CN203914868U - Bifocus is deutomerite synchronous at the moment - Google Patents
Bifocus is deutomerite synchronous at the moment Download PDFInfo
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- CN203914868U CN203914868U CN201420293123.4U CN201420293123U CN203914868U CN 203914868 U CN203914868 U CN 203914868U CN 201420293123 U CN201420293123 U CN 201420293123U CN 203914868 U CN203914868 U CN 203914868U
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Abstract
The utility model discloses a kind of bifocus deutomerite synchronous at the moment, what it comprised light source, and received the light beam of light source outgoing and be divided into the fiber coupler of two-beam, is connected with fiber coupler be respectively used to receive fiber coupler goes out reference arm and the sample arm of the two-beam of ejaculation, reference arm comprises the reference arm lens that are connected with fiber coupler and the reference arm reflecting mirror being connected with reference arm lens, and bifocus at the moment deutomerite synchronous also comprises the detector being connected with fiber coupler.The collimate in parallel light beam of incident can be divided into two-beam by the bifocal lens beam splitter of introducing in sample arm, make light beam focus on people's anterior ocular segment (cornea), another light beam focuses on people's oculi posterior segment (retina), the bifocal lens beam splitter light splitting technology adopting can focus on and scan people's oculi posterior segment and people's anterior ocular segment simultaneously, and completes the photodetection to inverse signal.
Description
Technical field:
This utility model relates to a kind of bifocus deutomerite synchronous at the moment, relates in particular to a kind of bifocus based on bifocal lens beam splitter deutomerite synchronous at the moment, and it belongs to Optical Coherence Tomography Imaging Technology field.
Background technology:
Optical coherent chromatographic imaging (optical coherence tomography, OCT) technology is a kind of biomedical optical image technology of high sensitivity, high-resolution of Noninvasive.OCT technology is based on low coherence interference technology, utilize the interference light reflecting from reference arm and sample arm, in conjunction with the advantage of Heterodyne detect and confocal imaging, through signals collecting and date processing, rebuild the tomographic map of biological tissue samples inside, can reflect the information such as microstructure, blood flow, birefringence of biological tissue, realize biology interior structure and physiological function in imaging body, non-invasive.OCT technology can comprise that live body sample carries out two dimension or three-dimensional imaging that resolution exceedes 10 microns to biological sample.
OCT technology can be divided into time domain OCT and Fourier OCT, and spectral coverage OCT (Spectral domain OCT, SDOCT) and frequency sweep OCT (Swept source OCT, SSOCT) are two kinds of ways of realization of Fourier domain OCT technology.Typical SDOCT system is based on spectral domain interference technique: reflection and scattering from the light of broadband LASER Light Source outgoing through sample, the light and the reference light that return interfere, then interference light lead-in light spectrometer is gathered the spectrum of interference signal, the interference spectrum signal detecting is carried out a series of date processing and can be reconstructed the tomographic map of biological sample.When SDOCT technology is applied to eyes imaging, because the overlayable investigation depth of SDOCT generally only has 4mm left and right, and the full-length of human eye is calculated generally at 28mm to 35mm with aerial optical length, therefore use typical SDOCT can only carry out at twice people's anterior ocular segment (cornea on surface) and the scanning of people's oculi posterior segment (retina).Usually, after the cornea on scanning human eye surface, the light that focuses on cornea need to be become to directional light, this directional light is focused on retina and could be scanned human eye retina again by the crystalline lens of human eye.The process that this focused light is transformed to directional light can realize by removing lens, or adopts more complicated double beam system respectively people's anterior ocular segment and oculi posterior segment scanning (as No. 7400410B2, US Patent No.) to be completed to the imaging to joint before and after human eye.In the OCT system of extensive use at present, consider the factors such as production cost, the OCT system that focused light is transformed to directional light is comparatively common, in this system, in order to ensure synchronizeing of interference signal and twice sweep signal, between twice sweep, need to move with reference to the reflecting mirror of arm the distance of a human eye degree of depth.Therefore traditional SDOCT system, in the time of the full eye imaging that completes human eye, not only has delay between twice imaging, can not accomplish imaging simultaneously, and need to regulate light path in sample arm and reference arm, wastes time and energy.And remove with mobile light path in optical element all can cause little disturbance to system.Particularly, because human eye can move to some extent between twice sweep, during therefore by the synthetic eye image of the image of twice detection, just may produce the situation that eye cornea is not corresponding with retina.And the design of double light path is applied in the sample arm of OCT system with the different parts imaging to eyes respectively (as No. 7400410B2, US Patent No.), adopting selector switch to switch two light paths makes two-beam alternately be incident upon the method for the different parts of human eye, this design has solved this problem that needs a human eye depth distance of mobile reference arm reflecting mirror in typical OCT, but do not accomplish that two parts light carries out imaging to joint before and after human eye simultaneously, cannot eliminate between twice measurement because human eye rotates or the mobile error of bringing.Thisly because moving the problem causing, human eye there will be too in other forms of OCT.Therefore, how on the basis of typical OCT system, with less change and comparatively easy method, the cornea to human eye surface and inner retina scan simultaneously to make OCT system, realize high sensitivity, the imaging of high-resolution full eye, just become a general objective of OCT imaging technique development.
Utility model content:
This utility model provides a kind of bifocus deutomerite synchronous at the moment, and it can carry out high sensitivity, high-resolution imaging to joint internal structure before and after human eye simultaneously.
This utility model adopts following technical scheme: a kind of bifocus is deutomerite synchronous at the moment, being respectively used to of comprising light source, receive the light beam of light source outgoing and be divided into the fiber coupler of two-beam, be connected with fiber coupler receives fiber coupler and goes out reference arm and the sample arm of the two-beam of ejaculation, described reference arm comprises the reference arm lens that are connected with fiber coupler and the reference arm reflecting mirror being connected with reference arm lens, and described bifocus at the moment deutomerite synchronous also comprises the detector being connected with fiber coupler.
Further, described sample arm is by optical fiber, optical fiber collimator, laser beam expander, bifocal lens beam splitter, X scanning galvanometer, Y scanning galvanometer, first lens, the second lens composition, described optical fiber is connected on optical fiber collimator, laser beam expander is connected on optical fiber collimator, bifocal lens beam splitter is close proximity to described laser beam expander and places, described bifocal lens beam splitter center equals the focal length of bifocal lens beam splitter to the distance at X scanning galvanometer center, and the central point of described X scanning galvanometer central point and bifocal lens beam splitter is contour in same level, the central point of described X scanning galvanometer equals the focal length of described first lens to the distance sum between the central point of first lens to the central point of the distance between the central point of Y scanning galvanometer and Y scanning galvanometer, and the central point of the central point of described Y scanning galvanometer and first lens and the second lens is contour in same level, distance between first lens and the second lens is the focal length sum of first lens and the second lens.
Further, described X scanning galvanometer is identical with the structure of Y scanning galvanometer, and described X scanning galvanometer and Y scanning galvanometer be by reflecting mirror, rotating shaft and galvanometer motor composition, and wherein galvanometer motor is connected with rotating shaft, and rotating shaft is connected with reflecting mirror.
Further, described bifocal lens beam splitter is lens stop, described lens stop is made up of mirror holder, ring-type glass plate, adapter ring and the 3rd lens, and described ring-type glass plate is fixed in mirror holder, and described the 3rd lens are fixed on the inside of ring-type glass plate by adapter ring.
Further, described bifocal lens beam splitter is birefringence triplet, and the calcite biconcave lens in the middle of described birefringence triplet is positioned at by forms with the convex lens of the birefringence triplet that is positioned at both sides.
Further, described light source is wideband light source or swept light source.
Further, described detector is spectrogrph or point probe.
The utlity model has following beneficial effect:
1). it is the focused beam and parallel collimated beam two parts of propagating in the same direction that described bifocal lens beam splitter can make collimate in parallel optical beam transformation incident thereon, this collimate in parallel light beam is parallel incident human eye after the whole light path of sample arm, process human lens Refractive focusing is on the retina of people's intraccular part, this focused beam focuses on the cornea on human eye surface after the whole light path of sample arm, the bifocal lens beam splitter light splitting technology adopting can focus on and scan people's oculi posterior segment and people's anterior ocular segment simultaneously, and complete the photodetection to inverse signal, solve in OCT system in the past eye cornea and retina imaging successively, time delay between twice imaging causes that human eye moves the problem causing, in the application of optical coherence tomography system, have great importance,
2). the change to typical optical coherence tomography system is less, be convenient to implement, compared with prior art, described bifocal lens beam splitter light splitting technology in the time measuring without change the focal position of light beam by adding or removing optics original paper in light path, imaging for diverse location place once completes, not only save Measuring Time but also reduced artificial operate miss, significant in actual applications;
3). by the improvement to optical coherence tomography system, the sample that the meeting that can have appropraite condition to other is equally moved carries out inside and outside imaging simultaneously, has solved the inaccurate problem of imaging causing due to mobile.
Brief description of the drawings:
Fig. 1 be this utility model bifocus at the moment deutomerite synchronous be applied in the structural representation in spectral coverage OCT system.
Fig. 2 is this utility model bifocus structural representation (wherein bifocal beam splitter is lens stop) of sample arm in deutomerite synchronous at the moment.
Fig. 3 is this utility model bifocus structural representation (wherein bifocal beam splitter is birefringence triplet) of sample arm in deutomerite synchronous at the moment.
Fig. 4 is the structural representation of lens stop in Fig. 2.
Fig. 5 is the structural representation of birefringence triplet in Fig. 3.
Fig. 6 is human eyes structure schematic diagram.
Fig. 7 be this utility model bifocus at the moment deutomerite synchronous be applied in the structural representation in frequency sweep OCT system.
Wherein:
1, light source (swept light source or wideband light source); 2, fiber coupler; 3, reference arm; 4, reference arm lens; 5, reference arm reflecting mirror; 6, sample arm; 7, detector; 8, computer; 9, optical fiber; 10, optical fiber collimator; 11, laser beam expander; 12, bifocal lens beam splitter (lens stop); 13, X scanning galvanometer; 14, Y scanning galvanometer; 15, first lens; 16, the second lens; 17, bifocal lens beam splitter (birefringence triplet); 18, mirror holder; 19, ring-type glass plate; 20, adapter ring; 21, the 3rd lens; 22, the convex lens of birefringence triplet; 23, calcite biconcave lens; 25, cornea; 26, crystalline lens; 27, vitreous body; 28, retina; 29, human eye.
Detailed description of the invention:
This utility model bifocus at the moment deutomerite synchronous being respectively used to of comprising light source 1, receive the light beam of light source 1 outgoing and be divided into the fiber coupler 2 of two-beam, be connected with fiber coupler 2 receives fiber coupler 2 and goes out reference arm 3 and the sample arm 6 of the two-beam of ejaculation, reference arm 3 comprises the reference arm lens 4 that are connected with fiber coupler 2 and the reference arm reflecting mirror 5 being connected with reference arm lens 4, wherein this utility model bifocus at the moment deutomerite synchronous also comprise the detector 7 being connected with fiber coupler 2.
Wherein sample arm 6 is by optical fiber 9, optical fiber collimator 10, laser beam expander 11, bifocal lens beam splitter 12, X scanning galvanometer 13, Y scanning galvanometer 14, first lens 15, the second lens 16 form, optical fiber 9 is connected on optical fiber collimator 10, laser beam expander 11 is connected on optical fiber collimator 10, bifocal lens beam splitter 12 is placed near laser beam expander 11, bifocal lens beam splitter 12 centers equal the focal length of bifocal lens beam splitter 12 to the distance at X scanning galvanometer 13 centers, and the central point of X scanning galvanometer 13 central points and bifocal lens beam splitter 12 is contour in same level, the central point of X scanning galvanometer 13 equals the focal length of first lens 15 to the distance sum between the central point of first lens 15 to the central point of the distance between the central point of Y scanning galvanometer 14 and Y scanning galvanometer 14, and the central point of the central point of Y scanning galvanometer 14 and first lens 15 and the second lens 16 is contour in same level, distance between first lens 15 and the second lens 16 is the focal length sum of first lens 15 and the second lens 16.
Wherein X scanning galvanometer 13 and Y scanning galvanometer 14, by reflecting mirror, rotating shaft and galvanometer motor composition, can be separately implemented at by swaying the beam flying of directions X and Y-direction.
In this utility model, bifocal lens beam splitter 12 can be a kind of lens stop, it can also be a kind of birefringence triplet, wherein lens stop 12 is made up of mirror holder 18, ring-type glass plate 19, adapter ring 20 and the 3rd lens 21, ring-type glass plate 19 is fixed in mirror holder 18, and the 3rd lens 21 are fixed on the inside of ring-type glass plate 19 by adapter ring 20.Calcite biconcave lens 23 in the middle of birefringence triplet 17 is positioned at by one forms with the convex lens 22 of the birefringence triplet that is positioned at both sides.
Below in conjunction with two specific embodiments set forth this utility model bifocus at the moment deutomerite synchronous acquisition method and be applied to the formation method in imaging system.
Embodiment mono-:
Please refer to shown in Fig. 1, this utility model based on bifocus at the moment deutomerite synchronous acquisition technology be applied in spectral coverage OCT system.Light source 1 is now wideband light source, and detector 7 is spectrogrph.
The light beam of wideband light source 1 outgoing is incident to fiber coupler 2 and is divided into two bundles, this two-beam is incident reference arm 3 and sample arm 6 respectively, the light beam that is imported sample arm 6 by optical fiber 9 is transformed to collimation directional light after optical fiber collimator 10 collimates, expand through laser beam expander 11, this collimation directional light spot size is expanded to suitable with bifocal lens beam splitter 12 sizes.Bifocal lens beam splitter 12 can be transformed into collimate in parallel light directional light and the focused light propagated in the same direction, this collimated light beam projects on X scanning galvanometer 13, parallel incident first lens 15 after reflection by X scanning galvanometer 13 and Y scanning galvanometer 14, because the distance of first lens 15 and the second lens 16 is the focal length sum of two lens, according to the thin-lens equation, be still directional light from the light of the outgoing of the second lens 16, and from the spot size of the second saturating 16 outgoing and the spot size of incident first lens 15 and first lens 15, the focal length of the second lens 16 is relevant.By choosing first lens 15 and second lens 16 of proper focal length, make this directional light incident human eye focus on and be incident upon human eye retina 28 places through human lens 26.The focused light that sees through the 12 rear formation of bifocal lens beam splitter focuses on X scanning galvanometer 13, be incident upon on first lens 15 through the reflection of Y scanning galvanometer 14, because the central point of X scanning galvanometer 13 equals the focal length of first lens 15 to the distance sum between the central point of first lens 15 to the central point of the distance between the central point of Y scanning galvanometer 14 and Y scanning galvanometer 14, so after first lens 15 refractions, project on the second lens 16 with directional light, focus on eye cornea 25 places through this segment beam of refraction of the second lens 16.
The light beam that enters sample arm 6 is divided into two parts by bifocal lens beam splitter 12, a part of light through sample arm light path focus on be radiated at people's anterior ocular segment place, another part parallel light incident human eye, through human lens Refractive focusing at people's oculi posterior segment place.This two parts light is realized respectively the beam flying of directions X and Y-direction by X scanning galvanometer 13 and swaying of Y scanning galvanometer 14, people's anterior ocular segment and oculi posterior segment is carried out to the detection of directions X and Y-direction simultaneously.By with interference effect formation interfering beam from reference arm 3 reflection and back scattered reference light, spectrogrph carries out photodetection to interfering beam, and detection data is transferred to computer, through computer 8 programs, data are separated and are in harmonious proportion data and image processing and restore the tomographic map of the internal structure of people's anterior ocular segment and oculi posterior segment, realization is to the imaging to people's anterior ocular segment and the high-resolution two dimension of oculi posterior segment internal structure high sensitivity or three-dimensional simultaneously.
Wherein, spectrogrph is high spectral resolution spectrogrph, and high spectral resolution spectrogrph imaging depth is long, has larger investigative range.When this spectrogrph is applied in spectral coverage OCT system, can be Polaroid to the interfering beam of formation from people's anterior ocular segment and oculi posterior segment return, carry out secondary imaging without the reference arm reflecting mirror by mobile reference arm.In existing OCT system, adopt common spectrogrph, imaging depth is limited, generally can only be near interference light imaging zero optical path difference, and investigation depth is shallow.OCT system in the past need provide the poor reference light of light aplanatism returning with people's anterior ocular segment and oculi posterior segment to carry out secondary imaging by mobile reference arm reflecting mirror.Compared with existing OCT system, the bifocus of this utility model based on bifocal lens beam splitter at the moment deutomerite synchronous acquisition technology can once complete imaging to joint before and after human eye without mobile reference arm reflecting mirror.
Embodiment bis-:
Please refer to shown in Fig. 7, this utility model based on bifocus at the moment deutomerite synchronous acquisition technology be applied in frequency sweep OCT system.Light source 1 is now swept light source, and detector 7 is point probe.
The light beam of swept light source 1 outgoing is incident to fiber coupler 2 and is divided into two bundles, this two-beam is incident reference arm 3 and sample arm 6 respectively, the light beam that is imported sample arm 6 by optical fiber 9 is transformed to collimation directional light after optical fiber collimator 10 collimates, expand through laser beam expander 11, this collimation directional light spot size is expanded to suitable with bifocal lens beam splitter 12 sizes.Bifocal lens beam splitter 12 can be transformed into directional light and the focused light propagated in the same direction by collimate in parallel light.This collimated light beam projects on X scanning galvanometer 13, parallel incident first lens 15 after reflection by X scanning galvanometer 13 and Y scanning galvanometer 14, because the distance of first lens 15 and the second lens 16 is the focal length sum of two lens, according to the thin-lens equation, be still directional light from the light of the outgoing of the second lens 15, by choosing the first saturating of proper focal length, 15 and second lens 16, make this directional light incident human eye focus on and be incident upon human eye retina 28 places through human lens 26.The focused light that sees through the 12 rear formation of bifocal lens beam splitter focuses on X scanning galvanometer 13, be incident upon on first lens 15 through the reflection of Y scanning galvanometer 14, because the central point of X scanning galvanometer 13 equals the focal length of first lens 15 to the distance sum between the central point of first lens 15 to the central point of the distance between the central point of Y scanning galvanometer 14 and Y scanning galvanometer 14, so after first lens 15 refractions, project on the second lens 16 with directional light, focus on eye cornea 25 places through this segment beam of refraction of the second lens 16.
The light beam that enters sample arm 6 is divided into two parts by bifocal lens beam splitter 12, and a part of light focuses on and is radiated at people's anterior ocular segment place through sample arm light path; Another part parallel light incident human eye, through human lens Refractive focusing at people's oculi posterior segment place.This two parts light is realized respectively the beam flying of directions X and Y-direction by X scanning galvanometer 13 and swaying of Y scanning galvanometer 14, people's anterior ocular segment and oculi posterior segment is carried out to the detection of directions X and Y-direction simultaneously.By with interference effect formation interfering beam from reference arm 3 reflection and back scattered reference light, point probe carries out photodetection to interfering beam, and detection data is transferred to computer, through computer program, data are separated and are in harmonious proportion data and image processing and restore the tomographic map of the internal structure of people's anterior ocular segment and oculi posterior segment, realization is to the imaging to people's anterior ocular segment and the high-resolution two dimension of oculi posterior segment internal structure high sensitivity or three-dimensional simultaneously.
The light beam of swept light source outgoing is the homogeneous beam of very narrow bandwidth, and the outgoing successively of the light beam of each different-waveband, because narrow bandwidth light beam penetration power is strong, therefore adopts swept light source to have investigation depth as the OCT system of light source long, the feature that investigative range is wide.Wherein detector is point probe,, forms interference light and incide point probe after reflection and scattering through light splitting from the light beam of swept light source outgoing, obtains the tomographic map of two dimension or people's anterior ocular segment of three-dimensional and the internal structure of oculi posterior segment by data and image processing.This kind of frequency sweep OCT system and above-mentioned spectral coverage OCT system do not need the reference arm reflecting mirror of mobile reference arm in the time of work simultaneously, operate miss is little, and to people's anterior ocular segment and once imaging simultaneously of oculi posterior segment, income earner's anterior ocular segment and oculi posterior segment image degree of correspondence are high, not because eyeball moves the error causing.
In above-described embodiment one and embodiment bis-, bifocal lens beam splitter 12 can be a kind of lens stop or be a kind of birefringence triplet.In the time that bifocal lens beam splitter 12 is lens stop, the light beam that enters sample arm 6 imports optical fiber collimator 10 through optical fiber 9 and collimates, and the collimated light beam collimating through optical fiber collimator 10 expands the cross section of light beam to suitable with the size of lens stop ring-type glass plate 19 place, outer ring circles by laser beam expander 11.The light beam that sees through lens stop ring-type glass plate 19 parts becomes annular collimate in parallel to project on X scanning galvanometer 13, after reflecting by X scanning galvanometer 13 and Y scanning galvanometer 14, be incident in first lens 15 with directional light, because the distance of first lens 15 and the second lens 16 is the focal length sum of two lens, according to the thin-lens equation, be still directional light from the light of the outgoing of the second lens 16.And relevant from the focal length of second spot size of lens 16 outgoing and the spot size of incident first lens 15 and first lens 15, the second lens 16.By choosing first lens 15 and second lens 16 of proper focal length, make this directional light incident human eye focus on and be incident upon human eye retina 28 places through human lens 26.The light that sees through lens stop the 3rd lens 21 parts focuses on X scanning galvanometer 13, be incident upon on first lens 15 through the reflection of Y scanning galvanometer 14, because the central point of X scanning galvanometer 13 equals the focal length of first lens 15 to the distance sum between the central point of first lens 15 to the central point of the distance between the central point of Y scanning galvanometer 14 and Y scanning galvanometer 14, so after first lens 15 refractions, project on the second lens 16 with directional light, focus on eye cornea 25 places through this segment beam of refraction of the second lens 16.
In the time that bifocal lens beam splitter 12 is a kind of birefringence triplet, the light beam that enters sample arm imports optical fiber collimator 10 through optical fiber 9 and collimates, and the collimated light beam collimating through optical fiber collimator 10 expands the cross section of light beam to suitable with the size of birefringence triplet by laser beam expander 11.See through the light beam of birefringence triplet because the birefringent characteristic of calcite biconcave lens 23 is divided into collimated light beam (o light) and the focused beam (e light) propagated in the same direction, this collimated light beam (o light) projects on X scanning galvanometer 13, parallel incident first lens 15 after reflection by X scanning galvanometer 13 and Y scanning galvanometer 14, because the distance of first lens 15 and the second lens 16 is the focal length sum of two lens, according to the thin-lens equation, be still directional light from the light of the outgoing of the second lens 16.And relevant from the focal length of second spot size of lens 16 outgoing and the spot size of incident first lens 15 and first lens 15, the second lens 16.By choosing first lens 15 and second lens 16 of proper focal length, make this directional light incident human eye focus on and be incident upon human eye retina 28 places through human lens 26.Focus on X scanning galvanometer 13 from the focused beam (e light) of birefringence triplet outgoing, be incident upon on first lens 15 through the reflection of Y scanning galvanometer 14, because the central point of X scanning galvanometer 13 equals the focal length of first lens 15 to the distance sum between the central point of first lens 15 to the central point of the distance between the central point of Y scanning galvanometer 14 and Y scanning galvanometer 14, so after first lens 15 refractions, project on the second lens 16 with directional light, focus on eye cornea 25 places through this segment beam of refraction of the second lens 16.
This utility model bifocus is deutomerite synchronous at the moment, realize high sensitivity, high-resolution human eye front and back joint synchronous imaging by introduce bifocal lens beam splitter in sample arm, bifocal lens beam splitter can be divided into two-beam by the collimate in parallel light beam of incident, wherein still collimate in parallel outgoing of light beam, another light beam focuses on the back focus place of bifocal lens beam splitter.By being positioned at bifocal lens beam splitter light path afterwards in sample arm, finally make light beam focus on people's anterior ocular segment (cornea), another light beam focuses on people's oculi posterior segment (retina).The sample light returning from the reflection of the forward and backward joint of human eye and scattering is through photodetection, the processing of signal solution mediation image, can form the high-definition picture of people's anterior ocular segment and oculi posterior segment simultaneously, realize synchronously high sensitivity, the high-resolution imaging to joint internal structure before and after human eye.In the application of optical coherence tomography system, have great importance.
The above is only preferred implementation of the present utility model; should be understood that; for those skilled in the art, under the prerequisite that does not depart from this utility model principle, can also make some improvement, these improve and also should be considered as protection domain of the present utility model.
Claims (7)
1. bifocus deutomerite synchronous at the moment, it is characterized in that: comprise light source (1), receive the light beam of light source (1) outgoing and be divided into the fiber coupler (2) of two-beam, being respectively used to of being connected with fiber coupler (2) receives reference arm (3) and the sample arm (6) of the two-beam that fiber coupler (2) goes out to penetrate, described reference arm (3) comprises the reference arm lens (4) that are connected with fiber coupler (2) and the reference arm reflecting mirror (5) being connected with reference arm lens (4), described bifocus at the moment deutomerite synchronous also comprises the detector (7) being connected with fiber coupler (2).
2. bifocus as claimed in claim 1 deutomerite synchronous at the moment, it is characterized in that: described sample arm (6) is by optical fiber (9), optical fiber collimator (10), laser beam expander (11), bifocal lens beam splitter (12), X scanning galvanometer (13), Y scanning galvanometer (14), first lens (15), the second lens (16) composition, described optical fiber (9) is connected on optical fiber collimator (10), laser beam expander (11) is connected on optical fiber collimator (10), bifocal lens beam splitter (12) is close proximity to described laser beam expander (11) and places, described bifocal lens beam splitter (12) center equals the focal length of bifocal lens beam splitter (12) to the distance at X scanning galvanometer (13) center, and the central point of described X scanning galvanometer (13) central point and bifocal lens beam splitter (12) is contour in same level, the central point of described X scanning galvanometer (13) equals the focal length of described first lens (15) to the distance sum between the central point of first lens (15) to the central point of the distance between the central point of Y scanning galvanometer (14) and Y scanning galvanometer (14), and the central point of the central point of described Y scanning galvanometer (14) and first lens (15) and the second lens (16) is contour in same level, distance between first lens (15) and the second lens (16) is the focal length sum of first lens (15) and the second lens (16).
3. bifocus as claimed in claim 2 deutomerite synchronous at the moment, it is characterized in that: described X scanning galvanometer (13) is identical with the structure of Y scanning galvanometer (14), and described X scanning galvanometer (13) and Y scanning galvanometer (14) are by reflecting mirror, rotating shaft and galvanometer motor composition, wherein galvanometer motor is connected with rotating shaft, and rotating shaft is connected with reflecting mirror.
4. bifocus as claimed in claim 3 deutomerite synchronous at the moment, it is characterized in that: described bifocal lens beam splitter (12) is lens stop, described lens stop is made up of mirror holder (18), ring-type glass plate (19), adapter ring (20) and the 3rd lens (21), described ring-type glass plate (19) is fixed in mirror holder (18), and described the 3rd lens (21) are fixed on the inside of ring-type glass plate (19) by adapter ring (20).
5. bifocus as claimed in claim 3 deutomerite synchronous at the moment, it is characterized in that: described bifocal lens beam splitter (12) is birefringence triplet, by one, the calcite biconcave lens (23) in the middle of being positioned at and the convex lens (22) that is positioned at the birefringence triplet of both sides form described birefringence triplet.
6. the deutomerite synchronous at the moment of the bifocus described in claim 4 or 5, is characterized in that: described light source (1) is wideband light source or swept light source.
7. the deutomerite synchronous at the moment of the bifocus described in claim 4 or 5, is characterized in that: described detector (7) is spectrogrph or point probe.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105411521A (en) * | 2015-12-07 | 2016-03-23 | 温州医科大学眼视光器械有限公司 | Crystalline lens image detection device |
| CN107320066A (en) * | 2017-06-30 | 2017-11-07 | 执鼎医疗科技（杭州）有限公司 | A kind of eyeground OCT image system of shared reference arm |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105411521A (en) * | 2015-12-07 | 2016-03-23 | 温州医科大学眼视光器械有限公司 | Crystalline lens image detection device |
| CN107320066A (en) * | 2017-06-30 | 2017-11-07 | 执鼎医疗科技（杭州）有限公司 | A kind of eyeground OCT image system of shared reference arm |
| CN107320066B (en) * | 2017-06-30 | 2023-09-15 | 执鼎医疗科技（杭州）有限公司 | Fundus OCT imaging system sharing reference arm |
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