U.S. patent application number 13/020616 was filed with the patent office on 2012-08-09 for apparatus, system and method for providing a coating for an implanatable lens.
This patent application is currently assigned to Abbott Medical Optics Inc.. Invention is credited to Rakhi Jain.
Application Number | 20120203338 13/020616 |
Document ID | / |
Family ID | 45755518 |
Filed Date | 2012-08-09 |
United States Patent
Application |
20120203338 |
Kind Code |
A1 |
Jain; Rakhi |
August 9, 2012 |
APPARATUS, SYSTEM AND METHOD FOR PROVIDING A COATING FOR AN
IMPLANATABLE LENS
Abstract
An apparatus, system and method for coating an implantable lens.
The apparatus, system and method may include at least one coating
layer applied to at least one surface of the optic of the
implantable lens, wherein the coating layer at least partially
protects the optic at least during the implantation, and wherein
the coating layer is removable following implantation. The coating
layer may include a lubricant and/or medication and may be in the
form of a biodegradable polymer and/or a film.
Inventors: |
Jain; Rakhi; (Irvine,
CA) |
Assignee: |
Abbott Medical Optics Inc.
Santa Ana
CA
|
Family ID: |
45755518 |
Appl. No.: |
13/020616 |
Filed: |
February 3, 2011 |
Current U.S.
Class: |
623/6.62 ;
427/2.24 |
Current CPC
Class: |
A61F 2002/1681 20130101;
A61F 2/1613 20130101; A61F 2230/0006 20130101; A61L 27/34 20130101;
A61F 2250/0004 20130101; A61F 2250/0067 20130101; A61L 2430/16
20130101; C08L 67/04 20130101; A61F 2250/0031 20130101; A61F
2210/0004 20130101; A61F 2250/0056 20130101; A61F 2/16 20130101;
A61F 2310/00389 20130101; A61F 2/1648 20130101; A61L 2300/452
20130101; A61L 27/34 20130101 |
Class at
Publication: |
623/6.62 ;
427/2.24 |
International
Class: |
A61F 2/16 20060101
A61F002/16; B05D 7/00 20060101 B05D007/00 |
Claims
1. A system, comprising: an implantable lens having an optic; at
least one coating layer applied to at least one surface of the
optic, wherein said coating layer is capable of at least partially
protecting the optic at least during implantation; wherein said
coating layer is capable of removal following the implantation.
2. The system of claim 1, wherein said coating layer comprises a
lubricant.
3. The system of claim 1, further comprising at least one
additional coating layer applied to a second surface of the optic,
wherein said additional coating layer is capable of at least
partially protecting the second surface of the optic.
4. The system of claim 1, wherein said at least one coating layer
comprises a film.
5. The system of claim 4, wherein said film is inert.
6. The system of claim 4, wherein said film comprises one or more
selected from the group consisting of polyethylene terephthalate
(PET), polytetrafluoroethylene (PTFE), polystyrene, polyethylene,
polypropylene, polymethylmethacrylate, ethyl acrylate, ethyl
methacrylate, and 2,2,2-trifluoroethyl.
7. The system of claim 4, wherein said film comprises a tab.
8. The system of claim 1, wherein the optic comprises a deformable
optic.
9. The system of claim 1, wherein said coating layer comprises a
biodegradable polymer.
10. The system of claim 9, wherein said biodegradable polymer is
selected from the group consisting of polylactic acid and
polyglycolic acid.
11. The system of claim 9, wherein said biodegradable polymer
comprises an impregnated medication.
12. The system of claim 1, wherein the application to the at least
one surface of the optic comprises at least one selected from the
group consisting of an adhesion, a contact force, and an
impregnation.
13. The system of claim 1, wherein said coating layer comprises
multiple layers.
14. The system of claim 1, wherein the capability of removal
comprises one selected from the group consisting of mechanical
removability and chemical removability.
15. The system of claim 1, wherein the capability of removal
comprises degradation over a predefined time period comprising one
selected from the group consisting of a range of about a day to
multiple years, and an approximation of a healing time from the
implantation.
16. The system of claim 1, further comprising a second implantable
lens.
17. The system of claim 1, wherein said lens is an accommodating
lens.
18. The system of claim 1, wherein the lens further comprises a
haptic comprising at least one haptic coating layer that is
chemically distinct from said at least one coating layer.
19. A method of maintaining characteristics of an intraocular lens,
comprising: coating the intraocular lens with at least one of a
protective coating, a protective medicinal coating, and a medicinal
coating prior to implantation; enabling the implantation of the
intraocular lens; and removing at least one selected from the group
consisting of the protective coating, the protective medicinal
coating, and the medicinal coating after the implantation.
20. An intraocular lens suitable for implantation into an eye, said
lens comprising: an optic for improving at least one vision
characteristic of the eye; a haptic for supporting said optic
within the eye; and at least one coating layer associated with at
least one of said optic and said haptic, wherein said at least one
coating layer at least partially protects the at least one of said
optic and said haptic at least during the implantation.
Description
FIELD OF THE INVENTION
[0001] The instant disclosure relates to implantable lenses, and,
more particularly, to an apparatus, system and method for providing
a one or more coatings or films for an implantable lens.
BACKGROUND OF THE INVENTION
[0002] Surgery on the human eye has become commonplace in recent
years. Many patients pursue eye surgery as an elective procedure,
such as to avoid the use of contacts or glasses, and other patients
may find it necessary to pursue surgery to correct an adverse
condition in the eye. Such adverse conditions may include, for
example, cataracts or presbyopia, as well as other conditions known
to those skilled in the art that may negatively affect elements of
the eye. For example, a cataract may increase the opacity of the
natural lens of the eye, causing impaired vision or blindness.
Correction of such adverse conditions may be achieved by surgically
removing a cloudy or diseased lens in the patient's eye and
replacing it with an artificial lens, known as an intraocular lens
(IOL).
[0003] The anatomy and physiology of the human eye is well
understood. Generally speaking, the structure of the human eye
includes an outer layer formed of two parts, namely the cornea and
the sclera. The middle layer of the eye includes the iris, the
choroid, and the ciliary body. The inner layer of the eye includes
the retina. The eye also includes, physically associated with the
middle layer, a crystalline lens that is contained within an
elastic capsule, referred to herein as the lens capsule, or
capsular bag.
[0004] Image formation in the eye occurs by entry of image-forming
light to the eye through the cornea, and refraction by the cornea
and the crystalline lens to focus the image-forming light on the
retina. The retina provides the light sensitive tissue of the
eye.
[0005] Functionally, the cornea has a greater, and generally
constant, optical power in comparison to the crystalline lens. The
power of the crystalline lens, while smaller than that of the
cornea, may be changed when the eye needs to focus at different
distances. This change, or "accommodation," is achieved by changing
the shape of the crystalline lens. Accommodation, as used herein,
includes the making of a change in the focus of the eye for
different distances. For example, in order to change the shape of
the crystalline lens for accommodation, the ciliary muscles may
relax to cause ligaments (zonules) that support the crystalline
lens to relax, thereby allowing the crystalline lens to become more
rounded.
[0006] The iris operates to change the aperture size of the eye.
More specifically, the diameter of the incoming light beam is
controlled by the iris, which forms the aperture stop of the eye,
and the ciliary muscles may contract, as referenced above, to
provide accommodation in conjunction with any needed change in the
size of the aperture provided by the iris. The opening, or
aperture, in the iris is called the pupil.
[0007] Correction of defects or degradation in the aspects of the
eye may occur surgically, as mentioned above, or non-surgically. In
a simple example, it is common to wear glasses or contact lenses to
improve vision by correcting myopic (near-sighted), hyperopic
(far-sighted) and astigmatic eyesight. Rather than relying on
glasses or contacts, elective laser refractive surgery, or other
eye surgery, may serve to improve the refractive state of the eye,
and may thereby decrease or eliminate dependence on glasses or
contact lenses. Additional surgeries may include various methods of
surgical remodeling of the cornea, or cataract surgery, for
example. Surgery may also serve to implant an IOL, either in
addition to the crystalline lens, which addition is referred to as
a phakic IOL, or upon removal of the crystalline lens, which
replacement is referred to as a pseudophakic IOL.
[0008] An IOL may be implanted in the eye, for example, as a
replacement for the natural crystalline lens after cataract
surgery, or to alter the optical properties of an eye in which the
natural lens remains. IOLs often include an optic, and may
preferably include at least one flexible fixation member, or
haptic, that extends from the optic and becomes affixed in the eye
to secure the lens in proper position to provide the desired vision
correction. The optic typically includes an optically clear lens,
and the opacity of the haptic may vary.
[0009] More specifically, the IOL may consist of a small plastic
lens with haptics comprised of plastic side struts. The IOL may
generally be made of an inflexible material, such as polymethyl
methacrylate (PMMA), for example, or of a flexible material. The
IOL may be a fixed monofocal lens matched to distance vision, or a
multifocal lens that provides the recipient with multiple-focused
vision at far and reading distances, for example. The IOL may also
be a toric IOL to correct for astigmatism or an accommodating IOL
that provides the recipient with vision at all distances (far,
intermediate, and near) by moving and/or changing shape with the
use of the muscles of the eye.
[0010] Flexible, softer materials may be preferred for the optic of
the IOL, such as in order to allow for greater deformation, and
thereby increased power change, in vivo. That is, the softer, more
flexible materials mimic the mechanical properties of the natural
lens material at a young age. However, with softer materials comes
the concern that the optic may be more easily damaged, particularly
during surgical insertion through a surgical incision and in
placement and manipulation of the IOL in the capsular bag.
[0011] Implantation of an IOL into the eye involves making this
surgical incision in the eye. Those skilled in the art will
appreciate that it is advantageous to minimize the size of the
surgical incision. Currently, the incision necessary for the
insertion of a soft IOL may be in a range up to approximately
3.2-4.1 mm. A smaller incision reduces trauma to the eye and may
speed healing and may reduce any surgically-related optical
effects. However, as the size of the incision is decreased, there
will arise a need to more compactly deliver lenses, particularly to
avoid damage to the IOL during insertion through the smaller
incision.
[0012] Further, insertion of a lens through the incision in the eye
during a surgical procedure may cause post-operative inflammation,
increased intraocular pressure, and/or posterior and anterior
capsular opacification (PCO and ACO), and, for example, and these
effects must be accounted for by the surgeon, both during and
following surgery. If not accounted for, these effects may cause
the onset of detrimental side effects, or may cause a failure to
correct vision.
[0013] Thus, an implanted optic may be damaged upon insertion into
the eye, and/or may cause temporary or permanent damage to the eye
due to the insertion, thereby adversely affecting optical
performance and/or cosmetic appearance. Likewise, surgical side
effects that may cause such temporary damage from the insertion
must be treated or prevented, preferably without further damage to
the lens or the eye, or performance of the implanted optic may be
adversely affected.
[0014] A need therefore exists to protect an implantable lens, such
as an intraocular lens, comprised of a soft optic material, during
insertion, and/or to negate the adverse side effects of
implantation of a lens.
SUMMARY OF THE INVENTION
[0015] An apparatus, system and method for coating an implantable
lens for implantation, wherein the lens includes at least an optic,
is disclosed. The apparatus, system and method may include at least
one coating layer applied to at least one surface of the optic,
wherein the coating layer may at least partially protect the optic
during the implantation, and wherein the coating layer may be
removable following implantation. The coating layer may include a
protectant, a lubricant and/or medication, and may be in the form
of a biodegradable polymer and/or a film.
[0016] The apparatus, system and method may, more specifically, be
for coating an intraocular lens. Such an apparatus, system and
method for coating and/or protecting an intraocular lens may
include a means physically associated with the intraocular lens for
protecting the lens at the implantation and a means for removing
the protective means upon the implantation. The means for removal
may include, for example, a tab. The tab may be sized to
accommodate a surgical tool for the implantation. The tab may
include one or more features that aid in removal of the protective
means. Such features may include one of color and texture.
[0017] The apparatus, system and method may also include
maintaining characteristics of an intraocular lens. For example,
the method of maintaining characteristics of an intraocular lens
may include coating the intraocular lens with a protective coating
and/or a medicinal coating prior to implantation, enabling the
implantation of the intraocular lens, and removing at least one of
the protective coating and/or the medicinal coating after the
implantation.
[0018] An intraocular lens suitable for implanting into an eye is
also disclosed. The lens may include an optic for improving the
vision of the eye, and a haptic for supporting the optic within the
capsular bag of the eye. At least one of the optic and the haptic
may include at least one coating layer, wherein the at least one
coating layer may at least partially protect the at least one of
the optic and the haptic at least during the implantation. In an
embodiment, the at least one coating layer is removable following
implantation. The coating layer may additionally provide
medication.
[0019] The medication is on the at least one surface of the coating
layer proximate to the optic. The medication may comprise a
treatment, such as for reducing intraocular pressure. The
medication may be, for example, a steroid. The medication may, for
example, be activated by the implantation.
[0020] Thus, the present invention protects an implantable lens
during insertion, and/or negates the adverse side effects of
implantation of a lens, such as an intraocular lens.
BRIEF DESCRIPTION OF THE FIGURES
[0021] Understanding of the present invention will be facilitated
by consideration of the following detailed description of the
preferred embodiments of the present invention taken in conjunction
with the accompanying drawings, in which like numerals refer to
like parts:
[0022] FIG. 1 illustrates a diagram of the eye;
[0023] FIG. 2 illustrates a diagram of an eye with an implanted
IOL;
[0024] FIG. 3 illustrates an IOL according to an embodiment of the
present invention;
[0025] FIG. 4 illustrates an exemplary optic for use in the present
invention;
[0026] FIG. 5 illustrates an exemplary haptic and optic for use in
the present invention;
[0027] FIG. 6 illustrates an exemplary dual optic lens for use in
the present invention;
[0028] FIG. 7 illustrates a coating formed on an optic of the type
discussed with respect to FIGS. 3-6;
[0029] FIG. 8 illustrates a coating formed on an optic according to
an aspect of the present invention;
[0030] FIG. 9 illustrates an optic with a film coating a surface
according to an aspect of the present invention;
[0031] FIG. 10 illustrates a method of providing a protective
coating on an optic according to an aspect of the present
invention; and
[0032] FIG. 11 illustrates a method of providing a protective
coating on an optic and haptic according to an aspect of the
present invention.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0033] It is to be understood that the figures and descriptions of
the present invention have been simplified to illustrate elements
that are relevant for a clear understanding of the present
invention, while eliminating, for the purpose of clarity, many
other elements found in typical lenses, lens systems and methods,
and in protective coatings and techniques. Those of ordinary skill
in the art may recognize that other elements and/or steps are
desirable and/or required in implementing the present invention.
However, because such elements and steps are well known in the art,
and because they do not facilitate a better understanding of the
present invention, a discussion of such elements and steps is not
provided herein. The disclosure herein is directed to all such
variations and modifications to such elements and methods known to
those skilled in the art.
[0034] The present invention provides protection for the
characteristics of implantable lenses, and may further provide
positive benefits to negate side effects often associated with a
surgical insertion of an implantable lens. In particular, the
present invention may include coating or treating the surface(s),
such as the anterior, posterior, or both, of any implantable IOL.
Such a coating or treatment may be temporary in nature. The coating
or treatment may be protective, and/or may be impregnated with
secondary materials, such as medicinal materials, to combat or
reduce side effects known to exist from surgery to the eye.
[0035] The present invention may additionally include an inert,
removable film on an implantable optic, separate from, integral
with, or equivalent to the aforementioned coating. The film may
provide protection and/or structural support during insertion. The
film may be removed late in the surgical process, such as after or
simultaneously with implementation in vivo.
[0036] Additionally, the present invention may include a protective
and/or medicinal coating on the surgical insertion tools employed
during an implantation of, for example, an IOL, to effectively
protect the optic and/or to protect from side effects of
implantation of the optic. A coating or protective layer on a
surgical tool may not require removal after the procedure is
complete, unlike a coating or layer on the optic.
[0037] The present invention may be utilized on any type of lens
and/or lens system that may cause harm, adverse effects, or that
may suffer from adverse performance due to the adverse effects or
based on damage during insertion, in the eye, for example. Such
lens systems include single lens designs including but not limited
to monofocal, multifocal, toric, accommodating IOLs, next
generation designs for accommodating IOLs, and dual optic lenses,
by way of non-limiting example.
[0038] FIG. 1 is a diagram of an eye. Eye 10 includes retina 12 for
receiving an image produced by cornea 14 and natural lens 16 from
light incident upon eye 10. Natural lens 16 is disposed within
capsular bag 20, which separates anterior and posterior chambers of
eye 10. Capsular bag 20 is a resilient material that changes the
shape and/or location of natural lens 16 in response to ocular
forces produced when ciliary muscles 22 contract and stretch
natural lens 16 via zonules 24 disposed about an equatorial region
of capsular bag 20.
[0039] This shape change effectuated by ciliary muscles 22 may
flatten natural lens 16, thereby producing a relatively low optical
power for providing distant vision in an emmetropic eye. To produce
intermediate and/or near vision, ciliary muscles 22 relax, thereby
relieving tension on zonules 24.
[0040] The resiliency of capsular bag 20 thus provides an ocular
force to modify the curvature of natural lens 16, to thereby
provide an optical power suitable for required vision. This
modification, or "accommodation," allows for changes the focus of
the eye for different viewing distances.
[0041] Eye 10 also includes iris 26. Iris 26 may operate to change
the aperture size of eye 10. More specifically, the diameter of the
incoming light beam is controlled by iris 26, which forms the
aperture stop of eye 10.
[0042] Referring now to FIG. 2, there is shown an eye 10 having a
lens (natural lens 16 of FIG. 1) replaced with an IOL 100. Natural
lens 16 may require removal due to a refractive lens exchange, or
due to a disease such as cataracts, for example. Once removed,
natural lens 16 may then be replaced by IOL 100 to provide improved
vision in eye 10. Eye 10 may include IOL 100 with optic 102, cornea
14, retina 12, haptics or support structure 104 for centering optic
102, and, in the case of an accommodating IOL (aIOL), haptics 104
for transferring ocular forces from ciliary muscle 22, zonules 24,
and/or capsular bag 20 to optic 102 to change its shape, power,
and/or axial location relative to retina 12.
[0043] Removal of natural lens 16 may occur during a surgical
procedure. The surgery typically includes a very small, self
sealing incision in the eye to permit insertion and removal of an
IOL 100 and tools. More specifically, IOL 100 is typically inserted
through an incision less than 4.5 mm, and preferably less than 2.5
mm, made in the eye 10 during the surgical procedure.
[0044] Various techniques may be employed for implanting IOL 100
through the surgical incision and into eye 10. A physician may, for
example, access the anterior aspect of the capsular bag 20 via an
appropriate technique. The physician may then incise the anterior
of the bag 20, such as by making a circular opening, or the
physician may make a dumbbell shaped incision by forming two small
circular openings and connecting them with a third straight line
incision. The natural lens 16 may then be removed from the capsular
bag by any of variety of techniques, such as phacoemulsification,
cryogenic and/or radiative methods.
[0045] In phacoemulsification, for example, an
irrigation-aspiration instrument having an ultrasonic vibration is
inserted through the incision to gently break up natural lens 16
and aspirate it out in tiny pieces in order to make way for the
placement of IOL 100. The tip of this instrument vibrates at
ultrasonic frequency to sculpt and emulsify the lens, while a pump
aspirates particles through the tip. To inhibit further cell
growth, often the physician may polish the capsular bag to remove
or kill remaining lens epithelial cells. Other treatments, such as
cryogenically and/or through radiative techniques, via
anti-metabolites, or via chemical and osmotic agents, for example,
have been attempted to remove or kill remaining cells.
[0046] IOL 100 may be surgically implanted into capsular bag 20
following removal of natural lens 16, in addition to natural lens
16, or to replace a lens that has previously replaced natural lens
16. In order to implant IOL 100, the incision may be enlarged, or
IOL 100 may be folded, or otherwise distorted to fit through the
incision, for example. To fold IOL 100, a holder/folder, or an
insertion device, such as a catheter, for example, may be used.
[0047] IOL 100 may be inserted in the posterior chamber in capsular
bag 20. If IOL 100 comprises separate anterior and posterior
portions, the physician may fold or roll the posterior portion, and
may place it in the capsular bag through the anterior opening after
allowing the posterior portion to unroll/unfold. The physician may
then manipulate IOL 100, using surgical tools, to adjust the
positioning of the posterior portion until it is within
satisfactory limits. Next, the physician may roll/fold and implant
the anterior portion, and may align and assemble the anterior
portion to the posterior portion as needed.
[0048] This rolling/folding, implantation, unrolling/folding and
alignment/assembly may be repeated until the lens system associated
with IOL 100 is inside the capsular bag. Because a smaller incision
is required to engage in the surgical insertion of folded lens
elements, as discussed immediately hereinabove, fewer or no
stitches may be needed and the patient's recovery time may be
appreciably shorter when using a foldable IOL. However, in such
cases, significant manipulation of the IOL 100 may be required, as
discussed above.
[0049] It is contemplated that conventional IOL folding devices,
injectors, syringes and or shooters may be used to manipulate
and/or insert the exemplary lens systems through or within the
surgical incision, as described herein. It is further contemplated
that, upon folding/rolling, the lens system may be placed in an
insertion tool, and/or may be inserted into the eye via an
insertion tool. Finally, the lens system may be adjusted by a
physician during implantation, and/or may be temporarily held in
place in the eye by the use of dissolvable sutures, or a detachable
or dissolvable clip, for example.
[0050] An exemplary insertion tool employs a hollow insertion tube
having a diameter that permits the folded IOL to pass through the
hollow space defined by the tube without permanent deformation, and
a plunger assembly including a rod, often made of metal, which is
moved longitudinally in the hollow space, in contact with optic 102
of IOL 100, to thereby push IOL 100 through the hollow space.
Several disadvantages are apparent in such insertion tools. For
example, pushing, without trapping or holding, IOL 100 through and
out of the hollow space defined by the tube may cause IOL 100 to be
released from the insertion device without precise control, so that
the released IOL may damage eye 10, may itself be damaged, and/or
may be mispositioned in eye 10. More particularly, the rod may mark
the surface of optic 102 and/or tear optic 102, particularly when
optic 102 is made of soft materials, such as soft elastomeric
silicone polymeric materials.
[0051] Of note, each of the insertion tools, adjustment techniques
and techniques for holding in place IOL 100 may result in damage to
optic 102, or eye 10. This damage may adversely affect eye 10,
and/or affect the performance of optic 102.
[0052] A number of different lens systems may be implanted to
provide optic 102 via the surgical implantation techniques
discussed hereinabove. It is preferable to avoid damage to the lens
during implantation, adjustment or holding in place of the lens,
via insertion tools, and to avoid abrasion from the sidewalls of
the incision, the physician, or the dissolvable clip, and to avoid
side effects following implantation, when surgically implanting
such lenses. In particular, lens systems including single lenses,
accommodating IOLs, next generation lenses for aIOLs, and dual
optic lenses, by way of non-limiting example, may benefit from the
protective embodiments discussed herein.
[0053] A single lens system, such as a single, fixed class IOL, has
a single fixed focal length, or an equivalent single fixed power.
Unlike the eye's natural lens, which may adjust its focal length
and/or axial location within a particular range by accommodation,
single focal length IOLs generally do not accommodate. As a result,
distant objects may appear in focus, while objects at closer
distances appear blurred.
[0054] On the other hand, an aIOL may move axially and/or adjust
optical power within a particular range. As a result, an eye with
an aIOL may clearly focus on objects at a range of distances from
the eye. This ability to accommodate is of large benefit to the
patient, and more closely approximates the patient's natural vision
than does a single focal length IOL.
[0055] Referring now to FIG. 3, an exemplary lens system comprising
aIOL 100 is shown disposed about optical axis A. Accommodating IOL
100 includes optic 102, and haptic 104 configured to effectively
transfer an ocular force from an eye to optic 102 so as to produce
a range of powers in response to the ocular force. Haptic 104
includes inner structure 208 and outer structure 210, and plurality
of arms 212 connecting coupling structures 208, 210 to one another
to efficiently and effectively transfer ocular forces. Haptic 104
thus changes the shape and/or axial location of optic 102, thereby
providing a change in optic power and/or focal plane location of
optic 202. Arms 212 each include proximal end 214 coupled to inner
structure 208, and distal end 216 coupled to outer structure
210.
[0056] Optic 102 may be formed directly onto haptic 104.
Alternatively, optic 102 may be fabricated separately from haptic
104, and attached to haptic 104. In certain embodiments, haptic 104
may be machined or molded, and optic 102 may be molded and/or
machined over, into or on top of haptic 104.
[0057] Optic 102 may be a relatively soft material, so that optic
102 may deform or change shape readily under the limited deforming
forces produced by capsular bag 20 and/or ciliary muscle 22. An
exemplary material for optic 102 is a relatively soft silicone
material, although other suitable materials may be used as will be
understood to those skilled in the art. The stiffness of optic 102
may be in the range of approximately 0.5 to 500 kPa, for example.
In more particular exemplary embodiments, the stiffness of optic
may be in the range of approximately 25 and 200 kPa, or more
specifically in the range of 25 and 80 kPa, for example.
[0058] In contrast with optic 102, at least portions of haptic 104,
such as arms 212, may generally be of a relatively stiffer material
than that of optic 102, so that haptic 104 may efficiently transmit
ocular forces to optic 102. An exemplary material for haptic 104 is
a relatively stiff silicone material, although other suitable
materials may be used, such as acrylic, polystyrene, polymethyl
methacrylate, or clear polyurethanes. The stiffness of haptic 104
may be greater than or equal to 500 kPa, or, in a more particular
exemplary embodiment, may be greater than or equal to 3000 kPa, for
example.
[0059] Arms 212 may extend into optic 102, and may include the
clear aperture of optic 102. As used herein, the term "clear
aperture" means the area of the optic that restricts the extent of
rays from a collimated source or a distant light source that can be
imaged by the optic. The clear aperture is usually circular, and
may be specified by its diameter. In some embodiments, the clear
aperture may have the same or substantially the same diameter as
optic 102. Alternatively, the diameter of the clear aperture may be
smaller than the diameter of optic 102, for example, due to the
presence of a glare or PCO reducing structure disposed about a
peripheral region of optic 102.
[0060] Since inner structure 208 and proximal ends 214 of arms 212
may be located inside optic 102 and within the clear aperture of
optic 102, at least these portions of haptic 104 may be
beneficially transparent or nearly transparent, so as to not
substantially block or scatter light transmitted through optic 102.
In addition, these portions of haptic 104 may have a refractive
index that matches the refractive index of optic 102, so that
interfaces between optic 102 and haptic 104 do not produce
significant reflections or refractions that might produce scattered
light within the eye, which scattered light might appear as a glare
or haze.
[0061] By way of example, for a planar surface at normal incidence
between air (a refractive index of 1) and glass (a refractive index
of 1.5), 4% of the incident power is reflected at the interface.
If, instead of relative refractive indices of 1 and 1.5, the
refractive indices differ by 4% or less, such as the difference
between 1.5 and 1.56, or 1.5 and 1.44, for example, reflection is
reduced to 0.04%, which is a factor of 100 improvement over the
air-glass interface. Finally, if the relative refractive indices
differ by only 0.3%, reflection is reduced to 0.00028%. The above
base value of a refractive index of 1.5 was chosen for simplicity
of illustration, and each of haptic 104 and optic 102 may have any
suitable refractive index, as will be understood to those skilled
in the art.
[0062] Thus, the refractive indices of optic 102 and at least
portions of haptic 104 are preferably equal, or substantially
equal, in order to minimize the reflection discussed above. Note
that haptic 104 and optic 102 may optionally have different
dispersions, wherein the refractive index variation, as a function
of wavelength, may be different for haptic 104 and optic 102.
[0063] Returning now more particularly to FIG. 3, the extension of
arms 212 into optic 102 generally allows more effective transfer of
radial forces along arms 212 to optic 102, since the inner diameter
of inner structure 208 is less than the outer diameter of optic
102. This relatively small "active area" of optic 102, located
inside inner structure 208, allows ocular forces to be distributed
over a smaller peripheral zone about the active area than if the
same force were distributed over a periphery of the outer diameter
of optic 102. Since ocular forces are thus effectively concentrated
over a relatively small area, the pressure near the center of optic
102 is increased, which in turn increases the amount of curvature
change, and thus optical power change, induced for a given amount
of radial force on outer structure 210 and arms 212. As a result,
the limited ciliary muscle or capsular bag force may produce a
greater accommodative power change, i.e., axial translation, of
optic 102. However, avoidance of modification, distortion, or
similar damage to at least the active area during insertion of IOL
100 is thus necessitated for proper performance of optic 102.
[0064] The inner diameter of inner structure 208 is generally
selected to be at least large enough for the active area of optic
102 to provide a change in optical power under scotopic lighting
conditions, such as with a pupil diameter of the eye of 2 to 3 mm,
for example. For example, when IOL 100 is used in the human eye,
the active area is generally sufficiently large if the inner
diameter of inner surface 208 is between 2 and 4 mm, or between 2.5
and 3.5 mm, or 3 mm+/-0.25 mm, for example.
[0065] In some embodiments, the axial thickness of inner structure
208 between arms 212, and/or overlapping proximal ends 214, is
relatively large, for example, to help distribute more radial force
on outer structure 210 to change the shape of the anterior and
posterior surfaces of optic 102. The ratio of the optic center
thickness to the axial thickness of inner structure 208 may be less
than or equal to 2, for example. Greater accommodative power change
in optic 102 may be provided when the ratio of the optic center
thickness to the axial thickness of inner structure 208 is less
than 1.8, or more specifically less than 1.5, for example. Areas of
greater thickness may, as will be understood in light of the
disclosure herein, necessitate less protection by, for example, the
coating and/or film discussed herein throughout, in order to avoid
damage during insertion, for example.
[0066] Inner structure 208 may be a continuous ring and may
generally have a radial thickness that is from 0.1 to 0.2 mm, or
specifically about 0.15 mm+/-0.03 mm, for example. While the
continuous ring form of inner structure 208 may maintain the form
of optic 102 upon deformation during accommodation, a relatively
small radial thickness of inner structure 208 may reduce the
stiffness of inner structure 208 so that a greater percentage of
the radial forces transferred from arms 212 are focused on changing
the shape, and thus the accommodative optical power, of optic
102.
[0067] Outer structure 210 may be broken at predetermined
locations. Arms 212 may be bifurcated or split at distal ends 216
to form openings 218. Of course, in light of the discussion herein
of relative indices of refraction, it may also be preferable to
protect arms 212 during insertion of IOL 100, such as to maintain a
designed-for relative refractive index and to prevent damage that
may cause unwanted reflections, for example. Openings 218 may have
a triangular shape, as shown in the illustrated embodiment.
Alternatively, openings 218 may have other shapes, such as an
oval-shape, for example. Openings 218 may be configured to reduce
the mass of haptic 104, to help direct radial forces towards inner
structure 208, and/or to control the shape of outer structure 210
during accommodation, such as to avoid bending or buckling, for
example.
[0068] Another exemplary optic for use in the present invention is
shown in FIG. 4. FIG. 4 shows a deformable optic 102 with an
exemplary haptic 104, shown in isometric view and removed from the
eye. The view of FIG. 4 shows that haptic 104 extends a full
360.degree. azimuthally around the edge of optic 102.
[0069] The exemplary haptic 104 of FIG. 4 has various segments 402,
or filaments, each of which extends generally in a plane parallel
to the optical axis of the IOL 100. For the exemplary haptic 104 of
FIG. 4, segments 402 are joined to each other at one end, extend
radially outward to contact the capsular bag, and extend radially
inward to contact the edge of optic 102. At the edge of optic 102,
the haptic segments 402 may remain separate from each other, as
shown in FIG. 4, or alternatively some or all segments may be
joined together. Any or all of the width, shape and thickness of
the segments may optionally vary along the length of the segments.
The haptic may have any suitable number of segments, including but
not limited 2, 4, 6, 8, 10, 12, 14, and 16 segments.
[0070] As shown, the region of contact between optic 102 and haptic
104 in FIG. 4 may extend into the edge of optic 102, in a manner
similar to the interface between a bicycle tire and a rim that
holds the tire in place. An exemplary region of contact between
haptic 104 and optic 102 is described and shown in greater detail
in United States Patent Publication 2008/0161913, the entire
disclosure of which is incorporated herein by reference as if set
forth in its entirety.
[0071] Another exemplary haptic 104 and optic 102 is shown in the
isometric illustration of FIG. 5. Exemplary haptic 104 has various
segments or filaments, each of which extends generally radially in
a plane roughly perpendicular to the optical axis of the IOL 100.
For the exemplary haptic 104 of FIG. 5, segments 402 may be joined
to each other at the outer circumference and extend radially inward
to contact the edge of optic 102. Alternatively, segments 402 need
not be joined together at the outer circumference. At locations
other than the outer circumference, haptic segments 402 may remain
separate from each other, as shown in FIG. 5, or alternatively some
or all segments may be joined together.
[0072] The exemplary haptic 104 is then compressed radially, so
that the overall diameter of haptic 104 is reduced. A typical
compression may be on the order of about 1 mm, although more or
less compression may be used. For instance, haptic 104 may be
compressed by a fraction of its diameter, such as a value in the
range of about 0.4% to about 2.0% compression.
[0073] Haptic 104 may engage a portion of the periphery of optic
102 in a region roughly around equator 115 of optic 102. This
exemplary haptic 104 contacts optic 102 in four regions, each
roughly equally spaced apart around equator 115 of optic 102,
although any suitable number of contact portions may be used and
these portions need not be spaced equally apart. Haptic 104
includes a ring, also known as a circumferential ring. The ring has
an inner diameter given by element 113, and an outer diameter given
by element 114. The ratio of inner to outer diameters may vary as a
function of the stiffness of haptic 104.
[0074] For haptic 104 in FIG. 5, the outer diameter 116 of the ring
is the outer portion of haptic 104, and the outer portion of haptic
104 may remain in contact with the capsular bag of the eye during
and after implantation, and such a configuration may be typical for
embodiments of haptic 104, certain of which exemplary embodiments
are discussed herein.
[0075] Alternatively, the annular ring may be contained in the
interior of haptic 104, with arms or filaments that may extend
outward beyond the outer diameter of the ring to contact the
capsular bag. As a further alternative, the inner diameter of the
ring may be the inner diameter of haptic 104, and may contact the
circumference or the equator of optic 102. Such a region of contact
between haptic 104 and optic 102 is described and shown in greater
detail in United States Patent Publication 2008/0161914, the entire
disclosure of which is incorporated herein by reference as if set
forth in its entirety.
[0076] An exemplary dual optic lens in accordance with the present
invention is shown in FIG. 6. FIG. 6 illustrates a rear perspective
of the exemplary dual optic lens. As illustrated, the posterior
portion of lens 300 includes posterior viewing element 318 and
posterior biasing element 320. Posterior biasing element 320
includes a first posterior translation member 322 extending from
the posterior viewing element 318 to the first apex 312, and second
posterior translation member 324 extending from posterior viewing
element 318 to second apex 316. In the illustrated embodiment, the
first posterior translation member comprises right arm 322a and
left arm 322b. Likewise, the depicted second posterior translation
member 324 comprises right arm 324a and left arm 324b. However,
either or both of the first and second posterior translation
members 322, 324 may comprise a single arm or member, or more than
two arms or members.
[0077] Anterior biasing element 308 and posterior biasing element
may be configured symmetrically. As used herein with respect to
biasing elements 308, 320, "symmetric" or "symmetrically" means
that, as the lens system 300 is viewed from the side, first
anterior translation member 310 and first posterior translation
member 322 extend from first apex 312 at substantially equal first
anterior and posterior biasing angles .theta..sub.1, .theta..sub.2
with respect to the edge of a plane which is substantially
orthogonal to the optical axis and intersects first and second
apexes 312, 316, and/or that the second anterior translation member
314 and the second posterior translation member 324 extend from the
second apex 316 at substantially equal second anterior and
posterior biasing angles .theta..sub.3, .theta..sub.4 with respect
to the same plane. Alternative or asymmetric configurations of
biasing elements are, of course, possible.
[0078] Both anterior viewing element 306 and posterior viewing
element 318 may comprise optic 102 having refractive (and
diffractive) power. In alternative embodiments, one or both of
anterior and posterior viewing elements 306, 318 may comprise optic
102 with a surrounding or partially surrounding perimeter members.
In still further variations, one of viewing elements 306, 318 may
comprise a zero-power lens or a transparent member.
[0079] Retention portion 326 may be coupled to anterior portion
302, preferably at anterior viewing element 306. Retention portion
326 may include first retention member 328 and second retention
member 330, although in alternative embodiments retention portion
326 may be omitted altogether, or may comprise only one retention
member or more than two retention members.
[0080] Posterior portion 304 may include distending portion 332,
attached to posterior viewing element 318. Distending portion 332
may include first distending member 334, which in turn may include
fixed end 334a, free end 334b opposite fixed end 334a and opening
334c. Distending portion 332 also comprises second distending
member 336 with fixed end 336a, free end 336b and opening 336c.
Distending portion 332 may be omitted altogether, or may comprise a
single distending member or more than two distending members.
[0081] Anterior and posterior biasing elements 308, 320 may
function in a springlike manner to permit anterior viewing element
306 and posterior viewing element 318 to move relative to each
other generally along the optical axis. Biasing elements 308, 320
bias the viewing elements 306, 318 apart so that elements 306, 308
separate to the accommodated state shown in FIG. 6. Thus, in the
absence of any external forces, the viewing elements are at their
maximum separation along the optical axis. Viewing elements 306,
318 of lens system 300 may be moved toward each other, such as in
response to a ciliary muscle force of up to 2 grams, to provide an
unaccommodated position by applying appropriate forces upon
anterior and posterior portions 302, 304 and/or apices 312,
316.
[0082] When the lens system 300 is implanted in capsular bag 20,
the above described biasing forces cause lens system 300 to expand
along the optical axis so as to interact with both the posterior
and anterior aspects of capsular bag 20. Such interaction occurs
throughout the entire range of motion of ciliary muscle 22. At one
extreme, ciliary muscle 22 may relax and zonules 24 pull capsular
bag 20 radially so as to cause bag 20 to become more disk shaped.
The anterior and posterior sides of bag 20, in turn, apply force to
anterior and posterior portions 302, 304, thereby forcing viewing
elements 306, 318 of optic 102 toward each other into the
accommodated position. At the other extreme, ciliary muscle 22 may
contract and zonules 24 move inwardly to provide slack in capsular
bag 20 and allow bag 20 to become more football-shaped. The slack
in bag 20 may be taken up due to the biasing-apart of anterior and
posterior viewing elements 306, 318. As the radial tension in bag
20 is reduced, viewing elements 306, 318 move away from each other
into an accommodated position. As the distance between anterior and
posterior viewing elements 306, 318 is varied, the focal length of
the lens system 300 changes accordingly. Such an optic is described
and shown in greater detail in United States Patent Publication
2006/0259139, and U.S. Pat. No. 7,118,596, the entire disclosures
of which are incorporated herein by reference as if set forth in
the entirety.
[0083] However, damage to optic 102, such as during implantation,
or adverse effects caused by implantation to capsular bag 20,
ciliary muscle 22, and/or zonules 24 may negate the anticipated
accommodation and/or optical properties of the implanted lens.
Further, because each of the aforementioned lens systems may, as
discussed, be implanted via the surgical techniques discussed, each
such lens or lens system may, upon implantation, suffer from the
aforementioned issues associated with surgical insertion, namely
damage to one or more of the referenced aspects of optic 102 during
implantation, damage to one or more aspects of haptic 104 during
implantation, or swelling, infection, or similar adverse side
effects, such as to capsular bag 20 and/or ciliary muscle 22, that
may cause underperformance of the implanted lens system.
[0084] Referring now to FIG. 7, there is shown a coating formed on
optic 102 of the type discussed in the exemplary embodiments of
FIGS. 3-6 to ameliorate certain of the surgical issues discussed,
according to an aspect of the present invention. As illustrated,
optical assembly 700 may include optic 102, such as those optics
described hereinabove, and coating 750. Coating 750 may include any
number of layers, such as one, two, three, five, or more layers.
One or more of the layers may vary in thickness, such as to
differentially protect various portions of optic 102 and/or haptic
104 that are of varied thickness, as referenced above with respect
to FIG. 3. Coating 750, as shown in the exemplary embodiment of
FIG. 7, may include first layer 720 and second layer 730 for
coating the anterior surface of optic 102. According to an
embodiment, an IOL may have multiple coating layers and after
implantation into to an eye, one or more layers may be removed
leaving one or more layers on the IOL either permanently,
temporarily for degradation, or a combination thereof.
[0085] Referring now additionally to FIG. 8, there shown a coating
750 formed on optic 102. Coating 750 on optic 102 may be on the
anterior of the optic (shown in FIG. 7), posterior of the optic
(shown in FIG. 8), or on both surfaces of the optic. Coating 750
may be a film deposition of a permanent or temporary material. A
temporary material may degrade away, dissolve, or the like, in some
defined period of time under in-use conditions, such as in less
than six weeks, less than two weeks, less than one week, in a few
days and/or in a few hours, for example. Degradation may occur over
a predefined time period, from as little as minute to as long as
three years depending upon the design of the film, the chemical
properties of the film, the medicinal attributes of the film, the
purpose of the film, patient healing time, physician preferences,
industry standards, and/or the like. Different layers of coating
750 may degrade over different time periods, such as to provide
timed release of different medicines impregnated within coating
750, such as steroidals, anti-infectants, or the like, which
medicines may be differently provided within each of the multiple
layers for release at different times upon degradation or
dissolution of the above layer, for example.
[0086] Coating 750 may include areas of variable thickness in order
to target greater or lesser protection, or of different time
release aspects, to different areas of the lens, as referenced
hereinabove. For example, such a variable thickness in coating 750
may for targeting the features of coating 750, such as the
medicinal features discussed above, to select portions of optic
102, of haptic 104 or of the eye in order to optimize the benefits
provided by those features.
[0087] Coating 750 may be inert or active. An inert coating may
take the form of a coating that is not chemically reactive. An
inert coating may also be conditionally inert. For example, coating
750 may be inert under ordinary conditions, but may become reactive
under certain conditions, such as under high pressure, high
temperature, or in the presence of a catalyst, for example.
[0088] An active coating may include an active material, such as
the medicinal material described hereinabove. An active coating may
provide implantation enhancements, such as an optically active
additive to be activated upon implantation of optic 102 into the
eye, or the like. Thus, the optically active additive may include
an organic or inorganic material which, when added to coating 750,
makes coating 750 reactive to certain catalysts, such as ultra
violet light or colored light, for example. Such additive may prove
useful in inspection of optic 102 before or during implantation, or
to ensure that coating 750 has been completely removed or
completely dissolved, for example.
[0089] Coating 750 may be applied, such as via adhesion,
impregnation, contact force association, or the like, to optic 102,
haptic 104, or both optic 102 and haptic 104. Further, the
constituents of coating 750 may be different over optic 102 and
haptic 104, such as due to the different properties, thicknesses,
or mechanical features of optic 102 and haptic 104. Similarly, the
constituents or thickness or number of layers of coating 750 may
vary as between, or within, optic 102 and/or haptic 104. For
example, because haptic 104 may be mechanically less pliable than
optic 102, haptic 104 may have coating 750 of high lubricity, such
as in order to aid in passing the lens, and particularly the stiff
haptic 104, through an injection tool. Moreover, in this exemplary
embodiment, coating 750 on optic 102 may not be high in lubricity,
but rather may be thicker and multilayered, such as in order to
better protect the more delicate nature of optic 102, and/or to
deliver medication via one of the layers of coating 750 upon optic
102.
[0090] Coating 750 may protect optic 102, and/or haptic 104, and
ideally may not degrade optic 710. Coating 750 may, for example,
address degradation from the folding/unfolding issues associated
with the insertion process, as discussed with respect to FIG. 2,
such as by providing lubrication to aid in the folding/unfolding.
Further, coating 750 may aid the delivery of optic 102 through an
insertion tool, such as by providing lubricity as needed, and/or by
reducing friction and tackiness, for example.
[0091] Coating 750 may be a thin film, such as to preclude coating
750 from substantially affecting the optical properties of the IOL
prior to dissolving completely, for example. The thickness of the
film may be on the order of 1-50 nm, in the range of 1-50 microns,
or in the range of 1 to 5 angstroms, for example. Coating 750 may
include layer(s) selected from a class of materials that include
biodegradable polymers, such as polylactic acid and poly-glycolic
acid, for example. As used herein, biodegradable polymers include
all polymers and like materials that are biocompatible and that may
degrade or dissolve in a predetermined amount of time, such as from
days to years, for example. Biodegradable polymers may be
impregnated with the aforementioned medicinal substance, such as a
steroid, to treat post operative inflammation, or to reduce or
prevent anterior capsular opacification/posterior capsule
opacification, or to reduce intra-ocular pressures, for
example.
[0092] The film may include a color or texture to aid in the
removal of coating 750 from the lens. Further, because the thin
film may adhere to the lens via surface tension, adhesion, or other
physical forces during the insertion process, certain steps for
removal of the thin film may be performed. For example, irrigation
after phacoemulsification may lift coating 750 from optic 102,
because silicone is less tacky when wet. Additionally or
alternatively, visco-elastic features may be included in coating
750 to create pressure differences to lift coating 750. Such a
visco-elastic feature may include any dispersive or cohesive
elements in coating 750 to aid removal.
[0093] Coating 750 may be an opaque film, such as to aid in the
insertion process. For example, coating 750 may provide a doctor a
visual cue to aid in the insertion process, and/or to aid in the
removal of coating 750. An opaque coating 750 may, in exemplary
embodiments, dissolve, or be otherwise removed, before use of the
lens, in part because such opacity may prohibit vision through the
lens.
[0094] Referring now to FIG. 9, there is shown optic 102 with a
film coating the top surface thereof, according to an aspect of the
present invention. As illustrated in FIG. 9, optic 102 is covered
with mechanical film 920, rather than chemical coating 750. Film
920 may have the properties and/or aspects of coating 750, as
discussed above, and may be mechanically removable from the lens
during implantation, or may dissolve substantially simultaneously
with implantation, for example.
[0095] Film 920 may have included thereon, as a part thereof, or
attached thereto, at least one tab 940 (FIG. 9 shows two exemplary
tabs 940, 950). Tab 940 may be an inert film that initially at
least partially covers optic 710, such as to protect at least a
part of the surface of optic 710. Tabs 940, 950 may readily enable
film 920 to be removed after, or during, insertion of optic 710
into the eye. Such tab(s) 940, 950 may thus include coloring to
enable the tab to be more clearly visible during the surgical
process. Tabs 940, 950 may match the area of the removal tool.
Further, tabs 940, 950 and film 920 may preferably be small to
remove through the surgical incision discussed above.
[0096] Examples of material(s) for removable film 920 include one
or more of the following: polyethylene terephthalate (PET),
polytetrafluoroethylene (PTFE), polystyrene, polyethylene,
polypropylene, polymethylmethacrylate, ethyl acrylate, ethyl
methacrylate, 2,2,2-trifluoroethyl, and the like. In an embodiment,
the film may include a copolymer of ethyl acrylate, ethyl
methacrylate, and 2,2,2-trifluoroethyl methacrylate, cross-linked
with ethylene glycol dimethacrylate. Incorporated within or under
film 920 may be adherents, medications, or the like, as discussed
hereinabove with respect to coating 750. Further, film 920 may be a
type of coating as discussed herein. Coating 750 and film 920 may
additionally be employed together, for example. As such, film 920
may provide protection, may allow for drug delivery for medications
in coating 750 that may be reactive if not sealed from the air, may
allow for coating 750 that does not provide protection of the
optic, or may allow for coating that is sensitive during the
surgical procedure, for example.
[0097] Film 920 may also be included on the haptic 104. Such film
920 may provide similar benefits to coating 750. For example, film
920 may differ as to the properties or thickness as between a film
on optic 102 and haptic 104. Separate films 920 may be upon optic
102 and haptic 104. Separate coatings 750 independent from or
associated with film 920 may deliver two stage medicinals, such as
wherein one medicinal stage is on the optic, and the second stage
is on the haptic. When placed together in the eye, the multi-part
or multi-stage medicinal may combine to provide desired medicinal
characteristics to the patient.
[0098] Additionally or alternatively, coating 750 and/or film 920
may be provided on the insertion tools discussed hereinthroughout.
This coating 750 or film 920 may be similar to that described above
for placement on the lens. Coating 750 or film 920 may include a
broader range of potential materials, in part because mechanical,
legal or technical requirements for coating surgical tools may be
less stringent than those for coating an implanted optic. In
particular, coatings on the tools may not be required to dissolve
or be removed. Coating 750 or film 920 may reduce impacts of the
tools on the lens and subsequent lens damage, and/or may increase
the lubricity of the tools, such as to thereby reduce friction
and/or tackiness of the lens during the insertion procedure.
[0099] FIG. 10 illustrates a method 1000 of protecting a lens
during surgical implantation, and/or of providing benefits to the
implantation process. Method 1000 may include providing a
protective coating or film on an optic at step 1010. Included
within this film or coating, or underlying or overlaying same, may
be an impregnating substance, such as medication, as discussed
herein throughout. Method 1000 may further include insertion of the
optic into an eye at step 1020. This insertion may include
folding/unfolding, injecting, and the like, as described herein.
Method 1000 may further include removal of the protective film or
coating at step 1030. This removal may include physical removal
during the surgical procedure, or may include dissolving or similar
chemical processing, related to or unrelated to the surgical
procedure, for example.
[0100] FIG. 11 illustrates a method 1100 of protecting a lens
during surgical implantation, and/or of providing benefits to the
implantation process. Method 1100 may include providing one or more
protective coatings or films on an optic or haptic at step 1110.
Included within this coating, film, or underlying or overlaying
same, may be an impregnating substance, such as medication, as
discussed herein throughout. Method 1100 may further include
insertion of the lens into an eye at step 1120. This insertion may
include folding/unfolding, injecting, and the like, as described
herein. Method 1100 may further include removal of one or more of
the protective coatings or films at step 1130. This removal may
include physical removal during the surgical procedure, and/or may
include dissolving or similar chemical processing, related to or
unrelated to the surgical procedure, for example.
[0101] Although the invention has been described and pictured in an
exemplary form with a certain degree of particularity, it is
understood that the present disclosure of the exemplary form has
been made by way of example, and that numerous changes in the
details of construction and combination and arrangement of parts
and steps may be made without departing from the spirit and scope
of the invention as set forth in the claims hereinafter.
* * * * *