CN111110183A - Binocular optical coherence automatic focusing imaging device and working method - Google Patents
Binocular optical coherence automatic focusing imaging device and working method Download PDFInfo
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Abstract
The invention discloses an optical coherence automatic focusing imaging device capable of adjusting focusing eyes simultaneously and a working method thereof.A pupil illumination branch emits illumination light, and the pupil illumination branch receives and judges the pupil position after entering a pupil for reflection; then the control mechanism adjusts the positions of the two pupil reflectors so that the two pupil branches respectively face the pupils on the same side. The laser emits laser, part of the laser irradiates into the pupil, scans the position information of different structures in the eye, and carries the position information to the receiving panel after being reflected; part of laser is reflected by the reference plane and then enters the receiving panel; and simultaneously, the reference plane moves back and forth until the reference light interferes with the information light, and the position of the intraocular structure corresponding to the information light is determined. In the scanning process, pupil positioning operation is repeatedly performed for a plurality of times. The positions of pupils at two sides are tracked in real time, so that focusing is kept, the steps of eye OCT operation are simplified, the time of eye scanning operation of a patient is saved, and the comfort level of the patient in seeing a doctor is improved.
Description
Technical Field
The invention relates to the field of eye OCT scanning imaging, in particular to a binocular optical coherence automatic focusing imaging device and a working method.
Background
Optical Coherence Tomography (OCT) is an imaging technique rapidly developed in the last decade, which uses the basic principle of weak coherent Optical interferometer to detect back-reflected or several scattered signals of incident weak coherent light at different depth levels of biological tissue, and then scans to obtain two-dimensional or three-dimensional structural images of biological tissue.
Since blood vessels in the pupils of human eyes are visible in vitro, the ophthalmic OCT examination is a very common examination item in clinical and physical examinations. The method specifically comprises the following steps: the internal conditions of the eye, such as blood circulation, blood disorders, and also nervous system disorders, are examined by means of instruments, based on the principle of light reflection. In the ophthalmologic examination, the ophthalmologic OCT examination can reflect peripheral vision of the eye, a blood circulation state of the fundus, and the like, in addition to macular degeneration and optic neuropathy. The main principle is that the interior of the pupil of the eye is scanned by continuous coherent infrared light waves, and the condition in the eye is drawn according to the position information carried by the reflected light of each layer in the pupil.
In the prior art, OCT equipment used in hospitals is used for detecting single eyes, namely, one eye of a patient is firstly aligned, adjusted and focused each time, after the fundus is scanned, the other eye is moved to be aligned, adjusted and focused again, and the fundus scanning work is carried out again.
And because the time required for adjusting focusing is longer, the patient can hardly control the two eyes to rotate in the whole process and keep the two eyes at the same pupil position all the time. If the pupil position changes during focusing and during scanning of the patient, the acquired scanned image loses sufficient sharpness and loses clinical analysis.
Therefore, for the ophthalmic examination, the OCT apparatus needs to be adjusted and focused twice for one eye examination, which is time consuming, and requires the patient to hold the eyeball against rotation for a long time, which also causes the patient to feel less comfortable.
Thus, the prior art is subject to further improvements and enhancements.
Disclosure of Invention
In view of the above-mentioned defects of the prior art, the present invention provides an optical coherence auto-focusing imaging apparatus and a working method thereof capable of adjusting focusing of two eyes simultaneously, so as to reduce the time required for the eye OCT examination and provide comfort for the patient.
In order to achieve the above object, the present invention provides a binocular optical coherence auto-focusing imaging apparatus, comprising an eye-alignment optical path, wherein the eye-alignment optical path comprises a main optical path and a plurality of branch optical paths, wherein the branch optical paths are vertically optically connected with the main optical path through a beam splitter disposed in the main optical path at an angle of 45 degrees; the branch light path comprises a pupil illumination branch for providing illumination light for illuminating pupils, a laser branch for providing a laser light source, a receiving branch for connecting vertical light to a receiving panel, and two pupil branches which are reflected by two pupil reflectors and are opposite to left and right pupils; the main light path is connected with a positioning structure for tracking and positioning two pupils, the positioning structure comprises an image sensor, the image sensor receives illumination light reflected by eyeballs, and identifies and feeds back the positions of the two pupils to a control mechanism, and the control mechanism is used for adjusting the distance between two pupil reflectors so that the two pupil branches respectively face one pupil; the laser scanning structure comprises a laser device, emits laser, respectively enters the two pupils along the eye alignment optical path, returns to the eye alignment optical path after being reflected by different layers of the eyes, and is sent to a receiving panel; the receiving panel is parallel to and opposite to the receiving panel, a total-reflection reference plane is arranged, the reference plane and the receiving panel are in optical connection through a receiving beam splitter, and the distance between the reference plane and the receiving panel is adjustable.
Preferably, the pupil reflectors are respectively mounted on a sliding block, each sliding block is connected with a piston of a linear motor, each linear motor is respectively controlled by the control mechanism, and the pistons are extended and retracted according to the pupil positions.
Preferably, the pupil illumination branch comprises a monochromatic illumination light source, and enters the eye-alignment light path after being emitted into the illumination beam splitter as parallel light through the illumination lens group.
Preferably, the main light path is further connected with a sighting target branch path for projecting a sighting target to a pupil, the sighting target branch path comprises a sighting target light source, visible light is emitted and irradiates a sighting target image after passing through a sighting target condenser lens, and light carrying sighting target information enters the main light path after being reflected by a sighting target beam splitter.
Preferably, a sighting target projecting mirror is further disposed between the sighting target image and the sighting target beam splitter, and the sighting target projecting mirror can adjust the size of the sighting target and project the sighting target on the sighting target beam splitter.
Preferably, each of the pupil branches is provided with a light valve switch for cutting off or communicating light passing through the pupil branch.
Preferably, the reference plane is carried on a carriage which is driven by the control mechanism to adjust the distance from the receiving panel.
Preferably, the illumination light is infrared light.
Preferably, the laser is an infrared laser.
The invention also discloses a working method of the binocular optical coherence automatic focusing imaging device, after a patient moves to the position that the eyes are opposite to the binocular optical coherence automatic focusing imaging device, the patient is controlled by the control mechanism to sequentially execute the following steps:
A. the pupil illumination branch works, illumination light is reflected from an eyeball and then enters the image sensor through the eye alignment light path, and the image sensor identifies and sends the pupil position to the control mechanism;
B. adjusting the specific positions of the two pupil reflectors to ensure that the two pupil branches respectively face the pupils on the same side;
C. closing the illuminating light, enabling the laser to emit laser, enabling part of the laser to enter a pupil, carrying position information of an eyeball internal tissue after the laser is reflected by different layers of the eye to form information light, returning the information light to the eye alignment light path, and enabling the information light to enter the receiving panel; part of laser is shot into the reference plane, is reflected by the reference plane to form reference light, and is shot into the receiving panel;
D. translating the reference plane back and forth along a vertical direction until the information light and the reference light interfere with each other;
E. recording the distance between the acceptance panel and the reference plane;
repeating the steps A to C for multiple times.
Technical effects
The invention discloses an optical coherence automatic focusing imaging device capable of adjusting focusing eyes simultaneously and a working method thereof.A pupil illumination branch emits illumination light, and the pupil illumination branch receives and judges the pupil position by an image sensor of a positioning structure after entering the pupil for reflection; then the control mechanism adjusts the positions of the two pupil reflectors so that the two pupil branches respectively face the pupils on the same side. Then the laser emits laser, part of the laser enters into the pupil through the eye-facing light path, the position information of different structures of the eye is scanned, and the laser carries the position information to the receiving panel after being reflected; part of laser is emitted into the reference plane and is also emitted into the receiving panel after being reflected by the reference plane; and meanwhile, the reference plane moves back and forth under the regulation of the control mechanism until the reference light interferes with the information light, and the position of the intraocular structure corresponding to the information light is determined. And in the scanning process, pupil positioning operation is repeatedly executed for a plurality of times, and the pupil position is positioned in real time. The invention keeps the focusing state by simultaneously focusing the pupils at two sides and tracking the positions of the pupils in real time, simplifies the steps of the OCT operation of the eyes, saves the time of the scanning operation of the eyes of the patient and improves the comfort level of the patient for seeing a doctor.
The conception, the specific structure and the technical effects of the present invention will be further described with reference to the accompanying drawings to fully understand the objects, the features and the effects of the present invention.
Drawings
FIG. 1 is a diagram of an operating optical path of a binocular optical coherence auto-focus imaging apparatus according to a preferred embodiment of the present invention.
FIG. 2 is a flowchart illustrating the operation of the binocular optical coherence auto focus imaging apparatus according to a preferred embodiment of the present invention.
In the figure, 10, a left pupil branch, 11, a left light valve switch, 12, a pupil beam splitter, 13, a left pupil reflector, 15, a left eyeball, 20, a right pupil branch, 21, a right light valve switch, 22, an end reflector, 23, a right pupil reflector, 25, a right eyeball, 30, a pupil illumination branch, 31, a sensor lens group, 32, an illumination beam splitter, 33, an image sensor, 35, a monochromatic illumination light source, 36, an illumination lens group, 40, a visual target branch, 41, a visual target condenser, 42, a visual target beam splitter, 43, a visual target projector, 44, a visual target image, 45, a visual target light source, 50, a laser source branch, 51, a laser, 52, a laser beam splitter, 60, an acceptance branch, 61, a reference plane, 62, an acceptance beam splitter, 65, an acceptance panel, 70 and a main light path.
Detailed Description
The technical contents of the preferred embodiments of the present invention will be more clearly and easily understood by referring to the drawings attached to the specification. The present invention may be embodied in many different forms of embodiments and the scope of the invention is not limited to the embodiments set forth herein.
In the drawings, structurally identical elements are represented by like reference numerals, and structurally or functionally similar elements are represented by like reference numerals throughout the several views. The size and thickness of each component shown in the drawings are arbitrarily illustrated, and the present invention is not limited to the size and thickness of each component. The thickness of the components may be exaggerated where appropriate in the figures to improve clarity.
The invention provides a binocular optical coherence auto-focusing imaging device, the optical path diagram of which is shown in figure 1 and comprises an eye alignment optical path, the eye alignment optical path comprises a main optical path 70 and a plurality of branch optical paths, and the branch optical paths are in vertical optical connection with the main optical path 70 through all beam splitters arranged in the main optical path, therefore, all the beam splitters are arranged in the main optical path 70 in a 45-degree angle direction, when light irradiates on the beam splitters at a 45-degree angle, part of the light passes through the beam splitters in the original direction, and the other part of the light is reflected by the beam splitters and forms a 90-degree angle with the original incident direction and leaves the beam splitters.
As shown in fig. 1, the main light path 70 is optically connected to a plurality of branch light paths, including a pupil illumination branch 30 for providing illumination light for illuminating a pupil, a laser branch 50 for providing a laser light source, a receiving branch 60 vertically optically connected to a receiving panel 65, and two pupil branches respectively facing a left pupil and a right pupil after being reflected by two pupil mirrors, which are respectively corresponding to the left pupil branch 10 and the right pupil branch 20. Accordingly, the pupil mirrors are the left pupil mirror 13 and the right pupil mirror 23.
The pupil illumination branch 30 preferably uses a monochromatic illumination light source 35 to emit illumination light, the illumination light forms parallel light after passing through an illumination lens group 36, and then is reflected by an illumination beam splitter 32, changes an angle, enters the main light path in the vertical direction, and is emitted downward.
After passing through a series of beam splitters, the illumination light reaches the pupil beam splitter 12, and part of the illumination light is vertically deflected to the left by the pupil beam splitter 12, passes through a distance L1, and then irradiates the left pupil reflector 13, and is reflected by the left pupil reflector 13 to illuminate the left eyeball 15. The reflected light of the left eye ball 15 returns to the main light path 70 in the original path, and is radiated to the illumination beam splitter 32 in a reverse direction, and after part of the reflected light passes through the illumination beam splitter 32 in the direction, the reflected light is focused by the sensor lens group 31, and forms an image of the left eye ball on an image sensor 33, and the position of the left pupil can be read in the left eye ball imaging.
The other part of the illumination light reaching the pupil beam splitter 12 passes through the pupil beam splitter 12 while maintaining the original direction, and is redirected by the end mirror 22 to the right pupil mirror 23 to illuminate the right eye 25. Similarly, the reflected light of the right eyeball 25 returns to the main light path 70 in the original path, and is irradiated to the illumination beam splitter 32 in the reverse direction, and a part of the reflected light also passes through the illumination beam splitter 32 in the direction and is focused by the sensor lens group 31, so that the right eyeball is imaged in the image sensor 33, and the position of the right pupil can be read in the right eyeball imaging process
Therefore, by connecting the pupil illumination branch 30 to the main light path 70 and connecting the positioning structure including the sensor lens group 31 and the image sensor 33, real-time positioning of the left and right pupils is achieved. In addition, the image sensor 33 feeds back the positions of the two pupils to a control mechanism in real time, and the control mechanism adjusts the positions of the two pupil mirrors, i.e., L1 and L2 in fig. 1, according to the positions of the pupils, so that the two pupil branches are respectively aligned to one pupil, thereby facilitating subsequent laser scanning.
Specifically, in one embodiment, for example, the pupil reflectors are respectively mounted on a slider, each slider is connected to a piston of a linear motor, each linear motor is respectively controlled by the control mechanism, and the pistons are extended and retracted according to the pupil positions, so as to adjust each pupil reflector to the pupil facing the corresponding side.
In addition, in the subsequent laser scanning process, the above real-time positioning operation still needs to be repeated for many times to prevent the scanning failure caused by the pupil position change due to the eyeball rotation.
Considering that the use of visible light as the illumination light may have some influence and discomfort on the human eye, the illumination light is preferably invisible light, particularly infrared light, i.e., the monochromatic illumination light source 35 is an infrared light source.
Although the positions of the eyes of different patients are not the same, i.e. the initial positions of the left pupil reflector 13 and the right pupil reflector 23 may not reflect the illumination light to illuminate all the eyes on the corresponding sides, this can be overcome by two aspects of hardware and software. For example, in hardware, the initial positions of two reflectors can be adjusted, and in software, in the prior art, the pupil position can be found according to incomplete eyeball imaging completely through image recognition processing.
In order to attract the attention of the patient's sight line and ensure the smooth scanning, a visual target branch 40 is further connected to the main optical path 70 for projecting the visual target to the pupil, thereby attracting the patient's sight line.
Specifically, as shown in fig. 1, the target branch 40 includes a target light source 45, which emits visible light, and irradiates the target image 44 after passing through the target condenser 41, and the light carrying the target information is converged on the target beam splitter 42, reflected by the target beam splitter 42, enters the main light path 70, and then reaches the pupil beam splitter 12 along the main light path 70, and then is projected into the eyeballs on both sides, so as to attract the eye of the patient and reduce the large-amplitude movement of the eyeballs.
In a more preferred embodiment, a visual target projecting mirror 43 is further provided between the visual target image 44 and the visual target beam splitter 42, and the visual target projecting mirror 43 can adjust the size of the visual target and project the visual target on the visual target beam splitter 42, in consideration of the perspective feeling generated by changing the size of the visual target.
When the pupil reflectors are adjusted to be opposite to the pupils on the same side, the laser scanning operation can be started to scan the structures in the pupils. Specifically, the main optical path 70 is also optically connected with a laser scanning structure, which includes a laser 51, and emits laser light, preferably infrared laser light, which is invisible and thus will not attract the attention of the eyeball to cause the movement of the eyeball. The laser beam is reflected by the laser beam splitter 52, enters the eye alignment optical path, and enters the two pupils along the eye alignment optical path, and after being reflected by different layers of the eye, such as corneal reflection, iris reflection, crystalline lens reflection, and retinal reflection, and reflected by the detail structures with different heights on the retina, the laser beam carries the height position information of each structure, and is returned to the eye alignment optical path as information light and transmitted to a receiving panel 65.
Considering that different layers of the eye are reflected, the reflected light of each layer needs to be distinguished, i.e. the position of each structure needs to be located. This is done in particular by optical interference. Specifically, as shown in fig. 1, a reference plane 61 for total reflection is provided parallel to and facing the receiving panel 65, the reference plane 61 and the receiving panel 65 are optically connected to each other through a receiving beam splitter 62, so that the laser light irradiated onto the laser beam splitter 52 travels downward to the entrance pupil, and the other laser light is reflected to the reference plane 61 and reflected back by the reference plane 61 to become reference light, which is also incident to the receiving panel 65 to be mixed with the information light.
The distance between the reference plane 61 and the receiving panel 65 is adjustable, for example, the reference plane 61 is loaded on a carriage, and the carriage is driven by the control mechanism to move, so as to adjust the distance between the reference plane 61 and the receiving panel 65. By changing the distance between the reference plane 61 and the receiving panel 65, the phase of the reference light can be changed until interference occurs. Therefore, when the reference plane 61 is at a proper position, i.e. from the receiving beam splitter 62, the optical path of the information light traveling downward in the figure to the inside of the pupil and returning to the receiving beam splitter 62 from a layer inside the pupil is equal to the optical path of the reference light traveling rightward in the figure to the reference plane 61 and being reflected back to the receiving beam splitter 62. When the reference light interferes with the information light, the position of the layer structure inside the pupil can be read according to the position of the reference plane 61, and by comparing the relative distance information between different positions, specific pupil internal structures, such as a cornea reflecting layer at the closest distance, an iris reflecting layer at a farther distance, a crystalline lens reflecting layer at a farther distance, a retina reflecting layer at a farthest distance, and even a depressed macular region, a raised blood vessel and other detailed structures on the retina reflecting layer can be drawn. That is, after the light interference occurs, the position of the reference plane 61 corresponding to the light interference at this time is recorded, i.e., the position information of a certain structure in the pupil is obtained.
Considering that the positions of the two eyes of a person are generally symmetrical, so that the optical paths of the left eye and the right eye are basically equal, the related information may not be easily distinguished, and at this time, a light valve switch may be disposed on each of the pupil branches to cut off or connect the light passing through the pupil branches. Specifically, as shown in fig. 1, a left light valve switch 11 is disposed on the left pupil branch 10, and a right light valve switch 21 is disposed on the right pupil branch 20. During scanning, the control mechanism sequentially opens the light path on one side and closes the light path on the other side.
Therefore, the working method of the binocular optical coherence auto-focusing imaging device is as shown in the flowchart of fig. 2, and sequentially comprises the following steps:
firstly, the patient moves to the front of the binocular optical coherence auto-focusing imaging device, and the positions of the two pupil reflectors are finely adjusted, so that the two eyes of the patient are opposite to the pupil reflectors on the same side;
secondly, the control mechanism controls the pupil illumination branch 30 to work, the monochromatic transparent light source 35 emits illumination light, the illumination light is irradiated to the eyeballs along the eye alignment light path and is reflected from the eyeballs, then the illumination light returns to the eye alignment light path and is incident to the image sensor 33, the image sensor 33 records eyeball images, the pupil illumination branch can be directly connected with a processor, the positions of the two pupils are identified in real time by using a general image identification technology, and the pupil positions are sent to the control mechanism;
thirdly, the control mechanism changes the sizes of L1 and L2 according to the pupil positions, namely, the specific positions of the two pupil reflectors are adjusted, so that the two pupil branches are respectively opposite to the pupils at the same side, and the subsequent scanning laser can be always shot into the pupils;
fourthly, the control mechanism closes the illumination light, the laser 51 emits laser, part of the laser enters the pupil, after being reflected by different layers of the eye, the laser carries eye information to form information light, the information light returns to the eye alignment light path and enters the receiving panel 65; the other part of the laser beam is incident on the reference plane 61, reflected by the reference plane 61 to form a reference beam, and incident on the receiving panel 65;
fifthly, the control mechanism translates the reference plane 61 back and forth along the vertical direction until the information light and the reference light are subjected to light interference;
sixthly, the control mechanism records the distance between the receiving panel 65 and the reference plane 61.
In addition, in the scanning process, in order to prevent the problem that the movement range of the eyeball of the patient is too large and the scanning is not clear, the second step to the fourth step need to be repeated for multiple times, namely, the position of the pupil is tracked in real time in the scanning process, and the specific positions of the two pupil reflectors are adjusted according to the real-time position of the pupil.
In summary, the present invention discloses an optical coherence auto-focusing imaging device and a working method thereof capable of adjusting focusing eyes simultaneously, wherein, first, a pupil illumination branch 30 emits illumination light, which enters into the pupil for reflection, and then an image sensor 33 of a positioning structure receives and determines the pupil position; then the control mechanism adjusts the positions of the two pupil reflectors so that the two pupil branches respectively face the pupils on the same side. Then, the laser 51 emits laser, part of the laser enters the pupil through the eye-facing light path, scans the position information of different structures in the eyeball, and carries the position information to the receiving panel 65 after being reflected; part of the laser beam is incident on the reference plane 61, and is reflected by the reference plane 61 and then also incident on the receiving panel 65; meanwhile, the reference plane 61 moves back and forth under the regulation of the control mechanism until the reference light interferes with the information light, and the position of the intraocular structure corresponding to the information light is determined. And in the scanning process, pupil positioning operation is repeatedly executed for a plurality of times, and the pupil position is positioned in real time. The invention keeps the focusing state by simultaneously focusing the pupils at two sides and tracking the positions of the pupils in real time, simplifies the steps of the OCT operation of the eyes, saves the time of the scanning operation of the eyes of the patient and improves the comfort level of the patient for seeing a doctor.
The foregoing detailed description of the preferred embodiments of the invention has been presented. It should be understood that numerous modifications and variations could be devised by those skilled in the art in light of the present teachings without departing from the inventive concepts. Therefore, the technical solutions available to those skilled in the art through logic analysis, reasoning and limited experiments based on the prior art according to the concept of the present invention should be within the scope of protection defined by the claims.
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| CN115474895A (en) * | 2022-09-29 | 2022-12-16 | 山东探微医疗技术有限公司 | OCT (optical coherence tomography) fundus imaging device and method |
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