Structure for brain signal measurement and electrical stimulation, and system including same

Abstract

The present invention relates to a structure for signal measurement and electrical stimulation, the structure comprising a sensor unit for measuring a signal generated in the brain or delivering external stimulation to the brain. The sensor unit includes: a flexible pad unit; and rib structure units disposed on the pad unit to enhance the resilience of the pad unit.

Description

Structure for measuring brain signals and electrical stimulation and system including the same

[0001] The present invention relates to a structure for measuring brain signals and electrical stimulation and a system including the same, and more particularly, to a structure for measuring brain nerve signals and electrical stimulation including a lip structure and a system including the same. The present invention was researched with the support of the following tasks.

[0002] 1. Alchemist Project ([Project Unique Number] 1415169915 / [Project Number] 20012355 / [Ministry Name] Ministry of Trade, Industry and Energy / [Project Management (Specialized) Agency Name] Korea Institute of Industrial Technology Evaluation and Planning / [Research Project Name] Industrial Technology Alchemist Project / [Research Project Name] Development of a Fully Implantable Closed-Circuit Brain to X for Voice Communication / [Contribution Rate] 100% / [Project Implementing Agency Name] G-Brain Co., Ltd. / [Research Period] September 1, 2020 ~ December 31, 2026 (Total Research Period))

[0003] 2. Materials and Components Technology Development Project ([Project Unique Number] 2410002762 / [Project Number] 00449917 / [Ministry Name] Ministry of Trade, Industry and Energy / [Project Management (Specialized) Agency Name] Korea Institute of Industrial Technology Planning and Evaluation / [Research Project Name] Materials and Components Technology Development (R&D) / [Research Project Name] Wireless Closed-Loop Cranial Nerve Stimulator for Parkinson's Disease Diagnosis / Treatment / [Contribution Rate] 100% / [Project Implementing Agency Name] G-Brain Co., Ltd. / [Research Period] July 1, 2024 - December 31, 2026)

[0004] In recent years, the incidence of various brain disorders, such as epilepsy, Parkinson's disease, Alzheimer's disease, and stroke, has steadily increased. Consequently, technologies for effectively diagnosing and treating serious brain disorders are becoming a crucial part of our healthcare system. One such advancement is the development of neural recording systems capable of monitoring electrocortical (ECoG) signals over a large area of ​​the cerebral cortex. These ECoG systems have proven to be an important diagnostic and therapeutic tool for patients experiencing severe epileptic seizures.

[0005] However, precisely locating the seizure focus often requires surgical procedures, such as craniotomy and durotomy, to insert large-scale ECoG electrodes into the exposed cortex. While essential, these procedures often result in significant postoperative symptoms, including cerebral edema, cerebral hemorrhage, and subsequent changes in intracranial pressure (ICP) and temperature (ICT).

[0006] Therefore, intracranial pressure (ICP) and temperature (ICT) monitoring technologies are frequently used to diagnose these conditions. However, these sensors typically feature bulky designs that require intracranial access, potentially limiting patient mobility and impairing brain function. Furthermore, the need for separate devices to monitor different vital signs complicates the surgical and postoperative process.

[0007] Accordingly, the industry is continuously and actively conducting research and development to resolve the above-mentioned conventional problems and develop more effective methods.

[0008] The present invention was created to solve the problems of the prior art as described above and to expand the scope of application, and the purpose of the present invention is to provide a structure for measuring brain signals and electrical stimulation and a system including the same, which can simplify the surgical and post-surgical process by minimizing the opening of the skull while minimizing damage when inserting the structure into the brain.

[0009] The present invention relates to a structure for signal measurement and electrical stimulation, including a sensor unit for measuring a signal generated in the brain or transmitting an external stimulus to the brain, wherein the sensor unit comprises: a pad unit having a flexible property; and a lip structure unit disposed on the pad unit to increase the resilience of the pad unit.

[0010] Specifically, it may be arranged in a bar shape on the upper side of the pad portion, and the bar shapes may be formed to intersect.

[0011] Specifically, the pad portion may have a radial mesh structure.

[0012] Specifically, the pad portion may include a first mesh portion formed by a plurality of rod-shaped portions extending radially and spaced apart from each other in the circumferential direction; and a second mesh portion formed by a plurality of circular-shaped portions formed to intersect the rod-shaped portions of the first mesh portion and forming a concentric circle and spaced apart from each other in the radial direction.

[0013] Specifically, an electrode or sensor may be installed at the portion where the first mesh portion and the second mesh portion intersect.

[0014] Specifically, the second mesh portion has a support structure formed in a circular shape formed at the outermost portion, and a plurality of support structures can be formed spaced apart from each other in the circumferential direction of the circular shape.

[0015] Specifically, the electrode may be composed of one or more of gold, a platinum-iridium alloy, graphene, carbon nanotubes, fullerene, graphite, or diamond, or a composite thereof.

[0016] Specifically, the electrode can be installed in a portion where the lip structure portion is arranged on the first mesh portion.

[0017] Specifically, the electrode measures a signal generated in the brain or transmits an external stimulus to the brain, and the sensor may include a pressure sensor for measuring intracranial pressure (ICP) or a temperature sensor for measuring intracranial temperature (ICT).

[0018] In addition, the present invention relates to a signal measuring and stimulating structure including a sensor unit that measures a signal generated in the brain or transmits an external stimulus to the brain, wherein the sensor unit includes a pad unit having a flexible property; and a lip structure unit that is arranged on the pad unit to increase the resilience of the pad unit, and may further include an electric pad unit for connection with the outside; and a connecting unit that connects the electric pad unit and the sensor unit.

[0019] A measurement and stimulation structure and a system including the same according to one embodiment of the present invention have the effect of providing structural stability to the structure by installing a lip structure on a pad of a mesh structure, and when the pad of a flexible mesh structure is folded and then unfolded upon injection into the brain, the effect of exerting a uniformly distributed elastic restoring force so that sufficient unfolding can be exerted.

[0020] In addition, the measurement and stimulation structure and the system including the same according to one embodiment of the present invention have a flexible radial mesh structure, thereby having unique mechanical flexibility, and thus having the effect of preventing damage to the structure.

[0021] FIG. 1 is a diagram illustrating a structure for measurement and stimulation according to one embodiment of the present invention being injected into the brain.

[0022] FIG. 2 is a step-by-step diagram illustrating a method of injecting a measurement and stimulation structure into the brain according to an embodiment of the present invention.

[0023] Figure 3 is an exploded view of a measurement and stimulation structure according to one embodiment of the present invention.

[0024] FIG. 4 is a detailed drawing of a sensor section of a measurement and stimulation structure according to one embodiment of the present invention.

[0025] FIG. 5 is a detailed drawing of a sensor section of a measurement and stimulation structure according to one embodiment of the present invention.

[0026] The objects, specific advantages, and novel features of the present invention will become more apparent from the following detailed description and preferred embodiments, taken in conjunction with the accompanying drawings. In this specification, when reference numerals are assigned to components in each drawing, it should be noted that, where possible, identical components are given the same reference numerals even if they appear in different drawings. Furthermore, in describing the present invention, if a detailed description of a related known technology is deemed to unnecessarily obscure the gist of the present invention, the detailed description thereof will be omitted.

[0027] The following detailed description will be provided in detail together with the drawings shown below.

[0028] FIG. 1 is a diagram illustrating a method of injecting a measurement and stimulation structure into a brain according to an embodiment of the present invention, FIG. 2 is a diagram illustrating a method of injecting a measurement and stimulation structure into a brain according to an embodiment of the present invention in steps, FIG. 3 is an exploded view of a measurement and stimulation structure according to an embodiment of the present invention, FIG. 4 is a detailed view of a sensor part of a measurement and stimulation structure according to an embodiment of the present invention, and FIG. 5 is a detailed view of a sensor part of a measurement and stimulation structure according to an embodiment of the present invention.

[0029] As shown in FIGS. 1 to 5, a measurement and stimulation structure (1) according to an embodiment of the present invention includes a sensor portion (10), a connection portion (20), and an electric pad portion (30).

[0030] Hereinafter, a measurement and stimulation structure (1) according to the present invention having the above-described configurations and a system including the same will be described in detail.

[0031] In the present invention, the measuring and stimulating structure (1) measures a signal generated in the brain or transmits a stimulation signal received from the outside to the brain.

[0032] The measurement and stimulation structure (1), referring to Fig. 1, has a sensor unit (10) which is a minimally invasive multimodal array having a flexible mesh structure so that it can be safely injected through a small hole (H) in the skull of a subject (M), thereby reducing the significant surgical risk of craniotomy while achieving accurate nerve monitoring.

[0033] Referring to FIGS. 1 and 2, a small hole (H) with a diameter of 1 mm to 2 mm is formed in the skull, and even with a hole (H) of this size, the measurement and stimulation structure (1) of the present invention is sufficient to be injected into the subdural space between the dura mater (B3) and the arachnoid mater (B4). At this time, the measurement and stimulation structure (1) of the present invention is folded and accommodated inside a syringe (S), and the inside of the syringe (S) is filled with a PBS (phosphate-buffered saline) solution (P) and is immersed in this solution. The measurement and stimulation structure (1) of the present invention can be injected with air pressure using air (A) when injected into the skull of the subject (M) through the hole (H) in the injection direction (J).

[0034] During injection, there are two key parameters: injection pressure and spread area fraction. An appropriate injection pressure (primarily determined by the device's bending stiffness) is required to effectively eject the contracted sensor portion (10) from the syringe (S), unfold, and adhere to the surface of the cerebral cortex (B5). In this case, the injection pressure must be controlled within a safe range that does not damage brain cells. Since an injection pressure exceeding 15 to 20 kPA can damage brain cells, the pressure is maintained below 15 kPA during intracerebral injection of the present invention, and a sufficient spread area fraction of at least 80% can be achieved after injection.

[0035] The measurement and stimulation structure (1) of the present invention is injected into the subdural space between the dura mater (B3) and the arachnoid membrane (B4) by penetrating the scalp (B1), the skull (B2), and the dura mater (B3) in the injection direction (J) through a syringe (S), as shown in (a) of Fig. 2. At this time, the measurement and stimulation structure (1) of the present invention is folded and accommodated inside the syringe (S).

[0036] After this, as shown in (b) of Fig. 2, the measurement and stimulation structure (1) of the present invention is dropped into the subdural space and immediately unfolded, and is suitably attached to the cerebral cortex (B5).

[0037] After this, as in (c) of FIG. 3, the measurement and stimulation structure (1) of the present invention is placed such that the sensor portion (10) is suitably attached to the cerebral cortex (B5), the connection portion (20) penetrates the scalp (B1), the skull (B2), and the dura mater (B3), and the electric pad portion (30) is placed on the scalp (B1), and at the same time, the syringe (S) is removed to the outside.

[0038] In this way, the measurement and stimulation structure (1) of the present invention helps to significantly reduce the surgical risk compared to existing surgical methods, and has the effect of simplifying the entire procedure of diagnosis, treatment, and post-surgical monitoring of brain diseases through multimodal ECoG signal recording, electrical stimulation administration, and intracranial pressure (ICP) and intracranial temperature (ICT) monitoring.

[0039] As shown in Fig. 3, the measurement and stimulation structure (1) of the present invention is divided into a sensor portion (10), a connection portion (20), and an electric pad portion (30).

[0040] The sensor portion (10) is formed with a pad portion (11) and a lip structure portion (12), and the pad portion (11) may be composed of first to fifth materials (P1 to P5). Here, the first material (P1) may be, for example, SU-8, the second material (P2) may be graphene, the third material (P3) may be molybdenum dioxide (MoS2), the fourth material (P4) may be chromium / gold (Cr / Au), and the fifth material (P5) may be polyimide. The lip structure portion (12) may be composed of, for example, SU-8. The connection portion (20) and the electric pad portion (30) may be composed of the first to fourth materials (P1 to P4).

[0041] Graphene and molybdenum dioxide, which are the core materials forming the measurement and stimulation structure (1) of the present invention, are atomically thin and have very flexible characteristics, and thus the measurement and stimulation structure (1) of the present invention can withstand considerable deformation that occurs when injected through a small tip at the end of a syringe (S), and in addition, the excellent electrochemical performance and biocompatibility of graphene, and the piezoelectric resistance and temperature-dependent characteristics of molybdenum dioxide can enable long-term stable and low-noise monitoring.

[0042] The sensor part (10) measures signals generated from the brain or transmits stimulus signals received from the outside to the brain, and includes a pad part (11) and a lip structure part (12).

[0043] The pad portion (11) is flexible and may have a radial mesh structure. Previously, the pad portion (11) had a square shape, which was prone to damage due to structural stress when folded, and tended to have poor durability. To overcome this, the present invention formed the pad portion (11) in a circular shape rather than a square shape, but adopted a mesh form for a flexible structure.

[0044] The pad portion (11) may have a thickness of, for example, 3 μm to 5 μm. Since the pad portion (11) has a mesh structure, bending rigidity is important. This bending rigidity is determined by the thickness of the pad portion (11) and the design of the lip structure portion (12) described later. These design dimensions have a great influence on mechanical dynamics such as injection pressure, mechanical stress distribution, and unfolding of the substrate after discharge. For example, if the thickness of the pad portion (11) is reduced, the bending rigidity and elastic restoring force decrease, which lowers the injection pressure and unfolding area ratio. Therefore, the thickness of the pad portion (11) and the lip structure portion (12) must be adjusted to optimize the injection pressure and unfolding area ratio. When the thickness of the pad portion (11) is thin, less than 3 μm, the injection pressure condition for safe injection can be satisfied, but the elastic restoring force decreases, resulting in a low unfolding area ratio of less than 34.6%. Meanwhile, if the pad portion (11) is thicker than 5 um, it will have a high spread area ratio of over 80%, but there is a problem that the required injection pressure far exceeds the safe 37 kPa, making it impractical. Therefore, in the present invention, the pad portion (11) is configured to have a thickness of, for example, 3 um to 5 um, thereby resolving these structural problems.

[0045] Meanwhile, even in the case of a pad portion (11) having such a thickness, a more effective design can be achieved through a lip structure portion (12). For example, when the lip structure portion (12) is formed in a cross shape, the pad portion (11) can be formed to be as thin as 1.2 um.

[0046] For example, in the case of the pad part (11) without the lip structure part (12), if the pad part (11) is formed as thin as 1.2 um, it is severely crumpled during injection, and thus exhibits a low spreading area ratio of 14.77% when unfolded. On the other hand, if the lip structure part (12) is formed in a cross shape, even if the pad part (11) is formed as thin as 1.2 um, it exhibits a high spreading area ratio even at a low injection pressure of 10 kPa due to the improved elastic restoring force. At this time, when the lip structure part (12) has a thickness of 5 um, the spreading area ratio is 30.92%, and when it has a thickness of 15 um, it exhibits a significantly improved spreading area ratio of 100%. As a result of analysis through computational fluid dynamics (CFD) and finite element analysis (FEA), when the pad part (11) is formed as thin as 1.2 um, the most optimized value is when the thickness of the lip structure part (12) is 15 um to 25 um, and the condition of an expansion area ratio exceeding 80% is satisfied at an injection pressure of less than 15 kPA.

[0047] This allows the injection pressure to be minimized even if the pad portion (11) is formed very thinly. At this time, when the lip structure portions (12) intersect in a cross shape, the angle between the two lip structure portions (12) was most suitable at 90 degrees. When the thickness of the pad portion (11) is 1.2 um and the thickness of the lip structure portion (12) is 15 um, the angle between the two lip structure portions (12) (symbol a in FIG. 4) shows a consistent trend in which, as the angle between the two lip structure portions (12) increases, the uniaxial bending stiffness increases along the X-axis (X-axis in FIG. 4) and proportionally decreases along the Y-axis (Y-axis in FIG. 4). Therefore, as a result, the ratio of the uniaxial bending stiffness in the X-axis and Y-axis directions increases as the angle between the two lip structure portions (12) (symbol a in FIG. 4) increases. The same bending stiffness along each axis is achieved when the angle (symbol a in FIG. 4) between the two lip structures (12) is 90 degrees, so that the restoring force is evenly distributed and the maximum spread area ratio is shown. As the bending stiffness along the X-axis increases, the injection pressure must inevitably increase, which consequently increases the applied strain. Therefore, although the injection pressure is not minimum when the angle (symbol a in FIG. 4) between the two lip structures (12) is 90 degrees, there is an advantage of a greatly improved spread area ratio due to the symmetry. That is, when the angle (symbol a in FIG. 4) between the two lip structures (12) is 90 degrees, the highest spread area ratio is shown, ensuring a safe injection pressure.

[0048] The pad portion (11) may include a first mesh portion (111) formed by a plurality of rod shapes extending in the radial direction and spaced apart from each other in the circumferential direction, and a second mesh portion (112) formed by a plurality of concentric circular shapes spaced apart from each other in the radial direction and formed to intersect the rod shapes of the first mesh portion (111).

[0049] There are multiple points where the first mesh portion (111) and the second mesh portion (112) intersect, and electrodes (15) or sensors (14) can be installed at any point in these multiple intersecting points.

[0050] The second mesh section (112) can have a support structure (13) formed in a circular shape at the outermost part.

[0051] In this way, the pad portion (10) having a radial mesh structure can alleviate the pressure applied during the injection process through the syringe (S).

[0052] The lip structure (12) is arranged on the pad part (11) to increase the resilience of the pad part (11). The lip structure (12) is arranged in a rod shape on the upper side of the pad part (11), and may be formed so that the rod shapes intersect in a cross shape. Here, the intersection of the rod shapes may be arranged to be located at the center of the pad part (11), and at least two may be arranged.

[0053] The lip structure (12) can ensure structural stability in the pad section (10) having a radial mesh structure, so that the pad section (10), which is crumpled due to injection through a syringe (S), can be uniformly distributed to quickly spread out within a limited space of about 10 mm to the surface of the cerebral cortex (B5) so that it can recover to its original shape.

[0054] If only one lip structure (12) is installed singly, the sensor unit (10) may not unfold properly due to weak restoring force when it is folded and then unfolded. If too many are installed, for example, 5 to 10 are installed, the structural rigidity may become too strong, which may cause a problem in that the sensor unit (10) may not fold properly. Therefore, in the present invention, for example, two lip structure parts (12) may be installed so as to intersect each other, so that the sensor unit (10) may have appropriate structural rigidity and restoring force so that it can fold and unfold properly.

[0055] The support structure (13) can be formed in a circular shape formed on the outermost surface of the second mesh portion (112), and a plurality of support structures can be formed in the circular shape spaced apart from each other in the circumferential direction.

[0056] If the support structure (13) is not formed in the circular shape formed at the outermost part of the second mesh portion (112), the sensor portion (10) has a flexible shape, so the frequency of folding increases, and a problem may arise in which the sensor portion (10) is folded not only when necessary but also in normal times. Therefore, in the present invention, the support structure (13) is formed in the circular shape formed at the outermost part of the second mesh portion (112), and preferably, three support structures may be formed.

[0057] The sensor (14) can be formed at least in one of the parts where the first mesh portion (111) and the second mesh portion (112) intersect.

[0058] The sensor (14) may include a pressure sensor (141) for measuring intracranial pressure (ICP) and a temperature sensor (142) for measuring intracranial temperature (ICT). Here, the sensor (14) may preferably be a molybdenum sulfide (MoS2)-based sensor. The sensor (14) may be formed by using atomically thin MOCVD-grown molybdenum sulfide (MoS2) as the main conductor sensing channel.

[0059] Since the measurement and stimulation structure (1) is injected into the brain using air pressure, pressure may also be applied within the brain. Accordingly, the pressure sensor (141) monitors the intracranial pressure during the injection of the measurement and stimulation structure (1), thereby ensuring that the injection is performed safely, thereby enhancing the safety of the present invention.

[0060] The pressure sensor (141) is formed of molybdenum dioxide (MoS2) and may have a serpentine structure.

[0061] The temperature sensor (142) closely monitors changes in brain temperature due to a heat generation phenomenon that may occur due to the operation of the measurement and stimulation structure (1) after the measurement and stimulation structure (1) is injected into the brain, thereby improving the safety of the present invention.

[0062] The temperature sensor (142) can be formed of gold (Au) electrodes with interdigitated molybdenum sulfur dioxide (MoS2) sensing channels, which can greatly improve sensitivity and detection within the standard intracranial temperature range.

[0063] The electrode (15) may be formed in at least one of the portions where the first mesh portion (111) and the second mesh portion (112) intersect. Here, the electrode (15) may be formed in a portion where the lip structure portion (12) is arranged on the first mesh portion (111), among the portions where the first mesh portion (111) and the second mesh portion (112) intersect.

[0064] The electrode (15) may be formed of one or more of gold, platinum-iridium alloy, graphene, carbon nanotubes, fullerene, graphite, or diamond, or a composite thereof. Here, the electrode (15) may preferably be a graphene-based sensor. The electrode (15) may be composed of CVD-grown graphene, which allows for a high signal-to-noise ratio (SNR) to precisely measure ECoG signals. This is mainly due to the excellent low contact impedance interface between the graphene-based electrode (15) and the surface of the cerebral cortex (B5). In addition, the inherent mechanical flexibility of graphene ensures that the electrode (15) is not damaged. In the present invention, in order to further minimize the impedance of the electrode (15), four layers of graphene may be used in the contact area with the surface of the cerebral cortex (B5) with interconnections composed of gold (Au).

[0065] The electrode (15) can be configured to measure signals generated in the brain or transmit external stimuli to the brain.

[0066] In this way, the sensor unit (10) of the present invention can maintain both structural integrity and electrical characteristics even when it is crumpled to fit a syringe (S) having a narrow end opening of 1 to 2 mm due to a configuration that secures flexibility through a pad unit (11) having a radial mesh structure and structural rigidity through a lip structure unit (12), and can quickly unfold and recover to its original shape within a limited space of about 10 mm from the end of the syringe (S) to the surface of the cerebral cortex (B5).

[0067] The connecting portion (20) can connect the electric pad portion (30) and the sensor portion (10). The connecting portion (20) can be configured to be connected to the sensor portion (10) in a long manner so that the electric pad portion (30) can interface with a device such as an external reading device (not shown).

[0068] The electric pad portion (30) may be formed for connection to the outside. The electric pad portion (30) may be configured to interface with a device such as an external reading device (not shown).

[0069] The electric pad unit (30) may be an integrated circuit with an external reading device, for example, a wireless chip. The integrated circuit may include a wireless power supply device, a recording device, a stimulation device, and a communication device, and may be a package capable of enhancing biocompatibility.

[0070] The present invention can construct a system in which a measurement and stimulation structure (1) is connected to an external reading device, i.e., an integrated circuit. This system is a system including a measurement and stimulation structure.

[0071] Although the electric pad portion (30) in the embodiment of the present invention is positioned outside the scalp as an example, it may be installed in the space between the skull and the skin. Accordingly, the integrated circuit may be installed in the space between the skull and the skin and connected to the electric pad portion (30).

[0072] Specifically, the wireless power supply unit is for supplying power to the integrated circuit, the recording unit is for recording measured brain waves, the stimulation unit is for providing stimulation to the brain, and the communication unit is a component for transmitting measured brain waves to the outside and receiving external commands.

[0073] Integrated circuits record radio wave measurements received from the brain, thereby acquiring biometric information and detecting abnormal signals. When an abnormality is detected, the integrated circuits apply energy, such as current, voltage, magnetic fields, or electric field stimulation, to neuromodulate the brain, treating the disease or regulating brain activity.

[0074] The integrated circuit includes a wireless chip power supply unit (not shown) which is a wireless power supply device, a recorder (not shown) which is a recording device, a stimulator (not shown) which is a stimulating device, a chip controller (not shown), and a communication device (not shown).

[0075] The wireless chip power supply includes a power regulator (not shown) and a battery (not shown).

[0076] The battery can harvest energy wirelessly using RF coils, etc., and store energy supplied wirelessly.

[0077] The battery can be charged wirelessly using WPT (Wireless Power Transfer) technology.

[0078] The power regulator converts AC from the battery to DC and delivers it to the chip controller.

[0079] EEG measurement uses a recorder to convert analog data into digital data, which is then transmitted to a chip controller. The chip controller then wirelessly transmits the data to an external device via a communication device. The recorder varies depending on the number of EEG measurement panels.

[0080] The recorder can input and convert multi-channel brainwave measurement data into digital signals.

[0081] The chip controller can control measurement signals and stimulus signals.

[0082] The communication device is wirelessly connected to an external communication network to enable monitoring from outside the body. The communication device can wirelessly transmit digital signals converted by the recorder via electrodes or an antenna.

[0083] Integrated circuits must ensure biocompatibility by ensuring that the packaging material of the integrated circuit is compatible with the body to address issues such as packaging heat generation, and the chip must not be affected during encapsulation formation.

[0084] Integrated circuits can be used as packaging materials without limitation as long as they are materials commonly used in vivo in the field, but PDMS (Polydimethylsiloxane), Parylene C, Polyimide, and biocompatible UV resin are suitable.

[0085] Specifically, when brain waves are measured through an electrode (15; graphene electrode layer) exposed to the outside in the sensor section (10) of the measurement and stimulation structure (1) and transmitted to an integrated circuit, they can be wirelessly transmitted to the outside through the integrated circuit.

[0086] If an abnormality is detected in the brainwave signal measured by the chip controller, it is transmitted externally via a communication device and a command is sent to the stimulator, which applies an electrical stimulation signal to the electrode (15). The stimulator varies depending on the number of electrical stimulation channels. The stimulator can generate or transmit the therapeutic stimulation commanded by the chip controller.

[0087] Brain waves measured through the electrodes (15) of the sensor section (10) of the measurement and stimulation structure (1) can be converted into digital signals through a recorder and transmitted to an integrated circuit, and these signals can be wirelessly transmitted to smart devices such as smartphones, smart pads, or computers. One or more of the above recorders can be included.

[0088] Conversely, radio waves received from the outside through the integrated circuit can be transmitted to the brain through the electrode (15) of the sensor section (10) of the measuring and stimulating structure (1).

[0089] Through this process, if an abnormality is detected in the brain waves measured by the electrode (15) of the sensor unit (10), this is transmitted to the outside, and the integrated circuit can be controlled to provide an electric signal, etc. to the electrode (15) of the sensor unit (10). For example, the integrated circuit can transmit a command to a stimulator to stimulate the cerebral cortex. One or more stimulators can be included.

[0090] Meanwhile, the integrated circuit can also play a role in transmitting external radio waves received by a separate wireless communication device to the integrated circuit through electrodes or antennas, thereby transmitting the external radio waves to the brain rather than accepting them as they are.

[0091] In this way, the measurement and stimulation structure (1) and the system including the same according to one embodiment of the present invention have the effect of providing structural stability to the measurement and stimulation structure (1) by installing a lip structure (12) on a pad part (11) of a mesh structure, and when the pad part (11) of a flexible mesh structure is folded and then unfolded upon injection into the brain, there is the effect of exerting an elastic restoring force that is uniformly distributed so that sufficient unfolding can be exerted.

[0092] In addition, the measurement and stimulation structure (1) and the system including the same according to one embodiment of the present invention have a flexible radial mesh structure, thereby having unique mechanical flexibility, and thus having the effect of preventing damage to the structure.

[0093] Through this, the present invention enables minimally invasive implantation for the diagnosis and treatment of various brain diseases, and has the effect of enabling efficient injection and adaptive contact with the cortical surface without damaging brain tissue through a mesh structure with excellent mechanical robustness and flexibility. In addition, when a graphene multi-channel electrode (15) and a molybdenum dioxide-based sensor (14) are suitably contacted with the cerebral cortex surface, seizures can be acutely detected from ECoG signals, and electrical therapy for epileptic discharge control can be performed according to a high signal-to-noise ratio (SNR) and excellent charge transfer efficiency, and there is the effect of clearly monitoring intracranial pressure (ICP) and intracranial temperature (ICT).

[0094] Ultimately, the present invention has the effect of reducing surgical risks in the treatment of various brain diseases and lowering the barriers to devices that can be implanted into the brain.

[0095] Although the present invention has been described in detail through specific embodiments, this is intended to specifically explain the present invention, and the present invention is not limited thereto, and it will be apparent that modifications and improvements can be made by those skilled in the art within the technical spirit of the present invention.

[0096] All simple modifications or changes of the present invention fall within the scope of the present invention, and the specific scope of protection of the present invention will be made clear by the appended claims.

Claims

1. In a structure for signal measurement and electrical stimulation including a sensor section that measures signals generated from the brain or transmits external stimuli to the brain, The above sensor part, A pad portion having a flexible property; and A signal measuring and stimulating structure characterized by including a lip structure disposed on the pad portion to increase the resilience of the pad portion.

2. In the first paragraph, the lip structure part, A signal measuring and stimulating structure characterized in that the structure is arranged in a bar shape on the upper side of the pad portion, and the bar shapes are formed so as to intersect.

3. In the first paragraph, the pad part, A signal measuring and stimulating structure characterized by having a radial mesh structure.

4. In the third paragraph, the pad part, A first mesh portion formed by a plurality of rod-shaped portions extending radially and spaced apart from each other in the circumferential direction; and A signal measuring and stimulating structure characterized by including a second mesh section formed to intersect the rod shape of the first mesh section and configured such that a plurality of concentric circular shapes are spaced apart from each other in a radial direction.

5. In the fourth paragraph, at the part where the first mesh portion and the second mesh portion intersect, A structure for signal measurement and stimulation characterized by having electrodes or sensors installed therein.

6. In paragraph 4, the second mesh portion, A signal measuring and stimulating structure characterized in that a support structure is formed in a circular shape formed at the outermost edge, and a plurality of support structures are formed in the circular shape and spaced apart from each other in the circumferential direction.

7. In the fifth paragraph, the electrode, A signal measuring and stimulating structure characterized by comprising one or more of gold, a platinum-iridium alloy, graphene, carbon nanotubes, fullerene, graphite, or diamond, or a composite thereof.

8. In the fifth paragraph, the electrode, A signal measuring and stimulating structure characterized in that it is installed in a portion where the lip structure is arranged on the first mesh portion.

9. In paragraph 5, The above electrodes measure signals generated in the brain or transmit external stimuli to the brain. The above sensor, A signal measuring and stimulating structure characterized by including a pressure sensor for measuring intracranial pressure (ICP) or a temperature sensor for measuring intracranial temperature (ICT).

10. In any one of paragraphs 1 to 9, Electrical pad section for connection with the outside; and A signal measuring and stimulating structure characterized by further including a connecting portion connecting the electric pad portion and the sensor portion.

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