Contact lens position and rotation control using eyelid margin pressure.

Abstract

An exemplary ophthalmic lens is described herein. The optic includes an anterior surface and a posterior surface opposite the anterior surface. The optic also includes a recess provided on the anterior surface of the optic and configured to engage a wearer's upper eyelid.

Description

[Technical Field]

[0001] The present invention relates to stabilization zones for ophthalmic devices requiring rotational stability, such as wearable lenses including toric contact lenses, and more particularly to contact lenses incorporating one or more concave stabilization zones having various inclined surfaces, which require positional and / or rotational stability. [Background technology]

[0002] Myopia or nearsightedness is a visual impairment or refractive error of the eye in which light rays from an image converge to a single point before reaching the retina. Myopia generally results from an eyeball or globe being too long, or from a corneal curvature that is too steep. Myopia can be corrected using spherical lenses with a negative power. Hyperopia or farsightedness is a visual impairment or refractive error of the eye in which light rays from an image converge to a single point after reaching the retina or behind the retina. Hyperopia generally results from an eyeball or globe being too short, or from a corneal curvature that is too flat. Hyperopia can be corrected using spherical lenses with a positive power. Furthermore, the terms myopia and hyperopia refer to refractive errors that are rotationally symmetric and therefore can be corrected with spherical lenses that have the same power in all directions. Astigmatism is a visual impairment or refractive error of the eye, where the refractive error is not rotationally symmetrical, resulting in blurred vision. Astigmatism can be corrected by incorporating cylindrical lenses. People with simple myopia or hyperopia usually only require spherical power prescriptions, while people with astigmatism usually require a combination of spherical and cylindrical prescriptions.

[0003] A toric lens is an optical element having two different powers in two mutually perpendicular orientations. Essentially, a toric lens has, within a single lens, one spherical power for correcting nearsightedness or farsightedness and one cylindrical power for correcting astigmatism. These powers are given by different angles of curvature that are preferably maintained relative to the eye. Toric lenses can be used in eyeglasses, intraocular lenses, and contact lenses. Toric lenses used in eyeglasses and intraocular lenses provide consistent vision correction at all times by being held in a fixed position relative to the eye. However, toric contact lenses tend to rotate on the eye, and may temporarily provide suboptimal vision correction. Therefore, toric contact lenses also include mechanisms to keep the contact lens relatively stable on the eye when the wearer blinks or looks around.

[0004] Additionally, it is known that correction of certain visual defects can be achieved by imparting non-rotationally symmetrical corrective properties, wavefront corrective properties, or dispersion of the visual zone to one or more surfaces of a contact lens, such as a cylindrical lens, bifocal lens, or multifocal lens. It is also known that certain cosmetic features, such as printed patterns or markings, are required to be positioned in a specific orientation relative to the wearer's eye. The use of such contact lenses presents problems when each of a pair of contact lenses must be maintained in a specific orientation so that it is effective while on the eye. When a contact lens is first placed on the eye, it may be positioned in the required orientation, or it may automatically position itself, or it may automatically position itself and then maintain that position over time. However, once a contact lens is positioned, it may rotate on the eye due to forces exerted on it during blinking by the movement of the eyelid and the eyelid and tear film.

[0005] Maintaining the orientation of a contact lens on the eye is typically achieved by altering the mechanical properties of the contact lens. Prism stabilization, including, for example, eccentricating the front surface of the contact lens relative to the rear surface, thickening the lower peripheral portion of the contact lens, forming ridges on the surface of the contact lens, and trimming the contact lens edge, are all methods that are used.

[0006] Furthermore, static stabilization has been used to stabilize contact lenses by utilizing thicker and thinner zones, or in some cases, areas where the thickness of the contact lens increases or decreases around its periphery. Typically, the thicker and thinner zones are located around the periphery of the contact lens, symmetrically with respect to the vertical and / or horizontal axes. For example, each of the two thicker zones may be positioned on either side of the visual zone, or they may be centered along the 0-180 degree axis of the contact lens. In another example, a single thicker zone may be designed located at the bottom of the contact lens, incorporating an area where the thickness increases from top to bottom to provide a weighting effect similar to that of prism stabilization and to utilize the force of the upper eyelid to stabilize the contact lens.

[0007] Currently, the challenges of static stabilization zones are the trade-off between contact lens stability and comfort, and the physical constraints associated with increased thickness. Static stabilization zones fix the inclination of the stabilization zone within the contact lens. Modifying the design to improve rotational speed, such as increasing the surface inclination of the stabilization zone, can increase the thickness of the contact lens, negatively impacting comfort. Additionally, contact lens design must achieve two things: rotation to the correct orientation upon insertion and maintenance of that orientation throughout the wearing period. Raised stabilization zone designs require a trade-off in performance between these two modes.

[0008] Certain translational multifocal lens designs incorporate both a lower eyelid contact surface and a sub-eyelid support structure in the lower eyelid, recognizing that interaction with the lower eyelid margin affects the lens's translational capability. Translational multifocal designs generally have little concern for rotational stability. However, the use of both a lower eyelid contact surface and a sub-eyelid support structure may not provide the desired level of rotational stability for toric lenses, electroactive lenses with sensor positioning requirements, or other contact lens applications where rotational stability is critical. [Overview of the Initiative] [Problems that the invention aims to solve]

[0009] Therefore, contact lenses with improved position and rotation control are still needed. [Means for solving the problem]

[0010] The ophthalmic lens of the present invention easily overcomes the drawbacks associated with the prior art described above.

[0011] In one implementation, the ophthalmic lens includes a front surface and a rear surface opposite to the front surface. The lens includes a recess provided on the front surface of the optical portion. The recess is displaced radially from the center point of the lens.

[0012] Alternatively or additionally, in some implementations, the recess is configured to provide rotational stability and / or positional control of the lens.

[0013] Alternatively or additionally, in some implementations, the recess is configured to interact with the subject's eyelid wiper.

[0014] Alternatively or additionally, in some implementations, the recess is configured to interact with the subject's upper eyelid wiper.

[0015] Alternatively or additionally, in some implementations, the recess is configured to interact with the subject's lower eyelid wiper.

[0016] Alternatively or additionally, in some implementations, the radial distance between the center point of the lens and the recess is from about 4 millimeters (mm) to about 4.5 mm.

[0017] Alternatively or additionally, in some implementations, the recess forms a thinning zone on the anterior surface of the lens.

[0018] Alternatively or additionally, in some implementations, the recess defines a first inclined surface that is farther from the center point of the lens than a second inclined surface that is closer to the center point of the lens.

[0019] Alternatively or additionally, in some implementations, the first inclined surface has a steeper slope than the second inclined surface.

[0020] Alternatively or additionally, in some implementations, the second inclined surface has a steeper slope than the first inclined surface.

[0021] Alternatively or additionally, in some implementations, the length of the first inclined surface is longer than the length of the second inclined surface.

[0022] Alternatively or additionally, in some implementations, the length of the second inclined surface is longer than the length of the first inclined surface.

[0023] Alternatively or additionally, in some implementations, the ophthalmic lens further comprises a plurality of recesses provided on the anterior surface of the lens. Each of the recesses is radially displaced from the center point of the lens. For example, the first recess is optionally configured to interact with the subject's upper eyelid wiper, and the second recess is optionally configured to interact with the subject's lower eyelid wiper.

[0024] Alternatively or additionally, in some implementations, the recess has a width of from about 0.8 millimeters (mm) to about 1.2 mm.

[0025] Alternatively or additionally, in some implementations, the recess has a length of from about 5 millimeters (mm) to about 6 mm.

[0026] Alternatively or additionally, in some implementations, the ophthalmic lens further comprises a ridge provided on the anterior surface of the lens, the ridge being disposed proximate to the recess.

[0027] Alternatively or additionally, in some implementations, the ridge is disposed radially outward relative to the recess. In some implementations, the ridge is disposed radially inward relative to the recess.

[0028] Alternatively or additionally, in some implementations, the radial distance between the center point of the lens and the ridge is from about 4.5 millimeters (mm) to about 5 mm.

[0029] Alternatively or additionally, in some implementations, the ophthalmic lens is an electroactive or "smart" lens.

[0030] Alternatively or additionally, in some implementations, the ophthalmic lens is a toric lens.

[0031] Alternatively or additionally, in some implementations, the ophthalmic lens is a spherical lens.

[0032] Alternatively or additionally, in some implementations, the ophthalmic lens is a multifocal lens.

[0033] Alternatively or additionally, in some implementations, the ophthalmic lens is an aspheric lens.

[0034] Alternatively or additionally, in some implementations, the ophthalmic lens is a cosmetically tinted lens. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] The aforementioned and other features and advantages of the present invention will become apparent from the following more specific description of preferred implementations of the invention, as shown in the accompanying drawings. [Figure 1] This shows a side view of the mounting configuration of an ophthalmic lens with a recess. [Figure 2A] Figure 2A shows a side view of an ophthalmic lens interacting with an eyelid wiper, according to the implementation described herein. Figure 2A shows an ophthalmic lens in which the upper eyelid wiper interacts with a recess. Figure 2B shows an ophthalmic lens in which the upper eyelid wiper interacts with both a recess and a protrusion. [Figure 2B] Figure 2A shows a side view of an ophthalmic lens interacting with an eyelid wiper, according to the implementation described herein. Figure 2A shows an ophthalmic lens in which the upper eyelid wiper interacts with a recess. Figure 2B shows an ophthalmic lens in which the upper eyelid wiper interacts with both a recess and a protrusion. [Figure 3] This specification shows a graph of sag (mm) versus distance from the center point (mm) for ophthalmic lenses having symmetrical recesses in the mounting configuration described herein. [Figure 4] This specification shows a graph of sag (mm) versus distance from the center point (mm) for ophthalmic lenses having asymmetrical recesses in the mounting configuration described herein. [Figure 5] This specification shows oblique views of ophthalmic lenses in various implementation configurations. [Figure 6A] Figure 6A shows the eyelid wiper interacting with the contact lens. Figure 6B shows the position of the contact lens relative to the pupil during downward gaze. [Figure 6B] Figure 6A shows the eyelid wiper interacting with the contact lens. Figure 6B shows the position of the contact lens relative to the pupil during downward gaze. [Figure 7] This shows the movement of the upper and lower eyelid wipers relative to the pupil for different amounts of downward gaze. [Figure 8]This shows a side view of an ophthalmic lens mounting configuration with multiple recesses. [Figure 9] This is a diagram illustrating an exemplary prescription contact lens in the implementation configuration described herein. [Figure 10] This is an exemplary computing device. [Modes for carrying out the invention]

[0036] It would be advantageous to design a contact lens having at least one recess on the contact lens surface configured to hold and / or maintain a desired position for optimal visual acuity, regardless of eye movement and blinking.

[0037] Minimizing rotation relative to the wearer's eye is beneficial for contact lens performance. For example, in toric lenses, if the lens is designed to treat astigmatism, minimizing rotation can significantly improve lens function. Rotation is typically minimized through the use of a thickened or raised stabilization zone. Toric contact lenses with a thickened stabilization zone are typically less comfortable than unstabilized (spherical) contact lenses because the eyelid interacts with the thickened zone during each blink. In some implementations of ophthalmic lenses, the orientation of the toric contact lens is maintained instead by the interaction of at least the upper eyelid with a recess on the front of the lens.

[0038] Some contact lenses with complex optical designs (multifocal or aspherical) are sensitive to eccentricity, and therefore these types of contact lenses can benefit from including a relatively thin area within the recess. The upper eyelid, by interacting with the recess, helps the lens maintain a consistent position relative to the pupil. As shown in Figures 6A, 6B, and 7, the position of the upper eyelid margin relative to the pupil remains relatively consistent from primary gaze to downward gaze. Some other contact lens types (such as parallel bifocal lenses) may also benefit from this inclusion of the recess. In some embodiments, since the lower eyelid is closer to the pupil during downward gaze, lower eyelid pressure can be used to help the lens achieve greater movement relative to the pupil during fluctuations in vertical gaze (shown in Figures 6A, 6B, and 7). Thus, if the recess and / or ridge on the contact lens surface is held by the lower eyelid, the lens moves upward relative to the pupil. The lower eyelid can act as a support to maintain the vertical position of the contact lens, providing support during downward gaze while preventing it from slipping down during straight gaze.

[0039] Glossary The following definitions are provided for terms used in this disclosure. The definition of polymer is consistent with the definition disclosed in the Compendium of Polymer Terminology and Nomenclature, IUPAC Recommendations 2008, edited by Richard G. Jones, Jaroslav Kahovec, Robert Stepto, Edward S. Wilks, Michael Hess, Tatsuki Kitayama, and W. Val Metanomski.

[0040] As used herein, the term “about” refers to a range of + / - 5% of the number being modified. For example, the phrase “about 10” would include both 9.5 and 10.5.

[0041] Unless otherwise specified, a number range, such as "2-10 (from 2 to 10)" or "2-10 (between 2 and 10)," includes the numbers that define the range (e.g., 2 and 10).

[0042] The term "(meth)" refers to optional methyl substitution. Therefore, terms such as "(meth)acrylate" refer to both methacrylate and acrylic groups. It should be understood that, wherever a chemical structure is given, any combination of the disclosed options for substituents in the structure is permitted. Therefore, if a structure has substituent R * and R ** If it contains and each of these contains a list of three possible groups, then nine combinations are disclosed. The same applies to combinations of properties. General formula [ *** ] n When a subscript such as "n" is used to indicate the number of repeating units in the chemical formula of a polymer, the formula should be interpreted as representing the number-average molecular weight of the polymer.

[0043] A "polymer" is an organic compound having a molecular weight greater than 1500, and may be reactive or nonreactive.

[0044] A "polymer" is a polymer of repeating chemical units linked together in a chain-like or network-like manner, consisting of repeating units derived from monomers and macromers contained in a reactive mixture.

[0045] A "homopolymer" is a polymer made from one monomer or macromer, while a "copolymer" is a polymer made from two or more monomers, macromers, or combinations thereof. A "terpolymer" is a polymer made from three monomers, macromers, or combinations thereof. A "block copolymer" consists of compositionally different blocks or segments. A diblock copolymer has two blocks. A triblock copolymer has three blocks. A "comb-shaped or graft copolymer" is made from at least one macromer.

[0046] A "repeating unit" or "repeating chemical unit" is the smallest repeating group of atoms in a polymer resulting from the polymerization of monomers and macromers.

[0047] The term “biomedical device” refers to any article designed for use in or on the tissues or fluids of a mammal, preferably in or on the tissues or fluids of a human. Examples of these devices include, but are not limited to, wound dressings, sealants, tissue grafts, drug delivery systems, coatings, adhesion barriers, catheters, implants, stents, sutures, and ophthalmic devices such as intraocular lenses and contact lenses. Biomedical devices may also include ophthalmic devices such as contact lenses, including contact lenses made from silicone hydrogels or conventional hydrogels.

[0048] The term "individual" includes humans and vertebrates.

[0049] The term “surface of the eye” includes the surface and glandular epithelium of the cornea, conjunctiva, lacrimal glands, accessory lacrimal glands, nasolacrimal ducts, and meibomian glands, as well as adjacent or related structures including their apical and basal matrices, puncta, and eyelids, which are connected as a functional system by epithelial continuity by innervation and by both the endocrine and immune systems.

[0050] The term “ophthalmic device” refers to any device located in or on the eye or any part of the eye, including the surface of the eye. These devices may provide optical correction, cosmetic enhancement, vision enhancement, therapeutic effects (e.g., as a bandage), or delivery of active ingredients such as pharmaceutical and nutritional supplements, or any combination thereof. Examples of ophthalmic devices include, but are not limited to, lenses, optical implants, and intraocular implants, including, but not limited to, punctal plugs. “Lenses” include soft contact lenses, hard contact lenses, hybrid contact lenses, intraocular lenses, and overlay lenses. Ophthalmic devices may include contact lenses.

[0051] The term "contact lens" refers to a structure or ophthalmic device that can be placed on the cornea of ​​a person's eye. Contact lenses may provide corrective, cosmetic, or therapeutic benefits, including wound healing, delivery of drugs or nutritional supplements, diagnostic evaluation or monitoring, or blocking ultraviolet light and reducing visible light or glare, or a combination thereof. Contact lenses may consist of any suitable material known in the art and may be soft lenses, hard lenses, or hybrid lenses having at least two different properties, such as modulus of elasticity, water content, light absorption properties, or a combination thereof.

[0052] The biomedical devices, ophthalmic devices, and lenses of the present invention may be composed of a silicone hydrogel or a conventional hydrogel. The silicone hydrogel typically contains silicone components and / or hydrophobic and hydrophilic monomers covalently bonded to each other in the cured device.

[0053] "Silicone hydrogel contact lenses" refer to contact lenses containing at least one silicone hydrogel material. Silicone hydrogel contact lenses generally have increased oxygen permeability compared to conventional hydrogels. Silicone hydrogel contact lenses utilize both their water content and polymer content to deliver oxygen to the eye.

[0054] A "polymer network" is a cross-linked polymer that can swell but is insoluble in solvents because a polymer network is essentially a single macromolecule. A "hydrogel" or "hydrogel material" refers to a polymer network that contains water in equilibrium. Hydrogels generally contain at least about 10% by weight of water.

[0055] "Conventional hydrogels" refer to polymer networks composed of monomers that do not contain any siloxy, siloxane, or carbosiloxane groups. Conventional hydrogels are prepared from monomer mixtures mainly containing hydrophilic monomers such as 2-hydroxyethyl methacrylate ("HEMA"), N-vinylpyrrolidone ("NVP"), N,N-dimethylacrylamide ("DMA"), or vinyl acetate. U.S. Patents No. 4,436,887, No. 4,495,313, No. 4,889,664, No. 5,006,622, No. 5,039,459, No. 5,236,969, No. 5,270,418, No. 5,298,533, No. 5,824,719, No. 6,420,453, No. 6,423,761, No. 6,767,979, No. 7,934,830, No. 8,138,290, and No. 8,389,597 disclose conventional hydrogel formation. Commercially available hydrogel formulations include, but are not limited to, etafilcon, polymacon, vifilcon, genfilcon, lenefilcon, hilafilcon, nesofilcon, and omafilcon, including all their variations.

[0056] "Silicone hydrogel" refers to a hydrogel obtained by copolymerizing at least one silicone-containing component with at least one hydrophilic component. The hydrophilic component may also include a non-reactive polymer. Each of the silicone-containing component and the hydrophilic component may be a monomer, macromer, or a combination thereof. The silicone-containing component contains at least one siloxane group or carbosiloxane group. Examples of commercially available silicone hydrogels include balafilcon, acquafilcon, lotrafilcon, comfilcon, delefilcon, enfilcon, fanfilcon, formofilcon, galyfilcon, senofilcon, narafilcon, falcon II, and asmofilcon A. A) Samfilcon, Riofilcon, Stenficlon, Somofilcon, and U.S. Patents No. 4,659,782, No. 4,659,783, No. 5,244,981, No. 5,314,960, No. 5,331,067, No. 5,371,147, No. 5,998,498, No. 6,087,415, No. 5,760,100, No. 5,776,999, No. 5,789,461, No. 5,849,811, No. 5,965,631, No. 6,3 No. 67,929, No. 6,822,016, No. 6,867,245, No. 6,943,203, No. 7,247,692, No. 7,2 No. 49,848, No. 7,553,880, No. 7,666,921, No. 7,786,185, No. 7,956,131, No. 8,02 No. 2,158, No. 8,273,802, No. 8,399,538, No. 8,470,906, No. 8,450,387, No. 8,487 ,058, 8,507,577, 8,637,621, 8,703,891, 8,937,110, 8,937,Examples include silicone hydrogels prepared in Patent Nos. 111, 8,940,812, 9,056,878, 9,057,821, 9,125,808, 9,140,825, 9,156,934, 9,170,349, 9,244,196, 9,244,197, 9,260,544, 9,297,928, 9,297,929, and International Publication Nos. 03 / 22321, 2008 / 061992, and U.S. Patent Application Publication No. 2010 / 048847. As with the other patents described in this paragraph, these patents are incorporated herein by reference in their entirety.

[0057] "Silicone-containing components" refer to monomers, macromers, prepolymers, crosslinking agents, initiators, additives, or polymers that contain at least one silicone-oxygen bond in the form of a siloxane [-Si-O-Si] group or a carbosiloxane group. Examples of silicone-containing components include, but are not limited to, silicone macromers, prepolymers, and monomers. Examples of silicone macromers include, but are not limited to, polydimethylsiloxane methacrylate having a pendant hydrophilic group. Examples of silicone-containing components useful in the present invention include U.S. Patent Nos. 3,808,178, 4,120,570, 4,136,250, 4,153,641, 4,740,533, 5,034,461, 5,962,548, 5,244,981, 5,314,960, 5,331,067, 5,371,147, and 5,760,100. These can be found in Patent Nos. 5,849,811, 5,962,548, 5,965,631, 5,998,498, 6,367,929, 6,822,016, 5,070,215, 8662,663, 7,994,356, 8,772,422, 8,772,367, European Patent No. 080539 and International Publication No. 2014 / 123959.

[0058] "Reactive mixture" and "reactive monomer mixture" refer to a mixture of components (both reactive and nonreactive) that, when exposed to polymerization conditions, form the silicone hydrogel of the present invention. The reactive mixture includes reactive components such as monomers, macromers, prepolymers, crosslinking agents, initiators, and diluents, and active components such as pharmaceutical compounds and nutritional supplements, any of which may be reactive or nonreactive, as well as any diluent, which can be retained within the resulting biomedical device. It will be understood that a variety of additives may be added depending on the biomedical device to be manufactured and how it is used. The concentration of components in the reactive mixture is expressed as a weight % of the total components in the reaction mixture, excluding the diluent. When a diluent is used, the concentration of components is expressed as a weight % based on the total amount of components in the reaction mixture and the diluent.

[0059] A "monomer" is a molecule having non-repeating functional groups that can undergo chain growth polymerization, particularly free radical polymerization. Some monomers have difunctional impurities that can act as crosslinking agents. A "macromer" is a linear or branched polymer having a repeating structure and at least one reactive group that can undergo chain growth polymerization. Monomethacrylateoxypropyl-terminated mono-n-butyl-terminated polydimethylsiloxane (molecular weight = 500-1500 g / mol) (mPDMS) and mono-(2-hydroxy-3-methacrylateoxypropyl)-propyl ether-terminated mono-n-butyl-terminated polydimethylsiloxane (molecular weight = 500-1500 g / mol) (OH-mPDMS) are referred to as macromers.

[0060] A "reactive component" is a component in a reactive mixture that becomes part of the structure of the polymer network of the resulting silicone hydrogel through the formation of covalent bonds, hydrogen bonds, or an interpenetrating network. Diluents and processing aids that do not become part of the polymer structure are not reactive components. In general, the chemical structure of a macromer differs from that of a target polymer, that is, the repeating unit of the pendant groups of the macromer is different from the repeating unit of the target polymer or its main chain.

[0061] "Polymerizable" means that the compound contains at least one reactive group capable of undergoing chain-growth polymerization, such as free radical polymerization. Examples of reactive groups include the monovalent reactive groups listed below. "Non-polymerizable" means that the compound does not contain such polymerizable functional groups.

[0062] A "monovalent reactive group" is a group capable of undergoing chain-growth polymerization such as free radical polymerization and / or cationic polymerization. Non-limiting examples of free radical reactive groups include (meth)acrylate, styrene, vinyl ether, (meth)acrylamide, N-vinyl lactam, N-vinyl amide, O-vinyl carbamate, O-vinyl carbonate, and other vinyl groups. In one embodiment, the free radical reactive groups comprise (meth)acrylate, (meth)acrylamide, N-vinyl lactam, N-vinyl amide and styryl functional groups, or (meth)acrylates, (meth)acrylamides and any mixtures of the foregoing. Examples of the foregoing include substituted or unsubstituted C 1~6 alkyl (meth)acrylates, C 1~6 alkyl (meth)acrylamides, C 2~12 alkenyl, C 2~12 alkenylphenyl, C 2~12 alkenylnaphthyl, C 2~6 alkenylphenyl C 1~6 alkyl, wherein the C 1~6 suitable substituents on alkyl include ether, hydroxyl, carboxyl, halogen, and combinations thereof.

[0063] Other polymerization pathways, such as living free radical polymerization and ionic polymerization, can also be employed. The element-forming monomers may form a hydrogel copolymer. For the hydrogel, the reactive mixture generally contains at least one hydrophilic monomer. The hydrophilic component is the component that produces a transparent single phase when mixed with deionized water at a concentration of 10% by weight at 25°C.

[0064] An "interpenetrating polymer" or "IPN" is a polymer that contains two or more polymer networks that are at least partially confounded at the molecular level but are not covalently bonded to each other and cannot be separated unless the chemical bonds are broken.

[0065] A “semi-interpenetrating polymer network” or “semi-IPN” is a polymer comprising one or more polymer networks and one or more linear or branched polymers, characterized by penetration at the molecular level of at least one of the networks by at least some of the linear or branched polymers. A “crosslinking agent” is a bifunctional or polyfunctional component that can undergo free radical polymerization at two or more positions on the molecule, thereby forming branching points and polymer networks. Common examples include ethylene glycol dimethacrylate, tetraethylene glycol dimethacrylate, trimethylolpropane trimethacrylate, methylenebisacrylamide, and triallyl cyanurate.

[0066] The term "optical zone" or "optical area zone" refers to the region of a lens through which light passes before it enters the wearer's retina.

[0067] The term "silicone hydrogel contact lens" refers to contact lenses containing at least one silicone hydrogel. Silicone hydrogel contact lenses generally have increased oxygen permeability compared to conventional hydrogels. Silicone hydrogel contact lenses utilize both their water content and polymer content to deliver oxygen to the eye.

[0068] "Real-time" refers not to an instantaneous period, but rather to a timeframe during which data can be received, processed, and acted upon without exceeding the acceptable subjective tolerance of a commercially important group of wearers.

[0069] "Adjustable" refers to the ability of a device to modify or change one or more of its operating parameters. A "dynamically" adjustable device can bring about such changes in operating parameters in real time or near real time, for example, in response to a change in physiological state or conditions.

[0070] In some implementations, electroactive ophthalmic lenses or “smart” contact lenses including an electronic system are described. The electronic system may actuate a variable focus lens or any other device or a number of devices configured to implement any number of functions that can be performed. The variable focus lens may be implemented using any number of preferred technologies, including but not limited to liquid crystal technology, electroactive polymer technology, variable fluid technology, and liquid meniscus technology, that are capable of changing the focal length of the lens in response to the wearer’s adjustment requests. In other implementations, the electroactive contact lens or other ophthalmic device may include, instead of or in addition to, the variable optical component, one or more other electroactive components configured to perform other functions such as biometric monitoring, wearer alerts, drug distribution, augmented reality, virtual reality, etc. The electronic system may include one or more batteries or other power sources, power management circuits, one or more sensors, clock generation circuits, control circuits implementing preferred control algorithms, and lens driver circuits. The combination of these components may vary in various ways depending on the required or desired functionality of the lens.

[0071] As described above, ophthalmic devices such as contact lenses comprising several components are described herein. While the appropriate combination of devices can potentially yield unlimited functionality, numerous challenges exist in incorporating extra components onto a single piece of optical-grade polymer that constitutes a contact lens. In general, it is difficult to manufacture such components directly onto a lens for a number of reasons, including challenges associated with mounting and interconnecting planar devices on a non-planar surface. Manufacturing them to a specific scale and shape is also difficult. Components placed on or within the lens may need to be miniaturized and integrated onto a small area, sometimes as small as 1.5 square centimeters, or more specifically, 17 square millimeters, of transparent polymer, while protecting the components from the liquid environment over the eye. Furthermore, the added thickness of the additional components can make it difficult to ensure that the contact lens is comfortable and safe for the wearer.

[0072] In addition to the size requirements described herein, electronic devices incorporated into contact lenses must be robust and safe for use in an inherently aqueous environment. Tears have a pH of approximately 7.4, are about 98.2% water, and consist of 1.8% solids, including electrolytes such as sodium, potassium, calcium, magnesium, and chlorides. This is a somewhat harsh environment for introducing electronic components. Furthermore, contact lenses are generally designed to be worn for at least 4 hours, preferably 8 hours or more.

[0073] Electronic components require energy. This energy may be supplied from any number of power sources, including a built-in battery. Because batteries and other potential energy sources have limited possibilities at their size, it is preferable that all electronic components, including, for example, lens drivers, be designed to consume as little power as possible so that they can be worn for a predetermined period even after being left idle for a predetermined period (storage life). Finally, all components of an electronic contact lens must be biocompatible and safe. Therefore, all electronic components incorporated into a contact lens must meet all of the above design parameters, namely size, viability in aqueous solutions, power consumption, and safety.

[0074] Control of electroactive ophthalmic lenses may be achieved through a manually operated external device that communicates wirelessly with the lens, such as a handheld remote unit. Alternatively, control of the motorized ophthalmic lens may be performed via direct feedback or control signals from the wearer. For example, a sensor embedded in the lens may detect blinking and / or blinking patterns. Based on the blinking pattern or sequence, the motorized ophthalmic lens may change its state, such as its refractive power, to focus on either near or far objects.

[0075] Electronic devices in these applications often require a power source. Therefore, it may be desirable to incorporate built-in power storage devices such as primary batteries, rechargeable batteries, and / or capacitors. Alternatively, electronic devices may be inductively powered remotely rather than from a built-in power storage device, and therefore do not require charging. One acceptable method for recharging a battery is by inductive coupling, which magnetically couples an external coil to a charging circuit, which is coupled, connected to, or otherwise coupled to a coil, and which is adapted to recharge a battery embedded in the device.

[0076] Embedding electrical equipment and communication functions into contact lenses presents common problems across numerous areas, including limitations on component dimensions, particularly thickness as well as maximum length and width; limited energy storage capacity in batteries or supercapacitors; limited peak current consumption due to higher internal resistance in small batteries and limited charge storage in small capacitors; limited average power consumption due to limited energy storage; and limited robustness and manufacturability of small, particularly thin components. With regard to communication devices, specific problems include limited antenna efficiency, which is directly related to dimensions or area, number of turns in the case of loop antennas, and antenna efficiency. In addition, the set of frequency bands allocated by regulatory bodies for these applications is also limited, and the selection affects the efficiency of a given structure, maximum allowable transmitter power, interference potential, and other aspects of the communication link. Further characteristics of propagation and absorption on the body depend on frequency, along with the adopted safety limits for the absorption of electromagnetic energy. Various government agencies may or may not issue guidelines or regulations regarding these matters. The antenna efficiency of a physical body decreases, especially if it is an electric field or "E-field" antenna. Similarly, with regard to contactless charging of batteries or similar devices, the dimensions of the antenna are related to the maximum achievable inductance and the maximum voltage or current that can be transmitted to the device.

[0077] A battery, battery cell, or cell is a device in which chemical energy contained in an active material, including the battery, is directly converted into electrical energy by an electrochemical oxidation-reduction reaction. A battery cell or cell comprises three main components: an anode (negative electrode), a cathode (positive electrode), and an electrolyte (ionic conductor). These batteries, battery cells, or cells may be broadly classified as either non-rechargeable primary batteries optimized for a single discharge cycle only, or rechargeable secondary batteries that can be recharged by reversing the oxidation-reduction reaction. Primary batteries offer several advantages, including good storage life, high energy density from low to moderate discharge rates, low maintenance, and ease of use. Secondary batteries also offer several advantages, including high power density, high discharge rate, flat discharge curve, and good low-temperature performance, in addition to their ability to be recharged. Secondary batteries typically have worse charge retention than primary batteries. However, this disadvantage is offset by the fact that secondary batteries are rechargeable. For ease of explanation, the term "battery" is used herein to mean a device comprising one or more electrochemical cells connected in parallel or in series, depending on the desired output voltage and capacity.

[0078] Various ophthalmic contact lenses, including hard and soft contact lenses, may be prepared. Preferably, the ophthalmic device is a soft contact lens that can be made from conventional or silicone hydrogel formulations. Such formulations may contain hydrophilic components, silicone-containing components, wetting agents such as polyamides, crosslinking agents, and further components such as diluents and initiators.

[0079] In some implementations, ophthalmic devices can be concentric contact lenses. Concentric contact lenses are characterized by a material having a refractive index different from that of the primary material surrounding the geometric center of the lens in a substantially concentric ring. Alternatively, a portion of the lens may be ground to a shorter focal length in a substantially concentric pattern with respect to the geometric center of the lens. Concentric contact lenses are always intended to be positioned at the center of the cornea. Distance vision is obtained through the central portion of the lens, which can have a diameter of 1 to approximately 4 mm. Near vision is obtained through the peripheral concentric portion of the lens.

[0080] In other implementations, ophthalmic devices can be non-concentric or segmented contact lenses. Non-concentric or segmented contact lenses are generally characterized in that a near-vision element, which has a different refractive index or is polished to provide a shorter focal length, is located in the lower sector or portion of the lens, away from the geometric center containing the far-vision portion of the lens, and is generally referred to as the bifocal segment of the lens. Most segmented contact lenses are intended to translate, i.e., move perpendicular to the pupil of the eye, when shifting between far-vision and near-vision modes. Such lenses have the advantage of providing a more focused image at both far and near distances, but have the disadvantage that the lens must be designed for controlled translation and to maintain translation and orientation during use.

[0081] Segmented bifocal lenses and other contact lenses that require a specific orientation on the eye, such as toric lenses intended to correct astigmatism, have generally utilized two basic techniques to ensure correct orientation. The lens may be provided with a base-down prism to increase the mass of the lower portion of the lens and create a weighting effect to align the lens. The lens may also be provided with horizontal trimming or chamfering along the lower and / or upper edges so that the combination of eyelid force and scleral molding effectively prevents the lens from rotating on the cornea.

[0082] Figures 1 to 5 illustrate various implementations of the ophthalmic lens 100. In one implementation, the ophthalmic lens 100 includes an optical section 102. The lens includes a front surface 104 and a rear surface 106 opposite the front surface 104. As used herein, the rear surface 106 contacts the cornea when worn by an individual. In some implementations, the lens is molded so that the rear surface 104 can fit snugly against a spherical or hemispherical object such as the cornea. Optionally, in some implementations, the optical section 102 may be a rigid or flexible insert. For example, the optical section 102 may be made from a conventional compound or a silicone hydrogel compound. Additionally, the optical section 102 may be formed using an optical design based on one or more of the wearer's ophthalmic optical characteristics, luminance, refraction, age, and convergence-divergence-momentum pupillary response.

[0083] The lens 100 also includes a recess 108 provided on the front surface 104. The recess is radially displaced from the center point 109 of the lens 100. As will be discussed in more detail below with respect to Figures 3 and 4, the radial distance between the center point of the lens 100 and the recess 108 may be about 4.5 mm to about 5 mm (e.g., 4.50 mm, 4.51 mm, 4.52 mm...4.98 mm, 4.99 mm, 5.0 mm) and any value or range in between, so that the cavity engages with the edge of the upper eyelid of the contact lens wearer. In some implementations, the recess 108 is smooth and is molded as a recess disposed within the front surface 104. The recess 108 forms a thinning zone 108a on the front surface 104. The recess 108 may optionally have a vertical depth to the front surface 104 of 30 to 50 micrometers (μm) at its deepest point (e.g., 30.0 μm, 30.01 μm, 30.02 μm...49.98 μm, 49.99 μm, 50.0 μm) and any value or range in between. As described herein, the recess 108 may define a first inclined surface 108b and a second inclined surface 108c. The thinning zone 108a is located between the first inclined surface 108b and the second inclined surface 108c, as shown in Figure 1. In other words, the first inclined surface 108b and the second inclined surface 108c curve inward or recess inward so that the material of the lens 100 is thinner than the adjacent area, forming a thinning zone 108a. As shown in Figure 1, the first inclined surface 108b is positioned further away from the center point of the lens 100 (i.e., closer to the peripheral region of the lens 100), and the second inclined surface 108c is positioned closer to the center point of the lens 100 (i.e., closer to the central region of the lens 100).

[0084] In some mounting configurations, the recess 108 has a width of approximately 0.8 mm to approximately 1.2 mm (e.g., 0.80 mm, 0.81 mm, 0.82 mm...1.18 mm, 1.19 mm, 1.20 mm) and any value or range between them. In other mounting configurations, the recess 108 has a length of approximately 5 mm to approximately 6 mm (e.g., 5.0 mm, 5.01 mm, 5.02 mm...5.98 mm, 5.99 mm, 6.0 mm) and any value or range between them (e.g., length 502 as shown in Figure 5).

[0085] As described herein, the position, size, and / or combination thereof of the recess 108 allow the ophthalmic lens 100 to interact with the upper eyelid without interfering with the wearer's vision. In some implementations, the recess 108 is configured to provide rotational stability and / or positional control of the lens 100. Thus, the recess 108 is configured to interact with the subject's eyelid wiper 201. The subject's eyelid wiper 201 can fix the position of the contact lens relative to the eye when the eye applies pressure against the recess 108 and holds it in a desired rotational position. Each of the upper and lower eyelids has its own eyelid wiper 201 that can interact with the ophthalmic lens. When the eyelid opens, the eyelid wiper 201 is pushed into the recess 108 and, by interacting with the first inclined surface 108b, pulls the ophthalmic lens 100 away from the pupil. As the eyelid closes, the eyelid wiper 201 is pushed into the recess 108 and interacts with the second inclined surface 108c to push the ophthalmic lens 100 toward the pupil.

[0086] In some implementations, the recess 108 is symmetrical. In this configuration, the widths of the first inclined surface 108b and the second inclined surface 108c are approximately the same. The symmetrical recess can be used in translational ophthalmic lens designs where approximately equal interaction with the lower eyelid wiper 201 between upward and downward gaze is desired. A graph showing the sag of an exemplary symmetrical recess from the lens center (e.g., the center point 109 in Figure 1) is shown in Figure 3. Plots of ophthalmic devices with symmetrical recesses are labeled 302. This is shown in relation to plot 304 of ophthalmic devices without recesses. In Figure 3, the width of the first inclined surface is 0.4 mm, and the width of the second inclined surface is also 0.4 mm. The width values ​​of each inclined surface (i.e., 0.4 mm each, resulting in a total width of 0.8 mm for the recess 108) are provided as examples only, and it should be understood that the width can have other values. As described above, the width of the recess 108 (for example, the width 114 shown in Figure 1) can be approximately 0.8 mm to 1.2 mm. Referring again to Figures 1 to 5, in some mounting configurations, the inclinations of the first inclined surface 108b and the second inclined surface 108c are approximately the same. In other mounting configurations, the inclinations of the first inclined surface 108b and the second inclined surface 108c are different. The inclinations of the first inclined surface 108b and the second inclined surface 108c can be controlled by the radius of curvature. For example, in Figure 3, the first inclined surface has a flatter inclination (e.g., radius 9.6 mm), and the second inclined surface has a steeper inclination (e.g., radius 7.9 mm). The values ​​for the inclinations of each inclined surface are provided as examples only, and it should be understood that the inclinations can have other values.

[0087] Referring again to Figures 1 to 5, in some implementations, the recess 108 is asymmetrical. In this configuration, the widths of the first inclined surface 108b and the second inclined surface 108c are different. Additionally, in some implementations, the length of the first inclined surface 108b is longer than the length of the second inclined surface 108c. In other implementations, the length of the second inclined surface 108c is longer than the length of the first inclined surface 108b. The difference in inclined surface lengths provides a change in surface area for the eyelid wiper 201 to interact. Thus, pressure can be distributed over the lens 100 in any desired configuration. Asymmetrical recesses can be used in ophthalmic lens designs where more or less wiper 201 interaction is desired, as described below. For example, in some implementations, the recess may be provided to interact with the upper eyelid wiper, and the first inclined surface 108b may have a smaller width and a steeper incline (larger width and gentler incline) compared to the second inclined surface 108c. As a result, there is greater interaction of the upper eyelid wiper 201 with the first inclined surface 108b, which exerts an upward holding force by the upper eyelid during primary gaze. Additionally, the gentler incline of the second inclined surface 108c is designed to minimize interaction with the upper eyelid wiper 201 while the eyelid is closed and / or during upward gaze. On the other hand, in other implementations, the recess may be provided to interact with the lower eyelid wiper, and the second inclined surface 108c may have a smaller width and a steeper incline (larger width and gentler incline) compared to the first inclined surface 108b. As a result, there is a greater interaction of the lower eyelid wiper 201 with the second inclined surface 108c, which exerts an upward holding force by the lower eyelid during primary gaze. Additionally, the gentler inclination of the first inclined surface 108b is designed to minimize interaction with the lower eyelid wiper 201 during downward gaze. A graph showing the sag of an exemplary asymmetrical recess versus the distance from the lens center (e.g., center point 109 shown in Figure 1) is shown in Figure 4. Plots of ophthalmic devices with symmetrical recesses are labeled 402. This is shown in relation to plot 404 of ophthalmic devices without recesses.In Figure 4, the width of the first inclined surface is 0.4 mm, and the width of the second inclined surface is also 0.8 mm. The width values ​​of each inclined surface (i.e., 0.4 mm and 0.8 mm, which result in a recess width of 1.2 mm) are provided as examples only, and it should be understood that the widths can have other values. Additionally, the inclination of the first inclined surface 108b and the second inclined surface 108c can be controlled by the radius of curvature. For example, in Figure 4, the first inclined surface has a flatter inclination (e.g., radius 9.6 mm), and the second inclined surface has a steeper inclination (e.g., radius 8.25 mm). The respective inclination values ​​of each inclined surface are provided as examples only, and it should be understood that the inclinations can have other values.

[0088] Alternatively or additionally, in some implementations, the recess 108 is configured to interact with the subject's upper eyelid wiper 201. The first inclined surface 108b and the second inclined surface 108c may be configured to interact with the upper eyelid wiper 201 of the eyelid. Alternatively or additionally, in some implementations, the recess 108 is configured to interact with the subject's lower eyelid wiper 201. The first inclined surface 108b and the second inclined surface 108c may be configured to interact with the lower eyelid wiper 201 of the eyelid.

[0089] Optionally, in some implementations, the ophthalmic lens 100 may further include a raised portion 202 as shown in Figure 2B. The raised portion 202 may be provided on the front surface 104 of the lens 100 and positioned close to the recess 108. In other words, the raised portion 202 may be provided in addition to the recess 108 to create an additional interaction with the eyelid wiper. The raised portion 202 provides an additional contact point between the eyelid wiper and the ophthalmic lens 100. When implemented to provide additional force by an upper eyelid wiper on the lens, the raised portion 202 is positioned radially outward relative to the recess 108. In some implementations, the radial distance between the center point of the lens (e.g., center point 109 in Figure 1) and the raised portion 202 is approximately 4.5 mm to approximately 5 mm (e.g., 4.50 mm, 4.51 mm, 4.52 mm...4.98 mm, 4.99 mm, 5.0 mm) and any value or range in between. The raised portion 202 is positioned on the front surface of the lens (e.g., front surface 104 in Figure 1) and can interact with the eyelid wiper 201 in the same way as the eyelid wiper 201 interacts with the recess 108 as described above. When the eyelid is opened, the eyelid wiper 201 presses against the raised portion 202 on the second side 202b, which is the side closest to the center of the ophthalmic lens. Thus, the eyelid wiper 201 exerts force on the ophthalmic lens 100 by interacting with the second side 202b. In some implementation configurations (not shown), the raised portion 202 is positioned radially inward relative to the recess 108, providing additional force to the lens 100 via the lower eyelid wiper 201.

[0090] Figure 6A shows the orientation of the contact lens 600 with the pupil 602 and eyelid wiper 201 during primary gaze, such as forward gaze, relative to the upper and lower eyelids. Figure 6B shows the orientation of the contact lens 600 with the pupil 602 and eyelid wiper 201 during downward gaze. In Figures 6A and 6B, the recess 108 is provided on the contact lens 600 to interact with the lower eyelid. During downward gaze, the lower eyelid interacts with the recess 108, stabilizing the position of the contact lens 600 relative to the pupil 602. For example, as shown in Figure 6B, the orientation of the contact lens 600 remains largely the same relative to the lower eyelid during downward gaze. Thus, the contact lens 600 shifts its position relative to the pupil 602.

[0091] Figure 7 shows the movement of the eyelid wiper 201 relative to the pupil 602 in the case of downward gaze at different angles (e.g., 20 degrees and 40 degrees). The location of the upper eyelid wiper 201 remains relatively consistent relative to the pupil 602 through downward gaze at different angles. Therefore, the upper eyelid can be used to stabilize the position of the contact lens relative to the pupil 602 by interacting with the recess on the contact lens. The location of the lower eyelid margin becomes closer to the pupil 602 during downward gaze, which means that it can be used to create a shift of the contact lens relative to the pupil 602 by interacting with the recess on the contact lens. As shown in Figures 6A and 6B, the recess provided on the contact lens can stabilize the position of the contact lens.

[0092] Figure 8 shows an implementation configuration of an ophthalmic lens 800 having an optical section 802. In some implementation configurations, the ophthalmic lens 800 includes a plurality of recesses 804a (which interact with the upper eyelid wiper) and 804b (which interact with the lower eyelid wiper) provided on the front surface 806 of the lens 800. This disclosure intends that each of the lens 800 and the recesses 804a, 804b may have similar features to the optical section and recesses described above with respect to Figures 1 to 5. Each recess 804a, 804b is radially displaced from the center point 808 of the lens 800. Multiple recesses 804a, 804b may be configured to interact with the upper and lower eyelids simultaneously. This configuration allows the subject to fix the position of the ophthalmic lens 800 using multiple contact points. In some implementations, the first recess 804a is configured to interact with the subject's upper eyelid wiper, and the second recess 804b is configured to interact with the subject's lower eyelid wiper. In some implementations, the radial distance between the center of the lens 800 and each of the recesses 804a and 804b is approximately 4.5 mm to 5 mm, and the first recess 804a and the second recess 804b are positioned away from the center of the ophthalmic lens 800 in opposite directions.

[0093] As described herein, this disclosure envisions that an ophthalmic lens may be a smart lens, for example, an ophthalmic device having a power supply and control circuit as described below. Such an ophthalmic device may include one or more recesses as described above with respect to Figures 1 to 5. The recesses provide positional and / or rotational control of the ophthalmic device. This may be particularly advantageous for a smart lens, for example, to prevent or minimize movement of the device and to ensure that the electronic circuitry does not interfere with the wearer's vision.

[0094] Referring here to Figure 9, an exemplary ophthalmic device having one or more power sources (e.g., batteries or microbatteries) and control circuits, according to the implementations described herein, is shown. In particular, Figure 9 shows a contact lens 900 including a lens body portion 902 made from any suitable ophthalmic material. Optionally, in some implementations, the lens body portion 902 may be a soft plastic portion. For example, the lens body portion 902 may be made from a conventional formulation or a silicone hydrogel formulation. Additionally, the lens body 902 may be formed using an optical design based on one or more of the wearer's ocular optical characteristics, luminance, refraction, age, and convergence-divergence-momentum pupillary response. In some implementations, the lens body portion 902 may optionally have one or more optical zones, each having optical powers such as a multifocal or bifocal design, positioned to one or more diameters relative to the center of the lens and having widths optimized to provide improved through-focus visual acuity performance. Alternatively or additionally, the lens body portion 902 may be optionally formed with one or a combination of multifocal surfaces, such as zone multifocal surfaces, bifocal surfaces, or continuous multifocal surfaces.

[0095] As shown in Figure 9, the lens body portion 902 surrounds the remaining components of the contact lens 900, such as the electronic insert 904. The electronic insert 904 may include one or more of the optical section 906, the circuit 908, multiple power supplies 910, the interconnection structure 912, and / or sensors 914. The electrical components described herein may be disposed on any suitable substrate, such as a thinned silicone wafer. Additionally, the electronic components described herein may be fabricated using thin-film technology and / or transparent materials. When these technologies are utilized, the electronic components described herein may be optionally placed in any suitable location, as long as they are compatible with the optical section. As shown in the exemplary mounting configuration in Figure 9, the electronic insert 904 has an annular shape, and the electronic components are arranged radially around the electronic insert 904. Certain electronic components may also exhibit an annular shape to better fit the annular substrate. For example, the power supply 910 shown in Figure 9 has an annular shape. There are advantages to providing multiple power supplies 910 as opposed to providing a single power supply. For example, it is difficult to manufacture a power supply (e.g., a battery) with the required capacity and voltage within a single package, especially for microscale applications such as ophthalmic devices. Therefore, multiple power supplies 910 can be used to address this problem. When multiple power supplies 910 are used, they can be connected in series or in parallel.

[0096] In Figure 9, the electronic insert 904 is located in the non-optical zone of the contact lens 100 so as not to interfere with the wearer's vision. For example, electronic components (e.g., circuit 908, power supply 910, interconnect structure 912, sensor 914) are arranged radially outward relative to the lens 900 in Figure 9 (e.g., in the peripheral area of ​​the electronic insert 904). However, it should be understood that electronic components may be arranged in other areas of the contact lens 900, including the optical zone, especially when transparent or nearly transparent electronic devices such as transparent conductive oxides or thin-film transistors are used, or when the components are miniaturized to the extent that they do not excessively affect vision. As is known in the art, refractive index matching techniques may be used to further reduce the visibility of components present in the optical zone of the contact lens 900. In yet another implementation within the scope of the present invention, electronic components may be arranged in other ways to maximize the density of electronic components, such as by arranging the electronic components on vertically stacked dies (not shown) or by forming an electrical substrate having a three-dimensional structure by a thermoforming process or the like. It should also be noted that, within the scope of the present invention, the electronic components and circuits described herein, such as processors and lens drivers, may be combined on a single integrated circuit (IC) or separated into separate ICs.

[0097] The lens 900 (sometimes referred to herein as the “functioning lens”) is operated or controlled by electronic equipment described herein, and can, for example, focus on near or far objects depending on the operation. In other words, the optical unit 906 may be a variable-focus optical unit. The circuit 908 may include, but is not limited to, any of the components described herein, including a processor, memory, lens driver, wake circuit, and / or control circuit, and the circuit 908 may be mounted on the circuit board of the electronic insert 904. It is important to note that the circuit 908 described herein may be implemented in hardware, software, or a combination of hardware and software. In addition, the circuit board used herein may include any suitable substrate, including a flexible polyimide substrate with copper traces and a nickel / gold surface finish. The circuit 108 is connected to a power source 910, such as a battery or battery cell, via an interconnection structure 912. Additional electronic components may also be connected via the interconnection structure 912. It should be understood that the interconnection structure 912, which may include one or more interconnection traces, may be made from any suitable material for electrically connecting electronic components.

[0098] In various implementations, ophthalmic lens recesses (e.g., recess 108 in Figures 1-5) can be used in different lens configurations to fix the ophthalmic lens and optimize the use of specific types of lenses. For example, in some implementations, the ophthalmic lens is a smart lens (shown in Figure 9), and the recess is configured to fix the lens in a fixed position relative to the subject's eyelid, ensuring that the electronic elements within the smart lens do not interfere with the subject's vision. In some implementations, the ophthalmic lens is a toric lens or any other aspheric lens. As mentioned above, toric lenses for astigmatism correction achieve optimal performance when rotation is minimized. This allows the subject to focus on the intended portion of the lens when looking through it. This promotes a consistent magnification effect across the lens surface. Additionally, in some implementations, the ophthalmic lens is a multifocal lens. Similar to toric lenses, multifocal lenses are best optimized when rotation is limited. Multifocal lenses are designed so that the subject can look into different parts of the lens to achieve different magnification effects. Ophthalmic lenses can be held in place using eyelid wipers, creating a stable viewing lens for the subject to see through. In some implementations, ophthalmic lenses are spherical lenses. It is beneficial for spherical lenses to remain in the intended position relative to the subject's eye, resulting in the subject having a consistent magnification focus when looking into the ophthalmic lens. Consistent positioning also helps limit discomfort and prevent the lens from sliding to undesirable positions, such as completely under the eyelid. In some implementations, ophthalmic lenses are cosmetically tinted lenses. Cosmetically tinted lenses may be configured so that the user can engage a recess to ensure that the cosmetically tinted lens maintains its intended appearance and position. Thus, ophthalmic lenses may be engaged in such a way that certain tinted portions of the cosmetically tinted lens do not obstruct the subject's vision.

[0099] It will be understood that the logical operations described herein with respect to various figures may be performed as (1) a sequence of computer implementation actions or program modules (i.e., software) executed on a computing device (e.g., the computing device shown in Figure 10), (2) as interconnected mechanical logic circuits or circuit modules (i.e., hardware) within the computing device, and / or (3) as a combination of software and hardware in the computing device. Therefore, the logical operations described herein are not limited to any particular combination of hardware and software. Implementation is a matter of choice depending on the performance and other requirements of the computing device. Accordingly, the logical operations described herein are referred to in various ways as operations, structural devices, actions, or modules. These operations, structural devices, actions, and modules may be implemented in software, firmware, particular-purpose digital logic, and any combination thereof. It should also be understood that more or fewer operations may be performed than those illustrated and described herein. These operations may also be performed in a different order than those described herein.

[0100] Referring to Figure 10, an exemplary computing device 1000 on which the method described herein can be implemented is shown. It should be understood that the exemplary computing device 1000 is merely an example of a suitable computing environment on which the method described herein can be implemented. Optionally, computing device 1000 may be a well-known computing system including a microprocessor-based system, a minicomputer, an embedded system, an application-specific integrated circuit (ASIC), and / or a distributed computing environment or network computing environment including a plurality of any of the above systems or devices. A distributed computing environment enables remote computing devices connected to a communication network or other data transmission medium to perform a variety of tasks. In a distributed computing environment, program modules, applications, and other data may be stored on local and / or remote computer storage media.

[0101] In its most basic configuration, the computing device 1000 typically includes at least one processing unit 1006 and system memory 1004. Depending on the exact configuration and type of the computing device, the system memory 1004 may be volatile (e.g., random-access memory (RAM)), non-volatile (e.g., read-only memory (ROM) or flash memory), or any combination of the two. This most basic configuration is shown in Figure 10 by the dashed line 1002. The processing unit 1006 may be a standard programmable processor that performs the arithmetic and logical operations necessary for the operation of the computing device 1000. The computing device 1000 may also include a bus or other communication mechanism for communicating information between the various components of the computing device 1000.

[0102] The computing device 1000 may have additional features / functionality. For example, the computing device 1000 may include additional storage such as removable storage 1008 and non-removable storage 1010. The computing device 1000 may also include a network connection 1016 that enables the device to communicate with other devices. The computing device 1000 may also have an input device 1014 such as infrared, light, ultrasound, Bluetooth, Zigbee, or other wired or wireless communication protocols and corresponding receivers. The output device 1012 may take the form of the same or similar wired or wireless communication protocols and corresponding transmitters, and the transmitter and receiver may be separate devices or a single transceiver device. The lens may also be equipped with other input devices specific to the ophthalmic device that allow the wearer to input commands through gestures or gaze characteristics, which may be intentional predetermined sequences (e.g., blinking sequences or extreme eye position sequences), or through unintentional natural indicators such as gaze characteristics, pupil diameter, ocular convergence and divergence movements, eye velocity, and eye movement patterns, which may individually or in combination indicate the wearer's wishes to the ophthalmic device to indicate that they wish to perform certain functions, such as changing focus, also known as the wearer's accommodation requests. Input devices useful for either or both intentional or natural input techniques may include accelerometers, light sensors, gyroscopes, and / or other devices capable of detecting the position or movement of the wearer's anatomical structures (e.g., eyes or pupils). Other manual input devices, such as handheld FOB devices or mobile devices (e.g., smartphones), may be configured to connect wirelessly to the ophthalmic device and may be configured to transmit and receive wireless signals to and from the lens to produce the effect of the lens's functions, such as changes in focal length. Additional devices may be connected to a bus to facilitate data communication between components of the computing device 1000.

[0103] The processing unit 1006 may be configured to execute program code encoded on a tangible computer-readable medium. A tangible computer-readable medium refers to any medium capable of providing data that causes the computing device 1000 (i.e., the machine) to operate in a particular manner. Instructions may be provided to the processing unit 1006 for execution using various computer-readable media. Examples of tangible computer storage media include, but are not limited to, volatile, non-volatile, removable, and non-removable media implemented in any way or technique for storing information such as computer-readable instructions, data structures, program modules, or other data. System memory 1004, removable storage 1008, and non-removable storage 1010 are all examples of tangible computer storage media. Exemplary tangible computer-readable recording media include, but are not limited to, integrated circuits (e.g., field-programmable gate arrays or application-specific ICs), solid-state devices, RAM, ROM, electrically erasable program read-only memory (EEPROM), flash memory, or other memory technologies and other storage devices.

[0104] In one exemplary implementation, the processing unit 1006 may execute program code stored in the system memory 1004. For example, a bus may transport data to the system memory 1004, and the processing unit 1006 may receive and execute instructions from the system memory 1004. The data received by the system memory 1004 may optionally be stored in the removable storage 1008 or the non-removable storage 1010 before or after execution by the processing unit 1006.

[0105] It will be understood that the various technologies described in this application may be implemented in relation to hardware or software, or, where appropriate, in relation to a combination thereof. Therefore, the methods and apparatus of the technical content of this disclosure, or certain aspects or parts thereof, may take the form of program code (i.e., instructions) embodied in a tangible machine-readable storage medium, and when the program code is loaded and executed by a machine such as a computing device, the machine becomes an apparatus for implementing the technical content of this disclosure. When the program code is executed on a programmable computer, the computing device may include a processor, a processor-readable storage medium (including volatile and non-volatile memory, and / or memory elements), at least one input device, and at least one output device. One or more programs may execute or utilize the processes described in relation to the technical content of this application, for example, by using an application programming interface (API), reusable controls, etc. Such programs may be executed in a high-level procedural or object-oriented programming language to communicate with a computer system. However, programs may be implemented in assembly language, machine language, and / or hardware description languages, as desired. In any case, the language may be a compiled language or an interpreted language, and can be combined with a hardware implementation.

[0106] Various ophthalmic contact lenses may be prepared, including hard contact lenses and soft contact lenses. Preferably, the ophthalmic device is a soft contact lens that can be made from conventional or silicone hydrogel formulations. Such formulations may contain hydrophilic components, silicone-containing components, wetting agents such as polyamides, crosslinking agents, and further components such as diluents and initiators.

[0107] The illustrated and described implementations are considered to be the most practical and suitable implementations; however, it will be clear to those skilled in the art that modifications from the specific designs and methods illustrated and disclosed herein are themselves obvious to them and can be used without departing from the spirit and scope of the invention. The invention is not limited to the specific configurations described and shown, but should be configured to be consistent with all modifications that may fall within the appended claims.

[0108] [Implementation Method] (1) Ophthalmic lenses, Front and The rear surface opposite the aforementioned front surface, An ophthalmic lens comprising: a first recess provided on the front surface, which is radially displaced at a position configured to interact with the upper eyelid of the wearer of the ophthalmic lens. (2) The ophthalmic lens according to Embodiment 1, wherein the recess is configured to provide rotational stability and / or positional control of the ophthalmic lens. (3) The ophthalmic lens according to Embodiment 1, further comprising a second recess configured to interact with the lower eyelid wiper of the wearer of the ophthalmic lens. (4) The ophthalmic lens according to Embodiment 1, wherein the radial distance between the center point of the optical part and the first recess is approximately 4 millimeters (mm) to approximately 4.5 mm. (5) The ophthalmic lens according to Embodiment 1, wherein the first recess forms a thinning zone on the front surface of the optical part.

[0109] (6) The ophthalmic lens according to Embodiment 1, wherein the first recess is defined by a first inclined surface that is further from the center point of the ophthalmic lens than a second inclined surface that is closer to the center point of the ophthalmic lens. (7) The ophthalmic lens according to Embodiment 6, wherein the first inclined surface has a steeper inclination than the second inclined surface. (8) The ophthalmic lens according to Embodiment 6, wherein the second inclined surface has a steeper inclination than the first inclined surface. (9) The ophthalmic lens according to Embodiment 6, wherein the length of the first inclined surface is longer than the length of the second inclined surface. (10) The ophthalmic lens according to Embodiment 6, wherein the length of the second inclined surface is longer than the length of the first inclined surface.

[0110] (11) The ophthalmic lens according to Embodiment 1, wherein the first recess has a width of about 0.8 mm to about 1.2 mm. (12) The ophthalmic lens according to Embodiment 1, wherein the first recess has a length of about 5 millimeters (mm) to about 6 mm. (13) The ophthalmic lens according to Embodiment 1, further comprising a raised portion provided on the front surface of the optical portion, wherein the raised portion is positioned in close proximity to the recess. (14) The ophthalmic lens according to embodiment 13, wherein the raised portion is arranged radially outward with respect to the recess. (15) The ophthalmic lens according to Embodiment 14, wherein the radial distance between the center point of the optical part and the raised part is approximately 4.5 millimeters (mm) to approximately 5 mm.

[0111] (16) The ophthalmic lens according to embodiment 13, wherein the raised portion is arranged radially inward with respect to the recess. (17) The ophthalmic lens according to Embodiment 1, wherein the ophthalmic lens is an electroactive lens. (18) The ophthalmic lens according to Embodiment 1, wherein the ophthalmic lens is a toric lens. (19) The ophthalmic lens according to Embodiment 1, wherein the ophthalmic lens is a spherical lens. (20) The ophthalmic lens according to Embodiment 1, wherein the ophthalmic lens is a multifocal lens.

[0112] (21) The ophthalmic lens according to Embodiment 1, wherein the ophthalmic lens is an aspherical lens. (22) The ophthalmic lens according to Embodiment 1, wherein the ophthalmic lens is a cosmetically colored lens.

Claims

1. It is a contact lens, Front and The rear surface opposite the aforementioned front surface, The first recess provided on the front surface is configured to interact with the upper eyelid of the wearer of the contact lens by being positioned at a location displaced upward with respect to the center point of the contact lens when it is fitted to the eye, The first recess is positioned between the first inclined surface and the second inclined surface which is closer to the center point than the first inclined surface. The inclination of the first and second inclined surfaces is asymmetrical and controlled by the radius of curvature. The radius of curvature of the inclination of the first inclined surface is greater than the radius of curvature of the inclination of the second inclined surface. Contact lenses.

2. The contact lens according to claim 1, wherein the recess is configured to provide rotational stability and / or positional control of the contact lens.

3. The contact lens according to claim 1, further comprising a second recess configured to interact with the lower eyelid wiper of the wearer of the contact lens.

4. The contact lens according to claim 1, wherein the radial distance between the center point of the optical part and the first recess is 4 millimeters (mm) to 4.5 mm.

5. The contact lens according to claim 1, wherein the first recess forms a thinning zone on the front surface of the optical part.

6. The contact lens according to claim 1, wherein the length of the first inclined surface is longer than the length of the second inclined surface.

7. The contact lens according to claim 1, wherein the length of the second inclined surface is longer than the length of the first inclined surface.

8. The contact lens according to claim 1, wherein the first recess has a width of 0.8 mm to 1.2 mm.

9. The contact lens according to claim 1, wherein the first recess has a length of 5 millimeters (mm) to 6 mm.

10. The contact lens according to claim 1, further comprising a raised portion provided on the front surface of the optical portion, wherein the raised portion is positioned in close proximity to the recess.

11. The contact lens according to claim 10, wherein the raised portion is arranged radially outward with respect to the recess.

12. The contact lens according to claim 11, wherein the radial distance between the center point of the optical part and the raised part is 4.5 millimeters (mm) to 5 mm.

13. The contact lens according to claim 10, wherein the raised portion is arranged radially inward with respect to the recess.

14. The contact lens according to claim 1, wherein the contact lens is an electroactive lens.

15. The contact lens according to claim 1, wherein the contact lens is a toric lens.

16. The contact lens according to claim 1, wherein the contact lens is a spherical lens.

17. The contact lens according to claim 1, wherein the contact lens is a multifocal lens.

18. The contact lens according to claim 1, wherein the contact lens is an aspherical lens.

19. The contact lens according to claim 1, wherein the contact lens is a cosmetically colored lens.

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