CN203885475U - Multifunctional ophthalmologic measurement device - Google Patents
Multifunctional ophthalmologic measurement device Download PDFInfo
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- CN203885475U CN203885475U CN201420291638.0U CN201420291638U CN203885475U CN 203885475 U CN203885475 U CN 203885475U CN 201420291638 U CN201420291638 U CN 201420291638U CN 203885475 U CN203885475 U CN 203885475U
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- 238000001514 detection method Methods 0.000 claims abstract description 6
- 210000000695 crystalline len Anatomy 0.000 claims description 101
- 230000005540 biological transmission Effects 0.000 claims description 64
- 210000004087 cornea Anatomy 0.000 claims description 36
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- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
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Abstract
The utility model discloses a multifunctional ophthalmologic measurement device. The multifunctional ophthalmologic measurement device comprises an OCT system light source, an optical fiber coupler, a detection system, a control system, a sample arm component and a reference arm assembly. The sample arm component comprises a collimating mirror and an anterior segment and posterior segment scanning component. The reference arm assembly comprises a reference arm optical path lens and a reference arm reflecting mirror. An optical distance compensation module is arranged on a first optical axis between the collimating mirror and the anterior segment and posterior segment scanning component or a second optical axis between the reference arm optical path lens and the reference arm reflecting mirror and is used in cooperation with the anterior segment and posterior segment scanning component to change the optical distance of an OCT system to carry out OCT imaging on different portions of the human eyes and achieve OCT imaging switching between the different portions of the human eyes. By means of the multifunctional ophthalmologic measurement device, numerous data of the human eyes can be obtained through one-time measurement, so that the working efficiency is improved and the cost is lowered.
Description
Technical field
This utility model relates to optoelectronic areas, relates in particular to a kind ofly can carry out to human eye different parts the OCT system of handover measurement.
Background technology
Nowadays the old people who suffers from cataract of eyes is more and more, and transplanting artificial intraocular lenses is the cataractous effective scheme of now widely used treatment.But artificial intraocular lenses's calculating is more to needed parameter request, as white distance and pupil diameter etc. are grown, arrived in vain to cornea front and rear surfaces curvature, corneal thickness, anterior chamber depth, lens thickness, crystalline lens front and rear surfaces curvature, axis oculi.The parameter of measuring is more, but after often needing several kinds of medical equipment to detect, could obtain above-mentioned partial data.
Optical coherent chromatographic imaging (OCT, Optical Coherence Tomography) be a kind of emerging optical image technology, with respect to traditional clinical imaging means, have that resolution is high, image taking speed is fast, the advantage such as radiationless damage, moderate cost and compact conformation, be the important potential instrument of basic medical research and clinical diagnostic applications.Current, in multiple optical Ophthalmologic apparatus, for the OCT device of ophthalmologic examination and treatment, become the indispensable Ophthalmologic apparatus of eye disease diagnosis.
Patent Application Publication 200710020707.9 discloses a kind of OCT of utilization and has measured the long measuring method of axis oculi.Although the method can realize the measurement of the axiallength of human eye and various living animals, there are following two shortcomings in the method: 1, and the mobile probe of employing motor, realizes the adjusting of light path, thereby realizes the imaging on cornea and optical fundus.And motor moves forward and backward and needs the regular hour, before and after cannot realizing, joint switches and realtime imaging fast, adds that the eyes of measurand can be shaken, and makes to measure axiallength inaccurate, and error is larger; 2. due to cornea and optical fundus structure difference, adopt same probe all to focus in these two positions, cause image quality poor, this is the unavoidable defect of this method.
And technology before can realize joint signal before and after quick handover measurement, but OCT imaging that cannot Polaroid acquisition human eye diverse location place.Especially during the measurement of crystalline lens front and rear surfaces curvature, if adopt when homogeneous is measured, due to eye movement, proofread and correct inaccurately, just cannot accurately measure crystalline lens front and rear surfaces curvature signal.Because the investigation depth of frequency domain OCT system is not enough at present, cannot directly obtain from eye cornea to crystalline lens rear surface the OCT image of so large depth bounds.If adopt segmentation, gradation to measure, obtained the OCT image of crystalline lens front and rear surfaces, now, because gradation is measured, people's eye movement etc. factor, must cause crystalline lens front and rear surfaces cannot carry out refraction correction accurately, thereby cannot obtain the accurate curvature of crystalline lens front and rear surfaces.
Utility model content
This utility model provides a kind of multi-functional ophthalmology measuring device and measuring method, and its object is to solve ophthalmic medical measuring device and can not realizes once gathering human eye different parts is carried out respectively to the defect of OCT imaging.
The technical solution of the utility model:
A multi-functional ophthalmology measuring device, comprises OCT system source, fiber coupler, detection system, control system, sample arm parts and reference arm assembly; Described OCT system source provides incident illumination to sample arm parts and reference arm assembly respectively through described fiber coupler, wherein the light through described sample arm parts is incident to human eye optical fundus reflection, the light reflecting interferes and produces interference light with the light reflecting from reference arm assembly after sample arm parts described bonder, described interference light is detected system and detects, after control system is processed, obtain the OCT fault imaging of human eye; Described sample arm parts comprise collimating mirror and anterior ocular segment oculi posterior segment scanning member, and described reference arm assembly comprises reference arm light Reuter mirror and reference arm reflecting mirror; It is characterized in that: on the primary optic axis between described collimating mirror and described anterior ocular segment oculi posterior segment scanning member or the second optical axis between described reference arm light Reuter's mirror and described reference arm reflecting mirror, be provided with optical path compensation module, described optical path compensation module coordinates described anterior ocular segment oculi posterior segment scanning member to change the light path of OCT system, to the OCT imaging of human eye different parts and realize OCT imaging switch between described different parts.
Further: described optical path compensation module comprises the optical path compensation mechanism of driving device and driven rotary thereof; Described optical path compensation mechanism is comprised of polylith light transmission piece; When described polylith light transmission piece is when rotation is inserted into separately described primary optic axis or the second optical axis respectively, the light path of described OCT system changes, and realizes and carries out OCT imaging at human eye different parts.
Further: described driving device is electric rotating machine; Described light transmission piece be arranged in parallel and its transparent surface all vertical with the incident illumination of described collimating mirror; The rotating shaft of described electric rotating machine is parallel with the incident illumination of crossing described collimating mirror.
Further: the different parts of described human eye at least comprises cornea, crystalline lens front surface, crystalline lens rear surface and amphiblestroid a kind of; Described polylith light transmission piece is arranged on separately respectively primary optic axis, and described multi-functional ophthalmology measuring device respectively corneal, crystalline lens front surface, crystalline lens rear surface and retina carries out OCT imaging.
Further: described anterior ocular segment oculi posterior segment scanning member comprises anterior ocular segment image-forming module and oculi posterior segment image-forming module;
Described anterior ocular segment image-forming module comprises: directions X scanning element, Y-direction scanning element, the first completely reflecting mirror, rotatably regulate completely reflecting mirror, the first dichroic mirror and connect order object lens; When carrying out anterior ocular segment imaging, the light of launching from described collimating mirror is through the optical path compensation mechanism of described optical path compensation module, reflection through described directions X scanning element, described Y-direction scanning element and described the first completely reflecting mirror, be irradiated on described rotatable adjusting completely reflecting mirror, again through described the first dichroic mirror reflects to described in connect order object lens, finally by crossing human eye, converge to people's anterior ocular segment;
Described oculi posterior segment image-forming module comprises: described directions X scanning element, described Y-direction scanning element, the second completely reflecting mirror to the five completely reflecting mirrors, Diopter accommodation unit, described rotatable adjusting completely reflecting mirror, described the first dichroic mirror and and described in connect order object lens; When carrying out oculi posterior segment imaging, the light of launching from described collimating mirror is through the optical path compensation mechanism of described optical path compensation module, successively after the reflection of described directions X scanning element, described Y-direction scanning element and described the second completely reflecting mirror to the five completely reflecting mirrors, through described Diopter accommodation unit, be irradiated on described rotatable adjusting completely reflecting mirror, again through described the first dichroic mirror reflects to described in connect order object lens, finally converge to human eye optical fundus.
Useful technique effect of the present utility model: by utilizing described multi-functional ophthalmology measuring device and measuring method, realized on the one hand the rapid switching function in human eye different parts OCT imaging, realization is measured human eye different depth, improved the investigative range (front and back joint imaging) of OCT system, switched system is stable, registration, does not affect system signal noise ratio; Can realize on the other hand light beam and focus on respectively at human eye diverse location, can for the human eye of different visions, realize the OCT imaging of high-quality different parts, there is higher lateral resolution.Meanwhile, by one-shot measurement, obtain the numerous supplemental characteristics of human eye, as cornea front and rear surfaces curvature, corneal thickness, anterior chamber depth, lens thickness, crystalline lens front and rear surfaces curvature, long, white white distance, the pupil diameter etc. of arriving of axis oculi.
Accompanying drawing explanation
Fig. 1 is the system light path figure of human eye different parts OCT imaging;
Fig. 2 is the index path that includes anterior ocular segment image-forming module 200;
Fig. 3 is the index path that comprises oculi posterior segment image-forming module 300;
Fig. 4 is the schematic diagram of Y-direction scanning element 110 present positions;
Fig. 5 is the index path of iris photographing module 400;
Fig. 6 is the index path of solid optometry module 500;
Fig. 7 is the structural representation of optical path compensation module 600;
The structural representation of Tu8Wei optical path compensation mechanism 601;
Tu9Wei optical path compensation mechanism 601 inserts the sequential schematic of one of them embodiment of the first primary optical axis;
Figure 10 synchronously coordinates Dynamic Graph in each light transmission piece 6011-6014 insertion process in Y-direction scanning element 110 and rotatable adjusting completely reflecting mirror 204 and Fig. 9;
Figure 11 is human eye different parts degree of depth principle optical path figure;
Figure 12 is the partial enlarged drawing one of Figure 11;
Figure 13 is the partial enlarged drawing two of Figure 11.
The specific embodiment
In order to make technical problem to be solved in the utility model, technical scheme and beneficial effect clearer, below in conjunction with drawings and Examples, this utility model is further elaborated.Should be appreciated that specific embodiment described herein is only in order to explain this utility model, and be not used in restriction this utility model.
The explanation of each functional module
With reference to figure 1, Fig. 1 is human eye different parts OCT imaging system index path, comprising: OCT system source 101, fiber coupler 102, reference arm assembly 1050, detection system 106, control system 107 and sample arm parts 800.The light of OCT system source 101 outputs provides light to sample arm parts 800 and reference arm assembly 1050 respectively through fiber coupler 102.Reference arm assembly 1050 comprises reference arm light Reuter mirror 104, reference arm reflecting mirror 105.Reference arm assembly 1050 there is known length and by reference to arm reflecting mirror 105 by luminous reflectance back into optical fibers bonder 102.Sample arm parts 800 provide light to tested human eye E, the light that the light that scattering is returned from human eye E reflects through sample arm parts 800 and reference arm assembly 1050 interferes in fiber coupler 102, interference light is detected system 106 and detects, through control system 107, process again, finally show the OCT image of tested human eye E.Directions X scanning element 109 and 110 couples of human eye E of Y-direction scanning element by sample arm parts 800 scan, and realize the fault imaging of the OCT of human eye E.Wherein, sample arm parts 800 comprise: Polarization Controller 103, collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700.As improvement part of the present utility model, be, human eye different parts OCT imaging system index path also comprises the optical path compensation module 600 that imaging is switched to human eye different parts OCT.Optical path compensation module 600 can be arranged on the primary optic axis between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700, also can be arranged on the second optical axis between reference arm light Reuter mirror 104 and reference arm reflecting mirror 105.Optical path compensation module 600 coordinates anterior ocular segment oculi posterior segment scanning member 700 or reference arm assembly 1050, change the light path of OCT imaging system, at the different parts of human eye, carry out OCT imaging on as cornea, crystalline lens front surface, crystalline lens rear surface and retina, and can between these imaging positions, realize mutually and switching; After having obtained cornea OCT image, crystalline lens front surface OCT image, crystalline lens rear surface OCT image, can obtain cornea front and rear surfaces curvature, corneal thickness, anterior chamber depth, lens thickness, crystalline lens front and rear surfaces curvature, retinal thickness, axis oculi long, arrive the human eyes structure important parameters such as white distance and pupil diameter in vain.In this utility model, only exemplified the situation of optical path compensation module 600 in primary optic axis, therefore, in the following description and each accompanying drawing of description, be to be all based upon on the basis of optical path compensation module 600 on primary optic axis.Situation for optical path compensation module 600 in the second optical axis, this utility model is undeclared temporarily, but its operation principle is similar on primary optic axis with it.
Optical path compensation module 600 comprises driving device 602 and the optical path compensation mechanism 601 that is entered OCT system light path by driving device 602 driven rotary.By the optical path compensation mechanism 601 in optical path compensation module 600 is put into the imaging system into OCT, the light path that switched system is different, the OCT imaging of realization to human eye different parts, thereby utilizing same ophthalmic medical equipment once to sample, realization just can measure the object of human eye different parts, reduce the manufacturing cost of product, improved certainty of measurement.
Particularly, with reference to figure 7 and Fig. 8, when optical path compensation mechanism 601 inserts after the primary optic axis between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700, by coordinating anterior ocular segment oculi posterior segment scanning member 700, realize the change of the light path of whole OCT system, thereby in the different parts imaging of human eye.As specific embodiment, driving device 602 described herein is electric rotating machine, the light transmission piece that optical path compensation mechanism 601 be arranged in parallel for polylith, in polylith light transmission piece wherein one when driven by motor enters OCT system light path, other several primary optic axis that do not enter between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700.With reference to figure 7, it should be noted that, the minute surface of the polylith light transmission piece of these different-thickness need to keep keeping vertical with the outgoing beam of collimating mirror 108, and the rotating shaft 603 of electric rotating machine needs the outgoing beam keeping parallelism of maintenance and collimating mirror 108, that is to say, the rotating shaft 603 of electric rotating machine is vertical with the minute surface of polylith light transmission piece.In addition, polylith light transmission piece keeping parallelism.
The different parts of the human eye described in present patent application file, include but not limited to cornea, crystalline lens front surface, crystalline lens rear surface and retina, for the convenience of setting forth, present patent application file utilizes optical path compensation module 600 corneal, crystalline lens front surface, crystalline lens rear surface and these positions of retina to carry out OCT imaging elaboration.
Further, with reference to figure 1, Fig. 2 and Fig. 3, anterior ocular segment oculi posterior segment scanning member 700 comprises anterior ocular segment image-forming module 200 and oculi posterior segment image-forming module 300.Anterior ocular segment image-forming module 200 comprises: directions X scanning element 109, Y-direction scanning element 110, the first completely reflecting mirror 202, rotatably regulate completely reflecting mirror 204, the first dichroic mirror 205 and connect order object lens 206.With reference to figure 2, when carrying out anterior ocular segment imaging, the light of launching from collimating mirror 108 is through the polylith light transmission piece of different parts OCT imaging light path compensating module 600, through directions X scanning element 109, the reflection of Y-direction scanning element 110, then after completely reflecting mirror 202, be irradiated on rotatable adjusting completely reflecting mirror 204, through the first dichroic mirror 205, reflex to and connect order object lens 206 again, finally by crossing human eye E, converge to people's anterior ocular segment.Wherein, the detecting light beam of anterior ocular segment imaging optical path system meets the parallel incident human eye of scanning light beam centrage, and any time OCT light beam focuses on people's anterior ocular segment.It should be noted that, when carrying out anterior ocular segment imaging, Y-direction scanning element 110 is controlled by control system 107.
As further optimization, with reference to figure 2, anterior ocular segment image-forming module 200 also comprises: be arranged on and in the light path between Y-direction scanning element 110 and the first completely reflecting mirror 202, be also provided with at least one first relay lens 201, at the first completely reflecting mirror 202 with rotatably regulate and be also provided with at least one second relay lens 202 in the light path between completely reflecting mirror 204.Said anterior ocular segment imaging herein comprises the OCT imaging of corneal, crystalline lens front surface and crystalline lens rear surface.
With reference to figure 4, in realizing the process of anterior ocular segment imaging, rotatably regulate completely reflecting mirror 204 and Y-direction scanning element 110 by control system 107, to be controlled simultaneously, Y-direction scanning element 110 is in realizing in the primary importance of anterior ocular segment imaging.Particularly, this primary importance is that to instigate the primary optical axis of the incident illumination of coming from directions X scanning element 109 and the angle of catoptrical primary optical axis be β.
When angle measurement film, crystalline lens front surface and crystalline lens rear surface, OCT light beam focuses on anterior ocular segment central region, can effectively improve the noise lateral resolution when of the OCT image of cornea, crystalline lens front and rear surfaces.And the parallel incident human eye of scanning light beam centrage, is conducive to the refraction correction of cornea and crystalline lens front and rear surfaces, thereby obtain cornea and crystalline lens front and rear surfaces curvature accurately.
With reference to figure 6 and Fig. 7.The flashlight reflection that the first dichroic mirror 205 can send OCT system source 101, and consolidating of sending from light source 501 in solid optometry module 500 looked to light transmission, and can also carry out transmission to the illumination light from lighting source 401 sends in iris photographing module 400.It should be noted that, the wavelength of OCT system source 101 is 790-890nm; 550nm is elected in consolidating depending on light wavelength that light source 501 sends as; The illumination light wavelength that lighting source 401 sends is preferably 740nm.
With reference to figure 3, Fig. 3 is the index path that comprises oculi posterior segment image-forming module 300.Oculi posterior segment image-forming module 300 comprises directions X scanning element 109, Y-direction scanning element 110 successively, the second completely reflecting mirror 301 is to the 5th completely reflecting mirror 304, Diopter accommodation device 305, rotatable adjusting completely reflecting mirror 204, the first dichroic mirror 205 and connect order object lens 206.When carrying out oculi posterior segment imaging, the light of launching from collimating mirror 108 is through the optical path compensation mechanism 601 of different parts OCT imaging light path compensating module 600, through the reflection of directions X scanning element 109 and Y-direction scanning element 110.Now, Y-direction scanning element 110 is controlled by control system 107, light beam is after 110 reflections of Y-direction scanning element, in succession after the reflection of the second completely reflecting mirror 301, the 3rd completely reflecting mirror 302, the 4th completely reflecting mirror 303 and the 5th completely reflecting mirror 304, through Diopter accommodation unit 305, be irradiated on rotatable adjusting completely reflecting mirror 204.Through the first dichroic mirror 205, reflex to and connect order object lens 206 again, finally by crossing human eye E, converge to human eye optical fundus.The detecting light beam of oculi posterior segment imaging optical path system meets scanning light beam centrage and converges near human eye pupil, and any time OCT light beam focuses on human eye optical fundus.Now, rotatable adjusting completely reflecting mirror 204 is controlled by control system 107 with Y-direction scanning element 110 simultaneously, and Y-direction scanning element 110 is in realizing in the second position of oculi posterior segment imaging.Particularly, with reference to figure 4, the second position refers to the residing position of Y-direction scanning element 110, and just making the primary optical axis of incident illumination and the angle of catoptrical primary optical axis of from directions X scanning element 109, coming is α.For different human eyes (its diopter is different), by regulating OCT imaging optical path Diopter accommodation unit, optical fundus 305, make OCT light beam can converge at human eye optical fundus, light beam focuses on retina, in the time of effectively improving like this retina measurement, the noise of OCT image is lateral resolution when.Particularly, Y-direction scanning element 110 not only plays the effect of Y-direction scanning, also plays the effect that light path is switched.In this utility model, Y-direction scanning element 110 is galvanometer or other high-precision positioners, meets the demand that system light path switches and scans fast.
The switching of anterior ocular segment light path and oculi posterior segment light path: with reference to figure 3 and Fig. 4, while measuring oculi posterior segment, by rotating Y-direction scanning element 110, allow light path primary optical axis reflex to the second completely reflecting mirror 301 from directions X scanning element 109, the primary optical axis of light beam changes α angle (as shown in Figure 4); And while surveying anterior ocular segment, rotation Y-direction scanning element 110, allows light path primary optical axis reflex to the first relay lens 201 from directions X scanning element 109, the primary optical axis of light beam changes β angle (as shown in Figure 4).Rotatable adjusting completely reflecting mirror 204 is also done corresponding rotation, and Y-direction scanning element 110 and rotatable adjusting completely reflecting mirror 204 cooperatively interact, and realize the switching of anterior ocular segment oculi posterior segment light path.
With reference to figure 5, Fig. 5 is iris imaging module 400, and it is a part for sample arm parts 800 in Fig. 1.Comprise: lighting source 401, connect order object lens 206, the first dichroic mirror 205, the second dichroic mirror 402, iris imaging mirror 403 and camera head 404.Lighting source 401 in iris photographing module 400 is irradiated to the iris of tested human eye E, and reflect at iris, reflected light is through connecing after order object lens 206, after the first dichroic mirror 205 transmissions and the second dichroic mirror 402 reflections, through iris imaging mirror 403, finally by camera head 404, photographed again.
With reference to figure 6, Fig. 6 is solid optometry module 500, and it is a part for sample arm parts 800 in Fig. 1.Comprise: connect order object lens 206, the first dichroic mirror 205, the second dichroic mirror 402, watch light path refraction compensation mirror 504, the 6th completely reflecting mirror 503, lens 502 and display screen 501 attentively.Display screen 501 shows the solid sighting target of admittedly looking for tested human eye E, light scioptics 502 from solid sighting target in display screen 501, by the 6th completely reflecting mirror 503 reflections, through watching light path refraction compensation mirror 504 attentively, after transmission the second dichroic mirror 402 and the first dichroic mirror 205, this light reenters and is mapped to tested human eye E through connecing order object lens 206.Finally, inner solid sighting target is projected to the optical fundus of tested human eye E.Further, display screen 501 can adopt LCD screen, OLED screen or LED array screen etc.Described solid sighting target is inner solid sighting target.Further, can change with the solid sighting target in described inside the solid apparent place of tested eye E.In addition, inner solid sighting target can be up and down, move left and right, and meets the needs of measuring tested diverse location detection.
Particularly, with reference to figure 1, when carrying out optical fundus OCT imaging, watch light path refraction compensation mirror 504 attentively and move together with control system 107 controls also with OCT imaging optical path Diopter accommodation unit 305, optical fundus.If this is because solid viewpoint maintains static, during the solid viewpoint of different eye-observations, Gu the readability of viewpoint is different, this causes uncomfortable to the solid apparent time of measured.Because optical fundus OCT light path is after OCT imaging optical path Diopter accommodation unit, optical fundus 305 tune are bent, can focus on the retina of optical fundus, human eye can be seen clear scanning line.Gu adjust if viewpoint is also introduced the mechanism of bending, can see clearly just can realize for different human eyes.But behind OCT imaging optical path Diopter accommodation unit, optical fundus 305, add and admittedly look light path (this light path is inevitable before 2-D vibration mirror, Gu because viewpoint can not be started with 2-D vibration mirror one), can affect optical fundus OCT light path, thereby the joint-action mechanism shown in employing Fig. 6, namely allow and watch light path refraction compensation mirror 504 attentively and move together with OCT imaging optical path Diopter accommodation unit, optical fundus 305, just can both realize human eye and admittedly look, not affect again optical fundus OCT light path.
Light path regulates explanation
This utility model has also been announced a kind of method of utilizing multi-functional ophthalmology measuring device test human eye different parts, comprises the steps:
The light path system of human eye different parts OCT imaging is set, comprises OCT system source, fiber coupler, detection system, control system, sample arm parts and reference arm assembly; Described sample arm parts comprise collimating mirror and anterior ocular segment oculi posterior segment scanning member, and described reference arm assembly comprises reference arm light Reuter mirror and reference arm reflecting mirror; On the second optical axis of the primary optic axis between described collimating mirror and described anterior ocular segment oculi posterior segment scanning member or described reference arm light Reuter's mirror and reference arm reflecting mirror, optical path compensation module is set;
Described optical path compensation module coordinates described sample arm parts or reference arm assembly to realize human eye different parts OCT imaging by changing light path.
Before said, embodiment of the present utility model is the situation on primary optic axis for optical path compensation module only, therefore following narration is to be also based upon on the basis of optical path compensation module on primary optic axis.Lower mask body is set forth and is utilized the method for testing of multi-functional ophthalmology measuring device to human eye different parts.
(1) measure cornea OCT image
With reference to figure 1, Fig. 4, Fig. 7 and Fig. 8.Before said, the light transmission piece that optical path compensation mechanism 601 be arranged in parallel for polylith, in this utility model, has 4 light transmission piece, is respectively the first light transmission piece 6011, the second light transmission piece 6012, the 3rd light transmission piece 6013 and the 4th light transmission piece 6014.While measuring cornea OCT image, the first light transmission piece 6011 is inserted in the primary optic axis between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700 through rotation, simultaneously rotatable adjusting completely reflecting mirror 204 is controlled by control system 107 with Y-direction scanning element 110, in realizing in the primary importance of anterior ocular segment imaging.Before said, the definition of primary importance is exactly the residing position of Y-direction scanning element 110, just making the primary optical axis of incident illumination and the angle of catoptrical primary optical axis of from directions X scanning element 109, coming is β.Now, rotatable adjusting completely reflecting mirror 204 is also done corresponding rotation.
With reference to figure 1 and Figure 12, the light path of definition angle measurement film OCT image sample arm is LSampleCornea, and it represents the light path from fiber coupler 102 to eye cornea C.Concrete LSampleCornea light path is characterized by, from fiber coupler 102 bright dippings, through Polarization Controller 103, collimating mirror 108, through the first light transmission piece 6011, through directions X scanning element 109, the reflection of Y-direction scanning means unit 110, again through the first relay lens 201, the first completely reflecting mirror 202, the second relay lens 203, be irradiated on rotatable adjusting completely reflecting mirror 204, through the first dichroic mirror 205, reflex to and connect order object lens 206 again, be finally irradiated to the light path in the cornea C of human eye E.
Set LSampleCornea light path and consist of three parts, the insertion primary optic axis of the first light transmission piece 6011 causes the total light path LSampleGongYou+ cornea OCT image apex of variable quantity+anterior ocular segment sample arm of light path to the light path hCornea of cornea signal in OCT image.Wherein nA characterizes the refractive index of the first light transmission piece 6011, and dA characterizes the thickness of the first light transmission piece 6011.Anterior ocular segment sample arm has light path LSampleGongYou, characterizes the light path from fiber coupler 102 to the corresponding locus CDK of cornea OCT image apex.Therefore the computing formula of LSampleCornea also can be write as
LSampleCornea＝(nA-1)·dA+LSampleGongYou+hCornea (1)
It should be noted that, when angle measurement film OCT image, the material of the first light transmission piece 6011 can be also air, and in other words, the first light transmission piece 6011 can be canceled, and now, dA is that 0, nA is 1.
(2) measure crystalline lens front surface OCT image
While measuring crystalline lens front surface OCT image, the second light transmission piece 6012 is inserted in the primary optic axis between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700 through rotation, the first light transmission piece 6011 is withdrawn from.Now rotatable adjusting completely reflecting mirror 204 still remains on the position of realizing anterior ocular segment imaging with Y-direction scanning element 110.
It is LSampleLensF that crystalline lens front surface OCT image sample arm light path is surveyed in definition, and it represents the light path from fiber coupler 102 to human lens front surface LF.Concrete, LSampleLensF light path is characterized by, from fiber coupler 102 bright dippings, through Polarization Controller 103, collimating mirror 108, the second light transmission piece 6012, directions X scanning element 109, the reflection of Y-direction scanning element 110, then through the first relay lens 201, the first completely reflecting mirror 202, the second relay lens 203, be irradiated on rotatable adjusting completely reflecting mirror 204, through the first dichroic mirror 205, reflex to and connect order object lens 206 again, be finally irradiated to the light path on the crystalline lens front surface LF of human eye E.
Setting LSampleLensF light path consists of four parts, the insertion primary optic axis of the second light transmission piece 6012 cause the corresponding locus of the total light path LSampleGongYou+ cornea OCT image apex of variable quantity (nB-1) the dB+ anterior ocular segment sample arm of light path to the light path LCDKtoLFDK+ crystalline lens front surface OCT image apex of the corresponding locus of crystalline lens front surface OCT image apex to OCT image in the light path hLF of crystalline lens front surface signal, the schematic diagram of hLF is with reference to Figure 12 and Figure 13.Wherein nB characterizes the refractive index of the second light transmission piece 6012, and dB characterizes the thickness of the second light transmission piece 6012.
Therefore, LSampleLensF also can be expressed as:
LSampleLensF＝(nB-1)·dB+LSampleGongYou+LCDKtoLFDK+hLF (2)
(3), the measurement of anterior chamber depth
For OCT system, by aplanatism volume, light path from fiber coupler 102 to the corresponding locus of cornea OCT image apex during angle measurement film OCT image, light path from fiber coupler 102 to the corresponding locus of crystalline lens front surface OCT image apex while equaling to survey crystalline lens front surface OCT image,
(nA-1)·dA+LSampleGongYou＝(nB-1)·dB+LSampleGongYou+LCDKtoLFDK (3)
That is: (nA-1) dA=(nB-1) dB+LCDKtoLFDK (4)
And anterior chamber depth LQ meets:
LQ＝LCDKtoLFDK-hCornea+hLF＝(nA-1)·dA-(nB-1)·dB-hCornea+hLF (5)
Because nA, nB, dA, dB are default values, and hCornea and hLF can record from corresponding OCT image, thereby just can obtain the human eye's anterior chamber degree of depth according to (5) formula.
(4), measure crystalline lens rear surface OCT image
With reference to figure 1, Fig. 7 and Fig. 8, while measuring crystalline lens rear surface OCT image, the 3rd light transmission piece 6013 is inserted in the primary optic axis between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700 through rotation, and now rotatable adjusting completely reflecting mirror 204 still remains on the position of realizing anterior ocular segment imaging with Y-direction scanning element 110.
It is LSampleLensB that crystalline lens rear surface OCT image sample arm light path is surveyed in definition, and it represents the light path from fiber coupler 102 to human lens rear surface LB.With reference to figure 1, concrete, LSampleLensB light path is characterized by, from fiber coupler 102 bright dippings, through Polarization Controller 103, collimating mirror 108, through the 3rd light transmission piece 6013, through directions X scanning element 109, the reflection of Y-direction scanning element 110, again through the first relay lens 201, the first completely reflecting mirror 202, the second relay lens 203, be irradiated on rotatable adjusting completely reflecting mirror 204, through the first dichroic mirror 205, reflex to and connect order object lens 206 again, be finally irradiated to the light path on the crystalline lens rear surface LB of human eye E.
Set LSampleLensB light path and formed by four parts, the corresponding locus of the total light path LSampleGongYou+ cornea OCT image apex of variable quantity (nC-1) dC+ anterior ocular segment sample arm that the insertion primary optic axis of the 3rd light transmission piece 6013 causes light path to the light path LCDKtoLBDK+ crystalline lens rear surface OCT image apex of the corresponding locus of OCT image apex, crystalline lens rear surface to OCT image in the light path hLB of crystalline lens rear surface signal.Wherein nC characterizes the refractive index of the 3rd light transmission piece 6013, and dC characterizes the thickness of the 3rd light transmission piece 6013.
Therefore, LSampleLensB also can be write as:
LSampleLensB＝(nC-1)·dC+LSampleGongYou+LCDKtoLBDK+hLB (6)
(5), the measurement of lens thickness
For OCT system, by aplanatism volume, light path from fiber coupler 102 to the corresponding locus of cornea OCT image apex during angle measurement film OCT image, light path from fiber coupler 102 to the corresponding locus of OCT image apex, crystalline lens rear surface while equaling to survey crystalline lens rear surface OCT image, that is:
(nA-1)·dA+LSampleGongYou＝(nC-1)·dC+LSampleGongYou+LCDKtoLBDK (7)
I.e. (nA-1) dA=(nC-1) dC+LCDKtoLBDK=(nB-1) dB+LCDKtoLFDK (8)
And lens thickness LLens meets:
LLens＝LCDKtoLBDK-LCDKtoLFDK-hLF+hLB＝(nB-1)·dB-(nC-1)·dC-hLF+hLB(9)
Because nB, nC, dB, dC are default values, and hLF and hLB can record from corresponding OCT image, thereby just can obtain human lens thickness according to (9) formula.
(6), measure retina OCT image
While measuring retina OCT image, the 4th light transmission piece 6014 is inserted in the primary optic axis between collimating mirror 108 and anterior ocular segment oculi posterior segment scanning member 700 through rotation, allow rotatable adjusting completely reflecting mirror 204 be controlled by control system 107 with Y-direction scanning element 110, in realizing in the second position of oculi posterior segment imaging simultaneously.Particularly, with reference to figure 4, the definition of the second position refers to Y-direction scanning element 110 residing position in the process of measuring retina OCT image, and just making the primary optical axis of incident illumination and the angle of catoptrical primary optical axis of from directions X scanning element 109, coming is α.Rotatable adjusting completely reflecting mirror 204 is also done corresponding rotation.
It is LSampleRetinal that retina OCT image sample arm light path is surveyed in definition, and it represents the light path from fiber coupler 102 to human eye retina R.With reference to figure 7 and Figure 11, concrete, LSampleRetinal light path is characterized by, from fiber coupler 102 bright dippings, through Polarization Controller 103, collimating mirror 108, through the 4th light transmission piece 6014, through directions X scanning element 109, the reflection of Y-direction scanning element 110, again through the second completely reflecting mirror 301, the 3rd completely reflecting mirror 302, after the reflection of the 4th completely reflecting mirror 303 and the 5th completely reflecting mirror 304, through OCT imaging optical path Diopter accommodation unit, optical fundus 305, rotatable adjusting completely reflecting mirror 204 reflections, through the first dichroic mirror 205, reflex to and connect order object lens 206 again, finally by mistake human eye E, converge to the light path of human eye optical fundus retina R.
Set LSampleRetinal light path and consist of several parts, the light path LCDKtoLRDK2+ retina OCT image apex of corresponding locus of OCT image apex when measuring retina, the corresponding locus of the intrinsic light path LSampleGuYou-of variable quantity (nD-1) dD+ oculi posterior segment sample arm optical path regulator regulated quantity 2X+ cornea OCT image apex that the insertion primary optic axis of the 4th light transmission piece 6014 causes light path is to the light path hRetinal of macula retinae central fovea in OCT image.Wherein nD characterizes the refractive index of the 4th light transmission piece 6014, and dD characterizes the thickness of the 4th light transmission piece 6014.The intrinsic light path LSampleGuYou of oculi posterior segment sample arm, characterizes when optical path regulator is during in initial position the light path from fiber coupler 102 to the corresponding locus CDK of cornea OCT image apex.In addition, the material of the 4th light transmission piece 6014 can be also air, and now dD is that 0, nD is 1.In other words, when surveying retina OCT image, can want any light transmission piece.
Because human eye axial length is not all identical, but the reference arm length of this OCT system is fixed, how to realize the amphiblestroid measurement of different depth? the method that this utility model adopts is that interpolation optical path regulator, moves the interference surface that waits of oculi posterior segment OCT imaging.Wherein optical path regulator consists of the second reflecting mirror 301, the 3rd reflecting mirror 302, the 4th reflecting mirror 303 and the 5th reflecting mirror 304.Specific to the present embodiment, allow the second completely reflecting mirror 301 and the 5th completely reflecting mirror 304 maintain static, and allow the 3rd completely reflecting mirror 302 second completely reflecting mirror 301 relative to the 4th completely reflecting mirror 303 or the 5th completely reflecting mirror 304 move up and down, specifically as shown in figure 11.With reference to Figure 12, when the 3rd reflecting mirror 302 and the 4th completely reflecting mirror 303 move up the distance of X from initial position, the corresponding locus of retina OCT image apex moves backward to the position of RDK2 from RDK1, and wherein the light path of RDK1 and RDK2 is 2X.
LSampleGuYou-2X+LCDKtoLRDK2＝LSampleGuYou+LCDKtoLRDK1 (10)
-2X+LCDKtoLRDK2＝LCDKtoLRDK1 (11)
When wherein the corresponding locus of cornea OCT image apex is to measurement retina, the light path of the corresponding locus of OCT image apex is LCDKtoLRDK2, the light path LCDKtoLRDK1 of cornea OCT image apex corresponding locus to the three completely reflecting mirrors 302 and the 4th completely reflecting mirror 303 corresponding locus of retina OCT image apex when reset position.
Wherein the initial position of the 3rd reflecting mirror 302 and the 4th completely reflecting mirror 303 is characterized by: the 3rd completely reflecting mirror 302 and the 4th completely reflecting mirror 303 are driven by same drive mechanism (not shown), when this drive mechanism is controlled through reset switch (not shown), in multiple bit position, be initial position.Further, and the amount of movement X of drive mechanism mechanism can adopt several different methods to record, and as motor, voice coil motor drive, calculates amount of movement; Or adopt grating scale, hold calculating amount of movements such as grid chi etc.
Therefore, surveying retina OCT image sample arm light path LSampleRetinal also can be expressed as
LSampleRetinal＝(nD-1)·dD+LSampleGuYou-2X+LCDKtoLRDK2+hRetinal ⑿
(7), survey different human eye axis oculi long
For OCT system, by aplanatism volume, light path from fiber coupler 102 to the corresponding locus of cornea OCT image apex during angle measurement film OCT image, the light path from fiber coupler 102 to the corresponding locus of retina OCT image apex while equaling to survey retina OCT image,
(nA-1)·dA+LSampleGongYou＝(nD-1)·dD+LSampleGuYou+LCDKtoLRDK1＝(nD-1)·dD+LSampleGuYou-2X+LCDKtoLRDK2 ⒀
And being calculated as of human eye axial length LEye:
LEye＝LCDKtoLRDK2+hRetinal-hCornea＝LCDKtoLRDK1+2X+hRetinal-hCornea＝((nA-1)·dA+LSampleGongYou)-((nD-1)·dD+LSampleGuYou)+2X+hRetinal-hCornea ⒁
Because nA, nD, dA, dD, LSampleGongYou, LSampleGuYou are default values, and hRetinal and hCornea can record from corresponding OCT image, thereby just can obtain human eye axial length according to (14) formula.
In addition, the change in optical path length amount causing due to the difference of the human eye's anterior chamber degree of depth and lens thickness is less than the investigation depth of OCT system, therefore while measuring cornea and crystalline lens front and rear surfaces, light path regulatory mechanism is not set.And while surveying human eye axial length, because the axis oculi of different human eyes is long different, but the reference arm 105 of this system is uncontrollable, thereby surveys in amphiblestroid light path and must have light path regulatory mechanism.Before said, this utility model has increased the second completely reflecting mirror 301, the 3rd completely reflecting mirror 302, the 4th completely reflecting mirror 303 and the 5th completely reflecting mirror 304 in fundus imaging light path.Only need to keep the second completely reflecting mirror 301 and the 5th completely reflecting mirror 304 entirely motionless, mobile the 3rd completely reflecting mirror 302 and the 4th completely reflecting mirror 303, just can realize light path and regulate simultaneously.For different human eyes, by regulating the 3rd completely reflecting mirror 302 and the 4th completely reflecting mirror 303, the optical path difference of joint before and after just reserving.While switching so fast, can not introduce Doppler frequency shift.
It should be noted that, in Fig. 7 and Fig. 8, the first light transmission piece 6011 is unrestricted to the material range of choice of the 4th light transmission piece 6014, as long as meet, light beam can be passed.Preferably, the first light transmission piece 6011 to the material of the 4th light transmission piece 6014 is glass.In addition, although in this utility model, optical path compensation mechanism 601 has only included the first light transmission piece 6011 to the 4th light transmission piece 6014, this does not illustrate that optical path compensation mechanism 601 only includes 4 light transmission piece, along with the increase to human eye test position, the quantity of light transmission piece also should increase.Moreover, measure cornea OCT image, measurement crystalline lens front surface OCT image, measurement crystalline lens rear surface OCT image and measurement retina OCT image and there is no specific sequencing relation.And the measurement of anterior chamber depth is, the long measurement of the measurement of lens thickness and different people axis oculi all obtains indirectly, for example, anterior chamber depth is by calculating on the basis of measuring cornea OCT image and crystalline lens front surface OCT image; Lens thickness is to obtain on the basis that records crystalline lens front and rear surfaces OCT image; Long the recording of different human eye axis oculi is to obtain on the basis of cornea OCT image and retina OCT image.
Sequencing contro
With reference to figure 9 and Figure 10, the matching timing of the rotary state of optical path compensation module 600, Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 is as shown in Fig. 9,10.Wherein the first light transmission piece 6011 to the 4th light transmission piece 6014 is inserted in primary optic axis separately respectively, play the effect of optical path compensation, and Y-direction scanning element 110 and rotatable adjusting completely reflecting mirror 204 is coordinating the relevant position that goes to front and back joint scanning.System can adopt a trigger switch (not shown), and while allowing the first light transmission piece 6011 proceed in light path, Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 are coordinating the primary importance that goes to prosthomere scanning; After the past 3t time, Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 switch the second position that goes to deutomerite scanning fast.After removing 1t, namely after the time of 4t, system enters next cycle: the first light transmission piece 6011 proceeds in light path separately again just, and Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 are switched go back to the position of prosthomere scanning, so repeatedly, just can realize cornea, the forward and backward surface of crystalline lens, amphiblestroid measurement successively fast.From Fig. 9 and Figure 10, can find out, when angle measurement film, the forward and backward surface of crystalline lens, Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 are coordinating the primary importance that goes to prosthomere scanning, and when surveying retina, Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 switch the second position that goes to deutomerite scanning fast.
Further, the parallel distance of the outgoing beam centrage of the rotating shaft of driving device 602 and collimating mirror 108 and the velocity of rotation of driving device 602, this two factor determines the speed of the speed of above-mentioned handover measurement jointly, namely determines the size of t.
It should be noted that, Fig. 9 and Figure 10 are only exemplary, within first cycle (0-4t), cornea, the forward and backward surface of crystalline lens, amphiblestroid testing sequence can change, therefore proceed to the first light transmission piece 6011 in light path to the sequencing of the 4th light transmission piece 6014 and also can change, Y-direction scanning element 110, rotatable adjusting completely reflecting mirror 204 residing anterior ocular segment position or oculi posterior segment position also change thereupon so.In ensuing second period (4t-8t), system is still repeating the order in first cycle, and human eye different parts is carried out to OCT imaging.
The foregoing is only preferred embodiment of the present utility model; not in order to limit this utility model; all any modifications of doing within spirit of the present utility model and principle, be equal to and replace and improvement etc., within all should being included in protection domain of the present utility model.
Claims (5)
1. a multi-functional ophthalmology measuring device, comprises OCT system source, fiber coupler, detection system, control system, sample arm parts and reference arm assembly; Described OCT system source provides incident illumination to sample arm parts and reference arm assembly respectively through described fiber coupler, wherein the light through described sample arm parts is incident to human eye optical fundus reflection, the light reflecting interferes and produces interference light with the light reflecting from reference arm assembly after sample arm parts described bonder, described interference light is detected system and detects, after control system is processed, obtain the OCT fault imaging of human eye; Described sample arm parts comprise collimating mirror and anterior ocular segment oculi posterior segment scanning member, and described reference arm assembly comprises reference arm light Reuter mirror and reference arm reflecting mirror; It is characterized in that: on the primary optic axis between described collimating mirror and described anterior ocular segment oculi posterior segment scanning member or the second optical axis between described reference arm light Reuter's mirror and described reference arm reflecting mirror, be provided with optical path compensation module, described optical path compensation module coordinates described anterior ocular segment oculi posterior segment scanning member to change the light path of OCT system, to the OCT imaging of human eye different parts and realize OCT imaging switch between described different parts.
2. multi-functional ophthalmology measuring device as claimed in claim 1, is characterized in that: described optical path compensation module comprises the optical path compensation mechanism of driving device and driven rotary thereof; Described optical path compensation mechanism is comprised of polylith light transmission piece; When described polylith light transmission piece is arranged on separately described primary optic axis or the second optical axis, the light path of described OCT system changes, and realizes and carries out OCT imaging at human eye different parts.
3. multi-functional ophthalmology measuring device as claimed in claim 2, is characterized in that: described driving device is electric rotating machine; Described light transmission piece be arranged in parallel and its transparent surface all vertical with the incident illumination of described collimating mirror; The rotating shaft of described electric rotating machine is parallel with the incident illumination of crossing described collimating mirror.
4. multi-functional ophthalmology measuring device as claimed in claim 2, is characterized in that: the different parts of described human eye at least comprises cornea, crystalline lens front surface, crystalline lens rear surface and amphiblestroid a kind of; Described polylith light transmission piece is arranged on separately respectively described primary optic axis, and described multi-functional ophthalmology measuring device respectively corneal, crystalline lens front surface, crystalline lens rear surface and retina carries out OCT imaging.
5. the multi-functional ophthalmology measuring device as described in claim 1 to 4 any one, is characterized in that: described anterior ocular segment oculi posterior segment scanning member comprises anterior ocular segment image-forming module and oculi posterior segment image-forming module;
Described anterior ocular segment image-forming module comprises: directions X scanning element, Y-direction scanning element, the first completely reflecting mirror, rotatably regulate completely reflecting mirror, the first dichroic mirror and connect order object lens; When carrying out anterior ocular segment imaging, the light of launching from described collimating mirror is through the optical path compensation mechanism of described optical path compensation module, reflection through described directions X scanning element, described Y-direction scanning element and described the first completely reflecting mirror, be irradiated on described rotatable adjusting completely reflecting mirror, again through described the first dichroic mirror reflects to described in connect order object lens, finally by crossing human eye, converge to people's anterior ocular segment;
Described oculi posterior segment image-forming module comprises: described directions X scanning element, described Y-direction scanning element, the second completely reflecting mirror to the five completely reflecting mirrors, Diopter accommodation unit, described rotatable adjusting completely reflecting mirror, described the first dichroic mirror and and described in connect order object lens; When carrying out oculi posterior segment imaging, the light of launching from described collimating mirror is through the optical path compensation mechanism of described optical path compensation module, successively after the reflection of described directions X scanning element, described Y-direction scanning element and described the second completely reflecting mirror to the five completely reflecting mirrors, through described Diopter accommodation unit, be irradiated on described rotatable adjusting completely reflecting mirror, again through described the first dichroic mirror reflects to described in connect order object lens, finally converge to human eye optical fundus.
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