The present invention relates to a device for implantation in a human eye with an electrode array or micro-contact structure for contacting nerve tissue in the visual system of the human eye.
A common cause of partial or complete loss of vision is the destruction of the photoreceptor layer in the retina of the human eye, whereby incident photons are not converted into appropriate stimulation of the ganglion cells. In this disease, the ganglion cells are only partially affected, so that external stimulation of the ganglion cells still present in the retina can produce visual perception.
Devices in the form of retinal implants have already been developed for the treatment of patients whose vision is partially or totally lost due to defects in the retina. A microelectronic device with a variety of light-sensitive pixels is implanted in the retina area to capture an image projected onto the retina by the still intact lens of the eye. Other vision devices are imaged by an external camera, in particular a video retina camera. The image captured by the pixels or camera is converted into electrical signals and re-stimulated via electrodes to the ganglia or the blind eye by means of electrical stimulation pulses to improve or reverse the patient's vision.
The epiretinal transmission of the stimulation impulses to the retinal cells and to the optic nerve cells is carried out by means of micro-contact structures, which are essentially made of a carrier material with unilaterally electrically conductive, pen- or needle-shaped contact elements protruding over the carrier film and evenly distributed over the surface of the implant with a constant surface area. However, the known vision prostheses have the disadvantage of requiring a high space.
Another problem with known prostheses is that the implants and their micro-contact structure or the surface of the electrodes need to be supplied with energy. According to current knowledge, an average power of about 40 mW is required to supply a retinal implant.
Active retinal implants therefore require an energy supply unit independent of the system for generating the visual impression, located outside the eye and working without wires to the retinal implant. DE 19705988 C2 is known as a subretinal implant, where the implant is equipped with a photovoltaic layer effective for invisible light. The energy supply is made by infrared light. The retinal implant is equipped with a surface adjacent to a retina, where the surface is equipped with electrodes to stimulate retinal cells.
The present invention is therefore intended to provide a visual prosthesis in the form of a retinal implant which is characterized by the least possible space requirement in the eye.
This problem is solved by a method according to the present invention with the features of claim 1. Beneficial extensions of the invention are given in the subclaims. The present invention solves the above problem by a prosthesis with a stimulation system for implantation in a human eye with an electrode array for contacting and stimulating living tissue or nerves in the visual system of the eye, which generates stimulation impulses by means of an electric circuit, the stimulation system comprising at least one intraocular implant and at least one extraocular implant providing energy to the intraocular implant.
The present invention provides a neurostimulation device for stimulating still existing ganglion nerve cells which can improve vision in degenerative retinal diseases but still intact optic nerves. By dividing the implant into an epirectal part and an extraocular part, a large number of the required components and the largest volume of the implant can be moved to the outer, extraocular part of the implant. The implant of the invention can minimise potential injury to the retina or other more sensitive structures of the eye in the arrangement of the stimulation system.
The visual prosthesis according to the invention thus has the advantage that almost all electronic components which do not necessarily have to be placed inside the eye with the intraocular implant can be placed outside the eyeball, for example on the so-called sclera or the epidermis. This reduces the space required for the stimulation system inside the eye and minimises the surgical intervention in implanting the stimulation system inside the eye. Another advantage of the visual prosthesis according to the invention is that the electrical supply of the intraocular implant can be provided via the extraocular implant, which increases the mobility of the eyeball without further obstruction.
The extraocular part of the implant is placed at the outer circumference of the eye on the sclera, so that the movement of the eyeball is as little affected as possible. It is particularly advantageous if the extraocular part of the implant is placed between two muscles that are used to move the eye, in which the fat tissue around the eye is placed. The extraocular implant can be sewn from the outside to the skin of the eye, thus allowing the eye to move within the eye socket without hindrance and pain.
The individual parts of the implant inside and outside the eye are preferably interconnected by means of a wire connection (with or without a plug). In the implanted state of the implant of the invention, this wire connection is preferably carried through the eye in the area of the parsplana, near the retina, where no retina is present. Both the transmission of energy or power supply and image data between the extraocular implant outside the eye and the further electronics can be carried out wirelessly by inductive means. The wireless transmission of energy and image data from the electronics far from the eye to the implant avoids disruptions and thus obstructions or obstructions.
The other electronics of the prosthesis, which are needed to process and process the image data captured by an external camera, can be placed away from the eye and outside the body. The electronic components can be housed in a so-called pocket computer, which can be carried in a separate pocket on the body.
Since the electronic components required to process the images of the signals supplied by the video camera are located outside the body, they can be easily maintained or replaced by a more modern version of the electronic interface. The electronic interface components can be individually adjusted to the respective electronic stimulation level of the implant system. This ensures a minimum level of electrical charge for all electrodes in the electrode array to minimize the strain on tissues or nerve cells affected by the electrical stimulation pulses. These electrodes are used to avoid damage to the retina of the patient caused by an excessive level of stimulation and to avoid pain sensations near the eye.
The stimulation system of the invention is essentially an image taken with an external camera, the image signals of which are then fed to the retina of the eye via the extraocular implant and the epiretinal implant after electronic pre-processing. The epiretinal implant comprises an integrated electrode array which, according to the image data received, locally stimulates the ganglion cells or retinal cells by electrical signals, thereby transmitting the image captured by the external camera to the nerves of the visual system. A particular advantage of the active epiretinal implant is that it can adapt to different conditions of ambient light density.
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The extraocular implant shall be equipped with an electric control unit, preferably trained as a digital control unit with analogue additional functions, which generates stimulation pulses from the image data captured by an external camera. To this end, the electric control unit shall comprise at least one current/voltage source and at least one pulse generator, which generates electrical stimulation pulses, which are amplified from the current/voltage source into stimulation pulses and/or stimulation currents and transmitted to the stimulation electrodes in the electrode array in the intraocular implant. In addition, the electric control unit may be equipped with electronic chip recorders in which the calculated photoelectrical output can be stored in a microelectrode and at least one of the extraoculars is integrated into the electrical circuitry, as opposed to the electrode, which can be used for the photoelectrical stimulation of the implant.
The electrical control unit has a contact pad for each stimulation electrode, i.e. a connecting surface, through which each stimulation electrode can be contacted by means of a separate wire connection. The wire connection is designed as a flexible implant and is placed between the extraocular implant and the intraocular implant preferably in the peripheral region of the eye, where there is no retina, so as to avoid retinal deterioration.
The conduction of the wire link between the epiretinal implant and the extraocular implant through the sclera of the eye in the area of the parsplana is a minimally invasive procedure and the least possible injury to the eye, which also reduces the risk of complications and infection during surgery. By attaching the flexible wire link implant together with the inner and outer part of the implant to the eye, they perform the same eye movements, which does not affect the freedom of movement of the eye by the wire link or the inner and outer part of the implant.
The wire connection for the coupling of the extraocular implant to the intraocular implant shall include at least one line for the transmission of the operating current and at least one signal line for the transmission of image data and/or electrical stimulation pulses from the digital control unit to the intraocular implant. According to a preferred embodiment of the present invention, the wire connection shall include, in addition to the electrical conduits for the transmission of the operating current, at least as many lines for the transmission of electrical stimulation pulses as are provided for by the stimulation electrodes in the intraocular implant. Furthermore, the wire connection may include one or more light conductors for the transmission of one- or two-way data by means of light signals between the intraocular part and the extraocular part of the implant.
To ensure the reliable fixation of the flexible implant with the electrode array or micro-contact structure and the wire connection between the micro-contact structure and the extraocular implant, the intraocular implant and/or the flexible implant of the wire connection can be fixed to the inside of the eye by means of a nail, called a tack, which is inserted surgically from the inside of the eye and passes through the flexible implant and the retina into the vein or the eyelid, where it anchors itself with its hooks.
The intraocular implant consists of a number of light-sensitive elements that, depending on the light incident on the intraocular implant, direct the electrode array contact points via the electrical circuit. At least one light receiver of the intraocular implant is capable of receiving light signals from a light transmitter outside the eye. According to a preferred embodiment, the light receiver of the intraocular implant is trained as an infrared receiver, which receives infrared signals from an infrared transmitter outside the eye, preferably via the eye's natural light pathway.
In this way, the interface between the light transmitter outside the eye and the light sensitive elements or the light receiver of the intraocular implant can transmit image data recorded by an external camera via light signals from the light transmitter outside the eye to the light sensitive elements or the light receiver of the intraocular implant.
The extraocular implant performs signal processing of the received image data, including signal amplification, which requires an external power coupling. This power coupling is performed wirelessly in the vision prosthesis of the invention by means of the inductive interface between an external high-frequency transmitting coil and the high-frequency receiving coil of the extraocular implant. For this purpose, according to another embodiment of the vision prosthesis of the invention, a stimulation system-based antenna is provided for an inductive interface that can transmit electromagnetic signals preferably in the high-frequency range. Furthermore, the extraocular implant is equipped with an electromagnetic signal that can be received preferably in the remote-implantation.
The high-frequency antenna of the extraocular implant receives the electromagnetic high-frequency signals emitted from the transmitting antenna of the electronics outside the body, which generates an inductive current that supplies the implant in the eye with sufficient energy. The current generated by the induction is transmitted from the outside of the implant via the wire line to the inside of the implant to supply the electrode array and the infrared receiver with electricity.
In addition, the inductive interface between the antenna outside the eye and the antenna of the extraocular implant may also be bi-directionally trained, the antenna removed from the stimulation system being able to receive electromagnetic signals preferably in the high frequency range and the antenna of the extraocular implant being able to transmit electromagnetic signals preferably in the high frequency range. In this preferred embodiment, the extraocular implant is trained to transmit information, e.g. on operating parameters of the stimulation system, via the inductive interface. According to another particular embodiment of the invention, the rate of data transmission from the initial data of the extraocular implant is different from the rate of data transmission from the extraocular implant.
In a bidirectional inductive interface, therefore, both the outer part of the implant in the eye and the electronics outside the body are equipped with a transmitting and receiving unit, each capable of transmitting and receiving electrical signals preferably in the high frequency range, which also allows signals generated by the epiretinal implant inside the eye to be transmitted via the wire to the outer part of the implant and from there transmitted via the transmitting unit in the form of high frequency signals to the electronics outside the body.
The electronics outside the body receive the high frequency signals from the extraocular implant transmitter via its receiver unit and route them to a central computer unit where the signals are evaluated, allowing the epiretinal implant inside the eye to transmit signals, such as the adequate power supply of the internal implant, the quality of the received image signals, the function of the stimulation electrodes in the electrode array, the efficiency of the inductive interface or the contact of the stimulation electrodes with the ganglion cells.
The intraocular implant may also contain at least one light-emitting element which emits light signals depending on the operating parameters of the stimulation system, including light signals emitted by the light-emitting element, encoded, for example, by modulating the duration and/or intensity of light signals, depending on the operating parameters of the intraocular implant. The light signals emitted by the light-emitting element may contain, for example, information on the position of the intraocular implant, the image data of the contact of the image received by the intraocular implant, the routes of electrical transmission of the implant and/or the quality and/or electrical resistance of the intraocular stimulation. The light-emitting element may also contain information on the selection of light from the stimulation ganglion and the electrical transmission of the light emitted by the stimulation ganglion.
This light-emitting element is preferably located inside the eye so that the light signals emitted by the light-emitting element can be detected by an observer through visual contact to the inside of the eye.
In addition to another aspect of the present invention, the above tasks are solved by a process for operating the device of the invention, which includes at least the following steps:Capture an image by an external camera,produce from the image captured image data in local resolution,calculate diagnostic,control or stimulation commands of a certain duration and intensity depending on the image data,transmit the diagnostic,control or stimulation commands to a stimulation system with an intraocular implant and an extraocular implant,calculate and generate electrical stimulation pulses or currents of a certain duration and intensity in the extraocular implant or perform a diagnostic response according to the diagnostic,control or stimulation commands,electrical stimulation or controls are placed in the intraocular implant and at least one of the intraocular stimulation or stimulation cells is in contact with the relevant electrical stimulation or stimulation device,or at least one of the intraocular stimulation or stimulation cells is in contact with the implant or the relevant electrical stimulation or stimulation device.
To prepare the image data taken by the external camera for use in the stimulation system, the image data is electrically evaluated or processed in the electric control unit before being transmitted to the stimulation system to produce the corresponding electrical stimulation pulses or currents, the components of the electric control unit being either part of the extraocular implant on the one hand or contained in an external computing unit carried separately by the patient or in a pair of glasses containing the external camera and/or the infrared light transmitter.
As described above, in the method of operation of the device according to the invention, the current required to operate the extraocular implant and the intraocular implant is transmitted wirelessly via an inductive interface between the high frequency transmitting antenna outside the eye and the high frequency receiving antenna of the extraocular implant, while the image data captured by the external camera is transmitted wirelessly via an infrared interface between the infrared transmitter outside the eye and the infrared receiver inside the eye. Alternatively, the transmission of the infrared data captured by the external camera may also be transmitted wirelessly via the inductive interface between the high frequency transmitting antenna outside the eye and the extraocular receiver.
The transmission of the image data, diagnostic commands, control commands or stimulation commands, taken by the external camera, may be in the form of a serial data stream from the infrared receiver in the eye via the wired connection to the digital control unit in the extraocular implant, whereby the serial data stream from the infrared receiver in the eye via the wired connection to the digital control unit in the extraocular implant contains information on the electrode address, e.g. 1 to 250, and the amplitude of the electrode, e.g. 0 to 1000 μA, the electrode address of the stimulation impulse for the stimulation input. Information on the electrode address and the electrode impulse for the stimulation input are calculated by the stimulation impulse generator and the amplitude of the electric current generated by the stimulation impulse is calculated by the electrical impulse generator and the amplitude of the electric current generated by the stimulation impulse is calculated by the electrical impulse generated by the implant and the amplitude of the electric current generated by the stimulation impulse is calculated by the electrical impulse generated by the implant and the amplitude of the electric current generated by the stimulation impulse is calculated by the electrical impulse generated by the implant.
The stimulation pulses or currents are transmitted from the extraocular implant electrical control unit as a parallel signal current via parallel wire connections to the stimulation electrodes in the intraocular implant. For this purpose, the electrical control unit of the extraocular implant or the retina stimulator chip has, for example, 250 connection pads to which wires for 250 stimulation electrodes in the intraocular implant electrode array can be connected.
In a preferred embodiment of the procedure, it is also possible for the intraocular implant to transmit diagnostic data on the operating parameters of the intraocular implant via the wire connection to the extraocular implant, e.g. as a serial data stream, and then the serial diagnostic data stream is inductively transmitted from the extraocular induction coil, e.g. by load modulation, to external diagnostic means, e.g. housed in the glasses.
Other preferred embodiments of the implant of the inventionAs described above, in particular, electronic components of the vision prosthesis of the invention may be housed in a device outside the body, preferably in glasses that the patient can wear like a normal vision aid. Below, the electronic components housed in a device outside the body are referred to as the extracorporeal part of the vision prosthesis of the invention, while the components of the vision prosthesis of the invention, including the intraocular in the eye and the extraocular implanted at the eye, located inside the body are summarized as the intracorporeal part of the vision devices of the invention.
A wireless inductive interface exists between the extracorporeal part of the prosthesis and the intracorporeal part in the patient's eye, respectively, through which both energy coupling and data transmission take place. According to a preferred embodiment of the present invention described above, this inductive interface is bi-directionally trained between the extracorporeal part and the intracorporeal part. To this end, both the extracorporeal and intracorporeal part are equipped with a transmitting coil that can transmit intracorporeal electrical signals preferably in the high-frequency range, and with a receiving coil or an amplified signal that transmits the electrical signals before the receiving coil in the high-frequency band. This signal can be transmitted both in the extrinsic and in the extrinsic direction of the transmitting part, although the receiving part can be transmitted in the extrinsic direction of the receiving part only.
In a further development of this preferred embodiment of the present invention, the bidirectional data line between the extracorporeal and intracorporeal portion of the prosthesis comprises at least two, preferably wireless transmission channels, at least one wireless transmission channel running from the extracorporeal portion (e.g. in the eyepiece) to the intracorporeal portion of the prosthesis in the eye, hereinafter referred to as the up-link, and at least one wireless transmission channel running from the intracorporeal portion of the prosthesis in the eye to the extracorporeal portion in the eyepiece, hereinafter referred to as the down-link.
Data transmission between the extracorporeal and intracorporeal parts of the prosthesis is preferably simultaneous, i.e. data are transmitted simultaneously on the transmission channel and on the relay channel. In particular, the relay channel can be used to transmit data on the status of the intracorporeal part of the prosthesis. This provides an additional safety benefit by continuously monitoring the condition and functionality of the intracorporeal part of the prosthesis and can signal a corresponding malfunction in the event of failure of the prosthesis or relay channel.
In another preferred embodiment of the present invention, data transmission between the extracorporeal and intracorporeal parts of the prosthesis may be alternated, for example, during certain periods the transmission channel from the extracorporeal to the intracorporeal part of the prosthesis may be active, and during other periods the retransmission channel from the intracorporeal to the extracorporeal part of the prosthesis may be active.
In normal operation, data transmission between the extracorporeal and intracorporeal parts of the prosthesis is predominantly by means of the transmission channel, i.e. the image data collected and processed by the extracorporeal part of the prosthesis (e.g. in the glasses) are transmitted via the transmission channel to the intracorporeal part of the prosthesis (in the eye).
The uplink can transmit different types of data from the glasses to the implant in the eye. For example, the uplink transmits stimulation commands from the extracorporeal part of the prosthesis to the stimulator chip of the intracorporeal part of the eye. Such stimulation commands may include the following information:electrode addresses, i.e. the addresses of the electrodes arranged in an electrode array to stimulate the ganglion cells in the retina of the eye,stromamplitudes, i.e. information for the stimulator chip, which information indicates the strength of the stimulating signal to be generated,phasorphorus, i.e. which information indicates the information for the stimulator to be generated,phasorphorus, the information for the stimulating signal to be generated, the information for the stimulating signal to be generated, the information for the stimulating signal to be generated, the information for the stimulating signal to be generated, the information for the stimulating signal to be stored, the information for the stimulating signal to be stored, the information for the stimulating signal to be stored, the information for the stimulating signal to be stored, the information for the stimulating signal to be stored, the stimulating signal to be stored, the information to be stored, the information to be stored, the information to be stored, the stored, the information to be stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the stored, the, the, the, the, the, the, the, the, the, the
Furthermore, measurement commands may be transmitted from the extracorporeal part of the prosthesis to the intracorporeal part via the transmission channel, for example, measurement commands are commands from the extracorporeal part of the prosthesis to the intracorporeal part to take certain measurements and transmit the measured value via the return transmission channel to the extracorporeal part of the prosthesis.Measurement of voltage at an electrode during stimulation,Measurement of voltage at an electrode outside stimulation,Measurement of nerve action potentials by means of one or more stimulation electrodes,Measurement of nerve action potentials by means of special measuring electrodes.
In addition, for example, status commands may be transmitted from the extracorporeal part to the intracorporeal part of the prosthesis via the transmission channel, including requests to the intracorporeal part of the prosthesis to capture certain state parameters and to transmit via the relay channel to the extracorporeal part of the prosthesis, for example, requests to the intracorporeal part of the prosthesis to capture the following state parameters and to transmit via the relay channel to the extracorporeal part of the prosthesis:the identification number (ID number) of the implant,a status overview of the implant,e.g.o the state of the charge-balancing systems or the state of the energy supply of the implant, i.e. whether it has too much or too little energy, the temperature of the stimulation chip or of implant parts,the moisture sensor reading.
According to another preferred embodiment of the vision prosthesis of the invention, at least the transmission channel from the extracorporeal to the intracorporeal part of the vision prosthesis is designed as an optical data transmission. The data can be transmitted by light signals by means of light-emitting diodes (LEDs) or by means of a laser, for example with infrared light. In optical data transmission, at least part of the natural light path of the eye can be used by directing the light signals of the light-emitting diodes or laser outside the eye through the lens opening of the eye to an optical receiving element inside the eye.
Data transmission between the intracorporeal and extracorporeal parts of the vision device can be carried out on the relay channel with any coding. Preferably, a balanced coding containing approximately equal numbers of zero and one states is used to avoid saturation of the optical receiver. For example, Manchester coding, so-called 4PPM coding, 4PPM+ coding or other suitable coding methods may be used.
According to another embodiment of the vision device according to the invention, the forward and/or backward transmission channel between the intracorporeal and extracorporeal parts of the vision device is designed as an electromagnetic data transmission, whereby the carrier frequency of the transmitter is modulated accordingly to transmit data. The electromagnetic data transmission may be actively trained, using as the carrier frequency of the transmitter, for example, the 13,56 MHz ISM frequency band, the 27,12 MHz ISM frequency band, the 125 kHz ISM frequency band or another suitable frequency band. In the case of electromagnetic data transmission between the carrier frequency and the extracorporeal part, a frequency modulation modulation or other suitable modulation method may also be used instead of the frequency modulation modulation modulation.
According to another modulation method applicable to the optical prosthesis of the invention, a separate carrier frequency, e.g. in the 433 MHz ISM frequency band or in another suitable frequency range, preferably different from the frequency for power coupling via the inductive interface, is used.The data are transmitted by means of a series of electronic signals, which are then transmitted to the data centre.
The downlink can transmit different types of data from the intracorporeal to the extracorporeal part of the prosthesis.In particular, the downlink can transmit diagnostic data on the condition of the intracorporeal part of the prosthesis or on the condition of the implant, such as:measurements of electrode impedance of certain stimulation electrodes,measurements of electrical voltage attached to stimulation electrodes,monitoring data on the condition of certain stimulation electrodes.
The feed-back channel may also provide information or diagnostic data on the system status of the flow control in the intracorporeal part of the prosthesis or implant, such as information on the following control details:Data from the extracorporeal to the intracorporeal part of the prosthesis is transmitted correctly (yes or no),the intracorporeal part or implant is initialized correctly (yes or no),System status reset is performed (yes or no),Implant power status,e.g.o status of the analogue component (s) of the stimulator chip,o state of the so-called power-down stage of the intracorporeal part to the extracorporeal part of the vision prosthesis,e.g. errors in stimulation of the retina of the eyeo maximum stimulation current is reached,o charge balance between stimulation electrodes is not achieved,o Charge balancing between stimulation electrodes takes too long,stimulation has been performed although not requested,e.g. due to a fault in the final stage of a power source,status of the electrical power supply,e.g.o operating voltage too low,o operating voltage too high,voltage at stimulation electrodes at certain measuring points.Diagnostic data on patient physiology,e.g.o derivation of the action potentials of individual nerve cells, especially ganglion cells,o derivation of the total action potentials of nerve cells, especially ganglion cells, which makes it possible to make a statement about the stimulability of the contacted adjoining cells,diagnostic data on the general status of the intracorporeal part of the prosthesis or implant, e.g.o temperature in the electronics area of the implant,o temperature at a specific point in the eye,o temperature at several points in the eye,o measurement of intraocular pressure,o measurement of implant acceleration,o Humidity measurement within the implant housing,
As described above in connection with the transmission channel, the retransmission channel can also be formed from the intracorporeal to the extracorporeal part of the prosthesis as an optical data transmission channel. For this purpose, as in the transmission channel, the data can also be transmitted in the retransmission channel by light signals by means of light-emitting diodes (LEDs) or by means of a laser, for example with infrared light. The natural light path of the eye can also be used at least partially by directing the light signals of a light-emitting element located inside the eye through the lens of the eye to an optical receiver outside the eye. The optical receiver captures the light-emitting signal of this element in an encoded form and directs it to an electronic signal for evaluation.
According to another embodiment of the vision device according to the invention, the back-transmission channel from the intracorporeal to the extracorporeal part of the vision device is designed as a passive electromagnetic data transmission, in which the carrier frequency of a transmitter is modulated accordingly to transmit data. For example, a load modulation of the energy transmitting frequency can be performed as a modulation process. The load modulation of the carrier frequency can be performed by turning on and off a resistive load, a capacitive load or an inductive load according to the data current to be transmitted. A combination or subcombination of the above methods is also possible in the electromagnetic data transmission between the intracorporeal and extracorporeal part of the vision device.
Data transmission via the feed-back channel from the intracorporeal part (in the eye) to the extracorporeal part (e.g. in the eyeglasses) of the vision device of the invention may be performed additionally or alternatively by using an error-correcting procedure.
For example, a method that can correct a defined number of incorrectly transmitted data bits per total transmitted data bits by redundancy in the encoding of the data transmission may be used as an error correction method.Hamming coding, bending coding, repeat coding or other appropriate error correction procedures.
In addition to or as an alternative to the use of a correction method, data transmission via the transmission channel from the extracorporeal part (in the eyeglasses) to the intracorporeal part of the prosthesis (in the eye) can be performed using a fault detection method. Similarly, data transmission via the return channel from the intracorporeal part (in the eye) to the extracorporeal part (in the eyeglasses) of the prosthesis of the invention can be performed in addition to or as an alternative to the correction method using a fault detection method. Such a fault detection method can be implemented by different coding methods, such as:The system shall be designed to provide a high level of security for the system and to provide a high level of security for the system.
For data transmission via the transfer channel from the extracorporeal part (in the glasses) to the intracorporeal part (in the eye) of the vision device of the invention, a data rate in the range of 100 kilobits/second to 10 megabit/second, preferably a data rate in the range of 1 megabit/second to 10 megabit/second, preferably 1 to 5 megabit/second and preferably 1 to 2 megabit/second, may be used.
For data transmission via the feed-back channel from the intra-corporeal part (in the eye) to the extracorporeal part (in the glasses) of the vision device of the invention, a data rate in the range of 1 KiloBit/s to 100 KiloBit/s, preferably a data rate in the range of 5 to 20 KiloBit/s, may be used.
Further details, preferred embodiments and advantages of the present invention are given in the following description by reference to the drawing:Figure 1a schematic representation of the cross-section by a human eye with a prosthesis according to a preferred embodiment of the present invention;Figure 2a prospective view of a stimulation system comprising a pair of glasses and a human eye with a prosthesis according to the present invention;Figure 3a figurative representation of the cross-section by a human eye with a prosthesis according to a second preferred embodiment of the present invention;Figure 4a schematic representation of the cross-section by a human eye with a prosthesis according to a third preferred embodiment of the present invention;Figure 5a schematic representation by a human eye with a quine and a quine according to a third preferred embodiment of the present invention;Figure 6a schematic representation of the cross-section by a human eye according to a third preferred embodiment of the present invention;Figure 5a schematic representation by a human eye with a quine and a quine according to a third preferred embodiment of the present invention;Figure 6a schematic representation by a human eye with a quine according to a preferred embodiment of the present invention;Figure 6a
Figure 1 shows a schematic representation in cross-section through a human eye with a visual prosthesis according to a preferred embodiment of the present invention. The eyeball 1 of the human eye has a substantially round shape, with the transparent cornea 21 having a greater curvature at its front. The area of the eyeball 1 located in the eye socket is composed of several layers, the outermost being the so-called sclera or dermis 11 respectively. To the dermis or dermis 11 the atria 12 are joined in the direction of the inner eye, on which the so-called retina or retina 13 with light-sensitive cells or photoreceptors (zap, stam cells) and ganglia are located.
In a healthy human eye, the natural light pathway passes through the transparent cornea 21 in the anterior region of the eyeball 1 through the iris 17 and the biconvex lens 14, whose shape or refractive power is altered by the tension of the ciliary muscle 15. The incoming light enters the eye under optical refraction of the cornea 21 and the lens 14 and is projected onto the retina 13 in the posterior region of the eyeball 1. The light-sensitive photoreceptors in the retina 13 convert the incident image light projected onto the retina into nerve signals that are directed to the brain by ganglion cells in the retina (not represented).
The purpose of the vision prosthesis of the present invention is to restore or improve vision impaired or destroyed by degenerative changes in the retina 13 and a prerequisite for the use of the vision prosthesis of the present invention is that the ganglion cells in the retina 13 are largely intact and capable of transmitting nerve impulses via the optic nerve to the brain.
The vision prosthesis of the invention consists of a stimulation system with an intraocular implant 6, 8 located inside the eyeball 1 and an extraocular implant 3, 4 located outside the eyeball 1 in accordance with the preferred embodiment shown in Figure 1.
The intraocular implant is connected to the extraocular implant via a wire link 5. The wire link 5 is designed as a flexible implant that leads from the extraocular implant outside the eyeball 1 immediately behind the conjunctiva 16 in the area of the so-called parsplana between the ciliary muscle 15 and the retina 13 to the intraocular implant. The wire link 5 includes electrical wires to ensure that the intraocular implant is powered via the extraocular implant. Furthermore, the wire link 5 includes electrical wires in sufficient numbers to allow the transmission of image data or diagnostic data, control data or voice signals in the form of voice errors/strokes between the intraocular and extraocular implant.
The intraocular implant consists of an electrode array 6 located epiretinal on the retina 13 and has a number of stimulation electrodes arranged, for example, in a matrix. The stimulation electrodes of the electrode array 6 are connected to ganglion cells and can stimulate them by stimulation impulses or stimulation currents. The electrode array 6 of the epiretinal implant is centered in the area of the macula of the eye, where most of the light falls on the retina 13 via the natural light pathway. To ensure a safe position of the intraocular implant on the retina, it is located by means of a so-called nail tackle 9 or 9 through which the intraocular retina 13 is stimulated and the retina 11 is implanted in the eye.
An infrared receiver 8 is located on the intraocular implant, which can receive light signals from an infrared transmitter 10 outside the eye via the natural light pathway. An external camera (not shown) captures an image, the pre-processed image data of which is transmitted via the infrared transmitter 10 on the natural light pathway of the human eye to the infrared receiver 8 of the intraocular implant. This image data is transmitted via the wired connection 5 from the intraocular implant to the extraocular implant preferably in the form of a serial data stream.
The position of the infrared receiver 8 is conceivable on the entire wire link 5 but preferably in the area of the nail 9. Alternatively, the infrared receiver 8 may be located on a branch 25 of the wire link 5 to adjust the reception properties favourably. This branch 25 is detached from the wire link 5 and conveniently protrudes into the eye in the beam path of the natural light path. In this way, the infrared signals coming into the eye from outside the eye via the natural light path can be directly transmitted to the infrared receiver 8 located on the branch 25 of the wire link 5.
The image data are evaluated in the retinal stimulator chip 3 of the extraocular implant and converted into stimulation pulses or stimulation currents. The stimulation pulses or stimulation currents are then transmitted in the form of a parallel signal stream via the wire link 5 to the stimulation electrodes in electrode array 6 of the intraocular implant and flow back to the respective power source via the counter electrode 22, 23 and/or 24. The stimulation electrodes stimulate the ganglion cells in the retina via the micro-contact structure in accordance with the local stimulation impulses, thereby producing a visual impression corresponding to the external image of the camera with the nerve impulses.
The stimulation system of the vision device of the invention also includes an extraocular implant located outside the eyeball 1 on the dermis 11. The extraocular implant contains all the components of the stimulation system which do not necessarily need to be located inside the eye on the intraocular implant. The extraocular implant includes a retina stimulator chip 3 which, based on image data received, can calculate and generate stimulation pulses or stimulation currents for the stimulation electrodes of the retina. In addition, the intraocular stimulator chip 3 includes electronic components for calculating the stimulation and coordinating the stimulation currents and can be used to generate the corresponding stimulation currents and the corresponding electronic stimulation currents required for the stimulation of the image and the stimulation co-generator.
The extraocular implant also comprises at least one counter electrode, which may be located, for example, in the positions indicated in Figure 1 by reference symbols 22, 23 and 24. The counter electrodes 22, 23, 24 serve as a back-current pathway for the stimulation current sources to close the current path to the stimulation electrodes in electrode array 6 through the tissues of the dermis 11, the veins 12 and the retina 13.
The extraocular implant also includes a high frequency antenna 4 which can receive high frequency signals 2 emitted by a high frequency antenna 18 located away from the eyeball 1 and the inductive interface between the high frequency antenna 4 of the extraocular implant and the external high frequency antenna 18 which can transmit inductive energy required for the operation of the extraocular implant and the intraocular implant.
For example, the external high frequency antenna 18 may be housed together with other electronic components outside the body in an extracorporeal part of the vision prosthesis of the invention, such as in a pair of glasses that the patient can wear like a normal vision aid. In contrast, the intraocular implant 6, 8 and the extraocular implant 3, 4 constitute an intracorporeal part 3, 4, 6, 8 of the vision prosthesis of the invention. A wireless contact can be made between the extracorporeal part and the intracorporeal part of the vision prosthesis of the invention via the inductive interface.
This inductive interface between the extracorporeal and intracorporeal parts can also transmit the image data captured by an external camera to the retinal stimulator chip 3, which generates stimulation pulses from the received image data and transmits them via the wire link 5 to the stimulation electrodes in the intraocular implant. In addition, the inductive interface between the high frequency antenna of the intraocular implant and the external high frequency antenna 18 can be bidirectionally formed so that the retinal stimulator chip 3 can transmit information about the operating parameters of the intraocular implant and/or the extraocular implant via the high frequency inductor 4 to the external antenna 18 which can be externally evaluated by an electronic device.
To provide the bidirectional inductive interface between the extracorporeal part and the intracorporeal part of the vision device of the invention, the extracorporeal part may have an antenna 18 outside the eye 1 which can preferably both transmit and receive electromagnetic signals 2 in the high frequency range.
Alternatively, the extracorporeal part of the vision device according to the invention may comprise at least two antennas 18 for the bidirectional inductive interface, of which one antenna may transmit electromagnetic signals 2 and a second antenna may receive electromagnetic signals 2, and the extracorporeal part of the vision device according to the invention, i.e. the extraocular implant 3, 4 and/or the intraocular implant 6, 8, may comprise at least two antennas 4 for the bidirectional inductive interface, of which one antenna may transmit electromagnetic signals 2 and a second antenna may receive electromagnetic signals 2.
The intraocular implant also includes a light-emitting element 19 which generates light signals depending on the operating parameters of the intraocular implant. This light-emitting element 19 is, for example, designed as an infrared diode, whose infrared light signals can be perceived by an observer or a corresponding infrared receiver outside the eye. The light signals emitted by the light-emitting element 19 allow, for example, the optimal position of the intraocular immat on the retina 13 during the operative implantation. The light-emitting element 19 can therefore also be called a status indicator. The position of the light-emitting element 19 covers the entire area of the 5th branch of the connector, but it can ideally be located on the 5th branch of the connector, which is ideally located on the 9th branch of the 5th branch of the light-emitting wire, but the alternating alternating current of the 5th branch of the connector may be in the area of the 9th branch.
For the transmission of information, the electromagnetic signals 2 in the bidirectional inductive interface and the light signals in the optical interface may be encoded using one of the methods described above, including the error correction and error detection methods described above.
The present invention solves the above problem by means of a vision prosthesis with an epiretinal implant, which is supplied with electricity via an extraocular device, whereby the extraocular device receives the electricity via an inductive interface and thus wirelessly from a high frequency transmitter.
Furthermore, the present invention solves the above problem by means of a bidirectional inductive interface between a transmitter/receiver or antenna located outside the eye and the body and a transmitter/receiver or antenna located inside the body at or in the eye, through which bidirectional data transmission between the extracorporeal and the intracorporeal part of the prosthesis can be carried out.
Figure 2 shows a perspective view of a stimulation system comprising a pair of glasses and a human eye with a vision prosthesis of the invention. In the stimulation system shown in Figure 2, the extracorporeal components of the vision prosthesis of the invention are housed in a pair of glasses or a frames 26 which the patient can wear like ordinary glasses. The pair of glasses 26 includes two brackets 27 for the usual positioning of the glasses 26 on the patient's head and two frames 28 for the reception of glasses, which may be without optical function and serve only to give the natural appearance of the glasses.
For example, the eyeglass bracket 27 may contain the external camera, in particular a video camera (not shown), which captures the image or sequences of images in front of the patient's field of vision. Electronic components of the prosthesis required to process and process the image data captured by the external camera may also be housed in the glasses or in the frame 26.
The receiving coil and the transmitting coil 18 of the extracorporeal part of the prosthesis may also be located in the spectacle 26, in particular in the spectacle bracelets 27 and can transmit and receive electromagnetic signals preferably in the high frequency range. In view of the transmitting and receiving functions of the transmitting or receiving coil 18 in the spectacle and the transmitting or receiving coil 4 of the extraocular, intracorporeal part of the prosthesis, the inductive interface between the extracorporeal and intracorporeal part of the prosthesis is bi-directionally designed. The receiving coils and/or S-S 18 and/or the transmitting or receiving coils of the extracorporeal pores of the spectacle 28 are located in the eyepiece, for example by means of the spectacle 28 itself.
In the embodiment of the stimulation system of the invention shown in Figure 2, an image is first taken in operation by the external camera in the spectacle 26 and, after electronic pre-processing, the image signals are transmitted by means of the transmitting or receiving coil 18 in the spectacle bracket 27 to the transmitting or receiving coil 4 of the intracorporeal part and from there, by means of the wire link 5 to the epiretinal nerve array 8 of the intraocular retinal implant. The electrode array 8 stimulates the cells of the retina by electrical signals in accordance with the received image data and thus reflects the electrical signals from the external camera to the electrical impediments of the visual system. In this way, the signal is transmitted by the camera to the patient's intraocular vision in order to transmit the electrical impulses to the external vision and thus improve the visual perception of the visual system.
In Figure 2 a dashed line S is also shown, passing through the eye 1 centrally and representing the plane of incision of Figures 3 to 6. Figure 3 shows a schematic representation of the cross section along the plane of incision S shown in Figure 2 by a human eye with a prosthesis according to a second preferred embodiment of the present invention. In this second preferred embodiment of the vision device of the invention, the intraocular part includes the electrode array or micro-contact structure 6, the nail or tack 9 to its epiral attachment, the infrared receiver 8 and the interconnection 5 between the intraocular and the extraocular part of the intraocular. As an extraocular component, the receiver 4 is designed to transmit and receive electromagnetic waves, and the intraocular receiver 2 is designed to transmit and receive electromagnetic waves.
Below the eye 1 is a transmitter coil 18 located outside the body, which transmits signals inductively to the transmitter/receiver coil 4 via electromagnetic waves 2 preferably in the high frequency range. The signals received from the extraocular transmitter/receiver coil 4 are then transmitted via the wire link 5 to the intraocular part of the prosthesis as described above. On the right side of the eye is a receiver coil 18 also located outside the body, which inductively receives the electromagnetic signals 2 emitted from the extraocular transmitter/receiver coil 4 and transmits these signals or inductively from outside the eye 1 to the intraocular part of the prosthesis in a parallel or inductive manner, as described above, and transmits the signals via the intraocular coil 1 as well as the data within the eye.
In addition, an infrared transmitter/receiver 8, 10 may be provided within eye 1 to transmit data from the intraocular part of the prosthesis by infrared signals 20 radiating outward through the pupil via the eye's natural light pathway and received by an infrared receiver 8 located outside the body; the extracorporeal infrared receiver 8 may also have the function of an infrared transmitter or the infrared receiver 8 may be provided with a separate infrared transmitter 10 within the eye pathway transmitting data by infrared signals 20 radiating outward from the eye via the eye's natural light pathway into the eye through the eye and received by the intraocular receiver 8 or by the intraocular receiver 20 via the intraocular part of the eye; or the data may be transmitted or received by the infrared signals 20 outside the eye through the intraocular part of the pupil.
Figure 4 shows a schematic representation of the cross-section along the plane of incision S shown in Figure 2 by a human eye with a prosthesis of vision according to a third preferred embodiment of the present invention. This third preferred embodiment of the prosthesis of vision according to the present invention, as well as the embodiment shown in Figure 3, includes an intraocular part with electrode array or micro-contact structure 6, the nail or tack 9, the infrared transmitter/receiver 8, 10 and the wire connection 5 between the intraocular and extraocular part of the prosthesis.
In contrast to the third embodiment of the vision device shown in Figure 3, the third embodiment shown in Figure 4 has a transmitter coil 18 located on the right side of the eye, located outside the body, which transmits signals inductively to the intracorporeal transmitter/receiver coil 4 via electromagnetic waves 2. The signals received from the intracorporeal transmitter/receiver coil 4 are then relayed via the wire link 5 to the intraocular part of the vision device. Below the eye 1, a receiver coil 18 is located, also located outside the body, which receives the inductive signals emitted by the extraocular transmitter/receiver coil 4 and the inductive signals 2 emitted by the extraocular transmitter/receiver coil 4. In this way, the inductive signals can be received from outside the eye or transmitted from the intraocular part 1 or transmitted in parallel to the data transmitter or transmitter in the upper part of the eye.
As with the prosthesis shown in Figure 3, the third preferred embodiment shown in Figure 4 may also have an infrared transmitter/receiver 8, 10 within eye 1 transmitting data from the intraocular part of the prosthesis by infrared signals 20 radiating outward through the eye's natural light pathway and received by an infrared receiver 8 located outside the body. In addition, the extracorporeal infrared receiver 8 may also have the function of an infrared transmitter or may have a separate infrared transmitter 10, transmitting data by infrared signals 20 transmitted by signals 20 transmitted from outside the eye through the natural light pathway in the intraocular part of the eye, and transmitting these signals 20 or more to or from the intraocular part of the eye.
Figure 5 shows a schematic representation of the cross-section along the plane of incision S shown in Figure 2 by a human eye with a prosthesis of vision according to a fourth preferred embodiment of the present invention. As with the previously described embodiments, this fourth preferred embodiment within eye 1 shows the electrode array 6, the tack 9, the infrared transmitter/receiver 8, 10 and the wire connection 5 between the intraocular part and the extraocular components of the prosthesis. The transmitter/receiver coil 4 is again intracorporeal but located outside eye 1 and can transmit and receive electromagnetic waves 2.
In contrast to the previous embodiments, this fourth preferred embodiment does not have a separate receiving coil, but the transmitter/receiver coil 18 can be used as well as the extraocular transmitter/receiver interface 4, electromagnetic waves 2 can both transmit and receive these signals. bidirnational signals can be transmitted or received via the inductive coil between the transmitter/receiver interface 4 and the transmitter/receiver interface 18 or by means of inductive signals transmitted or received from the transmitter/receiver interface 1 or from the transmitter/receiver interface 1 as described above, as well as data from the extraocular transmitter/receiver interface 4.
The fourth preferred embodiment, shown in Figure 5, also includes an infrared transmitter/receiver 8, 10 within eye 1 which transmits data from the intraocular part of the prosthesis by infrared signals 20 radiating outwards through the eye's natural light pathway and received by an infrared receiver 8 located outside the body; the extracorporeal infrared receiver 8 may also have the function of an infrared transmitter or the intraocular visual receiver 8 may have a separate infrared transmitter 10 which transmits data from the intraocular part of the prosthesis by infrared signals 20 transmitted outside the eye through the natural light pathway of the eye through the intraocular part of the eye and receive these signals 20 or 20 by means of intraocular receptors 8 and 20 by means of intraocular receptors 1 and 20 by means of intraocular receptors.
In accordance with the embodiments shown in Figures 3, 4 and 5, the infrared transmitter/receiver 8, 10 and the extracorporeal transmitter/receiver coil 18 can be combined in one device, preferably with a parabolic light-sensitive surface, to reliably capture the infrared signals 20 transmitted from the intraocular infrared transmitter 10 to the external surface via the natural light path of the eye 1.
Figure 6 shows a schematic representation of the cross-section along the plane of incision S shown in Figure 2 by a human eye with a prosthesis of vision according to a fifth preferred embodiment of the present invention. As with the previously described embodiments, this fifth preferred embodiment also contains within eye 1 the electrode array 6, the tack 9, the infrared transmitter/receiver 8, 10 and the wire connection 5 between the intraocular part and the extraocular components of the prosthesis of vision. The transmitter/receiver coil 4 is arranged intracorporally but outside eye 1 and can both transmit and receive electromagnetic waves 2.
In the case of the right eye, there is a transmitter/receiver coil 18 located outside the body, which transmits signals inductively to the transmitter/receiver coil 4 via electromagnetic waves 2 and transmits them from the extraocular through the wire link 5 to the intraocular part of the prosthesis. Similarly to the embodiments shown in Figure 5, this fifth embodiment does not have a separate receiver coil, but the extracorporeal transmitter/receiver coil 18 can, like the intracorporeal transmitter/receiver coil 4, both transmit and receive electromagnetic waves 2. This bidirectional inductive interface between the transmitter/receiver coil 4 and the transmitter/receiver data coil 18 or outside the intraocular part of the prosthesis can be described above, as well as transmitting or receiving signals from the intracorporeal part of the optical coil 1 or from the intraocular part of the prosthesis.
The fifth preferred embodiment, shown in Figure 6, also includes an infrared transmitter/receiver 8, 10 within the eye 1 which transmits data from the intraocular part of the prosthesis to the eye by means of infrared signals 20 radiating outwards through the eye's natural light pathway and received by an infrared receiver 8 located outside the body. Furthermore, the extracorporeal infrared transmitter/receiver 8, 10 also has the function of an infrared transmitter which transmits data from infrared signals 20 entering the eye from outside the body via the natural light of the eye and from the intraocular part of the prosthesis via the infrared transmitter/receiver 8, 10 which can be received by means of intraocular or extracorporeal infrared signals 20 or transmitted by means of intraocular or extracorporeal infrared signals 20 and transmitted by means of intraocular or intraocular tectesis.
In contrast to the embodiments shown in Figures 3, 4 and 5, in this fifth embodiment, the infrared transmitter/receiver 8, 10 and the extracorporeal transmitter/receiver coil 18 are not combined in a device but are arranged separately. The infrared transmitter/receiver 8, 10 again includes a parabolic surface with light-sensitive sensors to reliably capture the infrared signals 20 from the intraocular infrared transmitter 10 to the external eye via the natural light path of eye 1.
List of reference marks1human eye or eyeball2electromagnetic high frequency signals3retinal stimulator chip or RS chip4high frequency transmitter/receiver coil5Wire connection between RS chip 3 and electrode array 66Electrode array or micro-contact structure7macula or point of sharpest vision8infrared receiver9nail or tack10infrared transmitter11skin or sclera12skin13net skin or retina14eye lens15gilliar muscle16linked skin17arcuate skin18electrical frequency transmitter/receiver coil19brushed or brushed light20diode-infrared-frame20diode-infrared-cornea21diode-infrared-gill2222diode-infrared-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill22diode-gill or glass connector
The Commission1. a prosthesis for vision with a stimulation system for implantation in a human eye with an electrode array (6) for contacting and stimulating living tissue or nerves in the visual system of the eye (1), which generates stimulation pulses by means of an electric control unit (3),characterised by:The stimulation system shall include at least one intraocular implant (6, 8) and at least one extraocular implant (3, 4) to supply energy to the intraocular implant (6, 8).2.Visual prosthesis according to one of the aspects 1 or 2, where the extracorporeal part includes at least one antenna (18) outside the eye (1) for the bidirectional inductive interface (4, 18) which can transmit and receive electromagnetic signals (2) preferably in the high frequency range.18) between the antenna (18) of the extracorporeal part outside the eye (1) and the antenna (4) of the intracorporeal part (3, 4, 6, 8) is trained to transmit image data recorded by an external camera via electromagnetic signals (2) from the antenna (18) outside the eye (1) to the antenna (4) of the extraocular implant (3, 4).8) to transmit the required electrical energy inductively from the antenna (18) of the extracorporeal part outside the eye (1) to the antenna (4) of the intracorporeal part (3, 4, 6, 8).7. Vision prosthesis according to one of the preceding aspects, where the extracorporeal part includes at least two antennas (18) for the bidirectional inductive interface (4, 18), of which one antenna can transmit electromagnetic signals (2) and a second antenna can receive electromagnetic signals (2).8. Vision prosthesis according to one of the preceding aspects, where the extraocular implant (3, 4) and/or the intraocular implant (6, 8) includes at least two antennas (4) for the vector inductive interface (4, 18).of which a first antenna (4) can transmit electromagnetic signals (2) and a second antenna (4) can receive electromagnetic signals (2).9. Vision prosthesis according to one of the aspects 4 to 8, where the data rate of the signals received by the antenna (4) of the extraocular implant (3, 4) (2) differs from the data rate of the signals sent by the antenna (4) of the extraocular implant (3, 4).10. Vision prosthesis according to one of the aspects 4 to 9, where the bidirectional inductive interface (4, 18) between the antenna (18) of the extracorporeal part outside the eye (1) and the antenna (4) of the extraocular implant (3, 4) is formed and the extraocular implant (3, 4)The eye implant (6, 8) is trained as an epiretinal implant suitable for implantation within the eyeball (1) on the retina of the eye, preferably in the area of the macula.12. The eye implant is trained as an anterior aspect, the extraocular implant (3, 4) being suitable for implantation outside the eyeball and fixation on the epithelium of the eye.13.(8) comprises an electrode array (6) in which the stimulation electrodes are preferably arranged in a matrix.14. Vision prosthesis according to aspect 13, where the electrode array (6) of the intraocular implant (6, 8) has a number of contact points for contacting retinal or ganglion cells, through which the contacted retinal or ganglion cells can be stimulated by stimulation pulses.15. Vision prosthesis according to one of the foregoing aspects, where the extraocular implant (3, 4) comprises the electrical control unit (3) which generates the stimulation pulses and is preferably a digital control unit with analogue auxiliary functions.16.The electrical control unit (3) contains electronic storage media to store the duration and intensity of the stimulation pulses to be generated.18. The electrical control unit (3) contains at least one of the electronic components (3) in a partially integrated circuit, e.g. a photolithographic chip, and is pre-installed in a micro-ocular implant.20. prosthesis of vision of one of the previous aspects, wherein the extraocular implant (3, 4) is coupled to the intraocular implant (6, 8) by a wire connection (5), which includes at least one line for the transmission of the operating current and at least one signal line for the transmission of electrical stimulation impulses from the digital unit (3) to the extraocular implant (6, 8).8. comprises at least as many conduits for the transmission of electrical stimulation pulses as are provided for by stimulation electrodes in the intraocular implant (6, 8) 22. Vision prosthesis according to one of the aspects 19 to 21, whereby the wire connection (5) also includes one or more light conductors, especially for the bidirectional transmission of data by light signals between the extraocular implant (3, 4) and the intraocular implant (6, 8) 23. Vision prosthesis according to one of the aspects 19 to 22, the wire connection (5) between the extraocular implant (3, 4) and the intraocular implant (6, 8) is designed as a flexible implant, preferably in the area of the parlance, which is directed from outside the eyeball (1) into the inner eye.24. prosthesis of vision according to one of the foregoing aspects, wherein the intraocular implant (6, 8) comprises a number of light-sensitive elements which, depending on the light incident on the intraocular implant (6, 8), direct the contact points of the electrode array (6) via the electrical circuit (3). 25. prosthesis of vision according to one of the foregoing aspects, wherein the intraocular implant (6, 8) comprises at least one light receiver (8) trained to receive light signals (20) from a light transmitter (10) from outside the eye (1), preferably via the natural light path of the eye (1).to receive, preferably, the natural light path of the eye (1).27 Vision prosthesis according to one of the aspects 25 or 26, where the interface (4, 18) between the light transmitter (10) outside the eye (1) and the light-sensitive elements or light-receiver (8) of the intraocular implant (6, 8) is formed, to transmit image data obtained by an external camera via light signals (20) from the light transmitter (10) outside the eye (1) to the light-sensitive elements or light-receiver (8) of the intraocular implant (6, 8) 28.Vision prosthesis according to one of the aspects 25 to 27, where the light-receiver (8) and the electrical circuit (3) are coupled via a wired connection capable of transmitting image data,preferably in the form of a serial data stream.29. prosthesis according to one of the aspects 25 to 28, where the light receiver (8) is positioned on the wire connection (5), preferably in the area of a nail (5) or on a branch (25) of the wire connection (5).30. prosthesis according to one of the previous aspects, where the intraocular implant (6, 8) includes at least one light-emitting element (19) that emits light signals depending on the operating parameters of the stimulation system.31. prosthesis according to aspect 30, where the light-emitting element (19) is positioned on the wire connection (5), a wire pulling element (9) is positioned in the area of fixation of the nail (5) or pre-positioned on a wire connection (25).Vision device according to one of the aspects 30 or 31, whereby the light signals emitted by the light-emitting element (19) are modulated, for example, by modulating the duration and/or intensity of the light signals, depending on the operating parameters of the intraocular implant (6, 8).33. Vision device according to aspect 32, whereby the light signals emitted by the light-emitting element (19) contain information on the position of the intraocular implant (6, 8), the quality of the image data received by the intraocular implant, the quality of the electrical supply to the intraocular implant (6, 8) and/or the impedance of the stimulation electrodes.34.that the light signals emitted by the light-emitting element (19) are detectable by an observer by visual contact.35. Vision prosthesis according to one of the aspects 30 to 34, where the light-emitting element (19) is designed as a diode, emitting light, in particular infrared light, detectable by a light receiver (10), in particular an infrared receiver outside the eye (1).37. vision prosthesis according to one of the aspects 4 to 36, where the antenna (18) of the extracorporeal part is placed in a glass frame (28).38 vision prosthesis according to one of the aspects 4 to 37, where the infrared receiver (8) of the extracorporeal part has a parabolic light-sensitive surface to receive the signals (2) emitted by the intraocular infrared transmitter (10).39 prosthesis according to one of the aspects 25 to 38, where the infrared transmitter (10) and/or the infrared receiver (8) and the antenna (18) of the extracorporeal part are placed together in a foreground.40 procedures for operating the device according to one of the aspects comprising the following steps:Capture an image by an external cameraGenerate from the image captured,resolved image data,calculate diagnostic,control or stimulation commands of a duration and intensity determined by the image data,transmit the diagnostic,control or stimulation commands to a stimulation system with an intraocular implant (6, 8) and an extraocular implant (4, 3),calculate and generate electrical stimulation pulses or currents of a duration and intensity determined in the extraocular implant (4, 3) or perform diagnostic tasks according to the diagnostic,control or stimulation commands,injecting electrical stimulation or intraocular stimulation (6, 8),or at least one electrical stimulation or stimulation (6, 8), into the intraocular implant (6, 8),or at least one intraocular stimulation or stimulation (6, 8),in the intraocular implant (6, 8),or at least one intraocular stimulation or stimulation (6, 8),in the intraocular stimulation or at least one intraocular stimulation.The procedure described in paragraph 40 whereby the image data captured by the external camera is electrically evaluated or processed to produce corresponding electrical stimulation pulses or currents before being transmitted to the stimulation system.42. The procedure described in paragraph 40 or 41, whereby the current required to operate the extraocular implant (3, 4) and the intraocular implant (6, 8) is transmitted via the bidirectional inductive interface (4, 18) between the high frequency transmitting antenna (18) outside the eye (1) and the high frequency receiving antenna (4) of the extraocular implant (3, 4) is described in paragraphs 40 to 42.the transmission of the image data or the transmission of the diagnostic, control or stimulation commands recorded by the external camera is carried out wirelessly via one or several separate transmission channels of the bidirectional inductive interface (4, 18) between the high frequency transmitting antenna (18) outside the eye (1) and the high frequency receiving antenna (4) of the extraocular implant (3, 4).44 Process according to one of the aspects 40 to 43, whereby the transmission of the image data or the transmission of the diagnostic, control or stimulation commands recorded by the external camera is carried out wirelessly via an infrared interface between (10) Augarot (1) outside the eye and the infrared antenna (4) within the eye.44 Process according to one of the aspects 44 to 44, whereby the transmission of the diagnostic, control or stimulation commands or the transmission of the image data or the diagnostic, control or stimulation commands is carried out wirelessly via an infrared interface between (10) Augarot (1) outside the eye and (1) Augarot (1) inside the eye.45 Process according to one of the aspects 44 to 44.the transmission of the image data or the transmission of the diagnostic, control or stimulation commands recorded by the external camera as a serial data stream from the infrared receiver (8) within the eye (1) via the wire link (5) to the digital control unit (3) in the extraocular implant (3, 4) is carried out.46. Method according to paragraph 45, where the serial data stream from the infrared receiver (8) within the eye (1) via the wire link (5) to the digital control unit (3) in the extraocular implant (3, 4) contains information on the address of the stimulation electrode, e.g. 1 to 250, and on the amplitude associated with the electrode address, e.g. 0 to 1000μA, where the relevant stimulation electrode is the stimulation electrode,Diagnostic commands, control commands and/or stimulation commands.48. Method according to Aspect 45, using information on the electrode address and amplitude of the stimulation pulses from the electrical control unit of the extraocular implant (3, 4) to calculate and generate for each stimulation electrode stimulation pulses or currents of specified duration and intensity.48. Method according to Aspect 47, whereby the stimulation pulses or currents from the electrical control unit (3) of the extraocular implant (3, 4) are transmitted as parallel signal currents via parallel wires (5) to the stimulation electrodes in the implant (4, 5) and the information is transmitted via the intraocular wires (3, 6, 8) to the intraocular wires of the implant (4, 5).5) preferably transmitted in a parallel data stream.50. procedure according to one of the aspects 43 to 49, whereby data transmission between the extracorporeal part and the intracorporeal part (3, 4, 6, 8) is simultaneous via separate transmission channels of the bidirectional inductive interface (4, 18).51. procedure according to one of the aspects 40 to 50, whereby the condition and functionality of the intracorporeal part (3, 4, 6, 8) of the prosthesis are constantly monitored via the bidirectional interface (4, 18) and in the event of failure of the prosthesis or of a transmission channel of the bidirectional inductive interface (4, 18) a malfunction corresponding to a malfunction is signalled.52. procedure according to aspects 40 to 51,where the data transmission from the extracorporeal part to the intracorporeal part (3, 4, 6, 8) and the data transmission from the intracorporeal part (3, 4, 6, 8) to the extracorporeal part are carried out alternately via a transmission channel of the bidirectional inductive interface (4, 18).53. Process according to one of the aspects 40 to 52, where the data transmission from the extracorporeal part to the intracorporeal part (3, 4, 6, 8) is carried out via the bidirectional inductive interface (4, 18) The stimulation commands contain information on electrode addresses, current amplitudes, phase durations, phase ratios and/or signatures of the stimulation current pulses for the stimulated electrodes.54.4, 6, 8) transmit data via the bidirectional inductive interface (4, 18) containing the instructions to measure voltage at one or more stimulation electrodes during stimulation, to measure voltage at one or more stimulation electrodes outside stimulation, to measure nerve action potentials using one or more stimulation electrodes and/or to measure nerve action potentials using special measuring electrodes and the instruction to transmit the measured values via the bidirectional inductive interface (4, 18) to the extracorporeal part of the optic nerve.55.18) data are transmitted which include commands to determine the status of the intracorporeal part (3, 4, 6, 8), to record certain state parameters, the identification number, a status overview, the status of the charge compensation systems, the state of the energy supply, the temperature of the intracorporeal part (3, 4, 6, 8) or of certain components and/or the moisture sensor measurement and the command to determine the measured excess values via the bidirectional inductive interface (4, 18) at the extracorporeal part of the prosthesis.56. procedure according to one of the aspects 40 to 55, whereby the data transmission between the intracorporeal part (3, 4, 6, 8) and the extracorporeal part via the bidirectional inductive interface (4, 18) is carried out by applying a Kodi,which has approximately equal number of zero states and one-state states.57. procedure according to one of the aspects 40 to 56, where the data transmission between the intracorporeal part (3, 4, 6, 8) and the extracorporeal part via the bidirectional inductive interface (4, 18) is carried out using a Manchester coding, 4PPM coding and/or 4PPM+ coding.58. procedure according to one of the aspects 40 to 57, where the data transmission between the intracorporeal part (3, 4, 6, 8) and the extracorporeal part via the bidirectional inductive interface (4, 18) is carried out by amplitude modulation of a carrier frequency, preferably using the 13,56 MHz ISM frequency band, the 27,12 MHz ISM frequency band, the 125 kHz ISM frequency band or the 433 MHz ISM frequency band.59 Processes in one of the aspects 40 to 58, where the data transmission between the intracorporeal part (3, 4, 6, 8) and the extracorporeal part via the bidirectional inductive interface (4, 18) is by frequency modulation, phase modulation of a carrier frequency or a combination of these modulation methods. 60 Processes in one of the aspects 40 to 59, where the data transmission between the intracorporeal part (3, 4, 6, 8) and the extracorporeal part via the bidirectional inductive interface (4, 18) uses a frequency-separated carrier frequency for inductive power supply modulated by amplitude modulation, frequency modulation, phase modulation or a combination of these modulation methods. 61 Processes in aspects 40 to 60, where the data transmission between the intracorporeal part (3, 4, 6, 8) and the extracorporeal part via the bidirectional inductive interface (4, 18) is by means of a frequency-separated carrier frequency modulated by amplitude modulation, frequency modulation, phase modulation or a combination of these modulation methods.data transmission between the intra-corporeal part (3, 4, 6, 8) and the extra-corporeal part via the bidirectional inductive interface (4, 18) by load modulation of the carrier frequency while switching on and off a resistive load, a capacitive load, an inductive load or a combination of these loads.62. Procedures according to one of the aspects 40 to 61, transmitting diagnostic data on the condition of the intra-corporeal part (3, 4, 6, 8) of the prosthesis via the bidirectional inductive interface (4, 18) from the intra-corporeal part (3, 4, 6, 18) to the extra-corporeal part, measurements of the electrode impedance of certain electro-optic stem electrodes, measurements of the electrical voltage attached to the stimulation electrodes and monitoring/duty data of the specific electrode stimulation.63. procedures according to one of the aspects 40 to 62, transmitting from the intracorporeal part (3, 4, 6, 8) to the extracorporeal part via the bidirectional inductive interface (4, 18) diagnostic data on the system status of a flow control in the intracorporeal part (3, 4, 6, 8) of the prosthesis, information on the correct transmission of data from the extracorporeal part to the intracorporeal part (3, 4, 6, 8) of the prosthesis, information on the correct initialization of the intracorporeal part (3, 4, 6, 8), on the correct reset of the system status, on the status of the energy supply, on the correct status of the component of the intracorporeal part (3, 4, 6, 8), on the failure of certain stimulation methods, on the correct execution of the charge balance between stimulation electrodes,Duration of charge balance between stimulation electrodes, status of electrical energy supply, voltage at stimulation electrodes at certain measuring points, diagnostic data on patient physiology, derivation of action potentials of individual nerve cells, derivation of total action potentials of nerve cells, temperature in the electronics of the intracorporeal part (3, 4, 6, 8), temperature at certain points of the eye, intraocular pressure, acceleration measurement of the intracorporeal part (3, 4, 6, 8) and/or humidity within the enclosure of the intracorporeal part (3, 4, 6, 8) including procedures following one of the aspects 40 to 63, the data transfer between the intracorporeal part (3, 4, 6, 8) and the intracorporeal part (3, 4)The method of Aspect 64, using Hamming coding, fold coding, repeat coding and/or other appropriate error-correcting methods as error-correcting methods.66, as one of Aspects 40 to 65, using an error-detection method for data transmission between the intra-corporate part (3, 4, 6, 8) and the extra-corporate part via the bi-directional inductive interface (4, 18) using different coding methods.67, as one of Aspects 40 to 65, using an error-detection method for data transmission between the intra-corporate part (3, 4, 6, 8) and the extra-corporate part via the bi-directional inductive interface (4, 18) as error-detection methods.whereby cyclic redundancy check (CRC) coding, parity check coding and/or repeat coding are used to detect errors in data transmission between the intra-corporal part (3, 4, 6, 8) and the extra-corporal part via the bidirectional inductive interface (4, 18) using one of the aspects 40 to 67, whereby data transmission from the extra-corporal part via the bidirectional inductive interface (4, 18) to the intra-corporal part (3, 4, 6, 8) is carried out at a data rate in the range of 100 kilobits/second to 10 megabit/second or at a data rate in the range of 1 megabit/second to 2 megabit/second.69.where the data transmission from the intracorporeal part (3, 4, 6, 8) via the bidirectional inductive interface (4, 18) to the extracorporeal part is at a data rate in the range of 1 KiloBit/s to 100 KiloBit/s or at a data rate in the range of 10 KiloBit/s.70. Method according to one of the aspects 40 to 69, where the data transmission from the extracorporeal part via the bidirectional inductive interface (4, 18) to the intracorporeal part (3, 4, 6, 8) and the data transmission from the intracorporeal part (3, 4, 6, 8) via the bidirectional inductive interface (4, 18) to the extracorporeal part is at different data rates.