LENS AND ON-OFF PINHOLE

BACKGROUND

[0001] An intraocular lens can be implanted in a patient's eye to restore or improve vision, such as after cataract surgery. An accommodating intraocular lens is able to change focus, from near to far or from far to near. While the accommodating intraocular lens greatly enhances the patient's vision, there are drawbacks associated with existing mechanisms that power the accommodating intraocular lens. For example, an accommodating intraocular lens that includes a battery in the implant will eventually need to have the battery replaced, which requires the patient to undergo an additional intraocular surgery each time the battery needs replacement. Other mechanisms require continuous electricity fed to the accommodating intraocular lens. Still other mechanisms depend on the patient's capsular bag or ciliary muscles to affect a change in the implanted lens.

[0002] There is a need or desire for an accommodating intraocular lens that can be powered in way that does not require invasive techniques for routine maintenance. There is a further need or desire for an accommodating intraocular device that can be turned on and off without the need for continuous electricity. There is still a further need or desire for an accommodating intraocular device that is not reliant on the patient's capsular bag or ciliary muscles. SUMMARY

[0003] An intraocular implant, as described herein, includes a lens adapted to be implanted in a patient's eye. The lens typically includes at least two disks. One or both disks may have a pinhole, which may be covered by a polarized surface. Additionally or alternatively, one or both disks may have a magnetic surface. In certain embodiments, the disks may each have a discontinuous surface, such as in the form of segmented rings, that can be superimposed on one another. A source external to the patient's eye actuates movement of one or both of the disks causing a change in focusing ability of the implanted lens.

[0004] In embodiments including a pinhole in one or more disks, the pinhole can be turned on or off using magnetic energy, light, or electricity. Alternatively, the pinhole can be turned on or off by inducing a chemical or mechanical change in at least one of the disks, to switch from opaque or semi-opaque to transparent or semi-transparent. [0005] The polarized surfaces may block UVA and UVB and visible light, or they may allow for UV light passage. More particularly, the polarized surfaces may selectively allow passage of some wavelengths of light but not others. In certain embodiments, the disks can be rotated to produce a mask over an entire optic surface in both eyes to achieve pupillary dilation.

[0006] One or both of the disks may be part of a lens that is inserted into or onto a capsular bag, a cornea, a sulcus of an eye, a contact lens, intracorneal, or an anterior chamber lens.

[0007] One or both of the disks may be partially or wholly magnetic, in which case, the external source can actuate movement using magnetism. The disks may rotate, slide, or move in an x,y,z plane, to align polarized surfaces and/or to superimpose the pinholes of the disks onto one another, for example.

[0008] The lens may include more than two disks, such as three or more disks. The lens may include one disk that is rotatable and in proximity to a surface that is polarized and non-rotatable. One polarized surface may be devoid of a pinhole while an adjacent polarized surface does have a pinhole so that rotation of these surfaces relative to each other would produce a pinhole that is partially polarized centrally. Any number of the disks may include one or more independent pinholes, which may be aligned with pinholes of the other disks.

[0009] The disks may have the same or different diameters than one another. For example, the disks may have an outer diameter in a range between about 2 mm and about 7 mm. Furthermore, the pinholes within the disks may have a diameter in a range between about 0.3 mm and about 4 mm. The disks may have a thickness in a range between about 1 urn and about 300 urn.

[00010] A surface of one or more of the disks may include a treatment that facilitates actuation by a magnetic external source. Such treatment may include, for example, magnetochromatic microspheres, paramagnetic paint, and/or an optically transparent magnetic sheet.

[00011] The magnetic external source may be either handheld or adapted to be implanted in a periorbital area near the eye. For example, the magnetic source may be in the form of a ring worn on a finger, a wristband, a bracelet, or a punctal plug.

[00012] The system may include projections that are attached to one or both disks, or the projections may not be attached to either disk but instead be attached to areas surrounding the disks or attached to the patient's eye, to limit movement of one or both disks. In certain embodiments, one or both disks may be connected to an overcenter spring or an overcenter linkage to control the movement of at least one of the disks.

[00013] According to one embodiment, the intraocular lens system may comprise an ocular implant including a lens adapted to be implanted in a patient's eye, wherein the lens includes a first disk having a pinhole with a spinning ring that masks a light source and allows for communication with an external device. In such an embodiment, a neural link may link the patient's brain to the ocular implant and allow optical communication with an external device so that the neural link output is received external to the body with the ocular implant as a conduit for communication. Additionally, the disk may include photoactive materials or reflective materials that can be activated internally or externally to facilitate communication. A neuro control interface (NCI) may actuate movement of the disk to change focusing capability of the implanted lens. Also, the ocular implant may interact with the patient's retina to relay information to specific neocortical locations. The lens implant may act as an input and output center for communication from an NCI or from an external device in both directions.

[00014] Furthermore, an intraocular implant, as described herein, may include one or more electro-conductive protrusions adapted to partially or fully cross a scleral wall of an eye when implanted and remain covered by conjunctiva. The protrusions may abut the eye wall internally to limit rotation of the optical device but without crossing the tissue of the eye wall. The electro-conductive protrusion receives power from a power source external to the eye and transfers the power to a source inside the eye. The electro-conductive protrusion may receive power from an external source through capacitive power transfer. Alternatively, the electro-conductive protrusion may receive power from an implanted or external source through inductive transfer. In particular, electrical power may be received and stored adjacent to or within an optic adapted to be implanted in the eye.

[00015] According to certain embodiments, one or more electro-conductive protrusions may be coupled to a lens optic adapted to be implanted in the eye, and the power source may be an induction device that is either handheld or adapted to be implanted in a periorbital area near the eye. The induction device transmits power to the electro-conductive protrusion causing the lens optic to change refractive power. The induction device may be a ring worn on a finger, a wristband, a bracelet, or incorporated into a punctal plug, for example.

[00016] As an added feature, an externally worn device may be used to track vision and focal distance and to communicate with the induction device to effect a desired lens optic refractive change or change focusing capability through pinhole actuation or alteration. [00017] To effect a lens optic refractive change, the lens optic can expand, rotate, pivot, separate (dual optic), create a pinhole, or provide other means to enhance depth of focus.

[00018] A method of implanting and using an intraocular lens system may include implanting a lens comprising a lens optic into a patient's eye, electrically coupling the lens optic to an ocular surface through electro-conductive protrusions that at least partially cross a scleral wall of the eye and are covered by conjunctiva, and using a power source external to the eye to couple electric energy through the electro-conductive protrusions to the lens optic to change one or more optical properties of the lens optic. This method may be carried out after performing cataract extraction.

[00019] A contact lens system, as described herein, may include a lens adapted to be positioned on a patient's eye; one or more electro-conductive forming filaments integrated into the lens; and a power source external to the patient's eye that transmits power to the electro-conductive forming filaments causing a change in refractive power of the lens. Like the electro-conductive protrusions, the electro-conductive forming filaments can receive power from an external source through capacitive or inductive power transfer.

[00020] According to certain embodiments, the external power source may be a capacitive or inductive device that is either handheld or adapted to be implanted in a periorbital area near the eye and the device transmits power to the electro-conductive forming filament causing the lens to change refractive power. The capacitive or inductive device may be a ring worn on a finger, a wristband, a bracelet, or incorporated into a punctal plug, for example.

[00021] As an added feature, an externally worn device may be used to track vision and focal distance and to communicate with the capacitive or inductive device to effect a desired lens refractive change.

[00022] The change in refractive power of the contact lens may be effected using essentially any of the techniques that can be applied to an implanted lens.

BRIEF DESCRIPTION OF THE DRAWINGS

[00023] In order to describe the manner in which the above-recited and other advantages and features can be obtained, a more particular description is set forth and will be rendered by reference to specific examples thereof which are illustrated in the appended drawings. Understanding that these drawings depict only typical examples and are not therefore to be considered to be limiting of its scope, implementations will be described and explained with additional specificity and detail through the use of the accompanying drawings. [00024] Figure 1 is a diagram of a lens system implanted in an eye.

[00025] Figure 2 is an image of a lens system implanted in an eye.

[00026] Figure 3 is a diagram of two polarized films each having a pinhole, and showing how the films can be superimposed.

[00027] Figure 4 is a diagram of two segmented disks, and showing the disks superimposed.

[00028] Figures 5a through 5f each depict diagrams of scleral fixation of haptics.

[00029] The drawings have not necessarily been drawn to scale. Similarly, some components and/or operations may be separated into different blocks or combined into a single block for the purposes of discussion of some of the embodiments of the present technology. Moreover, while the technology is amenable to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and are described in detail below. The intention, however, is not to limit the technology to the particular embodiments described. On the contrary, the technology is intended to cover all modifications, equivalents, and alternatives falling within the scope of the technology as defined by the appended claims.

DETAILED DESCRIPTION

[00030] An electrically powered accommodating intraocular lens, or other prosthetic capsular device, can be powered in a way that does not require invasive techniques for routine maintenance. More particularly, the lens can be implanted in the eye, and a lens optic within the lens can be electrically coupled to an ocular surface through one or more electro-conductive protrusions so that electric energy may be coupled to the lens using a separately powered inductive or capacitive or capacitive induction device. The inductive or capacitive device may be handheld or implanted in the periorbital area so that it transmits a power signal to the protrusions. The protrusions may be connected to a rechargeable or secondary battery to receive power from the capacitive induction. With the power originating from the inductive or capacitive device that is external to the eye, there is no need to provide a primary battery or other source of power within the eye.

[00031] Alternatively, as described in greater detail below, an intraocular lens can be powered magnetically.

[00032] As used herein, the term "electro-conductive protrusion" refers to a thin strand or filament that is capable of conducting electricity from a power source external to the eye and transferring the power to a source inside the eye. Essentially, the electro-conductive protrusion is an electro-conductive suture that acts as the connection between the scleral wall and the lens optic.

[00033] The electro-conductive protrusions used in combination with accommodating intraocular lenses, when implanted in a patient's eye, either fully cross the scleral wall or partially cross the scleral wall, in which case one end of the protrusion may terminate within the scleral wall or the protrusion may include a bend embedded in or exposed through the scleral wall, such that enough of the protrusion is able to come within close enough contact with an external power source to be able to transfer power from the power source to the lens. Given the sturdy nature of the sclera, the electro-conductive protrusion may be screwed into the scleral wall to hold the protrusion in place. For instance, one end of the electro-conductive protrusion may be flush with the scleral wall. Whether the electro- conductive protrusion fully or partially crosses the scleral wall, in any case, the implanted protrusion remains covered by conjunctiva.

[00034] The electro-conductive protrusions are made of an electrically conductive material, such as an electroactive polymer or shape memory alloy. One example of a suitable electrically conductive material is a metal alloy of nickel and titanium, also known as Nitinol. Essentially any number of electro-conductive protrusions may be used to couple the lens to the ocular surface. For example, an intraocular lens system may include between 1 and 4 electro-conductive protrusions. Additionally, the intraocular lens system may include multiple lenses implanted in the eye.

[00035] As shown in Fig. 1 , the lens 20 can be implanted in a patient's eye, such as in the lens bag 24, sulcus, or anterior to the iris 26. Electrical power 28 can be received and stored adjacent to or within an optic 22 in the lens 20. Two electro-conductive protrusions 30 are shown in Fig. 1 , connecting the lens 20, and more particularly the lens optic 22, to an ocular surface. In Fig. 1 , the electro-conductive protrusions are illustrated as fully crossing a scleral wall 32 of the eye. As described but not shown, the ends of the protrusions 30 within or extending through the scleral wall 32 are covered by conjunctiva.

[00036] The lens optic 22 may be formed of liquid crystal or other energy responsive materials. The lens optic 22 may also be acrylic with mechanical means to change optical capabilities, such as thickening or thinning. Energy transmitted through the protrusions 30 leads to changes in optic shape or optical characteristics. More particularly, the optic 22 can accommodate or provide enhanced depth of focus (EDOF) by expanding, rotating, pivoting, separating (dual optic), creating a pinhole, or providing other means to enhance depth of focus. [00037] According to certain embodiments, the lens optic 22 may be constrained in a housing and adapted to rotate within the housing in response to the power from the power source, thereby altering a dioptric power of the lens optic 22. More particularly, the rotation of the lens optic 22 may polarize a peripheral segment of the lens optic 22 while leaving a central portion clear, thus resulting in a pinhole effect with enhanced depth of focus. Both the lens optic 22 and the housing may be polygon shaped, such that when the optic rotates against the housing, the polygon shapes interact so that the optic is compressed in one clock hour and uncompressed in another clock hour, thus altering the dioptric power of the optic.

[00038] According to other embodiments, when activated by the power source, fluid may be transferred from a peripheral receptacle to a central optic in the lens 20, thereby changing refractive power of the implanted lens 20. This type of migration of fluid, or other types of migration of fluid in the lens 20, may be induced by a piezoelectric pump. A change in refractive power of the implanted lens 20 may also be achieved through changes in alignment of liquid crystals within the lens optic 22.

[00039] In yet other embodiments, the change in refractive power of the implanted lens 20 may occur through forward or backward movement of the lens optic 22 in the lens 20 induced by an electroactive polymer or shape memory alloy. For example, a shape memory alloy may encircle the lens optic 22 and cause the optic to change thickness. An example of a suitable shape memory alloy is Nitinol. In such embodiments, the accommodating intraocular device is not reliant on the patient's capsular bag or ciliary muscles.

[00040] The power source external to the patient's eye that transmits power to the protrusion or protrusions 30, thereby causing a change in refractive power of the implanted lens 20, may transmit the power through capacitive power transfer or through inductive transfer. The inductive power source may be either external or implanted in a periorbital area near the eye. For example, an inductive power source may be implanted in a punctal plug. An external power source may be housed in a handheld device, such as in a ring worn on a finger, a wristband, a bracelet, or a pair of appropriately retrofitted glasses.

[00041] The capacitive device or inductive device transmits power to the electro- conductive protrusion(s) 30. For example, a handheld capacitive or inductive device can activate the lens optic 22 by holding the capacitive or inductive device up to the eye in close enough proximity to the protrusion(s) 30 to transmit power from the device to the protrusion(s) 30, which in turn transmits power to the lens optic 22.

[00042] The user can select the desired change in refractive power on the power source, such as by enhancing close-up focus or distant focus, and the power source can convey the selection to the lens optic, thereby adjusting the lens optic accordingly. For example, if the power source is implanted in a punctal plug, the user may press the punctal plug to achieve the desired setting. In a handheld device, one or more buttons, switches, touchscreens, or other selective devices may be available for the user to select the desired setting. Additionally, the power transmission from the power source to the lens optic 22 may be turned on and off without the need for continuous electricity to be transmitted to the lens optic 22.

[00043] An external device that tracks vision and focal distance and communicates with the power source may be used in combination with the power source or integrated into the power source. For example, the tracking device may be compatible with smart phones, fitness trackers, and the like, and may send alerts, if desired. Furthermore, the external tracking device may communicate with the power source to effect a desired lens optic refractive change.

[00044] Fig. 2 shows that sutures 34 can be used through loop haptics 36 in order to affix the lens 20 to an ocular surface. The haptics 36 may contain features, such as protrusions or anchors, that interact with adjacent tissues to limit rotation of the lens 20 post implantation. Alternatively, haptics 36 may be extended directly through the scleral wall 32 with the tips cauterized to trim them. Haptics 36 pulled through the sclera are covered with moist conjunctiva, just like the electro-conductive protrusions 30.

[00045] In other embodiments, as illustrated in Figs. 3 and 4, the lens 20 can include at least two disks 38, 40. One or both disks 38, 40 may have a pinhole 42, shown in Fig. 3, which may be covered by a polarized surface. Additionally or alternatively, one or both disks 38, 40 may have a magnetic surface. In certain embodiments, the disks 38, 40 may each have a discontinuous surface, such as in the form of segmented rings that can be superimposed on one another, shown in Fig. 4. Each of these embodiments is designed to enhance depth of field for vision. A source external to the patient's eye actuates movement of one or both of the disks 38, 40 causing a change in refractive power of the implanted lens 20 and enables the pinhole 42 or other refractive device to be turned on and off.

[00046] The pinhole 42 can be turned on or off using magnetic energy, light, or electricity. For example, magnets can be used to rotate the disks 38, 40. Alternatively, the pinhole 42 can be turned on or off by inducing a chemical or mechanical change in at least one of the first and second disks 38, 40 to switch from opaque or semi-opaque to transparent or semi-transparent. For example, the pinhole 42 can be formed by certain chemicals that can change color, or the pinholes 42 can darken when exposed to an external force such as light, laser, mechanical stretch, heating, cooling, electricity, or the like. More particularly, a pinhole 42 may change from semi-transparent or transparent to opaque due to stress or strain or stretch on a polymer or due to chemistry. The stress or strain may be heat-related or due to mechanical influence or other factors noted herein.

[00047] The polarized surface of one or both disks 38, 40 may block UVA and UVB and visible light, or it may allow for UV light passage. More particularly, the polarized surfaces may selectively allow passage of some wavelengths but not others.

[00048] The lens system may include a single disk 38, first and second disks 38 & 40, or even three or more disks, such as up to 10 disks. The disks 38, 40 may be combined to produce various sizes of pinholes 42, depending on the desired focal distance. At least one of the disks 38 may be partially or wholly magnetic. One or more of the disks 38, 40 may include a polarized surface and/or one or more independent pinholes 42. Each of the disks 38, 40 may have the same or different diameters, such as between about 2 mm and about 7 mm, or between about 2 mm and about 4 mm. The inner diameters of the disks 38, 40, or the diameters of the pinholes 42, may be between about 0.3 mm and about 4 mm, or between about 1 mm and about 3 mm. The disks 38, 40 may have a thickness between about 1 urn and about 300 urn, or between about 2 urn and about 30 urn.

[00049] A surface of one or more of the disks 38, 40 may include a treatment that facilitates actuation by a magnetic external source or even a magnetic internal device interaction. Such treatment may include, for example, magnetochromatic microspheres, paramagnetic paint, and/or an optically transparent magnetic sheet.

[00050] According to certain embodiments, a magnetic source external to the patient's eye can actuate movement of the magnetic surface or surfaces of the disk or disks 38, 40, thereby causing a change in refractive power of the implanted lens 20. More particularly, the magnetic source may cause the disk or disks 38, 40 to rotate at least to some degree, or to slide, or to move in an x,y,z plane, thereby superimposing the pinholes 42 of the disks 38, 40 and/or aligning polarized surfaces of the disks 38, 40.

[00051] The magnetic source may be either handheld or adapted to be implanted in a periorbital area near the eye. For example, the magnetic source may be encompassed in a ring worn on a finger, a wristband, or a bracelet that can be brought up to the patient's eye to induce movement of a ferromagnetic or magnetic surface on the disk or disks 38, 40, or in a punctal plug.

[00052] The magnetic source may actuate rotation of the magnetic surface of one disk 38 between about 0 degrees and about 90 degrees relative to another disk 40. This rotation may result in light transmission through the pinholes 42 of each of the disks 38, 40 between about 0% (when the disks are rotated 90 degrees relative to each other) and about 100% if less than 90 degrees. The transmission will never be 100% since each polarized sheet will block some percentage of light on their own. All of the techniques described with respect to this concept should include the ability to make a smaller versus a medium versus a larger pinhole 42 depending on the focal distance desired.

[00053] In one embodiment, bilateral lenses can produce a mask over the entire optic surface through rotation of one or more disks 38, 40, which can then lead to pupillary dilation. Dilation of the pupil would expose more of the lens that is posterior to the iris and allow for more direct optical communication with an external device. The disks 38, 40 rotating to block light from entering the eye may be independent of a pinhole device, or these devices may be complementary.

[00054] In another embodiment, one or more pinhole polarized sheets can be aligned to preferentially block light from digital devices so that an automatic opaque or semi-opaque pinhole 42 may be formed when viewing television or a smart phone or similar device. The same configuration would transmit more light when not viewing a digital or light emitting screen. This is related to light being transmitted from LCD screens being polarized at 90 or 45 degrees. Usually, in plane switching (IPS) mode uses 90-degree, while twisted nematic (TN) mode uses 45-degree polarization.

[00055] RFID may be used to trigger movement of the disk or disks 38, 40, or to trigger any mechanism in the system.

[00056] A reed switch is another optional component of the intraocular lens system. More particularly, a magnet may be used to activate the reed switch, which would then lead to activating the pinhole 42, either through rotation of the disk 38 or other movement of the disk 38.

[00057] Yet another optional component of the intraocular lens system is a hamel spinner, which can be used in conjunction with the magnets.

[00058] The first disk 38 having a magnetic surface may be an anterior disk and the second disk 40 may be a posterior disk. Alternatively, the first disk 38 having a magnetic surface may be a posterior disk and the second disk 40 may be an anterior disk. According to certain embodiments, one of the disks 38 may be fixed in place while the other disk 40, namely the disk with the magnetic surface, rotates. The first and second disks 38, 40 may be separate disks, or the first disk 38 may be a first surface of a disk and the second disk 40 may be merely an opposite surface of the same disk. Alternatively, the second disk 40 may include a ring over-molded into which the first disk 38 is embedded. [00059] The second disk 40 may include one or more projections extending from the second disk 40 that limit movement, such as rotation, of the first disk 38. The first disk 38 may also include one or more projections extending from the first disk 38 that interact with the projection or projections extending from the second disk 40 to limit movement of the first disk 38. The projections may be either in the same plane as the disks 38, 40 or out of the plane of the disks 38, 40. Additionally or alternatively, the system may include projections that are not attached to either of the disks 38, 40 yet the projections may limit movement of one or more disks 38, 40. Any of these projections may be extensions of a reed switch.

[00060] Another optional measure for controlling the movement of the disk or disks 38, 40 is the inclusion of an overcenter spring or an overcenter linkage in the system. One or more of the disks 38, 40 may be connected to an overcenter spring or an overcenter linkage so that the actuation or rotation of the disk or disks 38, 40 is limited to two positions.

[00061] The system may also include a plurality of gears between the first disk 38 and the second disk 40 to control movement of the disks 38, 40 with respect to one another. Furthermore, the system may include at least one of the gears married to an adjacent structure to control movement of the disks 38, 40 with respect to the rest of the system.

[00062] One or more of the disks 38, 40 may be attached to a capsular bag implanted intraocular lens, a cornea, a sulcus of an eye, a contact lens, an anterior chamber lens, or the disk or disks 38, 40 may be intracorneal, namely incorporated into the stroma of the cornea.

[00063] As shown in Fig. 4, the disks 38, 40 may each have a discontinuous surface, such as in the form of segmented rings, and these surfaces can be superimposed on one another. The segmented rings may include four segments, as shown in Fig. 4, or between about two and about 10 segments, for example.

[00064] The disks 38, 40 may be formed of metal, ceramic, hydrogel, silicone, hydrophobic acrylic, hydrophilic acrylic, or other polymers. In certain embodiments, the segmented rings may be formed of alternating ferromagnetic and non-ferromagnetic portions to cause rotation when acted upon by an independent magnet that is rotating in the opposite direction. As noted previously, ferromagnetic or electroconductive attachments may project up to the eye wall internally and may pass partially or wholly through the scleral wall. The protrusion may push against the inner eye wall without penetrating through it into tissue.

[00065] In certain embodiments, chemicals can be used to form the discontinuous surface of the segmented rings. In certain embodiments, the discontinuous surface of one or more disks 38, 40 may darken when exposed to an external force, such as light, laser, mechanical stretch, heating, cooling, electricity, chemicals, or combinations of any of these forces or other forces mentioned herein.

[00066] Electrochromic technology may be used to form the disks 38, 40 and/or other portions of the lens implant. In particular, the lens implant must be small enough and flexible enough to be folded and inserted into a very small incision. There is a risk of damage to both the mechanical structure and its actuation mechanism when the lens implant is rolled up or folded. The lens implant requires miniaturized internal circuitry to allow it to accomplish the required actions, such as changing transparency, holding both an on state and an off state for a period of time as needed, taking commands from an external wireless transmitter, and/or receiving and converting RF energy from an external wireless transmitter. Also, the miniaturized circuitry would likely use a custom Application Specific Integrated Circuit (ASIC) chip. A material that can work from an infrequent, low Direct Current (DC) voltage pulse is better for this application than a material requiring an Alternating Current (AC) voltage, as the DC material allows the circuitry component count to be lower and less complex than circuitry that would produce an AC voltage. The circuitry and material choice are interdependent.

[00067] Ideally, the material used in the lens implant would have as many of the following properties as possible: change state instantly, hold its state permanently without need for any power, require a miniscule amount of energy to actuate, be 100% opaque when on and 100% transparent when off, weigh very little, not interfere with normal vision, have no deleterious short- or long-term medical contraindications, have an economical cost to produce, and have a lifetime greater than the patient's expected lifetime.

[00068] According to one embodiment, the material used in the lens implant would have the following qualities: the on state is <50% opaque 400-700nm, the off state is >80% opaque 400-700nm, able to change states in a reasonable amount of time (1 -5 seconds), able to hold a given state for greater than 1 hour, suitably at least 4 hours, and fail in the open or off state of < 50% opaque. Other desirable qualities of the material used in the lens implant include an image quality through the pinhole >70% MTF, and transmittance through the pinhole >90% at 500nm and <10% at <400nm.

[00069] One example of a suitable material for the lens implant is a printed electrochromic display available from rdot AB in Gothenburg, Sweden. The display can be built on other flexible and transparent substrates that may allow the index to be selected as needed. The electrochromic layer can change optical state when a voltage is applied. The electrochromic layer thickness may be around 100 nm, for example. Additional layers required for circuits and barriers may be added. For example, the lens implant would also include an antenna, a radio frequency receiver, a capacitor charger, and logic sufficient for control.

[00070] The antenna could be a circular loop of one or more turns at the extreme periphery of the implant. This antenna could be printed from a conductive ink or similar material on the inner surface of the implant substrate so as to have minimal thickness. The antenna would gather the energy from the activating device (eyeglasses or similar outfitted appliance) to effect a change of state. The activating device could have a switch mechanism, radio frequency transmitter, and an easily replaceable or rechargeable battery. The antenna could be connected to a radio frequency receiver which converts the RF energy into very low voltage electricity which is used to charge a small capacitor. When sufficient energy has been stored, the Control Logic would then effect a change in state to either the opaque or transparent state. There are numerous possible mechanisms for distinguishing a request to transition between opaque or transparent. These mechanisms include pulse code modulation, amplitude modulation or frequency modulation among others. These control functions could be implemented in an Application Specific Integrated Circuit (ASIC) embodied in a very small die. The die, capacitor and antenna would be embedded in the implant area with the expectation that they would cause minimal or no impact to the patient's field of vision.

[00071] According to one embodiment, the intraocular lens system may comprise an ocular implant including a lens 20 adapted to be implanted in a patient's eye, wherein the lens 20 includes a first disk 38 having a pinhole 42 with a spinning ring that masks LED or other light source and allows for communication with an external device. The spinning may allow for pulse communication from the lens 20 to an external device, such as a phone or a computer. One example of such a pulse communication is Morse Code. In such an embodiment, this rapid digital output is based on a neural link that may link the patient's brain to the ocular implant and allow optical communication with an external device. Additionally, the disk 38 may include photoactive materials or reflective materials that can be activated externally to facilitate communication. A neuro control interface may actuate movement of the disk 38 to change refractive power or the implanted lens 20. Thus, the refractive power or focusing capability of the lens 20 can seemingly be "automatically" adjusted through this communication between the patient's brain and input received through the ocular implant. The change in refractive power may be carried out using any of the techniques described herein, such as through a transfer of fluid from a peripheral receptacle to a central optic in the lens 20, through a migration of fluid in the lens 20 induced by a piezoelectric pump, through forward or backward movement of a lens optic 22 in the lens 20 induced by an electroactive polymer or shape memory alloy, through induction of a shape memory alloy that encircles a lens optic 22 in the lens 20 and causes the optic to change thickness, or through changes in alignment of liquid crystals within an optic body in the lens 20. Also, the ocular implant may interact with the patient's retina to relay information to specific neocortical locations.

[00072] The method of implanting the intraocular lens system can be performed using currently known surgical steps. The intraocular lens system can be used in cataract surgery, after performing cataract extraction, to replace the natural lens. Figs. 5a through 5f show various types of intrascleral fixation methods to achieve stability of intraocular lenses. The illustrated techniques do not entail the use of sutures. Using a needle, a blade, or a trochar, sclerostomies can be performed using various techniques to gain intraocular access. Some surgeons prefer to create scleral tunnels while others may prefer to use scleral flaps for scleral fixation of haptics. The stability of the intraocular lenses is attained by the scar tissue formed around the haptics. In certain situations, such as when the natural bag is compromised, the lens optic can be attached to the scleral wall through the sulcus using sutures and/or haptics.

[00073] In particular, Fig. 5a shows the use of a blade 44 to make scleral lamellar incisions 46 that are each approximately 1 .5 mm and positioned approximately 1 .7 mm from the lens bag 24. As shown in Fig. 5b, the lens 20 with protrusions 30 can be implanted to replace the natural lens. Fig. 5c shows the use of forceps 48 to implant the lens 20 with the protrusions 30, while a 27-gauge needle 50, for example, can be inserted through a sclerotomy 52 to retrieve an end of one of the protrusions 30. In Fig. 5d, the 27-gauge needle 50 is inserted through a sclerotomy 52 to retrieve an end of the other protrusion 30. Fig. 5e shows the needle 50 pulling the ends of each of the protrusions 30 through the sclerotomies 52 and forming a scleral tunnel 54 extending from each scleral lamellar incision 46. In Fig. 5f, each of the ends of the protrusions 30 are secured in the scleral tunnels 54.

[00074] The intraocular lens system may be implanted using either an ab interno approach, pulling the protrusions 30 inward from inside the sclera, or an ab externo approach, pulling the protrusions 30 inward from outside the sclera. Furthermore, the protrusions 30 may be formed as a fixed part of the lens 20 prior to implantation, or the protrusions 30 may be attached to the lens 20 after implantation.

[00075] Once the lens 20 has been implanted and the lens optic 22 is electrically coupled to an ocular surface through the electro-conductive protrusions 30, a power source external to the eye can be used to couple electric energy through the protrusions 30 to the lens optic 22 to activate the optic in order to change one or more optical properties of the lens optic 22. Using either capacitive or inductive power transfer, the external power source can activate the optic 22 by bringing the external power source close enough to the protrusions 30, within close proximity to the eye. In the case of a periorbital implant, the implant can be manually activated.

[00076] Benefits of the electrically powered accommodating intraocular lens system described herein include simple circuitry, with no battery needed in the lens implant. Additionally, the power can be turned on and off, with no need for continuous electricity. Furthermore, a variety of techniques for achieving enhanced depth of focus can be used with the intraocular lens system. The external source of activation can be discreet and conveniently worn. Additionally, the user can program in a level of accommodation or focus desired.

[00077] Much of the same technology used in the electrically powered accommodating intraocular lens system can be applied to a contact lens system. More particularly, a contact lens system can include a lens adapted to be positioned on a patient's eye and one or more electro-conductive forming filaments integrated into the lens. A power source, as previously described, can be used to transmit power to the electro-conductive forming filaments or filaments to cause a change in the refractive power of the lens.

[00078] As used herein, the term "electro-conductive forming filament" refers to a thin strand or filament that is capable of conducting electricity from a power source external to the eye and transferring the power to a source within a lens.

[00079] The contact lens may include a lens optic as described in the previous embodiments. The lens optic may accommodate or provide enhanced depth of focus by any of the previously described means. In one particular example, the change in refractive power of the contact lens may occur through forward or backward movement of the lens optic in the lens induced by an electroactive polymer or shape memory alloy. For example, a shape memory alloy, such as Nitinol, may encircle the lens optic and cause the optic to change thickness.

[00080] The electro-conductive forming filament may receive power from an external source through either capacitive or inductive power transfer. In the contact lens system, the electrical power is received and stored within or on the lens. As in the previously described embodiments, the external power source may be either external or implanted in a periorbital area near the eye. For example, an inductive power source may be implanted in a punctal plug. An external power source may be housed in a handheld device, such as in a ring worn on a finger, a wristband, a bracelet, or a pair of appropriately retrofitted glasses. [00081] The capacitive device or inductive device transmits power to the electro- conductive forming filament(s). Charging the device could require the user to place the wireless charger device in the proximity of the eye for a short period of time. The charging device could transmit radio frequency energy over the air to the receiver antenna in the implanted device along with a small amount of information necessary to clearly dictate the target state of the device, such as activating the lens optic by holding the capacitive or inductive device up to the eye in close enough proximity to the forming filament(s) to transmit power from the device to the forming filament(s), which in turn transmits power to the lens optic.

[00082] As described with respect to the previous embodiments, an external device that tracks vision and focal distance and communicates with the power source may be used in combination with the external power source or integrated into the external power source.

[00083] The descriptions and figures included herein depict specific implementations to teach those skilled in the art how to make and use the best option. For the purpose of teaching inventive principles, some conventional aspects have been simplified or omitted. Those skilled in the art will appreciate variations from these implementations that fall within the scope of the invention. Those skilled in the art will also appreciate that the features described above can be combined in various ways to form multiple implementations. As a result, the invention is not limited to the specific implementations described above, but only by the claims and their equivalents.