U.S. patent application number 11/438812 was filed with the patent office on 2006-09-21 for capsular intraocular lens implant having a refractive liquid therein.
This patent application is currently assigned to Advanced Medical Optics, Inc.. Invention is credited to Randall Woods.
Application Number | 20060212116 11/438812 |
Document ID | / |
Family ID | 32107051 |
Filed Date | 2006-09-21 |
United States Patent
Application |
20060212116 |
Kind Code |
A1 |
Woods; Randall |
September 21, 2006 |
Capsular intraocular lens implant having a refractive liquid
therein
Abstract
An intraocular lens having a light-transmitting optic (32, 94a,
94b, 142, 216) comprised of a synthetic light-refractive material
(40, 102) operably coupled with a flexible optic positioning member
(34, 62, 74, 84, 100, 210) to refract light onto the retina in
order to correct refractive errors in the eye (10). The refractive
material has an index of refraction of from about 1.36 to 1.5 or
higher. The optic positioning member (34, 62, 74, 84, 100, 210) is
constructed of a flexible synthetic resin material such as
polymethylmethacrylate and permits focusing upon objects located
near to and far from the viewer. The optic (32, 94a, 94b, 142, 216)
of the present invention possess greater refractive capability than
optics conventionally used in IOL construction, and permits retinal
receipt of the image being viewed in order to correct refractive
errors.
Inventors: |
Woods; Randall; (Prescott,
AZ) |
Correspondence
Address: |
ADVANCED MEDICAL OPTICS, INC.
1700 E. ST. ANDREW PLACE
SANTA ANA
CA
92705
US
|
Assignee: |
Advanced Medical Optics,
Inc.
Santa Ana
CA
|
Family ID: |
32107051 |
Appl. No.: |
11/438812 |
Filed: |
May 22, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
10280918 |
Oct 25, 2002 |
|
|
|
11438812 |
May 22, 2006 |
|
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Current U.S.
Class: |
623/6.13 ;
623/6.34; 623/6.37 |
Current CPC
Class: |
A61F 2/1635 20130101;
A61F 2250/0053 20130101; A61F 2/1648 20130101; A61F 2002/1682
20150401; A61F 2210/0014 20130101 |
Class at
Publication: |
623/006.13 ;
623/006.34; 623/006.37 |
International
Class: |
A61F 2/16 20060101
A61F002/16 |
Claims
1. An implantable intraocular lens, comprising: an optic formed
from a resilient, shape-retaining synthetic material and responsive
to ciliary body movement in order to change the shape of the optic,
a positioning member operably coupled with the optic comprising
anterior and posterior segments. a rigid optic opposed to the
resilient optic.
2. The lens of claim 1, the rigid optic formed of synthetic resin
material selected from the group consisting of the silicones,
acrylates, and mixtures thereof.
3. The lens of claim 1, the optics being substantially between and
captively retained by the segments.
4. The lens of claim 3, the lens including an optic defining
protrusion extending beyond adjacent outer edges of the margins of
the anterior segment.
5. The lens of claim 4, the rigid optic being supported by the
posterior segment.
6. The lens of claim 1, the material being formed of a compound
comprising silicone.
7. The lens of claim 1, the material being a liquid or a gel.
8. An implantable intraocular lens, comprising: an optic formed
from a resilient, shape-retaining synthetic material and responsive
to ciliary body movement in order to change the shape of the optic;
a positioning member operably coupled with the optic comprising
opposing anterior and posterior arcuate wall segments; and a
flexible bag comprising a cavity filled with a resilient refractive
material; the opposing arcuate wall segments defining opposing
anterior and posterior optic surfaces of the optic.
9. The lens of claim 8, the material having an index of refraction
of at least about 1.36.
10. The lens of claim 8, the material being formed of a
biologically inert material.
11. The lens of claim 8, the material being formed of a compound
comprising silicone.
12. The lens of claim 8, the material being a liquid or a gel.
13. The lens of claim 8, the material having an elastic memory.
14. The lens of claim 8, the bag further comprising a fill aperture
with a plug therein closing the aperture.
15. An implantable intraocular lens, comprising: a resilient
light-transmitting optic formed of a synthetic light-refractive
material and configured to change shape in response to ciliary body
movement; a flexible positioning member coupled with the optic and
configured for changing the shape of said lens in response to
ciliary body movement; and a capsule with a liquid or a gel
material therein, the capsule comprising an anterior section and a
posterior section.
16. The lens of claim 15, the material being formed of a compound
comprising hydrocarbons.
17. The lens of claim 15, the material being formed of a compound
comprised of silicone.
18. The lens of claim 15, the lens further comprising a fixed optic
formed of synthetic resin material.
19. The lens of claim 15, each of the sections individually having
a wall thickness of from about 0.0005 to 0.025 mm.
Description
BACKGROUND OF THE INVENTION
[0001] 1. Field of the Invention
[0002] The present invention relates to an accommodating
intraocular lens implant (IOL), containing a refractive material
therein, for surgical replacement of the natural crystalline lens
to treat refractive errors in the human eye.
[0003] 2. Description of the Prior Art
[0004] Refractive errors in the eye affect one's ability to
properly focus an image upon the retina due to a change in the
refractive medium of the eye, e.g., the cornea, the natural
crystalline lens, or both. The refractive errors pertinent to this
application include myopia, hyperopia, and presbyopia. A myopic
lacks the ability to focus an image located at a distance from the
viewer because the cornea has become elongated, thereby increasing
the eye's focal length. A hyperopic lacks the ability to focus on
objects located near the viewer because the cornea is not elongated
enough or is too flat, and cannot refract light properly upon the
retina. Instead, light entering the eye does not bend sharply
enough to focus upon the retina. In contrast to myopia wherein the
image is brought to focus in front of the retina, hyperopia causes
the image to focus behind the retina. Presbyopia is another type of
refractive error which results in the inability of the eye to focus
because of hardening of the natural crystalline lens. The hardened
natural crystalline lens prevents focusing upon objects located
near to the viewer. Presbyopia occurs in conjunction with myopia or
hyperopia.
[0005] The known treatment varies with the type of refractive error
to be corrected. Each of the refractive errors may be corrected by
external spectacle lenses. Also, refractive surgery is known in the
art for correcting the aforementioned refractive errors, and
includes radial keratotomy, astigmatic keratotomy, photoreflective
keratectomy, and laser in situ keratomileusis (LASIK). Each of the
refractive surgical methods mentioned above involve making multiple
incisions into the cornea in order to reshape it. Possible side
effects of refractive surgery include irregular astigmatism,
infection, or haze formation which could result in permanent
changes in the cornea and possible loss of best-corrected visual
acuity. A possibility of under or over correction also exists with
the aforementioned refractive surgeries. Furthermore, none of these
refractive surgeries can be used to correct all of the
above-referenced refractive errors.
[0006] Various IOLs have been used to treat cataracts. The first
implant of an IOL within the eye to treat cataracts occurred in
1949. This experimental surgery attempted to place the replacement
lens in the posterior chamber of the eye behind the iris. Problems
such as dislocation after implantation forced abandonment of this
approach, and for some period thereafter IOLs were implanted in the
anterior chamber of the eye.
[0007] Others returned to the practice of inserting the IOL in the
area of the eye posterior to the iris, known as the posterior
chamber. This is the area where the patient's natural crystalline
lens is located. When the IOL is located in this natural location,
substantially normal vision may be restored to the patient, and the
problems of forward displacement of the vitreous humor and retinal
detachment encountered in anterior chamber IOLs are less likely to
occur. IOLs implanted in the posterior chamber are disclosed in
U.S. Pat. Nos. 3,718,870, 3,866,249, 3,913,148, 3,925,825,
4,014,049, 4,041,552, 4,053,953, and 4,285,072. None of these IOLs
have accommodation capability.
[0008] IOLs capable of focusing offered the wearer the closest
possible substitute to the natural crystalline lens. U.S. Pat. No.
4,254,509 to Tennant discloses an IOL which moves in an anterior
direction upon contraction of the ciliary body and which is located
anterior to the iris. Although the Tennant IOL claims to possess
accommodation capabilities, it presents the same disadvantages as
other anterior chamber lenses. U.S. Pat. No. 4,253,199 to Banko
approaches the problem of providing a focusable IOL in a different
manner, by providing a replacement IOL of deformable material
sutured to the ciliary body. This IOL functions in much the same
manner as the natural crystalline lens, but may cause bleeding
because it requires sutures.
[0009] U.S. Pat. No. 4,409,691 to Levy claims to provide an
accommodating IOL positioned within the capsule. This IOL is
located in the posterior area of the capsule and is biased toward
the fovea or rear of the eye. The Levy IOL is deficient because it
requires the ciliary muscle to exert force through the zonules on
the capsule in order to compress the haptics inward and drive the
optic forward for near vision. However, the ciliary muscles do not
exert any force during contraction because the zonules, being
flexible filaments, exert only tension, not compression on the
capsule. The natural elasticity of the IOL causes the capsule to
become more spherical upon contraction of the ciliary muscle. Thus,
there is no inward force exerted on the capsule to compress the
haptics of the Levy IOL, and therefore accommodate for near vision.
Even if such force were somehow available, the Levy IOL's haptics
are loaded inward when accommodating for near vision. Since
accommodation for near vision is the normal status of the capsule,
the Levy IOL's haptics are loaded, reducing the fatigue life of the
springlike haptics.
[0010] U.S. Pat. No. 5,674,282 to Cumming is directed towards an
allegedly accommodating IOL for implanting within the capsule of an
eye. The Cumming IOL comprises a central optic and two plate
haptics which extend radially outward from diametrically opposite
sides of the optic and are movable anteriorly and posteriorly
relative to the optic. However, the Cumming IOL suffers from the
same shortcomings as the Levy IOL in that the haptics are biased
anteriorly by pressure from the ciliary bodies. This will
eventually lead to pressure necrosis of the ciliary body.
[0011] Finally, U.S. Pat. No. 4,842,601 to Smith discloses an
allegedly accommodating IOL having anterior and posterior members
which urge against the anterior and posterior walls of the capsule.
The muscular action exerted on the capsule will cause the IOL to
flatten, thereby changing the focus thereof. The Smith IOL is
formed of first and second plastic lens members connected to one
another adjacent their peripheral edges so as to provide a cavity
therebetween. The connection between the lens members is
accomplished by way of a U-shaped flange on the first member which
forms an inwardly facing groove for receiving an outwardly extended
flange on the second member. The Smith IOL is faulty because the
structure of the lens members makes surgical implantation thereof
extremely difficult to accomplish, even for highly skilled
surgeons. Furthermore, the Smith IOL requires sutures which
increases the risk of bleeding.
[0012] The IOLs discussed above replaced the opaque crystalline
lens symptomatic of cataracts through a small incision in the iris
and anterior wall of the biological capsule. The IOLs for the
treatment of cataracts differed from the present invention in that
the present invention utilizes a highly refractive material to
compensate for defects in the eye's natural refractive media, e.g,
the cornea and the natural crystalline lens.
[0013] There is a great need in the art for a lightweight IOL which
can be used to correct a variety of refractive errors in
conjunction with other eye defects which require replacement of the
natural crystalline lens, such as cataracts. This IOL should be
readily insertable into the capsule and should last for a
substantial number of years without damaging any of the eye
components.
SUMMARY OF THE INVENTION
[0014] The IOL of the present invention addresses this need because
it provides a lightweight accommodating IOL, containing a highly
refractive material therein, which is safe for long term use in an
eye. The present invention presents a significant advance in the
art because it provides an IOL for the safe and effective treatment
of refractive errors in combination with other defects such as
cataracts.
[0015] In more detail, the IOL comprises a resilient optic formed
of a highly refractive material operably coupled to a flexible
optic positioning member to change shape in response to ciliary
body movement, i.e., contraction and retraction of the ciliary
body. When the ciliary body relaxes or retracts, it causes the
zonules to elongate and exert a tensional pull upon the IOL. Thus,
the IOL becomes discoid in shape and allows the viewer to focus
upon objects located at a distant therefrom. Similarly, when the
ciliary body contracts, it becomes thicker and causes the zonules
to ease the tensional pull. Thus, the IOL becomes spheroid in shape
and allows the viewer to focus upon objects located near to the
viewer. As noted above, the optic is formed of refractive material
that has an index of refraction of from about 1.36 to 1.5 or higher
(e.g., hydrocarbon oil, silicone oil, or silicone gel). In one type
of IOL in accordance with the invention, use is made of a
pre-formed capsule having a thin, continuous wall wherein the
refractive material is enveloped.
[0016] The optic may be coupled with various optic positioning
members commonly used in IOL construction depending upon the user's
eyesight. The optic may be positioned within the capsule of the eye
such that the anterior surface of the optic faces either the
anterior or the posterior portion of the eye. When the optic is
positioned to face the posterior portion of the eye, the optic will
vault posteriorly in response to contraction of the ciliary body.
However, the change in the radius of curvature of the optic will
counteract the effects of the negative accommodation, i.e.,
movement of the optic posteriorly. The resiliency of the optic
permits a small change in radius of curvature which, when coupled
with the relatively high index of refraction of the refractive
material, results in an optic having greater light-bending
properties than conventional optics.
[0017] Another preferred embodiment presents a resilient optic and
a posterior rigid optic both operably coupled on opposed sides of
an optic positioning member to change shape in response to ciliary
body movement. The optics are positioned on opposite segments of
the optic positioning members such that they share the same focal
point. A similar embodiment transposes the structure described
immediately above by implanting the IOL within the eye such that
the rigid optic is the anterior optic and the resilient optic is
the posterior optic.
[0018] Another embodiment of the present invention presents two
optics positioned on the same segment of the optic positioning
member wherein a rigid optic surrounds a resilient optic. Another
embodiment similar to the embodiment discussed immediately above,
presents two optics positioned on the same segment of the optic
positioning member wherein a resilient optic surrounds a rigid
optic. In this embodiment, the resilient optic changes shape in
response to ciliary body movement while the rigid optic essentially
retains its shape.
[0019] Yet another preferred embodiment of the IOL of the present
invention includes an optic positioning member comprised of an
enclosed flexible bag having resilient fill material therein. The
enclosed flexible bag presents an anterior segment and an opposed
posterior segment, each having an optic. The optic positioning
member is pre-formed to present opposed optic surfaces, hence, the
optics are integral with the optic positioning member. The
resilient fill material is comprised of the same refractive
material used in the above-referenced resilient optic construction.
This embodiment also functions similarly to the IOLs discussed
above because the anterior optic surface moves anteriorly and the
posterior optic surface moves posteriorly in response to
contraction of the ciliary body. The optic surfaces of the flexible
bag optic positioning member present a small change in the radius
of curvature (e.g., 5-4.6 mm) from the accommodated to
disaccommodated shapes, coupled with high refractive power thereby
permitting retinal receipt of an observed image.
[0020] Another embodiment of the present invention is similar to
the embodiments having opposed optics, described above, except that
the optic positioning member of this embodiment does not completely
house the refractive material. The refractive material of this IOL
protrudes outward to extend beyond the outer margins of the
anterior segment through an opening in the optic positioning member
to define a resilient optic. The posterior segment of the optic
positioning member supports a second posterior rigid optic
positioned in opposition to the resilient optic. The rigid optic is
constructed of the same material as the optic positioning member.
The resilient material is captively retained by the segments of the
optic positioning member, but also directly contacts the biological
capsule. Contraction of the ciliary body transfers sufficient force
to the resilient and protuberant refractive material which in turn
defines an optic operable to change shape in response to ciliary
body movement. This embodiment may be constructed without the
addition of a second opposed rigid optic depending upon
identifiable surgical needs.
BRIEF DESCRIPTION OF THE DRAWINGS
[0021] FIG. 1 is a vertical sectional view showing an IOL of the
invention within the capsule of an eye, with the eye focused on an
object distant from the viewer;
[0022] FIG. 2 is a vertical sectional view of a preferred IOL of
the invention;
[0023] FIG. 3 is an anterior perspective view of the IOL of FIGS. 1
and 2;
[0024] FIG. 4 illustrates another embodiment of the invention;
[0025] FIG. 5 illustrates another embodiment of the invention;
[0026] FIG. 6 illustrates another embodiment of the invention;
[0027] FIG. 7 is a vertical sectional view of the IOL of FIG. 3
showing the optic bonded to the anterior surface of the anterior
segment of the IOL of the present invention;
[0028] FIG. 8 is a vertical sectional view of the IOL of FIG. 3
showing the optic bonded to the posterior surface of the anterior
segment of the IOL of the invention;
[0029] FIG. 9 is a vertical sectional view of another embodiment of
the invention showing the optic located at the anterior segment of
the IOL and a posterior rigid optic at the posterior segment of the
IOL;
[0030] FIG. 10 is a vertical sectional view of the IOL of FIG. 9
positioned within the eye, with the optic located at the posterior
segment of the IOL and a rigid optic at the anterior segment;
[0031] FIG. 11 is a vertical sectional view of a preferred IOL of
the invention within the capsule of an eye, with the eye focused on
an object distant from the viewer;
[0032] FIG. 12 is a view similar to that of FIG. 11, but
illustrating the IOL in an accommodated position owing to
contraction of the ciliary body;
[0033] FIG. 13 is a plan view of a preferred IOL of the
invention;
[0034] FIG. 14 is a vertical sectional view taken along line 14-14
of FIG. 13; and
[0035] FIG. 15 is a greatly enlarged fragmentary of the IOL of
FIGS. 11-14;
[0036] FIG. 16 is a vertical sectional view similar to that of
FIGS. 7-10, but illustrating the optic constructed without an
enveloping capsule;
[0037] FIG. 17 is a vertical sectional view of another embodiment
of the present invention, illustrating a resilient optic surrounded
by a rigid optic;
[0038] FIG. 18 is a vertical sectional view of another embodiment
of the present invention, showing an IOL of the invention within
the capsule of an eye, with the eye focused on an object located at
a distance from the viewer; and
[0039] FIG. 19 is a view similar to that of FIG. 18, but
illustrating the IOL in an accommodated position owing to
contraction of the ciliary muscle;
[0040] FIG. 20 is a vertical sectional view showing an IOL of the
invention within the capsule of an eye, with the optic positioned
posteriorly;
[0041] FIG. 21 is a view similar to that of FIG. 20, but
illustrating the IOL in a disaccommodated position owing to
retraction of the ciliary muscle; and
[0042] FIG. 22 is a vertical sectional view of another embodiment
of the IOL of the present invention positioned within the capsule
of the eye.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0043] Referring now to the drawings, the present invention is in
the form of an IOL for surgical replacement of the natural
crystalline lens in the treatment of refractive error in the human
eye. FIG. 1 shows the various components of the human eye 10
pertinent to this invention. Briefly, the eye 10 includes an
anterior portion 12 and a posterior portion 14. The anterior
portion 12 of the eye 10 is covered by a cornea 16 which encloses
and forms an anterior chamber 18. The anterior chamber 18 contains
aqueous fluid and is bounded at the rear by an iris 20. The iris 20
opens and closes to admit appropriate quantities of light into the
inner portions of the eye 10. The eye 10 also includes a capsule 22
which ordinarily contains the natural crystalline lens (which would
be located at numeral 24 in the natural, unmodified eye). The eye
10 includes a ciliary muscle or body 26 having zonular fibers 28
(also referred to as zonules) which are attached to the eye 10. The
vitreous humor 30 is located posterior to the capsule 22 and
anterior to the retina (not pictured). The vitreous humor 30
contains vitreous fluid.
[0044] Most of the light entering the eye 10 is refracted at the
air-cornea interface. The cornea 16 has an index of refraction of
1.37, and is largely responsible for refracting light into the eye
10. The light then slightly diverges in the fluid-filled anterior
chamber 18 which has an index of refraction close to that of water,
e.g., approximately 1.33, and travels to the natural crystalline
lens 24. The natural crystalline lens 24 is a biconvex structure
having an index of refraction of 1.4 at its center and an index of
refraction of 1.38 at its outer portion. Next to the cornea 16, the
natural crystalline lens 24 is responsible for refracting much of
the light entering the human eye 10. The anterior portion of the
natural crystalline lens 24 converges light onto its posterior
portion where light is then diverged. It is at this point, that the
image being viewed is inverted. The inverted image (or light) then
travels into the vitreous humor 30 and through the vitreous fluid.
The vitreous fluid has an index of refraction close to that of
water, e.g. 1.33. After the inverted image travels through the
vitreous humor 30, it is brought to focus upon the retina. The
retina is responsible for relaying electric signals to the optic
nerve. The optic nerve then carries the message to the brain which
translates the inverted image into its upright position.
[0045] Ocular adjustments for sharp focusing of objects viewed at
different distances are accomplished by the action of the ciliary
body 26 on the capsule 22 and natural crystalline lens 24 through
the zonules 28. The ciliary body 26 contracts, allowing the capsule
22 to return to a more spherical shape for viewing objects near to
the viewer. When the ciliary body 26 retracts, the ciliary body 26
pulls on the zonules 28 to make the capsule 22 more discoid thus
permitting objects at a distance to be viewed in proper focus.
(FIG. 1) To summarize, when the eye 10 focuses, the capsule 22
changes shape to appropriately distribute the light admitted
through the cornea 16 and the iris 20.
[0046] Referring now to FIGS. 1-22, an IOL in accordance with the
invention comprises an optic 32 operably coupled to an optic
positioning member and implanted within the capsule 22 of the human
eye 10. The IOL changes shape in response to ciliary body 26
movement. As previously noted, the optic 32 of the present
invention is formed of a highly refractive material. The refractive
material has an index of refraction of from about 1.36 to 1.5 or
higher. Examples of preferred refractive materials include silicone
oil, hydrocarbon oil, and more preferably silicone gel (available
from Nusil Technology). When the refractive material used is a gel,
the gel may be pre-formed into the desired optic shape and adhered
onto the optic positioning member without encapsulating it.
[0047] The optic 32 may be utilized in a number of ways in a
variety of optic positioning members. The optic positioning members
discussed herein are preferably formed of any appropriate
biologically inert material conventionally used in IOL construction
(e.g., elastic, synthetic resin materials). Examples of suitable
materials include acrylates (such as polymethylmethacrylates),
silicones, and mixtures of acrylates and silicones. It is
contemplated that mixtures of silicones and acrylates comprise both
chemical mixtures, such as silicone-acrylate blends, and various
combinations of silicones and acrylates employed to construct the
lens. It is particularly preferred that the optic positioning
members according to the invention be constructed of a material
having an elastic memory (i.e., the material should be capable of
substantially recovering its original size and shape after a
deforming force has been removed). An example of a preferred
material having elastic memory is MEMORYLENS (available from Mentor
Ophthalmics in California).
[0048] The preferred embodiments of the IOL of the instant
invention discussed immediately below demonstrate the variety of
optic positioning members that may be operably coupled with the
inventive optic to correct refractive errors in the eye. The terms
rigid optic and resilient optic are used herein as relative terms
to one another. For instance, a rigid optic may be any optic that
is less resilient than the resilient optic of the present
invention, even though the rigid optic may be more resilient than
another rigid optic. The optics of the present invention may be
made of varying degrees of resiliency and rigidity depending upon
the materials used, therefore, the terms rigid and resilient should
not be used as limiting terms other than to convey a specific
relationship between two optics within the scope of this
invention.
The IOL of FIGS. 1-3 [IOL 61]
[0049] The optic 32 presents a convex anterior surface 36 and a
planar posterior surface 38 (hereinafter plano-convex). Although
the optic 32 is illustrated as plano-convex, the size and shape of
the optic 32 may be varied depending upon the user's eyesight. The
optic 32 is composed of a refractive material 40 that is enveloped
within a pre-formed capsule 42 formed of a thin continuous wall 43
made of the same flexible synthetic resin material as the optic
positioning member 34. The thin wall 43 has an anterior section 33
facing the anterior portion 12 of the eye 10 and a posterior
section 41 facing the posterior portion 14' of the eye 10
respectively. (See FIG. 2) The anterior section 33 of the thin wall
43 has a thickness of from about 0.0005 to 0.025 mm, and more
preferably of about 0.004 mm, when the material used is silicone.
The posterior section 41 of the thin wall 43 has a thickness of
from about 0.0005 to 0.025 mm, and more preferably of about 0.003
mm, when the material used is silicone. One of ordinary skill in
the art will appreciate that the anterior section 33 and the
posterior section 41 of the thin wall 43 may also be constructed of
uniform thickness. The optic 32 may also be constructed without the
refractive material housed within the pre-formed capsule 42 when
the refractive material used is the silicone gel material discussed
above. (See FIG. 16) The optic positioning member 34 may be
integral with optic 32 or may be structurally distinct. As
illustrated, the optic positioning member 34 comprises a main body
35 which includes an annular posterior segment 44 with a central
opening 46 and an anterior segment 37. Anterior segment 37 and
posterior segment 44 are located on either side of equatorial axis
56. A plurality of circumferentially spaced, arcuate in
cross-section positioning legs 48 extend from the segment 44 and
are joined to the margin of optic 32, with openings 50 defined
between adjacent pairs of the legs 48. As perhaps best seen in FIG.
2, the legs 48 cooperatively present, with the optic 32, a
substantially discoid shape with a central chamber 52. However, the
legs 48 also define an annular equatorial segment 54 disposed on
opposite sides of equatorial axis 56. (See FIG. 2) The overall IOL
61 further presents a central polar axis 58 as shown. Preferably,
the outside dimension of the IOL 61 at the equatorial segment 48 is
from about 8 to 12 mm. On the other hand, the outside dimension
along polar axis 58 is typically from about 1 to 5 mm. These
dimensions given immediately above, however, are only
representative of some typical dimensions within the ambit of the
present invention. A wide range of variance necessarily exists for
the dimensions of the IOLs of this invention because a wide degree
of biological variance exists. Clearly, the dimensions of the IOLs
of the present invention must conform to the size and shape of the
eye to be fitted. One of ordinary skill in the art will readily
appreciate this.
[0050] The optic positioning member 34 discussed herein is
configured so as to substantially conform with the capsule 22,
particularly to the equatorial portion 27 of the capsule 22. This
is shown in FIGS. 1 and 2 where it will be observed that the
equatorial segment 54 of the IOL 61 is in substantially conforming
contact with the inner surface of the equatorial portion 27 of
capsule 22. This close conforming relationship is maintained
notwithstanding the extent of accommodation of IOL 61.
[0051] IOL 61 is inserted into the human eye 10 in the following
manner. An ophthalmic surgeon would remove the natural crystalline
lens 24 by conventional methods, leaving an opening 21 in the
anterior wall 23 of the capsule 22. IOL 61 is then folded into a
compact size for insertion in the capsule 22 through opening 21.
Once inserted, the capsule 22 is filled with fluids (e.g., saline
solution) which enter the IOL 61 causing IOL 61 to return to its
original, non-deformed state as shown in FIG. 1. There is no need
to suture the IOL 61 to the capsule 22 because, due to the size and
shape of IOL 61 and conformance of the IOL 61 to the capsule 22,
the IOL 61 will not rotate or shift within the capsule 22.
[0052] Optionally, IOL 61 may be provided with a very thin membrane
(not shown) in covering relationship as disclosed in U.S. patent
application Ser. No. 09/940,018, filed Aug. 27, 2001, which is
incorporated by reference herein. It is contemplated that the
membrane would be formed of the same synthetic resin as the optic
positioning member 34 but would be much thinner (on the order of a
few thousandths of an inch) than the remainder of the optic
positioning member 34. The purpose of the membrane is to prevent or
at least impede the passage of migratory cells through openings
within the IOL 61 and into the inner chamber of the IOL 61.
[0053] Furthermore, optic positioning member 34 construction is
disclosed in previously filed application for U.S. patent Ser. No.
______ entitled Accommodating Intraocular Lens Implant and U.S.
patent Ser. No. 09/940,018 entitled Intraocular Lens Implant Having
Eye Accommodating Capabilities both to the same applicant, which
are hereby incorporated by reference herein as is necessary for a
full and complete understanding of the present invention.
[0054] Implantation of the inventive IOL 61 restores normal vision
by providing an optic 32 formed of highly refractive material
capable of bending light onto the retina. After implantation of the
IOL 61 in the human eye 10, light refracts at the air-cornea
interface in the same manner as the natural human eye 10. The light
travels through the fluid-filled anterior chamber 18 and onto the
optic 32. The radius of curvature of the optic 32 changes in
response to ciliary body 26 movement, thus affecting the optic's 32
refractive capabilities.
[0055] Not only does the IOL 61 project an observed image onto the
retina, but it also accommodates in response to action of the
ciliary body 26 in connection with the zonules 28 to view objects
located both near and far from the viewer. When the viewer is
observing an image located at a distance, the sensory cells within
the retina signal the ciliary body 26 to relax, thus pulling on the
zonules 28 to make the capsule 22 more discoid as shown in FIG. 1.
In doing so, the polar dimension of the capsule 22 narrows,
subsequently causing the polar dimension of the IOL 61 to similarly
narrow. Those ordinarily skilled in the art will appreciate that
the optic positioning member 34 is operably coupled with the optic
32 of the present invention to change shape in response to ciliary
body 26 movement. In this regard, the movement of the ciliary body
26 causes the optic 32 to move posteriorly and anteriorly,
respectively. Contraction of the ciliary body 26 and subsequent
relaxation of the zonules 28 will cause the optic 32 to vault
anteriorly.
[0056] The IOL 61 of the present invention typically has a diopter
value of from about 16 to 26. The diopter value of a lens is
defined as the reciprocal of the focal length in meters:
Diopter=1/focal length (m). Focal length is the distance from the
center of the lens to the object being viewed. The focal length
must decrease as magnification increases. The diopter value
expresses the refractive capacity of a lens which is associated
with the radius of curvature of the optics. Generally, an increased
diopter value indicates that the optic is thicker and also has a
lesser radius of curvature thus possessing greater light-bending
capability. The IOL of FIG. 4 [IOL 60]
[0057] The IOL 60 is similar to IOL 61 illustrated in FIGS. 1-3.
IOL 60 comprises an optic positioning member 62 wherein the optic
positioning member 62 presents an anterior segment 66 and a
posterior segment 68 each having a central opening therein 67, 69.
A plurality of individually continuous, circumferentially spaced,
arcuate in cross-section positioning legs 64 extend from anterior
segment 66 and are joined to the margin of optic 32, with openings
71 defined between adjacent pairs of the legs 64, by haptic arms
72. The haptic arms 72 extend between the posterior segment 68 to
the margin of the optic 32. The haptic arms 72 join the optic 32
and the optic positioning member 62. This embodiment is similar to
IOL 61 in that it may also be constructed with a thin membrane as
disclosed in U.S. patent application Ser. No. 09/940,018, filed
Aug. 27, 2001 which has been incorporated by reference herein.
[0058] In this embodiment, it is important that the posterior
segment 68 of the optic positioning member 62 not be fixed with
respect to the posterior portion of the capsule 22. This would not
be the case if the posterior segment 68 was continuously connected
with the positioning legs 64. While not shown in the figures, the
anterior segment 66 may be continuously connected by an annular
haptic. IOL 60 is implanted and operates in the same manner as IOL
61. The IOL 60 of the present invention typically has a diopter
value of from about 16 to 26.
[0059] Furthermore, optic positioning member 62 construction is
disclosed in previously filed application for U.S. patent Ser. No.
______ entitled Accommodating Intraocular Lens Implant and U.S.
patent Ser. No. 09/940,018 entitled Intraocular Lens Implant Having
Eye Accommodating Capabilities both to the same applicant, which
are hereby incorporated by reference herein as is necessary for a
full and complete understanding of the present invention.
The IOL of FIG. 5 [IOL 60a]
[0060] A preferred IOL 60a according to the invention is
illustrated in FIG. 5. Similar to the IOL 60 embodiment described
above, this IOL 60a comprises an optic 32 and an optic positioning
member 74 presenting an anterior segment 66a and a posterior
segment 68a. A plurality of circumferentially spaced, arcuate in
cross-section positioning legs 76 extend from the anterior segment
66a to the optic 32. The haptic arm 72a extends posteriorly from
the anterior segment 66a to the optic 32. In a further preferred
embodiment of IOL 60a, the optic 32 may be connected to the optic
positioning member 74 via a plurality of haptic arms (not shown).
The plurality of haptic arms are disposed at various locations
about anterior segment 66a and extend posteriorly towards the optic
32. The plurality of legs 76 are continuously attached to each
other through continuous sections 80 presenting annular orifices 82
therethrough. This embodiment is similar to IOL 61 and 60 in that
it may also be constructed with a thin membrane as disclosed in
U.S. patent application Ser. No. 09/940,018, filed Aug. 27, 2001
which has been incorporated by reference herein.
[0061] IOL 60a is implanted and operates in a similar manner to
IOLs 61 and 60. The IOL 60a of the present invention typically has
a diopter value of from about 16 to 26. Furthermore, the
construction of optic positioning member 74 is disclosed in
previously filed application for U.S. patent Ser. No. ______
entitled Accommodating Intraocular Lens Implant and U.S. patent
Ser. No. 09/940,018 entitled Intraocular Lens Implant Having Eye
Accommodating Capabilities both to the same applicant, which are
hereby incorporated by reference herein as is necessary for a full
and complete understanding of the present invention.
The IOL of FIG. 6 [IOL 60b]
[0062] FIG. 6 depicts yet another preferred IOL 60b according to
the invention. This IOL 60b also comprises an optic 32 and an optic
positioning member 84 presenting an anterior segment 66b and a
posterior segment 68b. The optic positioning member 84 further
comprises a plurality of circumferentially spaced, arcuate in
cross-section positioning legs 88 having openings 86 therein
between adjacent pairs of legs 88. In essence, the IOL 60b is
configured in much the same fashion as the IOL 60, with the
exception that a plurality of haptic arms 72b extend from
equatorial segment 54 toward the optic 32. When the IOL 60b is in
its original, non-compressed state, the haptic arms 72b are vaulted
slightly toward anterior segment 66b.
[0063] This embodiment is similar to IOL 61, 60, and 60a in that it
may also be constructed with a thin membrane as disclosed in U.S.
patent application Ser. No. 09/940,018, filed Aug. 27, 2001 which
has been incorporated by reference herein.
[0064] IOL 60b is implanted and operates in a similar manner to
IOLs 61, 60 and 60a. The IOL 60b of the present invention typically
has a diopter value of from about 16 to 26. Furthermore, the
construction of optic positioning member 84 is disclosed in
previously filed application for U.S. patent Ser. No. ______
entitled Accommodating Intraocular Lens Implant and U.S. patent
Ser. No. 09/940,018 entitled Intraocular Lens Implant Having Eye
Accommodating Capabilities both to the same applicant, which are
hereby incorporated by reference herein as is necessary for a full
and complete understanding of the present invention.
The IOL of FIGS. 7 and 8 [IOL 61d]
[0065] IOL 61d is another embodiment of the present invention. IOL
61d presents a variation upon the structure of IOL 61 wherein the
optic 32 is bound to either the anterior surface 31(a) or the
posterior surface 31(b) of the optic positioning member 34. IOL 61d
operates in and is implanted in the same manner as IOL 61.
[0066] Notably, IOL 61d illustrated in FIGS. 7 and 8 comprises a
liquid refractive material 40 enveloped within the capsule 42. The
indices of refraction of the wall 43 and the refractive material 40
may be varied to satiate surgical, medical, or manufacturing
needs.
The IOL of FIGS. 9 and 10 [IOL 61a]
[0067] IOL 61a differs from the embodiments discussed thus far in
that while the optic 32 is operably coupled to the anterior segment
37 of the optic positioning member, a second rigid optic 90 is
operably coupled to the posterior segment 44. The optics 32, 90 are
positioned on opposed segments 37, 44 of the optic positioning
member such that the optics 32, 90 share the same optical axis.
Opposition or opposed in this context is used consistently in this
application to mean positioned on the opposite side of equatorial
axis 56(a) such that both optics share substantially the same optic
axis, and are aligned such that the IOL provides undistorted
vision. The posterior optic 90 is made of the same material as the
optic positioning member 34, however, one of ordinary skill in the
art will recognize that the posterior optic 90 may be constructed
of the inventive refractive material as well.
[0068] This embodiment is implanted and operates in essentially the
same manner as the IOLs discussed thus far, but differs because it
includes a second opposed rigid optic 90. The anterior optic 32
converges light upon the posterior optic 90. The posterior optic
90, in turn, diverges the light onto the retina. Any irregularities
in the cornea 16 or the natural crystalline lens 24 are
counteracted by the highly refractive material 102, thereby
bringing the image to focus upon the retina. This embodiment also
accommodates in response to ciliary body 26 movement. When the
ciliary body 26 contracts, the IOL 61a assumes a spheroid shape.
The anterior optic 32 moves anteriorly whereas the posterior optic
90 moves posteriorly. When the ciliary body 26 retracts, the
zonules 28 exert a tensional pull upon the IOL to change the IOL to
a discoid shape. The anterior optic 32 moves posteriorly whereas
the posterior optic 90 moves anteriorly. The IOL 61a of the present
invention typically has a diopter value of from about 16 to 26.
[0069] IOL 61a may also be positioned within the eye 10 such that
the rigid optic 90 is located anteriorly and the optic 32 is
positioned posteriorly as illustrated in FIG. 10. When the IOL 61a
is positioned within the eye 10 in this manner, the IOL 61 has a
combined total refraction of about 16 to 26 diopters.
The IOL of FIGS. 11-15 [IOL 92]
[0070] Another preferred embodiment of the present invention
includes an anterior optic 94a and a posterior optic surface 96a
integral with an optic positioning member 98, such that the IOL 92
presents a unitary structure for implantation within the capsule 22
of the human eye 10. (See FIG. 11) IOL 92 comprises a main body
presenting a pre-formed enclosed flexible bag 100 having a
resilient fill material 102(a) therein. The pre-formed enclosed
flexible bag 100 may also be filled with other refractive media
disclosed herein. Flexible bag 100 comprises an anterior segment
104, and a posterior segment 106. Flexible bag further includes
wall 112 which, when viewed in cross section, forms and extends
radially from an anterior arcuate wall segment 94 and converges
upon the posterior segment 106 of the IOL 92 to form an opposing
posterior arcuate wall segment 96. The opposing arcuate wall
segments 94, 96 define opposed anterior and posterior optic
surfaces 94a, 96a when cavity 114 of enclosed flexible bag 100 is
filled with material 102(a). Although the terminology `optic
surface` is used herein to describe surfaces 94a and 96a, these
surfaces 94a, 96a, operate functionally as optics. Therefore, the
term optic may be used interchangeably to describe optic surfaces
94a, 96a within the remainder of this disclosure.
[0071] The anterior optic surface 94a and the posterior optic
surface 96a have a combined radius of curvature of from about 16 to
26 diopters. (See FIG. 11) The anterior optic surface 94a and the
posterior optic surface 96a are both illustrated as convex in
shape. When viewed in cross-section, anterior segment 94 and
posterior segment 96 are connected by a pair of opposed arcuate
equatorial segments 124a as shown in FIG. 14.
[0072] Wall 112 includes a fill aperture 118 with a plug therein
closing the aperture 118. Although aperture 118 is illustrated at
location 120 of the IOL 92, the aperture 118 can be formed at any
location on the IOL 92. Preferably the IOL 92 will have an outer
equatorial diameter (distance of IOL 92 taken through equatorial
axis 124) of from about 8 to 12 mm. (See FIG. 13) Preferably the
IOL will have an outside dimension through the central polar axis
122 of from about 2 to 5 mm. (See FIG. 13)
[0073] An ophthalmologist fills cavity 114 with material 102(a)
prior to surgical implantation of the IOL 92 within the human eye
10 by inserting the material 102(a) through the aperture 118. After
cavity 114 is filled, the aperture 118 is sealed. The
ophthalmologist removes the natural crystalline lens 24 by
conventional methods, leaving an opening in the anterior wall 23(a)
of the capsule 22. The IOL 92 is folded an inserted within the
capsule 22 through the opening. Implantation of the IOL 92 does not
require suturing of the eye 10 be because the instant IOL 92 is
capable of being implanted through a small opening in the capsule
22.
[0074] IOL 92 operates in the same manner as IOL 61a because IOL 92
includes opposed optic surfaces 94, 96. Anterior optic 94 converges
light upon the posterior optic 96, which in turn, diverges light
onto the retina. The IOL 92 responds to contraction of the ciliary
body 26 by assuming a spheroid shape.
IOL of FIG. 16 [IOL 61]
[0075] FIG. 16 illustrates optic 32 of the inventive IOL 61 formed
from a resilient silicone gel material. Therefore, the IOL 61 of
FIG. 16 does not depict the refractive material enveloped within a
pre-formed capsule 42 having a thin continuous wall 43. The capsule
42 is not needed when the refractive material is formed from a
resilient, shape-retaining synthetic material such as the silicone
gel discussed above.
IOL of FIG. 17 [IOL 61c]
[0076] Another preferred embodiment of the present invention
includes an optic positioning member 34 operably coupled with two
optics 142, 144 to change shape in response to ciliary body 26
movement. IOL 61c includes a resilient optic 142 surrounded by a
rigid optic 144. The resilient optic 142 is formed of the
refractive material discussed above. The rigid optic 144 is formed
of the same material as the optic positioning member 34. Both
optics 142, 144 are housed within a pre-formed capsule 42 as
described in connection with IOL 61.
[0077] IOL 61c operates in a similar manner as the embodiments
discussed so far, but differs in that the resilient optic142
surrounded by the rigid optic 144 maintains a constant volume in
response to ciliary body 26 movement. The constant volume of the
resilient optic 142 coupled with the relatively high refractive
index of the refractive material contained therein confers
increased light-bending properties upon the resilient optic
142.
IOL of FIGS. 18 and 19 [IOL 200]
[0078] Another preferred embodiment is an IOL 200 having an annular
optic positioning member 210 presenting spaced-apart arcuate
anterior 212 and posterior segments 214. The IOL 200 further
includes an anterior resilient optic 216 and a posterior rigid
optic 218 operably coupled to the optic positioning member 210 to
change shape in response to ciliary body 26 movement.
[0079] The anterior segment 212 of the optic positioning member 210
contains an opening 220 of from about 7 to 3 mm, and more
preferably of about 4 mm wide. The anterior segment 212 further
includes an outer margin 222 and an inner margin 224. The outer
margin 222 is defined as the anterior portion of the anterior
segment 212, or that portion of the segment 212 closest to the iris
20. The posterior segment 214 also includes an inner margin 226 and
an outer margin 228 wherein the inner margin 226 of the posterior
segment 214 is the margin closest to the iris 20 as well. The space
between the anterior segment 212 and the posterior segment 214 is
occupied by refractive material such that the refractive material
is adjacent to the inner margins 224, 226 of the segments 212, 214.
The refractive material protrudes beyond the outer margin 222 of
the anterior segment 212. This protrusion defines the resilient
optic 216. The refractive material used herein is the refractive
silicone gel discussed above. The silicone gel refractive material
may be pre-formed into the desired shape and connected, by posts,
to the segments 212, 214 of the optic positioning member 210. The
refractive material may also be encompassed within a bladder which
is also similarly connected to the segments 212, 214. In this case,
the refractive material used may also be a liquid.
[0080] The IOL 200 may further include a second rigid optic 218
opposed to resilient optic 216. The rigid optic 218 is made of the
same material as the optic positioning member 210 and is supported
by the posterior segment 214. As mentioned above, the space between
the segments 212, 214 is occupied by refractive material. This IOL
200 differs from the other embodiments discussed herein because the
refractive material is not completely contained by the optic
positioning member 210 in addition to the optic 216 defining
protrusion which extends beyond the outer margin 222 of the
anterior segment 212. The refractive material is positioned between
the two segments 212, 214 such that the refractive material comes
into direct contact with the biological capsule 22 at locations
230.
[0081] IOL 200 is implanted in the same manner as IOL 61 after IOL
200 is assembled, and operates in a similar manner to the other
IOLs having opposed optics discussed herein. Contraction of the
ciliary body 26 and subsequent relaxation of the zonules 28 exerts
force upon the refractive material causing the material to protrude
outward to extend beyond the outer margin 222 of the anterior
segment 212. When the ciliary body 26 retracts, the zonules 28
exert a tensional pull upon the capsule 22, and the refractive
material assumes its more flattened shape to view objects located
at a distance.
IOL of FIGS. 20 and 21 [IOL 61b]
[0082] The IOL 61b illustrated in FIGS. 20 and 21 demonstrate yet
another preferred embodiment of the invention. FIGS. 20 and 21
demonstrate any of the IOLs of FIGS. 1-8 and 16 discussed above
positioned within the eye 10 such that the optic 32 is positioned
posteriorly. One of skill in the art would readily appreciate that
although FIGS. 20 and 21 illustrate any of the IOLs of FIGS. 1-8
and 16 in the vertical sectional view, any of the IOLs of the
present invention may be positioned such that the anterior optic
faces posteriorly. FIG. 20 illustrates the IOL of the present
invention in the accommodated shape. FIG. 21 illustrates the IOL in
the disaccommodated shape.
IOL of FIG. 22 [IOL 61e]
[0083] IOL 61e illustrated in FIG. 22 is similar to IOL 61c
illustrated in FIG. 17. IOL 61e differs from IOL 61c in that the
resilient optic 142a surrounds the rigid optic 144a. FIG. 22
illustrates IOL 61e positioned posteriorly in the capsule 22 of the
eye 10. The resilient optic 142a changes shape in response to
ciliary body 26 movement. The change in curvature of the resilient
optic 142a provides about 3 diopters of convergence while the rigid
optic 144a essentially maintains its shape.
[0084] Although the invention has been described with reference to
the preferred embodiment illustrated in the attached drawing
figures, it is noted that equivalents may be employed and
substitutions made herein without departing from the scope of the
invention as recited in the claims. For example, the IOLs of the
present invention may all be constructed in the disaccommodated or
accommodated shapes. Also, while the foregoing method of inserting
the IOL in the capsule 22 presumed that a portion of the anterior
wall 23(a) of the capsule 22 would be removed with the natural
crystalline lens 24, it will be appreciated that it may be possible
to insert the IOL an incision in the posterior wall 53 of the
capsule 22. Furthermore, while the foregoing description discloses
that the IOL could be utilized to correct refractive error, the IOL
may be used in any situation where the natural crystalline lens 24
should be replaced. For example, the IOL may be used to correct
myopia, hyperopia, presbyopia, cataracts, or a combination thereof.
Various refractive media may be used to fill cavity 114 of IOL
depending upon the desired index of refraction.
* * * * *