CN215687754U - SD-OCT whole-eye imaging system - Google Patents
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- CN215687754U CN215687754U CN202121905127.XU CN202121905127U CN215687754U CN 215687754 U CN215687754 U CN 215687754U CN 202121905127 U CN202121905127 U CN 202121905127U CN 215687754 U CN215687754 U CN 215687754U
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Abstract
The utility model relates to the technical field of eyeball imaging, in particular to an SD-OCT whole-eye imaging system, which comprises a broadband light source, an optical fiber coupler, a reference arm, a sample arm, a spectrometer and a controller, wherein the broadband light source is connected with the reference arm; the reference arm comprises a collimator and a mirror; the sample arm comprises a two-dimensional galvanometer scanning unit and a zoom imaging component; the zoom imaging component comprises an electric tuning lens, a light ray delay line and a confocal lens group; the two-dimensional galvanometer scanning unit is positioned between the optical delay line and the confocal lens group; the light entering the sample arm sequentially passes through the electric tuning lens, the light delay line, the two-dimensional galvanometer scanning unit and the confocal lens group and finally is emitted into human eyes; the SD-OCT whole-eye imaging system can realize whole-eye imaging in a short time.
Description
Technical Field
The utility model relates to the technical field of eyeball imaging, in particular to an SD-OCT whole-eye imaging system.
Background
The Optical Coherence Tomography (OCT) is a novel optical imaging technology which is rapidly developed in recent years and applied to ophthalmic clinical diagnosis, can realize high-resolution non-invasive nondestructive detection on biological living tissues, and has wide application prospect. The basic working principle of OCT is based on Michelson interferometer, biological tissue is imaged by using near infrared ray, light beam is divided into two parts after light source enters an optical fiber coupler through optical fiber, one part enters eyes as a sample arm, the other part enters a reflection system as a reference arm, the two parts of light enter the optical fiber coupler again after being reflected, and when the optical paths of the two beams of light are consistent, the superposed light can generate interference. By using the interference principle, biological tissue signals with different depths can be obtained by changing the optical path of the reference arm, and the signals are analyzed by a computer to obtain a tomographic image of the biological tissue.
Currently, OCT is mainly classified into time-domain OCT (TD-OCT) and frequency-domain OCT (FD-OCT), wherein the frequency-domain OCT is further classified into spectral-domain OCT (SD-OCT) and swept-source OCT (SS-OCT). The TD-OCT realizes depth imaging by utilizing the movement of the reference arm by carrying out superposition interference on the optical signal returned from the biological tissue at the same time point and the optical signal returned by the reference arm. The FD-OCT system is structurally characterized in that the position of a reference arm is unchanged, and the interference of superposed signals of the reference arm and a sample arm is realized by changing the frequency of light waves of a light source. SD-OCT and SS-OCT are derived from the inverse fourier transform of the backscatter spectrum, so frequency domain OCT techniques improve the sensitivity of the system and the scan rate of the system over time domain OCT without the need for longitudinal scanning, while also improving the resolution of the acquired image.
However, the imaging depth of the current market products is not enough whether SD-OCT or SS-OCT is adopted, and the imaging on the whole eye depth (30mm) cannot be realized. For example, patent documents CN109965839A only provide an OCT imaging apparatus focusing on the anterior segment of the eye, and patent documents CN209285465U, CN107582020B, and CN209315847U provide apparatuses that can perform multi-segment imaging by one measurement and simultaneously perform imaging on the anterior segment of the eye and the posterior segment of the eye, but the design and combination of optical lens combinations are complex, the tissue precision is difficult to achieve, and real-time imaging cannot be guaranteed.
Therefore, the existing commercial OCT system based on the imaging depth of the time-domain OCT, the spectral-domain OCT and the swept-source OCT system does not have a mature product for whole-eye imaging, and some whole-eye diseases can affect the structure and parameters of the whole human eye. The imaging of the anterior segment of the eye or the imaging of the retina of the eye fundus leads to the simplification and one-sidedness of the imaging area, which is not beneficial to the systematic examination in the ophthalmology during the treatment.
Therefore, how to realize whole eyeball imaging in a short time becomes an urgent problem to be solved.
SUMMERY OF THE UTILITY MODEL
The present invention is directed to an SD-OCT whole-eye imaging system, which solves one or more of the problems of the prior art and provides at least one of the advantages.
In order to achieve the purpose, the utility model provides the following technical scheme:
an SD-OCT whole-eye imaging system, comprising: the device comprises a broadband light source, an optical fiber coupler, a reference arm, a sample arm, a spectrometer and a controller;
the broadband light source provides incident light to the sample arm and the reference arm through the optical fiber coupler respectively, the light passing through the sample arm is incident to the eye fundus of the human eye and is reflected, the reflected light is interfered with the light reflected from the reference arm in the optical fiber coupler after passing through the sample arm to generate interference light, the interference light is detected by the spectrometer, and the OCT tomography of the human eye is obtained after the interference light is processed by the controller;
the reference arm comprises a collimator and a mirror; the sample arm comprises a two-dimensional galvanometer scanning unit and a zoom imaging component; the zoom imaging component comprises an electric tuning lens, a light ray delay line and a confocal lens group; the two-dimensional galvanometer scanning unit is positioned between the optical delay line and the confocal lens group; the light entering the sample arm sequentially passes through the electric tuning lens, the light delay line, the two-dimensional galvanometer scanning unit and the confocal lens group and finally enters human eyes.
According to the scheme, the zoom imaging component is introduced into the light path of the sample arm, the large-depth optical path adjustment of the optical delay line is combined with the zooming of the electric tuning lens, the multipoint focusing of light is achieved, the precision is controllable, the anterior segment and the posterior segment of the eye can be imaged respectively, and the whole-eye imaging is achieved.
Further, the electric tuning lens comprises a liquid lens and a bias lens arranged in front of the liquid lens, and the zooming range of the electric tuning lens can be further expanded.
Further, an LC low-pass filter is arranged in the control circuit of the electric tuning lens. The zoom response time during small-step zooming can be reduced by arranging the LC low-pass filter, and the imaging frequency is further improved.
Furthermore, the two-dimensional galvanometer scanning unit comprises two galvanometers, and the rotating axes of the two galvanometers are parallel, so that the transverse scanning width can be improved. Preferably, the distance between the two galvanometers of the two-dimensional galvanometer scanning unit is less than 40mm, so that a larger imaging visual field is ensured.
Further, the spectrometer comprises a collimating lens, a diffraction grating, an achromatic imaging lens and a line camera, wherein the line camera is a 4096pixel camera. Therefore, the spectrometer has good signal attenuation performance and higher camera sensitivity, image acquisition is carried out, the imaging depth is obviously improved, and the requirement of whole-eye imaging is further met.
Furthermore, the center wavelength of the broadband light source is 840nm, the bandwidth is 49nm, the light entrance pupil power is less than 2mW, and the eyes cannot be damaged.
Further, the highest zoom frequency of the electrically tuned lens is 50Hz, and the focusing range is: 100-. The high focusing frequency of the electric tuning lens ensures that the final imaging rate is improved, and the limitation of the focusing range ensures the focusing control precision under the high focusing frequency.
Furthermore, the optical delay line is a centering crank-slider optical delay line and comprises a crank-slider mechanism, the crank-slider mechanism comprises a crank and a slider, the reflector is arranged on the slider, one end of the crank is connected with the slider, and the other end of the crank is connected with a synchronous motor; the reflector is a pyramid prism to ensure the stability of the movement of the optical delay line and the requirement of precision control.
Furthermore, the confocal lens group consists of two cemented lenses, so that chromatic aberration is small, and the imaging effect is better.
The utility model has the beneficial effects that: the utility model provides a whole-eye imaging system of SD-OCT, improve the traditional SD-OCT system, introduce and zoom the electric tuning lens and focus the lens battery in the sample arm, form and zoom the imaging optical path; an optical delay line with a large depth range is added in a zooming imaging light path, multi-point focusing of a sample arm is realized by adjusting zooming of an electric tuning lens and optical delay line optical path adjustment, anterior ocular segment and posterior ocular segment can be imaged respectively, and full-eye imaging is realized. The utility model realizes the imaging of the whole eyeball with lower cost and relatively simple optical system structure.
Drawings
The above and other features of the present invention will become more apparent by describing in detail embodiments thereof with reference to the attached drawings in which like reference numerals designate the same or similar elements, it being apparent that the drawings in the following description are merely exemplary of the present invention and other drawings can be obtained by those skilled in the art without inventive effort, wherein:
FIG. 1 is a schematic structural diagram of an SD-OCT whole-eye imaging system of the present invention;
FIG. 2 is a schematic diagram of the optical path of the sample arm focused at the anterior and fundus of the eye;
fig. 3 is a schematic structural diagram of an electric tuning lens in embodiment 1 of the present invention;
FIG. 4 is a schematic diagram of the spectrometer of embodiment 1 of the present invention;
FIG. 5 is a schematic main plan view of an imaging optical system of an anterior segment and a posterior segment of an eye of an SD-OCT whole-eye imaging system according to embodiment 1 of the utility model;
FIG. 6 is a schematic structural diagram of an SD-OCT whole-eye imaging system according to embodiment 2 of the utility model;
FIG. 7 is a schematic structural diagram of an SD-OCT whole-eye imaging system according to embodiment 3 of the utility model;
fig. 8 is a schematic structural diagram of an SD-OCT whole-eye imaging system according to embodiment 4 of the present invention.
Detailed Description
The conception, the specific structure and the technical effects of the present invention will be clearly and completely described in conjunction with the embodiments and the accompanying drawings to fully understand the objects, the schemes and the effects of the present invention. It should be noted that the embodiments and features of the embodiments in the present application may be combined with each other without conflict.
Referring to fig. 1, the present invention provides an SD-OCT whole-eye imaging system, including a broadband light source 1, a fiber coupler 2, a reference arm 3, a sample arm 4, a spectrometer 5, and a controller 6; light emitted by the broadband light source 1 is provided with incident light for the sample arm 4 and the reference arm 3 through the optical fiber coupler 2 respectively, wherein the light passing through the sample arm 4 is incident to the eye fundus of a human eye and is reflected, the reflected light is interfered with the light reflected from the reference arm 3 after passing through the sample arm 4 in the optical fiber coupler 2 to generate interference light, the interference light is detected by the spectrometer 5, and the OCT tomography of the human eye is obtained after the interference light is processed by the controller 6; wherein the reference arm 3 comprises a first collimator 301 and a mirror 302; light entering the reference arm 3 passes through a first collimator 301 and is reflected back by a mirror 302. The sample arm 4 comprises a two-dimensional galvanometer scanning unit 41 and a zoom imaging component 42; the zoom imaging assembly comprises an electric tuning lens 421, a light delay line 422 and a confocal lens group 423; the two-dimensional galvanometer scanning unit 41 is positioned between the optical delay line 422 and the confocal lens group 423; the light entering the sample arm 4 passes through the electric tuning lens 421, the light delay line 422, the two-dimensional galvanometer scanning unit 41, and the confocal lens group 423 in sequence, and finally enters the human eye.
According to the scheme provided by the application, the zoom imaging component is introduced into the light path of the sample arm, the large-depth optical path adjustment of the optical delay line is utilized, the multi-point focusing of light is realized, the precision is controllable, the anterior segment and the posterior segment of the eye can be imaged respectively, and the full-eye imaging is realized.
The whole-eye imaging process comprises the following steps: adjusting the control current of the electric tuning lens to focus the incident light entering the sample arm at a first section of zero optical path (cornea) to complete first section imaging; then, adjusting the optical delay line to reduce the optical path of the incident light entering the sample arm so as to expand the imaging depth to the depth direction of the eyeground, and adjusting the control current of the zooming electric tuning lens to zoom the sample light entering the reference arm to a second section of zero optical path to complete second section imaging; cycling sequentially until the last segment (retina) imaging is completed.
Referring to fig. 2, fig. 2 is a schematic diagram of the optical path of the sample arm incident light focused at the anterior and bottom of the eye. The zooming of the electrically tuned lens focuses the light at two positions, namely focus I and focus II, of the eye. And imaging the image at a zero optical path point through optical path matching adjustment, focusing the zooming electric tuning lens to an optimal position, and finally collecting and storing the high-resolution image at the optimal position by a system.
Example 1
In this embodiment, the center wavelength of the broadband light source 1 is 840nm, and the bandwidth is 49 nm; the fiber coupler 2 is an 50/50 coupler; the electro-tunable lens 421 consists of a liquid lens 4211 and a bias lens 4212 mounted in front of it, the bias lens 4212 is a plano-concave lens with a focal length of-150 mm, and the electro-tunable lens structure is shown in fig. 3. And an LC low-pass filter is arranged in a control circuit of the electric tuning lens, so that the zooming response time in small-step zooming can be reduced by arranging the LC low-pass filter, and the imaging frequency is further improved. The highest zoom frequency of the electrically tunable lens 421 is 50Hz, and the focusing range is: 100-.
The two-dimensional galvanometer scanning unit 41 comprises two galvanometers (411, 412), and the rotating axes of the two galvanometers (411, 412) are parallel, so that the transverse scanning width can be enlarged; the distance between the two galvanometers (411, 412) is < 40mm, so that the imaging field of view is maximum. The distance between the vibrating mirrors is the distance between the rotating shafts of the vibrating mirrors when the two vibrating mirrors are parallel.
The spectrometer 5 comprises a collimating lens 51, a diffraction grating 52, an achromatic imaging lens 53 and a line camera 54, and the structure is shown in fig. 4; the collimator lens 51 collimates the received interference light, the diffraction grating 52 diffracts the collimated interference light to form diffracted light, the achromatic imaging lens 53 removes chromatic aberration of the diffracted light, and the line camera 54 images the diffracted light. Wherein the line camera 54 is a 4096pixel camera; can guarantee to gather sensitivity, and have higher imaging depth, imaging depth can reach 9mm in the air to reduce the number of times of zooming, through a few times zoom imaging alright in order to accomplish the image acquisition of full eye, raise the efficiency.
The optical delay line 422 is a centering crank-slider optical delay line and comprises a crank-slider mechanism, the crank-slider mechanism comprises a crank and a slider, the reflector is arranged on the slider, one end of the crank is connected with the slider, and the other end of the crank is connected with a synchronous motor; the reflector is a pyramid prism to ensure the stability of the motion of the optical delay line and the requirement of precision control. Since the crank-slider mechanism is a structure that is common in large machines, it is not illustrated here. The synchronous motor selects a stepping motor, the highest rotating speed is 2000-3000rpm, the minimum stepping angle precision is 0.01 degree/pulse, and the optical path adjusting precision is ensured. The crank length is 10-15mm, so that the optical path adjusting range is about 4-5 times of the crank length, and the requirement of full-eye imaging optical path change is met.
The confocal lens group 423 is composed of two cemented lenses (4231, 4232) with focal lengths f1＝60mm，f2＝50mm。
In the imaging process, when the posterior segment of the eye is imaged, the galvanometer 411 is kept in a silent state (equivalent to a plane mirror), the galvanometer 412 scans, the imaging range is shown in (b) in fig. 5, and the confocal lens group and the crystalline structure form two 4F systems, so that the imaging resolution is ensured; when the anterior ocular segment is scanned and imaged, the galvanometer 411 scans, the galvanometer 412 keeps a silent state (equivalent to a plane mirror), the object plane position of the 4F system moves forward, the focusing is performed through the electric tuning lens, the optical main plane corresponding to the galvanometer 411 moves forward, and the imaging range is shown as (a) in fig. 5.
The optical path switches from cornea to retina are divided into several times, and 1 scan is performed at the depth every 1 time of optical path change. The optical path is controlled by a motor of an optical delay line fixed on the sample arm to perform displacement switching, and simultaneously, the zooming electric tuning lens performs zooming once, so that imaging in the depth range of the whole eye can be realized. According to the full-eye imaging device, the imaging frequency of a full-eye image can reach 33Hz at most, and the imaging speed reaches over 30Hz, so that the system can achieve a real-time imaging effect, splicing errors caused by eye pulsation and eye movement factors are avoided, and real-time imaging is really achieved.
Example 2
This embodiment differs from embodiment 1 in that a second collimator 43 is added to the sample arm light path; further ensuring the collimation of incident light beams and improving the imaging quality; the structure of the imaging system is shown in fig. 6.
Example 3
The difference between the embodiment and the embodiment 2 is that the polarizers 7 are added in the light paths of the sample arm and the reference arm and are positioned in front of the collimator, so that the beam quality is further ensured, the chromatic dispersion and the chromatic aberration are reduced, and the imaging quality is improved; the structure of the imaging system is shown in fig. 7.
Example 4
The difference between this embodiment and embodiment 3 is that a dispersion compensation component 44 is added to the optical path of the sample arm, and an existing dispersion compensation component with a corresponding model on the market is selected, and the structure of the imaging system is shown in fig. 8.
In the embodiment provided by the utility model, the imaging range is expanded to the full-eye depth through the dynamic movement of the optical delay line of the sample arm, so that the full-eye imaging of the SD-OCT system is realized. The light path structure is simpler, the cost is lower, the equipment precision is changeed the realization.
While the present invention has been described in considerable detail and with particular reference to a few illustrative embodiments thereof, it is not intended to be limited to any such details or embodiments or any particular embodiments, but it is to be construed as effectively covering the intended scope of the utility model by providing a broad, potential interpretation of such claims in view of the prior art with reference to the appended claims. Further, the foregoing describes the utility model in terms of embodiments foreseen by the applicant for which an enabling description was available, notwithstanding that insubstantial modifications of the utility model, not presently foreseen, may nonetheless represent equivalent modifications thereto.
Claims (10)
1. An SD-OCT whole-eye imaging system, comprising: the device comprises a broadband light source, an optical fiber coupler, a reference arm, a sample arm, a spectrometer and a controller;
the broadband light source provides incident light to the sample arm and the reference arm through the optical fiber coupler respectively, the light passing through the sample arm is incident to the eye fundus of the human eye and is reflected, the reflected light is interfered with the light reflected from the reference arm in the optical fiber coupler after passing through the sample arm to generate interference light, the interference light is detected by the spectrometer, and the OCT tomography of the human eye is obtained after the interference light is processed by the controller;
the reference arm comprises a collimator and a mirror; the sample arm comprises a two-dimensional galvanometer scanning unit and a zoom imaging component; the zoom imaging component comprises an electric tuning lens, a light ray delay line and a confocal lens group; the two-dimensional galvanometer scanning unit is positioned between the light ray delay line and the confocal lens group; the light entering the sample arm sequentially passes through the electric tuning lens, the light delay line, the two-dimensional galvanometer scanning unit and the confocal lens group and finally enters human eyes.
2. An SD-OCT whole-eye imaging system according to claim 1, wherein the electrically tuned lens comprises a liquid lens and an offset lens mounted in front of the liquid lens.
3. An SD-OCT whole-eye imaging system according to claim 1, wherein an LC low-pass filter is provided in the control circuit of the electrically tuned lens.
4. The SD-OCT whole-eye imaging system of claim 1, wherein the two-dimensional galvanometer scanning unit comprises two galvanometers, and the rotation axes of the two galvanometers are parallel.
5. An SD-OCT whole-eye imaging system according to claim 4, wherein the distance between the two galvanometers of the two-dimensional galvanometer scanning unit is < 40 mm.
6. An SD-OCT full-eye imaging system according to claim 1, wherein the spectrometer comprises a collimating lens, a diffraction grating, an achromatic imaging lens and a line camera, the line camera being a 4096pixel camera.
7. An SD-OCT whole-eye imaging system according to claim 1, wherein the broadband light source has a central wavelength of 840nm and a bandwidth of 49 nm.
8. An SD-OCT whole-eye imaging system according to claim 1, wherein the maximum zoom frequency of the electrically tuned lens is 50Hz, and the focusing range is: 100-.
9. The SD-OCT whole-eye imaging system of claim 1, wherein the light delay line is a centering slider-crank optical delay line comprising a slider-crank mechanism, the slider-crank mechanism comprises a crank and a slider, the mirror is arranged on the slider, one end of the crank is connected with the slider, and the other end of the crank is connected with a synchronous motor; the reflector is a pyramid prism.
10. An SD-OCT whole-eye imaging system according to claim 1, wherein the confocal lens group consists of two cemented lenses.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114847867A (en) * | 2022-05-06 | 2022-08-05 | 山东探微医疗技术有限公司 | Human eye focusing and imaging device and method of visible light OCT |
| CN117503047A (en) * | 2023-12-11 | 2024-02-06 | 始终(无锡)医疗科技有限公司 | Large target surface zoom OCT system and application thereof in fundus and anterior ocular segment detection |
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2021
- 2021-08-13 CN CN202121905127.XU patent/CN215687754U/en active Active
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114847867A (en) * | 2022-05-06 | 2022-08-05 | 山东探微医疗技术有限公司 | Human eye focusing and imaging device and method of visible light OCT |
| CN114847867B (en) * | 2022-05-06 | 2024-02-13 | 山东探微医疗技术有限公司 | Visible light OCT human eye focusing and imaging device and method |
| CN117503047A (en) * | 2023-12-11 | 2024-02-06 | 始终(无锡)医疗科技有限公司 | Large target surface zoom OCT system and application thereof in fundus and anterior ocular segment detection |
| CN117503047B (en) * | 2023-12-11 | 2024-05-10 | 始终(无锡)医疗科技有限公司 | Large target surface zoom OCT system and application thereof in fundus and anterior ocular segment detection |
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Denomination of utility model: A SD-OCT whole-eye imaging system Effective date of registration: 20230228 Granted publication date: 20220201 Pledgee: Bank of China Limited by Share Ltd. Foshan branch Pledgor: GUANGDONG WEIREN MEDICAL TECHNOLOGY Co.,Ltd. Registration number: Y2023980033590 |
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