CN201234974Y - Compensating device for measuring and correcting human eye wave front aberration - Google Patents
Compensating device for measuring and correcting human eye wave front aberration Download PDFInfo
- Publication number
- CN201234974Y CN201234974Y CNU2008200570132U CN200820057013U CN201234974Y CN 201234974 Y CN201234974 Y CN 201234974Y CN U2008200570132 U CNU2008200570132 U CN U2008200570132U CN 200820057013 U CN200820057013 U CN 200820057013U CN 201234974 Y CN201234974 Y CN 201234974Y
- Authority
- CN
- China
- Prior art keywords
- translation stage
- control translation
- electronic control
- human eye
- accurate electronic
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Images
Landscapes
- Eye Examination Apparatus (AREA)
Abstract
The utility model relates to a compensation device for the measurement and correction of wave-front aberrations to human eyes, which comprises a focusing system and a defocused compensation system, wherein the focusing system comprises an extended beam lens, a collimation lens and a precise electric control translation stage, and the collimation lens is fixed on the movable end of the precise electric control translation stage. The defocused compensation system is formed by a telescope system and a precise electric control translation stage, wherein the precise electric control translation stage is arranged between two lenses of the telescope system, and is connected with a computer control system, four reflectors are further arranged on the precise electric control translation stage of the defocused compensation system, wherein two of the reflectors are fixed on the fixed end of the precise electric control translation stage, and the other two reflectors thereof are fixed on the movable end of the precise electric control translation stage. The utility model has been improved greatly compared with the prior art, has better continuity in contrast with the insert type compensation way, can correct the defocusing amount with any size without limitation, and has the advantages of precision, rapid speed and definite movement amount compared with a hand-operated type translation stage.
Description
Technical field
This utility model relates to a kind of medical checkout equipment, in particular for human eyes wave-front optical aberration measurement and corrigent device.
Background technology
Eyes are that the mankind obtain the most important approach of external information, because internal structure is complicated and changeable, there are a large amount of wave front aberrations in human eye.Accurately measure human eye aberration and carry out refraction correction surgery to instructing the ophthalmologist, the image quality that improves human eye is significant.The individuation cutting needs very high accuracy to control laser cutting accurately in operation.Therefore in " individuation " cornea refractive surgery of wave front aberration guiding, the accurate measurement and the rectification of wave front aberration are vital.
Human eyes wave-front optical aberration measurement and apparatus for correcting are to utilize the adaptive optics principle, and the amphiblestroid wave front aberration in human eye optical fundus is measured and corrigent medical apparatus and instruments accurately.Inject ophthalmic with a branch of semiconductor laser from pupil in the measuring process, the light that scatters through the human eye optical fundus is attended by the wave front aberration of human eye, measures this aberration with Hartmann sensor, and directs variable shape reflecting mirror is corrected this aberration.
In human eyes wave-front optical aberration measurement, except measuring, can also measure the multinomial higher order aberratons that has a strong impact on visual quality in the human eye, thereby obtain than the more accurate measurement result of common optometry to the human eye low order aberration that common spectacles promptly can compensate.But concerning the human eye near-sighted, that hyperopia degree is very big, since Beacon Point be by semiconductor laser after a branch of small-bore directional light after the beam-expanding collimation optical system is by observed human eye pupil in the film formed bright spot of human eye optical fundus view, therefore human eye aberration has a direct impact the shape and the size of optical fundus Beacon Point, because the laser beam bore by the human eye pupil is little, the human eye of twenty-twenty vision aberration in small-bore is less, influence to the optical fundus Beacon Point is little, but the aberration of the human eye of ametropia eyesight abnormality in small-bore just has tangible influence to the optical fundus Beacon Point.For myopia or the very big human eye of hyperopia degree, beacon beam does not focus on the human eye retina after injecting the human eye pupil, but focuses on retina the place ahead or rear, no longer is directional light from the scattering of human eye optical fundus by the light that pupil penetrates.Therefore when this human eye was carried out wave-front optical aberration measurement, the detected signal of Hartmann sensor was very faint, can have a strong impact on the certainty of measurement of human eye aberration like this.
In the human eyes wave-front optical aberration correcting process, except correcting, can also correct the multinomial higher order aberratons that has a strong impact on visual quality in the human eye, thereby obtain than the better rectification effect of common spectacles to the human eye low order aberration that common spectacles can compensate.For deformation reflection mirror, can only correct less defocusing amount, the human eye very big to defocusing amount, deformation reflection mirror can't be finished rectification.The deformation reflection mirror that proves the native system use by experiment can only be corrected with interior defocusing amount by right ± 1.5D, surpasses the out of focus of this numerical value, and deformation reflection mirror can't be corrected.In addition, the major part of the deformation reflection mirror ability of correcting all is used for correcting this available common spectacles just can corrigent low order aberration, also is unnecessary waste.If taking certain indemnifying measure corrects defocusing amount in advance, the deflection of the deformation reflection mirror that native system is used just can be little a lot, not only can improve the rectification precision of deformable mirror, can also reduce design and difficulty of processing, thereby help reducing manufacturing cost.
Above-mentioned two kinds of problems have been carried out preliminary solution both at home and abroad at present.In patent " the precompensation device of living human eye retina cell imager ", adopting the fixed slot of the concave-sphere compensating plate that is provided for installing the compensation human eye in the side nearby of human eye carriage is the blade inserting penalty method, and the defocusing amount of human eye is carried out precompensation.This application number is 200420060165.X.And the modes of organizing before using the manual translation platform to change in other relevant patents between focusing lens and the back group focusing lens such as distance are carried out precompensation and rectification to human eyes wave-front optical aberration.But the compensation precision of blade inserting penalty method is limited, because the minimum number of degrees of most of eyeglass are 25 degree.Adopt the method for manual platform, speed, precision all are very limited, and amount of movement also is difficult to accurate Calculation simultaneously.
Summary of the invention
This utility model is that a kind of human eyes wave-front optical aberration measurement and corrigent compensation arrangement of being used for will be provided, this device is applied to accurate electronic control translation stage in the focusing system and defocusing compensation system in this device, by focusing system the defocusing amount of eyesight abnormality human eye is carried out precompensation, make beacon luminous energy focus on the retina of measured human eye accurately, improve optical fundus Beacon Point quality, and then improve the certainty of measurement of human eye aberration; By by the defocusing compensation system, the defocusing amount in the detected human eye aberration of Hartmann is carried out precision correct, thereby the rectification precision of raising deformable mirror reduces the deformation reflection mirror timing to the deflection requirement, and the instrument and equipment manufacturing cost is reduced.
The technical solution of the utility model is as follows:
A kind of human eyes wave-front optical aberration measurement and corrigent compensation arrangement of being used for, comprise focusing system, defocusing compensation system, be characterized in: focusing system comprises extender lens, collimating lens and accurate electronic control translation stage, wherein collimating lens is fixed on the movable terminal of accurate electronic control translation stage, and accurate electronic control translation stage links to each other with computer control system; Collimating lens is realized the focusing function of focusing system along with move jointly the mobile terminal of computer-controlled translation stage; The defocusing compensation system is arranged between spectroscope and the deformable mirror, and is made of a telescopic system and accurate electronic control translation stage, and wherein accurate electronic control translation stage is arranged between two lens of telescopic system, and links to each other with computer control system; On the accurate electronic control translation stage four reflecting mirrors are housed also, wherein two reflecting mirrors are fixed on the stiff end of accurate electronic control translation stage, other two reflecting mirrors are fixed on the movable terminal of accurate electronic control translation stage, and mobile jointly with computer-controlled accurate electronic control translation stage mobile terminal, change the optical distance between two lens.
Accurate electronic control translation stage stroke is 100mm in the defocusing compensation system.
The beneficial effects of the utility model are: accurate electronic control translation stage is applied in focusing system and the defocusing compensation system, in whole device, only just can realize focusing and defocusing compensation function by mobile electronic control translation stage, do not need any other optics original paper in the mobile device, by focusing system the defocusing amount of eyesight abnormality human eye is carried out precompensation, make beacon luminous energy focus on the retina of measured human eye accurately, improve optical fundus Beacon Point quality, and then improve the certainty of measurement of human eye aberration;
Use the defocusing compensation device that the detected human eye defocusing amount of Hartmann sensor is carried out precision and correct, thereby the rectification precision of raising deformable mirror reduces the deformation reflection mirror timing to the deflection requirement, and the instrument and equipment manufacturing cost is reduced.The adding of electronic control translation stage has increased the stability of system, and easy to operate.Make the mobile accuracy of translation stage reach micron dimension by computer control simultaneously, and then improved human eye aberration greatly and measured and correct precision.
This utility model compared with prior art has very big perfect; The compensation way of contrast blade inserting has more seriality, can unrestricted defocusing amount to any size correct; Compare with the manual type translation stage and advantage such as to have accurately, speed is fast, amount of movement is definite.
Description of drawings
Fig. 1 is the index path of human eyes wave-front optical aberration measurement of the present utility model and correction system;
Fig. 2 is the bucking-out system program control flow chart.
The specific embodiment
Below in conjunction with accompanying drawing this utility model is described in further detail.
As shown in Figure 1, human eyes wave-front optical aberration measurement and correction system comprise the beacon light source 1 that is made of the LD semiconductor laser, focusing system 2, reflecting mirror 3, spectroscope 4, measured human eye 5, defocusing compensation system 6, deformable mirror 7, No. two reflecting mirrors 8, bore matching system 9, Hartmann sensor 10, computer 11, high-voltage amplifier 12.
This utility model is for being used for human eyes wave-front optical aberration measurement and corrigent compensation arrangement, is arranged on by beacon light source 1, focusing system 2, defocusing compensation system 6, measures aberrations control and guiding deformation reflection mirror according to Hartmann wave front sensor 10 this aberration is carried out in the human eyes wave-front optical aberration measurement and correction system that corrigent optics Adaptable System forms.
(1) focusing system is made up of extender lens L1, collimating lens L2 and accurate electronic control translation stage, and this system can carry out precompensation to the defocusing amount of human eye.Wherein collimating lens L2 is fixed on the movable terminal on the translation stage, by computer control system 11 controls.Focus by controlling these translation stage collimation lens, and then realize the focusing function of focusing system, make beacon beam can accurately focus on the retina place of measured human eye 5, improve the certainty of measurement of human eye 5 aberrations.
(2) add defocusing compensation system 6 between spectroscope 4 and deformable mirror 7, this system is made of a telescopic system and accurate electronic control translation stage.Wherein accurate translation stage is arranged on two lens L3 of telescopic system, between the L4, by computer 11 controls, moves accurate electronic control translation stage, and the defocusing amount of observed human eye is corrected.Deformation reflection mirror 7 is only corrected other aberrations of removing out of focus in the human eye aberration, makes the rectification effect of human eye aberration better, precision is higher.Also greatly reduce simultaneously the requirement of deformation reflection mirror 7 correcting unit deflections, make design, manufacturing and the processing of wave-front corrector easier, manufacturing cost reduces.
(3) in whole device, only just can realize the defocusing amount precompensation and the correcting function of measured human eye by mobile electronic control translation stage.Do not need any other optics original paper in the mobile device.Not only can conveniently control but also can strengthen the stability of whole system by the method.Make the mobile accuracy of translation stage reach micron dimension by computer control simultaneously, and then improved human eye aberration greatly and measured and corrigent precision.
Operation principle of the present utility model is (as Fig. 1, so 2): the beacon beam that the beacon light source 1 that is made of the LD semiconductor laser sends, expand bundle, collimation by extender lens L1 in the focusing system 2 and collimating lens L2, after reflecting mirror 3 reflections, enter the pupil of human eye 5 again through spectroscope 4 reflections; The beacon beam of observed human eye 5 optical fundus scatterings sees through spectroscope and sees through defocusing compensation system 6 again, through deformation reflection mirror 7 reflections, by No. two reflecting mirror 8 reflections, 'go'gage matching system 9 enters Hartmann wave front sensor 10 again, Hartmann sensor 10 is delivered to Control Computer 11 with the error signal that records, observe the image of the signal that Hartmann sensors 10 receive, i.e. human eyes wave-front optical aberration hot spot dot chart by computer 11.Electronic control translation stage in the mobile focusing system 2, the hot spot dot chart of human eye is the most clear in display, carries out the measurement and the rectification of human eyes wave-front optical aberration then.Beacon beam by beacon light source 1 sends by focusing system 2, after reflecting mirror 3 reflections, is reflected into the pupil of human eye again through spectroscope; The beacon beam of observed human eye 5 optical fundus scatterings sees through spectroscope and sees through defocusing compensation system 6 again, through deformation reflection mirror 7 reflections, by No. two reflecting mirror 8 reflections, 'go'gage matching system 9 enters Hartmann wave front sensor 10 again, Hartmann sensor 10 is delivered to Control Computer 11 with the error signal that records, computer 11 converts the defocusing amount in the aberration to corresponding displacement, switching value outfan by computer 11 capture cards sends pulse signal to sub-circuit then, the motor that sub-circuit will drive translation stage moves, thereby the defocusing amount that Hartmann wave front sensor 10 records is corrected.Computer 11 again with except the defocusing amount other aberrations be processed into control signal, control signal is applied on the deformation reflection mirror 7, thereby the wave front aberration of human eye is corrected after sending high-voltage amplifier 12 to amplify.
Accurate electronic control translation stage stroke is 100mm in defocusing compensation system 6.On the accurate electronic control translation stage four mirror M 1, M2, M3, M4 are housed.Wherein mirror M 1, and the end that M2 is arranged on translation stage maintains static, and with mirror M 3, M4 is fixed on the movable terminal of translation stage, and by computer 11 control mirror M 3, M4 is along with move jointly the mobile terminal of accurate electronic control translation stage.Thereby change the optical distance between extender lens L1 and the collimating lens L2.In the system design, use 32 sub-circuits to control the motor of accurate electronic control translation stage, send pulse signal to sub-circuit, control moving of translation stage by computer 11 capture cards.Use VB that capture card is programmed and realize translation stage control.
Bucking-out system 6 programme-control processes are as shown in Figure 2: begin to measure, convert the detected defocusing amount of Hartmann sensor to corresponding displacement, move by the computer control translation stage, detected defocusing amount is corrected.Continuation detects with Hartmann sensor, if out of focus is non-vanishing in the aberration, continues mobile electronic control translation stage, and defocusing amount is corrected; If out of focus is zero in the aberration, stop mobile electronic control translation stage, quit a program.
Claims (2)
1. one kind is used for human eyes wave-front optical aberration measurement and corrigent compensation arrangement, comprise focusing system (2), defocusing compensation system (6), it is characterized in that, described focusing system (2) comprises extender lens (L1), collimating lens (L2) and accurate electronic control translation stage, wherein collimating lens (L2) is fixed on the movable terminal of accurate electronic control translation stage, and links to each other with computer (11) control system; Described defocusing compensation system (6) is arranged between spectroscope (4) and the deformable mirror (7), and constitute by a telescopic system and accurate electronic control translation stage, wherein accurate electronic control translation stage be arranged on telescopic system two lens (L3, L4) between, and link to each other with computer (11) control system; Four reflecting mirrors (M1, M2, M3, M4) also are housed on the described accurate electronic control translation stage, reflecting mirror (M1 wherein, M2) be fixed on the stiff end of accurate electronic control translation stage, reflecting mirror (M3, M4) be fixed on the movable terminal of accurate electronic control translation stage, (M3 M4) moves with the accurate electronic control translation stage mobile terminal of computer (11) control reflecting mirror jointly, change two lens (L3, L4) optical distance between.
2. human eyes wave-front optical aberration measurement and the corrigent compensation arrangement of being used for according to claim 1 is characterized in that the accurate electronic control translation stage stroke in described defocusing compensation system (6) is 100mm.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNU2008200570132U CN201234974Y (en) | 2008-04-08 | 2008-04-08 | Compensating device for measuring and correcting human eye wave front aberration |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNU2008200570132U CN201234974Y (en) | 2008-04-08 | 2008-04-08 | Compensating device for measuring and correcting human eye wave front aberration |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN201234974Y true CN201234974Y (en) | 2009-05-13 |
Family
ID=40647706
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNU2008200570132U Expired - Fee Related CN201234974Y (en) | 2008-04-08 | 2008-04-08 | Compensating device for measuring and correcting human eye wave front aberration |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN201234974Y (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102283631A (en) * | 2010-08-12 | 2011-12-21 | 中国科学院光电技术研究所 | Hartmann dynamic aberration measuring instrument capable of inducing human eyes to adjust automatically |
| CN103052368A (en) * | 2010-07-20 | 2013-04-17 | 约翰霍普金斯大学 | Surface tracking and motion compensating surgical tool system |
-
2008
- 2008-04-08 CN CNU2008200570132U patent/CN201234974Y/en not_active Expired - Fee Related
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103052368A (en) * | 2010-07-20 | 2013-04-17 | 约翰霍普金斯大学 | Surface tracking and motion compensating surgical tool system |
| CN103052368B (en) * | 2010-07-20 | 2016-01-20 | 约翰霍普金斯大学 | surface tracking and motion compensation surgical tool system |
| CN102283631A (en) * | 2010-08-12 | 2011-12-21 | 中国科学院光电技术研究所 | Hartmann dynamic aberration measuring instrument capable of inducing human eyes to adjust automatically |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101248983A (en) | Compensating mechanism of human eyes wave-front optical aberration measurement and correct system | |
| TWI520713B (en) | Apparatus and method for operating a real time large diopter range sequential wavefront sensor | |
| EP1059061B1 (en) | Method and apparatus for measurement of the refractive properties of the human eye | |
| JP6961059B2 (en) | How to calibrate the phoropter wheel assembly of an object folopter incorporating a wave surface analyzer | |
| CN100586406C (en) | Transmission type artificial crystal aberration Hartmann measuring instrument | |
| KR102053389B1 (en) | Device and method for determining at least one objective eye refraction parameter of a subject depending on a plurality of gaze directions | |
| CN101718542B (en) | Optical ranging device and portable refractometer thereof | |
| EP2417900A1 (en) | Instrument for simulating multifocal ophthalmic corrections | |
| CN203290874U (en) | Full-automatic computer optometry device | |
| US20140152958A1 (en) | Eye Refractive Power Measuring Apparatus and Calibration Method of Eye Refractive Power Measuring Apparatus | |
| CN103431837B (en) | Human eye axial chromatic aberration and transverse chromatic aberration measurement device based on Hartmann sensor and method thereof | |
| JP2019166346A (en) | Method for determining ophthalmological data | |
| CN112754420A (en) | Wavefront aberration measurement system, associated visual perception learning training system and method | |
| CN112244757A (en) | Ophthalmologic measurement system and method | |
| CN201234974Y (en) | Compensating device for measuring and correcting human eye wave front aberration | |
| CN113995373A (en) | Sight instrument focusing method based on H-S reconstruction human eye wavefront aberration | |
| CN103393401A (en) | Double wavefront corrector living body human eye retina high-resolution imaging system | |
| CN201653399U (en) | Optical distometer and its portable optometry unit | |
| CN112450867A (en) | Continuous variable focus and variable optical path biological measuring instrument and eye axis measuring method | |
| CN102028449B (en) | Human eye retina imaging system and method capable of carrying out layered imaging | |
| CN105942970A (en) | Binocular wave front aberration vision optical analysis system | |
| CN219021146U (en) | Aberrometer for measuring human eye regulation state | |
| CN2728418Y (en) | Precompensation device of living human eye retina cell imager | |
| CN216221411U (en) | Focusing and astigmatism compensation mechanism and subjective and objective integrated precise optometry device | |
| CN118168773A (en) | Defocusing mirror detection device and method |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C17 | Cessation of patent right | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20090513 Termination date: 20100408 |