KR20090094047A - Ophthalmic dynamic aperture - Google Patents

Abstract

Embodiments of the present invention relate to an electro-active element having a dynamic aperture. The electro-active element provides increased depth of field and may be used in a non-focusing ophthalmic device that that is spaced apart from but in optical communication with an intraocular lens, a corneal inlay, a corneal onlay, a contact lens, or a spectacle lens that provide an optical power. The electro-active element provides increased depth of field and may also be used in a focusing or non-focusing device such as an intraocular optic, an intraocular lens, a corneal inlay, a corneal onlay, or a contact lens which may or may not have an optical power. By changing the diameter of dynamic aperture either increased depth of field or increased light reaching the retina may be achieved.

Description

Ophthalmic dynamic aperture

Cross-References to Related Applications

This application claims the priority of the following provisional applications and includes them by reference in their entirety:

US Application No. 60 / 902,866, filed Feb. 23, 2007, entitled “Electro-Active Ophthalmic Device for Correcting Refractive Errors in Human Eyes”;

US application Ser. No. 61 / 020,759, filed Jan. 14, 208 under the name "Electro-Active Ophthalmic Optics or Lenses with Dynamic Aperture"; and

US Application No. 61 / 025,348, filed Feb. 1, 2008 entitled "Operational Lens or Optic Light Transmission Numerical Ranges With Central Aperture to Provide Increased Depth of Focus."

The present invention relates to intraocular optics, intraocular lenses, corneal inlays, corneal onlays and contact lenses. More specifically, the present invention relates to ophthalmic lenses and light that at least partially corrects the user's eye's common errors (low order aberrations such as myopia, hyperopia, regular astigmatism and presbyopia) and / or non-normal errors (such as high order aberrations). It relates to intraocular optics, intraocular lenses, corneal inlays, corneal onlays and contact lenses with dynamic apertures for increasing the depth of field used to or in communication thereof. The system of the present invention with optical aperture or optical aperture with an ophthalmic lens (single vision or multifocal lens) to provide increased depth of field and correct vision errors (such as presbyopia) is short to long range. It enables the most continuous range of perceived focus.

Description of related fields

There are two main conditions that affect an individual's ability to focus on long and medium distance objects. Presbyopia is a loss of regulation of the human eye lens, mainly associated with aging. For presbyopia individuals, this loss of control prevents them from focusing on a distant object first and then on a medium-range object. It is estimated that there are about 90 million to 100 million presbyopia in the United States. It is estimated that there are about 1.6 billion presbyopia worldwide. Aphakia is generally the absence of an ocular lens due to surgical removal during cataract surgery. In the case of an amorphous individual, the absence of the lens causes a complete loss of control that prevents the user from focusing on a distant or medium distance object. For all practical purposes an individual will get cataracts if he or she lives long enough. Moreover, most individuals with cataracts will have cataract surgery at some point in their lives. An estimated 1.2 million cataract surgeries are performed annually in the United States.

Standard tools for correcting presbyopia are reading glasses, multifocal ophthalmic lenses, and monocular fit contact lenses. Reading glasses have a single optical power to correct near focusing problems. Multifocal lenses are lenses with one or more focal lengths (ie optical powers) to correct focusing problems across a range of distances. Multifocal lenses are used in eyeglasses, contact lenses, corneal inlays, corneal onlays and intraocular lenses (IOLs). Multifocal ophthalmic lenses work by dividing the lens region into different optical power zones. Multifocal lenses consist of a continuous surface that produces continuous optical power as in progressive multifocal lenses (PAL). Multifocal lenses also consist of discontinuous surfaces that produce discontinuous optical power, such as in bifocal or trifocal. Monocular fit contact lenses are two contact lenses with different optical powers. One contact lens is mainly for correcting a far focusing problem and the other is mainly for correcting a short focusing problem.

The standard tool for correcting an amorphous phase is an intraocular lens (IOL). The first form of IOL is a single vision or multifocal IOL that is non-regulatory and cannot change its optical power. The second form of IOL is a modulating IOL that can change its focal power by, for example, compression of the surface, translation, mechanical bending, or a combination thereof. In addition, an amorphous lens is corrected by using a single vision IOL in one eye and multifocal or regulatory IOL in another eye or a combination thereof.

Another approach is also used to correct presbyopia. One approach is corneal inlays that provide small fixed crop diameters. As an example, the ACI 7000 corneal inlay manufactured by AcuFocus includes an opaque ring with a transparent opening of about 3.8 mm in diameter, 10 μm thick and 1.6 mm in diameter. Such openings serve to reduce the aperture of the human eye to a smaller diameter than generally achievable by the natural contraction of the pupil.

As known in the art, limiting the diameter of the optical system aperture increases the depth of field of the system. The depth of field is the distance between the front and back of the object plane that appears to be in focus on the image plane. In systems with increased depth of field, the optical system can only provide accurate focus of the object at the focal length, but the decrease in sharpness on the focal length side is gradual. Thus, the haze generated on the image plane within the depth of field is mild under normal viewing conditions. The aperture is used to increase the depth of field by eliminating at least some of the light rays that produce a large angle to the optical axis of the lens (non-axis light). Non-axis light rays are sharply focused when they are caused by objects located at focal lengths. For objects located at different distances, the non-axis light rays have a maximum deviation from the image plane. By eliminating non-axis light rays the deviation from the image plane is minimized and objects located within a fixed distance of the focal length (ie within the depth of field) are visible within the focal point.

Small apertures create a larger range of distances that appear in focus, obstructing some of the presbyopia effects and allowing the presbyopian to perform remote tasks without the need for multifocal contacts or spectacle lenses. ACI 7000 is made of a bio-compatible material with static optical properties such as, for example, polyvinylidene chloride or non-hydrogel porous perfluoroether. Thus, when the inlay is located in the cornea, its refractive optical power is fixed.

While effective, AcuFocus corneal inlays reduce the amount of light reaching the cornea. Moreover, inlays are generally implanted only if the harmful optical effects are too large, such as halos, field of view, light scattering, glare, loss of contrast, and / or reduction of light striking the retina and are acceptable if the inlay is implanted into both eyes. Can't be. These deleterious effects are caused by occluded rings related to the aperture size and pupil size of the inlay.

Another approach to correcting presbyopia is corneal refractive surgery in which one eye is corrected for distant and the other eye is corrected for near. Another approach is corneal inlays that provide multifocal effects, for example using diffractive optics.

However, each of these approaches to correct presbyopia and / or aphasis has drawbacks. Of course, some of these drawbacks are more serious than others. For example, eyewear can correct vision for long, near and medium distances, but this approach requires the wearing of devices that are inherently collected. In some cases, certain multifocal lenses also allow users to perceive distortion and experience dizziness.

Approaches for presbyopia and / or aphagia correction, including the use of contact lenses, can cause discomfort and include one or more of halo, doubled vision, light scattering, glare, loss of contrast, limited focus range, and / or reduction of light striking the retina. May cause. Approaches, including the use of IOLs, can cause one or more of light scattering, glare, halo, illusion, loss of contrast, limited focus range, and / or reduction of light striking the retina.

These defects or damage to vision can be very problematic, especially when driving at night, driving in the rain, or doing computer work, for example. Thus, there is a need for an excellent method of presbyopia and / or aphasis correction.

Embodiments of the present invention will be more fully understood and appreciated by the detailed description in conjunction with the drawings, wherein reference numerals indicate corresponding, similar or similar elements:

1 shows a cross-sectional view of a healthy human eye.

2A shows an exploded cross-sectional side view of an embodiment of an electro-active element with dynamic aperture.

FIG. 2B shows a breakaway cross-sectional view of the electro-active element of FIG. 2A.

3 illustrates a number of electrode rings that are feasible to create a dynamic aperture.

4A shows an exploded cross-sectional side view of an embodiment of an electro-active element with dynamic aperture.

FIG. 5 shows various arrangements of the electrode rings shown in FIG. 3 characterized in that the geometric center of the dynamic aperture is repositioned with respect to the geometric center of the pupil in accordance with an embodiment of the invention.

FIG. 6 shows a stack of five electro-active elements used for the other arrangement of electrode rings shown in FIG. 5 in accordance with an embodiment of the invention.

7A, 7B and 7C illustrate embodiments of the invention with dynamic aperture useful as corneal inlays, corneal onlays or contact lenses.

8 illustrates an IOO located in front of the eye and in optical communication with a healthy presbyopia lens in accordance with an embodiment of the invention.

9 illustrates an IOO located in front of the eye and in optical communication with the IOL in accordance with an embodiment of the present invention.

10 illustrates IOO in front of the eye and in optical communication with an IOL that corrects distant vision only in accordance with embodiments of the present invention.

11 shows an IOL located in front of the eye and correcting for far and near vision according to embodiments of the present invention and IOO for optical communication.

12 illustrates an IOO located in front of the eye and in optical communication with the IOL in accordance with an embodiment of the present invention.

FIG. 13 shows an IOL with dynamic aperture in the portion of the IOL closest to the eye pupil in accordance with embodiments of the present invention.

14 illustrates an IOL with dynamic aperture in the central portion of the IOL in accordance with an embodiment of the present invention.

15 illustrates an IOL with dynamic aperture in the portion of the IOL closest to the ocular retina in accordance with an embodiment of the present invention.

16 illustrates a corneal inlay with dynamic aperture in optical communication with a healthy presbyopia lens in accordance with an embodiment of the present invention.

17 illustrates a corneal inlay with dynamic aperture in optical communication with an IOL in accordance with an embodiment of the present invention.

FIG. 18 shows that the sensor senses an increase in light upon the pupil's pupil contraction during daylight or during light and according to an embodiment of the present invention, the controller causes the reverse aperture in the electro-active element to die.

FIG. 19 illustrates that the sensor senses darkness and the controller causes the dynamic aperture in the electro-active element to enlarge when the user pupil enlarges at night or in darkness in accordance with an embodiment of the present invention.

20 illustrates the normal operation of the ignored sensors and controllers in which the dynamic aperture in the electro-active element contracts for distant work in dim lighting conditions even when the user pupil is enlarged in accordance with an embodiment of the present invention.

Figure 21 illustrates an overlapping optic or lens of the present invention with one or more electro-active elements in accordance with embodiments of the present invention.

Summary of the Invention

In one embodiment of the present invention the ophthalmic device comprises an electro-active element comprising a mainly opaque ring for providing a substantially transparent dynamic aperture with a variable diameter and an increased depth of field, the ophthalmic device comprising a user's eye. And optical communication with one of an intraocular lens, corneal inlay, corneal onlay, contact lens or spectacle lens with optical power to provide at least partial correction of refractive error.

In one embodiment of the present invention the ophthalmic device comprises an electro-active element comprising a mainly opaque ring for providing a predominantly transparent dynamic aperture with an alterable diameter and an increased depth of field, said electro-active The element is characterized in that it is a component of one of an intraocular lens, corneal inlay, corneal onlay or contact lens with optical power to provide at least partial correction of the refractive error of the user's eye.

In an embodiment of the present invention the ophthalmic device comprises a first electro-active element with optical power to provide at least partial correction of the refractive error of the user's eye. The ophthalmic device further comprises a second electro-active element having substantially no optical power including mainly transparent dynamic apertures with varying diameters and mainly opaque rings to provide increased depth of field, first and second And the first electro-active element is in optical communication with each other.

In an embodiment of the present invention the ophthalmic device comprises an electro-active element comprising mainly transparent dynamic apertures with varying diameters and mainly opaque rings for providing increased depth of field, the center of the dynamic aperture of the user Repositioned to the line of sight.

Description of Preferred Embodiments

Electro-active elements are devices with optical properties that can be altered in electrical energy applications. Modifiable optical properties are, for example, optical power, focal length, diffraction efficiency, depth of field, transmittance, coloration, opacity or combinations of the above. The electro-active element consists of two substrates. The electro-active material is arranged between the two substrates. The substrate is of a shape and size that ensures that the electro-active material is contained within the substrate and that it cannot leak. One or more electrodes are arranged on each surface of the substrate in contact with the electro-active material. The electro-active element comprises a power supply operatively connected to the controller. The controller is operatively connected to the electrodes by electrical connections to apply one or more voltages to each electrode. When electrical energy is applied to the electro-active material by the electrode, the optical properties of the electro-active material change. For example, when electrical energy is applied to an electro-active material by an electrode, the refractive index of the electro-active material is changed to change the optical power of the electro-active element.

The electro-active element is recessed or attached to the surface of the ophthalmic lens to form an electro-active lens. The electro-active element is also recessed or attached to the surface of the optic that does not substantially provide optical power to form the electro-active optic. In this case, the electro-active element is in optical communication with the ophthalmic lens but is not separated from, or spaced apart from, the component. Ophthalmic lenses are optical substrates or lenses. A "lens" is a device or part of a device that causes light to converge or diverge (ie, a lens can focus light). The lens is concave, convex or flat on one or both surfaces. The lens is spherical, cylindrical, prism or a combination thereof. The lens is made of optical glass, plastic, thermoplastic, thermosetting resin, a mixture of glass and resin, or a mixture of other optical grade resins or plastics. It is to be appreciated that within the optics industry a device may be marked with a lens even when it has zero optical power (known to be flat or without optical power). In this case, however, the lens is generally referred to as a "planar lens." The lens is conventional or non-traditional. Conventional lenses correct eye errors, including low order aberrations such as myopia, hyperopia, presbyopia and regular astigmatism. Non-traditional lenses correct non-traumatic errors of the eye, including high-order aberrations that can be caused by ocular layer irregularities or malformations. The lens is a multifocal lens such as a single focal lens or progressive multifocal lens or a bifocal or trifocal lens. In contrast, as used herein, an "optic" is substantially free of optical power and cannot concentrate light (by refraction or diffraction). The term "refractive error" refers to a typical or non-normal error of the eye. It should be noted that light re-orientation does not correct the refractive error of the eye. Thus, for example, light re-orientation to the healthy part of the retina does not correct the refractive error of the eye.

The electro-active element is located in the entire viewing area or only a portion of the electro-active element of the lens. The electro-active element is located near the top, center or bottom part of the lens or optic. It should be noted that the electro-active element can concentrate light on itself and need not be combined with an optical substrate or lens.

1 shows a cross section of a healthy human eye 100. The white part of the eye is known as the sclera 110. The sclera is covered with a clear membrane known as the conjunctiva. The central transparent part of the eye that provides most of the optical power of the eye is the cornea 130. Iris 140 is the colored part of the eye and forms the pupil 150. The tightening muscles contract the pupil and the enlarged muscles enlarge the pupil. The pupil is the natural aperture of the eye. Anterior 160 is a fluid-filled space between the iris and the deepest surface of the cornea. The lens 170 remains within the capsular bag 175 and provides the remaining optical power of the eye. A healthy lens can change its optical power so that the eye, a process known as perspective control, can focus at far, medium and near distances. Posterior 180 is the space between the back surface of the iris and the front surface of the retina 190. The retina is the "image plane" of the eye and connects to the optic nerve 195, which delivers visual information to the brain.

Static (non-dynamic) small diameters benefit from large depth of field but also a loss of reduced light transmission through the lens or optics. Similarly, static large diameters benefit from increased light transmission through the lens or optics but also with a loss of reduced depth of field.

Embodiments of the present invention include an ophthalmic device (expressed herein as a lens or optic of the present invention) having an electro-active element (marked herein as a lens or optic of the present invention) having a dynamic aperture. Dynamic apertures are apertures with varying diameters. The aperture diameter of the dynamic aperture is switchable between two or more diameters, for example the first and second diameters. Dynamic apertures are switched between diameters continuously (ie in a flat transition) or discontinuously (ie in separate steps). Dynamic apertures have a minimum aperture diameter other than 0- or are fully proximate so that the aperture diameter is zero. Dynamic apertures produce apertures that are circular, elliptical, or of any shape.

Embodiments of the present invention have a dynamic aperture that can be changed between a reduced size for increased depth of field (and reduced light transmission) and an increased size for increased light transmission (and reduced depth of field). In one embodiment where the large depth of field is most beneficial to the user, the size of the dynamic aperture is reduced for far and / or medium distance vision. Dynamic apertures increase in size from moderate diameters to moderate distance vision to large diameters to moderate medium vision. Since large depth of field is not critical for far vision, the diameter of the dynamic aperture is further increased to a size suitable for far vision, in order to provide increased light transmission.

As used herein intraocular optics (IOOs) are optics (substantially free of optical power) that are inserted or implanted into the eye. Intraocular optics are inserted or implanted in the anterior or posterior of the eye, in the epilepsy of the cornea (similar to corneal inlays), in the epidermal layer of the cornea (similar to corneal onlays), or in any anatomical structure of the eye. The guided optics have substantially zero optical power and thus cannot concentrate light. In contrast, intraocular optics in embodiments of the present invention may have increased aperture and provide increased depth of field.

As used herein, an intraocular lens (IOL) is a lens (with optical power) that is inserted or implanted into the eye. The intraocular lens (IOL) is inserted or implanted in the anterior or posterior of the eye, in the epilepsy of the cornea (similar to the corneal inlay) or in the epidermal layer of the cornea (similar to the corneal onlay) or in any anatomical structure of the eye. The intraocular lens has one or more optical powers and with or without dynamic aperture in embodiments of the present invention. If the IOL has a dynamic aperture it is possible to provide increased depth of field.

As used herein, corneal inlays are optics (with virtually no optical power) or lenses (with optical power) that are inserted or recognized within the epilepsy of the cornea. The term "corneal inlay optics" or "planar corneal inlays" is used to describe corneal inlay optics in detail. In describing corneal inlay lenses in detail, the terms “corneal inlay lens” or “focal corneal inlay” are used. As used herein, corneal onlays are optics (with virtually no optical power) or lenses (with optical power) that are inserted or implanted into the epidermal layer of the cornea. In describing corneal onlay optics in detail, the terms "corneal onlay optics" or "planar corneal onlays" are used. In describing corneal onlay lenses in detail, the terms "corneal onlay lens" or "focal corneal onlay" are used. As used herein, a contact lens is a removable optic (with virtually no optical power) or a lens (with optical power) located at the top of the cornea. In describing the contact lens optics in detail, the terms "contact lens optic" or "planar contact lens" are used. The term "focusing contact lens" is used when describing the contact lens in detail.

In an embodiment of the present invention the electro-active element with dynamic aperture becomes a component of the contact lens, corneal inlay, corneal onlay, IOO or IOL (ie, recessed or attached thereto). IOO or IOL is inserted or implanted in the anterior or posterior of the eye, in the epilepsy of the cornea (such as corneal inlay) or in the epidermal layer of the cornea (such as corneal onlay). Corneal inlays, corneal onlays and contact lenses are lenses capable of concentrating light (and therefore with optical power) or optics (and therefore substantially having no optical power) that are unable to concentrate light. Embodiments of the present invention provide for increased depth of field. Some embodiments of the present invention provide increased depth of field and at least partially correct for common and / or non-traditional errors of the user's eye. Embodiments of the present invention are used for optical communication with one or more of the following devices capable of focusing light and at least partially correcting common and / or non-traditional errors of a user's eye: spectacle lenses, contact lenses, corneal inlays, Corneal onlay or intraocular lens. Embodiments of the present invention also provide a dynamic aperture that is in optical communication with or is a component of an ophthalmic lens (which is a single vision or multifocal lens) that provides increased depth of field and corrects vision errors (such as presbyopia). To provide a system. Most continuous ranges of focus range from near to far, far to middle, mid to far, or any distance range.

2A shows an exploded cross-sectional side view of an embodiment of an electro-active element 200 with dynamic aperture. FIG. 2B shows a breakaway cross-sectional view of the electro-active element of FIG. 2A. One or more electro-active elements 200 may be used in contact lenses, corneal inlays, corneal onlays, IOO or IOL. Where more than one electro-active element is used, the electro-active element is stacked on top of one another when a suitable insulator is present between the elements.

The electro-active element 200 comprises two optical substrates 210 or is joined by two optical substrates. Two substrates are substantially flat and parallel or bent and parallel or one substrate has a surface relief diffractive pattern and another substrate is substantially flat. The substrate provides optical power or the substrate does not have optical power. Each substrate has a thickness of 200 μm or less. Thinner substrates generally allow a higher degree of flexibility for the electro-active elements important in certain embodiments of the present invention to be inserted or implanted into the eye. A continuous optically transparent electrode 220 providing electrical ground is arranged on the second substrate. Electrode 225 determines the characteristics of the dynamic aperture, such as the size, shape and / or diameter of the dynamic aperture. Electrodes 220 and 225 are composed of, for example, known transparent conductive oxides (such as ITO) or conductive organic materials (such as PEDOT: PSS or carbon nano-tubes). As for the thickness of an optically transparent electrode, 1 micrometer or less but 0.1 micrometer or less are preferable, for example. Electrodes 220 and 225 are coated with alignment layer 230. Also only one of the electrodes is coated with the alignment layer. The electrode material 240 is arranged between the alignment layers. The thickness of the electro-active material is between 1 μm and 10 μm but preferably 5 μm or less. The electro-active material is a liquid crystal material. The liquid crystal material is a nematic liquid crystal, a twisted nematic liquid crystal, a top-twisted nematic liquid crystal, a cholesteric liquid crystal, a smectic double-stable liquid crystal or any form of liquid crystal material. The alignment layer is, for example, a thin film of 100 nanometers binomial thickness and consists of polyimide material. The thin film is applied on the substrate surface in direct contact with the liquid crystal material. Before assembly of the electro-active element, the membrane is cushioned in one direction (alignment direction) with a velvet-like cloth. When the liquid crystal molecules come into contact with the buffered polyimide layer, the liquid crystal molecules are preferentially placed in the plane of the substrate and aligned in the direction in which the polyimide layer is rubbed (ie parallel to the substrate surface). The alignment layer also consists of a photosensitive material which produces the same results as when a buffered alignment layer is used upon exposure to linearly polarized UV light.

Controller 250 is connected to electrodes 220 and 225 by electrical connection 255 and is capable of generating an electric field between the electrodes by applying one or more voltages to each electrode. In some embodiments the controller is part of an electro-active element. In another embodiment the controller is located outside of the electro-active element and connected to the electrode using an electrical contact point in the electro-active element. The controller is connected to a power supply, a sensor or any other necessary electronic component. In the absence of an electric field between the electrodes, the liquid crystal molecules are aligned in the same direction as the alignment direction. In the presence of an electric field between the electrodes, the liquid crystal molecules are deflected in the electric field direction. The electric field in the electro-active element is perpendicular to the alignment layer. Thus, when the electric field is strong enough, the orientation of the liquid crystal molecules will be perpendicular to the alignment direction. If the electric field is not strong enough, the orientation of the liquid crystal molecules will be some direction between the alignment direction and the perpendicular of the alignment direction. It should be noted that the substrate is as wide or wider than the electrode, the alignment layer and the electro-active material.

The electro-active element has an aperture 260 through which light passes and a ring 270 that absorbs or scatters light. As known in the art, the change in dynamic aperture size is generally inversely proportional to the change in depth of field of the electro-active element and is directly proportional to the change in light transmission through the electro-active element. The aperture is dynamic and switchable between one or more diameters. The ring is located at the peripheral boundary of the electro-active element and spaced apart from the peripheral boundary. The ring extends to the radial center of the electro-active element. The aperture is located at the geometric center of the electro-active element and extendable in all directions from the peripheral boundary of the electro-active element, a fixed distance from the peripheral boundary or a radial distance from the geometric center of the electro-active element. In another embodiment the aperture is repositionable such that the center of the aperture is not the same as the geometric center of the electro-active element. Collars generally frame the caliber and define the outer limits and size of the caliber. As described in more detail herein, the aperture is altered to achieve a diameter size of any continuous or discontinuous range.

The electro-active material includes a liquid crystal layer treated with a dye material such as a dichroic dye. By treating the liquid crystal molecules with a dye material, the dye molecules align themselves with the liquid crystal molecules. The dye molecules are polar and rotated to align with the applied electric field. Absorption of the dye material depends on the orientation of the individual dye molecules to the projected light waves. If the electric field between the electrodes is not strong enough in the inactivated state to the homogeneous (horizontal) alignment of the liquid crystal molecules, the dye molecules are aligned with the alignment layer and light absorption through the liquid crystal is maximized. When the electric field between the electrodes is strong enough in the activated state to the homogeneous (horizontal) alignment of the liquid crystal molecules, the dye molecules are rotated and aligned with the orientation of the electric field perpendicular to the direction of the spirit. Light absorption through the liquid crystal in this orientation is minimized. The opposite is the case where homeotropic (vertical) alignment of liquid crystals is used where absorption is minimized in the inactive state and maximized in the activated state. Ferroelectric liquid crystal materials are also used.

3 is a plurality of electrode rings 300 that may be implemented to create a dynamic aperture. The electrode ring is useful as an optically transparent electrode 225 in the electro-active element 200. In this embodiment, the electro-active material 240 is a liquid crystal treated with a dichroic dye. Electrode ring 300 is composed of electrodes 310, 320, 330 and 340 of various annular shapes. Of course, if the electro-active element is located in or above the eye, fewer or more rings are concentrated about multiple axes. The inner-electrode gap is about 5 μm to 10 μm but smaller. The inner diameter of the electrode 310 is r1, the outer diameter of the electrode 310 is r2, the outer diameter of the electrode 320 is r3, the outer diameter of the electrode 330 is r4, and the outer diameter of the electrode 340 is r5. The inner diameter of each electrode defines a different aperture size.

The electrode is "activated" if a sufficiently strong electric field is applied between the electrode and the ground electrode, or a voltage above the threshold is applied to the electrode or the condition of placing the electro-active material between the electrode and the ground electrode in an activated state is met. The electrode is " deactivated " if a sufficiently strong electric field is not applied between the electrode and the ground electrode, or a voltage below the threshold is applied to the electrode or the condition of placing the electro-active material between the electrode and the ground electrode in an inactive state is met.

In an embodiment of the invention using a liquid crystal material, the liquid crystal material is activated when a voltage above about 10 volts is applied between the electrodes and is deactivated when a voltage below about 10 volts is applied between the electrodes. The power used is about 1 microwatt. It should be appreciated that the potential can be, for example, 1 volt or less, 5 volts or less, 10 volts or less, or 10 volts or more.

Dual-stable liquid crystal materials are used to reduce power consumption. The double-stable liquid crystal material is switched between one of two stable states upon application of power (one state is active and the other is inactive). To convert the dual-stable liquid crystal material into another stable state, the double-stable liquid crystal material is kept in one stable state until sufficient power is applied. Thus, power is only needed to transition from one state to another, not to remain in that state. The double-stable liquid crystal material is converted to the first state when more than +5 volts are applied between the electrodes and to the second state when less than -5 volts is applied between the electrodes. Of course, other higher and lower voltages are possible.

In embodiments of the present invention, when electrodes 310, 320, 330 and 340 are activated, opaque ring 270 will be formed between r1 and r5 and aperture 260 will be formed between electrode center and r1. When the electrode 310 is deactivated, an opaque ring will be formed between the inner diameter of the electrode 320 and r5 and the aperture 260 will be formed between the center of the electrode and the inner diameter of the electrode 320. If the electrodes 310, 320, 330 and 340 are deactivated, the opaque ring 270 will not be present and the aperture 260 will not be formed between the center of the electrode and r5. The aperture is increased by first deactivating electrode 310 and then electrode 320 and finally electrode 340. The aperture is reduced by first activating electrode 340 and then electrode 330 and then electrode 320 and finally electrode 310. Thus, there are five possible aperture adjustment devices as shown in FIG. 3. However, fewer or more aperture adjustments are possible. As with the camera, each aperture adjuster provides an aperture with twice the following minimum aperture size area. That is, the square root of two correlations exists between the inner diameters of each electrode. Of course, other aperture sizes are possible. When fully retracted, the aperture diameter is between about 1.0 mm and about 3.0 mm, preferably between about 1.0 mm and about 2.5 mm, more preferably between about 1.0 mm and about 2.0 mm. When fully enlarged, the aperture diameter is about 7.0 mm or more. In certain embodiments, no aperture is present in a dark or dim environment (ie, no rings present, so the pupil of the eye acts as a natural aperture).

In embodiments of the present invention the outer boundary of the ring extends further (if fully enlarged or contracted) than the outer boundary of the pupil. If there is a gap between the outer boundary of the ring and the outer boundary of the pupil, deleterious effects such as, for example, halo, light scattering and reduced contrast sensitivity occur.

In one embodiment each electrode ring is activated almost simultaneously with a momentary change in aperture. In another embodiment each electrode ring is continuously activated or deactivated for fade in and out effects that gradually reduce or enlarge the dynamic aperture. For example, the outermost electrode ring is activated first and finally deactivated, and the innermost electrode ring is finally activated and deactivated first. In one embodiment the electrode is activated or deactivated for less than about 1 second and preferably activated or deactivated for less than about 0.5 seconds.

In another embodiment of the present invention, electrode 225 is a plurality of individually addressable electrodes arranged in a grid. Each electrode is labeled "pixel" (in this case, the electrode is labeled "pixelated"). Pixels can be any size or shape. Aperture 260 and ring 270 are formed by selectively electrically activating or deactivating the pixel.

4A shows an exploded cross-sectional side view of an embodiment of an electro-active element 400 with dynamic aperture. 4B shows a cross-sectional cross-sectional view of the electro-active element of FIG. 4A. Similar to the electro-active element 200, the electro-active element 400 comprises two optical substrates 210. A continuous optically transparent electrode 220 providing electrical ground is arranged on one substrate and one or more individually addressable optically transparent electrodes 225 are arranged on a second substrate. Electrode 225 determines the characteristics of the dynamic aperture, such as the size, shape and / or diameter of the dynamic aperture. Electrodes 220 and 225 are coated with alignment layer 230. The alignment layers have a 90 degree offset against each other but other values such as 180, 270, 360 degrees are possible. The electro-active material 240 is arranged between the alignment layers. The electro-active material is one of liquid crystal materials, preferably nematic, cholesteric or smectic double-stable liquid crystal materials. The liquid crystal material is treated with a dichroic dye and becomes a dichroic liquid crystal material. Controller 250 is connected to electrodes 220 and 225 by electrical connection 255 and is capable of generating an electric field between the electrodes. The electro-active element has aperture 260 through which light passes and ring 270 through which light is absorbed or scattered. The electro-active element 400 further comprises two polarizers located on the side of the electro-active material (eg outside of the electrode). The polarizer is also located on the outer surface of the substrate (the electrode is located on the innermost surface of the substrate). Each of the planarizers has a polarization direction parallel to the collimator of the liquid crystal layer (ie parallel to the alignment direction of the nearest alignment layer) at its respective outer surface. The polarizer has, for example, a relative direction of 90 degrees of polarization cancellation. Such offset polarizers are referred to as "crossed" polarizers.

If the electric field between the electrodes is not strong enough in the deactivated state, the alignment layer is directed towards the coordinator of the liquid crystal layer to align with the polarizer at the outer surface. In this orientation the light entering the first polarizer (ie light polarized parallel to the polarization direction of the first polarizer) can be rotated 90 degrees by the liquid crystal and pass through the second polarizer (ie light is the second polarizer). Polarized parallel to the polarization direction of. Thus light absorption through the electro-active element in the deactivated state is minimized. When the electric field between the electrodes is sufficiently strong in the activated state, the liquid crystal molecules are aligned with the electric field direction perpendicular to the alignment direction. In this orientation the light entering the first polarizer (i.e. light polarized parallel to the polarization direction of the first polarizer) is not rotated and is blocked by the second polarizer (i.e. the light is polarized perpendicular to the polarization direction of the second polarizer). being). Thus, the light absorption in the activated state is maximized.

The electrode ring shown in FIG. 3 is useful as an optically transparent electrode 225 in the electro-active element 400. As described above, when the electrodes 310, 320, 330 and 340 are activated, the opaque ring 270 will be formed between r1 and r5 and the aperture 260 will be formed between the center and r1 of the electrode. When the electrode 310 is deactivated, an opaque ring will be formed between the inner diameter of the electrode 320 and r5 and the aperture 260 will be formed between the center of the electrode and the inner diameter of the electrode 320. If the electrodes 310, 320, 330 and 340 are deactivated, the opaque ring 270 will not be present and the aperture 260 will be formed between the center of the electrode and r5.

One drawback of this embodiment is that the polarizing film absorbs about 50% of the projected light. Thus, the use of such films in practical devices limits the amount of light that reaches the retina. In an embodiment of the invention the concentric regions of the annular electrode are physically removed at one or both polarizers. The removed region may be of any size or shape but in a preferred embodiment is equal to the inner diameter of the minimum ring electrode. One or more polarizers are used while eliminating this central region to increase the overall transmission through the electro-active element. In this embodiment the functionality of the dynamic aperture is not affected and the overall transmission is increased. Moreover, the transmission contrast ratio between the aperture and the ring (the ratio between the light transmitted through the aperture and the light transmitted through the ring) is increased, making the dynamic aperture more effective in providing depth of field. In another embodiment, instead of removing the region, the region consists of a thinner or more effective polarizing film used to increase transmission, which favors performance in the transmission state over the opaque state. This embodiment increases the transmission contrast between the darkened region and the aperture region of the ring.

Since the eye is asymmetric in normal anatomical shape, it is practically impossible to have an implanted corneal inlay, corneal onlay, IOO or IOL that is perfectly focused on the optical axis of the eye. The most preferred implant position is aligned with the central axis of the pupil. Nevertheless, an eyeball deviation of about 0.1 mm or 0.2 mm should be expected with respect to the center of the eye pupil under normal anatomical conditions. The same is true for contact lenses that are not surgically implanted and that lie on the cornea or its tear layer.

FIG. 5 illustrates various arrangements of the electrode rings shown in FIG. 3 in accordance with an embodiment of the invention wherein the geometric center of the dynamic aperture is repositioned relative to the geometric center of the pupil. Array A has the geometric center of the ring electrode aligned with the geometric center of the substrate of the electro-active element. Arrangements B, C, D and E each have the geometric center of the ring electrode aligned to the left, right, top and bottom with respect to the geometric center of the substrate of the electro-active element. Each of the arrangements A, B, C, D and E is used in separate electro-active elements. FIG. 6 shows a stack of five electro-active elements, each used for another arrangement of the ring electrode shown in FIG. 5 in accordance with an embodiment of the present invention. Each electro-active element is suitably insulated from other electro-active elements. The distance between the geometric center of the ring electrode and the geometric center of the substrate is between about 0.0 mm and about 1 mm, more preferably between about 0.0 mm and about 0.5 mm. It should be noted that other alignment of any angle between the two centers is possible. This embodiment enables the ability to change the center of dynamic aperture by remote control after the implant of the present invention is surgically implanted. One or more arrangements of ring electrodes are activated to exclude other arrangements to re-align the dynamic aperture center with respect to the user's line of sight. This is important when the implant of the present invention is surgically implanted outside of alignment with the user's gaze. Certain retinal diseases or traumas such as macular degeneration, retinal tears or retinal detachment damage the retinal area. This embodiment is also useful for rearranging the user's gaze from the damaged retinal area to a healthy retinal area.

In embodiments of the invention where the electrode 225 is a plurality of individually addressable electrodes arranged in a grid, the individual pixels are selectively arranged to reposition the geometric centers of the apertures 260 and the ring 270 relative to the geometric center of the substrate or the pupil of the eye. It is activated or deactivated.

The electro-active element is switchable between the first optical power and the second optical power. The electro-active element has the first optical power in the inactive state and the second optical power in the active state. The electro-active element is deactivated when one or more voltages applied to the electrodes of the electro-active element are below the first predetermined threshold. The electro-active element is activated when one or more voltages applied to the electrodes of the electro-active element are above a second predetermined threshold. The electro-active element can also "tune" its optical power such that the electro-active element can provide a continuous or substantially continuous optical power change between the first and second optical powers.

Electro-active lenses are used to correct typical or non-traditional errors in the eye. Calibration is produced by electro-active elements, by optical substrates or ophthalmic lenses or by a combination of the two.

In an embodiment of the present invention, the electro-active element with dynamic aperture is attached to an optical conform, optic or substrate that does not refract or diffract light for the purpose of correcting visual acuity errors of the eye, thereby providing focusing power. In it. In certain embodiments of the present invention, an electro-active element with dynamic aperture is attached to or recessed in an ophthalmic lens that corrects a refractive error in a user caused by natural anatomical conditions or by removal of cataracts or healthy lenses. do. The ophthalmic lens also corrects any or all of the usual and / or non-traditional errors of the user's eye. Dynamic aperture therefore becomes a component of the focusing lens. The electro-active lens also has the first electro-active element with dynamic aperture. The second electro-active element in optical communication with the first electro-active element or the first electro-active element is capable of correcting any or all of the typical and / or non-normal errors of the user's eye. The embodiment is a contact lens, corneal onlay, corneal inlay, IOO or IOL. This embodiment is used, for example, in optical communication with a focusing lens such as an IOL, lens, corneal inlay, corneal onlay, contact lens or spectacle lens. The focusing lens is either static (immutable of its optical power) or dynamic (modifiable of its optical power).

7A, 7B and 7C illustrate embodiments of the invention with dynamic aperture useful as corneal inlays, corneal onlays or contact lenses. The embodiments shown in FIGS. 7A, 7B and 7C are somewhat modified, for example, by adding stabilization haptics for use with the front or rear IOO or IOL of the present invention with dynamic aperture. The optic or lens 500 has one or more electro-active elements 510. The electro-active element 510 does not have or have a dynamic aperture similar to the electro-active element 200 or 400 or instead provide a variable optical power. The electro-active element is recessed or attached to the substrate 520. The substrate does not have optical power or has one or more optical powers. The substrate and / or electro-active element are capable of correcting at least some of any or all of the typical and / or non-traditional errors of the eye. The controller 530 is electrically connected to the electrode in the electro-active element by electrical connection 535. The electrode defines mainly transparent aperture 540 and mainly opaque ring 545. The term "mainly transparent" means at least about 50% optical transmission (preferably at least 70%) and does not necessarily mean 100% optical transmission. The term "mainly opaque" means about 50% or less optical transmission (preferably 35% or less) and does not necessarily mean 0% optical transmission.

The substrate has one or more openings 550 and / or pores 555 to allow nutrients and / or cell waste products to pass through the substrate and / or electro-active elements. Openings and / or pores are for example generated by a laser, machine generated or stamped. Openings and pores are generally located in non-electrical or non-essential areas of the present invention, such as in the central area where the electrode does not extend or apply power. These shapes are particularly important when lenses or optics of the present invention with dynamic aperture are used as corneal inlays or corneal onlays.

The controller receives at least some power from the power supply 560. The power supply is attached to and becomes a component of the substrate, but is not attached to the substrate. The power supply is a thin film rechargeable battery as manufactured by Excellatron. Thin film rechargeable batteries can be cycled in excess of 45,000 cycles. This provides a useful life of 20-25 years in the lens or optic of the present invention. In an embodiment of the invention two thin film rechargeable batteries are used and one on top and the other stacked. In this embodiment one of the batteries is used for 20 to 25 years and another battery is switched when the first battery is no longer operational. Another battery is also switched by a signal sent remotely to the controller. This extends the life of the optics or lens of the present invention to 40-50 years. Also the power supply is a capacitor. The power supply is remotely charged by way of example.

Photo-sensitive cells 565 and piezoelectric materials are also used to supplement or increase the power of the power supply. Photo-sensitive cells and / or piezoelectric materials also obviate the need for power supplies. Photo-sensitive cells are solar cells. The photo-sensitive cell is also a 1.5 μm photovoltaic cell. The photovoltaic cell is used outside the user's line of sight and is more preferably used and positioned around the edge of the pupil if it is partially enlarged by dark but not sufficiently enlarged. Thus, the lens or optic of the present invention is charged by using an eye safety laser capable of passing current to a 1.5 μm photovoltaic cell or photocells. The user places his or her chin and forehead in a device that provides the eye safety laser energy needed to energize a 1.5 μm photovoltaic cell or photocells. This is achieved during the day or at home if necessary. Appropriate energy may be provided through normally enlarged pupils or sufficiently non-mediated enlarged pupils caused by darkrooms or devices that block ambient visible light. In most but not all embodiments when using 1.5 μm photovoltaic or photovoltaic cells within the lens or optic of the present invention, the cell or batteries need to be bendable. When using non-flexible 1.5 μm photovoltaic cells a number of cells are used and placed in a pattern that allows the lens or optic of the invention to be superimposed or curled on or around the cell prior to insertion into the eye.

In an embodiment of the invention the photo-sensitive cell 565 is a solar cell. The solar cells are located in front of the iris portion of the user's eye (close to the cornea of the eye) and individually arranged. Thin electrical wiring operatively connects the solar cell to the controller of the optics or lens of the present invention. The electrical wiring passes through the pupil without contacting the iris and is operatively connected to the IOO or IOL of the present invention within the front or rear of the eye. The photovoltaic cell is large enough to provide enough power to avoid the need for an individual power supply. Thin electrical wiring has a form factor with moderate tension to keep the solar cell in place without conducting electricity. In certain embodiments of the invention one or more small holes are created in the iris by an ophthalmic laser such that a thin electrical interconnect connects the solar cell to the IOO or IOL housed within the electro-active element.

The lens or optic of the present invention includes a memory metal material 570 for restoring the proper shape, position and alignment of the device after it is superimposed and inserted into the eye. The memory metal attempts to "remember" its shape and restore its original geometry after it has been deformed (eg, while overlapping in preparation for insertion into the eye). The memory metal also functions as an antenna to inductively charge a lens or optic of the present invention or to receive a signal from a transmitter. The transmitter transmits a signal to the lens or optic of the present invention to change the diameter of the dynamic aperture or to change the optical power of the lens of the present invention.

The lens or optic of the present invention includes a sensor 580. The sensor is a distance meter for detecting a distance that the user wants to focus on. The sensor is a light-sensitive cell 565 for detecting ambient and / or projected light of a lens or optic of the present invention. The sensor includes, for example, one or more of the following devices: photo-detector, photocell or UV sensitive photocell, tilt switch, light sensor, manual distance-measuring device, time-of-flight measuring device, eye tracker, where the user looks Visible detectors to detect, accelerometers, proximity switches, physical switches, manual invalidation controls, capacitive switches that are switched when the user contacts the nose of a pair of glasses, pupil diameter detectors, biomagnetic control devices connected to eye muscles or nerves, and the like. The sensor also includes one or more microelectromechanical systems (MEMS) adapted to detect tilt of the user's head or encyclorotation of the user's eye.

The sensor is operatively connected to the controller. The sensor detects sensory information and transmits a signal to a controller that causes activation and / or deactivation of one or more dynamic components of the lens or optic of the present invention. If the lens or optic of the invention comprises an electro-active element with a dynamic aperture, the sensor detects the light intensity as an example and conveys this information to the controller. In one embodiment of the invention the sensor is a photo-detector and is located within the peripheral region of the lens of the invention and located behind the iris. This location is useful for monitoring the increase and / or decrease in the available light caused by the contraction and enlargement of the user's pupil. 19 shows that when the user's pupil is enlarged at night or in the dark, the sensor detects darkness and the controller allows the dynamic aperture to be enlarged or maintained. 18 shows that the user's pupils are contracted during the day or during light, the sensor senses light increase and the controller causes the dynamic aperture to contract. The dynamic aperture maintains contraction until it senses the absence of available light below a certain threshold or dark when the controller causes the dynamic aperture to be enlarged. It should be appreciated that the present invention contemplates placing the sensor within any area of the lens or optic of the present invention that operates in an optimal manner. In certain embodiments of the present invention, the controller has a delay feature that ensures that the light intensity change is not transient (i.e., persists more than the delay of the delay feature). Thus, if the user flashes his or her eye, the aperture size will not change because the delay of the delay circuit is longer than the time required to flash. The delay is longer than dir 0.0ch, preferably at least 1.0 second.

In another embodiment of the invention the sensor detects the focusing distance as an example. When the sensor detects that the user focuses within the near range, the controller causes the dynamic aperture to contract and produce an increased depth of field. If the sensor detects that the user is focusing beyond the near range, the controller causes the dynamic aperture to be enlarged. In an embodiment of the invention the sensor comprises two or more photo-detector arrays with focusing lenses located above each array. Each focusing lens has a suitable focal length for a particular distance from the user's eye. For example, three photo-detector arrays are used, the first with a focusing lens that focuses properly over a short distance, the second with a focusing lens with focusing properly over a medium distance, and a third Has a focusing lens that focuses properly over long distances. The sum of the difference algorithms is used to determine which array has the highest contrast ratio (and therefore provides the best focus). The array with the highest contrast ratio is used to measure the distance from the user to the object that the user is focusing on.

It should be appreciated that in certain embodiments of the lenses or optics of the present invention, the sensors and controllers are governed by manually operated remote switches. The remote switch transmits the signal by wireless communication, auditory communication, vibration communication or optical communication such as infrared. For example, if the sensor detects a dark room, such as a dimly lit restaurant, the controller enlarges its dynamic aperture, allowing more light to reach the retina. However, this affects the user's ability to perform near field tasks, such as reading menus. To increase the depth of field and increase the user's ability to read the menu, the user controls the dynamic aperture of the lens or optic of the present invention to shrink the aperture. 20 illustrates normal operation of an invalidated sensor and controller whose dynamic aperture contracts under dark lighting conditions even when the user's pupil is enlarged. When the near-field work is completed, the user remotely causes the sensors and controllers to automatically re-enlarge the aperture, allowing the user to see the best in a dim restaurant for non-near-range work. Upon activation, the remote switch signal is received by the lens or optic of the present invention, for example, via an antenna formed of memory metal material 570.

The substrate of the lens or optic of the invention is coated with a material that is biocompatible with the anatomical object of the eye. Biocompatible materials include, for example, polyvinylidene chloride or non-hydrogel microporous perfluoroethers. The substrate and various electronic components attached to or embedded in the substrate are optionally coated with a weld seal to prevent or retard leaching. Furthermore, the substrate is designed to encapsulate a variety of electronic components and embedded in the substrate.

In an embodiment of the invention the lens or optic of the invention is bendable, overlapping or rolled-up to be suitable during insertion through a small incision of about 1 mm to 3 mm. Syringe-like devices commonly used in the implantation of IOLs with pistons are used as insertion tools to allow the lenses or optics of the present invention to be superimposed or curled in a suitable position within the front or rear of the eye. 21 shows an overlapping optic or lens of the invention with one or more electro-active elements. It should also be noted that the contact lenses and focusing contact lenses of the present invention are flexible.

Embodiments of the invention with dynamic aperture will be fitted or implanted into a monocular (only one eye of the user) or binocular (both eyes of the user). Since the dynamic aperture can be programmed to expand to larger sizes in night or dim lighting conditions where the user's admiration diameter naturally expands, glare, halo, illusion and costly reduced light of the user's retina are greatly eliminated. The present invention thus enables a binocular approach as opposed to other conventional IOLs, corneal onlays, corneal inlays and contact lenses that do not have dynamic aperture, and thus can be used as a compromise for glare, halo, phantom, etc. Is suitable for near-field correction within the other eye. It should be appreciated that the optics or lenses of the present invention can also be implanted or fitted in a monocular manner if desired. Moreover, the optics or lenses of the present invention disclosed herein are implanted within or on the eye to better align the central axis of the dynamic aperture with respect to the user's gaze and then the center of the dynamic aperture remotely with respect to the center of the optic or lens. It can be designed and manufactured in a repositioned manner.

The optics or lenses of the present invention are healthy but presbyopia of the lens, underperforming or fully capable of single focus IOL, static multifocal IOL, dynamic focusing IOL (such as electro-active focusing IOL), or lack of dynamic aperture. A perspective IOL, eyeballs with trauma, rupture, halo, or iris that does not contract or enlarge properly, pigmented deficiency irises such as irises of certain whiteness, sufficient performance or poor performance multifocal or without dynamic aperture Single vision contact lens, sufficient performance or performance without dynamic aperture multifocal or single vision corneal inlay or corneal onlay, sufficient performance or performance without dynamic aperture multifocal or single vision eyeglass lenses or poor performance refractive surgery It is used for optical communication with the eye.

A "sufficient performance" lens can properly focus light onto the retina. A "degraded" lens is unable to properly focus light onto the retina. In most cases the optics or lenses of the present invention will improve the quality of vision upon recognition by the user when used in optical communication in combination with the various examples provided in the preceding paragraph. When used with a lens of sufficient performance, the dynamic aperture increases the depth of field and serves to suppress or eliminate some or most of the high-order aberrations of the user's eye.

Lenses or optics of the present invention that receive the electro-active elements disclosed herein may be composed of ophthalmic materials known in the art and used in IOL, contact lenses or corneal inlays. The material may be flexible or non-flexible. In one embodiment of the invention (not shown), the IOO of the invention comprises two about 100 μm layer polysulfone materials, liquid crystal materials (treated with dichroic dyes), optical polarizing layers, power supplies, controllers, sensors with suitable electrodes. And other necessary electronic components. Each 100 μm layer is used to form a flexible sheath that sandwiches and receives electronic components and electro-active materials. The total thickness of the operating optics is about 500 μm or less. The outer diameter of this particular embodiment is about 9.0 mm (does not include any haptics). The IOO of the present invention can be superimposed and inserted into the eye through a small surgical incision up to about 2 mm. In certain embodiments of the invention, the thin layer memory metal is used as part of the IOO of the present invention to assist its proper shape and position when it is inserted into the front or back of the eye and then unfolds the IOO.

In some embodiments of the present invention, the tint or filter is incorporated within the lens or optic of the present invention to filter high energy blue light and / or ultraviolet light. Filters or hue are also used to increase the contrast sensitivity when perceived by the user.

The diameter of the IOO or IOL is between about 5 mm and about 10 mm, depending on the intended application of the lens or optic of the invention (not including haptics). Other sizes are also possible.

When used as a corneal inlay, the diameter of the optics or lenses of the present invention with dynamic aperture should be smaller than the diameter of the cornea. When used as a contact lens, the optics or lenses of the present invention may have a diameter between about 5 mm and about 14 mm. In some embodiments of the invention the outer surface of the substrate is bent to substantially match the curvature of the cornea (when used within the corneal inlay) or the ocular surface (when used within the contact lens). In other embodiments the outer surface of the substrate is planar.

8 illustrates an IOO located in front of the eye and in optical communication with a healthy presbyopia lens in accordance with an embodiment of the invention. 9 illustrates an IOO in optical communication with an IOL located in front of the eye and correcting only far vision in accordance with embodiments of the present invention. The embodiment shown in FIG. 10 is useful for providing increased depth of field for providing near and / or medium distance correction. FIG. 11 illustrates an IOO in optical communication with an IOL located in front of the eye that corrects distant and near vision in accordance with embodiments of the present invention. The embodiment shown in FIG. 11 is useful for providing increased depth of field for providing medium distance correction. 12 illustrates an IOO positioned behind the eye and in optical communication with the IOL in accordance with an embodiment of the present invention. FIG. 13 shows an IOL with dynamic aperture in the IOL portion closest to the eye pupil in accordance with an embodiment of the present invention. 14 illustrates an IOL having a dynamic aperture in the central portion of the IOL in accordance with an embodiment of the present invention. 15 illustrates an IOL with dynamic aperture in the IOL portion closest to the ocular retina in accordance with an embodiment of the present invention. 16 illustrates a corneal inlay with dynamic aperture in optical communication with a healthy presbyopia lens in accordance with an embodiment of the present invention. 17 illustrates a corneal inlay with dynamic aperture in optical communication with an IOL in accordance with an embodiment of the present invention. It should be noted that it is not possible to represent all possible embodiments, combinations and arrangements of the invention. For example, contact lenses and corneal inlay embodiments with dynamic apertures are not shown. However, these embodiments will be apparent to those skilled in the art.

The IOO or IOL of the present invention can be surgically inserted during the initial surgical procedure of inserting a conventional IOL without dynamic aperture. In addition, the IOO or IOL of the present invention is surgically inserted several hours, days, weeks, months or years after the initial IOL surgery.

Successful operation of the lens or optic of the present invention is dependent primarily on obtaining the maximum permissible transmission through the transparent aperture and the minimum acceptable transmission through the mainly opaque ring region. The experiment was performed with a neutral density (ND) optical filter with an ND value between 0 and 1.0 where holes with a diameter of 1.5 mm were formed in the filter to create apertures. In some embodiments a second filter was placed above the aperture to simulate penetration through the aperture. Neutral density is the light transmission dimension based on the logarithmic calculator and is related to transmission (T) through the following correlation:

T = 10 ^-ND Equation 1

In the experiment, the filter was kept very close to the front of the eye of a non-calibrated + 2.50D presbyopia patient. A presbyopia patient viewed from close range aimed at about 13 inches from the patient's eye through the aperture. It has been found that this aperture acts to increase depth of field by providing excellent vision and contrast, not only in certain conditions.

In general, good results were obtained when the ND value of the mainly transparent aperture was less than about 0.1 (T of about 80% or more) and the difference in ND values between the mainly transparent aperture and the mainly opaque rings was greater than about 0.3. In a preferred embodiment of the present invention the ND value for the mostly transparent aperture is about 0.04 or less (T 90% or more) and the ND of the mainly opaque ring is about 1.0 or more (T 10% or less). Increasing the difference in ND values between mainly transparent apertures and mainly opaque rings can compensate for high ND values mainly in transparent apertures, which will cause undesirable decreases in overall light transmission to the retina.

Claims (49)

In an ophthalmic device comprising an electro-active element comprising a mainly opaque ring with a predominantly transparent dynamic aperture with a changeable diameter and an increased depth of field, the ophthalmic device can at least partially correct the refractive error of the user's eye. Ophthalmic devices characterized by optical communication with intraocular lenses, corneal inlays, corneal onlays, contact lenses or spectacle lenses with optical power to provide The method of claim 1 wherein the electro-active element is First description; A plurality of electrodes arranged on the surface of the first substrate; A second substrate having a surface facing the surface of the first substrate; A single electrode arranged on the surface of the second substrate; Further comprising an electro-active material arranged between the facing surfaces of the first and second substrates, The plurality of electrodes provide the dynamic aperture and the ring The ophthalmic device according to claim 1, wherein the diameter of the dynamic aperture is changeable to a sufficiently enlarged size or a sufficiently contracted size. 4. The ophthalmic device according to claim 3, wherein the diameter of the dynamic aperture is changeable to one or more sizes between the sufficiently enlarged size and the sufficiently shrunk size. 3. The ophthalmic device of claim 2 wherein said diameter of said dynamic aperture is changeable by application of voltage to said plurality of electrodes. The ophthalmic device of claim 2, wherein the electro-active material comprises a double-stable liquid crystal. The ophthalmic device of claim 2, further comprising a controller operatively connected to the plurality of electrodes. 8. The ophthalmic device of claim 7, further comprising a sensor operatively connected to the controller. 8. An ophthalmic device as recited in claim 7, wherein said controller is operatively connected to a power supply. 10. The ophthalmic device of claim 9, wherein the power supply is one or more thin film rechargeable batteries. 11. An ophthalmic device according to claim 10, wherein a second of the thin film rechargeable battery is used when the first of the thin film rechargeable battery is first used and the first of the thin film rechargeable battery is no longer feasible. 9. The ophthalmic device of claim 8, wherein said controller is operatively connected to a photo-sensitive cell. The ophthalmic device according to claim 1, wherein the diameter of the dynamic aperture can be changed remotely. The ophthalmic device according to claim 1, wherein the center of the dynamic aperture can be remotely repositioned. 3. The ophthalmology of claim 2, further comprising a first polarizer arranged on the first substrate and a second polarizer arranged on the second substrate, wherein the first and second polarizers are cross polarizers. Device The ophthalmic device of claim 15 wherein the central region of the polarizer is removed. The ophthalmic device according to claim 2, wherein the electro-active material is treated with a dichroic dye. The ophthalmic device of claim 2, wherein the plurality of electrodes is pixelated. The ophthalmic device of claim 1, wherein said primarily transparent aperture has a neutral density of about 0.1 or less. The ophthalmic device of claim 1, wherein the mainly opaque ring has a neutral density of about 0.3 or greater. The ophthalmic device of claim 1 wherein the ophthalmic device is flexible and surgically implantable within the user's eye. In an ophthalmic device comprising an electro-active element comprising a mainly transparent dynamic aperture with a changeable diameter and a mainly opaque ring to provide an increased depth of field, the electro-active element is at least a partial correction of the refractive error of the user's eye. Ophthalmic device characterized in that it is a component of one of the intraocular lens, corneal inlay, corneal onlay or contact lens with optical power to provide The method of claim 22, wherein the electro-active element is First description; A plurality of electrodes arranged on the surface of the first substrate; A second substrate having a surface facing the surface of the first substrate; A single electrode arranged on the surface of the second substrate; Further comprising an electro-active material arranged between the facing surfaces of the first and second substrates, The plurality of electrodes provide the dynamic aperture and the ring 23. The ophthalmic device of claim 22, wherein the diameter of the dynamic aperture is changeable to a sufficiently enlarged or sufficiently retracted size. 25. The ophthalmic device of claim 24, wherein the diameter of the dynamic aperture is changeable to one or more sizes between the sufficiently enlarged size and the sufficiently shrunk size. 24. The ophthalmic device of claim 23, wherein said diameter of said dynamic aperture is changeable by application of voltage to said plurality of electrodes. The ophthalmic device of claim 23, wherein the electro-active material comprises a double-stable liquid crystal. 24. The ophthalmic device of claim 23, further comprising a controller operatively connected to the plurality of electrodes. 29. The ophthalmic device of claim 28, further comprising a sensor operatively connected to the controller. 29. The ophthalmic device of claim 28, wherein said controller is operatively connected to a power supply. 31. The ophthalmic device of claim 30, wherein said power supply is one or more thin film rechargeable batteries. 32. The ophthalmic device of claim 31 wherein a second of the thin film rechargeable battery is used when the first of the thin film rechargeable battery is used for the first time and the first of the thin film rechargeable battery is no longer feasible. 30. The ophthalmic device of claim 29, wherein said controller is operatively connected to a photo-sensitive cell. 23. The ophthalmic device of claim 22, wherein the diameter of the dynamic aperture can be changed remotely. 23. The ophthalmic device of claim 22, wherein the center of the dynamic aperture can be repositioned remotely. 24. The ophthalmology of claim 23, further comprising a first polarizer arranged on said first substrate and a second polarizer arranged on said second substrate, wherein said first and said second polarizers are cross polarizers. Device 37. The ophthalmic device of claim 36, wherein the central region of the polarizer is removed. 24. The ophthalmic device of claim 23, wherein the electro-active material is treated with a dichroic dye. The ophthalmic device of claim 23, wherein the plurality of electrodes is pixelated. 23. The ophthalmic device of claim 22, wherein said primarily transparent aperture has a neutral density of about 0.1 or less. 23. The ophthalmic device of claim 22, wherein said predominantly opaque ring has a neutral density of at least about 0.3. 23. The ophthalmic device of claim 22, wherein the ophthalmic device is flexible and surgically implantable into the user's eye. A first electro-active element with optical power to provide at least partial correction of refractive error of the user's eye; And A second electro-active element having substantially no optical power, including a predominantly transparent dynamic aperture with a changeable diameter and a predominantly opaque ring to provide increased depth of field, An ophthalmic device characterized in that said first and second electro-active elements are in optical communication with one another. An ophthalmic eye, characterized in that it comprises a predominantly transparent dynamic aperture with a changeable diameter and an electro-active element comprising mainly opaque rings to provide increased depth of field, the center of the dynamic aperture being repositioned with respect to the user's gaze. Device In an ophthalmic device comprising an electro-active element comprising a mainly opaque ring with a predominantly transparent dynamic aperture with a changeable diameter and an increased depth of field, the ophthalmic device provides at least partial correction of the refractive error of the user's eye. Ophthalmic device in optical communication with a lens having an optical power to provide said increased depth of field and said lens primarily providing a continuous range of cognitive focus. 2. An ophthalmic device according to claim 1, wherein said increased depth of field primarily provides a continuous range of cognitive focus. 23. The ophthalmic device of claim 22, wherein said increased depth of field primarily provides a continuous range of cognitive focus. 44. The ophthalmic device of claim 43, wherein said increased depth of field primarily provides a continuous range of cognitive focus. 45. The ophthalmic device of claim 44, wherein said increased depth of field primarily provides a continuous range of cognitive focus.