CN210355681U

CN210355681U - Retina prosthesis, implant device and flexible cable

Info

Publication number: CN210355681U
Application number: CN201920275308.5U
Authority: CN
Inventors: 戴聿昌; 庞长林; 迪迪埃·萨根; 张旭; 曾维波
Original assignee: Intellimicro Medical Co ltd
Current assignee: Intellimicro Medical Co ltd
Priority date: 2019-03-04
Filing date: 2019-03-04
Publication date: 2020-04-21
Anticipated expiration: 2029-03-04

Abstract

The utility model discloses a retina prosthesis, implantation device and flexible cable, wherein the flexible cable includes: a micro-electrode having a first mounting hole and an electrode region outside the first mounting hole; at least sixty stimulating electrodes which are arranged in the electrode area and are regularly arranged, and the end parts of the stimulating electrodes are exposed on one side surface of the microelectrode to be suitable for stimulating retina; and an abutting member having a second mounting hole corresponding to the first mounting hole and extending from the second mounting hole to the back surfaces of the plurality of stimulation electrodes, the abutting member being provided on the other side surface of the micro-electrode to transmit the force distribution obtained at the second mounting hole to the back surfaces of the plurality of stimulation electrodes. According to the utility model discloses flexible cable can make microelectrode atress even and can laminate in order to obtain more effective stimulation effect in order to obtain better in the retina.

Description

Retina prosthesis, implant device and flexible cable

Technical Field

The utility model belongs to the technical field of ophthalmology nerve stimulator technique and specifically relates to a retina prosthesis's flexible cable, have its implantation device and have this implantation device's retina prosthesis.

Background

In the related art, when the implantation device of the retinal prosthesis is implanted, only one retinal nail is usually implanted, so that only one fixed stress point is arranged on the micro electrode, and thus the other side opposite to the retinal nail is easy to tilt or uneven in stress, and further the distance between the part of the stimulating electrode on the micro electrode and the surface of the retina is larger, and finally the stimulating current with higher intensity is required to generate better visual perception effect.

Since the number of the stimulating electrodes in the microelectrode is generally dozens, hundreds or even thousands, if a large proportion of the stimulating electrodes need large stimulating current, the total stimulating current is increased, which not only consumes electric energy and reduces the battery service time, but also causes nerve damage or convulsion in severe cases.

SUMMERY OF THE UTILITY MODEL

The utility model discloses aim at solving one of the technical problem that exists among the prior art at least. Therefore, the utility model provides a retina prosthesis's flexible cable can guarantee that the distance between stimulating electrode and the retina surface is even to the injury of big stimulating current to the human body has been avoided.

The utility model also provides an implantation device of the retina that has above-mentioned flexible cable.

The utility model also provides a retina prosthesis with above-mentioned implantation device.

According to the utility model discloses retina prosthesis's flexible cable, include: a micro-electrode having a first mounting hole and an electrode region outside the first mounting hole; at least sixty stimulating electrodes which are arranged in the electrode area and are regularly arranged, and the end parts of the stimulating electrodes are exposed on one side surface of the microelectrode to be suitable for stimulating retina; and an abutting member having a second mounting hole corresponding to the first mounting hole and extending from the second mounting hole to the back surfaces of the plurality of stimulation electrodes, the abutting member being provided on the other side surface of the micro-electrode to transmit the force distribution obtained at the second mounting hole to the back surfaces of the plurality of stimulation electrodes.

According to the utility model discloses retina prosthesis's flexible cable supports through setting up and leans on the piece, can make microelectrode's atress even, and microelectrode can not the perk, has guaranteed that the distance between stimulation electrode and the retina surface is even to avoided big stimulation current to lead to the injury to the human body, also increased microelectrode's life simultaneously.

According to some embodiments of the invention, the abutment member comprises at least: a first end and a second end, wherein the second mounting hole is located at the first end; at least one connecting section connected between the first end portion and the second end portion, the connecting section being configured in a linear shape, a zigzag shape, or a curved shape.

According to some embodiments of the invention, the abutment further comprises at least one tree-like segment extending from the connecting segment to an edge of the microelectrode.

According to some embodiments of the invention, the connecting section is straight; the tree segments are two or more in number and are configured to be symmetrical with respect to the connection segment.

According to some embodiments of the invention, the connecting section comprises a first straight section and a second straight section connected thereto, the first straight section having a width greater than the second straight section; the tree-shaped segments comprise a plurality of tree-shaped segments, and the tree-shaped segments extend outwards from the connection position of the first straight line segment and the second straight line segment respectively.

According to some embodiments of the invention, the abutment member and the microelectrode are both formed substantially in a spherical shape, and the radius of curvature of the abutment member is greater than or equal to the radius of curvature of the microelectrode.

According to some embodiments of the utility model, the electrode zone has a plurality of electrode holes, a plurality of stimulation electrodes are established respectively in the electrode hole, the tip of stimulation electrode sink in the electrode hole or part surpass the electrode hole and expose in the microelectrode.

According to some embodiments of the invention, the microelectrode further comprises a clamping end portion located at a side of the electrode region remote from the first mounting hole.

According to a second aspect of the present invention, there is provided a retinal implantation device, comprising: the flexible cable according to the above-described first aspect of the present invention; a fixing member fixing the micro-electrode of the flexible cable to a retina through the first and second mounting holes; electronics having a chip connected to the lead-in portion to drive the plurality of stimulation electrodes; a first wireless annunciator connected to the electronic device to receive image information obtained from the outside and to transmit the image information to the chip within the electronic device.

According to a third aspect of the present invention, a retinal prosthesis comprises: the retinal implantation device according to the second aspect of the present invention; an external device, the external device comprising: the camera shooting device comprises a camera shooting unit, a video processing unit and a second wireless annunciator, wherein the camera shooting unit is electrically connected with the video processing unit, the video processing unit is electrically connected with the second wireless annunciator, and the second wireless annunciator is electrically connected with the first wireless annunciator.

Additional aspects and advantages of the invention will be set forth in part in the description which follows and, in part, will be obvious from the description, or may be learned by practice of the invention.

Drawings

The above and/or additional aspects and advantages of the present invention will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:

fig. 1 is a schematic view of a flexible cable according to a first embodiment of the present invention;

FIG. 2 is a schematic rear view of the flex cable shown in FIG. 1;

FIG. 3 is a schematic view of a microelectrode portion of the flexible cable shown in FIG. 2;

FIG. 4 is a schematic view of a microelectrode portion of a flexible cable according to a second embodiment of the present invention;

FIG. 5a is a schematic view of a microelectrode portion of a flexible cable according to a third embodiment of the present invention;

FIG. 5b is a schematic view of a microelectrode portion of a flexible cable according to a fourth embodiment of the present invention;

FIG. 5c is a schematic view of a microelectrode portion of a flexible cable according to a fifth embodiment of the present invention;

FIG. 5d is a schematic view of a microelectrode portion of a flexible cable according to a sixth embodiment of the present invention;

FIG. 6 is a longitudinal sectional view of a microelectrode portion of the flexible cable shown in FIG. 1;

FIG. 7 is a schematic view of the flexible cable shown in FIG. 1 after implantation into an eye;

FIG. 8a is a cross-sectional view of the flexible cable of FIG. 7 implanted in an eyeball;

FIG. 8b is a schematic view of a microelectrode and an abutment according to an embodiment of the present invention;

FIG. 8c is a schematic view showing the change from the unstressed state (shown by the solid line) to the stressed state (shown by the dotted line) of the microelectrode and the abutment according to the embodiment of the present invention;

figure 9 is a schematic view of a fixation element in an implant device according to an embodiment of the present invention;

fig. 10 is a schematic view of a retinal prosthesis according to an embodiment of the present invention.

Reference numerals:

a flexible cable 100;

microelectrodes 110; a first mounting hole 111; electrode regions 112; an electrode aperture 1121;

a flexible substrate 113; a clamping end 114; a chamfer 115;

a stimulation electrode 120;

an abutting member 130; a first end portion 131; a second mounting hole 1311; a second end portion 132;

a connecting section 133; a first straight line segment 1331; a second straight line segment 1332; a tree segment 134;

a first tree segment 1341; a second tree segment 1342;

an introduction portion 140; a connecting portion 150; a conductive line 151;

an implant device 1000; a fixing member 200;

a rod portion 210; an elastic member 220; a stopper 230; a nail head 240;

an electronic device 300; a first wireless annunciator 400;

a retina 2000; a retinal nerve disk 2100;

an eyeball 3000;

an external device 4000; an image pickup unit 4100; a video processing unit 4200; the second wireless signal 4300.

Detailed Description

Embodiments of the present invention are described in detail below, and the embodiments described with reference to the drawings are exemplary.

A flexible cable 100 for a retinal prosthesis according to an embodiment of the present invention is described below with reference to fig. 1-10.

As shown in fig. 1-6, a flexible cable 100 of a retinal prosthesis according to an embodiment of the present invention includes: a microelectrode 110, at least sixty stimulation electrodes 120, an abutment 130, an introduction section 140 and a connection section 150.

As shown in fig. 1, the micro-electrode 110 has a first mounting hole 111 and an electrode region 112 outside (e.g., right side in fig. 1) the first mounting hole 111. The electrode region 112 is located substantially at the center of the micro-electrode 110, and the first mounting hole 111 is located at one end (e.g., the left end in fig. 1 to 5 d) of the micro-electrode 110. A fixing member 200 may be installed in the first installation hole 111 to effectively fix the micro-electrode 110 on the surface of the retina 2000. The micro-electrodes 110 may include a flexible substrate 113, and the flexible substrate 113 may function to support and protect the stimulation electrodes 120. Alternatively, the first mounting hole 111 on the flexible substrate 113 may be formed by patterning through a MEMS process, or may be implemented by machining or the like.

At least sixty stimulating electrodes 120 are disposed in the electrode region 112 of the micro-electrode 110 and arranged regularly, and ends of the stimulating electrodes 120 are exposed to one side surface of the micro-electrode 110 to be suitable for stimulating the retina 2000. Electrode regions 112 on the microelectrodes 110 and at least sixty stimulation electrodes 120 disposed within the electrode regions 112 are typically disposed proximate to a stimulated portion of the eyeball 3000, such as the macular region. Here, it should be noted that the above-mentioned "exposure" is understood to mean that the ends of at least sixty stimulation electrodes 120 are visible from the above-mentioned one side of the micro-electrode 110, and in this case, the ends of at least sixty stimulation electrodes 120 may protrude from the above-mentioned one side surface of the micro-electrode 110, may be flush with the above-mentioned one side surface of the micro-electrode 110, or may be sunk into the above-mentioned one side surface of the micro-electrode 110. It will be appreciated that more stimulation electrodes 120 may be arranged according to different needs, for example hundreds or thousands of stimulation electrodes 120 may also be arranged.

As shown in fig. 6, the abutting member 130 has a second mounting hole 1311 corresponding to the first mounting hole 111, and extends from the second mounting hole 1311 to the rear surface of the plurality of stimulation electrodes 120. Referring to fig. 2 to 5d in combination with fig. 6, the abutment 130 is closely attached to the other side surface of the micro-electrode 110 (i.e., the other side surface of the micro-electrode 110 opposite to the above-mentioned side surface where the ends of the plurality of stimulation electrodes 120 are exposed) to transmit the force distribution obtained at the second mounting hole 1311 to the back surface of the plurality of stimulation electrodes 120. At this time, the abutment 130 and the above-mentioned ends of the plurality of stimulation electrodes 120 are exposed on both surfaces of the micro-electrode 110, respectively. When the abutting member 130 and the micro-electrode 110 are fixed through the first mounting hole 111 and the second mounting hole 1311, the force at the second mounting hole 1311 can be distributed and transmitted to the back of the plurality of stimulating electrodes 120 through the elastic deformation of the abutting member 130, so that the micro-electrode 110 is uniformly stressed, the tilting is not caused, and the mechanical damage of the retina 2000 caused by excessive local stress is not easy to occur. For example, in the example of fig. 6, the second mounting hole 1311 is aligned up and down with the first mounting hole 111, and the fixing member 200 may fix the micro-electrode 110 and the abutting member 130 on the surface of the retina 2000 through the first mounting hole 111 and the second mounting hole 1311 at the same time. The abutment 130 extends from the second mounting hole 1311 to the back of the plurality of stimulation electrodes 120. Here, the abutting member 130 may extend to the back of all the stimulation electrodes 120, and of course, may extend to only a part of the back of the stimulation electrodes 120.

From this, because microelectrode 110 only adopts a mounting 200 to fix, through set up on microelectrode 110 and lean on piece 130, can conduct the fixed pressure of mounting 200 to microelectrode 110 to the surface of electrode zone 112 for stimulating electrode 120, thereby make microelectrode 110's atress even, the condition that also can not have the perk takes place, and difficult emergence arouses retina 2000's mechanical force damage because local stress is too big, it is even to have guaranteed that the distance between stimulating electrode 120 and the retina 2000 surface is even, the electrostimulation effect has been improved relatively, the resolution ratio of increase electrostimulation, thereby avoided big stimulating current to lead to the injury to the human body, the power consumption has been reduced, the life of microelectrode 110 has also been increased simultaneously.

Alternatively, one end of the abutting member 130 and one end of the micro-electrode 110 may be fixedly connected by the fixing member 200, the other end of the abutting member 130 and the other end of the micro-electrode 110 may be connected by adhesion or the like, or both may be freely contacted. Of course, the two ends of the abutting member 130 and the micro-electrode 110 can be connected in advance by adhesion, and then the fixing member 200 can be inserted through the second mounting hole 1311 and the first mounting hole 111 to integrally mount the abutting member 130 and the micro-electrode 110 to the retina 2000.

Referring to fig. 1, 2 and 6, the lead-in portion 140 is adapted to connect to an electronic device. For example, the lead-in portion 140 may be used to connect chips within the electronic device 300, such as ASIC chips (application specific integrated circuits). The connection part 150 is connected between the micro-electrode 110 and the introduction part 140, and the connection part 150 includes a plurality of lead wires 151 respectively connected to the plurality of stimulation electrodes 120, so that each stimulation electrode 120 can be individually driven and electrical stimulation can be pertinently applied to a stimulated site such as the retina 2000. As shown in FIG. 7, the connection portion 150 is adapted to pass through a scleral incision in the wall of the eyeball and connect between the microelectrode 110 and the introduction portion 140. The plurality of conductive wires 151 in the connecting portion 150 may be disposed in the same layer (as shown in fig. 6) or may be disposed in multiple layers (not shown).

According to the utility model discloses retina prosthesis's flexible cable 100 supports through the setting and leans on piece 130, can make microelectrode 110's atress even, and microelectrode 110 can not the perk, has guaranteed that the distance between stimulation electrode 120 and the retina 2000 surface is even to avoided big stimulation current to lead to the injury to the human body, also increased microelectrode 110's life simultaneously. In addition, since there is only one first mounting hole 111 and one second mounting hole 1311, it is possible to use only one fixing member 200, thereby causing less damage to the wall of the eyeball and simplifying the surgical operation.

According to some embodiments of the present invention, as shown in fig. 2-5 d, the abutting member 130 at least includes: a first end 131, a second end 132, and at least one connecting segment 133 connected between the first end 131 and the second end 132, wherein the second mounting hole 1311 is located at the first end 131 of the abutting member 130. At this time, one end of the abutting member 130 is adapted to be fixed on the surface of the retina 2000 through the second mounting hole 1311.

Referring to fig. 2 to 5a, the connection segment 133 connected between the two ends of the abutting member 130 may be configured in a straight line shape, so that the abutting member 130 may extend to the back of the plurality of stimulating electrodes 120, and the acting force of the fixing member 200 may be transmitted to the other end of the abutting member 130, so that the whole abutting member 130 is uniformly stressed, the whole microelectrode 110 is uniformly stressed, it is ensured that the microelectrode 110 is not tilted, and the distance between the stimulating electrode 120 and the surface of the retina 2000 is uniform. In addition, by adopting the connecting section 133 in a straight shape, the processing of the abutting member 130 is facilitated, and the cost is reduced.

Of course, the present invention is not limited thereto, and the connection segment 133 may also be configured in a zigzag shape (as shown in fig. 5 b), or a curved shape (as shown in fig. 5 c). Through constructing the connecting section 133 into a zigzag line shape or a curve shape, the length of the connecting section 133 is relatively prolonged, so that the abutting part 130 can extend to the back surfaces of more stimulating electrodes 120, the stress of the microelectrode 110 can be more uniform, the uniformity of the distance between the stimulating electrodes 120 and the surface of the retina 2000 is further ensured, the damage to a human body caused by large stimulating current can be better avoided, and the service life of the microelectrode 110 is further prolonged.

According to a further embodiment of the present invention, referring to fig. 2 in combination with fig. 3 and 4, the abutting member 130 further comprises at least one tree-shaped segment 134, the tree-shaped segment 134 extending from the connecting segment 133 to the edge of the micro-electrode 110. Thus, by providing the tree-like segment 134 extending outwardly from any position of the connecting segment 133 and extending to the edge adjacent to the micro-electrode 110, the tree-like segment 134 can be diverged outwardly from approximately the central portion of the micro-electrode 110 to the edge portion of the micro-electrode 110, so that the stimulating electrode located at the central portion of the micro-electrode 110 can be brought into better proximity with the stimulated portion of the eyeball 3000 such as the macular region. Moreover, the tree-shaped segment 134 can make the whole leaning piece 130 extend to the back of more stimulating electrodes 120, so as to further ensure the uniform stress of the microelectrode 110, further ensure the uniformity of the distance between the stimulating electrode 120 and the surface of the retina 2000, further avoid the damage to the human body caused by the large stimulating current, and further prolong the service life of the microelectrode 110.

For example, 4 tree fragments 134 are shown in the examples of fig. 2 and 3, and 2 tree fragments 134 are shown in the example of fig. 4. 2, 4 tree segments 134 shown in fig. 2-4 are for illustrative purposes, but it is obvious to those skilled in the art after reading the technical solution of the present application that the solution can be applied to 3 or more than 4 tree segments 134, which also falls within the protection scope of the present invention.

Alternatively, as shown in fig. 2 to 4, the connection segment 133 is linear, and the number of the tree-shaped segments 134 is two or more, and is configured to be symmetrical with respect to the connection segment 133. Thus, by arranging the plurality of tree segments 134 to be symmetrical with respect to the connection segment 133, the stress uniformity of the micro-electrode 110 can be effectively secured, and the distance between the micro-electrode 110 and the surface of the retina 2000 can be further uniformly controlled.

Specifically, as shown in fig. 2 to 4, the connecting section 133 includes a first straight line segment 1331 and a second straight line segment 1332 connected thereto, the width of the first straight line segment 1331 is greater than that of the second straight line segment 1332; the tree segment 134 comprises a plurality of tree segments 134 extending outwardly from the junction of the first straight segment 1331 and the second straight segment 1332. For example, in the example of fig. 4, the plurality of tree segments 134 may include two first tree segments 1341, two first tree segments 1341 obliquely extend outward from a connection of the first straight line segment 1331 and the second straight line segment 1332, respectively, and two first tree segments 1341 obliquely extend toward a direction in which the second straight line segment 1332 is located.

Thus, the first straight line segment 1331 is made wider than the second straight line segment 1332, and the two first tree-like segments 1341 are obliquely extended from the connection point of the first straight line segment 1331 and the second straight line segment 1332 in the direction of the second straight line segment 1332, so that the manufacturing is simple and as many stimulation electrodes 120 as possible can be covered. Further, in the example of fig. 2-3, the tree segment 134 further includes two second tree segments 1342, and the two second tree segments 1342 respectively extend perpendicularly and outwardly from the connection of the first straight line segment 1331 and the second straight line segment 1332, and the abutting member 130 is formed substantially in a shape of "wood". Thereby, the micro-electrode 110 is further ensured to be uniformly stressed.

For example, one connection segment 133 is shown in each of the examples of fig. 5 a-5 c. However, it should be understood by those skilled in the art that the present invention is not limited thereto, and in other examples of the present invention, the connection segment 133 may further include at least two segments formed in a curved shape (as shown in fig. 5 d) or a zigzag shape (not shown), respectively, and the connection segment 133 passes at least adjacent to the edge of the micro-electrode 110. Further, the tree-like segments 134 may include at least one segment, and may be formed in a straight line, a polygonal line, or a curved shape, respectively, and the tree-like segments 134 may be distributed at the middle portion of the micro-electrode 110, as shown in FIG. 5 d. Thus, the uniformity of stress applied to the micro-electrode 110 can be also well secured.

According to some alternative embodiments of the present invention, referring to fig. 8b in combination with fig. 8c, the abutting member 130 and the micro-electrode 110 are both formed in a substantially spherical shape, and the radius of curvature of the abutting member 130 is greater than or equal to the radius of curvature of the micro-electrode 110. Of course, in other alternative embodiments of the present invention, the leaning component 130 may also be a curved surface shape that can generate elastic force when being applied with force, besides a spherical surface shape, and when being applied with force at the second mounting hole 1311, the elastic deformation can transmit the force to the back of the micro-electrode 110 in a uniform distribution.

For example, the abutting member 130 has a certain elasticity, and before the abutting member 130 and the micro-electrode 110 are fixed by the fixing member 200, the second mounting hole 1311 is not acted by the fixing member 200, as shown by a solid line in fig. 8c, and a gap is formed between the abutting member 130 and the micro-electrode 110; when the abutting member 130 and the micro-electrode 110 are fixed by the fixing member 200, the force applied by the fixing member 200 at the second mounting hole 1311 causes the abutting member 130 to be elastically deformed, so that the gap between the abutment 130 and the micro-electrode 110 is reduced, as shown by the dotted line in FIG. 8c, meanwhile, the force applied by the fixing member 200 at the second mounting hole 1311 may be transmitted to the rear surfaces of the plurality of stimulating electrodes 120, thereby ensuring that the stress of the microelectrode 110 is even, the situation of tilting can not occur, the mechanical force damage of the retina 2000 caused by overlarge local stress is not easy to occur, ensuring that the distance between the stimulating electrode 120 and the surface of the retina 2000 is even, relatively improving the electrical stimulation effect, increasing the resolution ratio of electrical stimulation, thereby avoiding the damage to the human body caused by large stimulating current, reducing the power consumption and simultaneously prolonging the service life of the microelectrode 110.

Optionally, the abutting member 130 and the micro-electrode 110 are of a separate structure. At this time, the abutment 130 and the micro-electrode 110 are separately formed and then connected by, for example, end bonding, or they are free to contact each other in use without being adhered in advance. Of course, the present invention is not limited thereto, and the abutting member 130 and the micro-electrode 110 may be integrally formed. Therefore, the structure is simple and the cost is low.

In some alternative embodiments, the material of the abutting member 130 may be silicone, Parylene, teflon, polyimide, poly (ethylene terephthalate), polyetheretherketone, stainless steel, titanium alloy, or other biocompatible polymer material or metal material.

According to some embodiments of the present invention, the electrode region 112 has a plurality of electrode holes 1121, the plurality of stimulation electrodes 120 are respectively disposed in the electrode holes 1121, and the ends of the stimulation electrodes 120 are sunk in the electrode holes 1121 or partially exceed the electrode holes 1121 and exposed out of the micro-electrode 110. For example, as shown in fig. 6, the end of the stimulating electrode 120 is sunk in the electrode hole 1121, and the top surface of the end of the stimulating electrode 120 is located below the top surface of the electrode hole 1121, and the gap between the top surface of the end of the stimulating electrode 120 and the top surface of the electrode hole 1121 is very small. Thereby, the distance between the micro-electrode 110 and the surface of the retina 2000 may be reduced as much as possible, for example, the distance between the micro-electrode 110 and the surface of the retina 2000 is zero, thereby reducing the occupied space of the entire flexible cable 100 while ensuring the distance between the stimulating electrode 120 and the surface of the retina 2000 to be uniform. Of course, the end of the stimulating electrode 120 may be exposed or partially exposed at one side of the micro-electrode 110, and the end of the stimulating electrode 120 may be in direct contact with the surface of the retina 2000, so that the distance between the stimulating electrode 120 and the surface of the retina 2000 is also well ensured to be uniform.

According to some embodiments of the present invention, as shown in fig. 1-5 d, the microelectrode 110 further includes a holding end 114 for holding during the operation of the surgeon, so as to facilitate the operation. The clamping end 114 is located at a side of the electrode region 112 away from the first mounting hole 111. For example, the clamping end 114 and the first mounting hole 111 are respectively located at both sides of the electrode region 112, and the clamping end 114 may be formed to extend outward from a side of the micro-electrode 110 away from the first mounting hole 111. The width of the holding end 114 is smaller than that of the electrode area 112, so that it is convenient for a tool such as tweezers to pick up. To facilitate gripping, the gripping end 114 may be angled, optionally at a 90 ° right angle, to the electrode region 112 during implantation.

Alternatively, as shown in fig. 1 to 5d, an end of one side of the electrode region 112, which is away from the first mounting hole 111, has a chamfer 115. Thus, by providing the chamfer 115, the end portion of the micro-electrode 110 can be easily disposed at the implantation site of the retina 2000, for example, through an incision on the eyeball 3000, so that damage to the tissue when the micro-electrode 110 is moved can be reduced.

Further, a plurality of stimulation electrodes 120 may be disposed in an array (e.g., in rows and columns) within the micro-electrodes 110, and the surfaces of the ends of the micro-electrodes 110 that contact the retina 2000 are configured to substantially match the curvature of the corresponding portions of the retina 2000. Thus, it is better adapted to the micro-electrode 110 where a larger number of stimulating electrodes 120 need to be arranged, and it is possible to make the plurality of stimulating electrodes 120 more effectively fit to the retina 2000 of the eyeball 3000, sufficiently contact the implanted portion of the retina 2000 such as the macular region, and generate more effective nerve stimulation.

Further alternatively, each of the stimulation electrodes 120 may be formed in a cylindrical shape having substantially the same height and cross-sectional area, so that self-impedance between each of the stimulation electrodes 120 is substantially the same, thereby being capable of reducing adverse effects caused by impedance differences between the stimulation electrodes 120.

In some embodiments of the present invention, the flexible cable 100 is integrally manufactured by a MEMS process (micro-fabrication process-generic term for micro-structure processing down to the nanometer scale and up to the millimeter scale), which may be made by chemical vapor deposition, sputtering, electroplating, evaporation, plasma etching, patterning, or a combination thereof.

In some alternative embodiments, the material of the flexible substrate 113 is preferably PMMA (poly (methyl methacrylate)), teflon, silicone, polyimide, poly (ethylene terephthalate), poly (xylylene) (especially Parylene-C). By using the flexible substrate 113 made of a flexible material, damage to an implantation site such as ocular tissue by the micro-electrode 110 during implantation can be suppressed. The flexible substrate 113 can be processed into a spherical shape of the retina by means of a mold and a vacuum high-temperature shaping method, and in addition, the curvature of the implantation part of the retina 2000 can be adapted through the flexible deformation of the flexible substrate 113, and the curvature change caused by the size difference of eyeballs of different patients can be adapted, so that the stimulation electrodes 120 arranged on the plurality of stimulation electrodes can be more fully attached to the implantation part of the retina 2000, and a better electrical stimulation effect is realized.

In some alternative examples, the ends of the stimulation electrodes 120 are exposed or partially exposed on one side of the flexible substrate 113 to facilitate delivery of electrical stimulation pulses to the retinal 2000 ganglion cells or bipolar cells. The maximum amplitude of the stimulation pulse current may preferably be 200 muA-800 muA.

The stimulation electrode 120 and the lead 151 are preferably made of Au, Ag, Pt, Pd, Ti, or an alloy of any combination thereof. Since the above metals or their alloys have good biocompatibility, the stimulation electrode 120 composed of these materials can ensure biocompatibility. In addition, such a stimulation electrode 120 can be more suitable for use in implantable devices that have stringent biocompatibility requirements.

An implantation device 1000 of a retina 2000 according to an embodiment of the second aspect of the present invention comprises: the flexible cable 100, the fixing member 200, the electronic device 300 and the first wireless annunciator 400 according to the above-described embodiments.

As shown in fig. 7 and 8a, the fixing member 200 fixes the micro-electrodes 110 of the flexible cable 100 to the retina 2000 through the first and second mounting

holes

111 and 1311. Therefore, the microelectrode 110 can be conveniently fixed, the stress of the microelectrode 110 is uniform, the situation of tilting does not occur, the uniform distance between the stimulating electrode 120 and the surface of the retina 2000 is ensured, the damage to the human body caused by large stimulating current is avoided, and the service life of the microelectrode 110 is prolonged. The electrical pulse signals transmitted to the retina 2000 through the stimulation electrodes 120 stimulate the neurons on the retina 2000 that remain functional and transmit the stimulation to the brain through the optic nerve, resulting in visual perception by the patient.

As shown in fig. 9, the fixing member 200 includes a shaft portion 210, an elastic member 220, a stopper portion 230, and a nail head 240. Shaft 210 is connected between stop 230 and stud 240, and stud 240 is used to pierce the surface of retina 2000. The elastic element 220 is disposed on the rod portion 210 in a penetrating manner, and two ends of the elastic element 220 respectively abut against the limiting portion 230 and the gasket. Thus, after the fixing member 200 fixes the micro-electrode 110 on the surface of the retina 2000, the elastic member 220 may serve as an elastic stopper, so that the transmission of pressure may be facilitated.

The electronic device 300 has a chip connected to the introduction part 140 to drive the plurality of stimulation electrodes 120. In some embodiments, the electronic device 300 may comprise an ASIC chip (application specific integrated circuit), a discrete raw device, or the like, for processing the received data signals to emit electrical stimulation pulses that drive the microelectrodes 110. The discrete primitive devices include electronic components such as capacitors, inductors, resistors, oscillators, and filters that may be provided according to circuit design. The connection portion 150 of the flexible cable 100 includes a plurality of conductive wires 151, and the connection portion 150 is connected to the electronic device 300 after passing through the wall of the eyeball 3000.

The first wireless annunciator 400 is connected to the electronic device 300 to receive image information acquired from the outside and transmit the image information to a chip within the electronic device 300. In some alternative embodiments, the electronic device 300 may be packaged integrally with the first wireless annunciator 400. Of course, the electronic device 300 may also be packaged separately from the first wireless annunciator 400. The first wireless annunciator 400 may include an internal wireless data coil and an internal wireless energy coil.

A process of implanting the retinal prosthesis implantation device 1000 according to an embodiment of the present invention into the eyeball 3000 will be described below with reference to fig. 7 and 8 a.

The physician holds the holding end 114 of the microelectrode 110 of the flexible cable 100 by a tool (e.g., forceps, not shown) and then applies the electrode regions 112 against the surface of the retina 2000. The holding device (not shown) holds a fixing member 200, and sends it into the eyeball 3000, so that the fixing member 200 passes through the second mounting hole 1311 of the abutting member 130, the first mounting hole 111 of the micro-electrode 110, the retina 2000, the choroid, and the sclera in this order, thereby fixing the micro-electrode 110 on the surface of the retina 2000.

The fixing piece 200 penetrates through the first mounting hole 111 on the microelectrode 110 and the second mounting hole 1311 on the abutting piece 130 to fix the microelectrode 110 and the abutting piece 130 to the retina 2000 together, the whole microelectrode 110 is uniformly stressed, one end of the microelectrode cannot be tilted, the damage to the surface of the retina 2000 can be avoided, and the visual perception effect can be ensured.

Generally, each receptor at the macular region of retina 2000 is associated with a separate bipolar cell, which in turn is associated with a separate ganglion cell. Thus, each cone of the macular region has a direct path to the brain, which provides the brain with a precise location of input. Therefore, by attaching the micro-electrode 110 of the flexible cable 100 according to the embodiment of the present invention to the macular region of the retina 2000, the stimulating electrode 120 can emit, for example, a bidirectional pulse current signal as an electrical stimulation signal. Here, interstitial fluid exists between the stimulating electrode 120 and the macular region of the retina 2000 (depending on the distance therebetween), and the electrical stimulation signal delivered by the stimulating electrode 120 electrically stimulates the ganglion cells of the retina 2000 or bipolar cells adjacent to the ganglion cells through interstitial fluid conduction. After the ganglion cells or bipolar cells are stimulated, the resulting stimulation signals create light sensation in the cerebral cortex via the visual pathway. After the stimulating electrode 120 is attached to the retina 2000 more closely, the stimulating efficiency of the stimulating electrode 120 structure to the retina 2000 can be improved more effectively.

A retinal prosthesis according to an embodiment of the third aspect of the present invention includes: the implantation device 1000 and the external device 4000 of the retina 2000 according to the above embodiments.

As shown in fig. 10, the external device 4000 includes: a camera unit 4100, a video processing unit 4200, and a second wireless signal 4300, the camera unit 4100 may be a camera, and the camera unit 4100 may be provided on a wearable device (e.g., glasses). It should be noted that the glasses may be replaced by other wearable devices such as a hat. The video processing unit 4200 may be worn elsewhere on the patient, such as on a belt, clothing belt, etc., or placed in a pocket of the patient's clothing.

The image pickup unit 4100 is electrically connected to the video processing unit 4200, and for example, the image pickup unit 4100 and the video processing unit 4200 may be connected by a cable. Alternatively, the camera on the glasses transmits video information to the video processing unit 4200, and the video processing unit 4200 converts the video signal into an electrical pulse data signal.

The video processing unit 4200 is electrically connected to the second wireless annunciator 4300, and the second wireless annunciator 4300 is electrically connected to the first wireless annunciator 400. The second wireless annunciator 4300 may include an external wireless data coil and an external wireless power coil, or may include only one coil and control data and power transmission through software. In some embodiments, the video processing unit 4200 may transmit the electrical impulse data signals back to the glasses through the cable, transmitting the data or energy to the first wireless annunciator 400 of the implant device 1000 through the second wireless annunciator 4300 mounted on the glasses.

In the description herein, references to the description of the term "one embodiment," "some embodiments," "an illustrative embodiment," "an example," "a specific example," or "some examples" or the like mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the present invention. In this specification, the schematic representations of the terms used above do not necessarily refer to the same embodiment or example.

While embodiments of the present invention have been shown and described, it will be understood by those of ordinary skill in the art that: various changes, modifications, substitutions and alterations can be made to the embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the claims and their equivalents.

Claims

1. A flexible cable for a retinal prosthesis, comprising:

a micro-electrode having a first mounting hole and an electrode region outside the first mounting hole;

at least sixty stimulating electrodes which are arranged in the electrode area and are regularly arranged, and the end parts of the stimulating electrodes are exposed on one side surface of the microelectrode to be suitable for stimulating retina;

and an abutting member having a second mounting hole corresponding to the first mounting hole and extending from the second mounting hole to the back surfaces of the plurality of stimulation electrodes, the abutting member being provided on the other side surface of the micro-electrode to transmit the force distribution obtained at the second mounting hole to the back surfaces of the plurality of stimulation electrodes.

2. The flexible cable of the retinal prosthesis of claim 1, wherein the abutment comprises at least:

a first end and a second end, wherein the second mounting hole is located at the first end;

at least one connecting section connected between the first end portion and the second end portion, the connecting section being configured in a linear shape, a zigzag shape, or a curved shape.

3. The flexible cable of the retinal prosthesis of claim 2, wherein the abutment further comprises at least one tree-like segment extending from the connecting segment to an edge of the microelectrode.

4. The flexible cable of the retinal prosthesis of claim 3, wherein the connecting segment is linear; the tree segments are two or more in number and are configured to be symmetrical with respect to the connection segment.

5. The retinal prosthesis flexible cable of claim 4, wherein the connecting segment includes a first linear segment and a second linear segment connected thereto, the first linear segment having a width greater than a width of the second linear segment;

the tree-shaped segments comprise a plurality of tree-shaped segments, and the tree-shaped segments extend outwards from the connection position of the first straight line segment and the second straight line segment respectively.

6. The flexible cable of the retinal prosthesis of any one of claims 1 to 5, wherein the abutment and the micro-electrodes are each formed generally in a spherical shape and the radius of curvature of the abutment is greater than or equal to the radius of curvature of the micro-electrodes.

7. The flexible cable of the retinal prosthesis of claim 1, wherein the electrode area has a plurality of electrode holes, the plurality of stimulating electrodes are respectively disposed in the electrode holes, and the ends of the stimulating electrodes are sunk into the electrode holes or partially exceed the electrode holes and exposed out of the micro-electrodes.

8. The flexible cable of the retinal prosthesis of claim 1, wherein the micro-electrode further comprises a clamping end portion located on a side of the electrode zone distal from the first mounting hole.

9. An implantation device for a retina, comprising:

the flexible cable according to any one of claims 1 to 8, further comprising an introduction portion and a connection portion connected between the micro-electrode and the introduction portion;

a fixing member fixing the micro-electrode of the flexible cable to a retina through the first and second mounting holes;

electronics having a chip connected to the lead-in portion to drive the plurality of stimulation electrodes;

a first wireless annunciator connected to the electronic device to receive externally acquired image information and transmit the image information to the chip within the electronic package electronic device.

10. A retinal prosthesis, comprising:

an implant device of the retina according to claim 9;

an external device, the external device comprising: the camera shooting device comprises a camera shooting unit, a video processing unit and a second wireless annunciator, wherein the camera shooting unit is electrically connected with the video processing unit, the video processing unit is electrically connected with the second wireless annunciator, and the second wireless annunciator is electrically connected with the first wireless annunciator.