Toric small aperture intraocular lens with extended depth of focus

Abstract

An intraocular lens is provided that includes a refractive element and a mask. The refractive element has a first power in a first meridian and a second power greater than the first power in a second meridian. A magnitude of the first and second powers and a location of the first and second meridians are configured to correct astigmatism in a human eye. The mask is configured to block a substantial portion of light from passing through an annular region thereof and to permit a substantial portion of light to pass through a central aperture thereof to enhance an astigmatism correction rotational misplacement range and depth of focus.

Description

BACKGROUND

Field

This application is directed to ophthalmic devices that can be used to improve vision in patients suffering from astigmatism.

DESCRIPTION OF THE RELATED ART

The human eye functions to provide vision by transmitting and focusing light through the cornea and through the crystalline lens in the eye to form a focused image on a retina. The quality of the focused image depends on many factors including the size and shape of the eye, the transparency of the cornea and the lens, as well as the capability of the lens to accommodate.

The optical power of the eye is a function of the optical power of the cornea and the crystalline lens. In a normal, healthy eye, sharp images of distant objects are formed on the retina. This vision state is called emmetropia. In myopic eyes, images of distant objects are formed at a location in front of the retina. This may be because the eye is abnormally long or the cornea is abnormally steep. In hyperopic eyes, images are formed at a location behind the retina. This may be because the eye is abnormally short or the cornea is abnormally flat. The focusing effect of the eye may be rotationally asymmetric, resulting in an uncompensated cylindrical refractive error referred to as astigmatism.

Some people suffer from cataracts in which the crystalline lens undergoes a loss of transparency. In such cases, the crystalline lens can be removed and replaced with an intraocular lens (IOL). However, commercially approved intraocular lenses do not restore full vision function and even small misplacement in the eye can result in sub-optimal vision correction. As a result, many patients are subject to inconvenient post-operative strategies to cope.

SUMMARY

This application is directed to providing a better outcome for patients undergoing intraocular refractive vision correction. This application discloses devices that can simplify treatment of complex cases, such as patients who have a lack of accommodation, cataract, and/or astigmatism.

In one embodiment, an intraocular lens is provided that includes a refractive element and a mask. The refractive element has a first power in a first meridian and a second power greater than the first power in a second meridian. A magnitude of the first and second powers and a location of the first and second meridians are configured to correct astigmatism in a human eye. The mask is configured to block a substantial portion of light from passing through an annular region thereof and to permit a substantial portion of light to pass through a central aperture thereof to enhance an astigmatism correction rotational misplacement range.

In another embodiment, an intraocular lens is provided that includes a refractive element that is adapted to counter astigmatism in a human eye and a mask. The mask is configured to prevent light from passing through an annular region thereof. The mask is configured to permit a light to pass through a central aperture thereof to increase depth of focus and to increase tolerance to rotational misplacement within the eye by as much as 15 degrees.

In another embodiment a method of correcting astigmatism is provided. In the method, an intraocular lens is placed into an eye of a patient. The intraocular lens has a cylinder power component aligned with a meridian thereof and a mask comprising a small aperture surrounded by an opaque member. It is then confirmed that the meridian of the intraocular lens is aligned within a range exceeding five degrees of a locally minimum power of the eye to reduce astigmatism in the eye such that the eye achieves functional acuity.

Any feature, structure, or step disclosed herein can be replaced with or combined with any other feature, structure, or step disclosed herein, or omitted. Further, for purposes of summarizing the disclosure, certain aspects, advantages, and features of the inventions have been described herein. It is to be understood that not necessarily any or all such advantages are achieved in accordance with any particular embodiment of the inventions disclosed herein. No aspects of this disclosure are essential or indispensable.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments are depicted in the accompanying drawings for illustrative purposes, and should in no way be interpreted as limiting the scope of the embodiments. Furthermore, various features of different disclosed embodiments can be combined to form additional embodiments, which are part of this disclosure.

FIG. 1 schematically illustrates uncorrected and corrected focusing effect along a horizontal meridian of an eye with astigmatism in which the lowest power meridian of the eye is aligned with the horizontal meridian.

FIG. 2 schematically illustrates uncorrected and corrected focusing effect along a vertical meridian of an eye with astigmatism in which the highest power meridian of the eye is aligned with the vertical meridian.

FIG. 3 illustrates a power distribution of a refractive element of an intraocular lens (IOL) configured to correct for rotationally asymmetric refractive error illustrated in FIGS. 1 and 2.

FIGS. 4A-4D illustrate an embodiment of an IOL having a refractive element and a mask coupled with the refractive element.

FIG. 5A illustrates an embodiment of a mask.

FIG. 5B illustrates another embodiment of the mask.

FIG. 6 schematically illustrates the depth of focus extending effect of the masks of FIGS. 5A and 5B.

FIG. 7 shows simulated defocus performance of a monofocal IOL with corneal aberration correction compared with the same IOL additionally incorporating a small aperture optic.

FIG. 8 shows simulated cylinder performance of a monofocal IOL with corneal aberration correction compared with the same IOL additionally incorporating a small aperture optic.

FIG. 9 shows simulated defocus performance of a monofocal tonic IOL in an eye system with cylinder cornea compared with the same IOL additionally incorporating a small aperture optic.

FIG. 10 shows simulated cylinder performance of a monofocal tonic IOL in an eye system with cylinder at the cornea and additional cylinder at the IOL plane compared with the same IOL additionally incorporating a small aperture optic.

FIG. 11 shows simulated rotational misalignment performance of a monofocal toric IOL in an eye system with cylinder at the cornea compared with the same IOL additionally incorporating a small aperture optic.

FIG. 12 is a schematic diagram of an eye showing increased tolerance to misplacement as provided by certain embodiments herein.

DETAILED DESCRIPTION

A patient with astigmatism has unequal optical power at different rotational positions of the eye. The power of the eye is greater in some meridians of the eye than in other meridians. Patients who undergo IOL implantation surgery may suffer from astigmatism. This may be because even if the IOL has perfectly symmetric optics, the cornea of the eye in which the IOL is placed may be formed in a way providing uneven, rotationally asymmetric powers.

FIGS. 1 and 2 illustrate a simple example of how an astigmatic eye 10 converges light passing through the lens. FIG. 1 illustrates a horizontal meridian H of the eye 10. Light incident on the horizontal meridian passes through the crystalline lens 18 and converges behind the retina 14. The solid lines show that the light passing along the horizontal meridian H is focused at a location rearward of the retina 14 by a first amount. FIG. 2 illustrates a vertical meridian V of the eye 10. In FIG. 2, solid lines illustrate that light passing along the vertical meridian V is focused at a location rearward of the retina 14 by a second amount greater than the first amount, which is the optical effect of astigmatism.

FIG. 3 shows a refractive element 100 that can correct for the rotational asymmetry of refractive power in an eye that causes astigmatism. The refractive element 100 includes a surface 104 that has a refractive power. That is, the surface 104 is configured to cause rays being refracted in an astigmatic eye and through the element 100 to converge at a common focal point. The surface 104 can have a refractive index that causes such convergence, can be curved to cause such convergence or can combine refractive index and curvature together or with other optical effects to cause such convergence. In one embodiment, the surface 104 has a first curvature 108 and a second curvature 112. The first curvature 108 is less than the second curvature 112. As a result, the first curvature 108 has less optical power than the second curvature 112. The second curvature 112 induces more convergence of the rays that are incident on the surface 104 along a line of the second curvature 112 than the first curvature 108.

If the refractive element 100 is properly placed in the astigmatic eye 10 illustrated in FIGS. 1 and 2, the refractive element 100 can correct the astigmatism. The refractive element 100 can be placed in the eye 10 such that the first curvature 108 is aligned with the horizontal meridian H which is illustrated in FIG. 1. When so placed, the first curvature 108 corrects the relatively smaller hyperopic error on the horizontal meridian H of the eye 10 by a first amount. The refractive element 100 can be placed in the eye 10 such that the second curvature 112 is aligned with the vertical meridian V which is illustrated in FIG. 2. When placed such that the second curvature 112 is aligned with the vertical meridian, the relatively larger hyperopic error is corrected by a larger amount than was corrected in the horizontal meridian H. As a result, the rays on both meridians are brought into focus at the same location. An additional power can be provided if needed to shift the focal plane to the retina as illustrated by the solid converging lines in FIGS. 1 and 2.

FIG. 3 shows the refractive element 100 surrounded by dashed lines. As discussed further below, other components of an IOL incorporating the refractive element 100 can be coupled with the refractive element 100 either prior to implantation or during the course of the useful life of the IOL incorporating the refractive element 100.

Intraocular Lens

As shown in FIGS. 4A-4D, an intraocular lens 1000 includes an optic 1004 and a mask 1012. The optic 1004 can be formed from an optically transmissive material, while the mask 1012 can be formed from an opaque material. The optic 1004 can include the refractive element 100 to correct refractive errors, such as rotationally asymmetric power, e.g., astigmatism. The optic 1004 can include other structures to improve the overall visual performance of the IOL 1000 in addition to the refractive element 100.

The optic 1004 can be monofocal or multifocal and it can have positive or negative optical power. The optic 1004 may be aspheric or any other configuration as the context may dictate. In various embodiments the optic 1004 has a cylinder power or other rotationally asymmetric power such that the optic 1004 can correct for astigmatism of an eye as discussed above. In some implementations, the greatest thickness of the optic 1004 is at the center of the optic 1004. In other implementations, the optic 1004 may have a reduced thickness at its center, which is further described in U.S. Publication No. 2011/0040376, filed Aug. 13, 2010, which is hereby incorporated by reference in its entirety herein. The optic 1004 may be substantially circular with an outer diameter between about 5.0 mm and about 8.0 mm, such as about 6.0 mm. A central thickness of the optic 1004 can be less than or equal to about 1.0 mm, such as between about 0.75 mm and about 1.0 mm.

The intraocular lens 1000 may include one or more haptics 1008 (e.g., one, two, three, four, or more) to prevent the intraocular lens 1000 from moving or rotating within the eye. As used herein the term “haptic” is intended to be a broad term encompassing struts and other mechanical structures that can be apposed against an inner surface of an eye and mounted to an optic to securely position an intraocular lens in an optical path of an eye. The haptics 1008 can be a variety of shapes and sizes depending on the location the intraocular lens 1000 is implanted in the eye. The haptics 1008 may be C-shaped, J-shaped, plate design, or any other design. The haptics 1008 may be manufactured substantially flat or vaulted with respect to the optic. Variations on the shape of the optic and the haptics can be found in U.S. Publication No. 2011/0040376, filed Aug. 13, 2010, which is hereby incorporated by reference in its entirety herein.

The mask 1012 can be formed on an anterior surface 1016 of the optic 1004 (see FIGS. 4A-4D), on a posterior surface 1020 of the optic 1004, or embedded within the optic 1004. When the mask 1012 is embedded within the optic 1004, the mask 1012 can be formed substantially at the midway line between the posterior 1020 and anterior surfaces 1016 of the optic 1004. But the mask 1012 can also be formed at other locations within the optic 1004. Additional information regarding the manufacturing of such intraocular lenses can be found in PCT/US2016/055207, filed Oct. 3, 2016, which is hereby incorporated by reference in its entirety herein.

Mask

FIG. 5A illustrates a mask 2034a having an annular region 2036a surrounding an aperture 2038a substantially centrally located on the mask 2034a. An anterior surface of the annular region 2036a can have a curvature from the outer periphery to the inner periphery of the annular region 2036a, and the posterior surface of the annular region 2036a can have a similar curvature. FIG. 5B shows that the mask 2034b can be flat in some embodiments. The mask 2034b can include an annular region 2034b surrounding an aperture 2038b substantially centered on the optical axis 2039b of the mask 2034b. Although the features described below are described with respect to the mask 2034a, one or the more of the features may be applied to the mask 2034b.

In some embodiments, the outer periphery of the mask 2034a is generally circular with an outer diameter of at least about 3 mm and less than about 6 mm. In some embodiments, the diameter of the outer periphery of the mask 2034a is at least about 3 mm and less than or equal to about 4 mm.

A thickness of the mask 2034a can be constant or can vary between the inner periphery (near the aperture) and the outer periphery. For example, the thickness may increase from an outer periphery and/or inner periphery of the mask 2034a and toward a radial midline of the annular region 2036a. In general, the thickness at any location of the mask 2034a can be less than or equal to about 200 microns, or less than or equal to about 100 microns, but preferably between about 1 micron and about 20 microns. For example, the thickness of the mask 2034a can be within the range: from about 1 micron to about 40 microns, from about 5 microns to about 20 microns, from about 5 microns to about 15 microns. In some implementations, the thickness of the mask 2034a can be within about two microns of: about 15 microns, about 10 microns, about 8 microns, or about 5 microns.

The aperture 2038a can transmit substantially all incident visible light along the optical axis 2039a. For example, the aperture 2038a can be a through-hole in the annular region 2036a or a substantially light transmissive (e.g., transparent to visible light) portion thereof. The aperture 2038a can be substantially circular and/or substantially centered around the optical axis 2039a of the mask 2034a. The size of the aperture 2038a can be any size that is effective to increase the depth of focus of an eye of a patient with presbyopia. In particular, the size of the aperture 2038a can be dependent on the location of the mask 2034a within the eye (e.g., distance from the retina). In some implementations, the aperture 2038a can have a diameter of at least about 0.85 mm and less than or equal to about 2.8 mm, at least about 1.1 mm and less than or equal to about 1.6 mm, or at least about 1.3 mm and less than or equal to about 1.4 mm.

The annular region 2036a can prevent transmission of substantially all or at least a portion of the spectrum of the incident visible light (e.g., radiant energy in the electromagnetic spectrum that is visible to the human eye) and/or the spectrum of non-visible light (e.g., radiant energy outside the range visible to humans). Preventing transmission of visible light through the annular region 2036a can block light that would not converge at the retina and fovea to form a sharp image. FIG. 6 illustrates this effect. In particular, the IOL 1000 is placed in the capsular bag of the eye 10. The mask 1012 is centered on the optical axis of the eye 10. Rays that would not converge on the retina 14 are illustrated by the dash lines. These rays are blocked by the annular region 2036a or the annular region 2036b of the mask 1012 and thus are prevented from degrading vision by causing a blur on the retina. Rays that converge on the retina 14 pass through the aperture of the mask 1012. A crisp image over a range of distances is provided by this focused light as discussed further below.

In some implementations, the annular region 2036a can prevent transmission of at least about: 90 percent of incident visible light, 92 percent of incident visible light, 95 percent of incident visible light, 98 percent of all incident visible light, or 99 percent of all incident visible light. The annular region 2036a can transmit no more than about: 10 percent of incident visible light, 8 percent of incident visible light, percent of incident visible light, 3 percent of incident visible light, 2 percent of incident visible light, or 1 percent of incident visible light.

In some embodiments, opacity of the annular region 2036a is achieved because the material used to make mask 2034a is naturally opaque. In other embodiments, the material used to make the mask 2034a may be naturally substantially clear but treated with a dye or other pigmentation agent (e.g., carbon black). In some embodiments, the mask is made of the same material as the lens body, with the addition of dye or other pigmentation agent. In other embodiments, the mask is made of a different material from the lens body.

Further variations of masks can be found in U.S. application Ser. No. 62/237,429, filed Oct. 5, 2015, U.S. Pat. No. 7,628,810, filed May 26, 2004, U.S. Publication No. 2012/0143325, filed Feb. 19, 2012, U.S. Publication No. 2011/0040376, filed Aug. 13, 2010; U.S. Publication No. 2013/0268071, filed Nov. 30, 2012; U.S. Publication No. 2014/0264981; U.S. Publication No. 2015/0073549, filed Aug. 7, 2014; U.S. Pat. No. 5,662,706, filed Jun. 14, 1996; U.S. Pat. No. 5,905,561, filed Jun. 14, 1996; and U.S. Pat. No. 5,965,330, filed Dec. 6, 1996, all of which are hereby incorporated by reference in their entirety herein.

Discussion of Simulation Tests

FIG. 7, upper row, is a Zemax optical simulation of the optical performance of a 21 diopter monofocal IOL. In the simulation, corneal aberration is corrected and the simulation assumes a realistic polychromatic model eye, with a 3 mm pupil. The left-most box shows the visual acuity for 0 diopter defocus. The acuity illustrated is acceptable at 20/20 or greater. The second box from the left shows the visual acuity for a −0.5 diopter defocus using the same lens and model used in the left-most box. One can see that the performance has declined, but the threshold acuity level is still at about 20/20. The third box from the left shows the visual acuity for a −1.0 diopter defocus using the same lens and simulation model used in generating the left-most box. One can see that this box does not register any level of visual acuity and thus the IOL is completely ineffective at this and greater defocus amounts.

FIG. 7, lower row, is a Zemax optical simulation of the optical performance of an IOL that has a small aperture mask disposed therein for extended depth of focus. The small aperture optic can have a 1.36 mm working aperture. The IOL had optimal focus. The simulation used a realistic polychromatic model eye with a 3 mm pupil. The left-most box shows the visual acuity for 0 diopter defocus, which is acceptable at 20/20 or greater. In contrast to the upper row, each of the defocus positions in the lower row from the left most box toward the right from −0.5 diopter, −1.0 diopter, −1.5 diopter and −2.0 diopter defocus show a 20/20 visual acuity or better. This simulation confirms the effectiveness of the small aperture optic illustrated in FIG. 6.

FIG. 8, upper row, is a Zemax optical simulation of the optical performance of a 21 diopter monofocal IOL correcting corneal aberration using a realistic polychromatic model eye, with a 3 mm pupil. The left-most box shows the visual acuity for 0 diopter added cylinder power. The acuity illustrated is acceptable at 20/20 or greater. The third box from the left shows the visual acuity for a −0.5 diopter addition of cylinder power using the same lens and model used in the left-most box. One can see that the performance has declined, but the threshold acuity level is still at about 20/20. The fifth box from the left shows the visual acuity for a −1.0 diopter addition of cylinder power using the same lens and model used in the left-most box. One can see that this box does not register any useful level of visual acuity and thus the IOL is completely ineffective at this and greater amounts of cylinder.

FIG. 8, lower row, is a Zemax optical simulation of an IOL with a small aperture mask that provides extended depth of focus. The mask was provided with a 1.36 working aperture and the IOL with optimal focus. The model again was constructed using a realistic polychromatic model eye with a 3 nm pupil. The left-most box shows the visual acuity for 0 added cylinder power and in this box the acuity illustrated is acceptable at 20/20 or greater. The third and fifth boxes from the left show the visual acuity for a −0.5 and −1.0 diopter added cylinder power using the same lens and model used in the left-most box, lower row. One can see that the performance has declined, but the threshold acuity level is still at about 20/20. In fact the performance of the small aperture IOL remains acceptable even to the right-most box which illustrates performance with −1.5 diopter of cylinder. FIG. 8 thus shows that a small aperture IOL can provide vision correction for small amounts of astigmatism even up to −1.5 diopters of added cylinder.

FIG. 9 shows the performance of a tonic IOL. In particular, FIG. 9, upper row, is a Zemax optical simulation of the optical performance of a 3 diopter tonic monofocal IOL using a realistic polychromatic model eye, with a 3 mm pupil and with a toric cornea. The performance of the tonic IOL is similar to that of the monofocal IOL illustrated in FIG. 7. That is, it can tolerate about −0.5 diopter defocus. But greater amounts of defocus degrade the visual acuity too much for the tonic IOL to provide functional visual acuity. In contrast, FIG. 9, lower row, shows that astigmatism in an eye can be more robustly corrected by a 3 diopter tonic IOL with a small aperture optic, e.g., having a 1.36 mm working aperture with the IOL having optimal focus. The lower row shows that the tonic IOL with small aperture optic can still perform well at up to −2.0 diopters of defocus.

FIG. 10 shows a further comparison of the performance of a 21 diopter monofocal toric IOL and the same IOL with a small aperture optic, e.g., an optic having a 1.36 mm working aperture. FIG. 10 shows the ability of these two IOLs to sustain visual acuity when working with progressively more additional cylinder power. The upper row shows that a tonic IOL can sustain acceptable visual acuity up to an additional −0.5 diopter of cylinder. The lower row shows that the toric IOL with a small aperture optic can perform well even when subject to up to −1.5 diopter of cylinder. This means that even in a patient with progressively worsening astigmatism, the toric IOL with small aperture optic can continue to provide good vision without additional lenses or procedures for much longer than the standard toric IOL.

FIG. 11 shows a further comparison of the performance of a 21 diopter monofocal toric IOL and the same IOL with a small aperture optic, an optic having a 1.36 mm working aperture. FIG. 11 shows the ability of these two IOLs to sustain rotational misplacement. The upper row shows that a tonic IOL can sustain a 5 degree rotational misplacement or misalimment. Beyond this amount, the visual acuity delivered by the standard tonic IOL is insufficient. The lower now shows that the toric IOL with a small aperture optic can perform well at up to 15 degrees of rotational misplacement or misalignment. This means that even where an IOL implantation procedure was not according to a pre-operative plan, the IOL will perform well. This is because the IOL has a much wider window of acceptable rotational placement. The lower row of FIG. 11 suggests that a 30 degree window can be provided within which a patient will have acceptable visual acuity. This is three times larger than the much more limited range of placement that a standard IOL can tolerate. This represents a significant improvement in toric IOL design, enhancing the robustness of the IOL such that the chance of a poor outcome even if placement is sub-optimal is greatly reduced.

The simulation performance can be summarized as follows:

	IOL Configuration
		Standard
	Standard	Monofocal	EDOF Small	EDOF Small
Performance	Monofocal	Toric	Aperture	Aperture Toric
Measurement	IOL	IOL	IOL	IOL
Tolerance to	≤0.5 D	≤0.5 D	≤1.5 D	±≤1.5 D
Astigmatism
Tolerance to	N/A	±≤5°	N/A	±≤15°
Angular
Rotational
Placement
Depth of Focus	±≤0.5 D	±≤0.5 D	±≤2.0 D	±≤2.0 D

FIG. 12 schematically illustrates aspects of certain embodiments. In particular, a cylinder power exists in the eye 10 prior to correction causing astigmatism. In this case, the power in the vertical meridian V is noticeably less than in the horizontal meridian H. The IOL 1000 including the refractive element 100 is provided and is placed in the eye 10. As discussed above, the refractive element 100 has different powers in different portions. For example, a meridian of the refractive element 100 can have the first curvature 108 and another meridian of the element 100 can have the second curvature 112 larger than the first curvature. The curvatures 108, 112 are along perpendicular meridians, but could be at other angles to each other as a function of the power profile of the eye. As discussed above, the steeper second curvature 112 induces more convergence. Accordingly, the second curvature 112 should optimally be aligned with the vertical meridian V of the eye 10 so that the locally lower power of the eye 10 is compensated by the second curvature 112 to enable the vertical and horizontal meridians V, H to converge at the same location. However, as shown, the refractive element 100 is rotationally offset from the optimal aligned position. Advantageously, the IOL 1000 is enabled by the combination of a tone configuration of the refractive element 100 and the mask 1012 to have a much larger than conventional acceptable rotational offset from the optimal position. FIG. 12 shows in the shaded pie-shaped region that there is an acceptable acuity over a large IOL placement range. In this embodiment, the range extends on both sides, e.g., symmetrically, of the optimal (vertical) position. As such IOL 1000 provides an increase in tolerance to rotational misplacement. The range extends beyond the angle of misplacement of the IOL 1000. In the conventional IOL, the range would be much less, for example between the position of the second curvature 112 and the vertical meridian V preventing the convention IOL when placed as shown in FIG. 12 from providing functional visual acuity.

Terminology

Conditional language, such as “can,” “could,” “might,” or “may,” unless specifically stated otherwise, or otherwise understood within the context as used, is generally intended to convey that certain embodiments include, while other embodiments do not include, certain features, elements, and/or steps. Thus, such conditional language is not generally intended to imply that features, elements, and/or steps are in any way required for one or more embodiments or that one or more embodiments necessarily include logic for deciding, with or without user input or prompting, whether these features, elements, and/or steps are included or are to be performed in any particular embodiment.

The terms “comprising,” “including,” “having,” and the like are synonymous and are used inclusively, in an open-ended fashion, and do not exclude additional elements, features, acts, operations, and so forth. Also, the term “or” is used in its inclusive sense (and not in its exclusive sense) so that when used, for example, to connect a list of elements, the term “or” means one, some, or all of the elements in the list.

The terms “approximately,” “about,” and “substantially” as used herein represent an amount close to the stated amount that still performs a desired function or achieves a desired result. For example, the terms “approximately,” “about,” and “substantially” may refer to an amount that is within less than 10% of the stated amount, as the context may dictate.

The ranges disclosed herein also encompass any and all overlap, sub-ranges, and combinations thereof. Language such as “up to,” “at least,” “greater than,” “less than,” “between” and the like includes the number recited. Numbers preceded by a term such as “about” or “approximately” include the recited numbers. For example, “about 3 mm” includes “3 mm.”

Although certain embodiments and examples have been described herein, it will be understood by those skilled in the art that many aspects of the methods and IOL shown and described in the present disclosure may be differently combined and/or modified to form still further embodiments or acceptable examples. All such modifications and variations are intended to be included herein within the scope of this disclosure. A wide variety of designs and approaches are possible. No feature, structure, or step disclosed herein is essential or indispensable.

For purposes of this disclosure, certain aspects, advantages, and novel features are described herein. It is to be understood that not necessarily all such advantages may be achieved in accordance with any particular embodiment. Thus, for example, those skilled in the art will recognize that the disclosure may be embodied or carried out in a manner that achieves one advantage or a group of advantages as taught herein without necessarily achieving other advantages as may be taught or suggested herein.

Moreover, while illustrative embodiments have been described herein, the scope of any and all embodiments having equivalent elements, modifications, omissions, combinations (e.g., of aspects across various embodiments), adaptations and/or alterations as would be appreciated by those skilled in the art based on the present disclosure. The limitations in the claims are to be interpreted broadly based on the language employed in the claims and not limited to the examples described in the present specification or during the prosecution of the application, which examples are to be construed as non-exclusive. Further, the actions of the disclosed processes and methods may be modified in any manner, including by reordering actions and/or inserting additional actions and/or deleting actions. It is intended, therefore, that the specification and examples be considered as illustrative only, with a true scope and spirit being indicated by the claims and their full scope of equivalents.

Claims

1. An intraocular lens comprising: a toric refractive element adapted to counter astigmatism in a human patient's eye;one or more haptics configured to position the intraocular lens in the eye, the one or more haptics extending from a fixed end disposed at a periphery of the toric refractive element to a free end adapted to contact an inner surface of the eye, the one or more haptics forming an anterior edge of the intraocular lens when implanted in the eye; anda mask configured to prevent a substantial portion of light from passing through an annular region thereof and to permit light to pass through a central aperture thereof to increase depth of focus, a diameter of the central aperture is at least 0.85 mm and less than or equal to 2.8 mm,wherein a combination of the toric refractive element and the mask is configured to increase tolerance to rotational misplacement within the patient's eye within a 30 degree window.

2. The intraocular lens of claim 1, wherein the mask is coupled with a face of an optic incorporating the mask.

3. The intraocular lens of claim 2, wherein the mask is formed on a piggyback IOL configured to couple with the eye to place the mask on the face of the optic.

4. The intraocular lens of claim 1, wherein the mask is embedded in an optic comprising the refractive element.

5. The intraocular lens of claim 1, wherein the mask comprises a plurality of small holes disposed through the annular region to secure the mask to an optic including the refractive element.

6. The intraocular lens of claim 1, wherein the mask is configured to increase depth of focus by a magnitude equivalent to up to 2 diopters of add power.

7. The intraocular lens of claim 1, wherein the refractive element comprises a rotational alignment feature.

8. The intraocular lens of claim 1, wherein the intraocular lens is configured to maintain visual acuity of at least 20/20 from 0.0 diopters to +/− 2.0 diopters of defocus.

9. The intraocular lens of claim 1, wherein the mask comprises an elastic material.

10. The intraocular lens of claim 1, wherein the 30 degree window is +/− 15 degrees.

11. The intraocular lens of claim 1, wherein the intraocular lens is a monofocal intraocular lens.

12. The intraocular lens of claim 1, wherein the one or more haptics are vaulted with respect to the refractive element.

13. The intraocular lens of claim 1, wherein the one or more haptics are flat with respect to the refractive element.

14. An intraocular lens comprising: a toric refractive element adapted to counter astigmatism in a human patient's eye;one or more haptics configured to position the intraocular lens in the eye, the one or more haptics extending from a fixed end disposed at a periphery of the toric refractive element to a free end adapted to contact an inner surface of the eye, the toric refractive element forming an anterior edge of the intraocular lens when implanted in the eye; anda mask configured to block a substantial portion of light from passing through an annular region thereof and to permit a substantial portion of light to pass through a central aperture thereof to increase depth of focus;wherein the intraocular lens is configured to maintain visual acuity of at least 20/20 within +/− 15 degrees of rotational misplacement.

15. The intraocular lens of claim 14, wherein the one or more haptics are vaulted with respect to the refractive element.

16. The intraocular lens of claim 14, wherein the one or more haptics are flat with respect to the refractive element.