Optics: eye examining – vision testing and correcting – Eye examining or testing instrument – Objective type
Reexamination Certificate
2001-10-15
2003-04-29
Manuel, George (Department: 3737)
Optics: eye examining, vision testing and correcting
Eye examining or testing instrument
Objective type
C351S246000
Reexamination Certificate
active
06554429
ABSTRACT:
BACKGROUND OF THE INVENTION
This invention relates generally to the field of ophthalmic diagnostic devices and, more particularly, to wavefront sensors used as diagnostic devices.
The human eye in its simplest terms functions to provide vision by transmitting light through a clear outer portion called the cornea, and focusing the image by way of a crystalline lens onto a retina. The quality of the focused image depends on many factors including the size and shape of the eye, and the transparency of the cornea and the lens.
The optical power of the eye is determined by the optical power of the cornea and the crystalline lens. In the normal, healthy eye, sharp images are formed on the retina (emmetropia). In many eyes, images are either formed in front of the retina because the eye is abnormally long (axial myopia), or formed in back of the retina because the eye is abnormally short (axial hyperopia). The cornea also may be asymmetric or toric, resulting in an uncompensated cylindrical refractive error referred to as corneal astigmatism. In addition, due to age-related reduction in lens accommodation, the eye may become presbyopic resulting in the need for a bifocal or multifocal correction device.
In the past, axial myopia, axial hyperopia and corneal astigmatism generally have been corrected by spectacles or contact lenses, but there are several refractive surgical procedures that have been investigated and used since 1949. Barraquer investigated a procedure called keratomileusis that reshaped the cornea using a microkeratome and a cryolathe. This procedure was never widely accepted by surgeons. Another procedure that has gained widespread acceptance is radial and/or transverse incisional keratotomy (RK or AK, respectively). In the 1990s, the use of photablative lasers to reshape the surface of the cornea (photorefractive keratectomy or PRK) or for mid-stromal photoablation (Laser-Assisted In Situ Keratomileusis or LASIK) have been approved by regulatory authorities in the U.S. and other countries.
In the past, the amount of tissue removed by the laser was determined by taking pre-operative measurements of the optical errors of the eye, sphere, cylinder and axis, termed “low order” optical aberrations. These measurements were manually loaded into the refractive laser and a proposed corrective “recipe” was calculated by the laser software. More recently, the use of wavefront sensor technology, which measures both the low order optical aberrations and the “higher” order aberrations, such as coma, trefoil and spherical aberrations, have been investigated. See for example U.S. Pat. Nos. 5,777,719, 5,949,521, 6,095,651 (Williams, et al.), U.S. patent application Ser. Nos. 09/566,409 and 09/566,668, both filed May 8, 2000, and in PCT Patent Publication No. WO 00/10448, the entire contents of which being incorporated herein by reference. These wavefront sensors are particularly useful when used in combination with a high-speed eye movement tracker, such as the tracker disclosed in U.S. Pat. Nos. 5,442,412 and 5,632,742 (Frey, et al.), the entire contents of which being incorporated herein by reference. The ultimate goal of these devices is to link the wavefront sensor to the laser and eye movement tracker to provide real-time diagnostic data to the laser during surgery. In the past, as best seen in
FIG. 1
, in order to focus wavefront sensing device
10
, the patient was seated at the device so that the patient's eye
12
views fixation target
14
though optical pathway
16
that includes adjustable focus mechanism
18
. Mechanism
18
compensates for defocus error (and possibly astigmatism) to allow the patient to see fixation target
14
relatively clearly regardless of the refractive error in the patient's eye
12
. Video camera
20
, disposed along optical pathway
22
allows device
10
operator (not shown) to position eye
12
relative to device
10
. Once the patient is in the correct position and is viewing fixation target
14
, probe beam
24
of optical radiation is sent into eye
12
. A fraction of the radiation is scattered by the retina exits the eye in the form of a re-emitted wavefront. Optical pathway
26
conveys this wavefront to the entrance face of wavefront sensor
28
.
The lens of the eye is a dynamic element, capable of changing the effective focal length of the eye through accommodation. In performing wavefront measurements, it is important to take this accommodative ability into account. Normally, the wavefront is measured with the lens as relaxed as possible, so that the eye is minimally refracting (most hyperopic). Relaxing the lens is typically achieved by adjusting the focus mechanism in the fixation pathway so that the fixation target appears to lie just beyond the patient's most hyperopic focal point. The fixation target in this instance will appear slightly out of focus to the patient. This process is known as “fogging”.
Prior to the present invention, wavefront sensors were typically only used to measure the refractive error of an eye when the eye was in its most relaxed or hyperopic state. The inventors have discovered that a wavefront sensor can be used to measure the range of accommodation of an eye, and to measure optical aberrations over the accommodative range. This capability may have diagnostic utility in characterizing age-related changes in performance of the crystalline lens and in interpreting certain visual symptoms. This capability may also allow for customization of the ablation pattern of the refractive laser to optimize the patient's vision at any accommodative state (i.e., at any desired focal point in front of the eye).
Accordingly, a need continues to exist for a method of determining the accommodative range of an eye.
BRIEF SUMMARY OF THE INVENTION
The present invention improves upon the prior art by providing an automated objective method for determining the accommodative range and aberration profile of an eye using a wavefront sensor that iteratively determines the change in accommodation of the lens of an eye.
Accordingly, one objective of the present invention is to provide an automated objective accommodative measurement method.
Another objective of the present invention is to provide an automated aberration profile measurement method.
Another objective of the present invention is to provide an accommodation measurement method for a wavefront sensor that does not require subjective determination of accommodation.
Another objective of the present invention is to provide an accommodation measurement method for a wavefront sensor that does not require participation by a skilled operator.
These and other advantages and objectives of the present invention will become apparent from the detailed description and claims that follow.
REFERENCES:
patent: 5442412 (1995-08-01), Frey et al.
patent: 5632742 (1997-05-01), Frey et al.
patent: 5777719 (1998-07-01), Williams et al.
patent: 5949521 (1999-09-01), Williams et al.
patent: 5963300 (1999-10-01), Horwitz
patent: 6095651 (2000-08-01), Williams et al.
patent: 6270221 (2001-08-01), Liang et al.
patent: 6271914 (2001-08-01), Liang et al.
patent: 1 153 570 (2001-11-01), None
patent: WO 00/10448 (2000-03-01), None
patent: WO 01/87201 (2001-11-01), None
Campin John A.
Gray Gary P.
Pettit George
Alcon Inc.
Manuel George
Schira Jeffrey S.
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