CN111436902A - Fundus camera optical system based on non-coaxial array illumination - Google Patents
Fundus camera optical system based on non-coaxial array illumination Download PDFInfo
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- 238000005286 illumination Methods 0.000 title claims abstract description 90
- 230000003287 optical effect Effects 0.000 title claims abstract description 45
- 238000003384 imaging method Methods 0.000 claims abstract description 64
- 230000004075 alteration Effects 0.000 claims description 9
- 210000002747 omentum Anatomy 0.000 claims description 4
- 230000000694 effects Effects 0.000 abstract description 7
- 230000001629 suppression Effects 0.000 abstract description 3
- 210000004087 cornea Anatomy 0.000 description 8
- 238000010586 diagram Methods 0.000 description 8
- 230000002207 retinal effect Effects 0.000 description 6
- 238000000034 method Methods 0.000 description 5
- 210000001525 retina Anatomy 0.000 description 5
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- 201000010099 disease Diseases 0.000 description 4
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 4
- 208000006550 Mydriasis Diseases 0.000 description 2
- 238000012937 correction Methods 0.000 description 2
- 238000001514 detection method Methods 0.000 description 2
- 210000004220 fundus oculi Anatomy 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012014 optical coherence tomography Methods 0.000 description 2
- 210000001747 pupil Anatomy 0.000 description 2
- 238000002310 reflectometry Methods 0.000 description 2
- 201000001320 Atherosclerosis Diseases 0.000 description 1
- 208000024172 Cardiovascular disease Diseases 0.000 description 1
- 208000002177 Cataract Diseases 0.000 description 1
- 208000010412 Glaucoma Diseases 0.000 description 1
- 206010020772 Hypertension Diseases 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 238000000605 extraction Methods 0.000 description 1
- 230000005764 inhibitory process Effects 0.000 description 1
- 230000002911 mydriatic effect Effects 0.000 description 1
- 208000010125 myocardial infarction Diseases 0.000 description 1
- 230000002265 prevention Effects 0.000 description 1
- 210000001210 retinal vessel Anatomy 0.000 description 1
- 238000004088 simulation Methods 0.000 description 1
- 230000009885 systemic effect Effects 0.000 description 1
- 238000012546 transfer Methods 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/0008—Apparatus for testing the eyes; Instruments for examining the eyes provided with illuminating means
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/14—Arrangements specially adapted for eye photography
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Abstract
The invention provides a fundus camera optical system based on non-coaxial array illumination, which comprises an illumination system and an imaging system, wherein the illumination system comprises a light source, a light source and a light source; the illumination system comprises a plurality of illumination sources; the illumination sources are uniformly distributed around a main optical axis of the imaging system, the main optical axis of each illumination source deflects 15 degrees from the main optical axis of the imaging system, the distance between the central point of a light outlet of each illumination source and the main optical axis of the imaging system is 7.5mm, the working distance of the illumination sources is 10mm, and the diameter of a light inlet of the imaging system is 26 mm. The LED lamp has the advantages that a good uniform illumination effect is realized, stray light is well avoided, and a good stray light suppression effect is realized. The invention is mainly used in the technical field of ophthalmic medical equipment.
Description
Technical Field
The invention relates to the technical field of ophthalmic medical equipment, in particular to an optical system of a fundus camera based on non-coaxial array illumination.
Background
The fundus camera mainly comprises an illumination system, an imaging system and an image sensor, wherein the illumination system illuminates the retina of the fundus, and the imaging system images capillary vessels on the retina to the image sensor. The fundus camera can be used for detecting and judging the influence of ophthalmic diseases and systemic diseases, such as glaucoma, cataract, hypertension, atherosclerosis, myocardial infarction, cardiovascular diseases and the like on the characteristics of width, tortuosity, branch angle and the like of retinal blood vessels. Compared with the examination devices commonly used in clinical medicine, such as ophthalmoscopes (ophthalmoscopes), Slit lamp microscopes (Slit lamp microscopes), Scanning laser ophthalmoscopes (Scanning laser ophthalmoscopes), Optical coherence tomography (Optical coherence tomography) and the like, real-time noninvasive fundus imaging examination of a fundus camera has become one of the most economical and commonly used medical Optical examination means, and has important significance for diagnosis and prevention of ophthalmological diseases and blood vessel related diseases. Among them, how to design an optical system that is simple, small in size, low in cost, and capable of achieving a good stray light suppression effect is a difficulty in designing an optical system of an eye fundus camera.
Disclosure of Invention
It is an object of the present invention to provide a fundus camera optical system based on non-coaxial array illumination to address one or more of the technical problems of the prior art, at least to provide a useful alternative or creation.
The solution of the invention for solving the technical problem is as follows: an optical system of a fundus camera based on non-coaxial array illumination comprises an illumination system, an imaging system; the illumination system comprises a plurality of illumination sources; the illumination sources are uniformly distributed around a main optical axis of the imaging system, the main optical axis of each illumination source deflects 15 degrees from the main optical axis of the imaging system, the distance between the central point of a light outlet of each illumination source and the main optical axis of the imaging system is 7.5mm, the working distance of the illumination sources is 10mm, and the diameter of a light inlet of the imaging system is 26 mm.
Further, the wavelength range of the emitted light of the illumination source is located in the near infrared wavelength range. By emitting the light, the human eyes are not sensitive, the detection is convenient, and the non-mydriatic illumination is realized.
Further, the wavelength of the emitted light of the illumination source is 940 nm.
Further, the imaging system includes: the imaging lens group is used for secondary imaging to correct residual eye aberration and system aberration. The aberration of the human eye is eliminated to the maximum extent by means of two corrections.
Further, the field of view angle of the omentum objective lens group is 30-45 degrees, and the field of view angle of the imaging lens group is 65 degrees.
Further, the retina objective lens group is a bractenophthalmia lens group.
Further, the number of the illumination sources is six.
The invention has the beneficial effects that: the LED lamp has the advantages that a good uniform illumination effect is realized, stray light is well avoided, and a good stray light suppression effect is realized. The system has simple design structure, small volume, good aberration correction effect and high imaging quality. The non-mydriasis shooting of the retina is realized, and the purpose of non-invasive examination is achieved.
Drawings
The above and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:
FIG. 1 is an optical path diagram of the optical system of the present fundus camera;
FIG. 2 is a light path diagram of an illumination source;
FIG. 3 is a schematic diagram of the reflection of light from an illumination source on a cornea;
FIG. 4 is a schematic diagram of an imaging system configuration;
FIG. 5 shows an MTF plot for an imaging system;
FIG. 6 is a dot diagram of an imaging system;
fig. 7 shows a field curvature and distortion diagram of the imaging system.
Detailed Description
It should be noted that the embodiments and features of the embodiments in the present application may be combined with each other without conflict. The present invention will be described in detail below with reference to the embodiments with reference to the attached drawings.
In order to make the technical solutions of the present invention better understood, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be obtained by a person skilled in the art without any inventive step based on the embodiments of the present invention, shall fall within the scope of protection of the present invention.
It should be noted that the terms "first," "second," and the like in the description and claims of the present invention and in the drawings described above are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It should be understood that the data so used is intended to cover a non-exclusive inclusion, such that a process, method, system, article, or apparatus that comprises a list of steps or elements is not necessarily limited to those steps or elements expressly listed, but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus.
The present invention will be described in detail below with reference to the embodiments with reference to the attached drawings.
According to an embodiment of the present invention, fig. 1 provides a fundus camera optical system using a non-coaxial ring array illumination mode, and for convenience of description, the fundus camera optical system is applied to a human eye model, and for this purpose, a cmos photosensitive chip 600 is disposed on an image plane of an imaging system 800, and the cmos photosensitive chip 600 is used as an image sensor.
The system is constructed as shown in fig. 1 and comprises an illumination system 700 and an imaging system 800, wherein the illumination system comprises a plurality of illumination sources 200 (only two are shown in fig. 1), the plurality of illumination sources 200 are uniformly distributed around a main optical axis 810 of the imaging system 800, the illumination sources 200 comprise a dodging mirror group and L ED point light sources, the light-emitting angle of the L ED point light sources is 30 degrees, the working distance of the L ED point light sources is 6.5mm, the working distance is the distance between the L ED point light sources and the dodging mirror group, the working distance of the illumination sources 200 is 10mm, and the working distance is the distance between the central point of a light outlet of the dodging mirror group and a cornea 110 of a human eye model.
Referring to fig. 2, the primary optical axis 230 of each illumination source 200 is deflected β from the primary optical axis 810 of the imaging system 800, the angle β is equal to 15 °, the distance between the central point of the light outlet of each illumination source 200 and the primary optical axis 810 of the imaging system 800 is h, the h is equal to 7.5mm, and the diameter of the light inlet of the imaging system 800 is 26mm, wherein the imaging system 800 comprises a retinal objective lens group 400 and an imaging lens group 500 which are coaxially arranged, the retinal objective lens group 400 is used for the first imaging and corrects partial human eye aberrations, and the imaging lens group 500 is used for the second imaging and corrects residual human eye aberrations and system aberrations.
The illumination system 700 includes six illumination sources 200, and each illumination source 200 is composed of a dodging mirror group and a point light source. Each dodging lens group comprises two plano-convex lenses with positive focal power. Six illumination sources 200 are annularly distributed at the front end of the retinal objective lens assembly 400. In the embodiment of the invention, the optical design software ZEMAX is used for designing the multiple structures of the illumination sources 200, the surface of the cornea 110 of the human eye model is taken as a global coordinate reference surface, the six illumination sources are evenly distributed at 360 degrees under the condition of deflecting 15 degrees and decentering 7.5mm relative to the main optical axis, and the multiple structure parameters of the illumination sources 200 are shown in the table 1. The first illumination source is Config1, the second illumination source is Config1, the third illumination source is Config1, the fourth illumination source is Config1, the fifth illumination source is Config1, and the sixth illumination source is Config 1.
TABLE 1 illumination source spatial distribution data
| Operand | Config1 | Config2 | Config3 | Config4 | Config5 | Config6 |
| CATX | -15 | -15 | -15 | -15 | -15 | -15 |
| CADY | -7.5 | -7.5 | -7.5 | -7.5 | -7.5 | -7.5 |
| CATZ | 0 | 60 | 120 | 180 | 240 | 300 |
In some preferred embodiments, the illumination source 200 emits light in the near infrared band, i.e., the L ED point light source emits light in the near infrared band, which makes the human eye insensitive and facilitates detection, and in some embodiments, the illumination source 200 emits light at 940 nm.
As shown in fig. 3, since the plurality of illumination sources 200 are arranged around the main optical axis 810 of the imaging system 800, an illumination system 700 for annular light extraction is formed. In the illumination system 700, light emitted from the illumination sources 200 is incident on the surface of the cornea 110 at an angle, so that the reflected light 120 (stray light) from the surface of the cornea 110 is reflected at an angle, and the distance between the central point of the light outlet of each illumination source 200 and the main optical axis 810 of the imaging system 800 is set by setting the deflection angle between each illumination source 200 and the main optical axis 810 of the imaging system 800. So that the reflected light 120 from the surface of the cornea 110 does not enter the imaging system 800, thereby achieving the effect of suppressing flare.
In this embodiment, lighttools stray light analysis software is used to model and analyze the bottom of the eye reflected stray light, when the power of the light source is set to be 100W and the divergence angle of the point light source is set to be 30 °, the trace is 1 × 106According to the light, the surface reflectivity of the cornea 110 is 4%, the surface reflectivity of the omentum objective lens group 400 is 2%, and the detected energy on the CMOS photosensitive chip 600 is 0, which indicates that all stray light of the cornea 110 overflows the imaging system 800, so that the design realizes a better stray light inhibition effect.
In the embodiment of the invention, the light tools are adopted to model and analyze the illumination uniformity of the fundus oculi, the power of the light source is set to be 100W, and when the divergence angle of the light source is 30 degrees, the trace 1 × 10 is set6Root ray, the power density of the fundus central region is about 0.084W/mm according to the simulation result2Maximum power density of 0.086W/mm2Radius in 30 ℃ illumination area 85%The power density of the magnetic field is about 0.070W/mm2. According to the definition of uniformity U
ΦcenterTo illuminate the power density of the central zone, phi85％Power density at 85% of the radius of the illuminated area, phimaxThe calculated U is 83.7% for the maximum power density in the illumination area, which illustrates that the scheme of six illumination sources 200 in this embodiment can achieve a better uniform illumination effect on the fundus oculi. With the above configuration, the total length of the illumination system in the embodiment of the present invention can be realized to be not more than 18 mm. The size of the entire fundus camera optical system is reduced.
As shown in fig. 4, parameters of respective optical elements in an optical path composed of a human eye model (gullsland-L e Grand), an imaging system 800 and a CMOS photosensitive chip 600 are provided:
table 3 data for mirror plane of imaging system 800
So that the field angle of the retinal objective lens group 400 is 30 ° to 45 °, the field angle of the imaging lens group 500 is 65 °, the present embodiment uses BAS L ER camera with 5.5 μm × 5.5.5 μm pixel size as the CMOS image sensor chip 600, which requires resolution of 6 μm retina structure, the ultimate resolution of the imaging system 800 can be obtained by the formula N1000/2 α (N is ultimate resolution, α is pixel size), the ultimate resolution of the imaging system 800 can be obtained by the formula ψ 1.22 λ/D (ψ is the ratio of the pixel size D to the optical system focal length f, D is the entrance pupil diameter, λ is the center wavelength), the diffraction limit aperture value can be obtained by 4.8, wherein, in the present embodiment, the entrance diameter of the retinal objective lens group is 26mm, the total length of the imaging system 800 is not more than 75mm by the configuration of the imaging system 800 described above, the parameters of the final imaging system 800 are as shown in table 3:
TABLE 3 parameters of imaging systems
| Wavelength (nm) | 935～945 |
| Imaging range of fundus | ±5.24 |
| Retinal resolution (μm) | 6 |
| Diameter of pupil (mm) | 2 |
| Total length of system (mm) | ≤130 |
| Distortion Rate (%) | <5 |
| MTF value | >0.2@91lp/mm |
FIG. 5 is a graph of MTF of the modulation transfer function 800 of the imaging system 800 according to the embodiment of the present invention, as shown in FIG. 5, when the Nyquist frequency is 911p/mm, the MTF value is greater than 0.2, which satisfies the requirement of using BAS L ER camera in the imaging system, FIG. 6 is a point diagram of the imaging system according to the embodiment of the present invention, FIG. 7 is a field curvature and distortion diagram of the imaging system according to the embodiment of the present invention, as shown in FIG. 6 and FIG. 7, the radius of Airy patch is 8.602 μm, the maximum RMS radius is 4.135 μm, the image quality is close to the diffraction limit, the field curvature of the full field is less than 0.2mm, and the distortion rate is less than 5%.
Through the non-coaxial design of the illumination system 700 and the imaging system 800 and the six annularly arranged illumination sources 200, the interference of stray light on the imaging system is effectively inhibited while a better uniform illumination effect is realized, and by adopting a near infrared L ED light source insensitive to human eyes, the mydriasis treatment in the fundus photographing process is avoided, the total length of the whole illumination system 700 can be not more than 18mm, the total length of the imaging system 800 can be not more than 75mm, and the whole illumination system has the advantages of simple structure, small size, low cost, portability and the like.
Although the present invention has been described in considerable detail and with particular reference to such embodiments, it is not intended to be limited to any such details or embodiments or any particular embodiments, but rather it is to be construed as effectively covering the intended scope of the invention by providing broad potential interpretations of such claims in view of the prior art with reference to the appended claims. Furthermore, the foregoing describes the invention in terms of embodiments foreseen by the inventor for which an enabling description was available, notwithstanding that insubstantial modifications of the invention, not presently foreseen, may nonetheless represent equivalent modifications thereto.
Claims (7)
1. An optical system of a fundus camera based on non-coaxial array illumination is characterized by comprising an illumination system and an imaging system; the illumination system comprises a plurality of illumination sources; the illumination sources are uniformly distributed around a main optical axis of the imaging system, the main optical axis of each illumination source deflects 15 degrees from the main optical axis of the imaging system, the distance between the central point of a light outlet of each illumination source and the main optical axis of the imaging system is 7.5mm, the working distance of the illumination sources is 10mm, and the diameter of a light inlet of the imaging system is 26 mm.
2. A fundus camera optical system based on non-coaxial array illumination according to claim 1 wherein: the wavelength range of the emitted light of the illumination source is in the near infrared wavelength range.
3. A fundus camera optical system based on non-coaxial array illumination according to claim 2 wherein: the wavelength of the emitted light of the illumination source is 940 nm.
4. A fundus camera optical system based on non-coaxial array illumination according to claim 1 wherein: the imaging system includes: the imaging lens group is used for secondary imaging to correct residual eye aberration and system aberration.
5. A fundus camera optical system based on non-coaxial array illumination according to claim 4 wherein: the field of view angle of the omentum objective lens group is 30-45 degrees, and the field of view angle of the imaging lens group is 65 degrees.
6. A fundus camera optical system based on non-coaxial array illumination according to claim 4 wherein: the omentum objective lens group is a lens group of Networkinjes.
7. A fundus camera optical system based on non-coaxial array illumination according to claim 1 wherein: the number of the illumination sources is six.
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN113208559A (en) * | 2021-05-18 | 2021-08-06 | 中国科学院长春光学精密机械与物理研究所 | Large-view-field non-mydriatic wide refraction compensation eye fundus imaging optical system |
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