CA2338060C - Apparatus and method for measuring vision defects of a human eye - Google Patents
Apparatus and method for measuring vision defects of a human eye Download PDFInfo
- Publication number
- CA2338060C CA2338060C CA002338060A CA2338060A CA2338060C CA 2338060 C CA2338060 C CA 2338060C CA 002338060 A CA002338060 A CA 002338060A CA 2338060 A CA2338060 A CA 2338060A CA 2338060 C CA2338060 C CA 2338060C
- Authority
- CA
- Canada
- Prior art keywords
- eye
- optical beam
- wavefront
- retina
- lens
- 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 - Lifetime
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/1015—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for wavefront analysis
Abstract
Optical characteristics of optical systems, such as the eye (14), are measured including vision defects of the eye using a collimated beam (12) from a diode laser (66) focused onto the anterior surface (22) of the comes (24) of the eye for providing a finite source (16) of secondary radiation on the retina (18) of the eye, the image of which is close to a desired diffraction limited spot. The secondary radiation is reflected back from the retina (18) as a reflected wavefront of radiation that passes through the eye and is directed onto a wavefront analyzer (42) where distortions associated with the reflected wavefront are measured. By focusing on the cornea (24) through a long focal length lens (70) and thus converging the beam through a small angle (13), as opposed to typically focusing a collimated light onto the retina (18), the need for lenses or lens combinations, and the time required to adjust such to accommodate the differing vision of each patient is eliminated.
Description
APPARATUS AND METHOD FOR MEASURING
VISION DEFECTS OF A HUMAN EYE
Background of Invention Field of Invention The invention relates generally to optical aberration measurements and correction, and in particular to projection techniques in the objective measurement and correction of the human eye using a wavefront sensor.
Description of Background Art ~o There has been and continues to be a need to provide a person with improved visual acuity. Remodeling of the cornea using refractive laser surgery or intra-corneal implants, adding synthetic lenses using intra-ocular lens implants or precision ground contact lenses or eye glasses provide known solutions.
Further, it is known to correct vision astigmatically by surgical modification of myopic or hyperopic astigmatism through laser keratoplasty, keratomileusis or photorefractive keratectomy. Laser sources are used to erode or ablate surfaces of the eye, typically reshaping the cornea. Prior to and during such surgery, precise measurements must be made to determine required surgical corrections.
The imprecise measurement technique of placing lenses of known refractive 2o power anterior to the cornea and asking a patient which lens or lens combination provides the clearest vision has been improved with the use of autorefractometers, as described in U.S. Patent No. 5,258,791 to Penny et al., or with the use of wavefront sensors as described by Liang et al. in "Objective Measurement of Wave Aberrations of the Human Eye with the Use of a Hartmann-Shack Wave-Front 25 Sensor," Journal of the Optical Society of America, Vol. 1, No. 7, July 1994, p.p 1949-1957, by way of examples. Penny '791 discloses the use of autorefractometer measurements for determining the appropriate corneal surface reshaping to provide ,..,.-..,..> ~. ~. -..<,..-,,,r,vclw..nc~~ v:~ ~ Gig- :~- v ............s>:.:-..~.... ... .
::.~:.::::::::::.~:::::::::.:~:::::..:.::::::a: l.:C.'11 ~ -. t W~ :a:-~.~:.~..:>s::::~::.::::::.
::::::::::::::::::.::::::::,.::.. :::.:::::::::::.....::.::.
:.:::.:::::::::::::.::::: l Lc.M 4'J- t3~J _,39~,~':.:::.:::.
::.::.:~::::::.:~:..
_:...::...;,:..::..;;;..;:.,;;...::1'VV t.LV~lli ::.:':.':..::.'..':.:w:~.'.:'.w.~..:::.w:: ~ :::~:':~:::v:':'.~'::..':::r:.::.
. :: ::: .::: S: ::: :%"::: ;i ; .:: w. ' ~..: .'.:: .. :.:: .' :It w 7 L I I
~ ;::::' :: ';' :..'~:nr;:;.:;f:~'..~,:.
::2....~:i3~',~..~:kQ~J~::: ;:~'TI.~~'~.~.l...QS~E~3:: >:I~E ..:. :
::::::::::::::...:.
VISION DEFECTS OF A HUMAN EYE
Background of Invention Field of Invention The invention relates generally to optical aberration measurements and correction, and in particular to projection techniques in the objective measurement and correction of the human eye using a wavefront sensor.
Description of Background Art ~o There has been and continues to be a need to provide a person with improved visual acuity. Remodeling of the cornea using refractive laser surgery or intra-corneal implants, adding synthetic lenses using intra-ocular lens implants or precision ground contact lenses or eye glasses provide known solutions.
Further, it is known to correct vision astigmatically by surgical modification of myopic or hyperopic astigmatism through laser keratoplasty, keratomileusis or photorefractive keratectomy. Laser sources are used to erode or ablate surfaces of the eye, typically reshaping the cornea. Prior to and during such surgery, precise measurements must be made to determine required surgical corrections.
The imprecise measurement technique of placing lenses of known refractive 2o power anterior to the cornea and asking a patient which lens or lens combination provides the clearest vision has been improved with the use of autorefractometers, as described in U.S. Patent No. 5,258,791 to Penny et al., or with the use of wavefront sensors as described by Liang et al. in "Objective Measurement of Wave Aberrations of the Human Eye with the Use of a Hartmann-Shack Wave-Front 25 Sensor," Journal of the Optical Society of America, Vol. 1, No. 7, July 1994, p.p 1949-1957, by way of examples. Penny '791 discloses the use of autorefractometer measurements for determining the appropriate corneal surface reshaping to provide ,..,.-..,..> ~. ~. -..<,..-,,,r,vclw..nc~~ v:~ ~ Gig- :~- v ............s>:.:-..~.... ... .
::.~:.::::::::::.~:::::::::.:~:::::..:.::::::a: l.:C.'11 ~ -. t W~ :a:-~.~:.~..:>s::::~::.::::::.
::::::::::::::::::.::::::::,.::.. :::.:::::::::::.....::.::.
:.:::.:::::::::::::.::::: l Lc.M 4'J- t3~J _,39~,~':.:::.:::.
::.::.:~::::::.:~:..
_:...::...;,:..::..;;;..;:.,;;...::1'VV t.LV~lli ::.:':.':..::.'..':.:w:~.'.:'.w.~..:::.w:: ~ :::~:':~:::v:':'.~'::..':::r:.::.
. :: ::: .::: S: ::: :%"::: ;i ; .:: w. ' ~..: .'.:: .. :.:: .' :It w 7 L I I
~ ;::::' :: ';' :..'~:nr;:;.:;f:~'..~,:.
::2....~:i3~',~..~:kQ~J~::: ;:~'TI.~~'~.~.l...QS~E~3:: >:I~E ..:. :
::::::::::::::...:.
emmetropia, a condition of a normal eye when parallel rays are focused exactly on the retina and vision is optimum. Spatially resohred refraction data, in combination with measured existing surface contour of the anterior surFace of the eye, enable a calculation of a detailed spatially resolved new contour which provides corrected vision, It would be an improvement in this a'rt if such vision correction could be made without the need for this contour data, and further without the need for feedback from the patient regarding an appropriate lens. i_iang et al.
disclose the use of a Hartmann-Shack wavefront sensor to measure ocular aberrations by measuting the waveftont emerging from the eye by retinal reflecfion of a focused 1D laser light spat on the retina's fovea. A parallel beam of laser light passes through beam splitters and a lens pair which brings the beam to a focus point on the retina by the optics of the eye. Possible myopia or hyperopia of the tested eye is corrected by movement of a lens within the lens pair. The focused light on the fovea is then assumed to be difFusely reflected and acts as a point source located on the retina.
~s The reflected light passes through the eye and forms a distorted wavefront in front of the eye that results from the ocular aberrations. The aberrated wavefront is then directed to the wavefront sensor.
A point source of radiation vn the retina would be ideal for such measurements. Hovrever, when the perfect eye receives a collimated beam of light, 2o the best possible image on the retina is a diffraction limited spot. As illustrated by way of example, with Penny et al. and Liang et al., discussed above, and typical far those of skill in the art, as further described in International Application Publication WO 9Bi27863 and German patent publication DE 42 22 385 A1, parallel cr collimated beams are used with the optics of the~eye being mea&ured to achieve this 2~ diffraction Limited spot for such objective rneasur~nents. By way of example, WO
98I278B3 teaches placing a '!.5 mm diameter beam at the pupil, and relies on the lens of the eye to focus the laser beam on the retina, and further teaches that possible myopia or hyperopia of the tested eye is corrected by movement of the eye and the lens corrtbinationg that provide the focus. The teachings of the prior art, are 3o cumbersome and impractical when dealing with an anxious patient, by way of example. The prior art teachings require a setup for each patient that includes include a corrective lens or lens combination and adjustments thereto for ...
:::, :1:::
.:!.VLIVV..lILI\ tJ.J ~1J- a7~ V ,_.
.v.;~.::::T':':.c.~,.~,.:;e:..'1: ..:: ' ::::::::::.~::::::::::::.~.~::::::::::v::::.::.~.:~'. ~.~.~~ (i ~'-T 1 'J' P::M:f.'.~....AS................
:::::.:.: :::::::::::. .:::.:.. , :. : :.:::::::::::::::....:::.: ::::::.::
:::: :..:.. : :. 1 ~1.~ 1 t4d t3;J _~i'-J ..
..::...::.:::;:...::.:....:.::::u v v t . t I I ,vl .; . .. . ..: .: :. .: ..
..:: .: . . .: :;; ~::::...:.~:.::..::::.;.::.::.::::.:_:::::
~::. .. ::;: :: :. : .'~: :; .._ _:.::. :.: ::: : : ~. : , ~. ~ : :: : :: :: ' ::: I I J. 1 L I I . .: ::: . :...: :. ;..'~::::i:::~:
:!~ .- 1 . . . :i ~:: ~: ~:::...::...~~:::::'.~,:::::i::?::.:i:
:.~ :y::.~..:::: :.:::: ..:~ ~ ..::::::.:~::::.~.~::.:~::::::.~:.~:.~:::::.::
:.;::i:: : .:.~::.~i:i':.~:.
...................... :. ;..~.v..
accommodating that patient's specific visual acuity. Providing a corrective or lens combination, as wail as setting up for their use becomes cumbersome, time consuming, arid requires additional expense. Eliminat<ng the need for such corrective optics is desirable and eliminates a variabi~ within optical measurement s systems that typically include many variables. Further, there is a need for providing optical characteristics of an eye without requiring feedback front the patient. By way of example, the patient may be a wild or domestic animal, living yr dead.
disclose the use of a Hartmann-Shack wavefront sensor to measure ocular aberrations by measuting the waveftont emerging from the eye by retinal reflecfion of a focused 1D laser light spat on the retina's fovea. A parallel beam of laser light passes through beam splitters and a lens pair which brings the beam to a focus point on the retina by the optics of the eye. Possible myopia or hyperopia of the tested eye is corrected by movement of a lens within the lens pair. The focused light on the fovea is then assumed to be difFusely reflected and acts as a point source located on the retina.
~s The reflected light passes through the eye and forms a distorted wavefront in front of the eye that results from the ocular aberrations. The aberrated wavefront is then directed to the wavefront sensor.
A point source of radiation vn the retina would be ideal for such measurements. Hovrever, when the perfect eye receives a collimated beam of light, 2o the best possible image on the retina is a diffraction limited spot. As illustrated by way of example, with Penny et al. and Liang et al., discussed above, and typical far those of skill in the art, as further described in International Application Publication WO 9Bi27863 and German patent publication DE 42 22 385 A1, parallel cr collimated beams are used with the optics of the~eye being mea&ured to achieve this 2~ diffraction Limited spot for such objective rneasur~nents. By way of example, WO
98I278B3 teaches placing a '!.5 mm diameter beam at the pupil, and relies on the lens of the eye to focus the laser beam on the retina, and further teaches that possible myopia or hyperopia of the tested eye is corrected by movement of the eye and the lens corrtbinationg that provide the focus. The teachings of the prior art, are 3o cumbersome and impractical when dealing with an anxious patient, by way of example. The prior art teachings require a setup for each patient that includes include a corrective lens or lens combination and adjustments thereto for ...
:::, :1:::
.:!.VLIVV..lILI\ tJ.J ~1J- a7~ V ,_.
.v.;~.::::T':':.c.~,.~,.:;e:..'1: ..:: ' ::::::::::.~::::::::::::.~.~::::::::::v::::.::.~.:~'. ~.~.~~ (i ~'-T 1 'J' P::M:f.'.~....AS................
:::::.:.: :::::::::::. .:::.:.. , :. : :.:::::::::::::::....:::.: ::::::.::
:::: :..:.. : :. 1 ~1.~ 1 t4d t3;J _~i'-J ..
..::...::.:::;:...::.:....:.::::u v v t . t I I ,vl .; . .. . ..: .: :. .: ..
..:: .: . . .: :;; ~::::...:.~:.::..::::.;.::.::.::::.:_:::::
~::. .. ::;: :: :. : .'~: :; .._ _:.::. :.: ::: : : ~. : , ~. ~ : :: : :: :: ' ::: I I J. 1 L I I . .: ::: . :...: :. ;..'~::::i:::~:
:!~ .- 1 . . . :i ~:: ~: ~:::...::...~~:::::'.~,:::::i::?::.:i:
:.~ :y::.~..:::: :.:::: ..:~ ~ ..::::::.:~::::.~.~::.:~::::::.~:.~:.~:::::.::
:.;::i:: : .:.~::.~i:i':.~:.
...................... :. ;..~.v..
accommodating that patient's specific visual acuity. Providing a corrective or lens combination, as wail as setting up for their use becomes cumbersome, time consuming, arid requires additional expense. Eliminat<ng the need for such corrective optics is desirable and eliminates a variabi~ within optical measurement s systems that typically include many variables. Further, there is a need for providing optical characteristics of an eye without requiring feedback front the patient. By way of example, the patient may be a wild or domestic animal, living yr dead.
Summary of Invention In view of the foregoing background, it is therefore an object of the present invention to provide a refraction measurement system that easily accommodates the measurement of vision characteristics of the eye, even in the presence of finite refractive errors. It is another object to improve upon the time required for a patient to be in a fixed position during examination, while at the same time providing a useful source of light on the retina of the eye to be measured regardless of the characteristics of the eye of that patient or other patients to be examined.
It is further an object to measure such characteristics without requiring patient or operator feedback.
These and other objects, advantages and features of the present invention are provided by a method aspect of the invention for measuring optical characteristics of an optical system including the focusing of an optical beam proximate an anterior surface of the optical system for placing a finite source of secondary radiation on a focal surtace of the optical system, which secondary radiation is emitted from the focal surface as a reflected wavefront of radiation that passes through the optical system, projecting the reflected wavefront onto a wavefront analyzer, and measuring characteristics of the optical system associated with the reflected wavefront. In a preferred embodiment, the method includes 2o measuring defects of the eye which includes the steps of focusing an optical beam onto an anterior surface of the eye for providing a finite source of secondary radiation on the retina of the eye, which secondary radiation is emitted from the retina as a reflected wavefront of radiation that passes through the eye;
directing the reflected wavefront onto a wavefront analyzer; and measuring distortions associated with the reflected wavefront. A preferred embodiment of the invention includes the step of focusing the projected optical beam on the anterior surface of the cornea.
An apparatus for effectively performing such measurements includes focusing means for focusing an optical beam onto an anterior surface of the optical system or eye for providing a finite secondary radiation source on the focal surface, or retina of so the eye, which finite secondary radiation source is emitted from the retina as a reflected wavefront of radiation that passes through the eye, directing means for directing the reflected wavefront onto a wavefront analyzer, and a wavefront analyzer for measuring distortions associated with the reflected wavefront. In one preferred embodiment of the present invention, a laser beam is focused onto the surface of the cornea with a long focal length lens which converges the beam through a small angle for passing through the iris of the eye and providing a finite s secondary radiation source on the retina of the eye, which mite secondary radiation source is emitted from the retina through the optics of the eye as the wavefront to be measured.
Brief Description of Drawings A preferred embodiment of the invention as well as alternate embodiments are described by way of example with reference to the accompanying drawings in which:
FIG. 1 is a diagrammatic illustration of an apparatus for measuring visual defects of an eye, according to the present invention;
~s FIG. 2 is a diagrammatic illustration of a eye to be measured by the apparatus of the present invention;
FIGS. 3A and 3B are diagrammatic illustrations of an ideal eye with perfect vision and an aberrated ideal eye, respectively;
FIG. 4 is a diagrammatic illustration of an eye being measure with collimated 20 light focused on the retina to a diffraction limited spot; and FIG. 5 is a partial perspective view of a pinhole imaging plate and detector plane of a wavefront sensor used in a preferred embodiment of the present invention.
25 Detailed Description of Preferred Embodiments The present invention will be described more fully hereinafter with reference to the accompanying drawings, in which preferred embodiments of the invention are shown. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein.
Rather, 3o these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
Like numbers refer to like elements throughout.
A preferred embodiment of a measurement apparatus 10 of the present invention is herein initially described with reference to the schematic diagram of FIG.1. A projected beam 12 of optical radiation is directed into an eye 14 to be measured, so that a small area or measurable spot 16 is formed as a secondary 5 radiation source in the foveal region of the retina 18 as illuminated with reference to FIG. 2. Specifically, the beam 12 is focused through a small angle 13 onto an anterior surface 20 of the eye 14, and in a preferred embodiment of the present invention, focused on an anterior corneal surface 22 of the cornea 24 for further projection through the iris 26 and lens 28 and onto the retina 18.
By way of further background, consider an "ideal" eye 14i with ideal vision, as illustrated with reference to FIG. 3A. The ideal eye 14i, having the ideal cornea 24i and ideal lens 28i will focus a collimated beam of light, illustrated with arrows 30 to a point 32, as the secondary radiation source, on the ideal retina 18i. This point 32 would then be a point source of light which would be diffusely reflected back through ~5 the optics of the ideal eye 14i as a sequence of plane waves 34. In actual fact, even an eye having perfect vision, as illustrated by way of example with reference to FIG. 4, will produce a diffraction limited illuminated area or spot 36, as the secondary radiation source, on the retina of the eye, under the best possible circumstances. In a typical eye, as illustrated with reference to FIG. 4, such a spot 36 is even larger, 2o where most of the blurring will be due to finite aberrations found in typical eyes. By way of further example, in an aberrated eye 14a, if the point source 32 could be realized, distorted wavefronts 38 result as illustrated with reference to FIG.
3B.
Having to deal with a series of distorted wavefronts 38 resulting from aberrations, and further dealing with a blurring of such distorted wavefronts 38 resulting from 25 diffraction effects and the finite aberrations of the eye, results in a spot 36 source of light rather than a point 32 source. Such provides one of the challenges in measuring the visual defects or an eye.
It is typical in the art of eye measurements to form a collimated beam and attempt to focus the collimated beam onto the retina, using lenses and lens so combinations with the optics of the eye to produce the smallest possible spot 36, as earlier described with reference to FIG 4. Lenses and focusing techniques typically take valuable time and include multiple attempts to focus a spot on the retina using various lenses and lens combinations to accommodate each unique vision of each patient being measured. With the present invention, and the understanding that most of the blurring results from the curvature of the cornea, the present invention eliminates the need to find lenses or fens combinations to minimize the size of the spot on the retina that is used as the secondary source of radiation.
With reference again to the embodiment described in FIGS. 1 and 5, the optical wavefronts 40 scattered from the retina 18 are transferred by a series of optical elements, which will be described in further detail later in this section, to a wavefront sensor 42, which wavefront sensor divides each incident wavefront into a group of "wavelets", referred to herein with numeral 50, using an opaque plate having a planar array of apertures 46 as illustrated with reference to FIG. 5.
Further, the wavefront sensor 42 records the position 48 at which each wavelet 50 passing through the aperture 46 strikes a detector plane 54 such as a charged coupled device (CCD) herein provided as one preferred embodiment, which plane is held a ~ 5 fixed small distance 56 behind the plate 44. The transverse displacement 58 of each wavelet 50 at the GCD detector plane 54 from a collimated light reference position 60 is then used to calculate a wavefront slope at each position of the apertures 46 within the planar aperture array. Alternate methods exist for using partial derivative data resulting from the measurements of the slope to calculate the 2o wavefront 40. One acceptable approach is that used by Liang et al. in the aforementioned paper where the wavefront is closely approximated using Zernike polynomials.
At each position 48, a spot 62 typically extending beyond the light measurement area of one CCD element 64 is produced. As earlier discussed, 25 blurring and a large diffraction limited spot make it difficult to make measurements.
Thus, reducing blurring improves measurement at the detector plane 54.
With reference again to FIG. 1, in one preferred embodiment of the present invention, the apparatus 10 includes the projected beam 12 of linearly polarized light (S-component) emitted from a diode laser 66 (670 nm, 3 mW by way of example), so which beam of light passes through an electro-mechanical shutter 68, which controls the duration of light exposure on the eye 14 of the patient, and in particular, the exposure of the retina 18 of the eye 14 illustrated with reference again to FIG. 2. It is expected that alternate sources of light, for example, non-coherent and non-polarized, as well as alternate light transmitting techniques will come to the mind of those skilled in the art without deviating from the teaching of the present invention.
As herein described, the use of coherent light from a laser and polarization techniques are presently preferred. When the shutter 68 is open, the projected beam 12, collimated light from the diode laser 66, is directed by a long focal length lens 70 for focusing on the anterior surface 22 of the cornea 24 of the eye 14, as illustrated with reference yet again to FIG. 2, passing through the pupil 72 and lens 28 of the eye 14, and onto the retina 18 as the small measurable spot 16. In an alternate embodiment, lens 70 comprises a zoom lens for varying the focus and moving the focus location as desired. By focusing on the cornea 24, the measurement is minimally dependent on the curvature of the cornea. However, other locations proximate the corneal surface are acceptable.
While diffraction and various aberrations are present, the present invention avoids the aberration effects from the cornea which typically dominate. The lens 28 of the eye 14 contributes a relatively small aberration effect when compared to that of the cornea 24. Further, and with regard to the selection of lens 70, selecting a lens with a short focal length would provide a large angle 13, a well focused point 78 on the surface of the cornea 24, and less aberration effects from the cornea .
2o However, a large angle 13 results in an undesirably larger retinal spot 16.
The use of a smaller angle 13 herein described provides a larger focus point on the cornea 24 but the more desirable smaller spot 16 on the retina 18. The spot 16 will depend on the wavelength and starting point size and focal length of the lens 70 selected. In preferred embodiments of the present invention, lenses with focal lengths of 25 approximately one half meter are selected for the lens 70. A 100 mm lens 70 has been effectively used.
In one preferred embodiment herein described, a mirror 74 and polarization beam splitter 76 direct the projected beam 12 to the focus point 78 on the anterior surface 20 of the cornea 24. The projected beam 12, focused on the anterior surface 22 of the cornea 24, provides the measurable spot 16 as a light source (about 1.5 3o milliradians in visual space, by way of example) on the retina 18 of the eye 14 being measured, as illustrated with reference again to FIG. 2. Such a spot 16 provides an acceptable substitute for a diffraction limited spot typically sought.
By way of one preferred example of use, a method for measuring vision characteristics of the eye 14 includes directing the beam 12 through the long focal length lens 70 for providing the small angle 13, as illustrated with reference again to FIG. 2, about an optical path for passing the beam 12 through the pupil 72 of the eye 14. The beam 12 is first focused at a fixed location without the eye or patient in place. All measuring equipment, the apparatus 10, is arranged without the patient in place and a convenient time prior to measuring. Then, the patient is positioned such that the anterior surface of the eye 14 of a patient is located at the fixed location 78 (Fig. 2) which is a preferred embodiment is the anterior surface of the cornea. This places a finite source of secondary radiation, the spot 16, as herein described, on the retina 18 of the eye 14, which provides light emitted from the retina 18 and through the pupil 72 as a reflected wavefront, the wavefront 38, described with reference to FIG. 3B. This wavefrant 38 is directed onto the wavefront analyzer 42 for measurement.
In a preferred embodiment, the laser power reaching the eye is physically limited to a maximum of 7NW. In measurements on human eyes using the apparatus 10, a laser pulse duration of 700 ms was used so that the total energy entering the eye would not exceed 4.9 NJ. For comparison, according to the ANSI
standard for direct "intrabeam" viewing, the maximum permissible exposure to a laser at the wavelength used is 530 NJ. Thus, the probing laser energies effectively used in the present invention are two orders of magnitude below an "eye-safe"
limit.
With reference again to FIG. 2, the light diffusely reflected by the retina 18 produces the wavefront 40, a distorted wavefront at the pupil plane due to the eye's aberrations. Diffuse reflection makes the returning light from the retina depolarized, 2s containing not only an S-component but also a P-component of polarization light.
The polarization beam sputter 76 in front of the eye 14 will only let the P-component pass through it and downstream to the wavefront sensor 42. The S-component is essentially totally reflected towards the diode laser 66. Because the light reflected by corneal surfaces preserves the polarization of the incoming beam (S-polarized), so the corneal reflection is reflected by the beam splitter 76, and is thus rejected from the path 80 heading toward the wavefront sensor 42. The P-component of the aberrated wavefront 40 at the subject's pupil plane is then recreated by the combination of lens 82 and lens 84, at a trial lens plane 86 indicated as "Trial Lens"
in F1G. 2. In one preferred embodiment, the diameter and the aperture of the lens 82 and lens 84 are 40 mm and 120 mm, respectively. The combination of lens 82 and lens 84 form an afocal image system with the eye's pupil 72 (the object plane) at the focal plane of the lens 82, and the image plane, trial lens 86, at the focal plane of the lens 84. Similarly, lens 88 and lens 90 also form an afocal image system with the possible trial lens 86 at the focal plane of the lens 88 and the lens combination at the image plane at the focal plane of the lens 90. The focal plane of the lens 90 is located at the plate 44 of the wavefront sensor 42, earlier described with reference ~o to FIG. 5. In a preferred embodiment, Lens 4 has a diameter of 30 mm and a focal length of 80 mm. Lens 5 has a diameter of 40 mm and a focal length of 120 mm.
With the apparatus 10, measured wavefront slopes leaving the eye 14 are recreated at the aperture of plate 44, and magnified by a factor of 1.5. Magnification of the wavefront 40 at the detector plane 54 reduces the wavefront slopes by the same degree. This extends the dynamic range of eye aberrations over which the device can measure.
By way of further explanation about the trial lens location or plane 86, because the wavefront 40 leaving the eye 14 is recreated at this location 86 with unity magnification, a trial lens of known refractive power inserted at this point 2o should exactly compensate for a prescribed refractive error. For example, a perfect five diopter spherical fens placed at this location should remove five diopters of spherical curvature from an incident wavefront, without altering other aberrations that may exist in the wavefront. The capability of inserting trial lenses at this location 86 extends the dynamic measurement range of the apparatus 10, without affecting 25 wavefront analyzing capability.
In a preferred embodiment, and with reference again to FIG. 5, the aperture array 46 of the wavefront sensor 42 samples the incident wavefront 40 which forms focus spots 62 on the detector plane 54 This is repeated at the detector plane for each aperture within the array 46. As a result, a localized direction of the 3o wavefront 40 is determined for each of a plurality of wavelets 50 within the array. By way of example, the use of lenslets 92 (as an alternate embodiment of apertures 46 alone), with a focal length of 87 mm and a dimension of 0.768 mm, forms an aerial image of the retinal light source (the spot 16 described earlier with reference to FIG.
2) on the detector plane 54. If a plane wave, corresponding to an aberration-free eye, were measured, the lenslet 92 array would produce a regular array of focused spots on the image sensor. When the real eye 14 is measured, the wave aberration 5 in the eye will displace the focus spot 62, described earlier with reference to FIG. 5, of each lenslet 92 from the reference position 60 to the measured position 50 in proportion to the local slopes of the wavefront 40. The wavefront sensor 42 measures the local wavefront slopes at an array of sampling locations across the pupil 72, from which the wavefront 40 itself can be reconstructed.
As illustrated again with reference to FIG. 1, in an alternate embodiment of to present inventive methods, a fixation target 94 may be used to insure that the patient is looking along the optical axis of the apparatus 10. The patient is asked to fixate on the target 94 located at the focal plane of a lens 96. By linearly moving the optics combination 96 of the fixation target 94, it is possible to provide the eye's spherical correction, and hence to make the fixation target 94 clearly visible to the subject. In one preferred use, the image of the fixation target 94 is intentionally under-corrected for each patient to ensure that the measured eye 14 is focused at infinity. By way of example, the fixation target consists of a dark cross-hair and a number of concentric circles on a white background that is back-illuminated by a tungsten lamp. The 2o patient is asked to look at the center of the cross-hair. The position of the eye 14 in reference to the optical axis is recorded by CCD camera 98. This CCD camera 98 is conjugate, in effect coupled, to the eye's pupil 72 through a second lens combination 100, preferably mounted on the camera, and the lenses 82, 84. In one method of the present invention, the camera 98 is used to view the eye 14 for aligning the eye 25 within the path of the beam 12 for assuring that the beam passes through the pupil 72. The camera 98 is also useful in an alternate embodiment of the present invention, for viewing the size of the spot 16 formed on the retina 18 as the user changes the focus point 78 through various anterior surface locations in obtaining an optimum size of the spot 16.
3o By way of further example of effective uses of the present invention, the earlier described Zernike coefficients of an eye, taken collectively, can be used as discriminating as fingerprints or DNA. The Zernike coefficients for a person might be used for identification of that person for permitting access to a confidential area, allowing funds to be distributed through an ATM, and the like. Further, the present invention allows eye measurements for a passive subject, such as in the examination of a corpse or sedated animal. The present invention is operable with human eyes, as herein described, as well as those of an animal, bird, or fish eyes, and in particular, non-biological focusing optical systems such as those found in cameras. The present invention is useful in developing optimized aspheric systems, where an aspheric element need to be designed last by observing and producing a single custom aspheric element that corrects the system. By way of example, the aspheric system may be designed on paper except for the correcting element, which would be developed experimentally using the present invention as herein described.
The design of afocal systems such as a telescope, a searchlight, or a projector which require an added corrective focus element will benefit from the present invention.
Many modifications and other embodiments of the invention will come to the mind of one skilled in the art having the benefit of the teachings presented in the foregoing descriptions and the associated drawings. Therefore, it is to be understood that the invention is not to be limited to the specific embodiments disclosed, and that modifications and alternate embodiments are intended to be included within the scope of the appended claims.
It is further an object to measure such characteristics without requiring patient or operator feedback.
These and other objects, advantages and features of the present invention are provided by a method aspect of the invention for measuring optical characteristics of an optical system including the focusing of an optical beam proximate an anterior surface of the optical system for placing a finite source of secondary radiation on a focal surtace of the optical system, which secondary radiation is emitted from the focal surface as a reflected wavefront of radiation that passes through the optical system, projecting the reflected wavefront onto a wavefront analyzer, and measuring characteristics of the optical system associated with the reflected wavefront. In a preferred embodiment, the method includes 2o measuring defects of the eye which includes the steps of focusing an optical beam onto an anterior surface of the eye for providing a finite source of secondary radiation on the retina of the eye, which secondary radiation is emitted from the retina as a reflected wavefront of radiation that passes through the eye;
directing the reflected wavefront onto a wavefront analyzer; and measuring distortions associated with the reflected wavefront. A preferred embodiment of the invention includes the step of focusing the projected optical beam on the anterior surface of the cornea.
An apparatus for effectively performing such measurements includes focusing means for focusing an optical beam onto an anterior surface of the optical system or eye for providing a finite secondary radiation source on the focal surface, or retina of so the eye, which finite secondary radiation source is emitted from the retina as a reflected wavefront of radiation that passes through the eye, directing means for directing the reflected wavefront onto a wavefront analyzer, and a wavefront analyzer for measuring distortions associated with the reflected wavefront. In one preferred embodiment of the present invention, a laser beam is focused onto the surface of the cornea with a long focal length lens which converges the beam through a small angle for passing through the iris of the eye and providing a finite s secondary radiation source on the retina of the eye, which mite secondary radiation source is emitted from the retina through the optics of the eye as the wavefront to be measured.
Brief Description of Drawings A preferred embodiment of the invention as well as alternate embodiments are described by way of example with reference to the accompanying drawings in which:
FIG. 1 is a diagrammatic illustration of an apparatus for measuring visual defects of an eye, according to the present invention;
~s FIG. 2 is a diagrammatic illustration of a eye to be measured by the apparatus of the present invention;
FIGS. 3A and 3B are diagrammatic illustrations of an ideal eye with perfect vision and an aberrated ideal eye, respectively;
FIG. 4 is a diagrammatic illustration of an eye being measure with collimated 20 light focused on the retina to a diffraction limited spot; and FIG. 5 is a partial perspective view of a pinhole imaging plate and detector plane of a wavefront sensor used in a preferred embodiment of the present invention.
25 Detailed Description of Preferred Embodiments The present invention will be described more fully hereinafter with reference to the accompanying drawings, in which preferred embodiments of the invention are shown. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein.
Rather, 3o these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
Like numbers refer to like elements throughout.
A preferred embodiment of a measurement apparatus 10 of the present invention is herein initially described with reference to the schematic diagram of FIG.1. A projected beam 12 of optical radiation is directed into an eye 14 to be measured, so that a small area or measurable spot 16 is formed as a secondary 5 radiation source in the foveal region of the retina 18 as illuminated with reference to FIG. 2. Specifically, the beam 12 is focused through a small angle 13 onto an anterior surface 20 of the eye 14, and in a preferred embodiment of the present invention, focused on an anterior corneal surface 22 of the cornea 24 for further projection through the iris 26 and lens 28 and onto the retina 18.
By way of further background, consider an "ideal" eye 14i with ideal vision, as illustrated with reference to FIG. 3A. The ideal eye 14i, having the ideal cornea 24i and ideal lens 28i will focus a collimated beam of light, illustrated with arrows 30 to a point 32, as the secondary radiation source, on the ideal retina 18i. This point 32 would then be a point source of light which would be diffusely reflected back through ~5 the optics of the ideal eye 14i as a sequence of plane waves 34. In actual fact, even an eye having perfect vision, as illustrated by way of example with reference to FIG. 4, will produce a diffraction limited illuminated area or spot 36, as the secondary radiation source, on the retina of the eye, under the best possible circumstances. In a typical eye, as illustrated with reference to FIG. 4, such a spot 36 is even larger, 2o where most of the blurring will be due to finite aberrations found in typical eyes. By way of further example, in an aberrated eye 14a, if the point source 32 could be realized, distorted wavefronts 38 result as illustrated with reference to FIG.
3B.
Having to deal with a series of distorted wavefronts 38 resulting from aberrations, and further dealing with a blurring of such distorted wavefronts 38 resulting from 25 diffraction effects and the finite aberrations of the eye, results in a spot 36 source of light rather than a point 32 source. Such provides one of the challenges in measuring the visual defects or an eye.
It is typical in the art of eye measurements to form a collimated beam and attempt to focus the collimated beam onto the retina, using lenses and lens so combinations with the optics of the eye to produce the smallest possible spot 36, as earlier described with reference to FIG 4. Lenses and focusing techniques typically take valuable time and include multiple attempts to focus a spot on the retina using various lenses and lens combinations to accommodate each unique vision of each patient being measured. With the present invention, and the understanding that most of the blurring results from the curvature of the cornea, the present invention eliminates the need to find lenses or fens combinations to minimize the size of the spot on the retina that is used as the secondary source of radiation.
With reference again to the embodiment described in FIGS. 1 and 5, the optical wavefronts 40 scattered from the retina 18 are transferred by a series of optical elements, which will be described in further detail later in this section, to a wavefront sensor 42, which wavefront sensor divides each incident wavefront into a group of "wavelets", referred to herein with numeral 50, using an opaque plate having a planar array of apertures 46 as illustrated with reference to FIG. 5.
Further, the wavefront sensor 42 records the position 48 at which each wavelet 50 passing through the aperture 46 strikes a detector plane 54 such as a charged coupled device (CCD) herein provided as one preferred embodiment, which plane is held a ~ 5 fixed small distance 56 behind the plate 44. The transverse displacement 58 of each wavelet 50 at the GCD detector plane 54 from a collimated light reference position 60 is then used to calculate a wavefront slope at each position of the apertures 46 within the planar aperture array. Alternate methods exist for using partial derivative data resulting from the measurements of the slope to calculate the 2o wavefront 40. One acceptable approach is that used by Liang et al. in the aforementioned paper where the wavefront is closely approximated using Zernike polynomials.
At each position 48, a spot 62 typically extending beyond the light measurement area of one CCD element 64 is produced. As earlier discussed, 25 blurring and a large diffraction limited spot make it difficult to make measurements.
Thus, reducing blurring improves measurement at the detector plane 54.
With reference again to FIG. 1, in one preferred embodiment of the present invention, the apparatus 10 includes the projected beam 12 of linearly polarized light (S-component) emitted from a diode laser 66 (670 nm, 3 mW by way of example), so which beam of light passes through an electro-mechanical shutter 68, which controls the duration of light exposure on the eye 14 of the patient, and in particular, the exposure of the retina 18 of the eye 14 illustrated with reference again to FIG. 2. It is expected that alternate sources of light, for example, non-coherent and non-polarized, as well as alternate light transmitting techniques will come to the mind of those skilled in the art without deviating from the teaching of the present invention.
As herein described, the use of coherent light from a laser and polarization techniques are presently preferred. When the shutter 68 is open, the projected beam 12, collimated light from the diode laser 66, is directed by a long focal length lens 70 for focusing on the anterior surface 22 of the cornea 24 of the eye 14, as illustrated with reference yet again to FIG. 2, passing through the pupil 72 and lens 28 of the eye 14, and onto the retina 18 as the small measurable spot 16. In an alternate embodiment, lens 70 comprises a zoom lens for varying the focus and moving the focus location as desired. By focusing on the cornea 24, the measurement is minimally dependent on the curvature of the cornea. However, other locations proximate the corneal surface are acceptable.
While diffraction and various aberrations are present, the present invention avoids the aberration effects from the cornea which typically dominate. The lens 28 of the eye 14 contributes a relatively small aberration effect when compared to that of the cornea 24. Further, and with regard to the selection of lens 70, selecting a lens with a short focal length would provide a large angle 13, a well focused point 78 on the surface of the cornea 24, and less aberration effects from the cornea .
2o However, a large angle 13 results in an undesirably larger retinal spot 16.
The use of a smaller angle 13 herein described provides a larger focus point on the cornea 24 but the more desirable smaller spot 16 on the retina 18. The spot 16 will depend on the wavelength and starting point size and focal length of the lens 70 selected. In preferred embodiments of the present invention, lenses with focal lengths of 25 approximately one half meter are selected for the lens 70. A 100 mm lens 70 has been effectively used.
In one preferred embodiment herein described, a mirror 74 and polarization beam splitter 76 direct the projected beam 12 to the focus point 78 on the anterior surface 20 of the cornea 24. The projected beam 12, focused on the anterior surface 22 of the cornea 24, provides the measurable spot 16 as a light source (about 1.5 3o milliradians in visual space, by way of example) on the retina 18 of the eye 14 being measured, as illustrated with reference again to FIG. 2. Such a spot 16 provides an acceptable substitute for a diffraction limited spot typically sought.
By way of one preferred example of use, a method for measuring vision characteristics of the eye 14 includes directing the beam 12 through the long focal length lens 70 for providing the small angle 13, as illustrated with reference again to FIG. 2, about an optical path for passing the beam 12 through the pupil 72 of the eye 14. The beam 12 is first focused at a fixed location without the eye or patient in place. All measuring equipment, the apparatus 10, is arranged without the patient in place and a convenient time prior to measuring. Then, the patient is positioned such that the anterior surface of the eye 14 of a patient is located at the fixed location 78 (Fig. 2) which is a preferred embodiment is the anterior surface of the cornea. This places a finite source of secondary radiation, the spot 16, as herein described, on the retina 18 of the eye 14, which provides light emitted from the retina 18 and through the pupil 72 as a reflected wavefront, the wavefront 38, described with reference to FIG. 3B. This wavefrant 38 is directed onto the wavefront analyzer 42 for measurement.
In a preferred embodiment, the laser power reaching the eye is physically limited to a maximum of 7NW. In measurements on human eyes using the apparatus 10, a laser pulse duration of 700 ms was used so that the total energy entering the eye would not exceed 4.9 NJ. For comparison, according to the ANSI
standard for direct "intrabeam" viewing, the maximum permissible exposure to a laser at the wavelength used is 530 NJ. Thus, the probing laser energies effectively used in the present invention are two orders of magnitude below an "eye-safe"
limit.
With reference again to FIG. 2, the light diffusely reflected by the retina 18 produces the wavefront 40, a distorted wavefront at the pupil plane due to the eye's aberrations. Diffuse reflection makes the returning light from the retina depolarized, 2s containing not only an S-component but also a P-component of polarization light.
The polarization beam sputter 76 in front of the eye 14 will only let the P-component pass through it and downstream to the wavefront sensor 42. The S-component is essentially totally reflected towards the diode laser 66. Because the light reflected by corneal surfaces preserves the polarization of the incoming beam (S-polarized), so the corneal reflection is reflected by the beam splitter 76, and is thus rejected from the path 80 heading toward the wavefront sensor 42. The P-component of the aberrated wavefront 40 at the subject's pupil plane is then recreated by the combination of lens 82 and lens 84, at a trial lens plane 86 indicated as "Trial Lens"
in F1G. 2. In one preferred embodiment, the diameter and the aperture of the lens 82 and lens 84 are 40 mm and 120 mm, respectively. The combination of lens 82 and lens 84 form an afocal image system with the eye's pupil 72 (the object plane) at the focal plane of the lens 82, and the image plane, trial lens 86, at the focal plane of the lens 84. Similarly, lens 88 and lens 90 also form an afocal image system with the possible trial lens 86 at the focal plane of the lens 88 and the lens combination at the image plane at the focal plane of the lens 90. The focal plane of the lens 90 is located at the plate 44 of the wavefront sensor 42, earlier described with reference ~o to FIG. 5. In a preferred embodiment, Lens 4 has a diameter of 30 mm and a focal length of 80 mm. Lens 5 has a diameter of 40 mm and a focal length of 120 mm.
With the apparatus 10, measured wavefront slopes leaving the eye 14 are recreated at the aperture of plate 44, and magnified by a factor of 1.5. Magnification of the wavefront 40 at the detector plane 54 reduces the wavefront slopes by the same degree. This extends the dynamic range of eye aberrations over which the device can measure.
By way of further explanation about the trial lens location or plane 86, because the wavefront 40 leaving the eye 14 is recreated at this location 86 with unity magnification, a trial lens of known refractive power inserted at this point 2o should exactly compensate for a prescribed refractive error. For example, a perfect five diopter spherical fens placed at this location should remove five diopters of spherical curvature from an incident wavefront, without altering other aberrations that may exist in the wavefront. The capability of inserting trial lenses at this location 86 extends the dynamic measurement range of the apparatus 10, without affecting 25 wavefront analyzing capability.
In a preferred embodiment, and with reference again to FIG. 5, the aperture array 46 of the wavefront sensor 42 samples the incident wavefront 40 which forms focus spots 62 on the detector plane 54 This is repeated at the detector plane for each aperture within the array 46. As a result, a localized direction of the 3o wavefront 40 is determined for each of a plurality of wavelets 50 within the array. By way of example, the use of lenslets 92 (as an alternate embodiment of apertures 46 alone), with a focal length of 87 mm and a dimension of 0.768 mm, forms an aerial image of the retinal light source (the spot 16 described earlier with reference to FIG.
2) on the detector plane 54. If a plane wave, corresponding to an aberration-free eye, were measured, the lenslet 92 array would produce a regular array of focused spots on the image sensor. When the real eye 14 is measured, the wave aberration 5 in the eye will displace the focus spot 62, described earlier with reference to FIG. 5, of each lenslet 92 from the reference position 60 to the measured position 50 in proportion to the local slopes of the wavefront 40. The wavefront sensor 42 measures the local wavefront slopes at an array of sampling locations across the pupil 72, from which the wavefront 40 itself can be reconstructed.
As illustrated again with reference to FIG. 1, in an alternate embodiment of to present inventive methods, a fixation target 94 may be used to insure that the patient is looking along the optical axis of the apparatus 10. The patient is asked to fixate on the target 94 located at the focal plane of a lens 96. By linearly moving the optics combination 96 of the fixation target 94, it is possible to provide the eye's spherical correction, and hence to make the fixation target 94 clearly visible to the subject. In one preferred use, the image of the fixation target 94 is intentionally under-corrected for each patient to ensure that the measured eye 14 is focused at infinity. By way of example, the fixation target consists of a dark cross-hair and a number of concentric circles on a white background that is back-illuminated by a tungsten lamp. The 2o patient is asked to look at the center of the cross-hair. The position of the eye 14 in reference to the optical axis is recorded by CCD camera 98. This CCD camera 98 is conjugate, in effect coupled, to the eye's pupil 72 through a second lens combination 100, preferably mounted on the camera, and the lenses 82, 84. In one method of the present invention, the camera 98 is used to view the eye 14 for aligning the eye 25 within the path of the beam 12 for assuring that the beam passes through the pupil 72. The camera 98 is also useful in an alternate embodiment of the present invention, for viewing the size of the spot 16 formed on the retina 18 as the user changes the focus point 78 through various anterior surface locations in obtaining an optimum size of the spot 16.
3o By way of further example of effective uses of the present invention, the earlier described Zernike coefficients of an eye, taken collectively, can be used as discriminating as fingerprints or DNA. The Zernike coefficients for a person might be used for identification of that person for permitting access to a confidential area, allowing funds to be distributed through an ATM, and the like. Further, the present invention allows eye measurements for a passive subject, such as in the examination of a corpse or sedated animal. The present invention is operable with human eyes, as herein described, as well as those of an animal, bird, or fish eyes, and in particular, non-biological focusing optical systems such as those found in cameras. The present invention is useful in developing optimized aspheric systems, where an aspheric element need to be designed last by observing and producing a single custom aspheric element that corrects the system. By way of example, the aspheric system may be designed on paper except for the correcting element, which would be developed experimentally using the present invention as herein described.
The design of afocal systems such as a telescope, a searchlight, or a projector which require an added corrective focus element will benefit from the present invention.
Many modifications and other embodiments of the invention will come to the mind of one skilled in the art having the benefit of the teachings presented in the foregoing descriptions and the associated drawings. Therefore, it is to be understood that the invention is not to be limited to the specific embodiments disclosed, and that modifications and alternate embodiments are intended to be included within the scope of the appended claims.
Claims (18)
PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. An apparatus (10) for measuring vision characteristics of an eye (14), the apparatus (10) comprising means (66) for placing a source of secondary radiation (36) on a retina (18) of the eye (14), which secondary radiation (36) is emitted therefrom as a reflected wavefront (38) of radiation that passes through the eye (14) and directed onto a wavefront sensor (42) for measuring distortions associated with the reflected wavefront (38), the apparatus (10) characterized by:
focusing means (70) converging an optical beam (12) through a small angle (13) for focusing the optical beam (12) at an anterior position (20) to the retina (18) of the eye (14) to form the source of secondary radiation (36) as an illuminated area on the retina (18) of the eye (14).
focusing means (70) converging an optical beam (12) through a small angle (13) for focusing the optical beam (12) at an anterior position (20) to the retina (18) of the eye (14) to form the source of secondary radiation (36) as an illuminated area on the retina (18) of the eye (14).
2. The apparatus (10) according to claim 1, wherein the focusing means (70) comprise a long focal length lens (70) for converging the optical beam (12) through the small angle (13).
3. The apparatus (10) according to claim 2, wherein the long focal length lens (70) has a focal length of at least one half meter in length.
4. The apparatus (10) according to claim 2, wherein the focusing means (70) comprise a zoom lens (70) for converging the optical beam (12) through the small angle (13) and for converging the optical beam (12) onto one (22) of a plurality of anterior positions (20).
5. The apparatus (10) according to claim 1, wherein the anterior position (20) includes an anterior surface (22) of the eye (14).
6. The apparatus (10) according to claim 1, wherein the anterior position (20) includes an anterior surface (22) of the cornea (24) of the eye (14).
7. The apparatus (10) according to claim 1, wherein the optical beam (12) comprises a laser beam.
8. The apparatus (10) according to claim 1, further comprising polarizing means (76) for polarizing the optical beam (12).
9. The apparatus (10) according to claim 1, further comprising a polarization beam splitter (76) for reflecting an S-component of the reflected wavefront (40) and for transmitting a P-component of the reflected wavefront (40) as a polarized wavefront therethrough.
10. A method for measuring vision characteristics of an eye (14), the method comprising placing a source of secondary radiation. (38) on a retina (18) of the eye (14) for emitting the secondary radiation therefrom as a reflected wavefront (40) passing through the eye (14), and directing the reflected wavefront (40) onto a wavefront sensor (42) for measuring distortions associated therewith, the method characterized by:
converging an optical beam (12) through a small angle (13) and focusing the optical beam (12) to a position anterior (22) the retina (18) of the eye (14) for forming the source of secondary radiation (38) as an illuminated area on the retina (18) of the eye (14).
converging an optical beam (12) through a small angle (13) and focusing the optical beam (12) to a position anterior (22) the retina (18) of the eye (14) for forming the source of secondary radiation (38) as an illuminated area on the retina (18) of the eye (14).
11. The method according to Claim 90, wherein the optical beam (12) converging includes use of a long focal length lens (70) placed in a path of the optical beam (12).
12. The method according to Claim 11, wherein the long focal length lens (70) has a focal length of at least one half meter in length.
13. The method according to Claim 10, wherein the optical beam (12) converging includes use of a zoom lens (70) for converging the optical beam (12) onto one (22) of a plurality of anterior positions.
14. The method according to Claim 10, wherein the anterior position (20) includes an anterior surface (20) of the eye (14) upon which the optical beam (12) is focused.
15. The method according to Claim 10, wherein the anterior position (20) includes an anterior surface (22) of the cornea (24) of the eye (14) upon which the optical beam (12) is focused.
16. The method according to Claim 10, wherein the optical beam (12) comprises a laser beam.
17. The method according to Claim 10, further comprising polarizing (78) the optical beam (12).
18. The method according to Claim 17, further comprising splitting (76) of the polarized beam (12) for reflecting an S-component of the reflected wavefront (40) and for transmitting a P-component thereof as a polarized wavefront therethrough.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US9708698P | 1998-08-19 | 1998-08-19 | |
| US60/097,086 | 1998-08-19 | ||
| PCT/US1999/008709 WO2000010448A1 (en) | 1998-08-19 | 1999-04-20 | Apparatus and method for measuring vision defects of a human eye |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2338060A1 CA2338060A1 (en) | 2000-03-02 |
| CA2338060C true CA2338060C (en) | 2005-03-15 |
Family
ID=22260948
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002338060A Expired - Lifetime CA2338060C (en) | 1998-08-19 | 1999-04-20 | Apparatus and method for measuring vision defects of a human eye |
Country Status (12)
| Country | Link |
|---|---|
| US (1) | US6270221B1 (en) |
| EP (1) | EP1105037B1 (en) |
| JP (1) | JP3599276B2 (en) |
| AT (1) | ATE222074T1 (en) |
| AU (1) | AU747840B2 (en) |
| BR (1) | BR9913130A (en) |
| CA (1) | CA2338060C (en) |
| DE (1) | DE69902549T2 (en) |
| ES (1) | ES2184445T3 (en) |
| MX (1) | MXPA01001167A (en) |
| PT (1) | PT1105037E (en) |
| WO (1) | WO2000010448A1 (en) |
Families Citing this family (96)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6450641B2 (en) * | 1992-06-02 | 2002-09-17 | Lasersight Technologies, Inc. | Method of corneal analysis using a checkered placido apparatus |
| US6547395B1 (en) * | 1998-02-06 | 2003-04-15 | Wavefront Sciences, Inc. | Methods of measuring moving objects and reducing exposure during wavefront measurements |
| US6598975B2 (en) * | 1998-08-19 | 2003-07-29 | Alcon, Inc. | Apparatus and method for measuring vision defects of a human eye |
| DE19904753C1 (en) * | 1999-02-05 | 2000-09-07 | Wavelight Laser Technologie Gm | Device for photorefractive corneal surgery of the eye for correcting high-order visual defects |
| US6619799B1 (en) * | 1999-07-02 | 2003-09-16 | E-Vision, Llc | Optical lens system with electro-active lens having alterably different focal lengths |
| DE19938203A1 (en) | 1999-08-11 | 2001-02-15 | Aesculap Meditec Gmbh | Method and device for correcting visual defects in the human eye |
| US7803153B2 (en) * | 1999-12-29 | 2010-09-28 | New England College Of Optometry | Method for preventing myopia progression through identification and correction of optical aberrations |
| US7455407B2 (en) * | 2000-02-11 | 2008-11-25 | Amo Wavefront Sciences, Llc | System and method of measuring and mapping three dimensional structures |
| US6550917B1 (en) | 2000-02-11 | 2003-04-22 | Wavefront Sciences, Inc. | Dynamic range extension techniques for a wavefront sensor including use in ophthalmic measurement |
| CA2377852C (en) | 2000-04-25 | 2007-08-07 | Alcon Universal Ltd. | Spatial filter for enhancing hartmann-shack images and associated methods |
| US6565209B2 (en) | 2000-04-25 | 2003-05-20 | Alcon Universal Ltd. | Range-extending system and spatial filter for enhancing Hartmann-Shack images and associated methods |
| US6460997B1 (en) * | 2000-05-08 | 2002-10-08 | Alcon Universal Ltd. | Apparatus and method for objective measurements of optical systems using wavefront analysis |
| KR20030036192A (en) * | 2000-05-23 | 2003-05-09 | 파마시아 그로닌겐 비.브이. | Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations |
| US8020995B2 (en) | 2001-05-23 | 2011-09-20 | Amo Groningen Bv | Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations |
| US6616279B1 (en) | 2000-10-02 | 2003-09-09 | Johnson & Johnson Vision Care, Inc. | Method and apparatus for measuring wavefront aberrations |
| JP4606559B2 (en) * | 2000-10-10 | 2011-01-05 | 株式会社トプコン | Ophthalmic optical characteristic measuring device |
| US6428533B1 (en) * | 2000-10-17 | 2002-08-06 | 20/10 Perfect Vision Optische Geraete Gmbh | Closed loop control for refractive laser surgery (LASIK) |
| US6464357B1 (en) * | 2000-10-20 | 2002-10-15 | Kestrel Corporation | Wavefront characterization of corneas |
| UA59488C2 (en) * | 2001-10-03 | 2003-09-15 | Василь Васильович Молебний | Method for measuring wave aberrations of eye and device for its realization (variants) |
| ATE508676T1 (en) | 2001-03-15 | 2011-05-15 | Amo Wavefront Sciences Llc | TOPOGRAPHIC WAVEFRONT ANALYSIS SYSTEM AND IMAGING METHOD FOR AN OPTICAL SYSTEM |
| US7111938B2 (en) | 2001-04-27 | 2006-09-26 | Novartis Ag | Automatic lens design and manufacturing system |
| US6598974B2 (en) * | 2001-05-08 | 2003-07-29 | Johnson & Johnson Vision Care, Inc. | Method and apparatus for measuring wavefront aberrations |
| US6394605B1 (en) | 2001-05-23 | 2002-05-28 | Alcon Universal Ltd. | Fogging method for a wavefront sensor |
| US6582079B2 (en) * | 2001-06-05 | 2003-06-24 | Metrologic Instruments, Inc. | Modular adaptive optical subsystem for integration with a fundus camera body and CCD camera unit and improved fundus camera employing same |
| US6964480B2 (en) | 2001-08-31 | 2005-11-15 | Metrologic Instruments, Inc. | Ophthalmic instrument having adaptive optic subsystem with multiple stage phase compensator |
| US6575572B2 (en) * | 2001-09-21 | 2003-06-10 | Carl Zeiss Ophthalmic Systems, Inc. | Method and apparatus for measuring optical aberrations of an eye |
| US6554429B1 (en) | 2001-10-15 | 2003-04-29 | Alcon, Inc. | Method for determining accommodation |
| US6712466B2 (en) * | 2001-10-25 | 2004-03-30 | Ophthonix, Inc. | Eyeglass manufacturing method using variable index layer |
| US7034949B2 (en) | 2001-12-10 | 2006-04-25 | Ophthonix, Inc. | Systems and methods for wavefront measurement |
| US6781681B2 (en) | 2001-12-10 | 2004-08-24 | Ophthonix, Inc. | System and method for wavefront measurement |
| US6802605B2 (en) * | 2001-12-11 | 2004-10-12 | Bausch And Lomb, Inc. | Contact lens and method for fitting and design |
| US6736509B2 (en) * | 2001-12-21 | 2004-05-18 | Bausch And Lomb, Inc. | Aberrometer illumination apparatus and method |
| EP1637101B1 (en) | 2002-01-14 | 2007-11-21 | Alcon, Inc | Adaptive wavefront method for ophthalmic surgery |
| US6682196B2 (en) | 2002-01-14 | 2004-01-27 | Alcon, Inc. | Adaptive wavefront modulation system and method for ophthalmic surgery |
| US6698889B2 (en) | 2002-01-14 | 2004-03-02 | Alcon, Inc. | Adaptive wavefront modulation system and method for refractive laser surgery |
| US6761454B2 (en) * | 2002-02-13 | 2004-07-13 | Ophthonix, Inc. | Apparatus and method for determining objective refraction using wavefront sensing |
| US20050174535A1 (en) * | 2003-02-13 | 2005-08-11 | Lai Shui T. | Apparatus and method for determining subjective responses using objective characterization of vision based on wavefront sensing |
| US7097301B2 (en) * | 2002-09-06 | 2006-08-29 | Synergeyes, Inc. | Hybrid contact lens system and method |
| US7104648B2 (en) * | 2002-09-06 | 2006-09-12 | Synergeyes, Inc. | Hybrid contact lens system and method |
| US7322694B2 (en) * | 2002-09-06 | 2008-01-29 | Synergeyes, Inc. | Hybrid contact lens system and method |
| US7163292B2 (en) * | 2002-09-06 | 2007-01-16 | Synergeyes, Inc. | Hybrid contact lens system and method |
| US6736510B1 (en) | 2003-02-04 | 2004-05-18 | Ware Tec Vision Systems, Inc. | Ophthalmic talbot-moire wavefront sensor |
| US7556378B1 (en) | 2003-04-10 | 2009-07-07 | Tsontcho Ianchulev | Intraoperative estimation of intraocular lens power |
| US7226443B1 (en) | 2003-11-07 | 2007-06-05 | Alcon Refractivehorizons, Inc. | Optimization of ablation correction of an optical system and associated methods |
| US7018039B2 (en) * | 2003-11-14 | 2006-03-28 | Synergeyes,Inc. | Contact lens |
| US7883505B2 (en) * | 2004-04-20 | 2011-02-08 | Wavetec Vision Systems, Inc. | Integrated surgical microscope and wavefront sensor |
| US20090082859A1 (en) * | 2004-10-22 | 2009-03-26 | Massachusetts Eye & Ear Infirmary | Polarization-sensitive vision prosthesis |
| US7141065B2 (en) | 2004-10-22 | 2006-11-28 | Massachusetts Eye & Ear Infirmary | Polarization-sensitive vision prosthesis |
| US20060135952A1 (en) * | 2004-12-21 | 2006-06-22 | Curatu Eugene O | Corrective intraocular lens and associated methods |
| US7401922B2 (en) * | 2005-04-13 | 2008-07-22 | Synergeyes, Inc. | Method and apparatus for reducing or eliminating the progression of myopia |
| US7543936B2 (en) * | 2005-05-06 | 2009-06-09 | Synergeyes, Inc. | Hybrid contact lens system and method of fitting |
| WO2007002487A2 (en) * | 2005-06-24 | 2007-01-04 | Boston Foundation For Sight | Scleral contact lens with grooves and method of making lens |
| US7377637B2 (en) * | 2005-10-11 | 2008-05-27 | Synergeyes, Inc. | Hybrid contact lens system and method of fitting |
| US7537339B2 (en) * | 2006-05-25 | 2009-05-26 | Synergeyes, Inc. | Hybrid contact lens system and method of fitting |
| US20080001320A1 (en) | 2006-06-28 | 2008-01-03 | Knox Wayne H | Optical Material and Method for Modifying the Refractive Index |
| US20080074611A1 (en) * | 2006-09-22 | 2008-03-27 | Meyers William E | Hybrid contact lens with improved resistance to flexure and method for designing the same |
| US20080084541A1 (en) * | 2006-10-06 | 2008-04-10 | Ming Lai | Ophthalmic system and method |
| WO2008131321A1 (en) | 2007-04-20 | 2008-10-30 | Alcon Refractivehorizons, Inc. | Adaptive wavefront modulation system and method for refractive laser surgery |
| US7828432B2 (en) | 2007-05-25 | 2010-11-09 | Synergeyes, Inc. | Hybrid contact lenses prepared with expansion controlled polymeric materials |
| US9545340B1 (en) | 2007-06-26 | 2017-01-17 | University Of Rochester | Multi-photon absorption for femtosecond micromachining and refractive index modification of tissues |
| WO2009003107A1 (en) * | 2007-06-26 | 2008-12-31 | Bausch & Lomb Incorporated | Method for modifying the refractive index of ocular tissues |
| US8157378B2 (en) * | 2007-08-23 | 2012-04-17 | Bausch & Lomb Incorporated | Eye illumination apparatus and method |
| US8333474B2 (en) | 2007-10-19 | 2012-12-18 | Wavetec Vision Systems, Inc. | Optical instrument alignment system |
| US7594729B2 (en) | 2007-10-31 | 2009-09-29 | Wf Systems, Llc | Wavefront sensor |
| US9060847B2 (en) * | 2008-05-19 | 2015-06-23 | University Of Rochester | Optical hydrogel material with photosensitizer and method for modifying the refractive index |
| WO2010054268A2 (en) | 2008-11-06 | 2010-05-14 | Wavetec Vision Systems, Inc. | Optical angular measurement system for ophthalmic applications and method for positioning of a toric intraocular lens with increased accuracy |
| US20100120013A1 (en) * | 2008-11-07 | 2010-05-13 | Mb Research Laboratories, Inc. | Procedure for long term corneal culture |
| US7695135B1 (en) | 2008-11-11 | 2010-04-13 | Boston Foundation For Sight | Scleral lens with scalloped channels or circumferential fenestrated channels |
| US8342688B1 (en) * | 2009-06-15 | 2013-01-01 | Casimir Andrew Swinger | Multifocal capable ophthalmic aberrometer |
| US8876290B2 (en) * | 2009-07-06 | 2014-11-04 | Wavetec Vision Systems, Inc. | Objective quality metric for ocular wavefront measurements |
| WO2011008606A1 (en) | 2009-07-14 | 2011-01-20 | Wavetec Vision Systems, Inc. | Determination of the effective lens position of an intraocular lens using aphakic refractive power |
| EP2453823B1 (en) | 2009-07-14 | 2015-05-13 | WaveTec Vision Systems, Inc. | Ophthalmic surgery measurement system |
| WO2011050164A1 (en) | 2009-10-21 | 2011-04-28 | Avedro, Inc. | Eye therapy |
| EP2547298B1 (en) | 2010-03-19 | 2019-05-08 | Avedro, Inc. | Systems for applying and monitoring eye therapy |
| WO2012162529A1 (en) | 2011-05-24 | 2012-11-29 | Avedro, Inc. | Systems and methods for reshaping an eye feature |
| US9020580B2 (en) * | 2011-06-02 | 2015-04-28 | Avedro, Inc. | Systems and methods for monitoring time based photo active agent delivery or photo active marker presence |
| US10813791B2 (en) | 2011-06-02 | 2020-10-27 | University Of Rochester | Method for modifying the refractive index of ocular tissues and applications thereof |
| US9144491B2 (en) | 2011-06-02 | 2015-09-29 | University Of Rochester | Method for modifying the refractive index of an optical material |
| EP4074294A1 (en) | 2012-07-16 | 2022-10-19 | Avedro, Inc. | Systems and methods for corneal cross-linking with pulsed light |
| US9072462B2 (en) | 2012-09-27 | 2015-07-07 | Wavetec Vision Systems, Inc. | Geometric optical power measurement device |
| US9498122B2 (en) | 2013-06-18 | 2016-11-22 | Avedro, Inc. | Systems and methods for determining biomechanical properties of the eye for applying treatment |
| US9498114B2 (en) | 2013-06-18 | 2016-11-22 | Avedro, Inc. | Systems and methods for determining biomechanical properties of the eye for applying treatment |
| KR102545628B1 (en) | 2014-10-27 | 2023-06-20 | 아베드로 인코퍼레이티드 | Systems and methods for cross-linking treatments of an eye |
| US10114205B2 (en) | 2014-11-13 | 2018-10-30 | Avedro, Inc. | Multipass virtually imaged phased array etalon |
| US10292583B2 (en) * | 2015-01-09 | 2019-05-21 | Smart Vision Labs, Inc. | Portable lensmeter |
| EP3285704B1 (en) | 2015-04-24 | 2020-11-18 | Avedro Inc. | Systems for photoactivating a photosensitizer applied to an eye |
| WO2016191342A1 (en) | 2015-05-22 | 2016-12-01 | Avedro, Inc. | Systems and methods for monitoring cross-linking activity for corneal treatments |
| CN116832158A (en) | 2015-07-21 | 2023-10-03 | 艾维德洛公司 | Systems and methods for treating eyes with photosensitizers |
| EP3389560A1 (en) | 2015-12-15 | 2018-10-24 | The University of Rochester | Refractive corrector incorporating a continuous central phase zone and peripheral phase discontinuities |
| JP7035081B2 (en) | 2017-01-11 | 2022-03-14 | アヴェドロ・インコーポレーテッド | Systems and methods for determining the cross-linking distribution and / or the structural features of the cornea in the cornea |
| US10932901B2 (en) | 2017-02-10 | 2021-03-02 | University Of Rochester | Vision correction with laser refractive index changes |
| EP3761928A1 (en) | 2018-03-08 | 2021-01-13 | Avedro, Inc. | Micro-devices for treatment of an eye |
| CA3099913A1 (en) | 2018-05-14 | 2019-11-21 | University Of Rochester | Vision correction with laser refractive index changes |
| US11256110B2 (en) | 2018-12-19 | 2022-02-22 | Alcon Inc. | System and method of utilizing computer-aided optics |
| CA3147045A1 (en) | 2019-08-06 | 2021-02-11 | Desmond C. Adler | Photoactivation systems and methods for corneal cross-linking treatments |
| WO2023107379A1 (en) | 2021-12-06 | 2023-06-15 | University Of Rochester | Thin large-diameter optics foldable intraocular lens |
Family Cites Families (98)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3880501A (en) * | 1973-04-16 | 1975-04-29 | Tropel | Optical system for objective refractor for the eye |
| US4069823A (en) | 1976-04-19 | 1978-01-24 | Viktor Leonidovich Isakov | Apparatus for laser therapy |
| JPS5838839A (en) | 1981-08-31 | 1983-03-07 | Tokyo Optical Co Ltd | Method and apparatus for measuring refractive index |
| DE3150124C2 (en) | 1981-12-18 | 1985-01-31 | Fa. Carl Zeiss, 7920 Heidenheim | Device for examining the anterior segments of the eye |
| DE3245939C2 (en) | 1982-12-11 | 1985-12-19 | Fa. Carl Zeiss, 7920 Heidenheim | Device for generating an image of the fundus |
| DE3339370A1 (en) | 1983-10-29 | 1985-05-09 | Meditec GmbH, 8501 Heroldsberg | PULSE LASER FOR MEDICAL APPLICATIONS |
| US4718418A (en) | 1983-11-17 | 1988-01-12 | Lri L.P. | Apparatus for ophthalmological surgery |
| US5507741A (en) | 1983-11-17 | 1996-04-16 | L'esperance, Jr.; Francis A. | Ophthalmic method for laser surgery of the cornea |
| US4729372A (en) | 1983-11-17 | 1988-03-08 | Lri L.P. | Apparatus for performing ophthalmic laser surgery |
| US5735843A (en) | 1983-12-15 | 1998-04-07 | Visx, Incorporated | Laser surgery apparatus and method |
| DE3422144A1 (en) | 1984-06-14 | 1985-12-19 | Josef Prof. Dr. 6900 Heidelberg Bille | DEVICE FOR DISPLAYING AREA AREAS OF THE HUMAN EYE |
| FR2566140B1 (en) | 1984-06-15 | 1986-09-05 | Onera (Off Nat Aerospatiale) | DEVICE FOR ANALYZING AND CORRECTING REAL-TIME WAVE SURFACES WITH A POLARIZED INTERFEROMETER |
| US4669466A (en) | 1985-01-16 | 1987-06-02 | Lri L.P. | Method and apparatus for analysis and correction of abnormal refractive errors of the eye |
| AU606315B2 (en) | 1985-09-12 | 1991-02-07 | Summit Technology, Inc. | Surface erosion using lasers |
| US4750818A (en) | 1985-12-16 | 1988-06-14 | Cochran Gregory M | Phase conjugation method |
| US5423801A (en) | 1986-03-19 | 1995-06-13 | Summit Technology, Inc. | Laser corneal surgery |
| US5177511A (en) | 1986-11-08 | 1993-01-05 | G. Rodenstock Instruments Gmbh | Apparatus for producing images of an object and in particular for observing the rear portions of the eye |
| US5324281A (en) | 1987-03-09 | 1994-06-28 | Summit Technology, Inc. | Laser reprofiling system employing a photodecomposable mask |
| FR2617986B1 (en) | 1987-07-08 | 1989-10-27 | Synthelabo | OPTICAL SYSTEM AND SURGICAL APPARATUS COMPRISING SAID SYSTEM |
| US5106183A (en) | 1987-11-25 | 1992-04-21 | Taunton Technologies, Inc. | Topography measuring apparatus |
| US4764930A (en) | 1988-01-27 | 1988-08-16 | Intelligent Surgical Lasers | Multiwavelength laser source |
| US4901718A (en) | 1988-02-02 | 1990-02-20 | Intelligent Surgical Lasers | 3-Dimensional laser beam guidance system |
| US4881808A (en) | 1988-02-10 | 1989-11-21 | Intelligent Surgical Lasers | Imaging system for surgical lasers |
| US4848340A (en) | 1988-02-10 | 1989-07-18 | Intelligent Surgical Lasers | Eyetracker and method of use |
| US4907586A (en) | 1988-03-31 | 1990-03-13 | Intelligent Surgical Lasers | Method for reshaping the eye |
| DE3821973A1 (en) | 1988-06-29 | 1990-02-08 | Rodenstock Instr | DEVICE FOR PRODUCING AN IMAGE OF AN OBJECT (III) |
| US4991953A (en) | 1989-02-09 | 1991-02-12 | Eye Research Institute Of Retina Foundation | Scanning laser vitreous camera |
| US5159361A (en) | 1989-03-09 | 1992-10-27 | Par Technology Corporation | Method and apparatus for obtaining the topography of an object |
| US5026977A (en) | 1989-04-05 | 1991-06-25 | The Charles Stark Draper Laboratory, Inc. | Wavefront sensing and correction with deformable mirror |
| US5196006A (en) | 1989-04-25 | 1993-03-23 | Summit Technology, Inc. | Method and apparatus for excision endpoint control |
| US4988348A (en) | 1989-05-26 | 1991-01-29 | Intelligent Surgical Lasers, Inc. | Method for reshaping the cornea |
| JP2931325B2 (en) | 1989-06-29 | 1999-08-09 | 興和株式会社 | Ophthalmic measurement device |
| US4972836A (en) | 1989-12-18 | 1990-11-27 | General Electric Company | Motion detector for high-resolution magnetic resonance imaging |
| DE4002029A1 (en) | 1990-01-24 | 1991-07-25 | Peter Hoefer | METHOD FOR THE PRODUCTION OF CONTACT LENSES AND CONTACT LENS PRODUCTION SYSTEM |
| JP2854657B2 (en) | 1990-03-14 | 1999-02-03 | 興和株式会社 | Ophthalmic measurement device |
| US5062702A (en) | 1990-03-16 | 1991-11-05 | Intelligent Surgical Lasers, Inc. | Device for mapping corneal topography |
| AT395523B (en) | 1990-07-24 | 1993-01-25 | Spellitz Fritz | OPTICAL MEASURING SYSTEM FOR THE HUMAN CORNUS |
| US5258791A (en) | 1990-07-24 | 1993-11-02 | General Electric Company | Spatially resolved objective autorefractometer |
| US5722427A (en) | 1993-05-10 | 1998-03-03 | Eyesys Technologies, Inc. | Method of refractive surgery |
| AU647533B2 (en) | 1990-10-16 | 1994-03-24 | Summit Technology, Inc. | Laser thermokeratoplasty methods and apparatus |
| US5139022A (en) | 1990-10-26 | 1992-08-18 | Philip Lempert | Method and apparatus for imaging and analysis of ocular tissue |
| US5221834A (en) | 1991-06-28 | 1993-06-22 | Eastman Kodak Company | Method for providing feedback correction for an imaging device |
| US5263950A (en) | 1991-07-24 | 1993-11-23 | L'esperance Medical Technologies, Inc. | Phaco-extractor for fragmenting cataractous-lens situs of fragmentation |
| US5214456A (en) | 1991-10-09 | 1993-05-25 | Computed Anatomy Incorporated | Mapping of corneal topography with display of pupil perimeter |
| US5339121A (en) | 1991-11-01 | 1994-08-16 | Visx, Incorported | Rectilinear photokeratoscope |
| US5229889A (en) | 1991-12-10 | 1993-07-20 | Hughes Aircraft Company | Simple adaptive optical system |
| US5246435A (en) | 1992-02-25 | 1993-09-21 | Intelligent Surgical Lasers | Method for removing cataractous material |
| US5439462A (en) | 1992-02-25 | 1995-08-08 | Intelligent Surgical Lasers | Apparatus for removing cataractous material |
| US5233174A (en) | 1992-03-11 | 1993-08-03 | Hughes Danbury Optical Systems, Inc. | Wavefront sensor having a lenslet array as a null corrector |
| US5279611A (en) | 1992-03-13 | 1994-01-18 | Mcdonnell Peter J | Laser shaping of ocular surfaces using ablation mask formed in situ |
| US5473392A (en) | 1992-05-01 | 1995-12-05 | Summit Technology, Inc. | Method and system for topographic measurement |
| US5841511A (en) | 1992-06-02 | 1998-11-24 | Eyesys Technologies, Inc. | Method of corneal analysis using a checkered placido apparatus |
| DE4222395A1 (en) * | 1992-07-08 | 1994-01-13 | Amtech Ges Fuer Angewandte Mic | Optical system for measuring refraction of eye with light source - has variable imaging optics adjustable in its power of refraction focussing light emanating from light source on retina of eye |
| US5298971A (en) | 1992-09-23 | 1994-03-29 | Industrial Technology Research Institute | Lateral shear interferometer for testing aspheric surfaces |
| US5437658A (en) | 1992-10-07 | 1995-08-01 | Summit Technology, Incorporated | Method and system for laser thermokeratoplasty of the cornea |
| US5307097A (en) | 1992-11-05 | 1994-04-26 | Kera-Metrics, Inc. | Corneal topography system including single-direction shearing of holograph grating in orthogonal directions |
| US5293871A (en) | 1993-05-05 | 1994-03-15 | Cornell Research Foundation Inc. | System for ultrasonically determining corneal layer thicknesses and shape |
| US5452031A (en) | 1993-05-05 | 1995-09-19 | Boston Eye Technology, Inc. | Contact lens and a method for manufacturing contact lens |
| US5556395A (en) | 1993-05-07 | 1996-09-17 | Visx Incorporated | Method and system for laser treatment of refractive error using an offset image of a rotatable mask |
| US5411501A (en) | 1993-06-04 | 1995-05-02 | Summit Technology, Inc. | Laser reprofiling system for correction of astigmatisms |
| US5395356A (en) | 1993-06-04 | 1995-03-07 | Summit Technology, Inc. | Correction of presbyopia by photorefractive keratectomy |
| US5461212A (en) | 1993-06-04 | 1995-10-24 | Summit Technology, Inc. | Astigmatic laser ablation of surfaces |
| US5360424A (en) | 1993-06-04 | 1994-11-01 | Summit Technology, Inc. | Tracking system for laser surgery |
| DE69414913T2 (en) | 1993-06-10 | 1999-07-01 | Konan Common Co | Method and device for obtaining images of the cornea |
| AU716040B2 (en) | 1993-06-24 | 2000-02-17 | Bausch & Lomb Incorporated | Ophthalmic pachymeter and method of making ophthalmic determinations |
| JP3359100B2 (en) * | 1993-06-29 | 2002-12-24 | キヤノン株式会社 | Optometry device |
| US5474548A (en) | 1993-07-14 | 1995-12-12 | Knopp; Carl F. | Method of establishing a unique machine independent reference frame for the eye |
| US5632282A (en) | 1993-07-20 | 1997-05-27 | Hay; S. Hutson | Ocular disease detection apparatus |
| US5502518A (en) | 1993-09-09 | 1996-03-26 | Scient Optics Inc | Asymmetric aspheric contact lens |
| EP0644411B1 (en) | 1993-09-17 | 1997-03-26 | ESSILOR INTERNATIONAL (Compagnie Générale d'Optique) | Procedure and apparatus for the absolute measurement of the geometrical or optical structure of an optical component |
| US5410376A (en) | 1994-02-04 | 1995-04-25 | Pulse Medical Instruments | Eye tracking method and apparatus |
| US5505723A (en) | 1994-02-10 | 1996-04-09 | Summit Technology, Inc. | Photo-refractive keratectomy |
| US5475452A (en) | 1994-02-24 | 1995-12-12 | Keravision, Inc. | Device and method for mapping objects |
| US5861955A (en) | 1994-04-25 | 1999-01-19 | Medjet Inc. | Topographical cornea mapping for corneal vision correction |
| US5442412A (en) | 1994-04-25 | 1995-08-15 | Autonomous Technologies Corp. | Patient responsive eye fixation target method and system |
| US5632742A (en) | 1994-04-25 | 1997-05-27 | Autonomous Technologies Corp. | Eye movement sensing method and system |
| US5493391A (en) | 1994-07-11 | 1996-02-20 | Sandia Corporation | One dimensional wavefront distortion sensor comprising a lens array system |
| DE69528024T2 (en) * | 1994-08-18 | 2003-10-09 | Zeiss Carl | Surgical apparatus controlled with optical coherence tomography |
| US5563709A (en) | 1994-09-13 | 1996-10-08 | Integrated Process Equipment Corp. | Apparatus for measuring, thinning and flattening silicon structures |
| US5491524A (en) | 1994-10-05 | 1996-02-13 | Carl Zeiss, Inc. | Optical coherence tomography corneal mapping apparatus |
| AU4197496A (en) | 1994-10-28 | 1996-05-23 | Eyesys Technologies, Inc. | Multi-camera corneal analysis system |
| DE4446183B4 (en) | 1994-12-23 | 2005-06-02 | Carl Zeiss Jena Gmbh | Arrangement for measuring intraocular distances |
| US5684545A (en) | 1995-07-07 | 1997-11-04 | New Mexico State University Technology Transfer Corp. | Adaptive optics wave measurement and correction system |
| AT402389B (en) | 1995-10-04 | 1997-04-25 | Fischer Adv Components Gmbh | SAFETY DEVICE FOR CONTAINERS INSTALLED IN THE AIRCRAFT INTERIOR AND CONTAINERS FOR THE AVIATION INDUSTRY |
| CN1072825C (en) | 1995-11-20 | 2001-10-10 | 三星电子株式会社 | Disk drive having eccentricity correction device |
| US5629765A (en) | 1995-12-15 | 1997-05-13 | Adaptive Optics Associates, Inc. | Wavefront measuring system with integral geometric reference (IGR) |
| US5784146A (en) | 1995-12-28 | 1998-07-21 | Nidek Co., Ltd | Ophthalmic measurement apparatus |
| US5936720A (en) | 1996-07-10 | 1999-08-10 | Neal; Daniel R. | Beam characterization by wavefront sensor |
| US5864381A (en) | 1996-07-10 | 1999-01-26 | Sandia Corporation | Automated pupil remapping with binary optics |
| US5785704A (en) | 1996-07-29 | 1998-07-28 | Mrc Systems Gmbh | Method for performing stereotactic laser surgery |
| US5822035A (en) | 1996-08-30 | 1998-10-13 | Heidelberg Engineering Optische Messysteme Gmbh | Ellipsometer |
| US5735283A (en) | 1996-10-09 | 1998-04-07 | Snook; Richard Kieth | Surgical keratometer system for measuring surface topography of a cornea during surgery |
| US5923399A (en) | 1996-11-22 | 1999-07-13 | Jozef F. Van de Velde | Scanning laser ophthalmoscope optimized for retinal microphotocoagulation |
| US5777719A (en) | 1996-12-23 | 1998-07-07 | University Of Rochester | Method and apparatus for improving vision and the resolution of retinal images |
| US5740803A (en) | 1997-03-07 | 1998-04-21 | Autonomous Technologies Corporation | Locating the center of the entrance pupil of an eye after pupil dilation |
| US5920373A (en) | 1997-09-24 | 1999-07-06 | Heidelberg Engineering Optische Messysteme Gmbh | Method and apparatus for determining optical characteristics of a cornea |
| US5963300A (en) | 1998-02-17 | 1999-10-05 | Amt Technologies, Corp. | Ocular biometer |
| US5966197A (en) | 1998-04-21 | 1999-10-12 | Visx, Incorporated | Linear array eye tracker |
-
1999
- 1999-04-20 JP JP2000565776A patent/JP3599276B2/en not_active Expired - Lifetime
- 1999-04-20 BR BR9913130-7A patent/BR9913130A/en not_active IP Right Cessation
- 1999-04-20 AU AU36576/99A patent/AU747840B2/en not_active Expired
- 1999-04-20 ES ES99918729T patent/ES2184445T3/en not_active Expired - Lifetime
- 1999-04-20 DE DE69902549T patent/DE69902549T2/en not_active Expired - Lifetime
- 1999-04-20 MX MXPA01001167A patent/MXPA01001167A/en active IP Right Grant
- 1999-04-20 WO PCT/US1999/008709 patent/WO2000010448A1/en active IP Right Grant
- 1999-04-20 EP EP99918729A patent/EP1105037B1/en not_active Expired - Lifetime
- 1999-04-20 CA CA002338060A patent/CA2338060C/en not_active Expired - Lifetime
- 1999-04-20 AT AT99918729T patent/ATE222074T1/en not_active IP Right Cessation
- 1999-04-20 PT PT99918729T patent/PT1105037E/en unknown
-
2000
- 2000-09-20 US US09/665,748 patent/US6270221B1/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| AU747840B2 (en) | 2002-05-23 |
| JP3599276B2 (en) | 2004-12-08 |
| CA2338060A1 (en) | 2000-03-02 |
| BR9913130A (en) | 2001-05-08 |
| AU3657699A (en) | 2000-03-14 |
| ATE222074T1 (en) | 2002-08-15 |
| MXPA01001167A (en) | 2002-04-24 |
| EP1105037A1 (en) | 2001-06-13 |
| PT1105037E (en) | 2002-11-29 |
| DE69902549D1 (en) | 2002-09-19 |
| JP2002523119A (en) | 2002-07-30 |
| WO2000010448A1 (en) | 2000-03-02 |
| US6270221B1 (en) | 2001-08-07 |
| ES2184445T3 (en) | 2003-04-01 |
| DE69902549T2 (en) | 2003-04-17 |
| EP1105037B1 (en) | 2002-08-14 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2338060C (en) | Apparatus and method for measuring vision defects of a human eye | |
| US6598975B2 (en) | Apparatus and method for measuring vision defects of a human eye | |
| CA2385903C (en) | Wavefront sensor having multi-power beam modes, independent adjustment camera, and accommodation range measurement | |
| US6439720B1 (en) | Method and apparatus for measuring optical aberrations of the human eye | |
| CA2311818C (en) | Objective measurement and correction of optical systems using wavefront analysis | |
| US6578963B2 (en) | Wavefront sensor for objective measurement of an optical system and associated methods | |
| EP1255483B1 (en) | Dynamic range extension techniques for a wave-front sensor | |
| US6271915B1 (en) | Objective measurement and correction of optical systems using wavefront analysis | |
| US20030025874A1 (en) | Method and apparatus for improving vision and the resolution of retinal images | |
| JP2004524053A (en) | Spatial filter and method for improving Hartmann-Shack images |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20190423 |