Patent Grant
8709078
The invention relates generally to methods and apparatus for vision restoration and optical nerve stimulation, and more particularly to a method and apparatus for transmission of infrared optical stimulation to nerves (in contrast to the regular optical sensing rod and cone cells) in a human eye to obtain a sensation of vision.
For many patients suffering from retinal degenerative diseases such as advanced or age-related macular degeneration (AMD) and retinitis pigmentosa (RP) there has been little hope for maintaining vision. Every year, 700,000 new cases of AMD in the U.S. are diagnosed and 10% of those patients will become legally blind. There are presently no cures for these debilitating diseases, and, at best, current treatments only slow the disease progression. The overall social and economic impact of AMD and RP is immense and the importance of treating blindness is profound as this is a problem of significant scope and breadth. There is an unmet need to treat this ailment by developing a visual prosthetic with a large number (e.g., thousands) of stimulation channels to realistically restore sight using infrared light to stimulate the retinal nerves. Advanced macular degeneration and retinitis pigmentosa are both diseases that degrade vision in patients and eventually will lead to blindness.
Researchers have artificially stimulated various parts of the human nervous system for many years as a way to restore lost or damaged neural function of various systems in the human body. Neuroprosthetic devices circumvent non-functioning physiological structures (hair cells in the ear, rods and cones in the eye) which would normally transduce an external stimulus (sound, light) into an action potential. Presently, there are numerous efforts underway to develop neuroprostheses to restore sight at various interventional anatomical locations: in the subretina, the epiretina, the optic nerve and in the visual cortex. These devices apply an electric current pulse to stimulate the neurons of the visual system which is inherently hindered by a lack of spatial selectivity. Electrical current spread leads to imprecise nerve stimulation and limits the ability of the neuroprosthesis to restore function. The limitation of spatial selectivity is based on fundamental physical principles of electrical stimulation. To date, after 20 years of development, electrical implants are just now hoping to make the jump to 64-channel systems from 16-channel systems. This is far less than the thousands of channels estimated to be needed for a good vision prosthetic. The technology is further limited by the fact that physical contact is required with tissue, which can lead to damage over time. Implantation of a complex powered device in very close proximity to sensitive neural tissue forms a significant drawback to this approach, making it impossible to update the technology without further risky surgeries.
There have been rudimentary attempts to stimulate the retinal nerves with electrical signals, which are being conducted by various groups globally. For example, the Argus™ II implantable device, by Second Sight Medical Products, Inc., 12744 San Fernando Road—Building 3, Sylmar, Calif. 91342, USA, which is intended to treat profoundly blind people suffering from degenerative diseases such as RP. The Second Sight Medical Products, Inc. Argus™ II system works by converting video images captured from a miniature camera, housed in the patient's glasses, into a series of small electrical pulses that are transmitted wirelessly to an epiretinal prosthesis array of electrodes implanted inside the eye on the retina. These pulses then stimulate the retina's remaining cells resulting in the corresponding perception of patterns of light in the brain. Patients supposedly learn to interpret these visual patterns thereby gaining some functional vision.
U.S. Pat. No. 7,079,900 issued Jul. 18, 2006, to Greenburg et al., titled “Electrode Array for Neural Stimulation,” is incorporated herein by reference. Greenburg et al. describe a retinal color prosthesis to restore color vision by electrically stimulating undamaged retinal cells, which remain in patients with lost or degraded visual function. There are three main parts: one is external to the eye, the second part is internal to the eye, and the third part communicates between those two parts. The external part has color imaging means (CCD or CMOS video camera), an eye-tracker, a head-motion tracker, a data processor, a patient's controller, a physician's local controller, a physician's remote controller, and a telemetry means. The color data is processed in the video data processing unit and encoded by time sequences of pulses separated by varying amounts of time, and also with the pulse duration being varied in time. The basis for the color encoding is the individual color code reference. Direct color stimulation is another operational basis for providing color perception. The electrodes stimulate the target cells so as to create a color image for the patient, corresponding to the original image as seen by the video camera. The physician's test unit can be used to set up or evaluate and test the implant during or soon after implantation.
U.S. Pat. No. 7,914,842 issued Mar. 29, 2011, to Greenberg et al., titled “Method of Manufacturing a Flexible Circuit Electrode Array,” is incorporated herein by reference. Greenberg et al. describe polymer materials and electrode array bodies for neural stimulation, especially for retinal stimulation to create vision. The method lays down a polymer layer, applies a metal layer to the polymer and pattern to create electrodes and leads, and applies a second polymer layer over the metal layer and pattern to leave openings for electrodes. The array and its supply cable are a single body.
Electrical stimulation represents a major challenge in developing implantable devices with long-term system performance while reducing their overall size. The Boston Retinal Implant Project has identified long-term biocompatibility as one of the most significant challenges to be met in order to develop a successful retinal prosthesis. For example, U.S. Pat. No. 6,324,429 issued Nov. 27, 2001, to Shire et al., titled “Chronically Implantable Retinal Prosthesis,” is incorporated herein by reference. Shire et al. describe a chronically implantable retinal prosthesis for the blind which will restore some useful vision to patients over at least several degrees of their former field of view. These thin, strong, and flexible epiretinal devices are constructed of or encapsulated in known biocompatible materials which will have a long working life in the eye's saline environment. The function of the implants is to electrically stimulate the ganglion cell layer at the surface of the retina using controlled current sources. Due to the exceptionally low mass of the implant and its flexible, nearly planar form, patient discomfort and fluid drag caused by the implant minimized. These physical attributes also substantially reduce the potential of harm to the most delicate structure of the eye, the retina, and therefore enhance the long term safety and biocompatibility of the device. Since no micro-cables are required to be attached to the device, and its overall form and edges are rounded, the device is not expected to stress the retina during chronic implantation. A provision is also made for nutrients to reach the retinal cells underneath the device to assure their long-term health.
U.S. Pat. No. 7,908,010 issued Mar. 15, 2011, to Greenberg et al., titled “Retinal Prosthesis with Side Mounted Inductive Coil,” is incorporated herein by reference. Greenberg et al. describe a retinal prosthesis with an inductive coil mounted to the side of the eye by means of a strap around the eye. This allows for close coupling to an external coil and movement of the entire implanted portion with movement of the eyeball.
Electrical stimulation, as described in the above devices and patents, is limited since the spread of electricity does not allow separate or independent stimulation of individual retinal nerve cells or even small-enough groups of nerve cells for sharp or clear vision. This electrical-stimulation technology is severely limited, as electricity spreads in human tissue and thus will severely limit the number of stimulation sites. Electrical stimulation thus greatly limits the number of sites that could be separately stimulated. Additionally, the electrical-stimulation approach will require implantation of a powered (e.g., an electrically powered) device, which has significant, difficult issues associated with obtaining power into the eye and using the power by devices in the eye.
Other work is being done in the area of optogenetics wherein a virus is used to genetically sensitize nerve cells to certain wavelengths of light, e.g., PCT publication WO 2010/011404 A2 titled “Vectors for Delivery of Light-Sensitive Proteins and Methods of Use,” which is incorporated herein by reference. This area may have some potential, however it will require significant development work, it involves injecting a virus into nerve tissue (which may have significant side effects and FDA-approval issues), and the virus is only partially taken up by nerve cells.
Materials that are compatible with the eye are described in U.S. Pat. No. 6,254,637 to Jin Hak Lee et al., titled “Artificial Cornea and Implantation Thereof”; U.S. Pat. No. 6,391,055 to Yoshito Ikada et al., titled “Artificial Cornea”; U.S. Pat. No. 6,976,997 to Noolandi et al., titled “Artificial Cornea”; U.S. Pat. No. 7,857,849 to David Myung et al., titled “Artificial corneal implant”; and U.S. Pat. No. 7,909,867 to David Myung et al., titled “Interpenetrating Polymer Network Hydrogel Corneal Prosthesis”; each of which is incorporated herein by reference in its entirety.
Numerous digital light projection micro-electro-mechanical-system (MEMS) devices exist. For example, U.S. Pat. No. 4,566,935 issued to Hornbeck on Jan. 28, 1986, titled “Spatial Light Modulator and Method” and is incorporated herein by reference in its entirety. Hornbeck described methods of fabrication of spatial light modulators with deflectable beams by plasma etching after dicing of a substrate into chips, each of the chips an SLM. Various architectures available with such plasma etching process were disclosed and include metal cloverleafs for substrate addressing, metal flaps formed in a reflecting layer over a photoresist spacer layer, and torsion hinged flaps in a reflecting layer.
As another MEMS display example, U.S. Pat. No. 7,776,631 issued to Miles on Aug. 17, 2010, titled “MEMS Device and Method of Forming a MEMS Device,” and is incorporated herein by reference in its entirety. Miles described light in the visible spectrum being modulated using an array of modulation elements, and control circuitry connected to the array for controlling each of the modulation elements independently, each of the modulation elements having a surface which is caused to exhibit a predetermined impedance characteristic to particular frequencies of light.
U.S. Pat. No. 7,177,081 issued to Tomita et al. on Feb. 13, 2007, titled “High Contrast Grating Light Valve Type Device,” and is incorporated herein by reference in its entirety. Tomita et al. describe a grating light valve with a plurality of spaced reflective ribbons that are spatially arranged over a substrate with reflective surfaces. The grating light valve is configured to optimize the conditions for constructive and destructive interference with an incident light source having a wavelength λ. The grating light valve preferably has a set of movable active ribbons alternating between the set of stationary bias ribbons. In operation, active ribbons are moved by a multiple of λ/4 to switch between the conditions for constructive and destructive interference.
U.S. Pat. No. 4,720,189 issued Jan. 19, 1988 to Heynen et al., titled “Eye-Position Sensor,” is incorporated herein by reference in its entirety. Heynen et al. describe an eye-position sensor for use in an eye-activated optical transducer in which a spatial filter is used to modify light reflected from the eye to form a substantially rectangular pattern on a quadrantal array of contiguous sensors. This arrangement provides a substantially linear change in the output signal from the sensors in response to an equivalent movement of the eye.
U.S. Pat. No. 6,055,110 issued Apr. 25, 2000, to Kintz et al., titled “Compact Display System Controlled by Eye Position Sensor System,” is incorporated herein by reference in its entirety. Kintz et al. describe a virtual image display system is provided which is made thinner through the use of an immersed beam splitter, and in one embodiment, total internal reflection. The display system includes an imaging surface on which a source object is formed, a first optical element having a reflective function and a magnification function, a second optical element having a magnification function and an immersed beam splitting element positioned between the first and second optical elements, the immersed beam splitting element including a beam splitter surrounded by an optically transparent material having a refractive index greater than air. An illumination source projects the source object formed at the imaging surface through the optically transparent material to the beam splitter. The beam splitter reflects the projected source object to the first optical element. The first optical element magnifies the projected source object and reflects a magnified virtual image of the projected source object to the beam splitter. The magnified virtual image traverses the beam splitter to the second optical element which magnifies the magnified virtual image to produce a compound magnified virtual image of the source object.
There remains a need in the art for an improved prosthesis and method for stimulating vision nerves to obtain a vision sensation that is more useful for the patient.
The present invention uses infrared nerve stimulation (INS) technology that uses infrared light to cause action potentials in nerve cells in the eye. In recent years, optical-stimulation technology has been developed to stimulate nerves. This INS technology can achieve much higher precision and selectivity of stimulation than using electrical current to trigger nerve action potentials. In some embodiments, the present technology uses pulsed, infrared lasers to excite the neural tissue next to the retina directly and without tissue damage. The advent of this technology represents a paradigm shift in artificial nerve stimulation because it allows a high degree of spatial selectivity of neural stimulation without the need for tissue contact.
The present invention provides an improved prosthesis and method for stimulating vision nerves to obtain a vision sensation that is useful for the patient that has lost vision due to AMD, RP, and other diseases. The invention utilizes infrared light to cause action potentials in the retinal nerves similar to those action potentials that result from rods and cones stimulated by visible light in healthy retinas. In a related invention by one of the inventors of the present invention, an eyeglass-mounted system is described that collects visual information and converts it into a stimulation pattern which is projected into the eye at an infrared wavelength with the purpose of causing an action potential in the retinal nerves with the purpose of recreating sight. As the infrared light stimulation wavelengths are normally strongly absorbed by the vitreous humor and tissues of the eye, in some embodiments the invention provides a pathway or “image pipe” for transmitting a stimulation pattern of infrared nerve-stimulation light, from an external infrared-light-emitting stimulator array, through the eye and focusing the stimulation pattern of infrared light on the nerves of the retina, especially the macula and fovea. In some embodiments, the invention provides improved resolution down to a group of nerves, or even the individual nerve level, with sufficient energy density so as to cause desired action potentials in the targeted nerves.
In some embodiments, a laser diode emitting light with a 1.87-micron wavelength stimulates nerves. This wavelength is important because devices capable of generating this wavelength are more available than longer mid-IR wavelengths. In some embodiments, laser-diode light of a 2.1-micron wavelength is used for nerve stimulation. Laser diodes that emit 2.1-micron-wavelength light are currently in research and would most likely work as well as other wavelengths, since this wavelength, when generated by a lamp-pumped solid-state laser, has been shown to be effective in stimulating nerves. In some embodiments, a laser-diode device (having one or more emitters) outputs light that is used for nerve stimulation, wherein the light has a wavelength of between about 1.5 microns and about 6 microns; in various embodiments, for example, the wavelength is in the far infrared at about 1.5 microns, or about 1.51 microns, about 1.52 microns, about 1.53 microns, about 1.54 microns, about 1.55 microns, about 1.56 microns, about 1.57 microns, about 1.58 microns, about 1.59 microns, about 1.6 microns, about 1.61 microns, about 1.62 microns, about 1.63 microns, about 1.64 microns, about 1.65 microns, about 1.66 microns, about 1.67 microns, about 1.68 microns, about 1.69 microns, about 1.7 microns, about 1.71 microns, about 1.72 microns, about 1.73 microns, about 1.74 microns, about 1.75 microns, about 1.76 microns, about 1.77 microns, about 1.78 microns, about 1.79 microns, about 1.8 microns, about 1.81 microns, about 1.82 microns, about 1.83 microns, about 1.84 microns, about 1.85 microns, about 1.86 microns, about 1.87 microns, about 1.88 microns, about 1.89 microns, about 1.9 microns, about 1.91 microns, about 1.92 microns, about 1.93 microns, about 1.94 microns, about 1.95 microns, about 1.96 microns, about 1.97 microns, about 1.98 microns, about 1.99 microns, about 2.0 microns, about 2.01 microns, about 2.02 microns, about 2.03 microns, about 2.04 microns, about 2.05 microns, about 2.06 microns, about 2.07 microns, about 2.08 microns, about 2.09 microns, about 2.1 microns, about 2.11 microns, about 2.12 microns, about 2.13 microns, about 2.14 microns, about 2.15 microns, about 2.16 microns, about 2.17 microns, about 2.18 microns, about 2.19 microns, about 2.2 microns, about 2.21 microns, about 2.22 microns, about 2.23 microns, about 2.24 microns, about 2.25 microns, about 2.26 microns, about 2.27 microns, about 2.28 microns, about 2.29 microns, about 2.3 microns, about 2.31 microns, about 2.32 microns, about 2.33 microns, about 2.34 microns, about 2.35 microns, about 2.36 microns, about 2.37 microns, about 2.38 microns, about 2.39 microns, about 2.4 microns, about 2.5 microns, about 2.6 microns, about 2.7 microns, about 2.8 microns, about 2.9 microns, about 3 microns, about 3.1 microns, about 3.2 microns, about 3.3 microns, about 3.4 microns, about 3.5 microns, about 3.6 microns, about 3.7 microns, about 3.8 microns, about 3.9 microns, about 4 microns, about 4.1 microns, about 4.2 microns, about 4.3 microns, about 4.4 microns, about 4.5 microns, about 4.6 microns, about 4.7 microns, about 4.8 microns, about 4.9 microns, about 5 microns, about 5.1 microns, about 5.2 microns, about 5.3 microns, about 5.4 microns, about 5.5 microns, about 5.6 microns, about 5.7 microns, about 5.8 microns, about 5.9 microns, or about 6.0 microns, or, in other embodiments, in ranges between any two of the above values. In other embodiments, an LED having output wavelengths centered in one of these ranges is used as a source of light to stimulate nerves.
In some embodiments, the implant includes a material which is both biocompatible in the eye and highly transmissive at the infrared stimulation wavelengths. In some embodiments, the implant includes optics that focus, collimate, and/or guide the stimulation light. In some embodiments, the implant is sewn, stapled, or otherwise secured at the sclera and/or sewn, stapled, or otherwise secured to those locations where the eye's natural lens is normally attached. In some embodiments, the implant is totally encapsulated within the eye, while in some other embodiments, the implant extends through the cornea and/or sclera. In some embodiments, the ocular implant uses materials and design features already used in artificial corneas and intraocular lenses, for example, such as described in U.S. Pat. No. 6,254,637 to Jin Hak Lee et al., titled “Artificial Cornea and Implantation Thereof”; U.S. Pat. No. 6,391,055 to Yoshito Ikada et al., titled “Artificial Cornea”; U.S. Pat. No. 6,976,997 to Noolandi et al., titled “Artificial Cornea”; U.S. Pat. No. 7,857,849 to David Myung et al., titled “Artificial corneal implant”; and U.S. Pat. No. 7,909,867 to David Myung et al., titled “Interpenetrating Polymer Network Hydrogel Corneal Prosthesis”; each of which is incorporated herein by reference in its entirety.
In some embodiments, once surgically implanted in the eye, the ocular implant has no internal moving parts relative to the eyeball and no internal electrical parts. Thus, such an ocular implant requires no internal or external electrical-power source. Additionally, the ocular implant does not impede movement of the eyeball after surgical implantation. In some embodiments, the freedom of eye movement relative to the external stimulator light can help provide enhanced patient comfort and enhanced perceived image resolution.
In some embodiments, the present invention provides a VCSEL array configured to output light pulses capable of optically stimulating neural tissue (e.g., cochlear nerve tissue, deep brain tissue, white brain matter tissue, gray brain matter tissue, spinal cord tissue, cardial nerve tissue, central nervous system nerve tissue, olfactory nerve tissue, optic nerve tissue, nerve bundles and the like). In some embodiments, the stimulating lights pulses have a wavelength that results in the appropriate penetration depth for effective stimulation of the tissue of interest without causing tissue damage (e.g., in some embodiments, the wavelength of stimulating light pulses is in the range of about 1.8 microns to about 2.2 microns, in some embodiments, the wavelength of stimulating light pulses is in the range of about 1.85 microns to about 2.0 microns, in some embodiments, the wavelength of stimulating light pulses is about 1.87 microns, in some other embodiments the wavelength of stimulating light pulses is in the range of about 4.0 microns to about 5.0 microns, in some other embodiments the wavelength of stimulating light pulses is in the range of about 4.2 microns to about 4.8 microns, in some other embodiments the wavelength of stimulating light pulses is in the range of about 4.4 microns to about 4.6 microns).
Although the following detailed description contains many specifics for the purpose of illustration, a person of ordinary skill in the art will appreciate that many variations and alterations to the following details are within the scope of the invention. Accordingly, the following preferred embodiments of the invention are set forth without any loss of generality to, and without imposing limitations upon the claimed invention. Further, in the following detailed description of the preferred embodiments, reference is made to the accompanying drawings that form a part hereof, and in which are shown by way of illustration specific embodiments in which the invention may be practiced. It is understood that other embodiments may be utilized and structural changes may be made without departing from the scope of the present invention.
The leading digit(s) of reference numbers appearing in the Figures generally corresponds to the Figure number in which that component is first introduced, such that the same reference number is used throughout to refer to an identical component which appears in multiple Figures. Signals and connections may be referred to by the same reference number or label, and the actual meaning will be clear from its use in the context of the description.
As used herein, an “image pipe” is an optical device that forms an image just beyond its posterior end (e.g., when an image pipe of the present invention is implanted in the eye, the image is formed on the nerves at the anterior surface of the retina) that is based on light 130 entering the anterior end. In some embodiments, an image pipe includes internal imaging components such as lenses, holographs, fiber optics or fiber-optic bundles, or the like, which assist in providing a focussed image at the retina. In other embodiments, the image pipe is simply a transparent path that allows external imaging components to form the image on the nerves at the front surface of the retina. Because some embodiments of the present invention use single-wavelength infrared lasers, holographic imagers are well suited to form images through such an image pipe.
In some embodiments, the image pipe 110 is substantially transparent to at least some infrared wavelengths of light between about 1000 nm and about 2000 nm, and in particular, is substantially transparent to those infrared wavelengths output by the source lasers of the stimulation apparatus. In some embodiments, the image pipe 110 has a substantially cylindrical shape such as shown in
Poly(methyl methacrylate) (PMMA) is a transparent thermoplastic. PMMA has been sold under many different names including Plexiglas®, Lucite® and Perspex®. PMMA is substantially transparent (i.e., a given thickness of about a centimeter or more passes a majority of incident light) to visible light (having wavelengths of 400 nm to 700 nm) and infrared light (IR) having wavelengths from about 700 nm to about 2800 nm. Colored or tinted PMMA varieties allow specific IR wavelengths to pass while blocking visible light and/or other IR wavelengths.
In some embodiments, ocular unit 100 is surgically secured in place to the cornea 99 and/or sclera 98 in the eye with anchoring collar 140 and hydrogel skirt 150. In some embodiments, the implant is sewn (or stapled or otherwise anchored) to the ciliary muscle or secured to other internal parts of the eye to hold it securely in place. Ocular unit 100 extends well into the vitreous humor 94, which is less transparent than is image pipe 110 to certain infrared light wavelengths useful for nerve stimulation.
The posterior end 114 of the image pipe 110 is closer to the fovea than the front of the eye. In some embodiments, image pipe 110 has a length such that the posterior end 114 of the image pipe 110 is near the retina 97 in the region of the macula 95 and fovea 96. In some embodiments, the image pipe 110 does not contact the retina 97, in order to leave a pathway for the vitreous humor 94 to circulate and nourish the cells of the retina. In some embodiments, the posterior end 114 is positioned close enough to the retina 97 and fovea 96 such that the remaining vitreous humor is thin enough and transparent enough that infrared light output from the posterior end of the image pipe 110 will be sufficiently intense to cause retinal-nerve stimulation (i.e., triggering of nerve action potentials in the nerves of the retina due to impinging pulses of infrared light).
In some embodiments, the ocular image pipe 110 is solid material. PMMA has a higher density than the vitreous humor. To more closely match the density of the vitreous humor, some embodiments of image pipe 110 include at least one hollow portion such that the overall density of the image pipe 110 is the same as the density of the surrounding vitreous humor and the center of mass of the image pipe 110 coincides with the center of rotation of the eye, in order that the image pipe 110 does not tend to move relative to the eye with movement. In some embodiments, the hollow portion is filled with an inert gas. In some embodiments, the hollow portion is filled with a low-pressure gas having a pressure of no more than about 1000 Torr. In some embodiments, the hollow portion is in the light path of the light path and at least one end of the hollow portion is shaped to form a lens to focus the infrared light on nerves of the retina.
The placement, size, and shape of the hollow portion in the image pipe 110 is used in some embodiments to not only match the density of the vitreous humor but to also control the center of gravity to help provide a more stable implant the is resistant to movement of the head or eyeball. In some embodiments, the light-transmitting portion of image pipe 110 is solid material and the hollow portion is formed in a peripheral portion outside and surrounding the light-transmitting path. This configuration reduces the number of optical interfaces in the light path. In some embodiments, the light-transmitting portion of image pipe 110 is solid material and the hollow portion is formed symmetrically around a peripheral portion outside and surrounding the light-transmitting path, such that regardless of whether the person's head is upright or is lying on one side, there is no rotational or other force acting to move the implant (i.e., image pipe 110) relative to the eye. In other embodiments, the hollow portion is formed in (or is very slightly larger in) a top portion of image pipe 110, in order to help keep the image pipe 110 upright and in the desired position when the patient's head is upright.
In some embodiments, one or both ends of the image pipe 110 are shaped to focus the external stimulator light signals 130 on the retina and fovea. In some embodiments, there is an external light source 180 that emits IR-wavelength stimulation light 130. For example, in some embodiments, source 180 includes a two-dimensional array of vertical-cavity surface-emitting lasers (VCSEL-array) that form an IR stimulator, which provides IR light 130 into the anterior end 112 of the ocular implant 100. In some embodiments, the user has an ocular unit 100 implanted in each eye, and the system provides there is a separate external two-dimensional array IR stimulator source 180 for each eye, wherein the two separate images help provide three-dimensional images to the brain through each eye's ocular unit 100. In some embodiments, image pipe 110 includes a lens or lens system 116, with a different index of refraction than the rest of image pipe 110, to focus the image on the retina 97. In some embodiments, the lens system 116 inverts the incoming image and focuses the image on the retina. In some other embodiments, the lens system 116 is noninverting and directs diverging, collimated, or converging light on the nerve-tissue layer of the retina 97. In some embodiments, the image pipe 110 and its lens 116, in combination with an external laser image-generation device 180 and its image processor(s) 182 and one or more cameras in camera system 181, produce an infrared image on the retina, similar to the inverted optical-wavelength image a normal human eye. Since the human brain will automatically accustom itself to any image consistently formed on the retina whether or not the image is inverted, the camera system 181, image processor 182 and stimulation light sources 180 can be configured to form the image as inverted or not according to the preferences of the user. In some embodiments, camera system 181 includes at least one camera directed toward the user's eye (e.g., to determine the locations of indicia 118 and/or 119) to determine the location and/or direction of movement of the gaze of the user, and this image of the eye (or of the indicia 118/119) is processed by image processor system 182 in order to control the position of the stimulation light sources that are generating the stimulation light signals 130, in order to position the projected pattern of stimulation light onto the desired locations on retina 122. In some embodiments, the array of light sources 180 themselves are physically moved to the desired position based on a detection of the position of the eye (e.g., a flat VCSEL array mounted on a gimbal and rotated on one or more axes by servos that are controlled by signals based on the detected eye position), while in other embodiments, different ones of the light sources 180 that are already in the desired positions relative to the eye are activated. In some embodiments, eye-position sensors (such as described in U.S. Pat. No. 4,720,189 issued to Heynen et al. on Jan. 19, 1988, titled “Eye-Position Sensor,” and U.S. Pat. No. 6,055,110 issued to Kintz et al. on Apr. 25, 2000, titled “Compact Display System Controlled by Eye Position Sensor System,” which are each incorporated herein by reference in its entirety) detect a position of the eye (e.g., the direction to which the eye is pointing and/or the distance between the eye and the stimulation-light projector 180) and provide signals to a display positioning device (such as servo-controlled gimbals) that then moves one or more components of the stimulation-light projector 180 in order to maintain a reference position of the display in a substantially constant spatial relationship to the eye, and/or adjusts a focussing element to maintain a focus of the IR-stimulation-light signals from stimulation-light projector 180 onto the desired nerve layer of the retina. In some embodiments, a power source 183 is operatively coupled to supply power to operate the camera system 181, the image processor system 182, and the stimulation light sources 180.
In other embodiments, one or more grating light valves (such as described in U.S. Pat. No. 7,177,081 titled “High Contrast Grating Light Valve Type Device,” which is incorporated herein by reference in its entirety) and/or one or more digital light projector devices (such as described in U.S. Pat. No. 4,566,935 issued to Hornbeck on Jan. 28, 1986, titled “Spatial Light Modulator and Method,” or U.S. Pat. No. 7,776,631 titled “MEMS Device and Method of Forming a MEMS Device,” which are each incorporated herein by reference in its entirety) are used to modulate and/or direct light (e.g., from one or more lasers, LEDs or other suitable light-source devices) to desired locations.
In some embodiments, the ocular unit 100 has at least one indicia mark to facilitate detection of the eye's position. In some embodiments, the ocular unit has at least one indicia mark 118 on the anterior end to facilitate external detection of the position of the eye and the pointing directions. In some embodiments, the ocular unit 100 has at least one indicia mark 119 on the posterior end to facilitate external detection of the position of the eye and the pointing directions. In some embodiments, one or more indicia marks are placed on both the anterior end posterior end, and/or on one or more other locations on the ocular unit 100. In some embodiments the location and/or orientation of the implant is determined, for example, by obtaining an image of, or detecting reflected or fluorescent light from, the indicia mark or marks 118 and/or 119 and the external stimulator array signals are adjusted to compensate for the position of the eye (e.g., the image or pattern is moved such that the desired nerve tissue continues to be stimulated). In some such embodiments, an eye-position processor in the external image processor 182 uses an “inward-pointing” camera in camera system 181 (i.e., a camera pointed toward the user to obtain an image of the eye and/or indicia 118/119) to detect movement or position of the user's eye(s), and generates control signals that direct an external camera view (i.e., the direction in which the camera system 181 is pointing, or if a very-wide-angle lens and/or multiple cameras are used, which of the images obtained by camera system 181 is used), providing a more realistic sensation of “looking around” to the user, instead of requiring movement of the user's entire head to obtain different images. In some embodiments, a plurality of “outward-pointing” cameras is included in camera system 181 (i.e., a plurality of cameras pointed toward different directions in the environment surrounding user to obtain a plurality of images from which to select based on the detected direction of the user's gaze).
In some embodiments of ocular unit 100 of
Note that in some embodiments, it is the entire system including exterior optics in the stimulation light source 180, along with the lens system 116 and body 110 of ocular unit 100 that act together to focus the image onto the desired nerve-tissue layer of the retina 97.
In some embodiments, the ocular unit 201 includes an image pipe 210 for transmitting a stimulation pattern of infrared light from an external stimulator array through the eye, the ocular unit 201 having a light-receiving anterior end 212 closest to the eye's anterior surface (behind the cornea) and extending to a posterior end 214 that is closer to the fovea than to the eye's anterior surface.
In some embodiments, the image pipe 210 is substantially transparent to at least some infrared wavelengths of light between about 1000 nm and about 2000 nm. In some embodiments, the image pipe 210 is substantially cylindrical-shaped such as shown in
The posterior end 214 of the image pipe 210 is closer to the fovea than the front of the eye. In some embodiments, image pipe 210 has a length such that the posterior end 214 of the image pipe 210 is near the retina 97 in the region of the fovea 96. In some embodiments, the image pipe 210 does not contact the retina, in order to leave a pathway for the vitreous humor of the eye to circulate and nourish the cells of the retina. In some embodiments, the posterior end 214 is positioned close enough to the retina 97 and fovea 96 such that the remaining vitreous humor 94 is thin enough and transparent enough that infrared light output from the posterior end of the image pipe 210 will be sufficiently intense to cause retinal-nerve stimulation (i.e., triggering of nerve action potentials in the nerves of the retina due to impinging pulses of infrared light).
In some embodiments, the ocular image pipe 210 is solid material. PMMA has a higher density than the vitreous humor. To more closely match the density of the vitreous humor, some embodiments of image pipe 210 include at least one hollow portion such that the overall density of the image pipe 210 is the same as the density of the surrounding vitreous humor and the center of mass of the image pipe coincides with the center of rotation of the eye, in order that the image pipe 210 does not tend to move relative to the eye with movement. In some embodiments, the hollow portion is filled with an inert gas. In some embodiments, the hollow portion is filled with a low-pressure gas having a pressure of no more than about 1000 Torr. In some embodiments, the hollow portion is in the light path of the light path and at least one end of the hollow portion is shaped to form a lens to focus the infrared light on nerves of the retina.
The placement, size, and shape of the hollow portion in the image pipe 210 is used in some embodiments to not only match the density of the vitreous humor but to also control the center of gravity to help provide a more stable implant the is resistant to movement of the head or eyeball. In some embodiments, the light-transmitting portion of image pipe 210 is solid material and the hollow portion is formed in a peripheral portion outside and surrounding the light-transmitting path. This configuration reduces the number of optical interfaces in the light path. In some embodiments, the light-transmitting portion of image pipe 210 is solid material and the hollow portion is formed symmetrically around a peripheral portion outside and surrounding the light-transmitting path, such that regardless of whether the person's head is upright or is lying on one side, there is no rotational or other force acting to move the implant (i.e., image pipe 210) relative to the eye. In other embodiments, the hollow portion is formed in (or is very slightly larger in) a top portion of image pipe 210, in order to help keep the image pipe 210 upright and in the desired position when the patient's head is upright.
In some embodiments, one or both ends of the image pipe 210 are shaped to focus the externally generated stimulator-array signals on the retina and fovea. In some embodiments, the present invention includes an external two-dimensional array VCSEL-array IR stimulator providing IR light 130 into the anterior end of the ocular implant 201.
In other embodiments of any of the embodiments of the present invention including the system described in
In some embodiments, there is an external two-dimensional array IR stimulator for each eye to help provide three-dimensional images to the user with an ocular unit 201 implanted in each eye. In some embodiments, image pipe 210 includes a lens 216, with a different index of refraction than the rest of image pipe 210, to focus the image on the retina 97. In some embodiments, the lens 216 is a convex lens that has a higher index of refraction than the surrounding tissue and/or the body 210 of ocular unit 201 (or is a concave lens that has a lower index of refraction) and lens 216 (along with any external lens(es) and the cornea 99) inverts the incoming image and focuses the image on the retina. Note that in some embodiments, it is the entire system including exterior optics in the light source 180 and the cornea of the eye, along with the lens system 216 that act together to focus the image onto the desired nerve tissue. In some other embodiments, on the lens is noninverting and directs collimated light on the retina. In some embodiments, the image pipe 210, lens 216, in combination with an external laser-signal generation device produce an inverted nerve-stimulation pattern on the retina, similar to the inverted image a normal human eye.
In some embodiments, the ocular unit 201 has at least one indicia mark 218, 219, and/or 220 to facilitate detection of the eye's position. In some embodiments, the ocular unit has at least one anterior indicia mark 118, posterior indicia mark 119, or both to facilitate external detection of the position of the eye and the pointing direction of the gaze used for controlling the camera system 181 (e.g., moving the position/direction of the camera 181, or shifting the portion of the image obtained from the camera 181 and used to generation the stimulation signals 130). In some embodiments, indicia marks are placed on one or more other locations on the ocular unit 100. In some embodiments, reflected light from the indicia mark or marks is detected and the external stimulator array signals are adjusted to compensate for the position of the eye.
In other embodiments (not shown), an aperture that is not part of such bubble features is provided in any of the embodiments described herein, where the aperture surrounds the expected focal point of the image light, to serve as a spatial filter, blocking light that is not part of the focussed stimulation-light image.
In some embodiments, the body 242 of the intraocular implant is shaped substantially like a cylinder. In other embodiments (not shown, but in a manner similar to
In some embodiments, one or both ends of the image pipe 310 are shaped to focus the externally generated stimulator-array signals on the retina and fovea. In some embodiments, there is an external two-dimensional array VCSEL-array IR stimulator providing IR light 130 into the anterior end of the ocular implant 300. In some embodiments, there is an external two-dimensional array IR stimulator for each eye to help provide three-dimensional images to the user with an ocular unit 300 implanted in each eye. In some embodiments, image pipe 310 includes a lens (see, for example, lens 216 of
In some embodiments, ocular unit 300 has the optional features of ocular unit 100 and intra-ocular unit 201, with the difference being the conical-shaped image pipe 310. In some embodiments, ocular unit 201 includes a conical-shaped image pipe instead of the cylindrically shaped image pipe 210 shown in
To more closely match the density of the vitreous humor, some embodiments of image pipe 410 include at least one hollow portion 422 such that the overall density of the image pipe 410 is the same as the density of the surrounding vitreous humor and the center of mass of the image pipe 410 coincides with the center of rotation of the eye, in order that the image pipe 410 does not tend to move relative to the eye with movement. In some embodiments, the hollow portion 422 is filled with an inert gas. In some embodiments, the hollow portion is filled with a low-pressure gas having a pressure of no more than about 1000 Torr.
The placement, size, and shape of the hollow portion in the image pipe 410 is used in some embodiments to not only match the density of the vitreous humor but to also control the center of gravity to help provide a more stable implant the is resistant to movement of the head or eyeball. In some embodiments, the light-transmitting portion of image pipe 410 is solid material and the hollow portion is formed in a peripheral portion outside and surrounding the light-transmitting path. This configuration reduces the number of optical interfaces in the light path. In some embodiments, the light-transmitting portion of image pipe 410 is solid material and the hollow portion 422 is formed symmetrically around a peripheral portion outside and surrounding the light-transmitting path, such that regardless of whether the person's head is upright or is lying on one side, there is no rotational or other force acting to move the implant (i.e., image pipe 410) relative to the eye. In other embodiments, the hollow portion is formed in (or is very slightly larger in) a top portion of image pipe 410, in order to help keep the image pipe 410 upright and in the desired position when the patient's head is upright.
In some embodiments, image pipe 410 includes a lens 416, with a different index of refraction than the rest of image pipe 410, to focus the image on the retina 97. In some embodiments (as shown by lens 216 in
In some embodiments, ocular unit 400 is fully contained intraocularly (i.e., completely inside the eye similar to ocular unit 201 of
To more closely match the density of the vitreous humor, some embodiments of image pipe 510 include at least one hollow portion 522A such that the overall density of the image pipe 510 is the same as the density of the surrounding vitreous humor and the center of mass of the image pipe 510 coincides with the center of rotation of the eye, in order that the image pipe 510 does not tend to move relative to the eye with movement. In some embodiments, the hollow portion 522A is filled with an inert gas. In some embodiments, the hollow portion 522A is filled with a low-pressure gas having a pressure of no more than about 1000 Torr.
The placement, size, and shape of the hollow portion 522A in the image pipe 510 is used in some embodiments to not only match the density of the vitreous humor but to also control the center of gravity (e.g., to balance relative to the mass of lens 516) to help provide a more stable implant the is resistant to movement of the head or eyeball. In some embodiments, the light-transmitting portion of image pipe 510 is solid material and the hollow portion is formed in a central portion of the light-transmitting path. In other embodiments, the hollow portion is formed in (or is very slightly larger in) a top portion of image pipe 110, in order to help keep the image pipe 510 upright and in the desired position when the patient's head is upright.
In some embodiments, image pipe 510 includes a lens 516, with a different index of refraction than the rest of image pipe 510, to focus the image on the retina 97. In some embodiments, the lens inverts the incoming image and focuses the image on the retina. In some other embodiments, on the lens is noninverting and directs collimated light on the retina. In some embodiments, the image pipe 510, lens 516, in combination with an external laser-signal generation device 180 produce an inverted nerve-stimulation pattern on the retina, similar to the inverted image a normal human eye.
In some embodiments, ocular unit 501 is fully contained intraocularly (i.e., completely inside the eye similar to ocular unit 201) after being surgically implanted. In some such embodiments, the image pipe 510 is surgically secured in place in the eye with the implant sewn, stapled, or otherwise secured to the ciliary muscle or secured to other internal parts of the eye to hold it securely in place. In some such embodiments, the ocular unit 501 is completely contained within the eye and the user's cornea 99 is maintained intact.
To more closely match the density of the vitreous humor, some embodiments of image pipe 610 include at least one hollow portion 622 such that the overall density of the image pipe 610 is the same as the density of the surrounding vitreous humor and the center of mass of the image pipe 610 coincides with the center of rotation of the eye, in order that the image pipe 610 does not tend to move relative to the eye with movement. In some embodiments, the hollow portion 622 is filled with an inert gas. In some embodiments, the hollow portion is filled with a low-pressure gas having a pressure of no more than about 1000 Torr.
The placement, size, and shape of the hollow portion in the image pipe 610 is used in some embodiments to not only match the density of the vitreous humor but to also control the center of gravity to help provide a more stable implant the is resistant to movement of the head or eyeball. In some embodiments, the light-transmitting portion of image pipe 610 is solid material and the hollow portion is formed in a peripheral portion outside and surrounding the light-transmitting path. This configuration reduces the number of optical interfaces in the light path. In some embodiments, the light-transmitting portion of image pipe 610 is solid material and the hollow portion 422 is formed symmetrically around a peripheral portion outside and surrounding the light-transmitting path, such that regardless of whether the person's head is upright or is lying on one side, there is no rotational or other force acting to move the implant (i.e., image pipe 610) relative to the eye. In other embodiments, the hollow portion is formed in (or is very slightly larger in) a top portion of image pipe 610, in order to help keep the image pipe 610 upright and in the desired position when the patient's head is upright.
In some embodiments, image pipe 610 includes a lens (see, for example, lens 216 of
In some embodiments, ocular unit 600 is fully contained intraocularly (i.e., completely inside the eye similar to ocular unit 600) after being surgically implanted. In some such embodiments, the image pipe 610 is surgically secured in place in the eye with the implant sewn, stapled, or otherwise secured to the ciliary muscle or secured to other internal parts of the eye to hold it securely in place. In some such embodiments, the ocular unit 600 is completely contained within the eye and the user's cornea 99 is maintained intact.
In some embodiments, the external stimulation IR source outputs IR light signals that represent a pre-processed version of an image scene, wherein the preprocessing mimics or replicates the internal optical processing of images normally performed by the millions of interconnections between the various cell layers of the retina. In some embodiments, the preprocessing needed is empirically determined by focussing various patterns on different ones of the cells in the various bipolar, amacrine and/or ganglion layers and having the subjects report the sensation perceived, and/or by actually measuring NAPs in the tissue of eyes of lab subjects. By triggering NAPs in the various nerve-cell layers 82, 83, and/or 85, certain degeneration effects, defects or diseases that cause loss of vision can be bypassed by triggering NAPs in the anterior layers of cells of the retina.
In other embodiments, the IR stimulation light is used to trigger NAPs in the rods or cones, and those NAPs are then combined in the normal way of processing by the various bipolar, amacrine and/or ganglion layers.
Neurons that make up the retina of an eye can be directly stimulated by light such that NAPs or CNAPs are triggered. The NAP or CNAP response of the neurons depends on the energy (power times pulse duration) absorbed per unit area and wavelength (absorption by various tissues varies as a function of wavelength) of the light pulses impinging on and thereby directly stimulating the neurons. Neurons are sensitive to wavelengths of light in the range of about 1800 nm to about 1900 nm.
In some embodiments, the light-receiving surface portion of the anterior end 212 of the ocular unit (according to any of the above-described embodiments of the present invention) is shaped so as to have a substantially constant spacing from (i.e., to substantially conform to) the inner surface of the cornea of the eye.
In some embodiments, this light-receiving surface portion of the anterior end of the ocular unit is located at a substantially constant spacing of no more than 2.5 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located at a substantially constant spacing of no more than 2.0 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located at a substantially constant spacing of no more than 1.5 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located at a substantially constant spacing of no more than 1.0 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located at a substantially constant spacing of no more than 0.5 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located no more than 0.2 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located at a substantially constant spacing of about 0.5 mm from the inner surface of the cornea of the eye. In some embodiments, this light-receiving anterior surface portion is located at a substantially constant spacing of about 0.2 mm from the inner surface of the cornea of the eye.
In some embodiments, the light-output surface portion of posterior end 214 of the ocular unit (according to any of the above-described embodiments of the present invention) is shaped so as to have a substantially constant spacing from (i.e., to substantially conform to) the ganglion layer of the retina of the eye.
In some embodiments, the light-output surface portion of posterior end of the ocular unit is located at a substantially constant spacing of no more than 2.5 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of no more than 2.0 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of no more than 1.5 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of no more than 1.0 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of no more than 0.5 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of no more than 0.2 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of about 0.5 mm from the ganglion layer of the retina of the eye. In some embodiments, this light-output surface portion is located at a substantially constant spacing of about 0.2 mm from the ganglion layer of the retina of the eye.
In some embodiments, the present invention provides an apparatus to aid in the treatment of a vision problem of an eye of a person, wherein the eye has an anteroposterior axis extending from the eye's anterior surface to the eye's fovea. The apparatus includes an ocular unit having an optical path 199 that is substantially transparent (i.e., transmitting at least 50% of incident light) to at least some infrared wavelengths of light between about 1000 nm and about 2000 nm, wherein the ocular unit has a light-receiving anterior end closest to the eye's anterior surface and extends to a posterior end, wherein the posterior end is closer to the fovea than to the eye's anterior surface, and wherein the ocular unit has an a secure-placement feature that is configured to be secured to an anatomical feature of the eye.
In some embodiments, the ocular unit extends across, and replaces, more than 90% of the optical path of the eye of the person, in order to provide an infrared-transparent optical path that is far more transparent to the wavelengths of the nerve-stimulation wavelengths of the optical stimulation signal light 130 than would have been the normal components of the eye.
In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared signal light that is incident on the anterior end and that has wavelengths in a range between about 1800 and about 2000 nm. In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared light that is incident on the anterior end and that has wavelengths in a range between about 1000 and about 1200 nm. In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared light that is incident on the anterior end and that has wavelengths in a range between about 1200 and about 1400 nm. In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared light that is incident on the anterior end and that has wavelengths in a range between about 1400 and about 1600 nm. In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared light that is incident on the anterior end and that has wavelengths in a range between about 1600 and about 1800 nm. In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared light that is incident on the anterior end and that has wavelengths in a range between about 2000 and about 2500 nm. In some embodiments, the ocular unit transmits out the posterior end more than 30% of infrared light that is incident on the anterior end and that has wavelengths in a range between about 2500 and about 3000 nm. In some embodiments, the ocular unit transmits out the posterior end more than 50% of infrared light that is incident on the anterior end and that has wavelengths in one or more of the above-listed ranges.
In some embodiments, the ocular unit transmits out the posterior end more than 60% of infrared light that is incident on the anterior end and that has wavelengths in one or more of the wavelength ranges of between about 1000 to about 1200 nm, between about 1200 and about 1400 nm, between about 1400 and about 1600 nm, between about 1600 and about 1800 nm, between about 1800 and about 2000 nm, between about 2000 and about 2500 nm, and between about 2500 and about 3000 nm. In some embodiments, the ocular unit transmits out the posterior end more than 70% of infrared light that is incident on the anterior end and that has wavelengths in one or more of the wavelength ranges of between about 1000 to about 1200 nm, between about 1200 and about 1400 nm, between about 1400 and about 1600 nm, between about 1600 and about 1800 nm, between about 1800 and about 2000 nm, between about 2000 and about 2500 nm, and between about 2500 and about 3000 nm. In some embodiments, the ocular unit transmits out the posterior end more than 80% of infrared light that is incident on the anterior end and that has wavelengths in one or more of the wavelength ranges of between about 1000 to about 1200 nm, between about 1200 and about 1400 nm, between about 1400 and about 1600 nm, between about 1600 and about 1800 nm, between about 1800 and about 2000 nm, between about 2000 and about 2500 nm, and between about 2500 and about 3000 nm. In some embodiments, the ocular unit transmits out the posterior end more than 90% of infrared light that is incident on the anterior end and that has wavelengths in one or more of the wavelength ranges of between about 1000 to about 1200 nm, between about 1200 and about 1400 nm, between about 1400 and about 1600 nm, between about 1600 and about 1800 nm, between about 1800 and about 2000 nm, between about 2000 and about 2500 nm, and between about 2500 and about 3000 nm. In some embodiments, the ocular unit transmits out the posterior end more than half of infrared light that is incident on the anterior end and that has wavelengths in two or more of the wavelength ranges of between about 1000 to about 1200 nm, between about 1200 and about 1400 nm, between about 1400 and about 1600 nm, between about 1600 and about 1800 nm, between about 1800 and about 2000 nm, between about 2000 and about 2500 nm, and between about 2500 and about 3000 nm.
In some embodiments of the apparatus, the ocular unit includes a thermoplastic material. In some embodiments of the apparatus, the ocular unit includes a biocompatible material. In some embodiments of the apparatus, the ocular unit includes a thermoplastic and biocompatible material. In some embodiments, this material transmits to the posterior end more than half of infrared light having wavelengths between about 1800 and about 2000 nm that is incident on the anterior end. In some embodiments, the material is substantially transparent to other wavelengths in addition to wavelengths between about 1800 and about 2000 nm.
In some embodiments of the apparatus, the biocompatible material includes poly(methyl methacrylate) (PMMA).
In some embodiments of the apparatus, the ocular unit includes a substantially cylindrical-shaped material from the anterior end to the posterior end, and wherein the posterior end of the material has a diameter substantially equal to a diameter of the anterior end of the material.
In some embodiments of the apparatus, the ocular unit includes a substantially conical-shaped material from the anterior end to the posterior end, wherein the posterior end of the material has a diameter that is larger than a diameter of the anterior end of the material.
In some embodiments of the apparatus, the anterior end of the ocular unit is shaped to form a lens to focus the infrared light on nerves of the retina.
In some embodiments of the apparatus, at least part of the ocular unit includes a hollow portion filled with a gas. In some embodiments, the gas is an inert gas having a pressure of less than or equal to about 1000 Torr. In some embodiments, the gas pressure is less than or equal to about 760 Torr. In some embodiments, the gas is under a vacuum of less than about 500 Torr. In some embodiments, at least one end of the hollow portion is shaped to form a lens to focus the infrared light on nerves of the retina.
In some embodiments of the apparatus, the anterior end of the ocular unit extends to through the anterior of the eye replacing at least part of the eye's cornea, and wherein the ocular unit is securely sealed to the sclera.
In some embodiments of the apparatus, the anterior end of the ocular unit is posterior to the eye's cornea and the ocular unit is secured internal to the eye.
In some embodiments of the apparatus, the ocular unit has at least one indicia mark to facilitate detection of the eye's position.
It is to be understood that the above description is intended to be illustrative, and not restrictive. Although numerous characteristics and advantages of various embodiments as described herein have been set forth in the foregoing description, together with details of the structure and function of various embodiments, many other embodiments and changes to details will be apparent to those of skill in the art upon reviewing the above description. The scope of the invention should, therefore, be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled. In the appended claims, the terms “including” and “in which” are used as the plain-English equivalents of the respective terms “comprising” and “wherein,” respectively. Moreover, the terms “first,” “second,” and “third,” etc., are used merely as labels, and are not intended to impose numerical requirements on their objects.
This application claims priority benefit under 35 U.S.C. §119(e) of U.S. Provisional Patent Application No. 61/514,894 filed Aug. 3, 2011, titled “Sight-Restoring Visual Prosthetic and Method Using Infrared Nerve-Stimulation Light”, which is incorporated herein by reference in its entirety. This invention is related to the following prior applications and patents: U.S. Provisional Patent Application No. 60/715,884 filed Sep. 9, 2005, titled “Apparatus and Method for Optical Stimulation of Nerves”; U.S. patent application Ser. No. 11/257,793 filed Oct. 24, 2005, titled “Apparatus for Optical Stimulation of Nerves and Other Animal Tissue” (now U.S. Pat. No. 7,736,382 issued Jun. 15, 2010); U.S. Provisional Patent Application No. 60/826,538 filed Sep. 21, 2006, titled “Miniature Apparatus and Method for Optical Stimulation of Nerves and Other Animal Tissue”; U.S. patent application Ser. No. 11/536,639 filed Sep. 28, 2006, titled “Miniature Apparatus and Method for Optical Stimulation of Nerves and Other Animal Tissue” (now U.S. Pat. No. 7,988,688 issued Aug. 2, 2011); U.S. patent application Ser. No. 11/536,642 filed Sep. 28, 2006, titled “Apparatus and Method for Stimulation of Nerves and Automated Control of Surgical Instruments”; U.S. Provisional Patent Application No. 60/884,619 filed Jan. 11, 2007, titled “Vestibular Implant Using Infrared Nerve Stimulation”; U.S. patent application Ser. No. 11/971,874 filed Jan. 9, 2008, titled “Method and Vestibular Implant using Optical Stimulation of Nerves” (now U.S. Pat. No. 8,012,189 issued Sep. 6, 2011); U.S. Provisional Patent Application No. 60/964,634 filed Aug. 13, 2007, titled “VCSEL Array Stimulator Apparatus and Method for Light Stimulation of Bodily Tissues”; U.S. patent application Ser. No. 12/191,301 filed Aug. 13, 2008, titled “VCSEL Array Stimulator Apparatus and Method for Light Stimulation of Bodily Tissues” (now U.S. Pat. No. 8,475,506 issued Jul. 2, 2013); U.S. Provisional Patent Application No. 61/015,665 filed Dec. 20, 2007, titled “Laser Stimulation of the Auditory System at 1.94 μm and Microsecond Pulse Durations”; U.S. Provisional Patent Application No. 61/147,073 filed Jan. 23, 2009, titled “Optical Stimulation Using Infrared Lasers (or In Combination with Electrical Stimulation) of the Auditory Brainstem and/or Midbrain”; U.S. patent application Ser. No. 12/693,427 filed Jan. 25, 2010, titled “Optical Stimulation of the Brainstem and/or Midbrain, including Auditory Areas”; U.S. Provisional Patent Application No. 61/349,813 filed May 28, 2010, by Jonathon D. Wells et al., titled “Laser-Based Nerve Stimulators for, e.g., Hearing Restoration in Cochlear Prostheses”; U.S. Provisional Patent Application No. 61/381,933 filed Sep. 10, 2010, by Jonathon D. Wells et al., titled “Laser-Based Nerve Stimulators for, e.g., Hearing Restoration in Cochlear Prostheses and Method”; U.S. patent application Ser. No. 12/890,602 filed Sep. 24, 2010, by Jonathon D. Wells et al., titled “Laser-Based Nerve Stimulators for, e.g., Hearing Restoration in Cochlear Prostheses and Method”; U.S. Provisional Patent Application No. 61/349,810 filed May 28, 2010, by Jonathon D. Wells et al., titled “Implantable Infrared Nerve Stimulation Devices for Peripheral and Cranial Nerve Interfaces”; U.S. Provisional Patent Application No. 61/386,461 filed Sep. 24, 2010, by Jonathon D. Wells et al., titled “Implantable Infrared Nerve Stimulation Devices for Peripheral and Cranial Nerve Interfaces”; U.S. patent application Ser. No. 13/117,121 filed May 26, 2011, by Jonathon D. Wells et al., titled “Implantable Infrared Nerve Stimulation Devices for Peripheral and Cranial Nerve Interfaces”; U.S. patent application Ser. No. 13/117,122 filed May 26, 2011, by Jonathon D. Wells et al., titled “Cuff Apparatus and Method for Optical and/or Electrical Nerve Stimulation of Peripheral Nerves” (now U.S. Pat. No. 8,652,187 issued Feb. 18, 2014); Nerves”; U.S. patent application Ser. No. 13/117,125 filed May 26, 2011, by Jonathon D. Wells et al., titled “Nerve-Penetrating Apparatus and Method for Optical and/or Electrical Nerve Stimulation of Peripheral Nerves”; U.S. patent application Ser. No. 13/117,118 filed May 26, 2011, by Jonathon D. Wells et al., titled “Optical Bundle Apparatus and Method for Optical and/or Electrical Nerve Stimulation of Peripheral Nerves”; each of which is incorporated herein by reference in its entirety.
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