JP2009082496A - Sight regeneration aid - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a sight regeneration aid which improves the durability of long-time implantation and appropriately gives electric stimulations. <P>SOLUTION: The sight regeneration aid is provided with electrodes formed on the respective tips of a plurality of lead wires formed on a prescribed board, and a control means to make the electrodes output electric stimulation pulse signals via the lead wires in order to electrically stimulate the cells or tissue composing the sight nerve system of a patient's sight. These electrodes consist of a first electrode with the shape of convex upward connected with the end of each lead wire on the board, and a second electrode larger than the first electrode in diameter and fitted to the end of the first electrode. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a visual reproduction assisting device for reproducing the vision of a patient.

In recent years, as one of the techniques for treating blindness, research on visual regeneration assisting devices that attempt to regenerate vision by implanting in-vivo devices with a substrate on which multiple electrodes are formed and electrically stimulating cells that make up the retina Has been. Such a visual reproduction assist device, for example, converts an image captured using an extracorporeal device into a predetermined signal and transmits it to an in-vivo device installed in the body, outputs a stimulation pulse signal from the electrode, and An apparatus that attempts to reproduce vision by electrically stimulating constituent cells is known (see, for example, Patent Document 1).
JP 2003-230590 A

  Such a device requires an electrode that has durability to withstand long-term implantation in the body and that can suitably stimulate the cells that make up the retina. In the apparatus of Patent Document 1, since the electrode is usually manufactured by a thin film forming method, it is difficult to give the electrode a thickness and it is difficult to increase the surface area of the electrode. As a result, there is a problem that the amount of current that can be output is limited and it is difficult to perform electrical stimulation suitably.

  In view of the above-described problems of the prior art, it is an object of the present invention to provide a visual reproduction assisting device that can improve the durability of long-term implantation and can suitably perform electrical stimulation.

In order to solve the above technical problem, the present invention is characterized by having the following configuration.
(1) The electrodes formed on the tips of a plurality of conductors formed on a predetermined substrate, and the cells or tissues constituting the visual nervous system that forms the vision of the patient via the conductors for electrical stimulation. And a control means for outputting an electrical stimulation pulse signal from the electrode, wherein the electrode is connected to a leading end of the conducting wire and formed in a convex shape on the substrate, and the first electrode The second electrode is larger than the diameter of the electrode, and the second electrode is joined to the tip of the first electrode.
(2) In the visual reproduction assisting device according to (1), the second electrode is formed with a recess or a through hole for fitting with at least a tip of the first electrode, and the second electrode is formed on the first electrode. It is characterized by being integrated as one electrode by caulking in a state of fitting.
(3) In the visual reproduction assisting device according to (1), the second electrode is clamped to a tip portion of the first electrode, whereby the substrate is sandwiched between the first electrode and the second electrode. Features.
(4) In the visual reproduction assisting device according to (1), the first electrode is a columnar member penetrating the flexible substrate and a base formed at a base portion of the columnar member, and the first electrode extends from the substrate. It is characterized by comprising a base formed in a size that prevents the falling off of the base.
(5) In the visual reproduction assisting device according to (1), the conductive wire is covered with a material having biocompatibility and insulating properties.
(6) In the visual reproduction assisting device according to (1), the substrate sandwiches the first electrode between the first substrate having a through-hole through which the tip of the first electrode passes, and the first substrate. It is characterized by comprising a second substrate.
(7) In the visual reproduction assisting device according to (6), the conducting wire is covered with a material having biocompatibility and insulating properties, and the conducting wire is connected to a tip of the first electrode. And being sandwiched between the first substrate and the second substrate.

  According to the present invention, durability of long-term implantation can be improved and electrical stimulation can be suitably performed.

  Embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a schematic diagram showing an external appearance of a visual reproduction assistance device, and FIG. 2 is a diagram showing an in-vivo device in the visual reproduction assistance device.

  As shown in FIGS. 1 and 2, the visual reproduction assisting device 1 includes an extracorporeal device 10 for photographing the outside world, and an in-vivo device 20 that promotes visual reproduction by applying electrical stimulation to cells constituting the retina. The extracorporeal device 10 includes a visor 11 on which a patient is placed, an imaging device 12 including a CCD camera attached to the visor 11, an external device 13, a transmission unit 14 including a primary coil, and the like.

  The external device 13 is provided with a data modulation means 13a having an arithmetic processing circuit such as a CPU, and a battery 13b for supplying power to the visual reproduction auxiliary device 1 (external device 10 and internal device 20). The data modulation unit 13a performs image processing on the subject image captured by the image capturing device 12, and further converts the obtained image processed data into electrical stimulation pulse data for reproducing vision. The transmission means 14 transmits the electrical stimulation pulse data converted by the data modulation means 13a and the power for driving the in-vivo device 20 described later to the in-vivo device 20 side as a predetermined signal, in this embodiment, an electromagnetic wave ( Wireless transmission). On this electromagnetic wave, electrical stimulation pulse data and power are superimposed. A magnet (not shown) is attached to the center of the transmission means 14. The magnet is used to fix the position with the receiving means 31 described later.

  The visor 11 has an eyeglass shape, and can be used by being mounted in front of the patient's eyes as shown in FIG. The photographing device 12 is attached to the front surface of the visor 11 and can photograph a subject to be visually recognized by the patient.

  Next, the configuration of the intracorporeal device 20 will be described. 2A shows an external appearance of the in-vivo device 20, and FIG. 2B shows a cross section of the stimulation unit 40. As shown in FIG. The in-vivo device 20 is roughly divided into a receiving unit (receiving unit) 30 that receives data and electric power for electrical stimulation pulse signals transmitted from the extracorporeal device 10 by electromagnetic waves, and a stimulating unit (stimulating unit) that electrically stimulates cells constituting the retina. ) 40. The receiving unit 30 is provided with a receiving unit 31 including a secondary coil that receives electromagnetic waves from the extracorporeal device 10 and a control unit 32. The control unit 32 separates the electrical stimulation pulse data and the power received by the receiving unit 31, and based on the electrical stimulation pulse data, an electrical stimulation pulse signal for obtaining vision, an electrical stimulation pulse signal, It has a role for converting to a control signal including an electrode designation signal for designating a corresponding electrode (for outputting an electrical stimulation pulse signal) and transmitting the control signal to the stimulation unit 40.

  These receiving means 31 and control unit 32 are formed on a substrate 33. The receiving unit 30 is provided with a magnet (not shown) for fixing the position of the transmitting unit 14. The counter electrode (return electrode) 34 is a member for opposing each electrode 44 to efficiently electrically stimulate cells and the like.

  The stimulation unit 40 includes a plurality of electrodes 44 that output electrical stimulation pulse signals, a stimulation control unit 42 (control means), and a substrate 43 on which these are installed. Each electrode 44 is connected to the stimulation control unit 42 by a manufacturing method (connection form) described later (details will be described later). The stimulation control unit 42 has a multiplexer function that distributes the corresponding electrical stimulation pulse signal to each of the electrodes 44 based on the control signal (including the electrode designation signal) sent from the control unit 32. For the electrode 44, a metal having high biocompatibility, for example, gold, platinum, titanium nitride, iridium oxide, or the like is used. Each electrode 44 has an outer diameter of 100 to 500 μm and a height of 100 to 500 μm. Since the substrate 43 used in the present embodiment is installed in the eye, particularly in a layered eye tissue, it preferably conforms to the shape of the eyeball, and even if it is implanted in the interlayer (in the layer) for a long period of time, it is a burden on the patient. It is preferable that there is little. For this reason, the board | substrate 43 uses what was processed into the flat plate shape extended in the longitudinal direction, such as parylene, a polypropylene, a polyimide, etc., which has high biocompatibility, and was bendable (flexible) in predetermined thickness. The thickness of the substrate 43 is 10 to 100 μm. On this substrate 43, a wire 41, which is a conductive wire that electrically connects the electrode 44 and the stimulation control unit 42, is disposed. The wire 41 is formed from a metal having high biocompatibility, such as gold or platinum, and the surface thereof is covered with a material having biocompatibility and insulation properties, such as a resin such as parylene or polyimide. The thickness (diameter) of the wire 41 is set to a thickness preferable for the flexibility and long-term installation of the substrate 43, for example, 10 to 100 μm. The stimulation control unit 42 mounted on the substrate 43 is connected to a plurality of electrodes 44 formed on the substrate 43 through wires 41. Since the wire 41 is covered with the substrate 43 by a method for manufacturing the electrode 44 described later, the metal portion of the wire 41 is doubly covered with an insulating coating, so that infiltration of body fluid or the like is infiltrated into the wire 41 portion. However, the possibility of leakage etc. is reduced.

  The stimulus control unit 42 is a semiconductor integrated circuit that performs a function by a combination of semiconductor elements, and is bonded to the surface of the semiconductor substrate on which the pattern wiring for functioning the integrated circuit is formed. Although detailed description is omitted, the stimulus control unit 42 is covered with plating or the like to reduce infiltration from a living body. The stimulus control unit 42 may be configured to be sealed using an airtight case formed of ceramics or metal. In such a case, the stimulus control unit 42 is connected to the wire 41 via a via provided in the case.

  In addition, the receiving unit 30 and the stimulating unit 40 placed at positions separated from each other in the body are electrically connected by a plurality of wires (conductive wires) 50. The wire 50 preferably has elasticity and durability corresponding to eye movement when placed in the body, and is made of the same material as the wire 41 described above. The wire 50 having one end connected to the receiving unit 30 is connected to the end portion of the wire 41 arranged in the stimulating unit 40. Although detailed description is omitted, the wire 50 and the wire 41 are connected by welding, pressure bonding, or the like. Further, the wire 50 is housed in a cable 51 made of a material having high biocompatibility, for example, silicone, parylene, etc. so as to be easily handled.

  In addition, although illustration is abbreviate | omitted, the receiving part 30 takes out the cable 51 and the counter electrode 34, is accommodated in a highly airtight container, and the lid | cover of the container is sealed. Furthermore, it is coated from above the container with a resin having good biocompatibility and insulating properties. Thereby, the receiver 30 is hermetically sealed.

  Next, the electrode 44 will be described. FIG. 3 is a schematic sectional view of the vicinity of the electrode 44. The electrode 44 is formed by joining two electrode members. FIG. 4 is a diagram showing stepwise a method for manufacturing the electrode 44 (a method for connecting the electrode 44 and the wire 41). In the figure, the scale of each member is schematic for ease of explanation.

  The substrate 43 includes a base portion 43a serving as a first substrate and a cover portion 43b serving as a second substrate. Between the base portion 43a and the cover portion 43b, a base 45 serving as a first electrode and The wire 41 connected to the pedestal 45 is sandwiched. The pedestal 45 includes a base part 43a formed in a flat plate shape and a base part 45a sandwiched between the cover part 43b, and a column member 45b extending in a columnar shape (convex shape) with the base part 45a as a base part. The pedestal 45 is biocompatible and is formed of a plastic or malleable conductor, for example, a metal such as platinum or gold. The length of the column member 45b (the height of the column) is longer than the thickness of the base portion 43a and protrudes longer than a washer (washer, eyelet) 46 described later. The distal end portion of the column member 45b penetrates the base portion 43a and protrudes from the substrate 43 (base portion 43a), and serves as an axis for caulking a washer 46 described later. The column member 45b is preferably formed in a tapered shape that tapers toward the tip. Thereby, it becomes easy to fit the washer 46 mentioned later to the pillar member 45b. The outer diameter D2 of the base 45a is made larger than the outer diameter D1 of the column member 45b, and has a role of preventing the base 45 from falling off the base portion 43a (substrate 43). The wire 41 is connected to the base 45a.

  The washer 46 is a columnar annular member that serves as a second electrode and has a through hole 46a through which the column member 45b passes. Further, the outlet of the through hole of the washer 46 has a mortar shape, and when the column member 45b is crushed, the tip of the column member 45b is pushed and expanded along the mortar shape. As with the base 45, the washer 46 is biocompatible and is formed of a plastic or malleable conductor, for example, a metal such as platinum or gold. The washer 46 is preferably made of the same material as the pedestal 45. As shown in the drawing, the washer 46 sandwiches the base portion 43 a with the pedestal 45. The pedestal 45 and the washer 46 are deformed and integrally connected to form the electrode 44. The outer diameter of the electrode 44 is preferably 100 to 500 μm, and the height of the portion protruding from the substrate 43 is preferably 100 to 300 μm. The pedestal 45 and the washer 46 are formed by pressing or cutting.

Next, a method for manufacturing the electrode 44 will be described with reference to FIG. In the step shown in FIG.
The wire 41 is connected to the base 45 a of the base 45. For this connection, welding techniques such as laser welding and resistance welding are used. At this time, the welded portion of the wire 41 is mechanically connected and electrically connected to the pedestal 45 and the wire 41 because the resin coating is removed by heat during welding. The length of the column member 45b is about 400 to 700 μm, and the outer diameter D1 is about 30 to 300 μm. The connection between the pedestal 45 and the wire 41 may be a mechanical connection using a crimping process (plastic deformation process) or the like. With the pedestal 45 and the wire 41 thus connected, the column member 45b of the pedestal 45 is then passed through the through hole 43c of the resinous base portion 43a produced in a flat plate shape (see FIG. 4B). The through hole 43c is formed to a size that allows the column member 45b to pass through by laser processing or machining. The through holes 43c are formed at predetermined positions in the base portion 43a by the number of the electrodes 44 (base 45). In this embodiment, the wire 41 and the pedestal 45 are connected to each other. However, the present invention is not limited to this. A conductive wire is formed in advance in the base portion 43a, and a pedestal is attached by opening a through hole at the tip. It can also be done.

  Next, with the base 45 attached to the base portion 43a, a flat plate-like cover portion 43b having flexibility is formed on the base 45a side using the same kind of resin as the base portion 43a by using a vapor deposition method or the like. (See FIG. 4C). At this time, in order not to form a resin layer at the tip of the column member 45b, the tip is masked or a resin layer is formed only on the base 45a side of the base portion 43a. In this way, the base 45a and the wire 41 are sandwiched (embedded) by the base portion 43a and the cover portion 43b, and the column member 45b is formed in a convex shape on the substrate 43. Further, since the outer diameter D2 of the base 45a is formed larger than the diameter of the through hole 43c, the pedestal 45 does not fall off the substrate 43. In this way, a substrate 45 in which the pedestal 45 to which the wire 41 is connected is disposed on the substrate 43 is manufactured.

  Next, the washer 46 is fitted to the tip of the column member 45b (base 45) (see FIG. 4D). The outer diameter D3 of the washer 46 is formed sufficiently larger than the outer diameter D1 of the column member 45b. The diameter D4 of the through hole 46a (the inner diameter of the washer 46) is preferably a diameter that allows the column member 45b to pass therethrough as little as possible (a diameter slightly larger than the outer diameter D1). The outer diameter D3 of the washer 46 is 300 to 700 μm, and the height (length in the hole direction) of the washer 46 is 300 to 500 μm.

  When the washer 46 is fitted to the column member 45 b, the tip of the column member 45 b protrudes from the upper surface of the washer 46 in a state where one end (bottom surface) of the washer 46 is in contact with the base portion 43 a. In this state, the other end (the upper portion in the figure) of the washer 46 and the tip end of the column member 45b are pressed, and the washer 46 is caulked with the column member 45b as an axis (support) in a state where the column member 45b is crushed. Then, the base 45 and the washer 46 are integrated, and an electrode 44 as shown in FIG. Further, by repeating this step, a plurality of electrodes 44 are formed on the substrate 43 as shown in FIG. At this time, since the washer 46 is pressed and fixed to the base portion 43a, body fluid or the like hardly infiltrates between the base portion 43a and the washer 46. For this reason, even if the through-hole 43c is formed to be large to some extent, the body fluid or the like hardly infiltrates into the substrate 43. At this time, the column member 45b is contracted in the direction of the base 45a and extended in the side direction (in the direction of the washer 46), and the column member 45b and the washer 46 are brought into close contact with each other. For this reason, there may be a slight gap between the column member 45 b and the washer 46. Thereby, the outer diameter of the electrode 44 is set to 100 to 500 μm, and the height of the portion protruding from the substrate 43 is set to 100 to 300 μm. Such an electrode 44 has a larger surface area than the thin film electrode having the same diameter and can pass a sufficient current. In addition, it is not easy to produce an electrode having a size like the electrode 44 by repeatedly forming a thin film layer by a thin film forming method.

  As described above, one electrode (bulk electrode) 44 having a large surface area (large volume) is produced on the substrate 43 from the base 45 and the washer 46. As a result, even if the stimulation unit 40 is implanted in the body for a long period of time and an electrical stimulation pulse signal is continuously output from the electrode 44 and a part of the electrode 44 is dissolved by an electrochemical reaction or the like, the surface area (volume) of the electrode 44 is Almost no change. Accordingly, even during long-term implantation, an electrical stimulation pulse signal with a sufficient amount of current can be output from the electrode 44 (a sufficient amount of charge can be injected), and cells and the like can be electrically stimulated. Further, by adopting such a configuration, the size and shape of the washer 46 as the second electrode can be arbitrarily set without changing the size and shape of the pedestal 45 as the first electrode. Size and shape.

  Further, when compared with a thin film electrode having the same diameter, the electrode 44 is produced by projecting three-dimensionally on the substrate 43, so that it has a large surface area and a large contact area with cells and the like. Here, since the amount of charge that can be injected by the electrode is proportional to the surface area of the electrode, the amount of charge that can be injected from the electrode 44 can be increased by increasing the surface area of the electrode 44. Thereby, a cell etc. can be electrically stimulated suitably.

  Further, when the electrical stimulation pulse signal having the same charge amount is output by the electrode 44 and the thin film electrode, the electrode 44 having a larger surface area can reduce the charge density. For this reason, an electrode with a large surface area is less likely to concentrate charges on specific cells or the like, even with the same amount of electrical stimulation as in the case of a thin film electrode. Therefore, by increasing the surface area of the electrode, the burden on cells and the like due to electrical stimulation can be reduced.

  Moreover, it is preferable that the visual resolution (resolution) perceived by the patient is improved. Therefore, it is necessary to arrange the electrodes at high density while reducing the range of cells and tissues that are electrically stimulated by one electrode. For this reason, it is necessary to increase the surface area of the electrode while reducing the diameter of the electrode as much as possible. In response to this, the outer diameters of the base 45 and the washer 46 used in the method for manufacturing the electrode 44 described above are reduced, and the heights of the column member 45b and the washer 46 are increased. As a result, an electrode 44 having a small diameter and a long protrusion length onto the substrate 43 can be produced. Thereby, while the range which one electrode stimulates can be made small, the density of the electrode 44 arrange | positioned on the board | substrate 43 can be improved, and the visual resolution which a patient perceives can be improved.

  In addition, since the electrode 44 has a large surface area, it is possible to inject an equivalent amount of charge with the same charge density in a shorter time compared to the injection of charge using a thin film electrode. For this reason, the time width of the electrical stimulation pulse signal can be shortened, and the stimulation frequency can be increased. Thereby, the visual temporal resolution (frame rate) perceived by the patient can be increased.

  In the above description, the through hole 46a is provided in the washer 46, which is the second electrode, but the present invention is not limited to this. The tip of the pedestal 45 (the column member 45b) that is the first electrode may be configured to fit into the member that becomes the second electrode, and may be a recess or the like instead of the through hole. A modification example of the present invention will be described with reference to FIG. FIG. 7 is a schematic cross-sectional view for explaining a modification of the electrode manufacturing method. In the modification example, a cap 47 having a recess is used instead of the washer 46. The outer diameter of the cap 47 is formed in the same manner as the outer diameter D3 of the washer 46, and the diameter D8 of the recess is formed in the same manner as the diameter D4 of the through hole of the washer 46. The electrode can also be integrally formed by pressing and crimping the periphery of the cap 47 toward the center with the column member fitted in the recess.

  In the present embodiment described above, the electrode 44 having a large surface area is manufactured by crimping (plastically deforming) the washer 46 after fitting the pedestal 45 and the washer 46. The electrode having a larger diameter than that of the first electrode can be formed by joining the second electrode having a larger diameter than the diameter of the first electrode that can be directly formed on the substrate to the first electrode. It suffices if it can be manufactured.

  In the above description, the electrode has a columnar portion protruding from the substrate, but is not limited to this shape. The electrode may have any shape as long as it is suitable for electrical stimulation. The shape of the electrode can be changed by changing the shape of the pedestal, washer or cap, and by changing the method of crimping in the caulking process of the pedestal and washer. For example, in caulking, a concave mold or the like is used to press the tip of the electrode so as to have a roundness. Thereby, the tip of the electrode can be hemispherical. With such a configuration, the electric charge is less likely to be biased to the corners of the electrodes during electrical stimulation. For this reason, electric charges are evenly discharged from the electrode 44, and the cells and the like around the electrode 44 are evenly electrically stimulated. In other words, since the charge is not concentrated on a specific portion of one electrode, the burden on the cell or the like is reduced.

  FIG. 5 is a schematic view showing a state in which the stimulating unit 40 is implanted in the eye. The counter electrode 34 is placed at a position near the anterior eye part in the center of the eye as shown in the figure. As a result, the retina E1 is positioned between the electrode 44 and the counter electrode 34 (counter electrode). The electrical stimulation pulse signal current from the electrode 44 efficiently penetrates the retina.

  On the other hand, the receiving means 31 is installed at a predetermined position in the living body that can receive signals (electric stimulation pulse data and power) from the transmitting means 14 provided in the extracorporeal device 10. For example, as shown in FIG. 1, the receiving unit 30 (only the receiving unit 31 is shown in the figure) is embedded under the skin of the patient's temporal region and transmitted to a position facing the receiving unit 30 through the skin. The means 14 is installed. Since the magnet is attached to the receiver 30 in the same manner as the transmitter 14, the transmitter 14 and the receiver 30 are attracted by the magnetic force by positioning the transmitter 14 on the implanted receiver 30. The transmission means 14 is held on the temporal region.

  The cable 51 in which the wires 50 are bundled extends from the receiving unit 30 embedded in the temporal region under the skin toward the patient's eye along the temporal region, and is inserted into the eye socket through the inside of the patient's upper eyelid. As shown in FIG. 5, the cable 51 placed in the eye socket passes through the outer side of the sclera E <b> 3 and is connected to the stimulation control unit 42 installed on the substrate 43.

  In the present embodiment, the position where the intracorporeal device 20 (stimulation unit 40) is installed is located on the sclera E3 side, and the cells constituting the retina E1 are electrically stimulated from the sclera E3 side (choroid side). However, it is not limited to this. It is only necessary that the electrode can be placed at a position where the cells constituting the retina of the patient's eye can be suitably stimulated at a site where the substrate on which the electrode is placed is preferably flexible. For example, an electrode and a substrate may be provided between the layers. The internal device is placed in the eye of the patient (on the retina or subretinal) and the tip of the substrate on which the electrode is formed is placed under the retina (between the retina and choroid) or on the retina. You can also.

  The operation of the visual reproduction assisting apparatus having the above configuration will be described with reference to the control system block diagram shown in FIG. The photographing data (image data) of the subject photographed by the photographing device 12 shown in FIG. 1 is sent to the data modulation means 13a. The data modulation means 13a converts the photographed subject into predetermined data parameters (electric stimulation pulse data) necessary for the patient to recognize, and further generates and transmits a modulation signal suitable for transmission as an electromagnetic wave. The electromagnetic wave is transmitted from the means 14 to the in-vivo device 20 side as electromagnetic waves.

  At the same time, the data modulation means 13a transmits the power supplied from the battery 13b to the in-vivo device 20 side together with the modulation signal as an electromagnetic wave having a band different from the band of the modulation signal (electric stimulation pulse data) described above. .

  On the in-vivo device 20 side, the modulation signal and power sent from the extracorporeal device 10 are received by the receiving means 31 and sent to the control unit 32. The control unit 32 extracts a signal in a band used by the modulation signal from the received signal, forms an electrical stimulation pulse parameter signal and a control signal based on the modulation signal, and generates a control signal as an electrode designation signal. It transmits to the stimulus control unit 42.

  The stimulus control unit 42 extracts power and a control signal based on the received signal. The stimulation control unit 42 distributes the electrical stimulation pulse signal supplied from the control unit 32 to each electrode 44 based on the control signal, and outputs it. The cells constituting the retina E1 are electrically stimulated by the electrical stimulation pulse signal output from each electrode 44, and the patient obtains vision (pseudo light sensation). The control unit 32 obtains electric power for driving the in-vivo device 20 by the receiving unit 31.

  In the embodiment described above, the substrate 43 is placed on the sclera E3 of the patient's eye and the retina E1 is electrically stimulated via the sclera E3. However, the present invention is not limited to this. Any structure may be used as long as it electrically stimulates cells or tissues constituting the visual nervous system that forms the vision of the patient. For example, a stimulation unit having an electrode for outputting an electrical stimulation pulse signal is arranged in the optic nerve head in the eye or the optic nerve part outside the eye, and a transmission unit for supplying power to the stimulation unit or sending a command signal is used for the subcutaneous part of the patient. It is good also as a structure which arrange | positions in a distant place and electrically stimulates an optic nerve. Alternatively, a stimulating unit having electrodes may be arranged in a tissue that performs higher-order visual processing of the visual nervous system such as the optic chiasm, outer knee, and cerebral cortex, and stimulates the cells that constitute each tissue. For example, in the case of the occipital lobe of the cerebral cortex, it stimulates pyramidal cells or the like, or stimulates the visual cortex V1, V2, etc. In the present embodiment described above, the image data from the imaging device is converted into a predetermined signal by the data modulation means, and the signal is sent from the transmission means to the inside of the body, and the signal from the extracorporeal device is received. An example of an external imaging type visual reproduction trapping device that includes an in-vivo device that receives an electrical stimulation pulse signal from each electrode based on the signal is given as an example. However, the present invention is not limited thereto. It may be an in-vivo imaging type visual reproduction auxiliary device in which an imaging device, data modulation means, etc. are implanted in the eye.

It is the schematic which showed the external appearance of the visual reproduction auxiliary | assistance apparatus. It is the schematic which showed the in-vivo apparatus of the visual reproduction assistance apparatus in this embodiment. 3 is a schematic cross-sectional view in the vicinity of an electrode 44. FIG. It is the figure which showed the procedure which produces the electrode 44 typically. It is the figure which showed the state which installed the in-vivo apparatus in the body. s It is the block diagram which showed the control system of the visual reproduction auxiliary | assistance apparatus in this embodiment. It is a figure explaining the modification of the preparation methods of the electrode.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Visual reproduction | regeneration assistance apparatus 10 External apparatus 20 In-vivo apparatus 30 Receiving part 31 Receiving means 32 Control part 34 Counter electrode 40 Stimulation part 41 Wire 42 Stimulation control part 43 Board | substrate 44 Electrode 45 Base 46 Washer 50 Wire 51 Cable

Claims (7)

Electrodes formed on the tips of a plurality of conductors formed on a predetermined substrate, and electricity from the electrodes via the conductors to electrically stimulate cells or tissues constituting the visual nervous system that forms the vision of the patient A visual reproduction assisting device comprising: control means for outputting a stimulation pulse signal;
The electrodes are a first electrode connected to the tip of the conducting wire and formed in a convex shape on the substrate, and a second electrode larger than the diameter of the first electrode, and the tip of the first electrode A visual reproduction assisting device comprising a second electrode to be joined. 2. The visual reproduction assisting device according to claim 1, wherein the second electrode is formed with a recess or a through hole for fitting with at least a tip of the first electrode, and the second electrode is fitted into the first electrode. A visual reproduction assisting device which is integrated as one electrode by caulking in a combined state. 2. The visual reproduction assisting device according to claim 1, wherein the second electrode clamps the substrate between the first electrode and the second electrode by being caulked to a tip portion of the first electrode. Visual reproduction assist device. 2. The visual reproduction assisting device according to claim 1, wherein the first electrode is a columnar member penetrating the flexible substrate and a base formed at a base portion of the columnar member, and the first electrode is dropped from the substrate. A visual reproduction assisting device comprising: a base formed in a size that prevents such a situation. 2. The visual reproduction assisting device according to claim 1, wherein the conducting wire is covered with a material having biocompatibility and insulating properties. 2. The visual reproduction assisting device according to claim 1, wherein the substrate includes a first substrate having a through-hole through which a tip end portion of the first electrode passes, and a second substrate sandwiching the first electrode with the first substrate. A visual reproduction assisting device characterized by comprising: 7. The visual reproduction assisting device according to claim 6, wherein the conducting wire is covered with a material having biocompatibility and insulating properties, and the conducting wire is connected to a tip of the first electrode, and is connected to the first electrode. A visual reproduction assisting device that is sandwiched between a substrate and a second substrate.

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