CN201042430Y - Device for retina cell imaging - Google Patents
Device for retina cell imaging Download PDFInfo
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- CN201042430Y CN201042430Y CNU2007200367942U CN200720036794U CN201042430Y CN 201042430 Y CN201042430 Y CN 201042430Y CN U2007200367942 U CNU2007200367942 U CN U2007200367942U CN 200720036794 U CN200720036794 U CN 200720036794U CN 201042430 Y CN201042430 Y CN 201042430Y
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Abstract
The utility model discloses a device for retinal cell imaging. The device includes a micro-imaging lighting unit, an optical fiber output laser lighting unit, and a first polarizing beam splitter PBS (401), a first aperture-matched lens assembly (700), a second polarizing beam splitter PBS (402), a second aperture-matched lens assembly (1000) and a micro-imaging optical unit sequentially arranged in the light axial line of a lighting system. A layer-by-layer scanning optical unit is arranged on another beam-split light path of the first polarizing beam splitter PBS (401). A 1/4 wave plate (800) and a wave-front corrector (900) are arranged in sequence on another beam-split light path of the second polarizing beam splitter PBS (402). A dichroic lens (1100) is arranged between the second aperture matched lens assembly (1000) and the micro imaging optical unit to divide the light path into two, and a wave-front sensor (1200) is arranged on the other light path. The utility model can be used for observing tissue state of retina in cell level clearly, thereby performing accurate analysis and judgment of eyeground condition.
Description
Technical field
This utility model belongs to human eye retina's armarium manufacturing technology field, relates in particular to a kind of device that is used for the retina cell imaging.
Background technology
The tissue morphology of retina on the cell yardstick can be clearly observed by the device that is used for the retina cell imaging, thereby the type of retinopathy can be accurately judged, accurately judge the feasibility of retinopathy Therapeutic Method, the effectiveness of objective judgement retinopathy medicine.
Photoelectric Technology Inst., Chinese Academy of Sciences be domestic to the technical research of retina self adaptive imaging early, deeply, than the unit of system, provide some retina cell micro-imaging techniques in the patents such as the CN99115051.1 of its application, CN99115052.X, CN99115053.8 and CN99115054.6.But with respect to this utility model a lot of differences and weak point are arranged: the adaptive optical technique that this utility model adopts is based on the MEMS technology, microminiaturized wavefront correction technology, and the optical fiber output point light source that laser beacon adopts is made up of optical fiber, coupling object lens and semiconductor laser; The eliminate stray light technology of this utility model exploitation adopts the polarization optics technology, and above-mentioned patent adopts confocal diaphragm eliminate stray light; The interfere phase contrast technique that this utility model adopts is to adopt the shear interference technology, and above-mentioned patent adopts the phase liner plate.In addition, in this device, also developed and to have carried out the demixing scan system that layering is observed to retinal structure.
The utility model content
The purpose of this utility model is: a kind of device that is used for the retina cell imaging is provided, can clearly observe the tissue morphology of retina on the cell yardstick by it, thereby can accurately judge the type of retinopathy, accurately judge the feasibility of retinopathy Therapeutic Method, the effectiveness of objective judgement retinopathy medicine.
The technical solution of the utility model is: the device that is used for the retina cell imaging, be used for structure by the optical system observing human eye retina, it comprises micro-imaging lighting unit, optical fiber output laser lighting unit, and be successively set on the first polarization beam splitter prism PBS on the described illuminator optical axis, first aperture coupling lens group, the second polarization beam splitter prism PBS, second aperture coupling lens group, micro-imaging optical unit; On another light path of the described first polarization beam splitter prism PBS beam splitting the demixing scan optical unit is set, before described demixing scan optical unit is positioned at human eye; Set gradually quarter wave plate and wave-front corrector on another light path of the described second polarization beam splitter prism PBS beam splitting; Be provided with half anti-pellicle mirror between described second aperture coupling lens group and the micro-imaging optical unit, divide two, one light paths connection micro-imaging optical unit, on another minute light path Wavefront sensor is set light path.
Below technique scheme is further explained:
1. described micro-imaging lighting unit comprises light source, is disposed with collecting objective, graticle, projection objective, bandpass filter on its optical axis.
2. described optical fiber output laser lighting unit comprises laser beacon and collimator objective, and described laser beacon is made up of optical fiber, coupling object lens and semiconductor laser.
3. be provided with a transparent retinal structure with phase-type between described half-reflecting half mirror and the micro-imaging optical unit and convert corresponding interference contrast optical unit to the strong and weak image that changes of light intensity.
4. described interference contrast optical unit includes first half-reflecting half mirror, first completely reflecting mirror, second half-reflecting half mirror, second completely reflecting mirror, compensating plate and wedge group; Four vertex position settings that described first half-reflecting half mirror, first completely reflecting mirror, second completely reflecting mirror and second half-reflecting half mirror are rectangle, wherein two completely reflecting mirror diagonal angle settings each other, two half-reflecting half mirror diagonal angle settings each other; Described compensating plate is between first half-reflecting half mirror and second completely reflecting mirror, and described wedge group is between first completely reflecting mirror and second half-reflecting half mirror; Incident light wave is divided into two halves after by first half-reflecting half mirror, this two-beam ripple is almost completely the same, a branch of light wave reflexes to second half-reflecting half mirror through behind the compensating plate by second completely reflecting mirror, another Shu Guangbo reflects the back by the wedge group by first completely reflecting mirror, and produced and require laterally moving of distance, be transferred to second half-reflecting half mirror then.
5. described demixing scan optical unit comprises first object lens and second object lens, and described first object lens and/or second object lens can be done accurate moving.
6. described micro-imaging optical unit comprises eyeglass head and little depth field imaging camera lens.
The utility model has the advantages that:
1. the device that is used for the retina cell imaging of the present utility model, can clearly observe the tissue morphology of retina on the cell yardstick by it, thereby can accurately judge the type of retinopathy, accurately judge the feasibility of retinopathy Therapeutic Method, the effectiveness of objective judgement retinopathy medicine.
2. the device that is used for the retina cell imaging of the present utility model has overcome the influence of the aberration that factors such as human eye defective, optical defect, assembling defective cause; Eliminated from human eye, optical system or extraneous veiling glare; Thereby solved retinal structure owing to be transparently to cause the not enough defective of image definition, thereby improved retina image-forming resolution greatly, obtained the retinal images of cell yardstick, can carry out layering to amphiblestroid structure simultaneously and observe.
Description of drawings
The utility model will be further described below in conjunction with drawings and Examples:
Fig. 1 is a structural representation of the present utility model.
Wherein: 101 illuminators; 102 light sources; 103 heat shields; 104 neutral density sheets; 110 collecting objectives; 111 graticles; 112 projection objectives; 113 bandpass filters; 201 laser beacons; 202 collimator objectives; 300 total reflective mirrors; 401 first polarization beam splitter prism PBS; 402 second polarization beam splitter prism PBS; 501 first object lens; 502 second object lens; 601 human eyes; 603 retinas; 700 first apertures coupling lens group; 701 apertures coupling camera lens; 702 apertures coupling camera lens; 8001/4 wave plate; 900 wave-front correctors; 1,000 second apertures coupling lens group; 1001 apertures coupling camera lens; 1002 apertures coupling camera lens; 1100 half-reflecting half mirrors; 1200 Wavefront sensors; 1301 half-reflecting half mirrors; 1302 completely reflecting mirrors; 1303 half-reflecting half mirrors; 1304 completely reflecting mirrors; 1305 compensating plates; 1306 wedge groups; 1401 eyeglass heads; 1402 little depth field imaging camera lenses; 1500 imaging surfaces.
The specific embodiment
Embodiment: as shown in Figure 1, the device that is used for the retina cell imaging, be used for structure by the optical system observing human eye retina, it comprises micro-imaging lighting unit, optical fiber output laser lighting unit, and lens group 1000, micro-imaging optical unit are mated in the first polarization beam splitter prism PBS, 401, the first apertures coupling lens group 700, the second polarization beam splitter prism PBS 402, second aperture that are successively set on the described illuminator optical axis.
On another light path of the first polarization beam splitter prism PBS, 401 beam splitting the demixing scan optical unit is set, before described demixing scan optical unit is positioned at human eye 601.
Set gradually quarter wave plate 800 and wave-front corrector 900 on another light path of the second polarization beam splitter prism PBS, 402 beam splitting.
Be provided with half anti-pellicle mirror 1100 between second aperture coupling lens group 1000 and the micro-imaging optical unit, divide two, one light paths connection micro-imaging optical unit, on another minute light path Wavefront sensor 1200 is set light path.
Described micro-imaging lighting unit comprises light source 102, is disposed with collecting objective 110 on its optical axis; Graticle 111; Projection objective 112; Bandpass filter 113.
Optical fiber output laser lighting unit comprises laser beacon 201 and collimator objective 202, and described laser beacon 201 is made up of optical fiber, coupling object lens and semiconductor laser.
Be provided with a transparent retinal structure with phase-type between half-reflecting half mirror 1100 and the micro-imaging optical unit and convert corresponding interference contrast optical unit to the strong and weak image that changes of light intensity.
The interference contrast optical unit includes first half-reflecting half mirror 1301, first completely reflecting mirror 1302, second half-reflecting half mirror 1303, second completely reflecting mirror 1304, compensating plate 1305 and wedge group 1306; Four vertex position settings that described first half-reflecting half mirror 1301, first completely reflecting mirror 1302, second completely reflecting mirror 1304 and second half-reflecting half mirror 1303 are rectangle, wherein two completely reflecting mirror 1302,1304 diagonal angle settings each other, two half-reflecting half mirror 1301,1302 diagonal angle settings each other.Compensating plate 1305 is between first half-reflecting half mirror 1301 and second completely reflecting mirror 1304, and described wedge group 1306 is between first completely reflecting mirror 1302 and second half-reflecting half mirror 1303.
Incident light wave is divided into two halves after by first half-reflecting half mirror 1301, this two-beam ripple is almost completely the same, a branch of light wave reflexes to second half-reflecting half mirror 1303 through compensating plate 1305 backs by second completely reflecting mirror 1304, another Shu Guangbo reflects the back by wedge group 1306 by first completely reflecting mirror 1302, and produced and require laterally moving of distance, be transferred to second half-reflecting half mirror 1303 then.
The demixing scan optical unit comprises first object lens 501 and second object lens 502.Wherein, first object lens 501 and/or second object lens 502 can be done accurate moving.In the present embodiment, choose that first object lens 501 are arranged to fix and second object lens 502 can be done accurate moving.
The micro-imaging optical unit comprises eyeglass head 1401 and little depth field imaging camera lens 1402.
When being used for the device use of retina cell imaging, at first will be (in the present embodiment by the visual acuity chart on the graticle 114 and first object lens 501 in the mobile demixing scan optical unit and/or second object lens 502, move second object lens 502), human eye 601 is carried out diopter regulate.After adjusting is finished, start ADAPTIVE OPTICS SYSTEMS and compensate or proofread and correct by 900 pairs of aberrations of wave-front corrector.Just can on imaging surface 1500, observe retinal images by the micro-imaging optical unit after proofreading and correct end.
For aberration compensation or trimming process, its mechanism is that 401 reflections then focus on the retina 603 by demixing scan optical unit (first object lens 501 and second object lens 502) and human lens through the first polarization beam splitter prism PBS for light beam from optical fiber output laser lighting unit (being made up of laser beacon 201 and collimator objective 202), after retina 603 reflections, also project on the reflecting surface of wave-front corrector 900 through the second polarization beam splitter prism PBS 402 and quarter wave plate 800 through layering scanning optical unit and the first polarization beam splitter prism PBS, 401 backs, wave-front corrector 900 is controlled the face shape of reflecting surface in real time according to the measurement result of 1200 pairs of wavefront of Wavefront sensor, and wave front aberration is compensated or proofreaies and correct.
The structure of laser beacon 201 is made up of optical fiber 213, coupling object lens 212 and semiconductor laser 211 as shown in Figure 2.Be coupled in the fiber core 213 behind the laser process coupling object lens 212 that semiconductor laser 211 gives off, behind the laser spherical wave process collimator objective of fiber core output, become plane wave.
Laser is closed behind the aberration correction, total reflective mirror 300 is withdrawn from light path, micro imaging system just can be worked, its mechanism is the micro-imaging lighting unit graticle 114 that evenly throws light on, the light beam that sees through from graticle 114 focuses on the retina 603 by demixing scan optical unit (first object lens 501 and second object lens 502) and human lens through collimator objective 115 collimation backs, after retina 603 reflection through the layering scanning optical unit and the first polarization beam splitter prism PBS 401, by interference contrast optical unit and micro-imaging optical unit, interference imaging on imaging surface 1500, formation can reflect the image of retina 603 CONSTRUCTED SPECIFICATIONs.Can in conjunction with micro-imaging optical unit (eyeglass head 1401 and little depth field imaging camera lens 1402), just can carry out demixing scan to the retina cell structure and observe this moment by second object lens 502 in the accurate mobile demixing scan optical unit.
At the device that is used for the retina cell imaging, the mechanism of demixing scan optical unit is when micro-imaging optical unit (eyeglass head 1401 and little depth field imaging camera lens 1402) during to the retina blur-free imaging, second object lens 502 in the accurate mobile demixing scan optical unit, the focusing surface that formed by people's refraction of eye body illumination beam this moment also synchronously moves forward and backward in retina, after turning back to the demixing scan optical system, the light beam that is reflected by light beam focal plane place layer forms collimated light beam, incide and connect order object lens 1401 back forms retina layer on its focal plane image, on its imaging surface 1500, form the image of this layer of retina again by little depth field imaging camera lens 1402 backs.Because the little depth field imaging camera lens 1402 imaging depth of field are little, therefore, other rete of retina can not blur-free imaging.
At the device that is used for the retina cell imaging, the mechanism of eliminating veiling glare is after the collimated light beam from light source 102 enters the first polarization beam splitter prism PBS 401, along the P light transmission of paper plane direction vibration, the S light of vertical paper plane direction vibration is reflected and transmits to human eye 601 pupil directions.Because people ocular tissue such as crystalline lens, cornea and some other surface that produces veiling glare do not change the polarisation of light characteristic substantially or change little the polarization reflection of light, therefore incident S light light beam after their reflections still is a S light, when they return the first polarization beam splitter prism PBS 401, reflected away, participate in imaging thereby can not enter in the follow-up imaging system by the first polarization beam splitter prism PBS 401.Because polarized light is behind retinal reflex, light beam loses polarization characteristic, therefore the S light through retinal reflex will lose polarization characteristic, occur the P light component in the reflected light, and can see through the first polarization beam splitter prism PBS 401 and enter in the follow-up imaging system and participate in imaging.As seen the eliminate stray light system that is made of the first polarization beam splitter prism PBS 401 has eliminated the veiling glare that is produced by people ocular tissue such as crystalline lens, cornea and some other surface that produces veiling glare effectively.
At the device that is used for the retina cell imaging, the effect of interference contrast optical unit is to shear from the wavefront of human eye 601, make it to produce shear interference, clearly reflect thereby the power of thin portion structure by light intensity that is transparent retina 603 surfaces of phase characteristics on the optics can be changed.Its working mechanism is that incident light wave is divided into two halves after by first half-reflecting half mirror 1301, and this two-beam ripple is almost completely the same; Light wave to the transmission of second completely reflecting mirror, 1304 directions reflexes to second half-reflecting half mirror 1303 through compensating plate 1305 backs by second completely reflecting mirror 1304, light wave to the transmission of first completely reflecting mirror, 1302 directions reflects the back by wedge group 1306 by first completely reflecting mirror 1302, and produced and require laterally moving of distance, be transferred to second half-reflecting half mirror 1303 then.After the two-beam ripple converges by second half-reflecting half mirror 1303, produced skew between relatively, the two-beam ripple will be interfered on imaging surface 1500.The intensity of interference light intensity depends on phase difference between the two, and the difference in height of two consecutive points on the corresponding retina 603 of this phase difference.Therefore the image on the imaging surface has reflected the CONSTRUCTED SPECIFICATION on the retina 603.
At the device that is used for the retina cell imaging, the micro-imaging optical unit is main optical unit, and other various subdivisions just its essence is in order to improve the micro-imaging optical unit, improve its resolution, make it to reach the image quality of diffraction-limited.
Certainly, the device that is used for the retina cell imaging of the present utility model also can have multiple conversion and remodeling, is not limited to the concrete structure of above-mentioned embodiment.In a word, protection domain of the present utility model should comprise those conspicuous to those skilled in the art conversion or substitute and remodeling.
Claims (7)
1. the device that is used for the retina cell imaging, be used for tissue morphology by the optical system observing human eye retina, it is characterized in that: it comprises micro-imaging lighting unit, optical fiber output laser lighting unit, and be successively set on the first polarization beam splitter prism PBS (401) on the described illuminator optical axis, first aperture coupling lens group (700), the second polarization beam splitter prism PBS (402), second aperture coupling lens group (1000), micro-imaging optical unit; On another light path of described first polarization beam splitter prism PBS (401) beam splitting the demixing scan optical unit is set, it is preceding that described demixing scan optical unit is positioned at human eye (601); Set gradually quarter wave plate (800) and wave-front corrector (900) on another light path of described second polarization beam splitter prism PBS (402) beam splitting; Be provided with half anti-pellicle mirror (1100) between described second aperture coupling lens group (1000) and the micro-imaging optical unit, divide two, one light paths connection micro-imaging optical unit, on another minute light path Wavefront sensor (1200) is set light path.
2. the device that is used for the retina cell imaging according to claim 1, it is characterized in that: described micro-imaging lighting unit comprises light source (102), is disposed with collecting objective (110), graticle (111), projection objective (112), bandpass filter (113) on its optical axis.
3. the device that is used for the retina cell imaging according to claim 1, it is characterized in that: described optical fiber output laser lighting unit comprises laser beacon (201) and collimator objective (202), and described laser beacon (201) is made up of optical fiber, coupling object lens and semiconductor laser.
4. the device that is used for the retina cell imaging according to claim 1 is characterized in that: be provided with a transparent retinal structure with phase-type between described half-reflecting half mirror (1100) and the micro-imaging optical unit and convert the corresponding interference contrast optical unit with the strong and weak image that changes of light intensity to.
5. the device that is used for the retina cell imaging according to claim 4 is characterized in that: described interference contrast optical unit includes first half-reflecting half mirror (1301), first completely reflecting mirror (1302), second half-reflecting half mirror (1303), second completely reflecting mirror (1304), compensating plate (1305) and wedge group (1306); Four vertex position settings that described first half-reflecting half mirror (1301), first completely reflecting mirror (1302), second completely reflecting mirror (1304) and the two or two half-reflecting half mirror (1303) are rectangle, wherein two completely reflecting mirrors (1302,1304) diagonal angle setting each other, two half-reflecting half mirrors (1301,1302) diagonal angle setting each other; Described compensating plate (1305) is positioned between first half-reflecting half mirror (1301) and second completely reflecting mirror (1304), and described wedge group (1306) is positioned between first completely reflecting mirror (1302) and second half-reflecting half mirror (1303); Incident light wave is divided into two halves after by first half-reflecting half mirror (1301), this two-beam ripple is almost completely the same, a branch of light wave reflexes to second half-reflecting half mirror (1303) through compensating plate (1305) back by second completely reflecting mirror (1304), another Shu Guangbo reflects the back by wedge group (1306) by first completely reflecting mirror (1302), and produced and require laterally moving of distance, be transferred to second half-reflecting half mirror (1303) then.
6. the device that is used for the retina cell imaging according to claim 1, it is characterized in that: described demixing scan optical unit comprises first object lens (501) and second object lens (502), and described first object lens (501) and/or second object lens (502) can be done accurate moving.
7. the device that is used for the retina cell imaging according to claim 1 is characterized in that: described micro-imaging optical unit comprises eyeglass head (1401) and little depth field imaging camera lens (1402).
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| CNU2007200367942U CN201042430Y (en) | 2007-04-25 | 2007-04-25 | Device for retina cell imaging |
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| Application Number | Priority Date | Filing Date | Title |
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| CNU2007200367942U CN201042430Y (en) | 2007-04-25 | 2007-04-25 | Device for retina cell imaging |
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Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101966076A (en) * | 2010-09-29 | 2011-02-09 | 中山联合光电科技有限公司 | Forward type annular lighting system with digital lens |
| CN102596127A (en) * | 2009-07-29 | 2012-07-18 | 爱尔康蓝斯克斯股份有限公司 | Optical system for ophthalmic surgical laser |
| CN102612353A (en) * | 2009-07-29 | 2012-07-25 | 爱尔康蓝斯克斯股份有限公司 | Optical system for ophthalmic surgical laser |
| CN103091823A (en) * | 2011-10-31 | 2013-05-08 | 徕卡显微系统(瑞士)股份公司 | Illumination device for a stereomicroscope, in particular a surgical microscope |
| CN103598872A (en) * | 2013-11-28 | 2014-02-26 | 温州雷蒙光电科技有限公司 | Fundus camera |
| CN105411524A (en) * | 2015-12-07 | 2016-03-23 | 温州医科大学眼视光器械有限公司 | Pupil detection device |
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2007
- 2007-04-25 CN CNU2007200367942U patent/CN201042430Y/en not_active Expired - Lifetime
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102596127A (en) * | 2009-07-29 | 2012-07-18 | 爱尔康蓝斯克斯股份有限公司 | Optical system for ophthalmic surgical laser |
| CN102612353A (en) * | 2009-07-29 | 2012-07-25 | 爱尔康蓝斯克斯股份有限公司 | Optical system for ophthalmic surgical laser |
| CN102612353B (en) * | 2009-07-29 | 2015-10-07 | 爱尔康蓝斯克斯股份有限公司 | For the optical system of ophthalmic surgical laser |
| CN101966076A (en) * | 2010-09-29 | 2011-02-09 | 中山联合光电科技有限公司 | Forward type annular lighting system with digital lens |
| CN101966076B (en) * | 2010-09-29 | 2012-03-28 | 中山联合光电科技有限公司 | Forward type annular lighting system with digital lens |
| CN103091823A (en) * | 2011-10-31 | 2013-05-08 | 徕卡显微系统(瑞士)股份公司 | Illumination device for a stereomicroscope, in particular a surgical microscope |
| CN103598872A (en) * | 2013-11-28 | 2014-02-26 | 温州雷蒙光电科技有限公司 | Fundus camera |
| CN105411524A (en) * | 2015-12-07 | 2016-03-23 | 温州医科大学眼视光器械有限公司 | Pupil detection device |
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