Patent Publication Number: US-2023157893-A1

Title: Comprehensive intraocular vision advancement

Description:
CROSS REFERENCES TO RELATED APPLICATIONS 
     This application is a divisional of and claims priority to and benefit of U.S. Pat. Application No. 17/716,670 filed Apr. 8, 2022 entitled COMPREHENSIVE INTRAOCULAR VISION ADVANCEMENT, which is a non-provisional of U.S. Provisional Pat. Application No. 63/173,019 filed Apr. 9, 2021 and which is also a continuation-in-part of U.S. Pat. Application No. 16/854,766 filed Apr. 21, 2020, which is a continuation of U.S. Pat. Application No. 15/812,433 filed Nov. 14, 2017, which is a non-provisional of U.S. Provisional Pat. Application No. 62/517,894 filed Jun. 10, 2017, all of which are incorporated by reference in their entireties. This application is a divisional of and claims priority to and benefit of co-pending U.S. Pat. Application No. 17/716,670 filed Apr. 8, 2022, which is a non-provisional of U.S. Provisional Pat. Application No. 63/173,019 filed Apr. 9, 2021 and which is also a continuation-in-part of U.S. Pat. Application No. 16/848,650 filed Apr. 14, 2020, which is a continuation of U.S. Pat. Application No. 15/812,294 filed Nov. 14, 2017, which is a non-provisional of U.S. Provisional Pat. Application No. 62/517,894 filed Jun. 10, 2017, all of which are incorporated by reference in their entireties. 
    
    
     STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT 
     Not Applicable. 
     REFERENCE TO SEQUENCE LISTING OR COMPUTER PROGRAM LISTING APPENDIX 
     Not Applicable. 
     BACKGROUND 
     The present disclosure relates generally to ophthalmologic devices for implantation into the eye, and more particular to intraocular implant devices and associated power supplies for enhancing or restoring vision in humans and animals. 
     Over the last few decades, vision related problems in rate of occurrence, age of onset, and severity are becoming increasingly worse to the point it is becoming alarming in the vision care industry. One cause appears to be humans increasingly spending more time viewing electronic display screens. Over time, although display technology improved, people began spending more time looking at electronic displays, including home computers, televisions and mobile electronic devices, often in harsh environments such as full sunlight. As people continue to spend more and more time viewing electronic displays such as small screens in harsh conditions such as sunlight, vision problems continue to increase. 
     Many people experience impaired vision as a result of corneal dysfunction or damage, lens dysfunction or damage, or other conditions of the eye that lead to inability of light to properly pass through the eye to the retina. Various medical procedures have been developed to attempt to correct these types of problems to improve or to restore vision. For example, lens replacement procedures are often used to remove a damaged or occluded lens from the eye. An artificial intraocular lens implant may be inserted into the eye through a small incision in the cornea during a surgical procedure to replace the removed lens. Such procedures are helpful to improve conditions such as cataracts or occluded lenses. 
     However, such conventional procedures for replacing occluded or damaged lenses with replacement intraocular lens implants are often inadequate to restore or enhance vision of patients with corneal conditions. As light initially enters the eye through the cornea, any conditions of the cornea which scatter or block light are generally not amenable to treatment via artificial lens replacement procedures. Although many corneal replacement procedures do exist, they are often inadequate in improving or restoring sight. Additionally, such procedures require extensive healing times and may cause other complications in the eye. 
     What is needed are improvements in devices and methods for improving or restoring vision in patients with impaired cornea or lens tissue in the eye. 
     BRIEF SUMMARY 
     This Brief Summary is provided to introduce a selection of concepts in a simplified form that are further described below in the Detailed Description. This Summary is not intended to identify key features or essential features of the claimed subject matter, nor is it intended to be used as an aid in determining the scope of the claimed subject matter. 
     The present disclosure provides comprehensive intraocular vision advancement (CIVA) using a variety of different embodiments. In some embodiments, a purely optical vision correction or vision enhancement platform provides an adjustable base accommodating lens (ABAL). The adjustable base accommodating lens (ABAL) includes one or more optical elements disposed in an intraocular implant that operate to optically correct or enhance light passing through the eye toward the retina to achieve an adjustable base configuration. As a user ages or develops vision-related changes in eyesight, such as but not limited to presbyopia, the adjustable base accommodating lens can be selectively configured to provide different base and/or accommodation settings to provide far vision correction and/or accommodation for correcting near vision. In some embodiments, the adjustable base accommodating lens includes a plurality of lenses within the intraocular implant that can be mechanically adjusted in relation to each other and in relation to the eye to achieve adjustable base accommodation. In further embodiments, adjustable base accommodating lens (ABAL) may be adjusted by remote input from a user or physician. In further embodiments the adjustable base accommodating lens (ABAL) may employ one or more variable refractive index lenses within the intraocular implant. 
     In additional embodiments, digital vision advancement includes a magie digitale (“MAGITAL”) solution to provide transmission of digital content to the intraocular lens implant for use within the eye. In further embodiments, the comprehensive intraocular vision advancement device and methods of the disclosure provides a dual optical and digital solution including digital information mixed into an optical vision stream (“MIXITAL”). Alternatively, the present disclosure provides systems including a full digital replacement of the optical vision stream wherein a user’s eye becomes a monitor for digital content (“MONITAL”). 
     In further embodiments, the present disclosure provides numerous devices, methods and modes of activating an intraocular implant inside the eye. In some embodiments, a transmitter may be housed inside a user’s mouth to transmit control signals and/or data to the intraocular implant. For example, one or more buttons may be placed on a tooth. The button may be activated by a user’s tongue or with the touch of a finger. Upon activation of the button a control signal may be transmitted wirelessly to a receiver in the intraocular implant, or a peripheral device with a receiver. In some embodiments, an array of buttons on teeth inside the mouth may be provided to provide wireless input to the intraocular implant or to an external peripheral device. In such embodiments, the button array may be used as a keyboard to provide text communications. The button array may communicate to any suitable external device such as a mobile phone or other external peripheral device with a receiver. In some applications, the basic function of the one or buttons is to communicate with intraocular implant. In some embodiments, a user may activate the implant using an external input, such as tapping a user’s teeth together according to a control sequence to activate, deactivate, or change programming modes of the implant. Other external control modalities may include a hardware-based control such as a control on a mobile device or a peripheral device with a transmitter that user may wear, such as a watch or ring. In other embodiments, any suitable peripheral including a transmitter may be used to activate, deactivate or change programming modes of the intraocular implant device. 
     One aspect of the present disclosure provides an intraocular photoelectric power supply system (IO-PEPS) for providing power to one or more microelectronic devices implanted into a human or animal eye. The intraocular photoelectric power supply system provides an implant shaped and sized to fit inside the intraocular lens chamber after a natural lens has been removed. The implant device of the intraocular photoelectric power supply system may be inserted into the lens chamber through a small hole in the cornea utilizing conventional lens replacement surgical tools and techniques. The implant device includes one or more photo-sensors, such as but not limited to a photoelectric device configured to convert incident light into electricity, such as a photovoltaic cell. The photo-sensor or photo-sensor array is positioned on the anterior side of the implant device such that light passing through the cornea will be incident on the sensor or sensor array when the implant device is housed in the lens chamber of the eye. The incoming light irradiating the sensor or sensor array is converted to electricity, which is then available for use by other electronics included on the implant device or otherwise installed within the eye. The incoming light may be specifically tuned to a desired frequency, wavelength, quantity, etc. for optimized power generation using the photoelectric device. The generated electricity may be used immediately, or may be stored in a power storage medium such as a battery on the implant or in the eye for later use. 
     Another aspect of the present disclosure includes an intraocular projection device configured for implantation into an intraocular cavity formed in the lens chamber after a natural lens is removed. The projector implant device, or artificial projector lens implant, includes an implant having an anterior side oriented toward the cornea and a posterior side oriented toward the retina. An optical light emitter, or projector, is installed on the implant posterior side of the implant facing back into the eye toward the retina. The projector is operable to emit light from the implant located in the lens chamber through the eye toward the retina, thereby forming a desired light pattern on the retina. The emitted light pattern from the projector corresponds to an image to be processed by the user’s brain, and may simulate a natural light array associated with a real or artificial image. The projector implant device is miniaturized such that the projector is compact enough to fit on a normal-sized lens implant in the intraocular lens chamber after removal of the natural lens of the eye. 
     In some embodiments, the implant includes both a projector and a photoelectric device of an intraocular photoelectric power supply to provide electrical power for the projector. The projector is positioned on the posterior side of the lens implant facing the retina, and the photoelectric array is positioned on the anterior side of the implant facing the cornea. Natural or artificial light entering the cornea is incident on the photoelectric array on the anterior side of the implant inside the lens chamber, and the electrical power generated by the photoelectric array is transferred to the projector located on the posterior side of the implant facing the retina. The generated electrical power is used to power the projector to emit photons in a light pattern corresponding to a desired image onto the retina. 
     Another aspect of the present disclosure provides an intraocular implant device configured for implantation into the lens chamber after removal of a natural lens. The intraocular lens implant device includes a projector on the posterior side facing toward the retina, a photoelectric array on the anterior side facing toward the cornea, and an external light source spaced from the eye configured to irradiate a beam of light through the cornea onto the photoelectric array. The light from the light source is tuned to provide optimal photoelectric conversion into electricity using the specific photoelectric material installed on the implant. The external light source may be operated with an intensity much higher than natural light because the light from the light source is not incident on the retina, but is rather blocked by the artificial intraocular lens implant and used for photoelectric generation of electric power for use by micro-electronics within the eye such as but not limited to the projector on the intraocular implant device. 
     Yet another aspect of the present disclosure provides an intraocular implant device configured for implantation into the lens chamber after removal of a natural lens, wherein the intraocular lens implant device includes an autofocusing digital camera in addition to the projector and photoelectric array. In this aspect, the projector is positioned on the posterior side of the lens implant facing the retina, and the autofocusing digital camera and photoelectric array are positioned on the anterior side of the implant facing the cornea. Natural or artificial light entering the cornea is incident on the photoelectric array on the anterior side of the implant inside the lens chamber, and the electrical power generated by the photoelectric array is transferred to both the autofocusing digital camera located on the anterior side of the implant and the projector located on the posterior side of the implant facing the retina. The generated electrical power is used to power the autofocusing digital camera to receive incident light through the cornea, actively adjust the lens to focus the incident light, convert the focused incident light into focused image data, and send focused image data to the projector. Additionally, the generated electrical power is also used to power the projector to emit photons in a light pattern corresponding to the focused image data onto the retina. 
     A refraction adjustment unit is provided in yet another aspect of the present disclosure. The refraction adjustment unit provides an intraocular implant device configured for implantation into the lens chamber after removal of a natural lens. The intraocular lens implant device includes an autofocusing electromechanical lens array, a photoelectric array, and a controller, wherein both the autofocusing electromechanical lens array and the photoelectric array are positioned on the anterior side of the implant facing the cornea and the controller is positioned to be in communication with the autofocusing electromechanical lens array. Natural or artificial light entering the cornea is incident on both the autofocusing electromechanical lens array and the photoelectric array on the anterior side of the implant inside the lens chamber, and the electrical power generated by the photoelectric array is transferred to the controller and autofocusing electromechanical lens array. The generated electrical power is used to power the controller to analyze the incoming light incident on the autofocusing electromechanical lens array as it passes through the lens array and to actively adjust the autofocusing electromechanical lens array until the incident light is focused, whereby the focused incident light passes through the autofocusing lens array and to the retina. 
     Other aspects of the present disclosure also provide for a glucose sensor or intraocular pressure sensor to be used in combination with any of the disclosed elements of an intraocular lens implant. The glucose sensor can be operable to measure certain glucose data from a user’s intraocular eye fluids, and wirelessly send the glucose data for an external receiver to receive, analyze, and store. Similarly, the intraocular pressure sensor can be operable to measure pressure levels in a user’s lens cavity, and wirelessly send the intraocular pressure data for an external receiver to receive, analyze, and store. 
     A further objective of the present disclosure is to provide a magie digitale, or “magital” solution to vision advancement. In some embodiments, the devices and methods disclosed herein may be controlled by a user’s voice commands to change accommodation setting or to change other settings such as focus, autofocus, on/off state, image capture, data transmission or other features. 
     Numerous other objects, advantages and features of the present disclosure will be readily apparent to those of skill in the art upon a review of the following drawings and description of a preferred embodiment. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG.  1    is a schematic view of an embodiment of an eye with an open lens chamber having a natural lens removed. 
         FIG.  2    is a schematic view of an embodiment of an eye with an intraocular implant device in accordance with the present disclosure positioned for installation into the open lens chamber of the eye. 
         FIG.  3    is a schematic view of an intraocular implant device in accordance with the present disclosure. 
         FIG.  4    is a schematic view of an intraocular implant device in accordance with the present disclosure. 
         FIG.  5    is a schematic view of an embodiment of an eye with an intraocular implant device in accordance with the present disclosure installed in the lens chamber, and an external light source irradiating the anterior side of the intraocular implant device through the cornea. 
         FIG.  6    is a schematic view of an embodiment of an eye with an intraocular implant device in accordance with the present disclosure installed in the lens chamber, and an external light source irradiating the anterior side of the intraocular implant device through the cornea while the intraocular implant device receives a wireless image data signal from a remote transmitter. 
         FIG.  7    is a schematic view of an embodiment of an intraocular implant device including an intraocular photoelectric power supply and an external light source irradiating light through the cornea onto the photoelectric array included on the implant installed in the lens chamber in the eye. 
         FIG.  8    is a schematic view of an intraocular implant device with an autofocusing digital camera, a photoelectric array, a power supply, and a projector. 
         FIG.  9    is a schematic view of an intraocular implant device with an autofocusing digital camera, a photoelectric array, a power supply, an external transmitter, a wireless receiver, and a projector. 
         FIG.  10    a schematic view of an intraocular implant device with an autofocusing electromechanical lens array, a controller, a photoelectric array, and a power supply. 
         FIG.  11    is a schematic view of an intraocular implant device with an autofocusing electromechanical lens array, a controller, a photoelectric array, a power supply, an external data transmitter, a wireless receiver, and a projector mechanically situated in an unengaged position. 
         FIG.  12    is a schematic view of the intraocular implant device of  FIG.  7   , wherein the projector is now mechanically situated in an engaged position. 
         FIG.  13    is a schematic view of an intraocular implant device with an autofocusing electromechanical lens array capable of axial movement, a controller, a photoelectric array, a power supply, and an external data transmitter. 
         FIG.  14    is a schematic view of an intraocular implant device with an autofocusing digital camera, a photoelectric array, a power supply, an external transmitter, a wireless receiver, a glucose sensor, an external receiver, and a projector. 
         FIG.  15    is a schematic view of an intraocular implant device with an autofocusing electromechanical lens array, a controller, a photoelectric array, a power supply, a intraocular pressure sensor, and an external receiver. 
         FIG.  16    is a schematic view of an eye including an intraocular implant device and a scleral lens positioned to recharge the implant. 
     
    
    
     DETAILED DESCRIPTION 
     While the making and using of various embodiments of the present invention are discussed in detail below, it should be appreciated that the present invention provides many applicable inventive concepts that are embodied in a wide variety of specific contexts. The specific embodiments discussed herein are merely illustrative of specific ways to make and use the invention and do not delimit the scope of the invention. Those of ordinary skill in the art will recognize numerous equivalents to the specific apparatus and methods described herein. Such equivalents are considered to be within the scope of this invention and are covered by the claims. 
     In the drawings, not all reference numbers are included in each drawing, for the sake of clarity. In addition, positional terms such as “upper,” “lower,” “side,” “top,” “bottom,” etc. refer to the apparatus when in the orientation shown in the drawing, or as otherwise described. A person of skill in the art will recognize that the apparatus can assume different orientations when in use. 
     Referring now to the drawings,  FIG.  1    illustrates an example schematic of an eye  10 , showing a cornea  12  through which light initially enters the eye. Eye  10  includes a retina  14  on the opposite side of the eye positioned to receive the incoming light. The sclera  16  surrounds the exterior of the eye  10 . A lens is typically positioned in lens chamber  18 . The iris  22  provides an opening allowing light to pass from the anterior chamber  24  into the lens chamber  18 . Many conventional procedures are currently known for removal of a damaged or occluded lens from lens chamber  18 . For example, in cataract surgery a damaged lens may be phaco-emulsified using a tool to break up the lens. The broken-up lens may then be aspirated from the eye using a negative pressure, and replaced with a liquid solution to maintain the form of the empty lens chamber  18 . Following such procedures, an artificial intraocular lens implant is inserted into the empty lens chamber  18  using known tools and techniques. Such implant procedures are easily reversed. 
     The present disclosure provides a new type of implant device for installation into an empty lens chamber  18 , as shown in  FIG.  1   . For example, as seen in  FIG.  2   , an intraocular implant device  40  is shown outside of the eye  10  for implantation into empty lens chamber  18  of eye  10 . Intraocular implant device  40  includes an anterior side  48  positioned to face cornea  12  after implantation, and a posterior side  50  positioned to face retina  14  after implantation. Intraocular implant device  40  includes numerous technological innovations, and is operable to provide artificial sight improvement or sight restoration. 
     Intraocular Photoelectric Power Supply (IO-PEPS) 
     One aspect of intraocular implant device  40  provides an electrical power supply configured to generate electrical power for use by on-board electronics on the intraocular implant device  40  or alternatively housed within the eye. As such, the intraocular implant device  40  includes an intraocular photoelectric power supply (IO-PEPS) device. 
     As seen in  FIG.  3   , in some embodiments, intraocular implant device  40  includes a body  42  having an anterior side  48 . A photoelectric array  44  including one or more photoelectric sensors is positioned on anterior side  48 . Such sensors include any suitable photovoltaic or photoelectric sensors known in the art capable of converting incident light  56  received upon photoelectric array  44  into electricity. Photoelectric array  44  covers a portion of the surface of the anterior side  48  of implant device  40 . Photoelectric array  44  includes at least one electrical output operable to transmit electric power to a circuit component. In some embodiments, photoelectric array  44  is coupled to a power supply  54 , as shown in  FIG.  3   . Power supply  54  includes any suitable power converter or power storage device on intraocular implant device  40 . Power supply  54  in some embodiments includes a battery configured for storing electrical power generated by photoelectric array  44  for later use by one or more other circuit components. Power supply  54  may be continuously recharging as additional incoming light is incident on photoelectric array  44  and also simultaneously distributing electrical power to other circuit components. 
     Intraocular implant device  40  is generally opaque when housed within the lens chamber  18  such that incident light  56  entering the eye does not pass optically through the lens body  42 . Thus, all incident light entering the eye may be utilized by photoelectric array  44  for energy conversion. As such, the incident light  56  entering the eye may be manipulated to various characteristics for optimization of photoelectric conversion by photoelectric array  44 . For example, in some embodiments, various photoelectric cells used in photoelectric array  44  provide improved energy conversion efficiencies when the incident light  56  has a chrominance in a spectral bandwidth tuned specifically to the properties of the photoelectric junctions. 
     Additionally, because the intraocular implant device  40  is generally opaque in some embodiments, and because the cornea may generally withstand greater luminance than the retina can, the incident light  56  may be further tuned to have increased luminance over natural light to further optimize energy conversion in photoelectric array  44 . Thus, the incident light  56  may be generated using an external light source with modulated chrominance and luminance characteristics as compared to natural light to further improve power generation from the intraocular photoelectric power supply. 
     Your Eye As the Screen (YEATS) 
     One application of the IO-PEPS feature on an intraocular implant device  40  is to power a projector device  46 , shown for example in  FIG.  3   , housed on the same implant device  40  or otherwise disposed within the eye  10 . For example, projector  46  may include any suitable light emitter positioned within the eye in an orientation to project a generated image  58  onto the retina. The emitted light from the projector  46  is incident on the retina much in the way natural light may be incident on the retina after passing through the cornea and the lens. However, in patients with damaged cornea tissue or damaged lens tissue, by the time the light entering the eye makes it to the retina the light pattern is greatly distorted or blocked entirely, causing vision to be distorted or blurred, or causing blindness. By placing a rearward-facing projector  46  on an intraocular implant device  40 , an artificial image may be projected onto the retina to simulate natural light, thereby allowing a user to see the artificial image generated by the projector much like the patient would see normally using natural light. A significant difference is that, when using projector  46 , the generated image  58  may be controlled to include image data from any source, so the patient’s vision may be enhanced or replaced entirely over the field of view available from natural light. 
     During use, projector  46  is powered by electric power generated on-board the intraocular implant device  40  using photoelectric array  44 . Photoelectric array  44  generates enough electric power to operate projector  46  either directly, or through a power supply  54 . In some applications, projector  46  may be turned off remotely while allowing photoelectric array  44  to charge power supply  54 . Once a sufficient amount of energy is stored in power supply  54 , projector  46  may be turned on wirelessly, and photons may be emitted by projector  46  using one or more light emitters. The generated image  58  is then illuminated onto retina  14  through the eye. The retina  14  processes the incident light much like it would natural light, forming an image in the brain and allowing a user to perceive the image. 
     The generated pattern of photons or a generated image  58  projected onto the retina  14  is generated by projector  46  using an input signal  66  received by a wireless receiver  52  in some embodiments, as seen in  FIG.  3    and in an alternative embodiment in  FIG.  4   . Input signal  66  includes information associated with the photon pattern to be generated by one or more light emitters within projector  46 . Thus, the projector  46  is configured to receive a digital input signal including the image data, and to emit photons from the light projector onto the retina in a pattern representative of the image data. The input signal  66  is passed to intraocular implant device  40  wirelessly from a remote transmitter  64 . The input signal  66  is passed to a wireless receiver  52  housed on-board the implant device  40  or alternatively housed at another location within the eye. In some embodiments, wireless receiver  52  is integrated onto projector  46  such that the two are combined as a single unit with wireless data receiver or transmission capabilities. Image data transmitter  64  includes any suitable external device for communicating an input signal  66  to intraocular implant device  40 , and specifically to wireless receiver  52  on intraocular implant device  40 . Any suitable wireless signal transmission protocol for transmitting data or analog signals associated with imagery may be used for input signal  66 . 
     Once the input signal  66  is received by intraocular implant device  40 , the signal is passed to the projector  46 , and the projector executes instructions associated with the signal to generate photons representative of an image to be displayed on the retina. In some embodiments, the input signal  66  corresponds to photographs, text, illustrations, videos or any other image data. 
     As shown in  FIG.  3    and  FIG.  4   , in various embodiments, power supply  54  is also connected to wireless receiver  52  in some embodiments. Thus, power supply  54  may simultaneously supply power to projector  46  and to wireless receiver  52 , if necessary. Alternatively, in some embodiments, photoelectric array  44  provides generated electricity directly to wireless receiver and projector. 
     Wireless receiver  52  may be positioned at any suitable location on intraocular implant device  40 , including on a common circuit board structure with one or more other circuit components, such as but not limited to power supply  54 , projector  46 , photoelectric array  44  or other components. In some embodiments, one or more antennae are connected to wireless receiver  66  to enhance reception of input signal  66  from image data transmitter  64 . In some embodiments, the device may be configured to provide enhanced low-light vision or night vision by using an external image data source that acquires an image using a material that responds more quickly than the retina, or by using a material that selectively processes incoming light with higher sensitivity. 
     One aspect of the present disclosure provides a system that may improve vision over natural analog vision. For example, when natural light enters the eye, the light incident on the retina is limited by the amount of light entering through the cornea and lens. However, using projector  46 , additional, higher resolution light patterns may be projected onto the retina to improve or enhance vision over natural analog vision. 
     As depicted in  FIG.  8   , in some embodiments, an autofocusing digital camera  45  can be provided with projector  46 . The autofocusing digital camera  45  can comprise any digital camera module that is capable of being disposed on the anterior side  48  of the intraocular implant device  40  and is operable to receive incident light  56  through cornea  12 , actively adjust internal camera lens(es) to focus the incident light  56 , convert the focused incident light into focused image data  43 , and send the focused image data  43  to projector  46 . For example, in one embodiment, the autofocusing digital camera  45  could comprise an OmniVision OVM6948 CameraCubeChip™ - a fully packaged, wafer-level camera module measuring 0.65 mm (W) x 0.65 mm (L) x 1.158 mm (H) camera module. In other embodiments, digital camera  45  could comprise a NanEyeC camera module made by Austrian company AMS and having a footprint of 1 x 1 mm, or even the “3D-printed Eagle Eye” - a compound microlens system created by German researchers at the University of Stuttgart and measuring 300 x 300 µm with a height of &lt;200 µm. In some embodiments, digital camera  45  can utilize any suitable lens to focus the incident light  56 , while other embodiments may utilize multiple hard lenses capable of being mechanically adjusted in order to focus the incident light  56 . In other embodiments, autofocusing digital camera  45  can additionally feature a digital zoom functionality, making it capable of enlarging portions of the focused image data  43 . 
     In some embodiments, autofocusing digital camera  45  can be powered by photoelectric array  44  and power supply  54 . However, in other embodiments, the autofocusing digital camera  45  can be integrated with the photoelectric array  44  such that the two are combined as a single unit. In such embodiments, in addition to gathering light  56  to provide focused image data  43  to projector  46 , the autofocusing digital camera  45  is also capable of and responsible for gathering light  56  to power the projector  46  and any other circuit components that may be included. 
     In some other embodiments, like that shown in  FIG.  9   , autofocusing digital camera  45  can be provided in conjunction with both the projector  46  and the wireless receiver  52 . In such embodiments, projector  46  may have a multi-channel input capable of receiving one or both of the focused image data  43  and/or the input signal  66 . Also in such embodiments, power supply  54  can be simultaneously connected and supply power to the autofocusing digital camera  45 , projector  46 , and wireless receiver  52 . In alternative embodiments wherein the autofocusing digital camera  45  is integrated with the photoelectric array  44 , autofocusing digital camera  45  may simultaneously supply power to projector  46  and wireless receiver  52 . 
     Artificial Vision System 
     Referring now to  FIG.  5   , an artificial vision system includes an intraocular implant device  40  including an intraocular photoelectric power supply, including a photoelectric array  44  disposed on the anterior side of implant device  40  facing toward the cornea  12 . Additionally, a projector  46  is disposed on the posterior side of implant device  40  facing the retina  14 . An external light source  68  generates a beam of artificial incident light  56  directed toward the cornea. The generated artificial light  56  is produced solely for the purpose of powering the intraocular photoelectric power supply housed on intraocular implant device  40  installed in the lens chamber  18  within the eye  10 . The generated artificial light  56  is tuned in both chrominance (wavelength and frequency) and luminance (brightness) to provide optimized energy conversion and electric power generation inside the photoelectric array  44 . The power generated by photoelectric array  44  is used to charge power supply  54 , and is subsequently used to power projector  46  to generate a pattern of photos or a generated image  58  for irradiation of the retina  14 . Thus, the only light incident on the retina  14  is the light generated by the projector  46 . 
     An external transmitter  64  sends a wireless input signal  66  to intraocular implant device  40 . Input signal  66  is received by a wireless receiver  52  on the implant device  40 , and the input signal  66  is passed to projector  46  to determine the pattern of generated photons or a generated image  58  projected onto retina  14  by projector  46 . Input signal  66  can include data packets corresponding to image data from any source, such as an external camera. 
     As seen in  FIG.  5   , the incident light beam  56  generated by external light source  68  is collimated in some embodiments to align with the opening of the iris  22  such that the light will be incident on the photoelectric array  44 . In some embodiments, photoelectric array  44  is dimensioned to correspond to the surface region on the body  42  of intraocular implant device  40  aligned with the circular opening defined by the iris  22 . 
     Referring to  FIG.  6    and  FIG.  7   , in additional embodiments, external light source  68  may include a wearable technology including one or more light emitters spaced from the eye  10  and configured to emit light back toward the eye  10  for the specific purpose of powering one or more intraocular photoelectric power supply (IO-PEPS) devices housed in the lens chamber  18  in one or both eyes. For example, in some embodiments, a wearable eyeglass frame  70  includes a first external light source  68   a  and a second external light source  68   b . Frame  70  includes first and second temples  72  positioned to engage a user’s head, as shown in  FIG.  7   . Each external light source  68  emits a beam of artificial light back toward the user’s eye  10 . The beam of generated external light  56  passes into the eye through the cornea  12 , and is incident on the photoelectric array  44  on intraocular implant device  40  housed in lens chamber  18 . The external light source  68  includes any suitable source of light for powering photoelectric array  44 . The light emitted by external light source  68  does not pass directly through the eye to the retina. Instead, the light is converted into electrical energy via the photoelectric array  44 , and is then subsequently converted back into photons using projector  46  to project a desired pattern corresponding to an image onto the retina  14 . 
     As shown in  FIG.  6   , the image generated by projector  46  may come from many different sources. In some embodiments, transmitter  64   a  includes a mobile device such as a cell phone, laptop, tablet computer, television, or other external electronic device. In some embodiments the transmitter  64   a  is a video camera which transmits a video feed. Transmitter  64   a  may include locally stored image data to be used for input signal  66 . Alternatively, transmitter  64   a  may connect dynamically to a remote image storage database  76  via a network, or cloud  74  to access content for input signal  66 . In some embodiments, digital image content, such as movies, images, etc. are streamed from a remote database  76  via a network  74  using network signals  78  to provide access to image data for input signal  66 . 
     Referring further to  FIG.  6   , in some embodiments, an external camera  64   b  is also configured to produce an input signal  66 . The camera  64   b  is positioned to acquire image data associated with the camera’s field of view. The camera  64   b  may be local to a user, for example may be installed on eyeglass frame  70 , or the camera  64   b  may be remote such that the field of view of the camera is not in the vicinity of the user. The artificial vision system allows a user to dynamically change the input on projector  46  such that the projector  46  may select to display an image pattern associated with input signal  66  from first transmitter  64   a  or alternatively from camera  64   b . In additional embodiments, camera  64   b  may instead include a second transmitter such as a cell phone, smart phone, laptop, tablet computer, television, or other external electronic device. In some embodiments, projector  46  includes multiple input channels, and is selectively operable to display image data associated with each separate channel, thereby allowing a user to switch between input signals from different external image data sources. 
     Non-Medical Uses 
     The above referenced devices may also be utilized for non-medical applications such as consumer entertainment, professional vision augmentation, virtual reality content generation and display, military applications, or other non-medical applications. For example, in some embodiments, a user with an intraocular implant device  40  installed in one eye is able to selectively turn on the device to receive image data from any external source via input signal  66 . The user may be able to maintain a natural lens in the second eye to continue to rely on natural analog vision when not using device  40 . As such, the intraocular implant device  40  provides an implantable brain-machine interface capable of delivering digital image content to the user through an image projected directly onto the retina  14 . The image may be manipulated in many ways prior to projection by projector  46  that are not possible via standard analog light transmission through the cornea and lens. This makes enhanced, augmented and artificial vision possible. In some embodiments, this embodiment may be referred to as MAGITAL. 
     Medical Uses 
     The above-referenced devices and methods may also be used in medical applications for sight restoration or sight improvement. In such medical applications a patient may receive an intraocular implant device  40  in the lens chamber of each eye. The patient may then utilize a wireless transmitter  64  to transmit image data from an external source to each intraocular implant device  40 . The transmitter  64  includes a camera oriented toward the user’s local environment in some applications simulating natural vision. Alternatively, transmitter  64  includes an auxiliary input from some other source of digital image content, such as computer, mobile phone, tablet or other source. Medical patients with conditions such as cornea damage may primarily rely on the intraocular implant devices  40  to provide artificial vision where natural analog vision simply is no longer possible due to the inability of light to properly enter and pass through the eye to the retina. 
     The present disclosure further provides associated methods of modifying, improving, restoring, augmenting or restoring vision in humans and animals using the previously-described devices and techniques. For example, a method of restoring vision in an eye comprises the steps of: (1) providing an intraocular implant device including an anterior side and a posterior side, a photoelectric array on the anterior side, and a projector on the posterior side; (2) positioning the intraocular implant device in the lens chamber of the eye such that the photoelectric array faces the cornea and the projector faces the retina; (3) illuminating the photoelectric array with input light from an external light source; (4) converting the input light into electrical energy via the photoelectric array; (5) powering the projector using the electrical energy converted by the photoelectric array; and (6) projecting photons generated by the projector onto the retina, wherein the projected photons correspond to digital image data received wirelessly by the intraocular implant device from a remote transmitter. The method may further comprise sending a wireless input signal to the projector from an external transmitter, wherein the wireless input signal contains image data; emitting photons from the projector in a pattern representative of the image data; providing an external light source positioned to emit light towards the photoelectric sensor; receiving the light in the photoelectric sensor; converting the light into electrical energy; and powering the intraocular implant device with the electrical energy. 
     Refraction Adjustment Unit 
     The embodiment depicted in  FIG.  10    is known as a Refraction Adjustment Unit and shows another application of the IO-PEPS feature on an intraocular implant device  40 , wherein the IO-PEPS is being used to power an autofocusing electromechanical lens array  47  and a controller  49  housed on the same intraocular implant device  40  or otherwise disposed within the eye. In a Refraction Adjustment Unit, the autofocusing electromechanical lens array  47  may include any suitable lens array positioned within the lens implant  40  to receive incident light  56  through the anterior side  48  of the lens implant  40 , actively adjust the incident light  56  as it passes through the lens array  47  until the light  56  becomes focused, and transmit the focused incident light  59  to the retina  14 . In some embodiments, a controller  49  is also provided and may include any suitable controller positioned within the lens implant  40  to be in communication with the autofocusing electromechanical lens array  47 , analyze the incident light  56  passing through the lens array  47 , and actively adjust the lens array  47  until the light  56  is focused. In other embodiments, the controller  49  can be integrated with the autofocusing electromechanical lens array  47  such that the two are combined as a single unit. When implanted in a user’s lens chamber  18 , the Refraction Adjustment Unit depicted in  FIG.  10    can essentially operate as a multifocal lens embedded in the user’s eye and can eliminate the user’s need for reading glasses or bifocals. 
     In some embodiments, the Refraction Adjustment unit embodied in  FIG.  10    is only capable of operating in an “optical mode,” wherein no digital signal is involved and nothing but focused incident light  59  actively passes through the lens  40  to the retina  14 . However, in another embodiment being shown in both  FIG.  11    and  FIG.  12   , the Refraction Adjustment Unit can be optionally operated in either an “optical mode” or a “digital mode.” In this embodiment, the autofocusing electromechanical lens array  47  can be used in conjunction with a wireless receiver  52 , an external transmitter  64 , and a projector  46 , wherein the projector  46  is capable of being mechanically situated in an engaged position or an unengaged position. When the Refraction Adjustment Unit is operating in an “optical mode,” as in  FIG.  11   , the projector  46  is mechanically situated in an unengaged position and inactive, while the autofocusing electromechanical lens array  47  is active and transmitting focused incident light  59  to the retina  14 . The Refraction Adjustment Unit in “optical mode,” in  FIG.  11   , operates in the same matter as the embodiment of the Refraction Adjustment Unit depicted in  FIG.  10   . 
     When operating in optical mode, the device may include autonomous functions to use ghost signals associated with natural tissue, such as electrical signals sent to nerves or muscles present in or around the eye. Such signals may be associated with electrical activity, used to control motion or associated with a pressure change. 
     On the other hand, when the Refraction Adjustment Unit is operating in a “digital mode,” as depicted in  FIG.  12   , the projector  46  is mechanically situated in an engaged position and active, while the autofocusing electromechanical lens array  47  is now inactive. While operating in a “digital mode,” an external transmitter  64  is operable to wirelessly send a digital input signal  66  including image data, a wireless receiver  52  disposed on the intraocular implant body  40  is operable to wirelessly receive the digital input signal  66  and to transmit the digital input signal to the projector  46  mechanically situated in the engaged position, and the projector  46  is disposed on the posterior side  50  of the intraocular implant body  40  and is operable to receive the digital input signal  66  including image data, and to emit photons from the projector onto the retina  14  in a pattern representative of the image data  58 . Thus, in such an embodiment of the Refraction Adjustment Unit, the projector  46  can be selectively engaged to transmit image data  58  to the retina, as in  FIG.  12   , or unengaged such that natural light can pass through the eye to the retina  14 , as seen in  FIG.  11   . 
     Yet another embodiment of the Refraction Adjustment Unit, shown in  FIG.  13   , is capable of correcting the vision problems associated with age-related myopia, presbyopia and hyperopia. Age-related myopia, presbyopia and hyperopia are vision conditions attributable to the size of a person’s eye, and more specifically to the distance between a person’s ocular lens and retina. Myopia, or nearsightedness, occurs when the distance between a person’s ocular lens and retina is too large and the incoming light gets focused in front of the retina, whereas hyperopia, presbyopia or farsightedness, occurs when the distance between a person’s lens and retina is too small and the incoming light gets focused behind the retina or the lens loses flexibility and makes it difficult to focus on near-field objects. As humans get older, the age-related effects of myopia, presbyopia and hyperopia may get worse as natural distancing between the lens and retina occurs. While the autofocusing electromechanical lens array  47  provides real-time focusing by focusing the incident light  56  and transmitting the focused incident light  59  to the retina, this will not work to address age-related myopia or hyperopia without moving the lens array  47  a few millimeters axially forwards or backwards inside the eye. Thus, in the embodiment illustrated in  FIG.  13   , the Refraction Adjustment Unit may additionally include a remote transmitter  64  whereby a user can wirelessly send a digital input signal  66  including axial location adjustment data. In this embodiment, the controller  49  is further operable to wirelessly receive the digital input signal  66  and to adjust the axial location of the optical autofocusing lens array  47  between the anterior side and posterior side of the intraocular implant body  40  in accordance with the location adjustment data. Such axial location adjustments can ensure that the outgoing focused incident light  59  is being focused directly on the retina so that the user does not experience the symptoms associated with age-related myopia or hyperopia. 
     Glucose and Intraocular Pressure Sensors and Pumps 
     In other embodiments, as in  FIGS.  14  &amp;  15   , a glucose sensor  65  may be provided as a convenient tool for users to keep track of their blood sugar levels. Such a feature can be of particularly help to diabetic users, who must constantly keep track of their blood sugar levels in order to adjust their insulin intake dosage. In these embodiments, glucose sensor  65  is disposed on an outer portion of the intraocular implant body  40  so that it can physically contact the user’s intraocular eye fluids when the intraocular implant body is positioned inside the lens chamber  18  of the user’s eye. The glucose sensor  65  is operable to measure glucose in intraocular eye fluids and wirelessly send a digital output signal  67  including glucose measurement data. Also provided in this embodiment is an external receiver  69  operable to wirelessly receive the digital output signal  67 , process the digital output signal  67 , and store the glucose measurement data included therein. 
     In some other embodiments, as in  FIGS.  14  &amp;  15   , an intraocular pressure sensor  65  may be provided as a convenient tool for users to monitor their eye pressure and address any eye pressure abnormalities detected. Normal intraocular pressure generally ranges from 10-21 mmHg and is a signal of generally healthy eye. However, an intraocular pressure greater than 21 mmHg is considered intraocular hypertension, or high eye pressure, and should be addressed by a medical professional immediately as it can either cause or signal to a variety of serious eye conditions such as glaucoma, optic nerve damage, and progressive vision loss. In these embodiments, intraocular pressure sensor  65  is disposed on an outer portion of the intraocular implant body  40 , so that it physically contacts a portion of the eye when the intraocular implant body  40  is positioned inside the lens chamber  18  of an eye. The intraocular pressure sensor  65  is operable to measure intraocular eye pressure and wirelessly send a digital output signal  67  including intraocular pressure data. Also provided in this embodiment is an external receiver  69  operable to wirelessly receive the digital output signal  67 , process the digital output signal  67 , and store the intraocular pressure data included therein. 
     Both the glucose sensor and intraocular pressure sensor  65  have the capacity and functionality to be integrated into each and every one of the intraocular lens implant embodiments disclosed herein. In further embodiments, a glaucoma pump may be integrated into the device and powered using the on-board electronics and power supply. 
     In further embodiments, the present disclosure provides comprehensive intraocular vision advancement (CIVA) devices and methods including an adjustable base accommodating lens (ABAL). As an example, an intraocular implant lens replacement may have a desired diopter to correct a patient’s far-vision, but such a solution does not address issues associated with accommodation or accommodative dysfunction, especially for reading at close ranges. By providing an adjustable base accommodating lens (ABAL) as part of the intraocular implant, precise base adjustments may be made post-operatively to fine-tune vision. In some embodiments, an adjustable base accommodating lens may be adjusted wirelessly using an input control signal from a peripheral device with a transmitter such as mobile electronic device. By adjusting the base setting following implantation, a user may address myopia or hyperopia by changing the base setting of the lens implant. In some applications, an adjustable base accommodating lens may be utilized to improve vision following lens replacement during cataract surgery. 
     In further applications, corrective LASIK surgery may be performed prematurely, causing reduction in vision as a patient continues to age. In such situations, an adjustable base accommodating lens may be implanted to correct myopia or hyperopia using the desired lens diopter. As the patient continues to age, accommodation may be provided at the appropriate time by adjusting the settings on the adjustable base accommodating lens to address age-related accommodative dysfunction. 
     The adjustable base accommodating lens (ABAL) includes one or more optical elements disposed in an intraocular implant that operate to optically correct or enhance light passing through the eye toward the retina to achieve an adjustable base configuration. As a user ages or develops vision-related changes in eyesight, such as but not limited to myopia, hyperopia and presbyopia, the adjustable base accommodating lens can be selectively configured to provide different base and/or accommodation settings to provide far-vision correction and accommodation. In some embodiments, the adjustable base accommodating lens includes a plurality of lenses within the intraocular implant that can be mechanically adjusted in relation to each other and in relation to the eye to achieve adjustable base accommodation. In further embodiments, adjustable base accommodating lens (ABAL) embodiments may employ a variable refractive index lens within the intraocular implant that may be adjusted using mechanical or electromechanical input from a user or physician. The variable refractive index lens includes any suitable variable refractive lens material, including but not limited to an adjustable refractive index material such as but not limited to a polymer, liquid or glass material, or a fixed thin lens with multiple refractive indices to provide a continuum across the lens. One or more lenses in the implant employs variable refractive index technology. 
     In some embodiments, an adjustable base lens includes a power supply such as a battery to provide power for limited adjustments to the optical elements within the implant without the need for a photoelectric array. In such embodiments, the adjustable base lens may be adjusted using the on-board power supply. Applications for such a device may include situations where adjustment may only be needed a few times for the life of the battery, typically shortly after implantation, and there will be no further need to adjust the optical elements. In such applications, it is not necessary to include a photoelectric array for continuous recharging of the device. 
     In further embodiments, the lens implant is configured to selectively filter light passing through the optical elements of the implant to provide darkening of the vision field, similar to the properties of sunglasses. In some embodiments, the optical lens assembly within the implant includes one or more shaded lenses that may be deployed opto-mechanically. Alternatively, in digital embodiments, the shading function can be achieved using a software-based control. In further embodiments, one or more lenses in the optical lens assembly includes photo-chromatic properties to filter light. Any other suitable light filtering modality may be employed to achieve a light filtering feature. Additionally, one or more lenses in the optical lens assembly includes a UV-protective coating to protect the user’s retina from undesirable bandwidths of ultraviolet light. 
     Referring further to  FIG.  6   , in come embodiments the external light source  68  may be positioned on a scleral contact lens  90  positioned on the exterior of the cornea. The scleral contact lens  90  defines an interstitial space between the scleral contact lens and the retina. In some embodiments, a light emitter  92  is disposed between the scleral contact lens  90  and the retina. The emitter  92  is configured to emit incident light  56  toward the intraocular implant body  42  such that the light may be used by a photoelectric array on the implant to power or recharge the intraocular implant. One advantage of this embodiment is that a user may power or re-charge the intraocular implant when the eye is closed, such as when a user is asleep. 
     Thus, although there have been described particular embodiments of the present invention of a new and useful COMPREHENSIVE INTRAOCULAR VISION ADVANCEMENT (CIVA), it is not intended that such references to particular embodiments be construed as limitations upon the scope of this invention.