CN221242849U - OCT ophthalmic imaging device - Google Patents
OCT ophthalmic imaging device Download PDFInfo
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- CN221242849U CN221242849U CN202322474569.9U CN202322474569U CN221242849U CN 221242849 U CN221242849 U CN 221242849U CN 202322474569 U CN202322474569 U CN 202322474569U CN 221242849 U CN221242849 U CN 221242849U
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- 238000003384 imaging method Methods 0.000 title claims abstract description 22
- 230000001427 coherent effect Effects 0.000 claims abstract description 36
- 230000003287 optical effect Effects 0.000 claims description 11
- 230000008878 coupling Effects 0.000 claims description 3
- 238000010168 coupling process Methods 0.000 claims description 3
- 238000005859 coupling reaction Methods 0.000 claims description 3
- 238000000034 method Methods 0.000 claims description 3
- 239000013307 optical fiber Substances 0.000 claims 1
- 238000009434 installation Methods 0.000 abstract description 3
- 238000001514 detection method Methods 0.000 abstract description 2
- 210000003128 head Anatomy 0.000 description 12
- 210000005252 bulbus oculi Anatomy 0.000 description 6
- 210000001508 eye Anatomy 0.000 description 3
- 201000010099 disease Diseases 0.000 description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 238000007689 inspection Methods 0.000 description 2
- MARDFMMXBWIRTK-UHFFFAOYSA-N [F].[Ar] Chemical compound [F].[Ar] MARDFMMXBWIRTK-UHFFFAOYSA-N 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
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Abstract
The utility model discloses an OCT ophthalmic imaging device, and belongs to the field of medical detection equipment. The ophthalmic imaging device comprises a light source, a deconcentrator, a sample arm, a reference arm and a signal processor, wherein the light source, the sample arm, the reference arm and the signal processor are all connected to the deconcentrator, coherent light emitted by the light source enters the deconcentrator and respectively enters the sample arm and the reference arm through the deconcentrator, the reflection distance in the reference arm can be adjusted, scanning patterns with different depths can be obtained by adjusting the distance of the reflected light in the reference arm, and pattern information is integrated to form a three-dimensional pattern; the sample arm is provided with a laser emitting head which is obliquely arranged so that laser emitted by the laser emitting head intersects coherent light emitted by the sample arm. The utility model can scan more sections, meanwhile, a plurality of groups of reflection light paths with different intervals are not required to be installed in the reference arm, and the utility model has the advantages of convenient installation, compact structure and simple operation.
Description
Technical Field
The utility model belongs to the field of medical detection equipment, and particularly relates to an OCT ophthalmic imaging device.
Background
The ophthalmic diseases need to be found and treated in time, the found earlier treatment effect is better, but the conventional observation of many ophthalmic diseases is difficult to check, along with the development of technology, the optical tomographic coherent scanning technology (OCT) is developed, the scanning diagnosis can be carried out on eyes by adopting a non-contact non-invasive inspection mode, but the function of the existing OCT equipment is single, the experience of operators is depended relatively, in order to solve the problem, the utility model patent worker with publication number 211796403U discloses an ophthalmic multifunctional anterior segment imaging device based on a slit lamp platform, the imaging system focuses on different positions of the anterior segment of the eye by switching lens groups, the ultra-long range imaging of the anterior segment structure of the eye is realized, the inspection is more convenient, the quantity of the mode of switching the lens groups for adjusting the optical paths is relatively fixed, and meanwhile, too many groups of switching optical paths cannot be installed due to the limitation of installation environments.
Disclosure of utility model
In view of the foregoing problems of the prior art, an object of the present utility model is to provide an OCT ophthalmic imaging apparatus.
In order to solve the problems, the technical scheme adopted by the utility model is as follows:
The OCT ophthalmic imaging device comprises a light source, a deconcentrator, a sample arm, a reference arm and a signal processor, wherein the light source, the sample arm, the reference arm and the signal processor are all connected to the deconcentrator, coherent light emitted by the light source enters the deconcentrator and respectively enters the sample arm and the reference arm through the deconcentrator, the coherent light reflected by the reference arm and the sample arm returns to the deconcentrator to interfere, the signal processor processes interference signals to obtain scanning patterns with specific depth, the reflection distance in the reference arm can be adjusted, the scanning patterns with different depths can be obtained by adjusting the distance of the reflected light in the reference arm, and the pattern information is integrated to form a three-dimensional pattern; the sample arm is provided with a laser emission head which is obliquely arranged so that laser emitted by the laser emission head intersects with coherent light emitted by the sample arm.
As a preferable scheme of the utility model, a first scanning vibrating mirror and a movable inclined plane reflecting mirror are arranged in the reference arm, the inclined plane reflecting mirror horizontally moves under the drive of a translation mechanism, a sensor is arranged on the translation mechanism, the position of the inclined plane reflecting mirror is fed back in real time through the sensor, and a second convex lens is arranged between the inclined plane reflecting mirror and the first scanning vibrating mirror.
As a preferable scheme of the utility model, a first collimating mirror, an optical power attenuation device and a first convex lens are further arranged in the reference arm, coherent light entering the reference arm passes through the first collimating mirror, the optical power attenuation device and the first convex lens in sequence, obliquely irradiates the first scanning vibration mirror and reflects on the first scanning vibration mirror, the reflected light reaches the inclined plane reflecting mirror after passing through the second convex lens, and the inclined plane reflecting mirror returns a coherent light source to the first scanning vibration mirror.
As a preferred scheme of the utility model, the sample arm 4 comprises a second scanning vibration mirror and a first dichroic mirror, the coherent light entering the sample arm passes through the second collimating mirror, is reflected at the second scanning vibration mirror and reaches the surface of the first dichroic mirror, the first dichroic mirror reflects a part of the coherent light to the eyeball position to be detected, the coherent light reflected at the eyeball position is reflected to the second scanning vibration mirror through the first dichroic mirror, and the first scanning vibration mirror and the second scanning vibration mirror send the reflected light to a coupling device in a deconcentrator.
As a preferable scheme of the utility model, an auxiliary camera and an auxiliary display screen are also arranged in the sample arm, a second dichroic mirror is arranged between the auxiliary camera and the auxiliary display screen, the auxiliary display screen and the auxiliary camera are both connected to a computer, the auxiliary display screen, the second dichroic mirror and the first dichroic mirror are positioned on the same straight line, the image position on the auxiliary display screen can be controlled and regulated, and a third convex lens is arranged between the second dichroic mirror and the first dichroic mirror.
As a preferred embodiment of the present utility model, the signal processor includes: the deconcentrator sequentially sends the coupled light into the third collimating mirror, the grating, the lens and the high-speed linear array camera, and then the high-speed linear array camera sends the signal into the computer for processing.
As a preferred embodiment of the present utility model, the laser emitting heads have a plurality of groups and are built into the housing in which the sample arm is located.
As a preferred embodiment of the present utility model, the laser emitting heads have three groups and are disposed around the coherent light outlet of the sample arm.
Compared with the prior art, the utility model has the beneficial effects that:
1. According to the utility model, the first scanning vibrating mirror and the movable inclined plane reflecting mirror are arranged in the reference arm, the inclined plane reflecting mirror horizontally moves under the drive of the translation mechanism, the distance between light paths in the reference arm is adjusted when the horizontal movement mechanism drives the inclined plane reflecting mirror to move, the reflected coherent light is optically coupled with the coherent light reflected by the sample arm, so that the scanning images of end faces with different depths are obtained, the number of the scanned sections is more, meanwhile, a plurality of groups of reflecting light paths with different distances are not required to be arranged in the reference arm, and the installation is convenient.
2. According to the utility model, the laser emission head is arranged on the sample arm, and the laser emission head is used for emitting laser on the surface tissue of the eyeball, so that a thermal effect is generated on the surface tissue of the focus, a mark is formed, the accurate focus position is provided, and the working efficiency is improved.
Drawings
FIG. 1 is a schematic diagram of an ophthalmic OCT imaging device;
FIG. 2 is a schematic perspective view of the end of the sample arm housing;
In the figure: 1-a light source; a 2-deconcentrator; 3-a reference arm; 301-a first collimating mirror; 302-an optical power attenuation device; 303-a first convex lens; 304-a first scanning galvanometer; 305-a second convex lens; 306-a beveled mirror; 4-sample arm; 401-a second collimating mirror; 402-a second scanning galvanometer; 403-a first dichroic mirror; 404-a second dichroic mirror; 405-auxiliary display screen; 406-an auxiliary camera; 407-a third convex lens; 408-a laser emitting head; 5-spectrometer; 501-a third collimating mirror; 502-grating; 503-a lens; 504-high speed line camera; 6-a computer;
Detailed Description
The utility model is further described below in connection with specific embodiments.
Example 1
As shown in fig. 1, the present utility model provides an OCT ophthalmic imaging apparatus, comprising: the device comprises a light source 1, a deconcentrator 2, a sample arm 4, a reference arm 3 and a signal processor, wherein the light source 1, the sample arm 4, the reference arm 3 and the signal processor are all connected to the deconcentrator 2, coherent light emitted by the light source 1 enters the deconcentrator 2 and respectively enters the sample arm 4 and the reference arm 3 through the deconcentrator, the coherent light reflected by the reference arm 3 and the sample arm 4 returns to the deconcentrator to interfere, the signal processor processes interference signals to obtain a scanning pattern with a specific depth, the reflection distance in the reference arm can be adjusted, scanning patterns with different depths can be obtained by adjusting the distance of the reflected light in the reference arm, and pattern information is integrated to form a three-dimensional pattern;
The reference arm is internally provided with a first scanning seismoscope 304 and a movable inclined plane reflecting mirror 306, the inclined plane reflecting mirror 306 horizontally moves under the drive of a translation mechanism, a sensor is arranged on the translation mechanism, the position of the inclined plane reflecting mirror is fed back in real time through the sensor, a second convex lens 305 is arranged between the inclined plane reflecting mirror and the first scanning seismoscope, the reference arm 3 is internally provided with a first collimating mirror 301, an optical power attenuation device 302 and a first convex lens 303, coherent light entering the reference arm sequentially passes through the first collimating mirror 301, the optical power attenuation device 302 and the first convex lens 303, obliquely irradiates the first scanning seismoscope 304 and reflects on the first scanning seismoscope 304, the reflected light reaches the inclined plane reflecting mirror 306 after passing through the second convex lens, and the inclined plane reflecting mirror 306 returns a coherent light source onto the first scanning seismoscope 304.
The sample arm 4 comprises a second scanning seismoscope 402 and a first dichroic mirror 403, coherent light entering the sample arm 4 passes through the second collimating mirror 401, is reflected at the second scanning seismoscope 402 and reaches the surface of the first dichroic mirror 403, the first dichroic mirror 403 reflects a part of coherent light to the eyeball position to be detected, the coherent light reflected at the eyeball position is reflected to the second scanning seismoscope 402 through the first dichroic mirror, the first scanning seismoscope 304 and the second scanning seismoscope 402 send reflected light to a coupling device in the deconcentrator 2, an auxiliary camera 406 and an auxiliary display screen 405 are further arranged in the sample arm 4, a second dichroic mirror 404 is arranged between the auxiliary camera 406 and the auxiliary display screen 405, the auxiliary display screen 405 and the auxiliary camera 406 are both connected to a computer, the auxiliary display screen 405, the second dichroic mirror 404 and the first dichroic mirror 403 are positioned on the same straight line, and the image position on the auxiliary display screen 405 can be controlled and adjusted, and a third convex lens 407 is arranged between the second dichroic mirror 404 and the first dichroic mirror 403.
The signal processor includes: the deconcentrator 2 sequentially sends the coupled light into the third collimating mirror 501, the grating 502, the lens 503 and the high-speed linear array camera 504, and then the high-speed linear array camera sends the signal into the computer 6 for processing.
Working principle: the laser of the light source 1 is divided into two beams by the beam splitter 2, and enters the reference arm 3 and the sample arm 4 respectively, and the coherent light entering the reference arm 3 passes through the flat first collimating mirror 301, the optical power attenuation device 302 and the first convex lens 303; the first scanning seismoscope 304, the second convex lens 305 and the inclined plane mirror 306 are then returned to the beam splitter 2 in the original path; the coherent light from the static beam to the sample arm is returned to the beam splitter 2 through the second collimating mirror 401, the second scanning vibration mirror 402, the first dichroic mirror 403 and the original path of the eyeball to be detected; the coherent light returned by the reference arm 3 and the sample arm 4 interferes in the beam splitter 2, single reflection is enhanced through interference, a scanning image with a specific depth is obtained after being processed by a third collimating mirror 501, a grating 502, a lens 503 and a high-speed linear array camera 504 of a signal processor, a translation mechanism in the reference arm drives a bevel mirror 306 to horizontally move, and the distance between a first scanning vibration mirror 304 and the bevel mirror 306 is precisely adjusted by matching with a sensor on the translation mechanism, so that coherent light interference of different depth reflections of the sample arm is enhanced, different depth scanning sectional images are obtained, and three-dimensional pattern information is formed after being processed and integrated by a computer 6.
Example 2
As shown in fig. 2, the present utility model provides an OCT ophthalmic imaging apparatus, compared with embodiment 1, the sample arm 4 is provided with a laser emitting head, the laser emitting head is obliquely arranged so that laser light emitted by the laser emitting head intersects with coherent light emitted by the sample arm 4, the laser emitting head has a plurality of groups and is built in a housing where the sample arm is located, and the laser emitting head has three groups and is circumferentially arranged around a coherent light outlet of the sample arm. This example uses an argon fluorine excimer laser with a wavelength of 193 nm. The rest of the structure is the same as in example 1.
It should be noted that the above embodiments are only for illustrating the technical solution of the present utility model and not for limiting the same, and although the present utility model has been described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that the technical solution of the present utility model may be modified or substituted without departing from the spirit and scope of the technical solution of the present utility model, which is intended to be covered in the scope of the claims of the present utility model.
Claims (8)
1. The OCT ophthalmic imaging device comprises a light source (1), a deconcentrator (2), a sample arm (4), a reference arm (3) and a signal processor, wherein the light source (1), the sample arm (4), the reference arm (3) and the signal processor are all connected to the deconcentrator (2), coherent light emitted by the light source (1) enters the deconcentrator (2) and respectively enters the sample arm (4) and the reference arm (3) through the deconcentrator, the coherent light reflected by the reference arm (3) and the sample arm (4) returns to the deconcentrator to interfere, and the signal processor processes an interference signal to obtain a scan pattern with a specific depth, and the OCT ophthalmic imaging device is characterized in that the reflection distance in the reference arm can be adjusted, the scan patterns with different depths can be obtained by adjusting the distance of the reflected light in the reference arm, and pattern information is integrated to form a three-dimensional pattern; the sample arm (4) is provided with a laser emitting head which is obliquely arranged so that laser light emitted by the laser emitting head intersects with coherent light emitted by the sample arm (4).
2. The OCT ophthalmic imaging device according to claim 1, wherein a first scanning mirror (304) and a movable inclined mirror (306) are disposed in the reference arm, the inclined mirror (306) is driven by a translation mechanism to move horizontally, the translation mechanism is provided with a sensor, the position of the inclined mirror is fed back in real time through the sensor, and a second convex lens (305) is disposed between the inclined mirror and the first scanning mirror.
3. An OCT ophthalmic imaging device according to claim 2, wherein the reference arm (3) is further provided with a first collimating mirror (301), an optical power attenuation device (302) and a first convex lens (303), the coherent light entering the reference arm passes through the first collimating mirror (301), the optical power attenuation device (302) and the first convex lens (303) in sequence, and obliquely irradiates the first scanning mirror (304) and reflects the light on the first scanning mirror (304), the reflected light passes through the second convex lens and then reaches the inclined plane mirror (306), and the inclined plane mirror (306) returns the coherent light to the first scanning mirror (304).
4. An OCT ophthalmic imaging device according to claim 3, wherein the sample arm (4) comprises a second scanning mirror (402) and a first dichroic mirror (403), the coherent light entering the sample arm (4) is reflected by the second collimating mirror (401) at the second scanning mirror (402) and reaches the surface of the first dichroic mirror (403), the first dichroic mirror (403) reflects a part of the coherent light to the eye position to be measured, the coherent light reflected by the eye position is reflected by the first dichroic mirror onto the second scanning mirror (402), and the first scanning mirror (304) and the second scanning mirror (402) send the reflected light to the coupling means in the splitter (2).
5. The OCT ophthalmic imaging device according to claim 4, wherein an auxiliary camera (406) and an auxiliary display screen (405) are further disposed in the sample arm (4), a second dichroic mirror (404) is disposed between the auxiliary camera (406) and the auxiliary display screen (405), the auxiliary display screen (405) and the auxiliary camera (406) are both connected to a computer, the auxiliary display screen (405), the second dichroic mirror (404), the first dichroic mirror (403) are located on the same straight line, the image position on the auxiliary display screen (405) can be controlled and adjusted, and a third convex lens (407) is installed between the second dichroic mirror (404) and the first dichroic mirror (403).
6. The OCT ophthalmic imaging device of claim 5, wherein the signal processor comprises: the optical fiber splitter (2) sequentially sends the coupled light into the third collimating mirror (501), the grating (502), the lens (503) and the high-speed linear array camera (504), and then the high-speed linear array camera sends the signal into the computer (6) for processing.
7. The OCT ophthalmic imaging device of claim 1, wherein the laser emitting heads have multiple sets and are built into a housing in which the sample arm is located.
8. The OCT ophthalmic imaging device of claim 7, wherein the laser emitting heads are in three sets and are circumferentially disposed around the sample arm coherent light exit.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202322474569.9U CN221242849U (en) | 2023-09-12 | 2023-09-12 | OCT ophthalmic imaging device |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202322474569.9U CN221242849U (en) | 2023-09-12 | 2023-09-12 | OCT ophthalmic imaging device |
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| Publication Number | Publication Date |
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| CN221242849U true CN221242849U (en) | 2024-07-02 |
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| Application Number | Title | Priority Date | Filing Date |
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| CN202322474569.9U Active CN221242849U (en) | 2023-09-12 | 2023-09-12 | OCT ophthalmic imaging device |
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| CN (1) | CN221242849U (en) |
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