U.S. patent application number 17/398944 was filed with the patent office on 2021-12-02 for hydrophilicity alteration system and method.
The applicant listed for this patent is PERFECT IP, LLC. Invention is credited to Josef F. Bille, Ruth Sahler, Stephen Q. Zhou.
Application Number | 20210369444 17/398944 |
Document ID | / |
Family ID | 1000005779384 |
Filed Date | 2021-12-02 |
United States Patent
Application |
20210369444 |
Kind Code |
A1 |
Sahler; Ruth ; et
al. |
December 2, 2021 |
HYDROPHILICITY ALTERATION SYSTEM AND METHOD
Abstract
A system/method allowing hydrophilicity alteration of a
polymeric material (PM) is disclosed. The PM hydrophilicity
alteration changes the PM characteristics by decreasing the PM
refractive index, increasing the PM electrical conductivity, and
increasing the PM weight. The system/method incorporates a laser
radiation source that generates tightly focused laser pulses within
a three-dimensional portion of the PM to affect these changes in PM
properties. The system/method may be applied to the formation of
customized intraocular lenses comprising material (PLM) wherein the
lens created using the system/method is surgically positioned
within the eye of the patient. The implanted lens refractive index
may then be optionally altered in situ with laser pulses to change
the optical properties of the implanted lens and thus achieve
optimal corrected patient vision. This system/method permits
numerous in situ modifications of an implanted lens as the
patient's vision changes with age.
Inventors: |
Sahler; Ruth; (Costa Mesa,
CA) ; Zhou; Stephen Q.; (Irvine, CA) ; Bille;
Josef F.; (Heidelberg, DE) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
PERFECT IP, LLC |
Dallas |
TX |
US |
|
|
Family ID: |
1000005779384 |
Appl. No.: |
17/398944 |
Filed: |
August 10, 2021 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14275325 |
May 12, 2014 |
11090151 |
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|
17398944 |
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13843464 |
Mar 15, 2013 |
9023257 |
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14275325 |
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61726383 |
Nov 14, 2012 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
B29C 2791/009 20130101;
A61F 2/1648 20130101; B29C 2035/0838 20130101; B29C 71/04 20130101;
B29K 2995/0092 20130101; A61F 9/00834 20130101; A61F 9/008
20130101; B29D 11/00125 20130101; A61F 2/1613 20130101; A61F 2/1627
20130101; A61F 2/16 20130101 |
International
Class: |
A61F 2/16 20060101
A61F002/16; A61F 9/008 20060101 A61F009/008; B29C 71/04 20060101
B29C071/04; B29D 11/00 20060101 B29D011/00 |
Claims
1. A method for modifying a polymeric material (PM) for use as a
lens comprising: modifying a single layer between an anterior
surface and a posterior surface of the lens; creating a set of
phase wrapped zones within the single layer with a femtosecond
laser utilizing an intermittent stream of laser pulses to make a
change to a hydrophilicity level of some or all of the phase
wrapped zones; utilizing a first energy of the intermittent stream
of laser pulses to create a first structure having a first
hydrophilicity level within a first phase wrapped zone, wherein the
first energy is different from a second energy of the intermittent
stream of laser pulses used to create a second structure having a
second hydrophilicity level within the first phase wrapped zone of
the set of phase wrapped zones, and the first energy and the second
energy are each used to create at least two structures within each
phase wrapped zone of the set of phase wrapped zones to create
multiple hydrophilicity changes within the PM.
2. The method of claim 1, further comprising causing water to be
absorbed by the PM within the at least two structures of each phase
wrapped zone of the set of phase wrapped zones through the use of
the intermittent stream of laser pulses.
3. The method of claim 1, further comprising initiating a chemical
reaction within the PM with the intermittent stream of laser
pulses.
4. The method of claim 1, wherein the PM comprises a hydrophobic
material.
5. The method of claim 1, wherein the PM comprises a hydrophilic
material.
6. The method of claim 1, further comprising changing at least one
refractive characteristic of the lens.
7. The method of claim 6, wherein the changing of the at least one
refractive characteristic further comprises changing the PM's
ability to transmit light and may include changes to a spherical
diopter, a cylindrical diopter, or an asphericity of the lens.
8. The method of claim 1, wherein the at least two structures
within each phase wrapped zone of the set of phase wrapped zones of
the single layer have an increased water content after application
of energy from the femtosecond laser when a laser modified area is
in relation to a liquid; and utilizing the laser modified area
adjusts a refractive index of the PM by application of different
levels of energy from the femtosecond laser to different structures
within each phase wrapped zone of the set of phase wrapped
zones.
9. The method of claim 8, wherein the liquid is a water based
solution.
10. The method of claim 8, wherein the liquid is a naturally
occurring liquid.
11. A system for producing a phase-wrapped gradient lens
comprising: a laser source capable of generating a pulsed laser
radiation output with a wavelength of selected to permit a
two-photon process within a modified polymeric material (PM); a
microscope having an input area for receiving the pulsed laser
radiation output, and distributing the pulsed laser radiation
output through a microscope objective into a set of structures;
wherein a first energy per structure of a first phase wrapped zone
is constant for each phase wrapped zone but a second energy of a
second set of structures within the first phase wrapped zone is
modulated to alter a hydrophilicity level of one or more structures
within each phase wrapped zone; and wherein a single layer within
the PM receives the pulsed laser radiation output.
12. The system of claim 11, wherein the pulsed laser radiation
output is received at a depth between 5 and 150 microns in the
single layer.
13. The system of claim 11, wherein the pulsed laser radiation
output is received at a depth of at least 5 microns in the single
layer.
14. The system of claim 11, wherein the pulsed laser radiation
output is received at a depth that is less than 250 microns in the
single layer.
15. The system of claim 11, wherein the set of structures define an
internal region that when modified changes a refractive index of
the internal region.
16. The system of claim 15, wherein the refractive index change is
negative.
17. The system of claim 11, wherein the set of structures are an
internal region that, when modified, changes the hydrophobic
properties of the internal region.
18. The system of claim 11, wherein the set of structures
structures are an internal region that, when modified, changes the
hydrophilic properties of the internal region.
19. The system of claim 11, further comprises pausing the pulsed
laser radiation output to allow for heat dissipation in the PM.
20. A phase wrapped gradient lens formed of a modified polymeric
material (PM) comprising: a single layer within the PM for
receiving a stream of laser pulses from a laser source; a set of
phase wrapped zones within the single layer, with each phase
wrapped zone having a set of structures; and wherein a first energy
per structure of a first phase wrapped zone is constant for each
phase wrapped zone but a second energy of a second set of
structures within the first phase wrapped zone is modulated to
alter the hydrophilicity of one or more structures within each
phase wrapped zone.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. application Ser.
No. 14/275,325, filed on May 12, 2014, which is a divisional of
U.S. patent application Ser. No. 13/843,464 filed on Mar. 15, 2013,
now U.S. Pat. No. 9,023,257, issued on May 5, 2015, which claims
benefit of U.S. provisional application No. 61/726,383, filed on
Nov. 14, 2012, the technical disclosures of which are hereby
incorporated herein by reference.
PARTIAL WAIVER OF COPYRIGHT
[0002] All of the material in this patent application is subject to
copyright protection under the copyright laws of the United States
and of other countries. As of the first effective filing date of
the present application, this material is protected as unpublished
material.
[0003] However, permission to copy this material is hereby granted
to the extent that the copyright owner has no objection to the
facsimile reproduction by anyone of the patent documentation or
patent disclosure, as it appears in the United States Patent and
Trademark Office patent file or records, but otherwise reserves all
copyright rights whatsoever.
STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT
[0004] Not Applicable
REFERENCE TO A MICROFICHE APPENDIX
[0005] Not Applicable
FIELD OF THE INVENTION
[0006] The present invention relates to the modification of the
hydrophilicity of a material. The hydrophilicity of the material is
changed by exposing the material to targeted laser pulses. The
laser pulses are absorbed and alter chemical bonds of the molecules
within the material. The material (if hydrophobic) then either
absorbs water because of the altered molecular structure or rejects
water (if the material is hydrophilic). By way of example only, the
present invention teaches a laser system and a method for modifying
the hydrophilicity of an optical lens in a predetermined region
inside the lens bulk body with or without a hydrophilicity change
on the lens surfaces. The material used in the experiments
described herein as applied to the present invention is a polymeric
acrylic lens material (PLM) but this material selection is
exemplary and should not be treated as a limitation of the present
invention.
PRIOR ART AND BACKGROUND OF THE INVENTION
Background (0100)-(0400)
[0007] Conventionally, intraocular lenses are manufactured using
cutting or molding techniques to fabricate polymer-based lenses
which may need a tumbling step to acquire optical grade quality.
Optical lenses can be surface modified by physical and chemical
methods.
[0008] Physical methods include, but are not limited to plasma,
corona discharge, and microwave processes. This treatment can
change the hydrophilicity of the lens surface. For example, U.S.
Pat. No. 5,260,093 issued on Nov. 9, 1993 to Ihab Kamel and David
B. Soll for METHOD OF MAKING BIOCOMPATIBLE, SURFACE MODIFIED
MATERIALS disclosed a method for permanently modifying the surface
of a substrate material by radio frequency plasma. One of the
substrates in disclosed in this patent is an intraocular lens.
[0009] Chemical modification of optical lenses is also well known.
The chemical modification of optical lenses can change the chemical
composition on the surface, thus this not only changes the
hydrophilicity of the lens surface, but also the physical and
chemical properties of the surface as well. For example, U.S. Pat.
No. 6,011,082 issued on Jan. 4, 2000 to Yading Wang, Robert van
Boxtel, and Stephen Q. Zhou for PROCESS FOR THE MODIFICATION OF
ELASTOMERS WITH SURFACE INTERPRETING POLYMER NETWORKS AND
ELASTOMERS FORMED THEREFROM disclosed a chemical modification
method which allows a polymeric silicone intraocular lens to be
chemically modified into a hydrophilic surface by heparin as well
as other hydrophilic agents.
[0010] However, the above prior art methods can only be used to
treat the lens surfaces. They cannot be used to modify the
hydrophilicity of the lens bulk body below the surface. In other
words, they cannot be used to treat a predetermined region inside a
lens material.
[0011] In contrast, recent laser technology has made it possible to
selectively target a predetermined region inside a material,
including optical lens materials without changing the lens surface.
For example, United States Patent Application Publication
US2002/0117624A for PLASTIC OBJECT published on Aug. 29, 2002
having inventors Shigeru Katayama and Mika Horiike disclosed a
general method using a laser to fabricate a plastic object which
has been structurally modified in one part of its internal body by
a laser light of ultrashort pulse duration of 10.sup.-12 second or
shorter. Examples of internal structures created using this prior
art technique are generally illustrated in FIG. 1 (0100) and FIG. 2
(0200).
[0012] A more recent application in United States Patent
Application Publication US2008/0001320A1 for OPTICAL MATERIAL AND
METHOD FOR MODIFYING THE REFRACTIVE INDEX published on Jan. 3, 2008
having inventors Wayne H. Knox, Li Ding, Jay Friedrich Kunzler, and
Dharmendra M. Jani disclosed a method for modifying the refractive
index of an optical polymeric material comprising irradiating the
selected region by femtosecond laser pulses (using a system
configuration as generally illustrated in FIG. 3 (0300)) resulting
in the formation of refractive optical structure of the laser
treated region which is characterized by a positive change in
refractive index. This patent application publication also
disclosed calculating the refractive index change (.DELTA.n) as
positive in the range of 0.03 to 0.06. This prior art teaches that
if the selected treatment region is a convex-plano shape, it will
create a positive lens while if the treated region is a biconcave
shape, then it will be a negative lens. This is described in
drawings of the US2008/0001320A1 patent application publication and
is reproduced as FIG. 4 (0400) herein.
[0013] The prior art does not address the modification of the
hydrophilicity of an internal region of a material.
[0014] Deficiencies in the Prior Art
[0015] While the prior art as detailed above can theoretically be
used to form optical lenses, it suffers from the following
deficiencies: [0016] Prior art limits the lens formed within the
lens material to 2.65 diopter in change for a lens with a 200
micron thickness and 6 mm diameter while the present invention
creates a up to a 20 diopter lens with the same lens diameter.
[0017] Prior art requires several hours to create a 2.65 diopter
lens while the present invention would produce the same lens in a
few minutes. Prior art paper publication show a shaping speed of
0.4 um/s for the high refractive index change. The following
parameters have been used: a spot size of lum in XY and 2.5 um in Z
and a convex lens diameter with 6 mm and a lens depth of 200 um.
Source: Li Ding, Richard Blackwell, Jay F. Kunzler and Wayne H.
Knox "LARGE REFRACTIVE INDEX CHANGE IN SILICONE-BASED AND
NON-SILICONE-BASED HYDROGEL POLYMERS INDUCED BY FEMTOSECOND LASER
MICRO-MACHINING". [0018] Prior art can only produce a positive
diopter change assuming a convex lens while the instant invention
can only produce a negative diopter change using a convex lens.
[0019] Prior art is limited to one lens within the material while
the invention can stack multiple lens to increase the diopter
change or alter asphericity, toricity or other lens properties.
[0020] Prior art discloses no relationship between hydrophilicity
change and UV absorption while the instant invention relies on UV
absorption to effect the change in hydrophilicity. [0021] Prior art
makes no change in hydrophilicity and the instant invention relies
upon a change in hydrophilicity to effect the change in the
material. To date the prior art has not fully addressed these
deficiencies.
OBJECTIVES OF THE INVENTION
[0022] Accordingly, the objectives of the present invention are
(among others) to circumvent the deficiencies in the prior art and
affect the following objectives: [0023] (1) provide for a system
and method that permits the modification of the hydrophilicity of
the interior of a material with or without a change in the
hydrophilicity of the surface of the material; [0024] (2) provide
for a system and method that alters the hydrophilicity of an entire
predetermined three dimensional region within a polymeric material;
[0025] (3) provide a system and method of manufacturing an optical
lens; and [0026] (4) provide a system and method for altering the
hydrophilicity of a predetermined internal region of an implanted
intraocular lens thus altering the refractive properties of the
implanted intraocular lens according to the individual patient's
need for a desirable vision outcome.
[0027] While these objectives should not be understood to limit the
teachings of the present invention, in general these objectives are
achieved in part or in whole by the disclosed invention that is
discussed in the following sections. One skilled in the art will no
doubt be able to select aspects of the present invention as
disclosed to affect any combination of the objectives described
above.
BRIEF SUMMARY OF THE INVENTION
[0028] The present invention pertains to a system, method, and
product-by-process wherein a pulsed laser system is used to modify
the hydrophilicity of a polymeric material (the material used in
all referenced experiments was a polymeric acrylic polymer ("PLM")
however that material is used as an example and is not limitation
of the present invention scope). The change in hydrophilicity may
be used to: [0029] form an optical lens having predetermined
refractive properties; [0030] create hydrophilic areas in an
otherwise hydrophobic material; or [0031] create hydrophilic areas
in an otherwise hydrophilic material.
[0032] The present invention is particularly, but not exclusively,
useful as describing the procedure to create a very thin,
multi-layered, micro-structured customized intraocular lens inside
a PLM. This technique could be used, but is not limited to
modifications of an existing lens which is currently implanted
within a human eye. The modifications can adjust diopter and/or add
additional properties like toricity and asphericity. The instant
invention is capable of creating new lenses which are thinner than
existing products and can be injected through a small incision. In
particular, a system and method for the shaping of a refractive
index within lenses based on the modification of the hydrophilicity
of the material is disclosed.
[0033] The present invention describes a laser system and a method
for modifying the hydrophilicity for a predetermined internal
region of PLM which may be used as an optical lens. The present
invention can be utilized to modify the optical properties of an
optical lens by adding (or reducing) its optical power, or altering
its asphericity, multifocalilty, toricity and other optical
properties. Typical application for this invention may include
correcting the post-operational residual refractive error of an
intraocular lens which has already been implanted in a patient's
eye.
[0034] In spite of the best effort by surgeons, residual refractive
error is inevitable in many cases due to deviations in lens power
selection, patient's history of past eye surgeries such as LASIK
procedure, surgery induced astigmatism, and progressive change in
vision of a patient. Currently, surgeons use LASIK, a procedure to
reshape a patient's cornea by destroying a portion of the cornea by
laser beams, to correct residual refractive error after cataract
surgery. Alternatively, patients may need to wear eye glasses to
correct post-operational refractive errors. The present invention
promotes a scenario in which these optical non-idealities may be
corrected in situ after the cataract surgery is completed.
[0035] Within the scope of the present invention a customized
intraocular lens may be manufactured using either all optical
processes or a combination of the traditional manufacturing in
combination with optical processes to reduce the lens thickness and
the needed incision size. The optical process is typically employed
by using a femtosecond laser with pulse energies of 0.17 to 500
nanjoules and a megahertz repetition rate of 1 to 100.
[0036] The focus spot of the laser beam is moved inside the lens
material to create a pattern of changes in the material, creating a
three dimensional lens. Different patterns will provide different
lens properties, for example a toric or aspheric lenses.
BRIEF DESCRIPTION OF THE DRAWINGS
[0037] For a fuller understanding of the advantages provided by the
invention, reference should be made to the following detailed
description together with the accompanying drawings wherein:
[0038] FIG. 1 illustrates a prior art methodology of internal
plastic modification as taught by United States Patent Application
Publication US2002/0117624A;
[0039] FIG. 2 illustrates a prior art methodology of internal
plastic modification as taught by United States Patent Application
Publication US2002/0117624A;
[0040] FIG. 3 illustrates a prior art system for lens formation as
taught by United States Patent Application Publication
US2008/0001320A1;
[0041] FIG. 4 illustrates a prior art lens form as taught by United
States Patent Application Publication US2008/0001320A1;
[0042] FIG. 5 illustrates an exemplary system block diagram
depicting a preferred exemplary system embodiment of the present
invention;
[0043] FIG. 6 illustrates an exemplary system block diagram of a
preferred exemplary system embodiment of the present invention
depicting a typical invention application setup context;
[0044] FIG. 7 illustrates a detail system block diagram
illustrating system components that may be used to implement some
preferred invention embodiments;
[0045] FIG. 8 illustrates a comparison of prior art lens
configurations using a convex lens for optical convergence and
present invention a lens configurations using a concave lens for
optical convergence;
[0046] FIG. 9 illustrates the use of the present invention to
modify the hydrophilicity of a PLM in single and multiple layer
configurations;
[0047] FIG. 10 illustrates an exemplary convex/biconvex lens
structure as taught by the present invention;
[0048] FIG. 11 illustrates an exemplary concave/biconcave lens
structure as taught by the present invention;
[0049] FIG. 12 illustrates exemplary phase wrapping lens structures
that may be formed using the teachings of the present
invention;
[0050] FIG. 13 illustrates the refractive index patterns associated
with exemplary phase wrapping lens structures that may be formed
using the teachings of the present invention;
[0051] FIG. 14 illustrates an exemplary PLM hydrophilicity
alteration method flowchart used in some preferred embodiments of
the present invention;
[0052] FIG. 15 illustrates an exemplary lens shaping/formation
method flowchart used in some preferred embodiments of the present
invention;
[0053] FIG. 16 illustrates an exemplary lens calculation method
flowchart used in some preferred embodiments of the present
invention;
[0054] FIG. 17 illustrates an exemplary experimental sample PLM
structure as taught by the present invention;
[0055] FIG. 18 illustrates a graph of experimentally measured PLM
water absorption measurements;
[0056] FIG. 19 illustrates an exemplary diffraction grid pattern as
taught by the present invention;
[0057] FIG. 20 illustrates an exemplary experimental refractive
index measurement setup as taught by the present invention;
[0058] FIG. 21 illustrates an exemplary experimental refractive
index pattern as taught by the present invention;
[0059] FIG. 22 illustrates an exemplary experimentally measured
diffraction grating power measurement over time as taught by the
present invention;
[0060] FIG. 23 illustrates an exemplary experimentally measured
diffraction grating 0 order power measurement as taught by the
present invention;
[0061] FIG. 24 illustrates an exemplary experimentally measured
water de-absorption curve as taught by the present invention;
[0062] FIG. 25 illustrates an exemplary experimentally constructed
convex phase wrapping DIC and theoretical side view as taught by
the present invention;
[0063] FIG. 26 illustrates a NIMO diopter reading of an exemplary
experimentally constructed convex phase wrapping DIC and
theoretical side view as taught by the present invention;
[0064] FIG. 27 illustrates an exemplary experimentally constructed
concave phase wrapping DIC and theoretical side view as taught by
the present invention;
[0065] FIG. 28 illustrates a NIMO diopter reading of an exemplary
experimentally constructed concave phase wrapping DIC and
theoretical side view as taught by the present invention;
[0066] FIG. 29 illustrates an exemplary experimental 3 mm convex
phase wrapping lens top view as constructed;
[0067] FIG. 30 illustrates an exemplary experimentally measured
diopter reading as it relates to water absorption comparison as
taught by the present invention, depicting the difference between
air drying and water hydration on measured lens diopter
readings;
[0068] FIG. 31 illustrates an exemplary experimentally measured
water absorption curve for water as taught by the present invention
and its variation based on time and ambient temperature;
[0069] FIG. 32 illustrates an exemplary experimentally measured
water absorption diopter dependency graph as taught by the present
invention;
[0070] FIG. 33 illustrates an exemplary method flowchart depicting
a generalized in-vivo lens shaping method as implemented by a
preferred invention embodiment;
[0071] FIG. 34 illustrates an exemplary method flowchart depicting
preparation details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0072] FIG. 35 illustrates an exemplary method flowchart depicting
lens data creation details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0073] FIG. 36 illustrates an exemplary method flowchart depicting
patient interface details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0074] FIG. 37 illustrates an exemplary method flowchart depicting
start initialization details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0075] FIG. 38 illustrates an exemplary method flowchart depicting
diagnostics details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0076] FIG. 39 illustrates an exemplary method flowchart depicting
lens shaping details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0077] FIG. 40 illustrates an exemplary method flowchart depicting
verification details of an in-vivo lens shaping method as
implemented by a preferred invention embodiment;
[0078] FIG. 41 illustrates an exemplary method flowchart depicting
a generalized manufacturing custom lens shaping method as
implemented by a preferred invention embodiment;
[0079] FIG. 42 illustrates an exemplary method flowchart depicting
preparation details of a manufacturing custom lens shaping method
as implemented by a preferred invention embodiment;
[0080] FIG. 43 illustrates an exemplary method flowchart depicting
lens data creation details of a manufacturing custom lens shaping
method as implemented by a preferred invention embodiment;
[0081] FIG. 44 illustrates an exemplary method flowchart depicting
positioning details of a manufacturing custom lens shaping method
as implemented by a preferred invention embodiment;
[0082] FIG. 45 illustrates an exemplary method flowchart depicting
start initialization details of a manufacturing custom lens shaping
method as implemented by a preferred invention embodiment;
[0083] FIG. 46 illustrates an exemplary method flowchart depicting
diagnostics details of a manufacturing custom lens shaping method
as implemented by a preferred invention embodiment;
[0084] FIG. 47 illustrates an exemplary method flowchart depicting
lens shaping details of a manufacturing custom lens shaping method
as implemented by a preferred invention embodiment;
[0085] FIG. 48 illustrates an exemplary method flowchart depicting
verification/shipping details of a manufacturing custom lens
shaping method as implemented by a preferred invention
embodiment.
DESCRIPTION OF THE PRESENTLY PREFERRED EXEMPLARY EMBODIMENTS
[0086] While this invention is susceptible of embodiment in many
different forms, there is shown in the drawings and will herein be
described in detailed preferred embodiment of the invention with
the understanding that the present disclosure is to be considered
as an exemplification of the principles of the invention and is not
intended to limit the broad aspect of the invention to the
embodiment illustrated.
[0087] The numerous innovative teachings of the present application
will be described with particular reference to the presently
preferred embodiment, wherein these innovative teachings are
advantageously applied to the particular problems of a
HYDROPHILICITY ALTERATION SYSTEM AND METHOD. However, it should be
understood that this embodiment is only one example of the many
advantageous uses of the innovative teachings herein. In general,
statements made in the specification of the present application do
not necessarily limit any of the various claimed inventions.
Moreover, some statements may apply to some inventive features but
not to others.
Hydrophilicity Not Limitive
[0088] Within the context of the present invention the term
"hydrophilicity" will be defined as the characteristic of a
material to "have a strong affinity for water or tend to dissolve
in, mix with, or be wetted by water."
Material (PLM) Not Limitive
[0089] The present invention may incorporate a wide range of
materials, including the PLM but not limited to the PLM, within the
scope of anticipated embodiments, many of which may be application
specific. PLM may in many preferred embodiments incorporate the use
of an ultraviolet (UV) (generally 300-400 nm wavelength) absorbing
material to augment the absorption of pulsed laser energy by the
PLM and thus affect a change in hydrophilicity of the PLM. PLM as
used herein should not be constrained as limiting its use to
materials that form optical lenses. Specifically, the term
"polymeric material (PM)" may be used herein to denote applications
of the invention system/method/product that are not necessarily
limited to the production of optical lenses. Thus, "PM" may cover a
broader application of the invention concepts than "PLM", although
the materials may be identical. Therefore, the term "polymeric lens
material (PLM)", "polymeric material (PM)" and their equivalents
should be given the broadest possible meaning within this
context.
UV Absorbers Not Limitive
[0090] The PLM may incorporate a number of chemicals which may
enhance the UV absorption of the PLM and thus enhance the change in
the PLM's hydrophilicity when irradiated with pulsed laser
radiation. The present invention makes no limitation on the types
and quantities of chemicals used to affect this behavior, and the
recitation of these chemicals within this document is only
exemplary of those anticipated.
Laser Radiation Not Limitive
[0091] The present invention may incorporate a wide variety of
laser radiation to affect changes in hydrophilicity within the PLM
described herein to form a lens. Therefore, the term "laser
radiation" and its equivalents should be given the broadest
possible meaning within this context, and not limited to near
infrared light laser radiation.
Laser Source Not Limitive
[0092] The present invention may incorporate a wide variety of
laser radiation sources provide the required pulsed laser radiation
used within the disclosed invention. Within this context, the term
"laser source" may also incorporate an Acousto-Optic Modulator
(AOM) (also called a Bragg cell) that uses the acousto-optic effect
to diffract and shift the frequency of laser light generated using
sound waves (usually at radio-frequency). Within this context, the
"laser source" may be globally defined as comprising a laser
radiation source and optionally an AOM, whether or not the AOM is
physically incorporated into the laser radiation source hardware.
Therefore, the term "laser source" and its equivalents should be
given the broadest possible meaning within this context.
Acousto-Optic Modulator (AOM) Not Limitive
[0093] Various invention embodiments may make use of an
Acousto-Optic Modulator (AOM) to act as a switch to enable/disable
or moderate the quantity of laser radiation pulse stream as
directed to the laser scanner within the context of the invention.
Within this context the AOM may incorporate "greyscale" modulation
wherein the switching function serves to switch a portion of the
laser radiation pulse train to the laser scanner and therefore
permit reductions in effective laser power as applied to the
targeted PLM to which the hydrophilicity is to be modified. Thus,
the utilization of "greyscale AOM" components to modulate laser
radiation intensity is specifically anticipated within the scope of
the invention.
[0094] The AOM as depicted in the present invention is used as a
shutter and as variable attenuator and as such could therefore be
replaced with another equivalent component which simulates the same
functionality as described above.
Laser Scanner Not Limitive
[0095] The use of a laser scanner within the preferred invention
embodiments described herein may incorporate many different
varieties of scanner, including but not limited to flying spot
scanners (generally vector-based modes) and raster scanners
(generally raster-based modes). The scanner is used to distribute
the laser pulse to the correct location within the objectives field
size. The present invention makes no limitation on the type of
laser scanner that may be used in this context.
Microscope Objective Not Limitive
[0096] References herein to a "microscope objective" may
equivalently utilize a "microscope objective or other focusing
device" to achieve these functions. Thus, the term "microscope
objective" should be given its broadest possible interpretation
within this application context.
Patient Not Limitive
[0097] The present invention may be applied to situations where a
lens placed in a living creature is modified in situ to
correct/modify the refractive properties of the lens without
removal from the eye of the creature. Within this context, the term
"patient" shall be broadly construed and should not be limited to
application only on human beings.
Lens Form Not Limitive
[0098] The present invention may incorporate a wide variety of
lenses formed to affect optical light bending and thus the
construction of an overall lens formation. While exemplary
embodiments of the present invention are described herein as being
used to construct convex, biconvex, concave, biconcave, and plano
lens structures, these structures are only exemplary of a plethora
of lens forms that may be constructed with the present invention.
Therefore, the term "lens formation" and its equivalents should be
given the broadest possible meaning within this context.
Two-Dimensional not Limitive
[0099] The present invention may incorporate the use of
two-dimensional pattern structures within the PLM to form
diffraction gratings and other thin planar structures which while
technically three-dimensional, will be termed herein as
two-dimensional. While no modification of the PLM hydrophilicity
can occur strictly in a zero-thickness plane, the term
two-dimensional will refer to the creation of structures which
occur within the PLM that do not require Z-axis focus repositioning
across the X-Y plane perpendicular to the optical axis. Thus, a
two-dimensional modification of the PLM refractive index could
occur along a non-planar boundary that comprises a singular Z-axis
focal distance for the laser pulses. Therefore, the term
"two-dimensional" and its equivalents should be given the broadest
possible meaning within this context.
Three-Dimensional Not Limitive
[0100] The present invention may incorporate the use of
three-dimensional pattern structures within the PLM to form complex
optical structures. These three-dimensional pattern structures and
their associated volumes may comprise multiple layers having
interstitial PLM having a hydrophilicity that has not been modified
by irradiation with laser pulses. Thus, a three-dimensional
structure may incorporate non-modified areas having unmodified or
slightly modified layer, or multiple layers comprising differing
levels of hydrophilicity and resulting refractive index changes.
Therefore, the term "three-dimensional" and its equivalents should
be given the broadest possible meaning within this context.
Intraocular Lens Not Limitive
[0101] The present invention may be advantageously applied to the
construction of dynamically adjustable optical lenses incorporating
a wide range of materials. The mechanisms of incorporation of a
wide variety of materials within the optical lens are not limited
by the present invention. Therefore, the term "intraocular lens"
and "optical lens (which would include contact lenses)" and its
equivalent construction embodiments should be given the broadest
possible meaning within this context.
General System Description
[0102] The present invention may be generally described as
utilizing a laser system which consists of a femtosecond laser
source, an AOM, a scanner, and an objective which delivers the
laser pulses into the predetermined region. The laser source
preferably has a pulse duration of approximately 350 fs or shorter,
a wavelength in the range of 690 to 1000 nm, and a repetition rate
of between approximately 0.1 to 100 MHz. The pulse energy is
typically in the range of 0.17 to 500 nanojoules. Those who are
skilled in the art understand that these laser parameters can be
adjusted and rebalanced to be outside above-specified range but
still be able to achieve the same level of energy delivered to the
targeted regions of the lens material. For example, a tunable laser
unit, such as Ti:Saphphire oscillator (Mai Tai By Newport, Irvine,
Calif.) can provide a variable wavelength in the range of
approximately 690-1040 nm, a pulse width of as low as 70 fs, and a
source power up to 2.9 W.
Generalized Hydrophilicity Modification System (0500)
[0103] A preferred exemplary system embodiment of the present
invention is generally illustrated in FIG. 5 (0500), wherein a
material (0501) is irradiated (0515) to produce a change in
hydrophilicity within a selected region (0502) within the PLM
(0501). This system (0500) generally incorporates a laser source
(0511) that is configured to generate pulsed laser radiation which
may be controlled/moderated/modulated/switched by an acousto-optic
modulator (AOM) (0512) to produce a predetermined laser pulse train
having specified energy and pulse timing characteristics. In some
invention embodiments the laser source (0511) and AOM (0512) may be
integrated into a single laser source module. The pulsed laser
radiation generated by the laser source (0511)/AOM (0512) is then
transmitted to a laser scanner (0513) that is configured to
distribute the laser pulses in an X-Y plane across an input area of
a microscope objective (0514). The microscope objective (0514)
incorporates a numerical aperture configured to accept the
distributed pulsed laser radiation and produce a focused laser
radiation output (0515). This focuses laser radiation output (0515)
is then transmitted by the microscope objective (0514) to a
polymeric lens material (PLM) (0501) region (0502) in which the
hydrophilicity of the PLM (0501) is to be changed. The position of
the hydrophilic-modified PLM region (0502) may be defined by the
laser scanner (0513) as well as a sample staging/positioning system
(0516) that mechanically positions the PLM (0501) to allow the
focused laser pulses (0515) to be properly localized within the
desired interior region (0502) of the PLM (0501).
[0104] This system may optimally operate under control of a
computer control system (0520) incorporating a computer (0521)
executing software read from a computer readable medium (0522) and
providing a graphical user interface (GUI) (0523) from which an
operator (0524) may direct the overall operation of the
hydrophilicity change (0502) within the PLM (0501).
System/Method Application Context Overview (0600)
[0105] A typical application context for the present invention is
generally illustrated in FIG. 6 (0600), wherein the present
invention is embodied in a hydrophilicity alteration system (0610)
used to configure patient lenses. This hydrophilicity alteration
system (0610) typically comprises a laser source (0611) that
generates a pulsed laser output that is then distributed in an X-Y
plane using a laser scanner (0613) and then focused using a
microscope objective (0614) (or other focusing apparatus). This
distributed and focused pulsed laser radiation (0615) is
transmitted within a lens structure (0601) having some portion of
which that is constructed of material (PLM) (0602). This PLM (0602)
is irradiated in a two or three-dimensional pattern (0603) within
the PLM structure (0602) to modify the hydrophilicity. Any
modifications in hydrophilicity will create some change in the
refractive index of the internal region of the PLM (0603). This
change in refractive index generated by the focused laser pulses
(0614) causes the two or three-dimensional pattern (0603) to form
an optical lens function within the overall lens structure
(0601).
[0106] In conjunction with this general system/method
configuration, the lens structure (0601) may be incorporated (0604)
within a human eye (0605) and the PLM (0602) modified in situ after
the lens structure (0601) has been surgically implanted within the
eye of a patient as generally illustrated in the diagram.
[0107] The described hydrophilicity alteration system (0610) is
typically operated under control of a computer system (0621)
executing instructions from a computer readable medium (0622). This
computerized control (0621) optimally incorporates a graphical user
interface (0623) permitting the system operator (0624) to interface
with the overall system and direct its operation. With respect to
the above-mentioned in situ lens formation application, the control
software (0622) may incorporate software implementing methods to
perform an automated patient eye examination to determine the
non-idealities in the patient's vision (0625), from which a map of
optical corrections (0626) necessary to improve the patient's
vision is generated, followed by automated laser pulse/position
control procedures to change in situ the refractive index of PLM
within the patient lens to fully correct the patient vision
(0627).
System/Method Application Context Detail (0700)
[0108] A more detailed system configuration of a preferred
invention application context is provided in FIG. 7 (0700), wherein
a computer system (0720) operating under control of software read
from a computer readable media (0721, 0722) is used to control and
supervise the overall lens fabrication process. Within this
application context, the following components generally comprise
the system: [0109] The laser source (0701) with a wavelength
suitable to treat the desired material and an energy-per-pulse
sufficient to change the refractive index of the target area
provided by the used objective (0710). [0110] The Dispersion
Compensator (0702) is used to pre-compensation the beam to allow a
pulse width around 100 fs. Without the feature the pulse width at
the target would be larger because the pulse width gets longer when
passing through an optical media like a lens. With a longer pulse
with more heat would occur on the treatment area, making the
process a little more imprecise and the treatment time a little
longer. This feature therefore is optional but part of the RIS
optimization. [0111] The Beam Shaping 1 (0703) unit can be used to
modify the laser beam diameter to fit the AOM specifications. This
also allows the exchange of the laser source without additional
modifications after the beam shaping 1 unit. [0112] The AOM (0704)
is used to modulate the number of pulses and the energy per pulse
which will be directed to the treatment area. Depending on the
received signal (normally 0 to 5V) the energy will be distributed
to the 0 or the 1.sup.st order of the AOM. Those orders are two
different beams, with an angle between them, coming out from the
AOM. The 1.sup.st order beam is normally the one going to the
target area and the 0 order beam is stopped directly after the AOM.
The receiving signal from the AOM driver is maximum (eg 5V) the
maximum energy per pulse is in the 1.sup.st order beam, when the
driver signal is at the minimum the 1.sup.st order beam will have
0% energy and everything will be delivered to the 0 order. [0113]
Beam Shaping 2, after the beam has passed through the AOM
additional beam shaping is required to fit the system. For example
the beam diameter has to be enlarged to fit the used objective
(0710), to allow the use of the numerical aperture of the
objective. [0114] A Diagnostics (0705) system is used to measure
the wavelength, energy per pulse and the pulse width of the laser
beam. This feature in included to allow the safe and repeatable use
of the system. If one of the variables is not performing as planned
the system will shut down and [0115] Laser Microscope Coupling
(Mirror Arm) (0706) is used to redirect the laser beam into the
laser microscope head. Depending on the system setup and laser
orientation it can contain between one and multiple mirrors to
redirect the laser beam to the needed position. [0116] The Camera
System (0707) is used to position the sample towards the microscope
objective. It also is used to find the correct Z location,
depending on the materials curvature. Additionally the camera can
be used for tracking purposes. [0117] The Scanner (0708) is used to
distribute the laser spot on the XY plane. Different scanners can
be used for this purpose. Depending on the scanner type the
untreated area would still be covered but with no laser energy per
pulse or only the treated areas would be covered. For this purpose
the software controlling will also control the AOM because the
scanner software will position the spot and the AOM will contribute
the energy per pulse for that spot. [0118] The Z Module (0709) can
be used to allow an extra focusing element in the system, this for
example can be used for tracking purposes for a plane in a
different Z location than the shaping plane. It also could be used
to change the Z location during the shaping process. [0119] The
Objective (0710) focuses the beam on the sample and determines the
spot size. With a larger spot size a larger energy per pulse is
required it therefore has to be fitted to the laser source and the
required precision of the process. Additionally it provides the
field size of the shaping process, if the field size of the
objective is smaller than the required lens, this requires
additional hardware for the lens shaping. [0120] The Objective and
Sample Interface (0711) is depending on the application. For the
lens manufacturing the space between the sample and the objective
is filled with water to reduce scattering and allow an additional
cooling element. For other applications different contact method
with other mediums like eye gel could be used. [0121] The Sample
(0712) can surprise of different optical mediums and could for
example be a hydrophobic polymer which is placed in front of the
objective. Depending on the application that sample will be
directly after the Objective and Sample interface or deeper inside
an additional medium combination like an eyeball. [0122] The
Positioning System (0713) can be used to position the blocks
comprising of the objective field sizes towards each other to allow
the shaping of a larger structure. It can also be used to move the
sample in the Z direction.
[0123] One skilled in the art will recognize that a particular
invention embodiment may include any combination of the above
components and may in some circumstances omit one or more of the
above components in the overall system implementation.
Comparison of Prior Art/Present Invention (0800)
[0124] A comparison of the prior art and present invention
methodologies for achieving optical convergence within a lens
structure is generally illustrated in FIG. 8 (0800). The prior art
as generally depicted in FIG. 8 (0800, 0810) makes use of convex
lens formation methodologies to generate optical convergence as
illustrated in this example. It is essential to note that the prior
art makes no change in hydrophilicity of the lens material but
simply changes the refractive index of the material. By contrast,
the present invention using changes in PLM hydrophilicity as
generally illustrated in FIG. 8 (0800, 0820) to generate optical
convergence. While both techniques may make use of multiple lens
structures, the present invention relies on negative diopter
material modification (0821) to create these lens formations (all
increases in hydrophilicity reduce the refractive index of the
material while all the prior art makes changes in the material that
create positive diopter material modification (0811).
Exemplary Application Context Overview (0900)
[0125] As generally depicted in FIG. 9 (0900), the present
invention uses a femtosecond pulse laser (0911) to enable a
hydrophilicity change (alteration) (0912) inside a PLM (0913). As
generally depicted in FIG. 9 (0900), a three dimensional layer
(0922) of hydrophilicity change (alteration) can be shaped in a PLM
(0921) using a XYZ stage system. The depth of the layer is
predetermined in the software. The layer could be positioned at the
surface (0923) or intermediate layers (0924, 0925).
[0126] The present invention also anticipates a system configured
to form optical lenses from a PLM, a method by which lenses may be
formed using PLM, and the lenses formed by the method using the
PLM. Any of these invention embodiments may be applied to
situations in which a lens implanted in a human (or other biologic
eye) may be modified and/or corrected in situ without the need for
removal of the lens from the patient.
[0127] The present invention can also be used to create hydrophilic
channels within a PLM. Such areas can be used to facilitate the
passage of other chemical substances into our out of such
materials.
Exemplary Lens Formation Structures (1000)-(1300)
[0128] While the present invention may in many contexts be applied
to the formation of a wide variety of lens structures, several
forms are preferred. These include but are not limited to convex
(1001) and biconvex (1002) structures as depicted in the profiles
of FIG. 10 (1000); concave (1101) and biconcave (1102) structures
as depicted in the profiles of FIG. 11 (1100); and phase wrapping
convex (1201) and phase wrapping concave (1202) structures as
depicted in the profiles of FIG. 12 (1200). One skilled in the art
will recognize that these lens structures are only exemplary of a
wide variety of lenses that may be formed using the teachings of
the present invention. Additionally, the layering of PLM modified
structures as depicted in FIG. 9 (0900, 0921) may permit the
layering of a plurality of lens structures within a single PLM.
Phase Wrapping Lens (1200,1300)
[0129] The present invention may be used to form phase wrapping
lens as generally depicted in the phase wrapping convex (1201) and
phase wrapping concave (1202) structures depicted in FIG. 12 (1200)
and the associated exemplary refractive indexes depicted in FIG. 13
(1300). Phase wrapping lenses use the same theoretical idea as the
Fresnel lens (1204). The difference in quality can be summarized in
three different factors: [0130] the original lens curvature is
preserved for the Phase Wrapping lens; [0131] the laser shaping
technique allows the preservation of the 90 degree angle at each
zone for the Phase Wrapping lens; and [0132] the micrometer
precision to which the Phase Wrapping lens may be shaped. In
contrast, the limitations for the Fresnel lens (1205) are generally
derived from the manufacturing process in which it is created. The
main manufacturing difference for a Phase Wrapping Lens and a
Fresnel lens are shown in image 1206.
Refractive Index Gradient Lens (1300)
[0133] The present invention may be used to form a refractive index
gradient lens as generally depicted in FIG. 13 (1300). The
information of the lens curvature is in this concept is stored in a
single layer. The grayscale values are used to represent the energy
per pulse. Therefore 256 variations of the power between 0% and
100% are possible and allow the precise shaping of a single layered
lens. The top view of a refractive index lens (1301) shows the
different zones of an original convex phase wrapping lens. Each
original discussed lens type data information can be compressed to
one single layer. The side view of the refractive index gradient
lens (1302) shows the energy distribution at each spot for one
horizontal slice through the center of the lens.
[0134] The modulation of the pulse energy can be accomplished using
the AOM or an automatic variable attenuator.
PLM Method (1400)
[0135] The present invention method anticipates a wide variety of
variations in the basic theme of implementation, but can be
generalized as depicted in FIG. 14 (1400) as a lens formation
method using hydrophilicity alteration comprising: [0136] (1)
generating a pulsed laser radiation output from a laser source
(1401); [0137] (2) distributing the pulsed laser radiation output
across an input area of a microscope objective (1402); [0138] (3)
accepting the distributed pulsed radiation into a numerical
aperture within the microscope objective to produce a focused laser
radiation output (1403); and [0139] (4) transmitting the focused
laser radiation output into a PLM to modify the hydrophilicity
within the PLM (1404). This general method may be modified heavily
depending on a number of factors, with rearrangement and/or
addition/deletion of steps anticipated by the scope of the present
invention. Integration of this and other preferred exemplary
embodiment methods in conjunction with a variety of preferred
exemplary embodiment systems described herein is anticipated by the
overall scope of the present invention. This and other methods
described herein are optimally executed under control of a computer
system reading instructions from a computer readable media as
described elsewhere herein.
[0140] As generally depicted in FIG. 9 (0900, 0912), this region of
hydrophilic alteration may form arbitrary optical lens structures
as generally depicted in FIG. 10 (1000)-FIG. 13 (1300) having
multiple optical inner layers of hydrophilic alteration as
generally depicted in FIG. 9 (0900, 0921).
Lens Shaping/Formation Method (1500)
[0141] The present invention also teaches a lens shaping/formation
method wherein a lens of arbitrary complexity may be formed within
PLM. The lens shaping consists of different parts. First the lens
diopter and curvature have to be calculated depending on the
selected material. The laser wavelength afterward is also adjusted
towards this material. The AOM functions as the shutter and also as
a variable power attenuator in the setup, allowing (in combination
with the scanner) the lens structure to be precisely shaped inside
the polymer. The AOM is controlled by the input images of the
calculated lens information, providing the laser power information
for each area (micrometer) of irradiated area. The scanner
afterward distributes the power to the correct location and the
microscope objective focuses the pulsed laser beam to the desired
focus spot inside the polymer. The PLM sample is kept in a sample
holder after the microscope objective and is optionally positioned
on a stage system (mechanized X/Y/Z positioning system) to allow
the shaping of a larger lens structure. The stage system could also
be replaced with a mirrored laser arm which ends with the
microscope objective. The mirrored arm in this case would not only
replace the stage system but the whole camera and scanner
board.
[0142] The present invention method may incorporate an embodiment
of this lens shaping/formation method as depicted in FIG. 15 (1500)
comprising: [0143] (1) executing lens calculations to determine the
form and structure of lens to create (1501); [0144] (2) selecting
the laser wavelength suitable for the desired hydrophilicity change
in the PLM (1502); [0145] (3) shuttering and/or power regulating a
laser using an AOM or equivalent modulator to generate laser pulses
(1503); [0146] (4) scanning the laser pulses across a microscope
objective (1504); [0147] (5) forming a laser spot size and
precisely positioning the focused laser within a PLM using a
microscope objective (1505); [0148] (6) retaining/holding the PLM
for hydrophilicity alteration by the laser pulse stream (1506); and
[0149] (7) optionally positioning the target PLM sample using X/Y/Z
positioning system (1507). This general method may be modified
heavily depending on a number of factors, with rearrangement and/or
addition/deletion of steps anticipated by the scope of the present
invention. Integration of this and other preferred exemplary
embodiment methods in conjunction with a variety of preferred
exemplary embodiment systems described herein is anticipated by the
overall scope of the present invention.
[0150] This method may be applied to one or more layers within the
PLM to achieve formed lens structures of arbitrary complexity. The
lens calculations associated with this procedure as identified in
step (1) are detailed in FIG. 16 (1600) and described below.
Lens Calculation Method (1600)
[0151] The present invention also teaches a lens calculation method
wherein lens parameters are used to determine the internal PLM lens
structure that is customized for a particular patient and their
unique optical requirements. This method generally involves the
following steps: [0152] Calculating the curvature of the lens to be
formed; [0153] Determining the required lens depth; [0154]
Calculating the number of zones which must be processed via the
laser; [0155] Determining the zone radius for each zone to be
processed; [0156] Create phase wrapping lens data files for the
laser; and [0157] Loading the data files into the RIS mapping
system. These steps will now be discussed in more detail.
[0158] Before the lens parameters for a custom intraocular lens
(IOL) can be calculated the patient needs to be examined, the
different existing aberrations can be measured and the needed
diopter (Dpt) changes can be evaluated. The material (n) for the
shaping process has to be known to calculate the lens curvature
(C).
C = D .times. p .times. t ( n ' - n ) ( 1 ) ##EQU00001##
Where n is the refractive index of the original IOL material and n'
is the refractive index after the RIS shaping, and therefore the
refractive index of the new lens.
C = 1 r ( 2 ) ##EQU00002##
[0159] The curvature is related to lens radius (r) and the radius
can be calculated with the lens diameter 2w.sub.Lens and the lens
depth h.sub.Lens.
r = h L .times. e .times. n .times. s 2 + w L .times. e .times. n
.times. s 2 2 .times. h L .times. e .times. n .times. s ( 3 )
##EQU00003##
[0160] Afterward the Phase Wrapping Lens Information is calculated
for the given information and the output images are created. All
required information for the Phase Wrapping Lens already exists in
the information of the original lens and its curvature. The Phase
Wrapping depth of the lens is determined by the refractive index
change amount. Afterward the radius of each zone and for the
curvature information of each zone can be easily calculated.
Depending on the shaping technique the lens diopter can be larger
than the objective field size, in this case a stage system (as
described above) is used to align the different areas for the lens
shaping. To allow this technique the input images are chopped into
their images sizes to represent the block system.
[0161] The lens calculation method described above and generally
depicted in FIG. 15 (1500, 1501) may be embodied in many forms, but
several preferred embodiments of the present invention method may
implement this method as depicted in FIG. 16 (1600) using the
following steps: [0162] (1) measuring or determining required lens
properties for desired optical performance (1601); [0163] (2)
selecting a lens material appropriate for lens fabrication (1602);
[0164] (3) calculating the desired lens curvature (1603); [0165]
(4) calculating phase wrapping lens information necessary to form
the lens (1604); [0166] (5) creating output images that correspond
to the desired phase wrapping lens characteristics (1605); [0167]
(6) determining if the lens treatment area is larger than the
objective field size, and if not, proceeding to step (8) (1606);
[0168] (7) chopping the output images into segments that fit within
the field size (1607); [0169] (8) determining if the patient (or
lens formation) requires additional lens properties, and if so,
proceeding to step (1) (1608); and [0170] (9) terminating the lens
calculation method (1609). This general method may be modified
heavily depending on a number of factors, with rearrangement and/or
addition/deletion of steps anticipated by the scope of the present
invention. Integration of this and other preferred exemplary
embodiment methods in conjunction with a variety of preferred
exemplary embodiment systems described herein is anticipated by the
overall scope of the present invention.
[0171] This method may be applied to the formation of lenses that
are retained/held by a staging apparatus, or in some circumstances
the lens shaping/formation process may be performed in situ within
the eye of a patient. In this situation, the lens PLM may be
surgically inserted into the patient while the PLM is in a
generally unmodified (or previously modified) state and then
"dialed-in" to provide optimal vision for the patient.
Application #1--Optical Lens (1700)-(1800)
[0172] The following experimental application example discusses an
internal hydrophilicity change for a polymeric acrylic polymer
suitable for making optical lenses.
Step 1--Preparation of Testing Optical Material
[0173] A small sheet of crosslinked polymeric copolymers may be
constructed by free radical polymerization of [0174] (1) 140 grams
of mixture of butylacrylate,
ethylmethacrylate,N-benzyl-N-isopropylacrylamide, and ethylene
glycol dimethacrylate; [0175] (2) 11.4 grams of
2-[3-(2H-benzotriazol-2-yl)-4-hydroxyphenyl]ethyl methacrylate; and
[0176] (3) a yellow dye less than 0.5%. under a curing cycle
starting at 65.degree. C. up to 140.degree. C. for a total time of
approximately 14 hours in a glass mold sealed with silicone tube.
Slightly yellow transparent sheet, about 2 mm thick, obtained this
way can be cut into round buttons which can be further lathe
machined into intraocular lenses. Alternatively, small trips can
also be cut out from the sheet or from the buttons for laser
treatment. The refractive index of the yellow sheet or button
prepared this way is approximately 1.499.
Step 2--Pre-Soaking
[0177] A small strip (1.91 mm.times.1.33 mm.times.14.35 mm) of an
optically transparent lens material prepared above weighs 38.2 mg.
This strip of lens material is soaked in water until no more weight
increase, an indication for reaching saturation at room
temperature. The saturated strip, after water droplets on its
surface are wiped with dry paper tissues, weighs 38.3 mg,
indicating water absorption is approximately 0.3%.
Step 3--Laser Treatments
[0178] The water saturated strip was then exposed to laser pulses
from a femtosecond laser source (pulse width: 200 fs, repetition
rate: 50 MHz, energy per pulse: 5.4 nJ, wavelength: 780 nm). Only a
predetermined region (2 mm.times.2 mm.times.165 .mu.m, 165 .mu.m is
the thickness of the treated region) as generally illustrated in
FIG. 17 (1700) of the strip was treated. After the treatment the
strip was allowed to be saturated with water and then weighed
again. The strip was 38.9 mg with an increase of 0.2 mg which
represents approximately 30% water absorption by the treated region
(0.2 mg 2.times.1.9.times.0.165=0.318=32%). After the first region
was treated, a second region of same dimension was treated,
approximately another 0.2 mg increase was observed. This way, a
total of 3 regions were treated, final strip weights 38.9 mg. The
weight gains after each laser treatment are summarized in the graph
depicted in FIG. 18 (1800).
Application #2--Diffraction Gratings (1900)-(2400)
[0179] The following experimental application example discusses the
use of the present invention as applied to Diffraction gratings
efficiency dependency on water absorption.
Step 1
[0180] A diffraction grating was shaped inside the acrylic
polymeric material as generally depicted in FIG. 19 (1900). The
grid size is 3 mm with an X spacing of 18 um in this example.
Step 2
[0181] The sample is then water saturated.
Step 3
[0182] The efficiency of the refractive index grating was measured
(2103) using the setup depicted in FIG. 20 (2000) for different
scan speeds. A red (640 nm) laser was placed in front of the
sample. The sample is mounted on a set of XY stages to allow
positioning of the grating in regards of the laser. At some
distance a screen (2101-2103) was positioned and the power of the
different orders of the gratings (as depicted in FIG. 21 (2100)) is
recorded for different times as depicted in FIG. 22 (2200). The
power in the 1.sup.st to the 10.sup.th order decreases with the
water desaturation as illustrated in FIG. 22 (2200), while the
energy is going into the zero (0) order as generally depicted in
FIG. 23 (2300).
[0183] This can be compared with the water de-absorption curve of
the acrylic polymeric material as depicted in FIG. 24 (2400) which
shows the material weight loss due to water de-absorption. The
graph in FIG. 24 (2400) shows the averaged sample weight
measurement in percentage for 10 samples. The important information
is shown in the first five (5) hours. The main change is occurring
within the first five hours comparing the graphs in FIG. 23 (2300)
and FIG. 24 (2400). The diffraction grating starts decrease slower
because the grating is shaped inside the material and the water
de-absorption takes some time before it will be noticed in the
measurement. After the main water amount is de-absorbed the
diffraction grating gets very weak.
Application #3--Phase Wrapping Convex Lens (2500)-(2900)
[0184] The following experimental application example discusses a
negative refractive index change due to hydrophilicity change.
Step 1
[0185] A lens shaping of a phase wrapping convex lens is generated
as depicted in FIG. 25 (2500). The phase wrapping concave lens
shows the negative refractive index change which is induced by the
hydrophilicity change inside the material. The NIMO diopter reading
for this structure is depicted in FIG. 26 (2600).
[0186] The convex phase wrapping lens shows a negative diopter
reading and the concave phase wrapping lens as generally depicted
in FIG. 27 (2700) shows a positive diopter reading. The NIMO
diopter reading for this structure is depicted in FIG. 28
(2800).
[0187] The image depicted in FIG. 29 (2900) illustrates an
exemplary 3 mm convex phase wrapping lens top view as
constructed.
Application #4--Water Saturation (3000)-(3100)
[0188] The following experimental application example discusses a
full diopter reading only after water saturation of the
material.
Step 1
[0189] A concave lens with a positive diopter reading was
shaped.
Step 2
[0190] The lens diopter is measured after shaping.
Step 3
[0191] The lens is not stored in water but in air for 18 days and
afterward placed in water.
Step 4
[0192] The diopter reading of the lens after placed in water is
measured.
[0193] The diopter reading of the lens directly after shaping is
minimal. The material still has to be water saturated before the
final diopter reading is possible. During the shaping process it
already can absorb some water, therefore some diopter reading will
be possible after shaping but the full diopter reading will always
only be possible after the material is fully water saturated.
[0194] After the lens is placed in water the lens diopter is fully
recovered after 24 hours. FIG. 30 (3000) depicts the diopter
reading of a 5 diopter 2 mm lens. The first diopter measurement
directly after shaping was only 1.5 D.
[0195] For comparison graph in FIG. 31 (3100) depicts the water
saturation curve for the polymeric material and its relationship to
time.
Application #5--Pre-Soaking
[0196] The following experimental application example discusses the
diopter reading of a pre-soaked sample.
[0197] The saturation period can be shortened if the sample was
pre-soaked in water before the lens shaping. Directly after shaping
the lens shows a larger diopter reading and will recover to the
full diopter value much quicker, compared to a non-pre-soaked
sample. The pre-water soaking will only shorten the time period of
the sample to fully saturate. It will not change the final diopter
reading of the lens.
Application #6--Temperature Dependency (3100)
[0198] The following experimental application example discusses the
temperature dependency of lens diopter.
[0199] The water absorption of the material is dependent on the
surrounding temperature. An incubator can be used to change the
sample temperature. After allowing the sample sufficient time to
adapt to the temperature change the lens diopter was measured and
differences of up to .+-.1 D for different temperature settings
were observed.
[0200] The water absorption is temperature dependent, therefore the
diopter reading of the lens is also temperature dependent. This can
be seen from the graph in FIG. 31 (3100), wherein more water is
absorbed for 35 degree Celsius than for 22 degree Celsius.
Application #7--Diopter Memory (3200)
[0201] The following experimental application example discusses the
temperature dependency of lens diopter.
[0202] The diopter of the treated area is fixed. The sample can be
kept in air storage, never allowing it to develop the full lens
diopter, but when placed in water the full diopter of the lens will
recover to the full, theoretically calculated diopter after
saturation.
[0203] Diopter reading of sample increases when hydrated after
sample was dehydrated, the lens starts with approximately 0 D and
increases the diopter reading to its full -6 D within 27 hours as
depicted in FIG. 32 (3200), which is in accordance with the image
in FIG. 31 (3100).
In-Vivo Lens Shaping Method (3300)-(4000)
[0204] The present invention anticipates that lenses may be
formed/shaped using the systems/methods described herein in-vivo as
generally illustrated in FIG. 33 (3300), comprising the following
steps: [0205] (1) Preparation (3391); [0206] (2) Lens Data Creation
(3392); [0207] (3) Patient Interfacing (3393); [0208] (4) Start
Initialization (3394); [0209] (5) Diagnostics (3395); [0210] (6)
Lens Shaping (3396); and [0211] (7) Verification (3397). As
generally illustrated in FIG. 34 (3400)-FIG. 40 (4000), these
generalized steps may be further defined in terms of more detailed
steps as follows: [0212] (1) Patient existing lens material
determination (3401) wherein this information is used to determine
the laser properties and to calculate the refractive index material
change induced by the refractive index shaping. [0213] (2) Patient
aberration measurement (3402) wherein the different patient
specific aberrations are determined. [0214] (3) Patient selects
which aberrations need treatment (3403) wherein the selection could
be but is not limited to common vision defects like myopia,
hyperopia and astigmatism. [0215] (4) Doctor selects needed lens
information and lens material (3504) wherein the selection is
depending on the consultation with the patients' needs and the
available options. [0216] (5) Determining if needed lens
information exists, and if the information already exists, proceeds
to step (11) (3505). This section is completely software based and
not accessible by the doctor or the patient. This step is
integrated for the case that a patient has a unique diopter value
which is not preloaded to the system. [0217] (6) Calculating lens
curvature (3506) wherein the curvature is depending on the required
lens diopter and the refractive index change induced by the
refractive index shaping and the surrounding refractive index
change of the material. [0218] (7) Determining phase weighting
height (3507) wherein the height is depending on the induced
refractive index change difference and therefore also the
surrounding material. [0219] (8) Phase wrapping lens creation
(3508) wherein the information of the Phase Wrapping Lens is given
by the Phase Wrapping Lens height and the original lens curvature
information. For each layer the radii for each zone can be
determined using this information. [0220] (9) Data output file
creation (3509), the information for each layer, and possible each
block of each layer will be created using the information from the
phase wrapping lens (3508). [0221] (10) Data loading to system
(3510) wherein the data files (3509) might need additional time to
be loaded into the existing software to be analysed and depending
on the material the line pitch can be used to fill the 3
dimensional structure. [0222] (11) Patient is positioned towards
the system (3611) wherein this positioning is the initial step for
the patient interface positioning. The patients head is aligned
towards the refractive index shaping work station. [0223] (12)
Doctor positions the objective towards the patient's iris (3612)
The doctor can use the camera module to get a good idea of the
position of the objective towards the iris. This is an important
step because this position will also be used for the tracking.
[0224] (13) Doctor enters patient ID into the system (3713) wherein
the software will display the patient's information and the
pre-selected shaping options. [0225] (14) Doctor verifies
information and selects START (3714) wherein the doctor verifies in
the first step the patient's identity and afterward the selected
treatment options. [0226] (15) System checks if laser wavelength is
correct (3815) wherein the laser wavelength is selected in regards
of the original lens material. The diagnostic tool for of the
system afterward checks that the displayed wavelength and the real
time value of the system are a match; [0227] (16) System checks if
energy is stable (3816) wherein the laser energy is measured. The
diagnostic tool for of the system afterward checks that the
theoretical calculated energy and the real time value of the system
are matching. [0228] (17) System check if pulse width is stable
(3817) wherein the diagnostic tool is used to internal check that
the pulse width of the system has not changed. [0229] (18) Z module
is used for the Z positioning of the focus spot (3918) wherein the
Z module is used to vary the distance between the lens shaping
focus spot and the iris tracking focus spot. The IOL inside the
patient's eye can settle differently and also the patients cornea
thickness and anterior chamber thickness is variable, therefore the
Z module is used to find the correct location for the refractive
index shaping lens. [0230] (19) Scanner is used for the focus spot
position (3919) wherein the scanner positions the focus spot to the
correct shaping location. [0231] (20) AOM is used for the energy
distribution (3920) wherein the AOM provides the correct energy per
pulse for the scanner location. and [0232] (21) New lens diopter is
verified (4021) wherein the patient's new diopter reading is
measured and verified. This general method may be modified heavily
depending on a number of factors, with rearrangement and/or
addition/deletion of steps anticipated by the scope of the present
invention. Integration of this and other preferred exemplary
embodiment methods in conjunction with a variety of preferred
exemplary embodiment systems described herein is anticipated by the
overall scope of the present invention.
Manufacturing Custom Lens Shaping Method (4100)-(4800)
[0233] The present invention anticipates that lenses may be
formed/shaped using the systems/methods described herein with a
custom manufacturing process as generally illustrated in FIG. 41
(4100), comprising the following steps: [0234] (1) Preparation
(4191); [0235] (2) Lens Data Creation (4192); [0236] (3)
Positioning (4193); [0237] (4) Start Initialization (4194); [0238]
(5) Diagnostics (4195); [0239] (6) Lens Shaping (4196); and [0240]
(7) Verification/shipping (4197). As generally illustrated in FIG.
42 (4200)-FIG. 48 (4800), these generalized steps may be further
defined in terms of more detailed steps as follows: [0241] (1)
Patient selects lens material determination (4201) wherein the
patient has the option to choose the material used from the list of
available options. [0242] (2) Patient aberration measurement (4202)
wherein the patient's aberrations are measured. [0243] (3) Patient
selects which aberrations need treatment (4203) wherein depending
on patient's requirement or availability the treatment option is
chosen. [0244] (4) Doctor selects needed lens information and lens
material (4304) wherein the patient's choice for the material and
required changes is revised and if needed a new selection is
required and will be discussed with the patient. [0245] (5)
Determining if needed lens information exists, and if existing,
proceeding to step (11) (4305) wherein the software checks
internally if the required aberration code already exists or if new
code has to be created for the patient. [0246] (6) Calculating lens
curvature (4306) wherein the curvature is depending on the required
lens diopter and the refractive index change induced by the
refractive index shaping and the surrounding refractive index
change of the material. [0247] (7) Determining phase wrapping
height (4307) wherein the height is depending on the induced
refractive index change difference and therefore also the
surrounding material. [0248] (8) Phase wrapping lens creation
(4308) wherein the information of the Phase Wrapping Lens is given
by the Phase Wrapping Lens height and the original lens curvature
information. For each layer the radii for each zone can be
determined using this information. [0249] (9) Data output file
creation (4309) wherein the information for each layer, and
possible each block of each layer will be created using the
information from the phase wrapping lens (3508) [0250] (10) Data
loading to system (4310) wherein the lens/blank is positioned
inside the system. [0251] (11) Lens/blank is positioned in the
manufacturing system (4411) wherein the system selects the starting
position for the lens shaping. [0252] (12) Technician enters the
Customer ID (4512) wherein the software will display the patient's
information and the pre-selected shaping options. [0253] (13)
Technician verifies information and selects START (4513) wherein
the technician verifies in the first step the patient's identity
and afterward the selected treatment options. [0254] (14) System
checks if laser wavelength is correct (4614) wherein the laser
wavelength is selected in regards of the original lens material.
The diagnostic tool for of the system afterward checks that the
displayed wavelength and the real time value of the system are a
match. [0255] (15) System checks if energy is stable (4615) the
laser energy is measured. The diagnostic tool of the system
afterward checks that the theoretical calculated energy and the
real time value of the system are matching; [0256] (16) System
check if pulse width is stable (4616) wherein the diagnostic tool
is used to internal check that the pulse width of the system has
not changed. [0257] (17) Z module is used for the Z positioning of
the focus spot (4717) wherein the Z module is used to vary the
distance between the lens shaping focus spot and the iris tracking
focus spot. The IOL inside the patient's eye can settle differently
and also the patients cornea thickness and anterior chamber
thickness is variable, therefore the Z module is used to find the
correct location for the refractive index shaping lens. [0258] (18)
Scanner is used for the focus spot position (4718) wherein the
scanner positions the focus spot to the correct shaping location.
[0259] (19) AOM is used for the energy distribution (4719) wherein
the AOM provides the correct energy per pulse for the scanner
location. [0260] (20) A X and Y stage system is used to support a
larger treatment area (4720) wherein the X and Y stages are used to
shape a lens which is larger than the shaping area of the given
objective. and [0261] (21) A Z-stage is used to allow the movement
between layers (4721) wherein the Z stage can additional be used
for the Z movement of the different layers of the lens. [0262] (22)
New lens diopter is verified (4822) wherein the IOL's new diopter
reading is measured and verified. [0263] (23) Lens is packaged and
shipped to doctor (4823) wherein the product is packed and shipped.
This general method may be modified heavily depending on a number
of factors, with rearrangement and/or addition/deletion of steps
anticipated by the scope of the present invention. Integration of
this and other preferred exemplary embodiment methods in
conjunction with a variety of preferred exemplary embodiment
systems described herein is anticipated by the overall scope of the
present invention.
PM System Summary
[0264] The present invention system may be broadly generalized as a
system for changing the hydrophilicity of an internal region of a
polymeric material, said system comprising: [0265] (a) laser
source; [0266] (b) laser scanner; and [0267] (c) microscope
objective; [0268] wherein [0269] the laser source is configured to
emit a pulsed laser radiation output; [0270] the laser scanner is
configured to distribute the pulsed laser radiation output across
an input area of the microscope objective; [0271] the microscope
objective further comprises a numerical aperture configured to
accept the distributed pulsed laser radiation and produce a focused
laser radiation output; and [0272] the focused laser radiation
output is transmitted by the microscope objective to an internal
region of a polymeric material (PM); [0273] the focused laser
radiation output changes the hydrophilicity within the internal
region of the PM.
[0274] This general system summary may be augmented by the various
elements described herein to produce a wide variety of invention
embodiments consistent with this overall design description.
PLM System Summary
[0275] The present invention system anticipates a wide variety of
variations in the basic theme of construction, but can be
generalized as a lens formation system comprising: [0276] (a) laser
source; [0277] (b) laser scanner; and [0278] (c) microscope
objective; [0279] wherein [0280] the laser source is configured to
emit a pulsed laser radiation output; [0281] the laser scanner is
configured to distribute the pulsed laser radiation output across
an input area of the microscope objective; [0282] the microscope
objective further comprises a numerical aperture configured to
accept the distributed pulsed laser radiation and produce a focused
laser radiation output; and [0283] the focused laser radiation
output is transmitted by the microscope objective to a PLM; [0284]
the focused laser radiation interacts with the polymers within the
PLM and results in a change the hydrophilicity within the PLM.
[0285] This general system summary may be augmented by the various
elements described herein to produce a wide variety of invention
embodiments consistent with this overall design description.
PM Method Summary
[0286] The present invention method may be broadly generalized as a
method for changing the hydrophilicity of an internal region of a
polymeric material, the system comprising: [0287] (1) generating a
pulsed laser radiation output from a laser source; [0288] (2)
distributing the pulsed laser radiation output across an input area
of a microscope objective; [0289] (3) accepting the distributed
pulsed radiation into a numerical aperture within the microscope
objective to produce a focused laser radiation output; and [0290]
(4) transmitting the focused laser radiation output to an internal
region of polymeric material ("PM") to modify the hydrophilicity
within the internal region of the PM. This general method may be
modified heavily depending on a number of factors, with
rearrangement and/or addition/deletion of steps anticipated by the
scope of the present invention. Integration of this and other
preferred exemplary embodiment methods in conjunction with a
variety of preferred exemplary embodiment systems described herein
is anticipated by the overall scope of the present invention.
PLM Method Summary
[0291] The present invention method anticipates a wide variety of
variations in the basic theme of implementation, but can be
generalized as a lens formation method comprising: [0292] (1)
generating a pulsed laser radiation output from a laser source;
[0293] (2) distributing the pulsed laser radiation output across an
input area of a microscope objective; [0294] (3) accepting the
distributed pulsed radiation into a numerical aperture within the
microscope objective to produce a focused laser radiation output;
and [0295] (4) transmitting the focused laser radiation output into
a PLM to modify the hydrophilicity within the PLM. This general
method may be modified heavily depending on a number of factors,
with rearrangement and/or addition/deletion of steps anticipated by
the scope of the present invention. Integration of this and other
preferred exemplary embodiment methods in conjunction with a
variety of preferred exemplary embodiment systems described herein
is anticipated by the overall scope of the present invention.
PM Product-by-Process
[0296] The present invention method may be applied to the
modification of the hydrophilicity of an arbitrary polymeric
material, wherein the product-by-process is a modified polymeric
material (PM) comprising synthetic polymeric materials further
comprising a plurality of modified hydrophilicity zones formed
within the polymeric material (PM), the plurality of modified
hydrophilicity zones created using a method comprising: [0297] (1)
generating a pulsed laser radiation output from a laser source;
[0298] (2) distributing the pulsed laser radiation output across an
input area of a microscope objective; [0299] (3) accepting the
distributed pulsed radiation into a numerical aperture within the
microscope objective to produce a focused laser radiation output;
and [0300] (4) transmitting the focused laser radiation output to
an internal region of polymeric material (PM) to modify the
hydrophilicity within the internal region of the PM. This general
product-by-process method may be modified heavily depending on a
number of factors, with rearrangement and/or addition/deletion of
steps anticipated by the scope of the present invention.
Integration of this and other preferred exemplary embodiment
methods in conjunction with a variety of preferred exemplary
embodiment systems described herein is anticipated by the overall
scope of the present invention.
PLM Product-By-Process
[0301] The present invention method may be applied to the formation
of an optical lens, wherein the product-by-process is an optical
lens comprising synthetic polymeric materials further comprising a
plurality of optical zones formed within a PLM, the plurality of
optical zones created using a lens formation method comprising:
[0302] (1) generating a pulsed laser radiation output from a laser
source; [0303] (2) distributing the pulsed laser radiation output
across an input area of a microscope objective; [0304] (3)
accepting the distributed pulsed radiation into a numerical
aperture within the microscope objective to produce a focused laser
radiation output; and [0305] (4) transmitting the focused laser
radiation output into a PLM to modify the hydrophilicity within the
PLM. This general product-by-process method may be modified heavily
depending on a number of factors, with rearrangement and/or
addition/deletion of steps anticipated by the scope of the present
invention. Integration of this and other preferred exemplary
embodiment methods in conjunction with a variety of preferred
exemplary embodiment systems described herein is anticipated by the
overall scope of the present invention.
System/Method/Product-by-Process Variations
[0306] The present invention anticipates a wide variety of
variations in the basic theme of construction. The examples
presented previously do not represent the entire scope of possible
usages. They are meant to cite a few of the almost limitless
possibilities.
[0307] This basic system, method, and product-by-process may be
augmented with a variety of ancillary embodiments, including but
not limited to: [0308] An embodiment wherein the distribution of
the focused laser radiation output is configured to be larger than
the field size of the microscope objective by use of an X-Y stage
configured to position the microscope objective. [0309] An
embodiment wherein the laser source further comprises a femtosecond
laser source emitting laser pulses with a megahertz repetition
rate. [0310] An embodiment wherein the pulsed laser radiation
output has energy in a range of 0.17 to 500 nanojoules. [0311] An
embodiment wherein the pulsed laser radiation output has a
repetition rate in the range of 1 MHz to 100 MHz. [0312] An
embodiment wherein the pulsed laser radiation output has a pulse
width in the range of 10 fs to 350 fs. [0313] An embodiment wherein
the focused laser radiation output has a spot size in the X-Y
directions in the range of 0.5 to 10 micrometers. [0314] An
embodiment wherein the focused laser radiation output has a spot
size in the Z direction in the range of 0.01 to 200 micrometers.
[0315] An embodiment wherein the PLM is shaped in the form of a
lens. [0316] An embodiment wherein the PLM is water saturated.
[0317] An embodiment wherein the PLM comprises an intraocular lens
contained within an ophthalmic lens material. [0318] An embodiment
wherein the PLM comprises an intraocular lens contained within an
ophthalmic lens material, the ophthalmic lens material located
within the eye of a patient. [0319] An embodiment wherein the laser
scanner is configured to distribute the focused laser radiation
output in a two-dimensional pattern within the PLM. [0320] An
embodiment wherein the PLM comprises an intraocular lens contained
within an ophthalmic lens material, the ophthalmic lens material
located within the eye of a patient. [0321] An embodiment wherein
the laser scanner is configured to distribute the focused laser
radiation output in a three-dimensional pattern within the PLM.
[0322] An embodiment wherein the laser scanner is configured to
distribute the focused laser radiation output in a
three-dimensional pattern within the PLM, the pattern forming a
convex lens within the PLM. [0323] An embodiment wherein the laser
scanner is configured to distribute the focused laser radiation
output in a three-dimensional pattern within the PLM, the pattern
forming a biconvex lens within the PLM. [0324] An embodiment
wherein the laser scanner is configured to distribute the focused
laser radiation output in a three-dimensional pattern within the
PLM, the pattern forming a concave lens within the PLM. [0325] An
embodiment wherein the laser scanner is configured to distribute
the focused laser radiation output in a three-dimensional pattern
within the PLM, the pattern forming a biconcave lens within the
PLM. [0326] An embodiment wherein the laser scanner is configured
to distribute the focused laser radiation output in a
three-dimensional pattern within the PLM; the focused laser
radiation creating a hydrophilicity change in the volume associated
with the three-dimensional pattern; and the hydrophilicity change
resulting in a corresponding change in refractive index of the
volume associated with the three-dimensional pattern. [0327] An
embodiment wherein the refractive index change is negative for the
PLM having an initial refractive index greater than 1.3. [0328] An
embodiment wherein the refractive index change is greater than
0.005. [0329] An embodiment wherein the three-dimensional pattern
comprises a plurality of layers within the PLM. [0330] An
embodiment wherein the PLM comprises a crosslinked polymeric
copolymer. [0331] An embodiment wherein the PLM comprises a
crosslinked polymeric acrylic polymer. [0332] An embodiment wherein
the laser source further comprises an Acousto-Optic Modulator
(AOM). [0333] An embodiment wherein the laser source further
comprises a greyscale Acousto-Optic Modulator (AOM). [0334] An
embodiment wherein the PLM has been presoaked in a liquid solution
comprising water. [0335] An embodiment wherein the PLM comprises an
ultraviolet (UV) absorbing material.
[0336] One skilled in the art will recognize that other embodiments
are possible based on combinations of elements taught within the
above invention description.
Generalized Computer Usable Medium
[0337] In various alternate embodiments, the present invention may
be implemented as a computer program product for use with a
computerized computing system. Those skilled in the art will
readily appreciate that programs defining the functions defined by
the present invention can be written in any appropriate programming
language and delivered to a computer in many forms, including but
not limited to: (a) information permanently stored on non-writeable
storage media (e.g., read-only memory devices such as ROMs or
CD-ROM disks); (b) information alterably stored on writeable
storage media (e.g., floppy disks and hard drives); and/or (c)
information conveyed to a computer through communication media,
such as a local area network, a telephone network, or a public
network such as the Internet. When carrying computer readable
instructions that implement the present invention methods, such
computer readable media represent alternate embodiments of the
present invention.
[0338] As generally illustrated herein, the present invention
system embodiments can incorporate a variety of computer readable
media that comprise computer usable medium having computer readable
code means embodied therein. One skilled in the art will recognize
that the software associated with the various processes described
herein can be embodied in a wide variety of computer accessible
media from which the software is loaded and activated. Pursuant to
In re Beauregard, 35 USPQ2d 1383 (U.S. Pat. No. 5,710,578), the
present invention anticipates and includes this type of computer
readable media within the scope of the invention. Pursuant to In re
Nuijten, 500 F.3d 1346 (Fed. Cir. 2007) (U.S. patent application
Ser. No. 09/211,928), the present invention scope is limited to
computer readable media wherein the media is both tangible and
non-transitory.
CONCLUSION
[0339] A system/method allowing the modification of the
hydrophilicity of a polymeric material (PM) has been disclosed. The
modification in hydrophilicity (i) decreases the PM refractive
index, (ii) increases the PM electrical conductivity, and (iii)
increases the PM weight. The system/method incorporates a laser
radiation source that generates focused laser pulses within a
three-dimensional portion of the PM to affect these changes in PM
properties. The system/method may be applied to the formation of
customized intraocular lenses comprising material (PLM) wherein the
lens created using the system/method is surgically positioned
within the eye of the patient. The implanted lens refractive index
may then be optionally altered in situ with laser pulses to change
the optical properties of the implanted lens and thus achieve
optimal corrected patient vision. This system/method permits
numerous in situ modifications of an implanted lens as the
patient's vision changes with age.
[0340] A lens formation system/method that permits dynamic in situ
modification of the hydrophilicity of the PLM has also been
disclosed. The system/method incorporates a laser that generates
focused pulses within a three-dimensional portion of PLM to modify
the hydrophilicity and thus the refractive index of the PLM and
thus create a customized lens of arbitrary configuration. The
system/method may be applied to the formation of customized
intraocular lenses wherein an ophthalmic lens material
incorporating homogeneous PLM is surgically positioned within the
eye of a patient. The patient's vision is analyzed with the
ophthalmic lens installed and the homogeneous PLM is then
irradiated in situ with laser pulses to modify the internal
refractive characteristics of the PLM to achieve optimal corrected
patient vision. This exemplary application may permit in situ
modification of intraocular lens characteristics on a dynamic basis
as the patient ages.
[0341] Although a preferred embodiment of the present invention has
been illustrated in the accompanying drawings and described in the
foregoing Detailed Description, it will be understood that the
invention is not limited to the embodiments disclosed, but is
capable of numerous rearrangements, modifications, and
substitutions without departing from the spirit of the invention as
set forth and defined by the following claims.
* * * * *