCT imaging module 110, or the infrared light output by the imaging light source 1601, is incident on the eye to be tested person E, and the optical path scanning device 1109 is used to implement two-dimensional scanning, and the eyepiece objective lens 1305 is used for adjustment, and the fundus image is synthesized by receiving the return light from the fundus. The fundus confocal scanning infrared preview imaging diagram is used for the preview and imaging functions when the eye to be tested is operated.

[0097] Furthermore, the near-infrared light passes through the light hole 15011 of the aperture prism 1501, is reflected by the optical path scanning device 1109, and realizes two-dimensional scanning. Then, the light passes through the field lens 1301, is reflected to the eyepiece objective lens 1305 by the pre-beam splitter 1303, and finally converges to the fundus Er by the human eye E to be tested. The light returning from the fundus Er returns to the optical path scanning device 1109 along the original path. After the returning light is reflected by the optical path scanning device 1109, the returning light passes through the light hole peripheral area 15012 of the light hole 15011 of the aperture prism 1501, and is refracted by the light hole peripheral area 15012 of the aperture prism 1501. The light beam is deflected, and then refracted by the compensation prism 1503, and then received by the multi-color light detection device 1500 after passing through the converging lens 1505. Thus, the single-point infrared imaging information of the fundus Er of the human eye E to be tested is obtained. By two-dimensional scanning of the optical path scanning device 1109, infrared imaging of the fundus Er can be obtained.

[0098] Similarly, when performing fundus confocal scanning visible light imaging, the white light output by the imaging light source 1601 is incident on the human eye E to be tested, the optical path scanning device 1109 is used to achieve two-dimensional scanning, the eyepiece objective lens 1305 is used for adjustment, and the fundus image is synthesized by receiving the return light from the fundus.

[0099] Further, taking the case where the imaging light source 1601 emits white light as an example: the white light passes through the light hole 15011 of the aperture prism 1501, is reflected by the optical path scanning device 1109, and realizes two-dimensional scanning. Then the light passes through the field lens 1301, is reflected by the pre-beam splitter 1303 to the eyepiece objective lens 1305, and finally converges to the fundus Er through the eye to be tested E. The light returning from the fundus Er returns to the optical path scanning device 1109 along the original path. After the returning light is reflected by the optical path scanning device 1109, the returning light passes through the light hole peripheral area 15012 of the light hole 15011 of the aperture prism 1501, and is refracted by the light hole peripheral area 15012 of the aperture prism 1501. The light beam is deflected, and then refracted by the compensation prism 1503, and then by the converging lens 1505, it is received by the multi-color light detection device 1500. Thus, the single-point color imaging information of the fundus Er of the human eye E to be tested is obtained. The color imaging of the fundus Er can be obtained by two-dimensional scanning of the optical path scanning device 1109. It can be understood that the imaging light source 1601 emits red light, green light, blue light or composite light, which can be inferred from the above description of emitting white light, and will not be repeated here.

[0100] In this embodiment, infrared preview imaging is first used to assist doctors in operating the device. When a good fundus OCT image and fundus infrared preview imaging are obtained, the device can be switched to fundus confocal scanning visible light color imaging. A fundus color image is obtained by using the fast two-dimensional scanning of the optical path scanning device 1109, thereby solving the problem that the eye to be tested cannot be tested for a long time due to the high stimulation of visible light, and also solving the problem of damage to the eye to be tested.

[0101] As described above, the light source, scanning device, part of the optical path, and adjustment device of the fundus confocal scanning imaging module 150 are all shared with the OCT imaging system, thereby greatly reducing the system hardware cost. Due to the shared adjustment device, when the OCT scanning line is clearly projected on the fundus Er to be measured, the fundus confocal scanning imaging module 150 is also in the best adjustment position for clear imaging.

[0102] Since the above-mentioned polychromatic light has a certain wavelength bandwidth, the return light will be dispersed after being refracted by the peripheral area 15012 of the light hole of the aperture prism 1501, thereby dispersing the focusing state of the converging lens 1505, that is, the light beam is dispersed at the polychromatic light detection device 1500. This will reduce the image clarity and signal-to-noise ratio of fundus confocal scanning imaging. Therefore, embodiment 1 introduces a compensation prism 1503 so that the return light does not disperse. It can improve the focusing state of the return light through the converging lens 1505, thereby improving the image clarity and signal-to-noise ratio of fundus confocal scanning imaging.

[0103] The multicolor light detection device 1500, such as Figure 2bAs shown, it is composed of a spectroscopic device 506 and a multi-color detector 1509. The above figure schematically represents an infrared detector 1509IR, a red light detector 1509R, a green light detector 1509G, and a blue light detector 1509B. The multi-color detector 1509 can be composed of one or more structures. The multi-color light received by the multi-color light detection device 1500 is split by the spectroscopic device 506 and then received by the multi-color detector 1509 respectively. At this time, the spectroscopic device 506 can use a demultiplexer.

[0104] In addition, the multi-color signals SR, SG, and SB obtained by the multi-color detector 1509 have different transmittances and absorptivity of each color light through the optical path system and the eye to be measured E, so the final synthesized white light signal SW is synthesized by weighting the RGB three-color light signals in this embodiment, that is, SW = a*SR+b*SG+c*SB.

[0105] Example 2

[0106] Compared with Example 1, the multi-color light detection device 1500 in Example 2 has a different configuration.

[0107] The multicolor light detection device 1500, such as Figure 3 As shown, it is composed of multiple spectroscopes, a multi-path aperture 1507 and a multi-color detector 1509. Figure 3 Schematically represented are an infrared detection light path aperture 1507IR and an infrared detector 1509IR, a red light detection light path aperture 1507R and a red light detector 1509R, a green light detection light path aperture 1507G and a green light detector 1509G, and a blue light detection light path aperture 1507B and a blue light detector 1509B. The multi-path aperture 1507 and the multi-color detector 1509 can be constructed by one group or multiple groups. The multi-color light received by the multi-color light detection device 1500 is split by multiple spectroscopes and respectively converged on the multi-path aperture 1507. The multi-color light passes through the multi-path aperture 1507 and is then received by the multi-color detector 1509.

[0108] like Figure 3 As schematically shown, the plurality of beam splitters are composed of a first beam splitter 1506 , a second beam splitter 1508 , and a third beam splitter 1510 .

[0109] Example 3

[0110] It is also easy to know from the above that if the bandwidth of each color light source in the multi-color light source is narrow, the dispersion effect of the refraction through the peripheral area 15012 of the light hole of the aperture prism 1501 is not obvious, and the compensation prism 1503 can be eliminated. That is, after the return light is refracted through the peripheral area 15012 of the light hole of the aperture prism 1501, it is received by the multi-color light detection device 1500 after passing through the converging lens 1505, as shown in FIG. 4.

[0111] This embodiment also includes a fixation optical module 170 and an iris split-image imaging module 180 .

[0112] 1. Fixation Optical Module 170

[0113] See also Figure 1c The fixation light source 1701 in the fixation optical module 170 is used as a fixation mark (internal fixation mark) for the subject's eye E to fixate. The light from the fixation light source 1701 passes through the fixation optical path lens 1703 and the fixation optical path aperture 1705, transmits through the fixation relay lens 1707 and the pre-beam splitter 1303, and then passes through the eye contact objective lens 1305 and enters the subject's eye E. Finally, the internal fixation mark is projected onto the fundus Er of the subject's eye E.

[0114] The fixation light source 1701 can be a single-point LED, or an LCD screen, an OLED screen, or an LED array screen.

[0115] When performing fundus OCT imaging, different eyes have different degrees of clarity when observing the fixation point, which makes the subject uncomfortable when fixating, and is not convenient for the fixation and fixation of the eye being tested. Since the fundus OCT light can be focused on the fundus retina Er after being adjusted by the eyepiece objective lens 1305, that is, the OCT scanning line can be clearly projected on the fundus Er to be tested. By allowing the posterior segment OCT optical path and the fixation optical path to share the eyepiece objective lens 1305 adjustment, it is possible to achieve clear OCT imaging of the fundus while allowing different eyes to see the fixation mark clearly.

[0116] 2. Iris Split Image Imaging Module 180

[0117] Combination Figure 1d , Figure 2a and Figure 5 As shown, the iris split-image imaging module 180 is installed on the left and right sides of the eyepiece objective lens 1305. It is composed of an iris illumination light source 1811 (left iris illumination light source 1811L, right iris illumination light source 1811R), a left iris imaging lens 1803L, a right iris imaging lens 1803R, a left iris camera device 1801L, a right iris camera device 1801R, etc.

[0118] The light emitted by the iris illumination light source 1811 (infrared light) irradiates the anterior chamber of the eye to be tested E, and the light is reflected by the anterior chamber tissue. The reflected light passes through the left and right iris imaging lenses 1803L / 1803R, and is finally photographed by the left and right iris camera devices 1801L / 1801R.

[0119] The iris split-image imaging module 180 is preferably distributed on the left and right sides of the eyepiece lens 1305. If it is distributed in the upper and lower directions of the probe 10, it is easily blocked by the eyelids and the iris split image is not utilized. The iris illumination light source 1811 can be composed of one or more light sources, and its distribution can also be as follows Figure 5 Relative to the eyepiece objective lens 1305 , the iris illumination light source 1811 may be arranged left and right, or up and down, or in an array, etc. If a single iris illumination light source 1811 is used, the preferred solution is to arrange it below the eyepiece objective lens 1305 .

[0120] Since the two iris split-image optical paths are symmetrically distributed on the left and right sides, the left\right iris split-image optical paths L18L / L18R intersect with the main optical axis L1 of the system optical path. Similar to the principle that binoculars can measure distance, the two iris split-image optical paths can determine the working position of the eye to be tested. Or the two iris split-image optical paths can obtain the upper and lower anterior chamber images of the eye to be tested E through imaging, and the working distance can be determined by splicing the upper and lower anterior chamber images of the eye to be tested. When the images of the upper and lower anterior chamber images can just form a complete iris image or pupil image, it can be determined that the eye to be tested is in the required working position.

[0121] When the eye E to be tested deviates from the working position, the pupil or iris image will deviate to one side in the upper and lower anterior chamber images, so that the pupil or iris is not symmetrically distributed along the upper and lower anterior chamber images.

[0122] When the measuring eye E deviates from the working position to the left or right, the pupil or iris image in the upper and lower parts of the anterior chamber image will deviate from the center of the image in the same direction.

[0123] When the measuring eye E deviates from the working position forward or backward, the pupil or iris image in the upper and lower anterior chamber images will deviate to opposite directions, making it impossible to complete the splicing of the pupil or iris image.

[0124] From the above determination method, the two iris split-image optical paths can be used to assist the probe module in performing three-dimensional adjustments up and down, left and right, and front and back, ultimately placing the eye E to be tested in the working position required for fundus imaging.

[0125] Example 4

[0126] like Figure 6 , Figure 7b As shown, compared with Example 2, in Example 4, the aperture prism 1501 and the compensation prism 1503 are replaced with an aperture reflecting mirror 2501.

[0127] Therefore, for the OCT sample arm module 130 , when performing OCT imaging, the light emitted from the fiber collimator 1107 passes through the aperture reflector light hole 25011 of the aperture reflector 2501 and is reflected by the optical path scanning device 1109 .

[0128] For the fundus confocal scanning imaging module 150, the OCT light source 1101 of the OCT imaging module 110 is emitted through the fiber collimator 1107; and the imaging light source 1601 is emitted through the collimator lens 1607, and the two light beams are emitted after being combined by the light-emitting beam splitter 1609. The light passes through the aperture reflector light hole 25011 of the aperture reflector 2501, is reflected by the optical path scanning device 1109, and realizes two-dimensional scanning. Then the light passes through the field lens 1301, is reflected by the pre-beam splitter 1303 to the eye lens 1305, and finally passes through the eye to be tested E and converges to the fundus Er. The light returned through the fundus Er returns to the optical path scanning device 1109 along the original path. After being reflected by the optical path scanning device 1109, the returned light is reflected by the peripheral area 25012 of the aperture reflector light hole of the aperture reflector 2501, and then is received by the multi-color light detection device 1500 after passing through the converging lens 1505. Due to the use of the aperture reflector 2501, the returned light reflected by it will not be dispersed.

[0129] The embodiments of the present invention have the following advantages:

[0130] The system of the embodiment of the present invention adopts the traditional ophthalmic OCT imaging technology and utilizes the scanning mechanism and light source of the OCT system to realize fundus confocal scanning imaging, thereby greatly saving the system cost. It can not only provide infrared preview of the fundus, assist the doctor in adjusting the bending and aligning the optical path, but also provide color imaging of the fundus, thus facilitating the doctor's clinical detection and disease diagnosis.

[0131] The embodiment of the present invention combines the fixation optical path and the split-image iris alignment optical path to form an ophthalmic OCT detection device that is convenient for doctors to use.

[0132] The embodiment of the present invention combines wavelength division multiplexing, and can obtain fundus OCT images, fundus infrared imaging and / or visible light color imaging without adding a scanning mechanism.

[0133] The ophthalmic imaging system designed in the embodiment of the present invention can automatically adjust the working distance according to the principle of iris split-image imaging, and align the main optical axis of the probe optical path with the pupil center of the eye to be tested; it can assist in fundus refractive adjustment through the quality of posterior segment OCT imaging; or assist in fundus refractive adjustment through information such as image clarity and sharpness of fundus infrared confocal scanning imaging; a common imaging optical path refractive adjustment mirror is used to achieve synchronous refractive adjustment of the fixation optical path, the fundus OCT imaging optical path, and the fundus confocal scanning imaging optical path; and combined with technologies such as automatic recognition of posterior segment OCT images, fully automated detection of the system can be achieved.

[0134] The system solution provided in the embodiment of the present invention can provide a low-cost solution for OCT detection for the person to be tested, which is not only conducive to the popularization of OCT equipment, but also allows more patients to enjoy the non-destructive fundus detection technology, and can provide doctors with an intuitive graphical detection method for diagnosis.

[0135] It should be noted that the apertured spectrometer (apertured prism 1501 or apertured reflector 2501) can play a role in splitting light, and the apertured spectrometer can allow all the light output by the OCT light source 1101 or the imaging light source 1601 to pass through the aperture (light-through hole 15011 or apertured reflector light-through hole 25011), and the light returned from the fundus is then split by the apertured spectrometer. It is easy to understand that if an ordinary or non-apertured spectrometer is used as a substitute, the light is split according to different wavelength bands or according to partial transmission and partial reflection, which will reduce the utilization of the light source, that is, the same effect as the apertured spectrometer cannot be achieved.

[0136] The above contents are further detailed descriptions of the present invention in combination with specific preferred embodiments, and it cannot be determined that the specific implementation of the present invention is limited to these descriptions. For those skilled in the art of the present invention, several equivalent substitutions or obvious variations can be made without departing from the concept of the present invention, and the performance or use is the same, which should be regarded as belonging to the protection scope of the present invention.

Claims

1. An ophthalmic optical imaging system, characterized in that: The device comprises an OCT light source, an imaging light source, a reference arm module, an OCT sample arm module, a fiber coupler, an OCT signal acquisition module and a fundus confocal scanning imaging module, wherein the fundus confocal scanning imaging module comprises an aperture spectrometer and a multicolor light detection device, and the aperture spectrometer has a light-through hole; after the illumination light emitted by the OCT light source is split by the fiber coupler, a part of the illumination light is transmitted to the reference arm module and then to the fiber coupler as a reference light, and the other part is input to the OCT sample arm module; the imaging light source generates infrared light and / or light for confocal scanning imaging. Or visible light is input into the OCT sample arm module; the light input into the OCT sample arm module passes through the light-through hole of the aperture spectrometer to illuminate the fundus, and the signal light returned from the fundus is split by the aperture spectrometer, a part of the signal light is returned to the fiber coupler through the light-through hole, and is combined with the reference light returned by the reference arm module and then transmitted to the OCT signal acquisition module to generate an OCT image, and the other part of the signal light is guided by the aperture spectrometer to the multi-color light detection device to realize confocal scanning infrared preview imaging and / or confocal scanning visible light color imaging of the fundus.

2. The ophthalmic optical imaging system according to claim 1, wherein: The light generated by the imaging light source passes through a collimating lens and is coupled with the light input from the OCT light source to the OCT sample arm module through a light output spectroscope to be combined into one path for output; or the light generated by the imaging light source and the light output from the OCT light source are coupled through a wavelength division multiplexer to be combined into one path and then output through a fiber optic collimator.

3. The ophthalmic optical imaging system according to claim 1, wherein: The multicolor light detection device comprises a spectroscopic device and a multicolor detector. The multicolor light received by the multicolor light detection device is split by the spectroscopic device and then received by the multicolor detector respectively. The spectroscopic device comprises a wavelength division multiplexer.

4. The ophthalmic optical imaging system according to claim 1, wherein: The polychromatic light detection device comprises a plurality of spectroscopes, a multi-path aperture and a polychromatic detector. The polychromatic light received by the polychromatic light detection device is split by the plurality of spectroscopes and respectively converged on the multi-path aperture. Each color light passes through the multi-path aperture and is then respectively received by the polychromatic detector.

5. The ophthalmic optical imaging system according to any one of claims 1 to 4, characterized in that: The open-hole spectroscopic device is an open-hole prism with a light hole. The light input into the OCT sample arm module passes through the light hole of the open-hole prism and then illuminates the fundus. A portion of the signal light returning from the fundus returns to the fiber coupler through the light hole of the open-hole prism, while the other portion is refracted through the peripheral area of ​​the light hole of the open-hole prism and then transmitted to the multi-color light detection device.

6. The ophthalmic optical imaging system according to claim 5, characterized in that: A compensation prism is arranged between the aperture prism and the polychromatic light detection device. The signal light refracted by the aperture prism is further refracted by the compensation prism and then received by the polychromatic light detection device.

7. The ophthalmic optical imaging system according to any one of claims 1 to 4, characterized in that: The apertured spectroscopic device is an apertured reflector with a light hole. The light input into the OCT sample arm module passes through the light hole of the apertured reflector and then illuminates the fundus. A portion of the signal light returning from the fundus returns to the fiber coupler through the light hole of the apertured reflector, while the other portion is reflected by the peripheral area of ​​the light hole of the apertured reflector and then transmitted to the multi-color light detection device.

8. The ophthalmic optical imaging system according to any one of claims 1 to 4, characterized in that: The OCT sample arm module includes an iris split-image imaging module, which includes an iris illumination light source, an iris imaging lens and an iris camera device, wherein the light emitted by the iris illumination light source is irradiated to the anterior chamber of the eye to be tested, and is reflected by the anterior chamber tissue of the eye to be tested. The reflected light passes through the iris imaging lens and is captured by the iris camera device.

9. The ophthalmic optical imaging system according to claim 8, wherein: The OCT sample arm module includes an optical path scanning device, a field lens, a front beam splitter and an eyepiece objective lens. The irradiated light passing through the light hole of the open-aperture beam splitter device is reflected by the optical path scanning device, passes through the field lens, is reflected by the front beam splitter to the eyepiece objective lens, and converges to the fundus through the eye to be tested; the iris split-image imaging modules are distributed in pairs on the left and right sides of the eyepiece objective lens.

10. The ophthalmic optical imaging system according to claim 9, wherein: The OCT sample arm module also includes a fixation optical module, which includes a fixation light source for providing a fixation mark for the subject's eye to fixate; the front beam splitter transmits the fixation light from the fixation light source.

Images