CN204636295U - For the myopia scan module of OCT - Google Patents
For the myopia scan module of OCT Download PDFInfo
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Abstract
A kind of OCT, comprise the optical coherence tomography module for carrying out retina scanning to emmetropic eye, OCT also comprises myopia scan module, myopia scan module can be attached to the outside of optical coherence tomography module, to realize OCT to the scan function of emmetropic eye and the conversion to the bathomorphic scan function that axis oculi extends; Myopia scan module has negative power, thus make the scanning light beam from OCT produce and disperse before entering the myopia that axis oculi extends, thus increase the focusing angle of the scanning light beam focused on bathomorphic retina that axis oculi extends and reduce the maximum optical path difference crossed over by amphiblestroid imaging region, to obtain stronger sweep signal and larger signal to noise ratio and to avoid " mirror image " scanogram of mistake.
Description
Technical field
This utility model relates to optical medical field, particularly a kind of OCT (OCT System, Optical Coherence TomographySystem) with myopia scan module.
Background technology
Optical coherence tomography is a kind of interferometric method, for obtaining by the scattering properties of scanning samples.OCT can be divided into Time Domain Optical coherence tomograph (TD-OCT) and domain optical coherence tomoscanner (FD-OCT) two kinds.Compared with Time Domain Optical Coherence Tomography, domain optical coherence layer scanning technology has obvious advantage in speed and signal to noise ratio.The spectral information of domain optical coherence tomoscan is differentiated usually to realize in the following manner: when spectral domain optical coherence tomography (SD-OCT), the spectrometer in feeler arm can be utilized to carry out light splitting; When frequency sweep (length scanning) optical coherence tomography (SS-OCT), spectral information can be obtained by the frequency converting LASER Light Source rapidly.
The FD-OCT system for collecting 3D rendering data of prior art has been shown in Fig. 1.FD-OCT system comprises light source 101, and traditional light source includes but not limited to have the shorter wideband light source of temporal coherent length or scanning lasing light emitter.Light from light source 101 is led to illuminate sample 110 by optical fiber 105 usually, and typical sample is the tissue at the rear portion of human eye.Light scans between optical fiber and sample by means of scanning device 107 usually, thus light beam (dotted line 108) scanned region or volume are imaged.Be collected from the light of sample scattering, typical case is collected in the optical fiber 105 identical with the optical fiber of the light illuminating sample for leading.The reference light obtained from identical light source 101 transmits in independently path, in this case, comprises optical fiber 103 and retroeflector 104.Those skilled in the art can expect utilizing conduct reference path.The sample light collected is combined with reference light usually in fiber coupler 102, thus forms the interference of light in detector 120.The data exported from detector are transmitted to processor 130.Result can store within a processor or be illustrated on display 140.Process and memory function can realize in OCT inside, or also can manage unit realization in the outside, and the data be collected can be transferred to this external processing unit.This external processing unit can be specifically designed to date processing, or can also perform other the common task being not limited to optical coherence tomography function.
The reference arm of sample and interferometer can form bulk-optics, optical fibers or bulk-optic hybrid system, and different structures can be had, such as Michelson, Mach-Zehnder or the design based on shared path well known by persons skilled in the art.Light beam used herein should be understood to the light path of any careful guiding.In time domain system, reference arm needs to have adjustable light delay thus produces and interferes.The detection system of balance can be used in TD-OCT system and SS-OCT system usually, and spectrometer is used in the detection port of SD-OCT system usually.Utility model described herein may be used for the OCT system of any type.OCT system can encapsulate in the housing usually, and it has the multiple patient's setting element comprising lower jaw frame and the headstock.
In prior art, OCT has been used to scan the retina of patient, thus carries out assisted medical diagnosis.Fig. 2 shows a kind of detailed description of the invention of the optical coherence tomography module of OCT for scanning the retina of patient in prior art, optical coherence tomography module shown in Fig. 2 comprises optical fiber 1, collimating mirror 2, dispersion compensation post 3, X/Y scanning element 4, retina scanning lens 5, eyeglass 6 and the optical mirror for light path folding between retina scanning lens 5 and eyeglass 6, thus provides the incident scanning optical bundle of collimation to schematic eyes 8.
The light source of OCT can be the shorter broadband light source of coherence length or frequency scanning laser.The light that these light sources send enters optical coherence tomography system via the guiding of optical fiber 1.Be collected again from the light of sample reflection/scattering and enter optical fiber 1, the sample light be collected and reference light form the interference of light in (not shown) in intervention module, and optical interference signals is detected device (not shown) and receives.The data exported from detector are transferred to processor (not shown).Result can store within a processor or show over the display.Process and memory function can realize in OCT inside, or also can manage unit realization in the outside, and the data be collected can be transferred to this external processing unit.This external processing unit can be specifically designed to date processing, or can also perform other the common task being not limited to optical coherence tomography function.
OCT can be placed in eyes 8 a distance above, emergent pupil (the emergent pupil of OCT, exit pupil, namely from the pivotal point of the single scanning light beam of OCT) be in the position of the pupil of eyes.As shown in Figure 2, the single scanning light beam from OCT all can focus to the retina of eyes 8, and single scanning light beam focusing angle is α
1, corresponding numerical aperture N.A.=n_eyeball (refractive index of eyeball) * sin (α
1), this numerical aperture N.A. determines the intensity (signal to noise ratio) of obtained sweep signal.For an emmetropic eye (emmetropic eye), along with the scanning of light beam, the single scanning light beam of an a lot of different incidence angles degree focuses on (set that " scanning light beam " mentioned in this patent refers to single scanning light beam or be made up of multiple single scanning light beam like this) on the amphiblestroid diverse location of eyes 8, the chief ray of these single scanning light beams forms visual field (angle) β (FOV on the retina, i.e. scanning angle β), cover the retinal area of certain angle in a lateral direction, maximum optical path difference (the MaximumOPD crossed over by amphiblestroid imaging region in the degree of depth formed thus, namely, Maximum Optical Path Difference) H
1.
Myopia is a kind of common ametropia phenomenon, in OCT clinical diagnosis, often can run into myopia.And, existing research display pathological myopia can increase the probability of some fundus oculi disease, these fundus oculi diseases by OCT auxiliary diagnosis, can too increase myopia in clinical diagnosis and need use the probability of OCT thus.
(a) and (b) in Fig. 3 illustrates respectively and utilizes existing OCT to scan emmetropic eye and bathomorphic single order optical schematic diagram.Compared with the situation of scanning emmetropic eye, in the prior art, when scanning myopia, its compensation principle is the refractive error size according to checked eyes, make the outgoing scanning light beam of coherence tomograph become corresponding divergent beams, again focus on myopia retina to make scanning light beam.Can such as be compensated, as the OCT system that Zeiss company released in 2007 by the distance between change retina scanning lens 5 and eyeglass 6 or the refractive error of distance to checked eyes changed between light source and collimating mirror.Such as, as shown in (b) in Fig. 3, distance between retina scanning lens and eyeglass can be shortened, the scanning light beam of outgoing becomes divergent beams, and the pupil of checked eyes is positioned at the focus of eyeglass thus makes the pupil of eyes be positioned at the pivotal point of the multi beam scanning light beam from OCT.Under this regulatory mechanism, according to first-order theory character, the single scanning light beam diameter of section (H_eye) of provable incident emmetropic eye equals the bathomorphic single scanning light beam diameter of section of incidence after adjusting the distance between retina scanning lens and eyeglass (H ' _ eye), namely
wherein, Δ is the distance be conditioned between retina scanning lens and eyeglass, f
2be the focal length of eyeglass, d is distance between eyeglass and the pupil of eyes and equals f
2.And as shown in Figure 3, the space between retina scanning lens and eyeglass is the parallel space of each scanning light beam chief ray, the distance change between retina scanning lens and eyeglass can not affect the visual field β of each scanning light beam chief ray after eyeglass.
Myopia specifically comprises two types, and wherein the myopia of a type is axial myopia eye, and axial myopia eye extends relevant with axiallength.The axial myopia eye that axiallength extends causes the increase of corneal curvature.The myopia of another kind of type is retractive myopia eye, and retractive myopia eye is relevant with the refractive status of internal eye tissues.
(a) and (b) in Fig. 4 illustrates the axial myopia eye of the retractive myopia eye with normal axis oculi and the axis oculi with elongation respectively.Still keep normal retractive myopia eye for axiallength, the distance L ' eye between retina and the pupil of eyes equals the distance Leye between the retina of emmetropic eye and pupil substantially, and this distance is approximately 20mm.Under existing regulatory mechanism effect, now the numerical aperture N.A. of OCT in emmetropic eye situation equals the numerical aperture N.A. ' of OCT in retractive myopia eye situation, that is:
N.A. '=n_eyeball*sin (α
1) ≈ n_eyeball*tg (α
1)=n_eyeball* (H ' _ eye/L ' eye)=n_eyeball* (H_eye/Leye)=N.A. (H ' _ eye and H_eye demonstrate,proved identical, the diameter of section of incident bathomorphic single scanning light beam after being respectively incident emmetropic eye and compensating adjustment).Further, because the visual field of scanning light beam chief ray and axiallength all do not change, the maximum optical path difference that the degree of depth is crossed over by amphiblestroid imaging region of axiallength normal retractive myopia eye also keeps identical with normal eyes.
But according to medical research, most of high myopic eye caused by the axial length elongation of axis oculi usually, namely has axial myopia.For axial myopia eye, existing refraction compensation mechanism then can produce some problems.
Fig. 5 illustrates the bathomorphic schematic diagram of the axis oculi utilizing existing OCT to scan emmetropic eye and to have elongation based on the principle same with Fig. 3.As shown in Figure 5, for the myopia of axis oculi with elongation.Distance between retina scanning lens 5 and eyeglass 6 is shortened thus makes scanning light beam again focus to retina to compensate by the bathomorphic refractive error scanned.Single scanning light beam focusing angle α after compensating
2be less than the scanning light beam focusing angle α of normal eyes
1.So, although scanning light beam diameter of section H_eye remains unchanged as previously analyzed, compared with the situation of emmetropic eye, because axis oculi extends with coefficient (L_eye+ δ L)/L_eye, wherein L_eye is that the axis oculi of standard normal eyes is long, sin (α
2) and tg (α
2) compare sin (α
1) and tg (α
1) reduce.Therefore, in the bathomorphic situation of axis oculi with elongation, the numerical aperture N.A.=n_eyeball*sin (α of OCT
2) ≈ n_eyeball*tg (α
2) can diminish.Because OCT collects signal when the numerical aperture of reduction from retina, so, the intensity of the sweep signal obtained reduces relative to the situation not having axis oculi to extend, and this causes the signal to noise ratio of sweep signal to be less than the situation not having axis oculi to extend.
In addition, due to the visual field β of scanning light beam chief ray in compensation process
1do not change, so the maximum optical path difference H that the myopia retina that scanning light beam chief ray is extended by axis oculi is formed
2be greater than the maximum optical path difference H formed on the retina of emmetropic eye
1.Because current domain optical coherence tomoscanner only supports limited scan depths scope, the maximum scan degree of depth that the maximum optical path difference crossed over by amphiblestroid imaging region exceedes OCT can cause OCT to produce mistake " mirror image " scanogram.Such as, " mirror image " scanogram of this mistake has been shown in Fig. 6.In frequency domain OCT, the energy spectral density signal that spectroscope obtains, obtains sample depth direction signal after Fourier transformation.For any real number signal a (ν),
If FT [c (v)]=C (t), then
this signal is symmetric about zero-bit.Spectrum density due to energy is real number signal, from fourier transform property, two depth direction signals about depth zero positional symmetry can be obtained, therefore, when object is crossed over depth zero position measurement, because depth difference is greater than the scan depths of OCT, thus before creating depth zero position (on) the mirror image of a part of object and the transversal scanning image be folded into as shown in Figure 6.
In sum, in prior art, utilizing OCT myopia scanned and there is certain defect.If utilize the distance between retina scanning lens and eyeglass to adjust, refractive error correction can be carried out, but, for the myopia that axis oculi extends, the focusing angle of single scanning light beam is less than the focusing angle of the scanning light beam of emmetropic eye, thus the numerical aperture of whole system is diminished, cause the intensity of the sweep signal obtained to reduce relative to the situation of emmetropic eye, the signal to noise ratio of sweep signal is little compared with the situation of emmetropic eyes.In addition, because axis oculi extends and the increase of retina curvature, the maximum optical path difference that the degree of depth is crossed over by amphiblestroid imaging region can increase.Because current domain optical coherence tomoscanner only supports limited scan depths scope, the increase of the maximum optical path difference of amphiblestroid imaging region can cause OCT to produce mistake " mirror image " scanogram.
Utility model content
In order to solve the problem, the OCT that this utility model provides comprises: for carrying out the optical coherence tomography module of retina scanning to emmetropic eye, described OCT also comprises myopia scan module, described myopia scan module can be attached to the outside of described optical coherence tomography module, to realize described OCT to the scan function of emmetropic eye and the conversion to the bathomorphic scan function that axis oculi extends; Described myopia scan module has negative power.
In one preferred embodiment, myopia scan module can make to produce from the scanning light beam of OCT and disperse before entering the myopia that axis oculi extends, thus increases the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation.This external near-sighted scan module with negative power makes the visual field of the chief ray of the scanning light beam from OCT reduce simultaneously, thus reduces the maximum optical path difference crossed over by amphiblestroid imaging region.
In one preferred embodiment, described myopia scan module is independently detachable module, and can be attached to the outside of described optical coherence tomography module.
In one preferred embodiment, described myopia scan module comprises one or more simple lens, cemented doublet, many balsaming lenss, reflection border or the simple lens of variable optical strength.
In one preferred embodiment, described myopia scan module can be a series, and series comprises multiple module with different fixed light focal power.Preferably, the module with larger negative power extends longer myopia for axiallength, and the module with less negative power extends shorter myopia for axiallength.
In one preferred embodiment, described myopia scan module comprises the variable focus lens package of signal-lens multiple lens with such as simple lens, cemented doublet, many balsaming lenss, reflection border or variable optical strength, and the focal power of described variable focus lens package can be conditioned.Preferably, by regulating the distance between multiple lens of described variable focus lens package or the focal power by regulating the signal-lens focal power of variable optical strength to regulate described variable focus lens package.Preferably, the distance between multiple lens of described variable focus lens package can be conditioned by electronic or manual mode.
In one preferred embodiment, the distance scalable between the retina scanning lens of described optical coherence tomography module and eyeglass.
In one preferred embodiment, the distance scalable between the light source of described optical coherence tomography module and collimating mirror.
This utility model additionally provides the myopia scan module for OCT, described OCT comprises the optical coherence tomography module for carrying out retina scanning, wherein, described myopia scan module can be attached to the outside of described optical coherence tomography module, to realize described OCT to the scan function of emmetropic eye and the conversion to the bathomorphic scan function that axis oculi extends; Described myopia scan module has negative power.
In one preferred embodiment, myopia scan module can make to produce from the scanning light beam of OCT and disperse before entering the myopia that axis oculi extends, thus increase the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation, and reduce the visual field from the chief ray of the scanning light beam of OCT.
In one preferred embodiment, described myopia scan module is independently detachable module, and can be attached to the outside of described optical coherence tomography module.
In one preferred embodiment, described myopia scan module comprises one or more simple lens, cemented doublet, many balsaming lenss, reflection border or the simple lens of variable optical strength.
In one preferred embodiment, described myopia scan module can be a series of modules, and in series, each module has different focal power.
In one preferred embodiment, the myopia scan module with larger negative power extends longer myopia for axiallength, and the myopia scan module with less negative power extends shorter myopia for axiallength.
In one preferred embodiment, described myopia scan module comprises the variable focus lens package of signal-lens multiple lens with such as simple lens, cemented doublet, many balsaming lenss, reflection border or variable optical strength, and the focal power of described variable focus lens package can be conditioned.Preferably, by regulating the distance between multiple lens of described variable focus lens package or the focal power by regulating the signal-lens focal power of variable optical strength to regulate described variable focus lens package.Preferably, the distance between multiple lens of described variable focus lens package can be conditioned by electronic or manual mode.
Compared with prior art, OCT of the present utility model at least has the following advantages: because the myopia scan module in OCT of the present utility model has negative power, scanning light beam from OCT was produced before the myopia entering axis oculi elongation disperse, and the visual field of the chief ray of scanning light beam reduces, thus increase the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation and reduce the maximum optical path difference crossed over by amphiblestroid imaging region, to obtain stronger sweep signal (larger signal to noise ratio) and to avoid wrong " mirror image " scanogram.
Accompanying drawing explanation
Fig. 1 shows the schematic diagram of OCT of the prior art;
Fig. 2 shows another schematic diagram of OCT of the prior art;
Fig. 3 shows and utilizes existing OCT to scan emmetropic eye and bathomorphic schematic diagram;
Fig. 4 shows the bathomorphic schematic diagram of the axis oculi having normal axis oculi and have elongation;
Fig. 5 shows another and utilizes existing OCT to the bathomorphic schematic diagram of axis oculi scanning emmetropic eye and have elongation;
Fig. 6 shows " mirror image " scanogram that the myopia that utilizes existing OCT to scan to have the axis oculi of elongation obtains;
Fig. 7 shows the schematic diagram with the OCT of additional myopia scan module of the present utility model;
Fig. 8 shows a detailed description of the invention with the OCT of additional myopia scan module of the present utility model;
Fig. 9 shows another detailed description of the invention with the OCT of additional myopia scan module of the present utility model.
Detailed description of the invention
OCT according to embodiment of the present utility model is described with reference to the accompanying drawings.In the following description, many details have been set forth to make person of ordinary skill in the field more fully understand this utility model.But be apparent that for the technical staff in art, realization of the present utility model can not have some in these details.In addition, should be understood that, this utility model is not limited to introduced specific embodiment.On the contrary, can consider to implement this utility model by the combination in any of characteristic sum key element below, and no matter whether they relate to different embodiments.Therefore, aspect below, feature, embodiment and advantage use for illustrative purposes only and should not be counted as key element or the restriction of claim, unless clearly proposed in the claims.
Fig. 7 shows the OCT with additional myopia scan module of the present utility model, in the OCT shown in Fig. 7, except the conventional optics of the OCT for scanning the retina of emmetropic eye, also comprise additional myopia scan module, the myopia scan module 7 with negative power is attached to the outside of the mechanical interface of existing OCT, to realize OCT to the scan function of emmetropic eye and the conversion to the bathomorphic scan function that axis oculi extends.Additional myopia scan module 7 is placed in the outside of eyeglass 6, myopia scan module 7 has negative power, the single scanning light beam of each bundle leaving the eyeglass 6 of OCT can become after the myopia scan module 7 by adding to be dispersed more, thus scanning light beam is increased at the beam cross section diameter of the pupil position of eyes.Because the beam cross section diameter of scanning light beam at pupil position increases, thus increase the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation.Meanwhile, the chief ray of scanning light beam is diminishing via the rear visual field of the additional near-sighted scan module 7 with negative power, thus the maximum optical path difference crossed over by amphiblestroid imaging region is reduced.As shown in Figure 7, owing to being attached the myopia scan module 7 with negative power, add scanning light beam focusing angle and decrease the maximum optical path difference crossed over by amphiblestroid imaging region, namely, due to dispersing of scanning light beam, there is the scanning light beam focusing angle α of additional myopia scan module
3be greater than the scanning light beam focusing angle α of not additional myopia scan module
2.According to numerical aperture formula N.A.=n_eyeball (refractive index of eyeball) * sin (α 3), be attached the corresponding increase of numerical aperture N.A. of the OCT of the myopia scan module 7 with negative power, the numerical aperture N.A. that even can be increased to than scanning emmetropic eye when not adding myopia scan module is also large.In addition, each scanning light beam chief ray is under the effect of near-sighted scan module 7 with negative power, its visual field can reduce, the visual field β 3 namely with the scanning light beam chief ray of additional myopia scan module is less than the visual field β 2 (equaling the β 1 in background technology) of the scanning light beam chief ray of not additional myopia scan module, thus makes maximum optical path difference H when having additional myopia scan module
3be less than maximum optical path difference H when not adding myopia scan module
2.Therefore, after being attached the near-sighted scan module 7 with negative power, the focusing angle focusing on the scanning light beam on the bathomorphic retina of the axis oculi with elongation is replied and keeps and the emmetropia at the moment approximately equal of scanning, thus with additional myopia scan module and adopt in prior art the method compensating refractive error to scan the axis oculi with elongation bathomorphic situation compared with obtain stronger sweep signal (signal to noise ratio), and, owing to make use of additional myopia scan module, the visual field of scanning light beam reduces, the maximum optical path difference crossed over by amphiblestroid imaging region is corresponding reduction also, avoid " mirror image " scanogram of mistake thus in most cases.
In this utility model, without the need to the refractive error correction mechanism of existing OCT, namely without the need to regulating the distance between the retina scanning lens in OCT and eyeglass, by means of the additional myopia scan module with negative power, can scan the high myopic eye of the axis oculi with elongation, obtain stronger sweep signal (signal to noise ratio) and wrong " mirror image " scanogram can be avoided.If the technical solution of the utility model combines with the refractive error correction mechanism of existing OCT, then can further expand refractive error correcting range.
In this utility model, lens numbers, type and focal length in additional myopia scan module are variable.Such as, the battery of lens that additional myopia scan module can comprise one or more simple lens, cemented doublet, many balsaming lenss or be made up of several lens, as long as the equivalent negative focal power of myopia scan module that simple lens, cemented doublet, many balsaming lenss or battery of lens are formed can meet the bathomorphic scanning demand for certain dioptric scope.Preferably, described myopia scan module can adopt multiple there is different fixed light focal power lens or zoom system, pancreatic system cover larger myopia power range, the focal power of described zoom-lens system can be conditioned.Zoom-lens system can comprise the simple lens (i.e. liquid lens) of simple lens, cemented doublet, many balsaming lenss, reflection border, variable optical strength.In actual product, described myopia scan module can be a series of modules, and in series, each module has different negative power.
Fig. 8 illustrates a detailed description of the invention with the OCT of additional myopia scan module of the present utility model, comprises the myopia scan module that two have the cemented doublet of fixed light focal power in which.In Fig. 8 (a), larger myopia is extended for axiallength, the myopia scan module of the cemented doublet with stronger negative power can be used.And in Fig. 8 (b), less myopia is extended for axiallength, the myopia scan module of the cemented doublet with more weak negative power can be used.
Fig. 9 illustrates another detailed description of the invention with the OCT of additional myopia scan module of the present utility model.As shown in Figure 9, myopia scan module 7 is the zoom system, pancreatic systems comprising two lens 7-1,7-2, and one of them lens 7-1 can have negative power, and another lens 7-2 then has positive light coke, and the zoom system, pancreatic system that they form has negative power.Fig. 9 (a) shows the spacing of two lens 7-1,7-2 from little to large different conditions to 9 (c), by regulating the distance between two lens 7-1,7-2 of zoom system, pancreatic system, myopia scan module 7 can cover the myopia diopter (myopia corresponding to having different axis oculi elongation) of certain limit.Particularly, when the myopia larger for axis oculi elongation, two of zoom system, pancreatic system lens 7-1, a 7-2 can be adjusted to and there is less spacing, when the myopia less for axis oculi elongation, two of zoom system, pancreatic system lens 7-1, a 7-2 can be adjusted to and there is larger spacing.Particularly, can be regulated the distance between the lens in zoom system, pancreatic system by electronic or manual mode, this zoom system, pancreatic system also can comprise plural lens or battery of lens.
The OCT with myopia scan module of the present utility model can not changing existing OCT internal structure, do not increase on the basis of the cost of OCT itself and overcome defect of the prior art.Because myopia scan module has negative power, scanning light beam from OCT was produced before the bathomorphic pupil entering axis oculi elongation disperse, thus increase the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation.And make the visual field from the scanning light beam chief ray of OCT diminish to reduce the maximum optical path difference crossed over by amphiblestroid imaging region.Thus obtain stronger sweep signal (signal to noise ratio), and avoid " mirror image " scanogram of mistake.
In addition, the myopia scan module that this utility model describes is used for normal eye when scanning, because visual field diminishes, actual sweep limits on normal retina is also corresponding to diminish.Now less sweep limits is still presented at identical viewing area by OCT instrument, serves one is carried out partial enlargement effect to normal eye's scanning.
Although this utility model discloses as above with preferred embodiment, this utility model is not defined in this.Any those skilled in the art, not departing from the various change and amendment done in spirit and scope of the present utility model, all should include in protection domain of the present utility model, therefore protection domain of the present utility model should be as the criterion with claim limited range.
Claims (22)
1. have an OCT for myopia scan module, described OCT comprises the optical coherence tomography module for carrying out retina scanning,
It is characterized in that, described OCT also comprises myopia scan module, described myopia scan module can be attached to the outside of described optical coherence tomography module, to realize described OCT to the scan function of emmetropic eye and the conversion to the bathomorphic scan function that axis oculi extends;
Described myopia scan module has negative power.
2. the OCT with myopia scan module according to claim 1, it is characterized in that, myopia scan module can make to produce from the scanning light beam of OCT and disperse before entering the myopia that axis oculi extends, thus increase the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation, and reduce the visual field from the chief ray of the scanning light beam of OCT.
3. the OCT with myopia scan module according to claim 1, is characterized in that, described myopia scan module is independently detachable module, and can be attached to the outside of described optical coherence tomography module.
4. the OCT with myopia scan module according to claim 1, it is characterized in that, described myopia scan module comprises one or more simple lens, cemented doublet, many balsaming lenss, reflection border or the simple lens of variable optical strength.
5. the OCT with myopia scan module according to claim 1, is characterized in that, described myopia scan module can be a series of modules, and in series, each module has different focal power.
6. the OCT with myopia scan module according to claim 5, it is characterized in that, the myopia scan module with larger negative power extends longer myopia for axiallength, and the myopia scan module with less negative power extends shorter myopia for axiallength.
7. the OCT with myopia scan module according to claim 1, is characterized in that, described myopia scan module comprises the variable focus lens package with multiple lens, and the focal power of described variable focus lens package can be conditioned.
8. the OCT with myopia scan module according to claim 7, is characterized in that, described variable focus lens package has simple lens, cemented doublet, many balsaming lenss, reflection border or the simple lens of variable optical strength.
9. the OCT with myopia scan module according to claim 7, it is characterized in that, by regulating the distance between multiple lens of described variable focus lens package or the focal power by regulating the signal-lens focal power of variable optical strength to regulate described variable focus lens package.
10. the OCT with myopia scan module according to claim 9, is characterized in that, the distance between multiple lens of described variable focus lens package can be conditioned by electronic or manual mode.
11. OCTs with myopia scan module according to claim 1, is characterized in that, the distance scalable between the retina scanning lens of described optical coherence tomography module and eyeglass.
12. OCTs with myopia scan module according to claim 1, is characterized in that, the distance scalable between the light source of described optical coherence tomography module and collimating mirror.
13. 1 kinds of myopia scan modules for OCT, described OCT comprises the optical coherence tomography module for carrying out retina scanning,
It is characterized in that, described myopia scan module can be attached to the outside of described optical coherence tomography module, to realize described OCT to the scan function of emmetropic eye and the conversion to the bathomorphic scan function that axis oculi extends;
Described myopia scan module has negative power.
The 14. myopia scan modules for OCT according to claim 13, it is characterized in that, myopia scan module can make to produce from the scanning light beam of OCT and disperse before entering the myopia that axis oculi extends, thus increase the focusing angle of the scanning light beam on the bathomorphic retina focusing on axis oculi elongation, and reduce the visual field from the chief ray of the scanning light beam of OCT.
The 15. myopia scan modules for OCT according to claim 13, is characterized in that, described myopia scan module is independently detachable module, and can be attached to the outside of described optical coherence tomography module.
The 16. myopia scan modules for OCT according to claim 13, it is characterized in that, described myopia scan module comprises one or more simple lens, cemented doublet, many balsaming lenss, reflection border or the simple lens of variable optical strength.
The 17. myopia scan modules for OCT according to claim 13, it is characterized in that, described myopia scan module can be a series of modules, and in series, each module has different focal power.
The 18. myopia scan modules for OCT according to claim 17, it is characterized in that, the myopia scan module with larger negative power extends longer myopia for axiallength, and the myopia scan module with less negative power extends shorter myopia for axiallength.
The 19. myopia scan modules for OCT according to claim 13, it is characterized in that, described myopia scan module comprises the variable focus lens package with multiple lens, and the focal power of described variable focus lens package can be conditioned.
The 20. myopia scan modules for OCT according to claim 19, is characterized in that, described variable focus lens package has simple lens, cemented doublet, many balsaming lenss, reflection border or the simple lens of variable optical strength.
The 21. myopia scan modules for OCT according to claim 19, it is characterized in that, by regulating the distance between multiple lens of described variable focus lens package or the focal power by regulating the signal-lens focal power of variable optical strength to regulate described variable focus lens package.
The 22. myopia scan modules for OCT according to claim 21, it is characterized in that, the distance between multiple lens of described variable focus lens package can be conditioned by electronic or manual mode.
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106031629A (en) * | 2015-03-10 | 2016-10-19 | 卡尔蔡司医疗技术公司 | A myopic eye scanning module used for an optical coherence tomography instrument |
| CN108366713A (en) * | 2016-03-18 | 2018-08-03 | 株式会社吉田制作所 | Optical coherence tomographic imaging apparatus and its application method |
| CN112351757A (en) * | 2018-04-06 | 2021-02-09 | 克拉诺瓦公司 | Device for treating tissue comprising an original optical system for laser deflection and focusing |
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106031629A (en) * | 2015-03-10 | 2016-10-19 | 卡尔蔡司医疗技术公司 | A myopic eye scanning module used for an optical coherence tomography instrument |
| CN108366713A (en) * | 2016-03-18 | 2018-08-03 | 株式会社吉田制作所 | Optical coherence tomographic imaging apparatus and its application method |
| US10799099B2 (en) | 2016-03-18 | 2020-10-13 | The Yoshida Dental Mfg. Co., Ltd. | Optical interference tomographic image generating apparatus and method for using same |
| CN112351757A (en) * | 2018-04-06 | 2021-02-09 | 克拉诺瓦公司 | Device for treating tissue comprising an original optical system for laser deflection and focusing |
| CN112351757B (en) * | 2018-04-06 | 2023-09-29 | 克拉诺瓦公司 | Apparatus for treating tissue comprising an original optical system for laser deflection and focusing |
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