U.S. patent application number 12/436736 was filed with the patent office on 2009-08-27 for method and systems for laser treatment of presbyopia using offset imaging.
This patent application is currently assigned to AMO Manufacturing USA, LLC.. Invention is credited to Kenneth Greenberg, Jerome A. Legerton, Charles R. Munnerlyn, Marc Odrich, John K. Shimmick.
Application Number | 20090216217 12/436736 |
Document ID | / |
Family ID | 22134180 |
Filed Date | 2009-08-27 |
United States Patent
Application |
20090216217 |
Kind Code |
A1 |
Odrich; Marc ; et
al. |
August 27, 2009 |
METHOD AND SYSTEMS FOR LASER TREATMENT OF PRESBYOPIA USING OFFSET
IMAGING
Abstract
An ophthalmic surgery system and method for treating presbyopia
by performing ablative photodecomposition of the corneal surface.
The offset image of a variable aperture, such as a variable width
slit and variable diameter iris diaphragm, is scanned in a
preselected pattern to perform ablative sculpting of predetermined
portions of a corneal surface. The scanning is performed to ablate
an optical zone sized to match the patient pupil with a peripheral
transition zone outside the pupil. The shape of the ablated optical
zone is different from the shape of the final optical correction on
the anterior surface of the cornea. The optical zone corrects for
near-vision centrally and far-vision peripherally. A movable image
displacement mechanism enables radial displacement and angular
rotation of the profiled beam exiting from the variable aperture.
The invention enables wide area treatment with a laser having a
narrower beam than the treatment area, and can be used in the
treatment of many conditions in conjunction with presbyopia such as
hyperopia, hyperopic astigmatism and irregular refractive
aberrations.
Inventors: |
Odrich; Marc; (Riverdale,
NY) ; Greenberg; Kenneth; (Ridgefield, CT) ;
Legerton; Jerome A.; (San Diego, CA) ; Munnerlyn;
Charles R.; (San Jose, CA) ; Shimmick; John K.;
(Belmont, CA) |
Correspondence
Address: |
TOWNSEND AND TOWNSEND AND CREW, LLP
TWO EMBARCADERO CENTER, EIGHTH FLOOR
SAN FRANCISCO
CA
94111-3834
US
|
Assignee: |
AMO Manufacturing USA, LLC.
Milpitas
CA
|
Family ID: |
22134180 |
Appl. No.: |
12/436736 |
Filed: |
May 6, 2009 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10600027 |
Jun 19, 2003 |
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12436736 |
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09901964 |
Jul 9, 2001 |
6663619 |
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10600027 |
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09261768 |
Mar 3, 1999 |
6280435 |
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09901964 |
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60076786 |
Mar 4, 1998 |
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Current U.S.
Class: |
606/5 |
Current CPC
Class: |
A61F 9/00817 20130101;
A61F 9/00802 20130101; A61F 2009/00882 20130101; A61F 2009/00844
20130101; A61F 2009/00872 20130101; A61F 9/00808 20130101; A61F
2009/0088 20130101; A61F 9/00806 20130101; A61F 2009/00895
20130101; A61F 9/008 20130101 |
Class at
Publication: |
606/5 |
International
Class: |
A61F 9/008 20060101
A61F009/008; A61B 18/20 20060101 A61B018/20 |
Claims
1. A method of treating an eye of a patient to mitigate presbyopia,
the eye having a pupil and a cornea, the method comprising:
identifying a multifocal shape modification for the cornea, the
shape modification including a first region providing a near vision
correction centrally and a second region providing a far vision
correction peripherally; adjusting the size of the shape
modification in response to a size of the pupil so as to provide a
balance of the near vision correction provided by the first region
and the far vision correction provided by the second region for the
patient; and modifying the shape of the cornea according to the
adjusted shape modification.
2. The method of claim 1, wherein the adjusted shape modification
further comprises a transition zone disposed beyond the pupil.
3. The method of claim 1, wherein the multifocal shape modification
further comprises a third region disposed between the first region
and the second region, the third region providing an intermediate
vision correction.
4. The method of claim 3, wherein the third region has a varying
optical power that continuously varies between the first region and
the second region.
5. The method of claim 4, wherein the optical power of the third
region varies over a range from about 1 to 4 D.
6. The method of claim 1, further comprising scaling the shape
modification in relation to the size of the pupil.
7. The method of claim 6, wherein the optical power of the first
region is substantially unchanged during the step of scaling.
8. The method of claim 6, wherein the optical power of the second
region is substantially unchanged during the step of scaling.
9. The method of claim 1, wherein the size of the pupil is selected
to correspond to its size when dilated at night.
10. The method of claim 1, further comprising adjusting the size of
the shape modification corresponding to an anticipated
healing-induced shape change.
11. The method of claim 1, wherein the eye comprises a first
refractive error and the shape modification substantially corrects
the first refractive error, the first refractive error being
selected from the group consisting of myopia, hyperopia,
astigmatism and irregular aberration.
12. The method of claim 1, wherein the shape modification has an
aspheric shape.
13. A system for reshaping an eye of a patient to mitigate
presbyopia, the eye having a pupil and a cornea, the system
comprising: a processor comprising a tangible medium comprising
instructions that when executed cause the processor to: identify a
multifocal shape modification for the cornea, the shape
modification including a first region providing a near vision
correction centrally and a second region providing a far vision
correction peripherally, and adjust the size of the shape
modification in response to a size of the pupil so as to provide a
balance of the near vision correction provided by the first region
and the far vision correction provided by the second region for the
patient; and an eye modification assembly for modifying the cornea
according to the adjusted shape modification.
14. The system of claim 13, wherein the adjusted shape modification
further comprises a transition zone disposed beyond the pupil.
15. The system of claim 13, wherein the multifocal shape
modification further comprises a third region disposed between the
first region and the second region, the third region providing an
intermediate vision correction.
16. The system of claim 15, wherein the third region has a varying
optical power that continuously varies between the first region and
the second region.
17. The system of claim 16, wherein the optical power of the third
region varies over a range from about 1 to 4 D.
18. The system of claim 13, wherein the multifocal shape
modification is scaled in relation to the size of the pupil.
19. The system of claim 18, wherein the optical power of the first
region is substantially unchanged by the scaling.
20. The system of claim 18, wherein the optical power of the second
region is substantially unchanged by the scaling.
21. The system of claim 13, wherein the eye comprises a first
refractive error and the shape modification substantially corrects
the first refractive error, the first refractive error being
selected from the group consisting of myopia, hyperopia,
astigmatism and irregular aberration.
22. The system of claim 13, wherein the shape modification has an
aspheric shape.
Description
CROSS-REFERENCES TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. patent
application Ser. No. 10/600,027, filed on Jun. 19, 2003, (Attorney
Docket No. 018158-011140US), which is a continuation of U.S. patent
application Ser. No. 09/901,964, filed on Jul. 9, 2001, now U.S.
Pat. No. 6,663,619, (Attorney Docket No. 018158-011120US), which is
a division of U.S. patent application Ser. No. 09/261,768, filed on
Mar. 3, 1999, now U.S. Pat. No. 6,280,435, (Attorney Docket No.
018158-01111US), which claims the benefit of U.S. Patent
Application No. 60/076,786, filed on Mar. 4, 1998, the full
disclosures of which are hereby incorporated herein by
reference.
BACKGROUND OF THE INVENTION
[0002] 1. Field of the Invention
[0003] This invention relates to surgical modifications to the eye.
In a specific embodiment, the invention provides ophthalmic surgery
techniques which employ a laser to effect ablative
photodecomposition of corneal tissue to correct presbyopia and/or
other vision defects.
[0004] With aging, a condition of the eye known as presbyopia
develops. With this condition, the crystalline lens of the eye
loses the ability to focus on near objects when the eye is
corrected for far-vision.
[0005] Presbyopia is often treated with bifocal eyeglasses. With
bifocals, one portion of the lens is corrected for far-vision, and
another portion of the lens is corrected for near-vision. By
looking down through the bifocals, the user looks through the
portion of the lens corrected for near-vision. When viewing distant
objects, the user looks higher, through the portion of the bifocals
corrected for far-vision.
[0006] Efforts have been made to treat presbyopia using partitioned
lenses positioned directly over the pupil of the eye. Examples
include multifocal contact lenses. Unfortunately, when presbyopia
is corrected with bifocal or multifocal lenses attached to the
cornea, the user is simultaneously looking through the near- and
far-vision corrected lenses. As a result, the user will see both
in-focus and out-of-focus images simultaneously when viewing an
object. This out-of-focus image superimposed on the in-focus image
can cause glare and degrade vision when viewing objects at low
contrast.
[0007] Another technique for treating presbyopia has been to
correct one eye of the patient for near-vision and to correct the
other eye for distance-vision. This technique is known as
monovision. With monovision, a patient uses one eye to see distant
objects and the other eye to see close objects. Unfortunately with
monovision, the patient may not clearly see objects that are
intermediately positioned because the object is out-of-focus for
both eyes. Also, a patient may have trouble seeing with only one
eye.
[0008] Laser-based systems and methods are known for enabling
ophthalmic surgery on the cornea in order to correct vision defects
by the technique known as ablative photodecomposition. Changing the
shape of the anterior surface of the cornea will change the optical
properties of an eye. These ablative photodecomposition systems and
methods control ultraviolet laser radiation flux density and
exposure time upon the cornea so as to achieve a desired surface
change in the cornea and thereby correct an optical defect.
[0009] Several different ablative photodecomposition techniques
have been described to correct specific optical errors of the eye.
For example, a myopic condition may be corrected by laser sculpting
a corneal surface to reduce curvature. An astigmatic condition,
which is typically characterized by a cylindrical component of
curvature (departing from the otherwise generally spherical
curvature of the cornea), can be corrected by a cylindrical
ablation. Laser sculpting a corneal surface to increase the
curvature can correct a hyperopic condition.
[0010] In a typical laser surgical procedure, the optically
functional region of the corneal surface to be ablated is
designated the optical zone. Depending on the nature of the desired
optical correction, the optical zone may or may not be centered on
the center of the pupil or on the apex of the anterior corneal
surface. One technique for increasing the curvature of the optical
zone for hyperopia error correction involves selectively varying
the area of the cornea exposed to the laser beam radiation so as to
produce an essentially spherical surface profile of increased
curvature. This selective variation of the irradiated area may be
accomplished in a variety of ways. For example, the optical zone
can be scanned with a laser beam having a relatively small
cross-sectional area (compared to the optical zone) in such a
manner that the ablation depth increases with distance from the
intended center of ablation. The result is a substantially
spherical profile for the anterior corneal surface with maximum
depth of cut at the extreme outer boundary of the optical zone.
Another technique for sculpting the optical zone employs a
rotatable mask having a plurality of apertures. The apertures are
sequentially introduced into the laser beam path to provide
progressive shaping of the laser beam in order to achieve the
desired profile.
[0011] Efforts have also been made to treat presbyopia using
ablative photodecomposition. One specific technique of treating
presbyopia creates near-vision correction by ablating a region of
the lower portion of the cornea adjacent the pupil rim. With this
eccentric positioning of the ablation, the near-vision lens is not
centered over the pupil. Consequently, constriction of the pupil
may occlude the ablated near-vision lens. Constriction of the pupil
is a natural response of the eye to illumination, and could
potentially disrupt near-vision.
[0012] Alternative suggested presbyopia treatments include laser
ablation of a small annular region of the cornea (having a diameter
not exceeding 3.5 mm), or the ablation of a central lens for
near-vision, surrounded by a gradual blend zone, and then a
peripheral far-vision lens, all within the optically used portion
of the cornea.
[0013] Efforts have been made in the past to laser sculpt a
transition zone to provide a more gradual sloping of the walls and
to eliminate the sharp discontinuity between the ablation zone and
the surrounding untreated cornea. These efforts have included the
use of a beam rotation or scanning mechanism operated by a computer
to provide programmed ablation of the transition zone to achieve a
sigmoid or other profile. While somewhat effective, these efforts
often suffer from the added complexity of additional optical
elements, such as a rotatable off-axis mirror or revolving prism
having suitable optical properties.
[0014] 2. Description of the Background Art
[0015] Systems and methods relevant to laser-based treatments for
presbyopia are disclosed in the following U.S. patents and patent
applications, the entire disclosures of which are hereby
incorporated by reference: U.S. Pat. No. 5,395,356, issued Mar. 7,
1995, entitled "Correction of Presbyopia by Photorefractive
Keratectomy"; U.S. Pat. No. 5,533,997, issued Jul. 9, 1996,
entitled "Apparatus and Method for Performing Presbyopia
Correction"; and U.S. Pat. No. 5,314,422, issued May 24, 1994,
entitled "Equipment for the Correction of Presbyopia by Remodeling
the Corneal Surface by Means of Photoablation."
[0016] Ablative photodecomposition systems and methods are
disclosed in the following U.S. patents and patent applications,
the entire disclosures of which are hereby incorporated by
reference: U.S. Pat. No. 4,665,913, issued May 19, 1987, entitled
"Method for Ophthalmical Surgery"; U.S. Pat. No. 4,669,466, issued
Jun. 2, 1987, for "Method and Apparatus for Analysis and Correction
of Abnormal Refractive Errors of the Eye"; U.S. Pat. No. 4,732,148,
issued Mar. 22, 1988, entitled "Method for Performing Ophthalmic
Laser Surgery"; U.S. Pat. No. 4,770,172, issued Sep. 13, 1988,
entitled "Method of Laser Sculpture of the Optically Used Portion
of the Cornea"; U.S. Pat. No. 4,773,414, issued Sep. 27, 1988,
entitled "Method of Laser Sculpture of the Optically Used Portion
of the Cornea"; U.S. patent application Ser. No. 07/109,812, filed
Oct. 16, 1987, entitled "Laser Surgery Method and Apparatus"; U.S.
Pat. No. 5,163,934, issued Nov. 17, 1992, entitled "Photorefractive
Keratectomy"; U.S. Pat. No. 5,556,395, issued Sep. 17, 1996,
entitled "Method and System for Laser Treatment of Refractive Error
Using an Offset Image of a Rotatable Mask"; U.S. patent application
Ser. No. 08/368,799, filed Jan. 4, 1995, entitled "Method and
Apparatus for Temporal and Spatial Beam Integration"; U.S. patent
application Ser. No. 08/058,599, filed May 7, 1993, entitled
"Method and System for Laser Treatment of Refractive Errors Using
Offset Imaging"; U.S. Pat. No. 5,683,379, issued Nov. 4, 1997,
entitled "Apparatus for Modifying the Surface of the Eye Through
Large Beam Laser Polishing and Method of Controlling the
Apparatus"; and U.S. Pat. No. 5,827,264, issued Oct. 27, 1998
entitled "Method of Controlling Apparatus for Modifying the Surface
of the Eye Through Large Beam Laser Polishing."
[0017] Techniques for treating presbyopia with contact lenses are
disclosed in the following U.S. patents and patent applications,
the entire disclosures of which are hereby incorporated by
reference: U.S. Pat. No. 5,835,192, issued Nov. 10, 1998, entitled
"Contact Lens and Method of Fitting a Contact Lens"; U.S. Pat. No.
5,485,228 issued Jan. 16, 1996 entitled "Multifocal Ophthalmic Lens
Pair;" and U.S. Pat. No. 5,864,379 issued Jan. 26, 1999 entitled
"Contact Lens and Process for Fitting."
BRIEF SUMMARY OF THE INVENTION
[0018] It is an object of the invention to mitigate and/or inhibit
presbyopia with minimal vision degradation by ablating a transition
zone peripheral to an optical zone. It is a further object of the
invention to ablate a cornea to produce a healed cornea with an
aspheric optical zone that corrects presbyopia. In one aspect, the
invention provides for ablating the cornea to a desired shape that
compensates for changes in the corneal shape as the cornea heals.
In another aspect, the invention provides for the simultaneous
correction of presbyopic and other refractive corrections such as
nearsightedness, farsightedness and astigmatism. In a yet further
aspect, the invention provides for scaling the aspheric optical
zone to match the size of the pupil. In yet another aspect, the
invention provides for a method for treating presbyopia which
includes ablating a transition zone outside an optical zone. One of
the major difficulties encountered in the application of laser
surgery techniques to effect hyperopic and presbyopic refractive
error corrections lies in the nature of the boundary between the
optical zone and the untreated area. When the anterior surface of
the cornea is sculpted to have an increased curvature, the maximum
depth of cut occurs at the outer boundary of the optical zone. The
generally annular region between this outer boundary and the
adjacent untreated anterior surface portion of the cornea typically
exhibits steep walls after the completion of the photoablation
procedure. After the surgery, the eye tends to eliminate these
steep walls with a stimulated healing response involving concurrent
epithelial cell growth and stromal remodeling by the deposition of
collagen, which results in corneal smoothing by filling in tissue
in the steep walled region. This natural healing response acts to
eliminate the discontinuity, resulting in a buildup of tissue in
the steep walled region and over the outer portion of the optical
zone. This natural phenomenon, sometimes termed the "hyperopic
shift" in phototherapeutic keratectomy, causes a lack of precision
for a given surgical procedure and diminished predictability,
counteracting the beneficial effects of the refractive correction
procedure and thereby reducing the desirability of the procedure to
the prospective patient.
[0019] According to the present invention, the ablated surface can
be contoured to provide an aspheric surface on a healed cornea. The
invention provides for adjusting the ablation to compensate for
factors effecting the final geometry of the healed cornea. These
factors include corneal healing and the spatial variation of
ablation. The shape of tissue ablated with a uniform laser beam
pulse will depend upon the size and shape of the laser beam spot.
The spatial variation of the total ablation may also cause
variations in the ablated corneal shape. For example, a hyperopic
ablation intended to produce a spherical ablation may demonstrate
greater steepening near the center of the optical zone. This
increased central curvature may form an aspheric surface that
corrects for presbyopia.
[0020] The ablated surface is covered following the surgery,
typically by a new epithelial layer or a repositioned anterior flap
of the corneal tissue. Consequently, the final shape of the
anterior surface of the cornea may be a different shape than the
ablated shape. However, it is the final change in shape of the
anterior surface of the cornea, not the initial ablated surface,
which determines the refractive change effected by the surgery.
Therefore, it may be desirable to ablate a shape on the cornea that
is different from the final intended shape on the anterior surface
of the cornea. For example, the optical zone may be ablated to a
substantially spherical shape for correcting hyperopia. This
ablated surface may then heal to an aspheric surface that corrects
presbyopia.
[0021] The invention includes a method and system for performing
ablative photodecomposition of the corneal surface that is capable
of providing relatively smooth transition zones along with accurate
sculpting of the anterior or other corneal surface to effect
simultaneous symmetric or asymmetric refractive and presbyopic
corrections with relatively large area coverage. The invention
preferably employs a laser beam of smaller beam size than the total
treatment area.
[0022] The invention further provides for the ablation of an
optical zone that substantially matches the area of the pupil. For
presbyopic patients, the maximum pupil diameter is typically about
5 mm. Therefore, it is an aspect of the invention that the ablated
optical zone have a diameter of about 5 mm, and be user selectable
(by the user of the ablation system) to a diameter between 3 and 7
mm. The optical zone is preferably ablated to form a healed
aspheric surface. Preferably, the central portion of the optical
zone provides near-vision correction and the peripheral portion of
the optical zone provides far-vision correction.
[0023] The invention additionally provides for scaling a diameter
of the aspheric surface to the pupil. This scaling of the aspheric
surface permits an appropriate balance between near and far-vision
correction within the pupil. For example, a patient with a 5 mm
diameter pupil may have a 2.5 mm diameter zone corrected for
near-vision, while a patient with a 3 mm diameter pupil may have a
1.5 mm diameter zone corrected for near-vision. Scaling of the
aspheric lens may be based on areas of the pupil and/or aspheric
surface.
[0024] The invention also provides for ablating a transition zone
peripheral to the optical zone and to the pupil. This positioning
of the ablated transition zone will produce optimal results once
the cornea heals. The ablated transition zone provides greater
control over the healing process and provides greater control of
the shape of the healed surface within the adjacent optical zone.
Because the transition zone is ablated to control the shape of an
adjacent healed surface, the transition zone may produce a corneal
shape which corrects for neither near- nor far-vision. Thus, the
transition zone is preferably positioned outside the pupil.
Further, the transition zone is preferably sized so that healing of
the cornea can be controlled within the adjacent optical zone. The
optimal size of the transition zone is an annular region extending
radially outward about 2 mm from the outer edge of the ablated
optical zone. An ablation with a 5 mm diameter ablated optical zone
and an optimally sized ablated transition zone will extend about 9
mm across the cornea. Transition zones of other sizes may be
ablated outside the optical zone. Dimensions of the transition zone
extending radially outward from the optical zone range from about 1
to 3 mm and preferably from about 1.5 to 2.5 mm.
[0025] In a first aspect, the present invention provides a method
for reprofiling an anterior surface of the cornea of the eye. The
anterior surface is reprofiled from an initial shape to a
multifocal aspheric shape for correcting presbyopia. The method
comprises aligning a laser system with the eye. The laser system is
operable to deliver ablative radiation to the cornea. A surface of
the cornea is ablated to a desired shape by selectively exposing
the cornea to the ablative radiation. The cornea is ablated to an
ablated shape so that an optical zone extends across the pupil and
so that a transition zone is disposed beyond the pupil. The ablated
surface is covered to produce a final aspheric anterior corneal
surface.
[0026] In some embodiments, the covering step will comprise
regenerating an epithelial layer over an ablated anterior surface
of the cornea. In other embodiments, the covering step will
comprise repositioning a flap of the cornea over the eye after a
portion of either the flap, or the underlying corneal tissues, has
been ablated.
[0027] In another aspect, the present invention provides an
ophthalmic surgery system for performing selective ablation of a
corneal surface of the eye so as to create a desired aspheric shape
for correcting presbyopia on the anterior surface of a healed
cornea. The system comprises means for directing a laser beam along
a path. Means are also provided for profiling the beam to produce a
profiled beam with a center. Means for displacing the center of the
profiled beam over an area of the corneal surface will generally be
coupled to the profiling means. A computer controls the positioning
of the beam center over the area, and creates a plurality of
successive laser beam pulses. The position of the plurality of
pulses is determined by a laser treatment table that is scaled to a
dimension of a pupil.
[0028] In another aspect, the present invention provides a laser
eye surgery method comprising selectively ablating corneal tissue
from an eye having an uncorrected surface shape. Corneal tissue is
ablated so as to produce an initial ablated shape on an anterior
surface of the cornea of the eye. The ablated eye heals, and the
healed eye has a healed anterior surface shape which differs
significantly from the initial ablated shape. This healed shape
substantially, and in some instances entirely, corrects a
refractive error of the eye.
[0029] In yet another aspect, the present invention provides a
laser eye surgery method comprising selectively ablating corneal
tissue from an eye having a refractive error. The refractive error
is selected from the group consisting of myopia, hyperopia, and
astigmatism. The ablating step removes a portion of cornea so as to
simultaneously correct the refractive error and mitigate presbyopia
of the eye.
[0030] In yet another aspect, the present invention provides a
method for treating presbyopia of an eye. The eye has a pupil, and
the method comprises selectively ablating corneal tissue from the
eye so as to produce an ablated corneal surface. The corneal
surface has an optical zone, and a transition zone surrounding the
optical zone. The optical zone of the corneal surface defines an
aspheric shape to mitigate the presbyopia, and a dimension of the
optical zone substantially matches a dimension of the pupil under
scotopic conditions.
[0031] In yet another aspect, the present invention provides a
method for treating presbyopia of an eye. The eye has a pupil, and
the method comprises selectively ablating corneal tissue from the
eye so as to produce a corneal surface having an optical zone, and
a transition zone surrounding the optical zone. The optical zone of
the corneal surface defines an aspheric shape to mitigate the
presbyopia. The transition zone is disposed outside of the
pupil.
[0032] For a fuller understanding of the nature and advantages of
the invention, reference should be had to the ensuing detailed
description taken in conjunction with the accompanying
drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
[0033] FIG. 1 is a side sectional view of an eye treated for
presbyopia with the invention.
[0034] FIG. 2 is a side sectional view of an ablation profile
illustrating the effect of corneal healing on ablation shape.
[0035] FIG. 3 illustrates the refractive power over the pupil of an
aspheric surface for treating presbyopia.
[0036] FIG. 4 is a block diagram of an ophthalmic surgery system
for incorporating the invention.
[0037] FIG. 5 is a schematic plan view illustrating a movable slit
and variable diameter aperture used in the system 20 of FIG. 4.
[0038] FIG. 6 is a schematic diagram illustrating the offset lens
principle.
[0039] FIG. 7 is a schematic diagram illustrating the lens offset
viewed along the axis of rotation.
[0040] FIG. 8 is a schematic view showing the ablation geometry for
the aperture of FIG. 5.
[0041] FIG. 9 is a schematic view of the delivery system
optics.
[0042] FIG. 10 illustrates an ablation profile on a corneal surface
in comparison to an intended +3 D spherical optical correction.
[0043] FIG. 11 illustrates an optical correction on a healed
anterior corneal surface in comparison to an intended +3 D
spherical optical correction.
[0044] FIG. 12 illustrates the effect of covering and healing over
an ablated optical zone.
[0045] FIG. 13 illustrates an initial ablated shape derived from a
desired shape and a healing-induced change.
[0046] FIG. 14 illustrates overcorrecting and restricting an
ablated surface shape relative to a desired anterior surface
correction.
[0047] FIG. 15 illustrates a small untreated zone centered on the
optical zone of an ablated surface.
DETAILED DESCRIPTION OF THE INVENTION
[0048] Turning now to the drawings, FIG. 1 illustrates a schematic
side view of a cornea 200 treated with the invention. The cornea
200 has an anterior surface that provides most of the refractive
power of the eye. The initial anterior surface 205 of the cornea
200 has been reshaped to a desired healed profile. The desired
healed profile includes anterior optical surface 210 and anterior
transition surface 215. The anterior optical surface 210 has a
multifocal aspheric shape that corrects for near-vision centrally
and far-vision peripherally.
[0049] While the present invention will often be described with
reference to the mitigation of presbyopia in combination with
refractive hyperopia treatment, it should be understood that the
benefits of the present invention are not limited to these specific
procedures. These presbyopia treatment techniques may be used when
no other refractive correction (other than the correction,
mitigation, and/or inhibition of presbyopia) is desired, or the
present treatment may be combined with therapies for one or more of
myopia, astigmatism, irregular refractive aberrations, and the
like, as well as with hyperopia. Still other aspects of the present
invention, including methods and systems which accommodate and
adjust for re-epithelization, may find uses in a broad variety of
ophthalmic procedures.
[0050] The peripheral positioning of the far-vision correction
advantageously permit distance viewing when the pupil is dilated at
night. Anterior transition surface 215 is the anterior surface of
the cornea that provides a gradual change in shape between anterior
optical surface 210 and the portion of the cornea retaining the
initial anterior surface 205. The outer boundary 212 of the
anterior optical surface preferably extends entirely across, and is
ideally substantially coextensive with, the pupil which is bounded
by iris 220. The light rays passing through anterior transition
surface 215 do not contribute to the image formed by anterior
optical surface 210. Therefore, anterior transition surface 215 is
desirably positioned outside the pupil. This positioning of
anterior transition surface 215 causes the light rays passing
through anterior transition surface 215 to be substantially
occluded by iris 220. This occlusion improves patient vision
because the light rays are blocked that do not contribute to image
formation, and which would otherwise reduce the contrast of the
image.
[0051] The optical correction effected by an ablative surgical
procedure to the cornea is derived from a change in the anterior
corneal surface from an initial anterior surface 205 to
post-operative anterior optical surface 210. The anterior optical
correction is the post-operative anterior optical surface 210 minus
the initial anterior surface 205. An ablation profile is a change
in an exposed surface profile occurring immediately after the
tissue removal process. Therefore, the ablation profile is the
exposed surface profile immediately after the tissue removal
process minus the initial exposed surface profile. As used herein,
"ablated shape" can refer either to an ablation-induced change in a
surface topography on a surface of the cornea, or to the surface
topography of the cornea after ablation. Similarly, "healed shape"
can mean either a final corneal topography once healing is
complete, or a change in the corneal topography from an initial
topography to a final corneal topography once healing is complete.
A healed shape differs significantly from an ablated shape when a
difference between the two shapes is sufficient to be perceptible
by a patient. Healing can refer either to an initial covering of an
ablated surface contour or changes in a tissue structure of the
cornea following an initial covering of an ablated surface
contour.
[0052] The relationship of the ablated surface and the anterior
corneal surface overlying the ablated surface is shown in FIG. 2.
Initial ablated surface 202 includes ablated optical zone 211 and
ablated transition zone 216. Ablated optical zone 211 includes
ablated central optical zone 231 for the correction of near-vision,
ablated peripheral optical zone 241 for the correction of
far-vision, and ablated intermediate optical zone 236 for the
correction of vision intermediate to near- and far-vision. Ablated
central optical zone 231 is shaped to appropriately form anterior
central optical surface 230 when ablated surface 202 is covered and
cornea 200 is healed to form anterior optical surface 210. Ablated
intermediate optical zone 236 is shaped to form anterior
intermediate optical surface 235 when ablated surface 202 is
covered and cornea 200 is healed. Ablated peripheral optical zone
241 is shaped to appropriately form anterior peripheral optical
surface 240 when ablated surface 202 is covered and cornea 200 is
healed. Ablated transition zone 216 is ablated to minimize the
effect of corneal healing on anterior optical surface 210.
[0053] In one embodiment, covering of the ablated shape will cause
the final shape of anterior optical surface 210 of the anterior
surface of cornea 200 to be different from ablated optical zone
211. This aspect of the present invention is more fully described
in the publication entitled "Corneal Ablation Profilometry and
Steep Central Islands," Journal of Refractive Surgery, 1997, Vol.
13, pp. 235-45, the entire disclosure of which is herein
incorporated by reference.
[0054] Initial ablated shape 202 is covered after the ablation.
Proximity to ablated transition zone 216 may cause anterior
peripheral optical surface 240 to be a different shape than
underlying ablated peripheral optical zone 241. However, anterior
central optical surface 230 of anterior optical surface 210 is
distant from ablated transition zone 216. Therefore the shape of
anterior central optical surface 230 will more closely match the
shape of ablated central optical zone 231. In one aspect, the
covering may include regeneration of the epithelial layer following
ablation of Bowman's membrane and adjacent stromal layers. In
another aspect, covering includes replacing a resected portion of
the cornea as is described in U.S. Pat. No. 4,903,695, issued Feb.
27, 1990, entitled "Method and Apparatus for Performing a
Keratomileusis or the Like Operation." In this aspect, the resected
portion includes an epithelial layer. In a yet further aspect of
covering, a tear film forms over the epithelial layer to form the
anterior surface when cornea 200 is fully healed. The final shape
of anterior optical surface 210 will substantially determine the
optical properties of the cornea. Therefore, it may be desirable to
ablate cornea 200 to form ablated optical zone 211 that is a
different shape than the shape of anterior optical surface 210.
[0055] In another embodiment, ablated optical zone 211 includes
ablated central optical zone 231 and ablated peripheral optical
zone 241. Ablated intermediate optical zone 241 may be replaced by
extending ablated peripheral optical zone 241 and ablated central
optical zone 231 to border one another. Ablated central optical
zone 231 provides about 2.5 D of near-vision correction with a
range from about 0.5 to 4 D, preferably about 2 to 3 D and a
diameter from about 1.0 to 3.5 mm and preferably from about 2 to 3
mm. Ablated peripheral optical zone 241 is ablated to provide
far-vision correction and is sized to extend radially outward from
the outer boundary of ablated central optical zone 231 to a
diameter of about 5 mm with a range from about 3 to 7 mm and
preferably from about 4 to 6 mm. Ablated transition zone 216
extends radially outward from the outer boundary of ablated optical
zone 211 to a diameter of about 9 mm with a range from about 6 to
11 mm and preferably from about 7 to 10 mm. Covering of ablated
optical zone 211 will cause anterior intermediate optical surface
240 to form over the border between ablated central optical zone
231 and ablated peripheral optical zone 241. Anterior central
optical surface 230 will form over ablated central optical zone
231. Anterior peripheral optical surface 240 will form over ablated
peripheral optical zone 241. Therefore, anterior optical surface
210 may be formed as a multifocal aspheric surface on cornea 200 by
ablating only two optical zones within ablated optical zone
211.
[0056] An illustrative plot of the relative refractive power of
anterior optical surface 210 as a function of radial position
across the pupil is shown in FIG. 3. The refractive power decreases
from the center toward the periphery. Anterior central optical
surface 230 of cornea 200 has a relative refractive power from
about 1 to 4 D, and preferably from about 2 and 3 D that corrects
for near-vision. This central surface ranges from about 1 to 3 mm
in diameter and preferably from about 1.5 to 2.5 mm in diameter.
Anterior peripheral optical surface 240 corrects for far-vision.
This peripheral surface has an inner boundary from about 2 and 4 mm
in diameter and an outer boundary 212 that may be scaled to match
the outer boundary of the pupil as shown in FIG. 1. Outer boundary
212 may be scaled to a diameter of between about 3 and 7 mm.
Anterior intermediate optical surface 235 has continuously varying
refractive power. This region is desirable and provides focus for
objects appropriately positioned intermediate to near and far
positions.
[0057] In an exemplary embodiment, ablated central optical zone
231, ablated intermediate optical zone, 236 and ablated peripheral
optical zone 241 are scaled to match a dimension of the pupil. The
scaling dimensions may be an area of the pupil, a diameter of the
pupil, a radius, or the like. For example, ablated optical zone 211
may be decreased by about 20% from a diameter of about 5 mm to 4 mm
for a patient with a 4 mm diameter pupil. In this case, ablated
central optical zone 231, ablated intermediate optical zone 236 and
ablated peripheral optical zone 241 are each decreased by about
20%. This scaling is desirable because it keeps the ratios of near,
intermediate and far-vision nearly constant for varying pupil size.
The inner boundary of ablated transition zone 216 is scaled to
border the outer boundary of ablated optical zone 211. During the
scaling of ablated optical zone 211, the outer boundary of ablated
transition zone 216 may be scaled to match the scaling of ablated
optical zone 211. Alternatively, the outer boundary of ablated
transition zone 216 may be fixed to a constant value while the
inner boundary of ablated transition zone 216 is varied.
[0058] FIG. 4 illustrates a block diagram of an ophthalmic surgery
system for incorporating the invention. As seen in this Figure, a
personal computer (PC) work station 10 is coupled to an embedded
computer 21 of a laser surgery unit 20 by means of a first bus
connection 11. The PC work station 10 comprises a tangible medium
12 and a treatment table 14. The laser treatment table 14 includes
a listing of coordinate references of the laser beam during an
ablation of the cornea. The sub-components of laser surgery unit 20
are known components and preferably comprise the elements of the
VISX STAR.TM. EXCIMER LASER SYSTEM and of the STAR S2.TM. System
available from VISX, INCORPORATED of Santa Clara, Calif. Thus, the
laser surgery system 20 includes a plurality of sensors generally
designated with reference numeral 22 which produce feedback signals
from the movable mechanical and optical components in the laser
optical system, such as the elements driven by an iris motor 23, an
image rotator 24, an astigmatism motor 25 and an astigmatism angle
motor 26. The feedback signals from sensors 22 are provided via
appropriate signal conductors to the embedded computer 21. The
embedded computer 21 controls the operation of the motor drivers
generally designated with reference numeral 27 for operating the
elements 23-26. In addition, embedded computer 21 controls the
operation of the excimer laser 28, which is preferably an
argon-fluorine laser with a 193 nanometer wavelength output
designed to provide feedback stabilized fluence of 160 mJoules per
square centimeter at the cornea of the patient's eye 30 via the
delivery system optics generally designated with reference numeral
29 and shown in FIG. 9. Other lasers having a suitable wavelength
may be used to make an ablative energy for removing a tissue from
the eye. For example, solid state lasers such as a yittrium
aluminum garnet (YAG) laser producing a fifth harmonic of a
fundamental wavelength may be used to generate an ablative energy.
Other ancillary components of the laser surgery system 20 which are
not necessary to an understanding of the invention, such as a high
resolution microscope, a video monitor for the microscope, a
patient eye retention system, and an ablation effluent
evacuator/filter, as well as the gas delivery system, have been
omitted to avoid prolixity. Similarly, the keyboard, display, and
conventional PC subsystem components (e.g., flexible and hard disk
drives, memory boards and the like) have been omitted from the
depiction of the PC work station 10. If desired, embedded computer
21 may be constructed with PC work station components and built
into laser surgery system 20. In this case embedded computer 21 may
supplant PC workstation 10.
[0059] The iris motor 23 is used to control the diameter of a
variable diameter iris schematically depicted in FIG. 5. The
astigmatism motor 25 is used to control the separation distance
between a pair of cylinder blades 35, 36 which are mounted on a
platform 38 for bi-directional translational motion in the
direction of arrows 40, 41. Platform 38 is rotatably mounted on a
second platform (not illustrated) and is rotationally driven by
astigmatism angle motor 26 in a conventional way in order to enable
alignment of the slit axis (illustrated in a vertical orientation
in FIG. 5) with the appropriate coordinate axes of the patient's
eye. Iris 32 is driven by iris motor 23 in a known way to change
the diameter of the iris opening from a fully opened position (the
position illustrated in FIG. 5) to a fully closed position in which
the aperture is closed to a minimum diameter of 0.8 mm. It is
understood that the variable diameter iris 32 and the cylinder
blades 35, 36 are positioned with respect to the output of laser 28
in such a manner as to intercept the beam prior to irradiation of
the corneal surface of the patient's eye 30. For the purpose of
this application, it may be assumed that iris 32 and cylinder
blades 35, 36 are part of the delivery system optics subunit 29
shown in FIG. 4.
[0060] The system of FIGS. 4 and 5 is used according to the
invention to effect presbyopic, hyperopic, myopic, astigmatic, and
other error corrections to the anterior surface of the cornea, to
provide a smooth transition zone between the outer edge of the
optical zone and the untreated surface of the cornea, and to effect
surface smoothing when desired. Other techniques besides the above
area profiling of a laser beam may be used to profile the laser
beam to a desired size and energy distribution on the surface of
the eye. For example a lens may be used to profile a beam exiting
from an aperture by focusing the beam to a suitably small area and
desired energy profile as described in U.S. Pat. No. 4,718,418, the
full disclosure of which is herein incorporated by reference. Also
a diffractive optic may be used to adjust an energy profile of the
laser beam on the surface of the eye as described in co-pending
application entitled Laser Delivery System and Method with
Diffractive Optic Beam Integration, U.S. patent application Ser.
No. 09/015,841 filed on Jan. 29, 1998 the full disclosure of which
is herein incorporated by reference.
[0061] With reference to FIG. 6, an imaging lens 51 is laterally
offset from an axis 52 by a variable amount in the manner set forth
more fully below. Lens 51 preferably comprises the existing imaging
lens found in the delivery system optics 29 of the FIG. 4 system.
Axis 52 is the axis corresponding to the center of rotation of lens
51. Displacing lens 51 by translating the lens in a radial
direction off the axis 52, which may or may not correspond to the
laser beam axis, displaces the image 54 of aperture 53 in a related
manner. By also rotating lens 51 about the axis 52 in an eccentric
fashion, as illustrated in FIG. 7, the displaced image 54 of
aperture 53 can be scanned about axis 52. This scanning is along a
preselected path, which in the hyperopic correction procedure
described below is an annular path about the axis 52. Depending
upon the manner in which the lens offset, lens rotation, slit
width, slit rotation and iris diameter are controlled, various
types of ablation corrections can be effected. These corrections
include presbyopia correction, hyperopic error corrections,
hyperopic astigmatism corrections, and other vision error
corrections, along with simultaneous or successive edge contouring
to form a smooth transition zone.
[0062] FIG. 8 illustrates the aperture positioning relative to the
intended ablation center when employing the variable diameter iris
32 and cylinder blades 35, 36 of FIG. 5 to effect a refractive
error correction. In this Figure, R2 represents the half width of
the slit between blades 35, 36, Ri is the radius of the iris 32, r
is the radius of a circle covered by the aperture, is the radial
offset of the center of the image of the slit aperture relative to
the center of rotation 52, and 0 is the half angle for which the
circle of radius r is covered by the aperture. The intended ablated
optical zone is the central region bounded by circle 61 and the
intended ablated transition zone is the annular region bounded by
circles 61 and 62.
[0063] The manner in which the slit width and diameter are varied
by the computer depends upon the type of vision correction desired.
For a hyperopic correction, a fixed value of the refractive
correction may be used to generate the cut profile C(r). For a
hyperopic refractive correction of a given fixed value, the
sequencing of the aperture is done in such a manner as to satisfy
the hyperopic lens equations described in "Photorefractive
Keratectomy: A Technique for Laser Refractive Surgery" authored by
Munnerlyn et al., J. Cataract Refract. Surg. Vol. 18, pages 46-52
(January, 1988), the entire disclosure of which is hereby
incorporated by reference. Also, European Patent Office publication
number EP 0 628 298 A1, published Dec. 14, 1994, discloses an
aperture sequencing for correcting hyperopia, the entire disclosure
of which is hereby incorporated by reference.
[0064] For the correction of presbyopia, it may be desirable to
vary the refractive power across the ablated surface. The cut
profile C(r) may be calculated by calculating the incremental cut
profiles along the surface. The incremental cut profiles are then
summed to calculate the overall cut profile C(r). The incremental
cut profiles may be calculated using the above hyperopic lens
equation, the desired ablated refractive correction, and the
position from the center of the aspheric lens.
[0065] The cut profile is given by the equation:
C(r)=(d/.pi.).SIGMA..sub.i(n.sub.i.theta.(r)) (1)
where n.sub.i is the number of laser pulses for the i.sup.th
aperture in a sequence of aperture dimensions and radial positions,
and d is the amount of material removed with each laser pulse or a
scaling factor which also takes into account corneal healing. Once
the cut profile has been calculated, the sequence of aperture
dimensions and pulses may be calculated. The sequence of aperture
dimensions is created by control of the width of the slit and the
diameter of iris 32 throughout the surgical procedure. The sequence
of aperture dimensions and positions are preferably incorporated
into a laser treatment table.
[0066] The sequence of aperture dimensions may also be tailored to
accommodate variations in the ablation profiles of individual
pulses from the laser beam. For example, the spatial variation of
tissue ablation may cause the geometry of tissue ablated with a
single laser pulse to be deeper at the edges of an ablation
adjacent the image of iris 32 and cylinder blades 35 and 36. For an
individual laser pulse, this increased ablation depth near the edge
of an ablation may be 50% greater than the central ablation depth.
Therefore, a 4D intended hyperopic ablation that assumes a uniform
layer of tissue is removed with each laser pulse will ablate about
6 D of correction near the center of ablated optical zone 211.
Clinically, the inventors have observed that patients treated with
the above ablation algorithm for 3 to 4 D of hyperopia have also
been successfully treated for presbyopia. However, with a +2D
correction, the correction of presbyopia is only partial. Therefore
to correct presbyopia and hyperopia, it may be desirable to combine
the +2 D correction with an aspheric ablation. In this case, the
aspheric correction is about one half of the aspheric correction
that would be ablated on an eye with no refractive error.
[0067] Preferably, the refractive correction of cut profile C(r) is
scaled to match a dimension of the pupil. This scaling may be
achieved by appropriately varying the refractive correction entered
into the hyperopic lens equation. For example, consider the scaling
of an ablation for a 5 mm pupil compared to a 4 mm pupil. If the
aspheric surface includes a 1.5D ablated curvature 1.25 mm from the
aspheric lens center for the 5 mm pupil, this 1.5D curvature will
be ablated 1.0 mm from the aspheric lens center on a 4 mm pupil.
This scaling maintains a balance of near and far-vision correction
by accommodating individual variability in pupil size. By scaling
the cut profile C(r), the scaling of the ablated optical zone is
incorporated into the laser treatment table.
[0068] For the example shown in FIG. 8, the values of s and R2 are
varied to produce the correct value of radial offset (s) and slit
width (2.times.R2) so that the inner edge of blade 35 is moved in
steps from close to the center of the ablation (starting at
approximately 0.6 mm from the center) to the edge of the corrected
optical zone at approximately 2.5 mm. R, (the iris radius) is fixed
at a predetermined value (3 m in one specific procedure), and s and
R2 are chosen to anchor the edge of the ablation at the outer edge
of the intended transition zone of approximately 5 mm radius. The
number of pulses for each successive position of the inner edge is
calculated to give the desired depth from the hyperopic lens
equation. For a procedure requiring the least number of pulses, the
treatment is ended as soon as the inner edge of the aperture
reaches the boundary of the corrected optical zone. Initially, the
slit width is set to a maximum value and the imaging lens 51 is
positioned laterally of the axis of rotation 52 such that the inner
slit edge is positioned at the minimum distance from the center of
the optical zone and the intersections of the iris diaphragm 32 and
the outer slit edge are positioned over the outer edge of the
intended transition zone.
[0069] The image of the aperture is now ready to be scanned over
the anterior surface of the cornea. While several different
scanning sequences are possible, the following sequence has been
actually implemented with effective results. The radial position
along the optical zone is broken into a series of discrete,
equidistant (typically 0.1 mm apart) nodes. The number of pulses
required to ablate tissue to cut depth C(r) at a node adjacent to
the edge of the inner slit is calculated using
n=(.pi.*.delta.C(r.sub.n)/.theta..sub.i(r.sub.n)*d)
where n is the number of pulses, .delta.C(r.sub.n) is the
difference between the actual ablation depth from previous pulses
and the desired ablation depth at the node, .theta..sub.i (r.sub.n)
is the half angle coverage of the aperture at r.sub.n as previously
defined. The radial ablation profile from previous pulses is
calculated by summing the ablation depth from previous positions
and pulses at each node as described by equation I. For the initial
position, .delta.C(r.sub.n)=C(r). The number of pulses required for
each subsequent node is calculated for each node adjacent to the
inner cylinder blade as the blade moves toward the edge of the
optical zone. Having determined the correct number of pulses at
each node, the treatment must be smoothed rotationally to ensure
that it is correct and free from aberrations.
[0070] FIG. 9 is a schematic view of the delivery system optics in
an embodiment. As seen in this Fig., the beam from laser 28 is
reflected by a first mirror 71 and a second mirror 72, and enters a
spatial integrator 73, where the beam is modified in cross-section.
A diffractive optic may be used to modify a cross section of the
laser beam as described in co-pending application entitled Laser
Delivery System and Method with Diffractive Optic Beam Integration,
U.S. patent application Ser. No. 09/015,841 filed on Jan. 29, 1998,
the full disclosure of which is incorporated herein by reference.
The modified beam exiting from spatial integrator 73 is reflected
by mirrors 74 and 75 and passed through a dove prism 76 to the
iris/slit mechanism 78 which contains the variable width slit and
variable diameter iris described above. The profiled beam exiting
from the unit 78 is reflected by a mirror 79 and enters the image
offset control unit 80 which contains imaging lens 51. The offset
profiled image exiting from unit 80 is reflected from a mirror 82
onto the patient's eye. To smooth out fluctuations in beam energy
across the beam area, dove prism 76 is rotatably mounted, and is
typically rotated during beam generation either continuously or
between pulses.
[0071] The invention affords great flexibility in performing
various types of corrections by virtue of the fact that the system
can be programmed to accommodate patients having differently sized
physical eye parameters and refractive and presbyopic correction
requirements. The variable slit width/variable diameter iris
arrangement is particularly adaptable for use in the simultaneous
treatment of presbyopia, hyperopia, hyperopic astigmatism and
irregular refractive aberrations. For simultaneous treatment of
presbyopia, hyperopia and hyperopic astigmatism, the ablation
geometry is solved as a function of radial displacement and angular
position of the aperture image about the rotational center.
Further, in all procedures requiring a smoothing of the transition
zone at the periphery of the ablation zone, the diameter of the
iris is varied over a predetermined range along with the slit width
variation. For presbyopia and refractive aberrations, a device such
as a spatially resolved refractometer or a topography machine or
both may be used to map the irregular surface contour of the cornea
to determine the exact surface corrections required. Thereafter,
the slit width and the iris diameter can be programmed such that
corneal sculpting will achieve the desired aspheric surface
geometry on a healed cornea. Alternatively, a wavefront sensor may
be used to map the irregular refractive aberrations of the eye. One
suitable embodiment of such a wavefront sensor is the
Hartmann-Shack sensor described in U.S. Pat. No. 5,777,719, the
entire disclosure of which is herein incorporated by reference.
[0072] For any of the above specific correction procedures, a
treatment table is normally constructed. The treatment table
contains the value of all of the discrete radial and angular
positions of the optomechanical elements used to scan the image
over the relevant portion of the anterior corneal surface. This
table also contains the number of laser pulses per position. A
typical treatment table contains on the order of about 500
different entries.
[0073] The treatment table for a given procedure may incorporate
special features designed to improve the efficiency of the
procedure. For example, for some procedures (e.g., simultaneous
hyperopic and presbyopic correction) it can be beneficial to leave
a small zone centered on the optical zone untreated. This can be
done by constraining motion of the inner cylinder blade to
guarantee occlusion in the small zone of interest. The diameter of
the untreated zone varies from about 0.1 to 1.5 mm, is preferably
from about 0.5 to 1.0 mm and is ideally about 0.7 to 0.9 mm. Also,
standard tables can be constructed for a specific procedure--e.g.,
hyperopic correction--to different Dioptric correction values, and
these standard tables can be sorted and combined to perform
multiple repetitions of one or more standard tables to effect a
given Dioptric correction. For example, standard tables may be
created for a myopic correction for values of 1/4, 1/2 and 1
Diopter. Using these tables, a 3.75 Diopter correction would
proceed by performing the standard 1 Diopter correction three
times, followed by the 1/2 Diopter correction and the 1/4 Diopter
correction.
[0074] While the invention has been described above with specific
reference to ablation of an anterior corneal surface, various
portions of the cornea may also be treated using the invention. For
example, the epithelium may be mechanically removed by scraping, as
is typically done in photorefractive keratectomy, and the exposed
surface may be ablated. Further, the invention can also be used for
laser keratomileusis of corneal lamella removed from the cornea.
This procedure is described in U.S. Pat. No. 4,903,695, issued Feb.
27, 1990, entitled "Method and Apparatus for Performing a
Keratomileusis or the Like Operation."
[0075] In applying the invention to this procedure, a flap of
corneal tissue is physically removed (either fully or partially)
from the cornea, the size of the removed portion typically lying in
the range from about 8 to 10 mm wide and a variable thickness up to
400 microns. This flap of tissue is typically removed using a
microkeratome. Next, the flap is placed in a suitable
fixture--typically an element having a concave surface--with the
anterior surface face down. Thereafter, the required ablation is
performed on the reverse exposed surface of the flap, after which
the ablated flap is repositioned on the cornea. Alternatively,
after the flap is removed from the cornea, the exposed stromal
tissue of the eye can be ablated according to the invention, after
which the flap is reattached over the freshly ablated stromal
tissue.
[0076] The technique of shaping a cornea is further illustrated in
FIGS. 10-15. These figures illustrate measured ablation profiles,
intended optical corrections and measured anterior corneal surface
optical corrections. The effect of the spatial variance of ablation
on ablation shape is illustrated in FIG. 10. A measured ablation
shape is plotted as a function of radial position over the ablated
optical zone. This figure illustrates an ablated optical zone using
an ablation algorithm that assumes a uniform layer of tissue is
removed with each laser beam pulse. The intended optical correction
is a +3 D optical correction 410. However, illustrated ablated
optical zone 420 is significantly different. The ablated optical
zone 420 is overcorrected by about 100% in the central ablation
zone 422. The ablated optical zone 420 is over corrected in the
peripheral ablation zone 424 by about 60%. The initial shape of
ablated optical zone 420 differs significantly from the healed
anterior surface shape, and the healed shape substantially corrects
the initial hyperopic refractive error of the eye.
[0077] The covering and healing of the ablated surface decrease the
difference between the intended optical correction and the anterior
corneal surface optical correction as illustrated in FIG. 11. A
measured anterior corneal surface optical correction is plotted as
a function of radial position over an ablated optical zone. The
anterior optical correction 430 of the healed cornea more closely
matches the intended +3 D spherical optical correction 410.
However, errors between the intended optical correction 410 and the
anterior surface optical correction 430 are still present. The
central anterior optical correction 432 is over corrected compared
to the intended +3 D spherical optical correction 410. This over
correction of the central optical correction 432 is by about 25%
relative to the intended +3 D optical correction, and corresponds
to a 0.75 D near-vision correction at 2 mm. However, the peripheral
anterior optical correction 434 is slightly under corrected
relative to the intended +3 D optical correction. This correction
of the peripheral anterior optical correction 434 appropriately
provides distance vision correction. Therefore, the anterior
optical correction 430 is multifocal and will provide some
correction of presbyopia. This multifocal effect occurs because the
ablated shape compensates for changes in corneal shape as the
cornea heals. The peripheral ablated optical zone is overcorrected
to provide distance vision on a healed cornea. The central optical
zone is overcorrected to provide near-vision on the healed cornea.
Commercially available corneal topography systems measure healed
anterior corneal surfaces. Examples of such systems include the
Atlas Corneal Topography System.TM. available from HUMPHREY
INSTRUMENTS of San Leandro, Calif. and the PAR CTS System.TM.
available from PAR VISION SYSTEMS CORPORATION of New Hartford,
N.Y.
[0078] The effect of the covering and corneal healing of an ablated
optical zone is illustrated in FIG. 12. This figure illustrates the
difference in shape between an ablated shape and the final anterior
optical correction on the anterior surface of the cornea. This
difference in shape is described as a healing-induced change 440
shown in FIG. 12. The healing-induced change 440 is illustrated for
a patient treated for +3 D of hyperopia. The ablated shape is
partially filled in by covering and healing to form the anterior
optical correction. However, this partial filling is not constant
over the ablated optical zone. The center of the ablated optical
zone shows less filling than the peripheral optical zone. The
peripheral optical zone is filled in by about 50% while the central
optical zone is filled in by about 30%. A peripheral filling 444 is
greater than a central filling 442. Proximity to the ablated
transition zone causes the peripheral optical surface to be a
different shape than the underlying ablated peripheral optical
zone. However, the anterior central optical surface is distant from
the ablated transition zone. Therefore, the shape of the anterior
central optical surface more closely matches the shape of the
ablated central optical zone. With the above differential healing,
an optical zone ablated to a substantially spherical shape for
correcting hyperopia will heal to an aspheric shape that corrects
for presbyopia.
[0079] By estimating a healing-induced change, an initial ablated
surface shape may be derived from a desired anterior corneal
surface shape and a healing-induced change as illustrated in FIG.
13. For example, consider a desired anterior surface correction 450
that corrects for +3 D of hyperopia and corrects for presbyopia
with a central zone providing +3 D of near-vision correction. The
desired anterior surface correction 450 is also illustrated in FIG.
13. An initial ablated surface shape 460 is calculated from the
healing-induced change 440 and the desired anterior surface
correction 450. The initial ablated shape 460 for the desired
anterior surface correction 450 is illustrated in FIG. 13. The
initial ablated shape 460 is overcorrected relative to the desired
anterior surface correction. The initial ablated shape 460 is
calculated by multiplying the desired anterior surface correction
450 by the ratio of the ablated shape 420 to the healed shape 430.
A processor may be used to generate the ablated shape in response
to the desired correction input by the system operator, typically
making use of the embedded computer of the laser workstation, the
PC workstation, and/or the programming and hardware of an external
computer.
[0080] The ablated shape may be restricted or reduce relative to a
desired anterior surface correction to obtain the desired anterior
surface correction. The diameter of the relative restriction is
between about 0.1 and 2 mm, preferably between about 0.2 and 1 mm
and is ideally between about 0.3 and 0.7 mm. In an exemplary
embodiment this restriction is about 0.5 mm as illustrated in FIG.
14. After covering an ablated corneal surface feature (such as a
presbyopia correction) and allowing healing of a cornea, an
anterior surface correction may extend beyond the initial ablated
dimensions of the ablated surface feature. Ablated central zone 470
on reference 480 includes dimension 472 across the central ablated
zone. Ablated central zone 470 also includes elevation 474 relative
to the reference 480. Reference 480 may be any suitable reference
such as a spherical reference surface on an anterior optical
surface or an ablated surface. Covering of ablated central zone 470
and healing of the cornea will form a central anterior optical
surface 490. Central anterior optical surface 490 includes
dimension 492 across the central anterior optical surface and
elevation 494 relative to reference 480. A 1.5 mm dimension 472
across the ablated central zone 470 will typically extend to a 2 mm
dimension 492 across the central anterior optical surface 490.
Therefore, to form a 2 mm central anterior optical surface, the
ablated central zone is preferably restricted by a relative amount
of about 0.5 mm. Also, it may be desirable to increase the
elevation 474 of the ablated feature by a relative amount as
illustrated above. For example, an ablation intended to produce a 4
um surface elevation 494 relative to a reference 480 on the
anterior surface of a healed cornea may be over ablated as an 8 um
surface elevation 474 relative to a reference 480. This
overcorrecting of the ablated feature is by a relative amount of 4
um. Relative over-correction ranges from about 1 to 25 um. A
desired final 2 mm diameter zone on an anterior surface to correct
for near-vision with 3 D might typically have an elevation of about
4 um. To correct presbyopia using such a healed shape (in other
words, to produce a central zone having a diameter of about 2 mm
and an elevation of about 4 um on the anterior surface of a healed
cornea), a central ablation zone having a restricted diameter of
about 1.5 mm and an overcorrected elevation of about 8 um is
ablated onto an exposed surface of the cornea. Although the term
"diameter" is used to indicate a lateral dimension of these
features (and in general in this application), it should be
understood that the features need not necessarily be circular.
[0081] In some instances, it may be desirable to treat presbyopia
by leaving a central region of the optical zone untreated as
illustrated in FIG. 15. A small untreated zone 500 centered on the
optical zone 502 of an ablated cornea has a dimension 504 across
the untreated zone. The untreated zone 504 is smoothed by covering
and healing of the cornea and contributes to the formation of a
central anterior optical surface that corrects presbyopia.
[0082] The above techniques can be used to calculate initial
ablation shapes for treating conditions besides hyperopia and
presbyopia. These techniques may be used to calculate the initial
ablation shapes used to treat astigmatism, myopia and irregular
refractive aberrations of the eye. For example, the higher order
aberration terms of an irregular refractive aberration may be over
corrected on an ablated corneal surface to form an anterior surface
on a healed cornea with a desired optical correction of the higher
order aberrations.
[0083] The above technique of making a multifocal optical
correction on the anterior surface of the cornea can be applied to
both eyes of a patient to provide an improved correction of
presbyopia with binocular vision. The correction of presbyopia
preferably covers about a 3 D range. However, with binocular vision
this approximately 3 D range of presbyopia correction may be
treated by treating each eye with a multifocal optical correction
having less than the full 3 D range of presbyopia correction. In
this case, the average refraction of each of the two eyes is
different to provide clear vision over the full 3 D range. A first
eye is corrected for near-vision, and a second eye is corrected for
distance vision. The multifocal anterior optical surface provides
improved focus for objects intermediate to near and far-vision. For
example, one eye is treated to have an average refraction of -0.75
D with a 1.5 D multifocal range of focus. This eye has an effective
focus from 0 to -1.5 D. The other eye is treated to have an average
refraction of about -2.25 D with a 1.5 D multifocal range of focus.
This eye has an effective focus from about -1.5 D to -3 D. The
effective range of focus of the two eyes combined is about 3 D. The
multifocal range on each eye varies between about 0.5 and 2.0 D,
and is preferably between about 1.0 and 1.5 D. The difference
between the average refraction of the two eyes varies between about
0.5 and 2.5 D, and is preferably between about 1 and 2 D.
[0084] While the above provides a full and complete disclosure of
the preferred embodiments of the invention, various modifications,
alternate constructions and equivalents may be employed as desired.
For example, while the invention has been described with specific
reference to the system of FIGS. 4 through 9, other systems may be
employed, as desired. Further, lasers of other appropriate
wavelengths than laser 28 may be used, if desired and effective.
Also, laser systems which operate on the principle of thermal
ablations, such as lasers having wavelengths lying in the infrared
portion of the electromagnetic spectrum, may be used to implement
the invention. In addition, while the radial and angular
positioning of the profiled beam is accomplished with imaging lens
51 in the preferred embodiment, other optical scanning
elements--such as rotating mirrors and prisms--may be employed, if
desired. Therefore, the above description and illustrations should
not be construed as limiting the invention, which is defined by the
appended claims.
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