CN1299633C - Refraction and diffraction mixed zoom optical system suitable for Hartmann wave front sensor - Google Patents
Refraction and diffraction mixed zoom optical system suitable for Hartmann wave front sensor Download PDFInfo
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- CN1299633C CN1299633C CN 200310110055 CN200310110055A CN1299633C CN 1299633 C CN1299633 C CN 1299633C CN 200310110055 CN200310110055 CN 200310110055 CN 200310110055 A CN200310110055 A CN 200310110055A CN 1299633 C CN1299633 C CN 1299633C
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Abstract
The present invention relates to the structure improvement of an optical imaging system for a refraction and diffraction mixed zooming system in a Hartmann wave front sensor for correcting hyperopia and myopia. The optical imaging system comprises a detector 2, a laser 3, a microlens array 4, a reflecting mirror 5, a semi-penetrating semi-reflecting mirror 6, a first refraction lens 8, a second refraction lens 9, a dyadic diffracting surface 10 and the human eye 11 to be measured. According to requirements for measuring human eye wave aberrations with different wavelength by the Hartmann wave front sensor, the focusing characteristic of the zooming system and reverse direction dispersion characteristic of the dyadic diffracting surface are used for solving the problem that the wave front chromatic aberration of the human eye and a common individual human eye, such as presbyopia, myopia, etc. can not be measured by the Hartmann sensor. When the system is used for measuring improper eyes, a tested light beam can be focused on the retinae by focusing and can return on the semi-penetrating semi-reflecting mirror in an original path to be reflected to CCD to obtain human eye information. Consequently, the wave aberration measurement of the improper eyes can be realized. The whole system has the advantages of simple and compact structure, high performance and weight reduction.
Description
Technical field: the invention belongs to optical imaging system, relate to a kind of improvement, particularly relate in the Hartmann wave front sensor and roll over/spread out compound zoom is corrected hypermetropia, bathomorphic optical imaging system structure apart from system improvement the Hartmann wave front sensor measurement means.
Background technology: the optical system of human eye is a complicated optical system that is changed by aspheric surface and graded index, in order to measure the wave aberration of human eye, what the overseas utilization Hartmann sensor adopted in recent years is by measuring wavefront slope, finish wavefront measurement through suitable wavefront reconstruction algorithm again, whole system is simple in structure, compact, because what research was adopted is monochromatic light, so only relate to monochromatic aberration; When using white light that human eye is tested, the contrast sensitivity function (CSF) of finding to correct the human eye high spatial frequency thing after the senior aberration can only improve 2 times, and this is because when using white light, the wavefront chromatic aberration of existence has hindered the raising of human eyesight.If obviously correct monochromatic aberration and wavefront chromatic aberration simultaneously, human eye vision will better be improved, and therefore the aberration of human eye of measuring under the different wave length also has very important meaning.And at present with Hartmann sensor to the research of aberration of human eye all based on monochromatic wavelength with measure the normal eye, structure be the monochromatic light that sends by laser instrument through microlens array and half-reflecting half mirror are parallel incide human eye and arrive retina after, return by former road again and arrive the half-reflecting half mirror back reflection obtains the human eye retina to the CCD camera image.Based on this structure of background technology Hartmann sensor, it is energy measurement human eye wavefront chromatic aberration and common individual human eye such as hypermetropia and myopia not.
Summary of the invention: at the problem that exists in the above-mentioned background technology, the objective of the invention is to solve in the background technology with Hartmann sensor not energy measurement human eye wavefront chromatic aberration and problems such as hypermetropia and myopia, the present invention will provide a kind of zoom system, pancreatic system of multiple wave absorption aberration, adopt polychromatic source, can be used to measure the wavefront chromatic aberration of common individual human eye.Based on above-mentioned needs, the present invention has designed the folding/compound zoom of spreading out that a kind of secondary color Hartmann sensor aberration of human eye that is used for measuring aberration of human eye under different wave length measures apart from optical system.
Technical scheme of the present invention comprises: Hartmann sensor 1, zoom system, pancreatic system 7, human eye to be measured 11, and wherein Hartmann sensor 1 comprises: detector 2, laser instrument 3, microlens array 4, reflecting mirror 5, semi-transparent semi-reflecting lens 6; Zoom system, pancreatic system 7 comprises: first refractor 8, second refractor 9, binary diffraction face 10; Zoom system, pancreatic system 7 of the present invention between human eye 11 to be measured and Hartmann sensor 1 and the three be in same optical axis; Binary diffraction face 10 is etched in any one side in the plane of refraction in first refractor 8 or second refractor 9; The position of first refractor 8 and second refractor 9 can exchange; First refractor 8, second refractor 9, binary diffraction face 10 be vertical the placement or the placement of tilting on systematic optical axis.
When the present invention works, when focusing on the human eye retina, laser beam goes up the formation picture point, the light beam that this picture point process human eye refracting media reflects is by the microlens array imaging, this microlens array is divided into array before the wavelet with incident wavefront, by measuring the phase slope before each wavelet, reconstruct actual wavefront through the wavefront reconstruction algorithm, thereby can obtain the various aberrations of human eye.Because there is out of focus (myopia or hypermetropia) in various degree in the human eye of different improper visions, this will cause can not being imaged on the retina from the collimated light beam of light source outgoing, thereby the light intensity that reflexes on the microlens array is died down, and signal to noise ratio reduces, and can not obtain wavefront information to be measured exactly.The present invention compensates the out of focus that the Different Individual human eye exists by focusing system, just can make incident beam focal imaging on retina, thereby the individual eye to different all can acquire higher signal to noise ratio, can obtain the defocusing amount that human eye to be measured is compensated by zoom system, pancreatic system simultaneously.Therefore the present invention can be used for Hartmann sensor and accurately measures individual aberration of human eye.
Good effect of the present invention: the present invention measures the needs of aberration of human eye under the different wave length according to Hartmann wave front sensor, has designed to be made of to roll over/spread out two refractors and binary diffraction face and has mixed the polychrome zoom system, pancreatic system.The binary diffraction face that adopts in this system is because its unique dispersion characteristics have shown the irreplaceable advantage of refracting element.The binary diffraction mask has big negative sense dispersion characteristics, can constitute achromatic system with refracting element; And the binary diffraction face is the embossment structure that directly is produced on the refractor, simplied system structure effectively, weight reduction.Solved the not problem of energy measurement human eye wavefront chromatic aberration and common individual human eye such as hypermetropia and myopia of background technology.This system places between Hartmann sensor and the human eye, to the myopia or the improper eye of hypermetropia when measuring in various degree arranged, focusing by this system, make test beams all can focus on the retina, former again road turns back to and reflexes to upward acquisition human eye information of CCD on the half-reflecting half mirror again, thereby the individual eye to different all can obtain higher signal to noise ratio, thereby realizes comprising myopia, hypermetropia, the normally measurement of the wave aberration of eye.Burnt long adjusting range be-200mm-200mm, can be used for out of focus to spend-500+in the 500 degree scopes improper.Under the collimation situation, systematic function reaches diffraction limited; In 0.488 μ m-0.655 mum wavelength scope, the colo(u)rimetric shift of focus is less than 3 μ m.Whole system is simple and compact for structure, and is functional, can be complementary with Hartmann wave front sensor well.
Description of drawings:
Fig. 1 is a structural representation of the present invention
Figure (2a) is the collimating status sketch map of zoom system, pancreatic system of the present invention
Figure (2b) is the focal length of a zoom system, pancreatic system of the present invention divergent state sketch map during for-200mm
Converged state sketch map when figure (2c) is a zoom system, pancreatic system focal length of the present invention for+200mm
Fig. 3 is the focus colo(u)rimetric shift sketch map of zoom system, pancreatic system of the present invention
Fig. 4 is the modulation transfer function (MTF) curve of colimated light system of the present invention
Fig. 5 is the variation with the element radial coordinate of the line frequency (a) of binary diffraction face of the present invention and phase place (b)
The specific embodiment:, enforcement of the present invention is described further below in conjunction with the embodiment accompanying drawing:
The present invention such as Fig. 1 comprise Hartmann sensor 1, zoom system, pancreatic system 7, human eye to be measured 11, and wherein Hartmann sensor 1 comprises: detector 2, laser instrument 3, microlens array 4, reflecting mirror 5, semi-transparent semi-reflecting lens 6; Zoom system, pancreatic system 7 comprises: first refractor 8, second refractor 9, binary diffraction face 10.Detector 2 adopts ccd detector.Laser instrument 3 adopts helium neon laser.Microlens array 4 adopts glass to make.Reflecting mirror 5 adopts silver-plated plane mirror.Semi-transparent semi-reflecting lens 6 adopts on the plate glass and is coated with part reflective semitransparent film.The material of first refractor 8 and second refractor 9 is generally made by K9 glass, perhaps forms monochromatic zoom system, pancreatic system by TF1, TF2, TF3, TF4, TF5, TF6, K1, K2, K3, K4, K5, K6, K7, K8 etc.First refractor 8 in the zoom system, pancreatic system, second refractor 9, binary diffraction face 10 both can vertically have been placed also to tilt to place on optical axis, and the angle of placement can be chosen in 85 degree-95 degree, for example selects 85 degree, 88 degree, 90 degree, 92 degree, 95 degree etc.Binary diffraction face 10 is etched in any one side in the plane of refraction in first refractor 8 or second refractor 9; The position of first refractor 8 and second refractor 9 can exchange.
Design the incident beam bore of zoom system, pancreatic system according to the beam size of Hartmann sensor; The general pupil of human eye when scotopic vision is about about 8mm, and the outgoing beam bore that therefore designs this zoom system, pancreatic system is 8mm to the maximum, can be complementary with the microlens array in the Hartmann sensor from human eye retina's beam reflected guaranteeing; Wavelength is chosen 0.488 μ m, 0.514 μ m, 0.655 μ m;-500 spend for satisfying+the human eyesight adjusting ranges of 500 degree, burnt long excursion should be at-200mm-200mm.
For dwindling the length of zoom system, pancreatic system 7, first refractor 8 is selected minus lens for use.For guaranteeing that system's outgoing beam bore is 8mm to the maximum in the zoom process, under the collimated light path situation, rationally set the interval between first refractor 8 and second refractor 9, make the outgoing beam bore be about 6.5mm.Add desirable virtual lens in the design, optimize each curvature of face spherical aberration corrector.If the zoom system, pancreatic system that will only be made of two refractors is used for the polychrome situation, then there are bigger aberration and spherochromatism, the binary diffraction mask has big negative sense dispersion characteristics, can constitute achromatic system with refracting element, as shown in Figure 3.
The Zoom structure of optimizing the back system is shown in Fig. 2 (a), Fig. 2 (b), Fig. 2 (c), the front surface of second refractor 9 is the binary diffraction face, zoom system, pancreatic system 7 length are 60mm, and when Jiao Changcong-200mm changed in the 200mm scope, second refractor, 9 displacements were 32mm.Structure when wherein Fig. 2 (a) is the beam collimation outgoing, Fig. 2 (b), Fig. 2 (c) represent respectively focal length be-200mm and+structure during 200mm.Focus colo(u)rimetric shift situation under the beam collimation situation as shown in Figure 3, curve becomes parabolic type, it is 3 μ m that maximum Jiao moves; Fig. 4 has provided the modulation transfer function (MTF) characteristic curve of colimated light system, and zoom system, pancreatic system is a diffraction limited as can be known.
The face shape parameter curve that has provided the binary diffraction face according to Fig. 5 can be made the binary diffraction face, and wherein curve a represents the variation of line frequency with the element radial coordinate, and curve b represents the variation of phase place with the element radial coordinate.By curve a as can be known, the line frequency at the aperture edge place is 1.84periods/mm, and corresponding minimum feature is 543 μ m.When the etching number of steps of selecting weekly the phase was 8, corresponding diffraction efficiency was 95%, and this moment, the minimum feature size of binary face was 67.9 μ m.
Hartmann sensor 1 comprises that (detector 2, laser instrument 3), microlens array 4, reflecting mirror 5, semi-transparent semi-reflecting lens 6 place in the housing that adopts metal or other load-bearing material to make and is assembled into subsystem.The zoom system, pancreatic system that first refractor 8, second refractor 9, binary diffraction face 10 formed is formed a tubular structure and dock with above-mentioned subsystem, thereby the compound zoom that is formed for the human eye measurement is apart from optical system structure.
Claims (1)
1, is suitable for the folding/compound zoom of spreading out of Hartmann wave front sensor apart from optical system, comprise Hartmann sensor (1), zoom system, pancreatic system (7), human eye to be measured (11), wherein Hartmann sensor (1) comprising: detector (2), laser instrument (3), microlens array (4), reflecting mirror (5), semi-transparent semi-reflecting lens (6), it is characterized in that zoom system, pancreatic system (7) comprising: first refractor (8), second refractor (9), binary diffraction face (10), zoom system, pancreatic system (7) are positioned between human eye to be measured (11) and the Hartmann sensor (1) and the three is in same optical axis; Binary diffraction face (10) is etched in any one side in the plane of refraction in first refractor (8) or second refractor (9); The position of first refractor (8) and second refractor (9) can exchange; First refractor (8), second refractor (9), binary diffraction face (10) be vertical the placement or the placement of tilting on systematic optical axis.
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| Application Number | Priority Date | Filing Date | Title |
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| CN 200310110055 CN1299633C (en) | 2003-11-13 | 2003-11-13 | Refraction and diffraction mixed zoom optical system suitable for Hartmann wave front sensor |
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| CN 200310110055 CN1299633C (en) | 2003-11-13 | 2003-11-13 | Refraction and diffraction mixed zoom optical system suitable for Hartmann wave front sensor |
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| CN1299633C true CN1299633C (en) | 2007-02-14 |
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Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102462485A (en) * | 2010-11-18 | 2012-05-23 | 沈阳理工大学 | Human eye optical system modulation transfer function detector based on wavefront aberration |
| CN102495474B (en) * | 2011-12-09 | 2013-04-03 | 北京理工大学 | Visible light/long-wave infrared broad band spectrum joint focusing optical imaging system |
| CA2871891C (en) * | 2012-04-30 | 2016-11-01 | Clarity Medical Systems, Inc. | Ophthalmic wavefront sensor operating in parallel sampling and lock-in detection mode |
| CN103431837B (en) * | 2013-08-23 | 2015-04-29 | 饶丰 | Human eye axial chromatic aberration and transverse chromatic aberration measurement device based on Hartmann sensor and method thereof |
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