Medical flexible miniature cerebral cortex electrode implanted in body

Abstract

The utility model discloses a medical flexible miniature cerebral cortex electrode implanted in vivo. The medical flexible miniature cerebral cortex electrode comprises an electrode contact area, an electrode welding spot area and a connecting area for connecting the electrode contact area and the electrode welding spot area, the electrode contact area is provided with a plurality of electrode contacts, the electrode welding spot area is provided with a plurality of electrode welding spots, the connecting area is provided with connecting wires, and the connecting wires are electrically connected with the electrode contacts and the electrode welding spots respectively; the electrode contact area comprises a plurality of contact subareas, the plurality of contact subareas extend along a first direction and are arranged along a second direction, and a hollow part is arranged between every two adjacent contact subareas along the second direction; the first direction is the direction in which the electrode contact area points to the electrode welding spot area, and the second direction intersects with the first direction. According to the technical scheme, the electrode contact area is divided into a plurality of contact subareas, on one hand, the electrode contact area can be more effectively adapted to the rugged surface of the cerebral cortex, and on the other hand, the electrode contact area can go deep into the trench to collect the electroencephalogram signals in the trench.

Description

Technical Field

[0001] The utility model relates to the technical field of brain-computer interfaces, and particularly relates to a flexible micro-cortical electrode implanted in vivo for medical use. Background Art

[0002] Brain-computer interface is an important technology that directly connects the brain with a computer or other external devices through a sensing terminal to extract, decode brain signals and finally convert them into command signals that can be used to control external devices, without relying on traditional output channels. Among them, one of the key components of the brain-computer interface is information extraction, that is, reading the information in the biological brain. At present, there are mainly two main information extraction methods, namely non-invasive and invasive information extraction methods. The non-implanted method reads electroencephalogram (EEG) data through an EEG cap worn on the scalp; while the implanted methods include obtaining EEG data through implanted microelectrode arrays, deep brain electrodes, and semi-implanted electrocorticography (EcoG) electrodes, etc. Among these technologies, EcoG electrodes have been widely used in the field of brain-computer interfaces due to their high signal resolution, relatively long-term stability, and relatively less invasiveness.

[0003] Existing flexible electrodes cannot collect EEG signals in sulci and gyri and cannot adapt to the structure of the complex surface of the brain. Summary of the Utility Model

[0004] The utility model provides a flexible micro-cortical electrode implanted in vivo for medical use, which can not only enable the electrode contact area to more effectively adapt to the rugged surface of the cerebral cortex, improve the adhesion and stability between the flexible micro-cortical electrode and biological tissues, but also can deeply penetrate into the sulci and gyri to collect EEG signals in the sulci and gyri, and at the same time, the flexible micro-cortical electrode can be firmly fixed by means of the sulci and gyri.

[0005] According to the utility model, a flexible micro-cortical electrode implanted in vivo for medical use is provided, which includes an electrode contact area, an electrode soldering area, and a connection area connecting the electrode contact area and the electrode soldering area;

[0006] The electrode contact area is provided with a plurality of electrode contacts, the electrode soldering area is provided with a plurality of electrode solders, the connection area is provided with connection traces, and the connection traces are electrically connected to the electrode contacts and the electrode solders respectively;

[0007] The electrode contact area includes a plurality of contact partitions, and the plurality of contact partitions extend in a first direction and are arranged in a second direction. Along the second direction, there is a hollow between two adjacent contact partitions; the first direction is the direction from the electrode contact area to the electrode solder joint area, and the second direction intersects with the first direction.

[0008] Optionally, the flexible microcortical electrode further includes a flexible substrate;

[0009] The flexible substrate includes a contact substrate part located in the electrode contact area, a solder joint substrate part located in the electrode solder joint area, and a connection substrate part located in the connection area;

[0010] The hollow penetrates the contact substrate part.

[0011] Optionally, along the first direction, the extension lengths of two of the contact partitions are the same; or,

[0012] Along the first direction, the extension lengths of two of the contact partitions are different; along the second direction, the extension widths of two of the contact partitions are the same; or,

[0013] Along the second direction, the extension widths of two of the contact partitions are different.

[0014] Optionally, along the second direction, the extension width of the contact partition is greater than the extension width of the hollow;

[0015] Or, along the second direction, the extension width of the contact partition is equal to the extension width of the hollow;

[0016] Or, along the second direction, the extension width of the contact partition is less than the extension width of the hollow.

[0017] Optionally, along the second direction, the width of the electrode contact area is greater than the width of the connection area and greater than the width of the electrode solder joint area.

[0018] Optionally, each contact partition is provided with a plurality of the electrode contacts, and the plurality of electrode contacts are evenly arranged in the contact partition; or,

[0019] The contact partition includes a plurality of contact sub - partitions, and a plurality of the electrode contacts are arranged in each contact sub - partition, and the arrangement densities of the electrode contacts in two of the contact sub - partitions are different;

[0020] The plurality of electrode solder joints are evenly arranged in the electrode solder joint area.

[0021] Optionally, the electrode contacts are electrically connected to the electrode solder joints correspondingly;

[0022] Multiple connection traces electrically connected to the electrode contacts in the same contact partition are located on opposite sides of the contact partition.

[0023] Optionally, the flexible microcortical electrode further includes a packaging layer located on one side of the flexible substrate and covering the connection traces, at least part of the electrode contacts, and at least part of the electrode solder joints;

[0024] The height of the electrode contact is greater than the thickness of the packaging layer.

[0025] Optionally, the diameter of the electrode contact is between 10 μm and 1000 μm.

[0026] Optionally, the distance between two adjacent electrode contacts on the contact partition is between 50 μm and 1000 μm.

[0027] In the embodiment of the present invention, by dividing the electrode contact area into multiple contact partitions, each independent contact partition can be adapted according to the complex morphology of the cerebral cortex surface, which can not only make the electrode contact area more effectively adapt to the rugged surface of the cerebral cortex, improve the adhesion and stability between the flexible microcortical electrode and biological tissue, but also can deeply collect the electroencephalogram signals in the sulci, and at the same time, the flexible microcortical electrode can be firmly fixed by means of the sulci.

[0028] It should be understood that the content described in this part is not intended to identify the key or important features of the embodiments of the present invention, nor is it used to limit the scope of the present invention. Other features of the present invention will become easily understood through the following description. Description of the Drawings

[0029] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following will briefly introduce the drawings required for the description of the embodiments. Obviously, the drawings in the following description are only some embodiments of the present invention. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0030] Figure 1 is a top view of a flexible microcortical electrode provided according to an embodiment of the present invention;

[0031] Figure 2 is a cross-sectional view of a flexible microcortical electrode provided according to an embodiment of the present invention;

[0032] Figure 3 is a schematic structural diagram of a first electrode contact partition provided according to an embodiment of the present invention;

[0033] Figure 4 is a schematic structural diagram of the second electrode contact partition provided according to an embodiment of the present invention;

[0034] Figure 5 is a schematic structural diagram of the third electrode contact partition provided according to an embodiment of the present invention;

[0035] Figure 6 is a schematic structural diagram of the first electrode contact area provided according to an embodiment of the present invention;

[0036] Figure 7 is a schematic structural diagram of the second electrode contact area provided according to an embodiment of the present invention;

[0037] Figure 8 is a schematic structural diagram of the third electrode contact area provided according to an embodiment of the present invention;

[0038] Figure 9 is a schematic structural diagram of the fourth electrode contact partition provided according to an embodiment of the present invention;

[0039] Figure 10 is a schematic connection diagram of an electrode contact and a connection trace provided according to an embodiment of the present invention;

[0040] Figure 11 is a schematic connection diagram of an electrode solder joint and a connection trace provided according to an embodiment of the present invention;

[0041] Figure 12 is a schematic structural diagram of the fourth electrode contact area provided according to an embodiment of the present invention;

[0042] Figure 13 is a schematic structural diagram of the fifth electrode contact area provided according to an embodiment of the present invention. Detailed implementation manners

[0043] In order to enable those skilled in the art to better understand the solution of the present invention, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0044] It should be noted that the terms "first", "second", etc. in the description, claims and the above drawings of the present utility model are used to distinguish similar objects and do not necessarily describe a specific order or sequence. It should be understood that the data used in this way can be interchanged under appropriate circumstances so that the embodiments of the present utility model described herein can be implemented in an order other than those illustrated or described herein. In addition, the terms "comprising" and "having" any variations are intended to cover non-exclusive inclusion. For example, a process, method, system, product or device comprising a series of steps or units does not necessarily limit to those steps or units clearly listed, but may include other steps or units not clearly listed or inherent to these processes, methods, products or devices.

[0045] Figure 1 is a top view of a flexible microcortical electrode provided according to an embodiment of the present utility model. This embodiment is applicable to long-term implantation under the dura mater of the brain to collect neuron activity data. As Figure 1 shown, the flexible microcortical electrode includes an electrode contact area 1, an electrode solder area 2, and a connection area 3 connecting the electrode contact area 1 and the electrode solder area 2. The electrode contact area 1 is provided with a plurality of electrode contacts 11, the electrode solder area 2 is provided with a plurality of electrode solder joints 21, and the connection area 3 is provided with connection traces 31. The connection traces 31 are electrically connected to the electrode contacts 11 and the electrode solder joints 21 respectively. The electrode contact area 1 includes a plurality of contact partitions 4. The plurality of contact partitions 4 extend along the first direction X and are arranged along the second direction Y. Along the second direction Y, there is a hollow 5 between two adjacent contact partitions 4. The first direction X is the direction from the electrode contact area 1 to the electrode solder area 2, and the second direction Y intersects the first direction X.

[0046] Specifically, there are a plurality of uniformly distributed electrode contacts 11 on the electrode contact area 1. The electrode contact area 1 contacts the brain tissue through the electrode contacts 11 to measure neuron activity signals. There are a plurality of uniformly distributed electrode solder joints 21 on the electrode solder area 2. The electrode solder joints 21 are electrically connected to the electrode contacts 11 through the connection traces 31 on the electrode connection area 3 to transmit the neuron activity signals obtained by the electrode contact area 1 to the electrode solder area 2. The electrode solder area 2 is soldered to a flexible printed circuit board (FPC) (not shown in the figure) through the electrode solder joints 21. The flexible printed circuit board receives the neuron activity signals and, as a signal transmission medium, transmits the neuron activity signals to the main board or the processor for processing and analyzing the neuron activity signals to extract, decode and finally convert the brain signals into instruction signals that can be used to control external devices.

[0047] It can be understood that the direction from the electrode contact area 1 to the electrode solder joint area 2 is defined as the first direction X, and the second direction Y intersects with the first direction X. The intervals between the electrode contacts 1 on the electrode contact area 1 in the second direction Y are the interval areas. Since the surface of the cerebral cortex often has complex morphological features, such as folds, grooves, etc., by dividing and cutting the interval areas to form hollowings 5, the electrode contact area 1 is divided into a plurality of contact partitions 4 that extend along the first direction X and are arranged along the second direction Y. In this way, the appearance of the electrode contact area 1 presents a comb-like structure. The advantage of setting the comb-like structure is to reduce the strength of the electrode contact area 1. Each contact partition 4 can be deformed and adapted according to the complex morphology of the cerebral cortex surface, so that the electrode contact area 1 can better adapt to the complex morphological features of the cerebral cortex surface, further reducing the gap between the electrode contact area 1 and the biological tissue, and helping to increase the contact area and stability between the electrode contact area 1 and the biological tissue. It should be noted that the flexible micro-cerebral cortex electrode in the present application can penetrate into the sulci to collect the electroencephalogram signals in the sulci, and can also be firmly fixed by means of the sulci.

[0048] It should be noted that in the micro-cerebral cortex electrode, the concept of "micro" is mainly reflected in the size of the electrode contacts 1. The contact size of the existing clinical cerebral cortex electrodes is above the millimeter level, while the diameter of the electrode contacts 1 in this embodiment is between 10 μm and 1000 μm, that is, the electrode contact size is at the micron level. The micro-cerebral cortex electrode in the present application has micron-level electrode contacts. Such a small electrode size can not only improve the spatial resolution and obtain higher signal quality, but also reduce the damage to the surrounding tissues. In addition, the micro-cerebral cortex electrode is applicable to clinical application scenarios that require high-precision brain activity monitoring, complex nerve function research, and high positioning accuracy.

[0049] It should be noted that each electrode contact 11 can be electrically connected to the electrode solder joint 12 through the connection trace 31 on the electrode connection area 3. Figure 1 Only some of the electrode contacts 11 are taken as an example for illustration through the connection trace 31 on the electrode connection area 3, rather than a limitation.

[0050] In the embodiment of the present utility model, by dividing the electrode contact area into a plurality of contact partitions, each independent contact partition can be deformed and adapted according to the complex morphology of the cerebral cortex surface, which can not only enable the electrode contact area to more effectively adapt to the rugged surface of the cerebral cortex, improving the adhesion and stability between the flexible micro-cerebral cortex electrode and the biological tissue. Moreover, it can penetrate into the sulci to collect the electroencephalogram signals in the sulci, and at the same time, the flexible micro-cerebral cortex electrode can be firmly fixed by means of the sulci.

[0051] Based on the above embodiments, this embodiment further describes the substrate of the flexible microcortical electrode. Figure 2 is a cross-sectional view of a flexible microcortical electrode provided according to an embodiment of the present invention. As Figure 2 shown, the flexible microcortical electrode further includes a flexible substrate 6, and the flexible substrate 6 includes a contact substrate portion 61 located in the electrode contact area 1, a solder substrate portion 62 located in the electrode solder area 2, and a connection substrate portion 63 located in the connection area 3. The hollow 5 penetrates through the contact substrate portion 61.

[0052] Specifically, as Figure 2 shown, the flexible microcortical electrode can be composed of a metal layer and a flexible substrate 6. The metal layer is disposed in the electrode contact area 1, the electrode solder area 2, and the connection area 3. By performing a patterning process on the metal layer, different structures can be obtained in different areas. For example, electrode contacts 11 are prepared in the electrode contact area 1, electrode solder joints 21 are prepared in the electrode solder area 2, and connection electrodes 31 are prepared in the connection area 3. The flexible substrate 6 includes a contact substrate portion 61 corresponding to the electrode contact area 1, a solder substrate portion 62 corresponding to the electrode solder area 2, and a connection substrate portion 63 corresponding to the connection area 3. In addition, in order to make each contact partition 4 independent, the hollow 5 needs to penetrate through the flexible substrate 6. By providing that the flexible microcortical electrode further includes a flexible substrate 6, the contact partition 4 can be easily bent through the flexible substrate 6, which is convenient for effectively adapting to the rugged surface of the cerebral cortex and improving the adhesion between the flexible microcortical electrode and biological tissue.

[0053] It should be noted that the material of the flexible substrate 6 may include at least one of polyimide, liquid crystal polymer, and Parylene-C. The specific material of the flexible substrate 6 in the embodiments of the present invention is not limited, as long as it has the characteristics of flexibility and easy bending.

[0054] Furthermore, the thickness of the flexible substrate 6 can be between 5 μm and 100 μm. In the field of brain-computer interface technology, the selection of the material and thickness of the flexible substrate 6 is one of the key factors. These selections not only affect the performance of the final product but also determine its application possibilities and scope. Considering the flexibility and functionality of the flexible microcortical electrode, the thickness of the substrate is set between 5 μm and 100 μm. It can be understood that when the substrate thickness is less than 5 μm, the processing difficulty is high, the cost is high, and the production yield is low. When the substrate thickness is greater than 100 μm, the relatively thick substrate usually has a large mechanical stiffness, which will cause the flexibility of the flexible microcortical electrode to deteriorate, increase the damage to brain tissue during the implantation process, and increase the risk of inflammatory reactions.

[0055] In the embodiment of the present utility model, a hollow-through flexible substrate is provided, so that each contact area can independently adapt to the complex morphology of the cerebral cortex surface and deform accordingly, further enabling the electrode contact area to more effectively adapt to the rugged surface of the cerebral cortex, and improving the adhesion and stability between the flexible micro-cortical electrode and biological tissue. In addition, the flexible micro-cortical electrode in the present application can penetrate into the sulci to collect electroencephalogram signals in the sulci, and can also be firmly fixed by means of the sulci.

[0056] On the basis of the above embodiment, this embodiment further describes the extension length and extension width of the contact areas of the flexible micro-cortical electrode. Figure 3 is a schematic structural diagram of the first electrode contact area provided according to the embodiment of the present utility model; Figure 4 is a schematic structural diagram of the second electrode contact area provided according to the embodiment of the present utility model; Figure 5 is a schematic structural diagram of the third electrode contact area provided according to the embodiment of the present utility model. As Figure 1 、 Figure 3 、 Figure 4 and Figure 5 shown, along the first direction X, there are two contact areas 4 with the same extension length; or, along the first direction X, there are two contact areas 4 with different extension lengths; along the second direction Y, there are two contact areas 4 with the same extension width; or, along the second direction Y, there are two contact areas 4 with different extension widths.

[0057] Specifically, referring to Figure 1 、 Figure 3 、 Figure 4 and Figure 5 , taking four contact areas 4 as an example for illustration. For example, Figure 1 , the extension lengths and extension widths of the four contact areas 4 are all the same. Such a setting improves the symmetry of the electrode contact area 1, increases the structural stability, and facilitates the collection of neuron activity signals by each contact area 4.

[0058] As Figure 3 shown, along the first direction X, the extension lengths of the four contact areas 4 are the same, and along the second direction Y, the extension widths of the four contact areas 4 are different. The four electrode areas 4 are arranged in sequence along the second direction Y as the first area 41, the second area 42, the third area 43, and the fourth area 44. Among them, the extension lengths of the first area 41, the second area 42, the third area 43, and the fourth area 44 are the same. However, the extension widths of the first area 41, the second area 42, the third area 43, and the fourth area 44 gradually become narrower along the second direction Y.

[0059] As Figure 4As shown, along the first direction X, the extension lengths of the four contact zones 4 are different, and along the second direction Y, the extension widths of the four contact zones 4 are the same. The four electrode zones 4 are arranged in sequence along the second direction Y as the first zone 41, the second zone 42, the third zone 43, and the fourth zone 44. Among them, the extension widths of the first zone 41, the second zone 42, the third zone 43, and the fourth zone 44 are the same. The extension lengths of the first zone 41, the second zone 42, the third zone 43, and the fourth zone 44 gradually increase along the second direction Y.

[0060] As Figure 5 shown, along the first direction X, the extension lengths of the four contact zones 4 are different, and along the second direction Y, the extension widths of the four contact zones 4 are different. The four electrode zones 4 are arranged in sequence along the second direction Y as the first zone 41, the second zone 42, the third zone 43, and the fourth zone 44. Among them, the extension widths of the first zone 41, the second zone 42, the third zone 43, and the fourth zone 44 gradually narrow along the second direction Y. The extension lengths of the first zone 41, the second zone 42, the third zone 43, and the fourth zone 44 gradually increase along the second direction Y.

[0061] It should be noted that the above content is only for illustration, and the specific extension lengths and extension widths of the first zone, the second zone, the third zone, and the fourth zone are not limited. The contact zones can be adaptively / matchingly designed according to the structure and size of the cerebral cortex surface. Thus, the electrode contact area can further effectively adapt to the rugged surface of the cerebral cortex, improving the adhesion and stability between the flexible micro-cortical electrode and biological tissue. In addition, the flexible micro-cortical electrode in this application can penetrate the sulci and gyri to collect the electroencephalogram signals in the sulci and gyri, and can also be firmly fixed by means of the sulci and gyri.

[0062] On the basis of the above embodiments, the embodiments of the present utility model further illustrate the extension widths of the contact zones and the hollowing. Figure 6 is a schematic diagram of the first electrode contact area structure provided by the embodiment of the present utility model. Figure 7 is a schematic diagram of the second electrode contact area structure provided by the embodiment of the present utility model. Figure 8 is a schematic diagram of the third electrode contact area structure provided by the embodiment of the present utility model. As Figure 6 shown, along the second direction Y, the extension width of the contact zone 4 is greater than the extension width of the hollowing 5. Or, as Figure 7 shown, along the second direction Y, the extension width of the contact zone 4 is equal to the extension width of the hollowing 5. Or, as Figure 8 shown, along the second direction Y, the extension width of the contact zone 4 is less than the extension width of the hollowing 5.

[0063] Specifically, asFigure 6 As shown, taking four contact partitions 4 as an example, three cutouts with the same extended width divide the electrode contact area 1 into four equal parts, and the extended width of the contact partition 4 is greater than that of the cutout, and the extended lengths of the contact partition 4 and the cutout 5 are the same. Therefore, the area of the contact partition 4 is larger than that of the cutout 5. The advantage of such a setting is that the area of the contact partition 4 is made larger, with more detection areas, thereby improving the acquisition efficiency of the contact partition 4 for neuron activity signals, so as to acquire high-fidelity and high-resolution neuron activity signals.

[0064] As Figure 7 shown, three cutouts 5 with equal extended widths divide the electrode contact area 1 into four equal parts, and the extended width of the contact partition 4 is equal to that of the cutout 5, and the extended lengths of the contact partition 4 and the cutout 5 are the same. Therefore, the area of the four contact partitions 4 is larger than the area of the cutout 5. The advantage of such a setting is that the stability of the structure is increased.

[0065] As Figure 8 shown, three cutouts with equal extended widths divide the electrode contact area 1 into four equal parts, and the extended width of the contact partition 4 is less than that of the cutout 5, and the extended lengths of the contact partition 4 and the cutout 5 are the same. Therefore, the area of the four contact partitions 4 is smaller than the area of the cutout 5. The advantage of such a setting is that the flexibility of the contact partition 4 is increased, and the adhesion and stability between the contact partition 4 and biological tissue are further improved.

[0066] On the basis of the above embodiments, the embodiments of the present invention further illustrate the width of the electrode contact area, the width of the connection area, and the width of the electrode solder joint area. As Figure 1 shown, along the second direction Y, the width of the electrode contact area 1 is greater than the width of the connection area 3 and greater than the width of the electrode solder joint area 2.

[0067] Specifically, as Figure 1 shown, the width of the electrode contact area 1 is the largest. In the case where the extended lengths of the contact partitions 4 are the same, the larger the width of the electrode contact area 1, the larger its area. In this way, more contact partitions 4 can be divided. On the one hand, the more the contact partitions 4, the larger the area of the detection area, which can improve the efficiency of collecting cerebral cortex neuron activity signals. On the other hand, the more the contact partitions 4, the more flexible the electrode contact area 1, and the adhesion and stability between the contact partition 4 and biological tissue are further improved.

[0068] On the basis of the above embodiments, the embodiments of the present invention further illustrate the distribution of the electrode contacts in the contact partitions and the distribution of the electrode solder joints in the electrode solder joint area. Figure 9 is a schematic diagram of the fourth electrode contact partition structure provided by the embodiments of the present invention. As Figure 1 andFigure 9 As shown, each contact partition 4 is provided with a plurality of electrode contacts, and the plurality of electrode contacts are evenly arranged within the contact partition 4; alternatively, the contact partition 4 includes a plurality of contact sub-partitions, and a plurality of electrode contacts 11 are provided in each contact sub-partition, and the arrangement densities of the electrode contacts 11 in two contact sub-partitions are different; the plurality of electrode solder joints 21 are evenly arranged in the electrode solder joint area 2.

[0069] Specifically, as Figure 1 shown, the plurality of electrode contacts 11 are evenly distributed on the contact partition 4. It can be understood that the distance between adjacent two electrode contacts 11 is equal or close. The advantage of such an arrangement is that the brain cortex neuron activity signals can be collected evenly, which is convenient for collecting high-fidelity and high-resolution neuron activity signals.

[0070] As Figure 9 shown, the contact partition 4 has two contact sub-partitions, and the arrangement densities of the electrode contacts on the two contact sub-partitions are different; for example, the distance between adjacent two electrode contacts on the first contact sub-partition 45 is smaller, so the arrangement density is larger, and the distance between adjacent two electrode contacts on the second contact sub-partition 46 is larger, so the arrangement density is smaller. It should be noted that the above arrangement of the electrode contacts is only for illustration and does not specifically limit that the distance between adjacent two electrode contacts on the contact partition is between 50 μm and 1000 μm. The distribution of the electrode contacts can be customized according to the brain area where the flexible micro-brain cortex electrode is implanted, so as to facilitate the collection of high-fidelity and high-resolution neuron activity signals.

[0071] Continuing to refer to Figure 1 , the plurality of electrode solder joints 21 are evenly distributed in the electrode solder joint area 2. It can be understood that the distance between adjacent two electrode solder joints 21 is equal or close. The advantage of this is that it is convenient for the electrode contacts 11 to correspond to the electrode solder joints 21, making the arrangement of the connection traces 31 neater. In addition, the electrode solder joints 21 need to be soldered to the flexible circuit board, and the uniform arrangement of the electrode solder joints can improve the soldering quality, laying a foundation for extracting high-fidelity and high-resolution neuron activity signals.

[0072] Based on the above embodiments, the embodiments of the present invention further illustrate the corresponding relationship between the electrode contacts and the electrode solder joints and the routing method of the connection traces. Figure 10 FIG. is a connection schematic diagram of an electrode contact and a connection trace according to an embodiment of the present invention. Figure 11 FIG. is a connection schematic diagram of an electrode solder joint and a connection trace according to an embodiment of the present invention. Combining Figure 1 , Figure 10 and Figure 11, the electrode contact 11 is electrically connected to the electrode solder joint 21 correspondingly, and multiple connection traces electrically connected to the electrode contacts in the same contact partition 4 are located on the opposite sides of the contact partition 4.

[0073] Specifically, the connection relationship between the electrode contact 11 and the electrode solder joint 21 can be one-to-one corresponding connection. As Figure 1 shown, each electrode contact 11 is correspondingly connected to one electrode solder joint 21. If there are electrode solder joints 21 that are not electrically connected to the electrode contacts at this time, the unconnected electrode solder joints 21 can be used as spares.

[0074] Alternatively, the connection relationship between the electrode contact 11 and the electrode solder joint 21 can be one-to-many corresponding connection (not shown in the figure). For example, each electrode contact 11 is correspondingly connected to at least two electrode solder joints 21 to accurately transmit the activity signals of the cerebral cortex neurons.

[0075] As Figure 10 shown, the connection trace 31 of the electrode contact 11 on the contact partition 4 can be routed on the left side of the electrode contact 11 or on the right side of the electrode contact 11. As Figure 11 shown, the connection trace 31 of the electrode solder joint 21 on the electrode solder joint area 2 can be routed on the left side of the electrode solder joint 21 or on the right side of the electrode solder joint 21. That is to say, the connection trace 31 connecting the electrode contact 11 and the electrode solder joint 21 can be arranged on the opposite sides of the contact partition. The advantage of such routing is that the routing method is simple and neat, improving the connection quality between the electrode contact 11 and the electrode solder joint 21, and further laying a foundation for extracting high-fidelity and high-resolution neuron activity signals.

[0076] Based on the above embodiments, the embodiments of the present invention further describe the encapsulation layer of the flexible micro-cerebral cortex electrode. As Figure 2 shown, the flexible micro-cerebral cortex electrode further includes an encapsulation layer 10. The encapsulation layer 10 is located on one side of the flexible substrate 6 and covers the connection trace 31, part of the electrode contacts 11, and part of the electrode solder joints 21; the height of the electrode contact 11 is greater than the thickness of the encapsulation layer 10.

[0077] Specifically, the material of the encapsulation layer 10 can include at least one of polyimide, silicon carbide, liquid crystal polymer, Parylene-C, ceramic, and silicon dioxide. During the preparation process of the flexible micro-cerebral cortex electrode, after the encapsulation layer 10 covers the connection trace 31, the electrode contacts 11, and the electrode solder joints 21, it is necessary to remove the upper part of the encapsulation layer 10 above the electrode contacts 11 and the electrode solder joints 12, so as to form a structure that covers the connection trace 31, partially covers the electrode contacts 11 in the height direction, and partially covers the electrode solder joints 21. The purpose of doing this is to expose the electrode contacts 11 for collecting the activity signals of the cerebral cortex neurons and expose the electrode solder joints 21 for welding with the flexible circuit board.

[0078] It should be noted that, in order to improve the accuracy of the electrode contact 11 for collecting the brain cortical neuron activity signals, the height of the electrode contact 11 needs to be set greater than the thickness of the encapsulation layer 10. Further, in the preparation process of the flexible micro-brain cortical electrode, platinum or iridium is deposited by electroplating to precisely lift the electrode contact or the micro-indentation to be flush with or beyond the plane of the encapsulation layer 10. The advantage of such a setting is that it not only ensures a micron-level close contact between the electrode contact 11 and the brain tissue, but also significantly improves the stability of the interface and the efficiency of signal conduction, thus laying a solid foundation for collecting high-fidelity and high-resolution neuron activity data.

[0079] Optionally, on the basis of the above embodiments, the embodiments of the present invention further describe the structure of the contact partition. Figure 12 FIG. 4 is a schematic diagram of the fourth electrode contact area structure provided by the embodiments of the present invention. Figure 13 FIG. 5 is a schematic diagram of the fifth electrode contact area structure provided by the embodiments of the present invention. As Figure 12 shown, along the first direction X, the extension width of the contact partition 4 gradually becomes smaller; or, as Figure 13 shown, along the first direction X, the extension width of the contact partition 4 gradually becomes larger.

[0080] Specifically, as Figure 12 shown, the extension width of the contact partition 4 gradually becomes smaller, forming a structure with a wide end and a narrow tail. Such a structure can make the flexibility of the tail area lower and the flexibility better. Thus, it further enables the electrode contact area 1 to more effectively adapt to the rugged surface of the cerebral cortex, and improves the adhesion and stability between the flexible micro-brain cortical electrode and the biological tissue.

[0081] As Figure 13 shown, the extension width of the contact partition 4 gradually becomes larger, forming a structure with a narrow end and a wide tail. Such a structure has a higher degree of freedom at the narrow end and better stability at the wide tail, and can further adapt to the rugged surface of the cerebral cortex, and improve the adhesion between the flexible micro-brain cortical electrode and the biological tissue.

[0082] In summary, in the technical solutions of the embodiments of the present invention, by setting that the electrode contact area has multiple contact partitions, the electrode contact area can more effectively adapt to the rugged surface of the cerebral cortex, and improve the adhesion and stability between the flexible micro-brain cortical electrode and the biological tissue. On this basis, the shape of the contact partition is reasonably set according to the actual application situation to further match the rugged surface of the cerebral cortex and improve the detection accuracy. In addition, the flexible micro-brain cortical electrode in the present application can penetrate into the sulci to collect the electroencephalogram signals in the sulci, and can also be firmly fixed by means of the sulci.

[0083] The above specific embodiments do not constitute a limitation on the protection scope of the present utility model. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can be made according to design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principle of the present utility model shall be included within the protection scope of the present utility model.

Claims

1. A flexible micro-cortical electrode for medical in vivo implantation, characterized in that: comprising an electrode contact area, an electrode welding area, and a connection area connecting the electrode contact area and the electrode welding area; The electrode contact area is provided with a plurality of electrode contacts, the electrode soldering point area is provided with a plurality of electrode soldering points, the connection area is provided with connection wirings, and the connection wirings are electrically connected to the electrode contacts and the electrode soldering points respectively; The electrode contact area includes multiple contact partitions, which extend along a first direction and are arranged along a second direction. Along the second direction, there is a hollow space between two adjacent contact partitions. The first direction is the direction from the electrode contact area to the electrode solder point area, and the second direction intersects with the first direction.

2. The flexible micro-cortical electrode according to claim 1, characterized in that: The flexible micro-cortical electrode also includes a flexible substrate; The flexible substrate comprises a contact substrate section located in the electrode contact area, a soldering point substrate section located in the electrode soldering point area, and a connection substrate section located in the connection area; The hollowing extends through the contact substrate portion.

3. The flexible micro-cortical electrode according to claim 1, characterized in that: Along the first direction, there are two contact partitions with the same extension length; Alternatively, along the first direction, there are two contact partitions with different extension lengths; Along the second direction, there are two contact partitions with the same extension width; Alternatively, along the second direction, there are two contact partitions with different extension widths.

4. The flexible micro-cortical electrode according to claim 1, characterized in that: Along the second direction, the extension width of the contact partition is greater than the extension width of the hollowing; Alternatively, along the second direction, the extension width of the contact partition is equal to the extension width of the hollowing; Alternatively, along the second direction, an extension width of the contact partition is smaller than an extension width of the hollowing.

5. The flexible micro-cortical electrode according to claim 1, characterized in that: Along the second direction, the width of the electrode contact area is greater than the width of the connection area, and greater than the width of the electrode pad area.

6. The flexible micro-cortical electrode according to claim 1, characterized in that: Each of the contact partitions is provided with a plurality of the electrode contacts, and the plurality of the electrode contacts are evenly arranged in the contact partition; Alternatively, the contact partition includes a plurality of contact sub-partitions, each of which is provided with a plurality of electrode contacts, and the arrangement density of the electrode contacts in two of the contact sub-partitions is different; The plurality of electrode welding points are evenly arranged in the electrode welding point area.

7. The flexible micro-cortical electrode according to claim 6, characterized in that: The electrode contacts are electrically connected to the electrode welding points accordingly; The plurality of connection wires electrically connected to the electrode contacts in the same contact partition are located on two opposite sides of the contact partition.

8. The flexible micro-cortical electrode according to claim 2, characterized in that: The flexible micro-cortical electrode further comprises a packaging layer, which is located on one side of the flexible substrate and covers the connecting wires, part of the electrode contacts and part of the electrode welding points; The height of the electrode contact is greater than the thickness of the packaging layer.

9. The flexible micro-cortical electrode according to claim 1, characterized in that: The diameter of the electrode contact is between 10 μm and 1000 μm.

10. The flexible micro-cortical electrode according to claim 1, characterized in that: The distance between two adjacent electrode contacts on the contact partition is between 50 μm and 1000 μm.

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