Plasma brain-machine interface

Abstract

The embodiment of the application provides a kind of plasma brain-computer interface, including brain-computer interface electrode assembly and plasma generation module;The brain-computer interface electrode assembly includes the interface electrode for collecting neural electrical signal;The plasma generation module is integrated with the brain-computer interface electrode assembly to form integrated implant structure, for generating plasma active substance in vivo and acting on the surface of the interface electrode.The plasma brain-computer interface can improve the long-term anti-inflammatory stability of brain-computer interface.

Description

Technical Field

[0001] This application relates to the field of brain-computer interfaces, and more particularly to a plasma brain-computer interface. Background Technology

[0002] Brain-computer interface (BCI) is a technology that enables two-way information exchange between the brain and external devices without relying on peripheral nerves and muscles. Its core is to collect and decode brain neural activity signals through electrode components, and at the same time, it can regulate neural activity through electrical stimulation. It is widely used in the treatment of neurological diseases, neurological rehabilitation, and basic research in brain science.

[0003] Implantable brain-computer interface (BCI) electrodes are prone to causing problems such as immune rejection and glial scar hyperplasia during implantation. Current methods pre-activate the BCI electrode components using plasma before implantation, allowing the activated components to inhibit the release of inflammatory factors and promote tissue repair. However, the activation of the electrode components cannot be maintained for a long time, resulting in low long-term anti-inflammatory stability of the BCI. Summary of the Invention

[0004] The main objective of this application is to propose a plasma brain-computer interface to improve the long-term anti-inflammatory stability of the brain-computer interface.

[0005] To achieve the above objectives, this application proposes a plasma brain-computer interface, including a brain-computer interface electrode assembly and a plasma generation module; The brain-computer interface electrode assembly includes interface electrodes for acquiring neural electrical signals; The plasma generation module and the brain-computer interface electrode assembly are integrated to form an integrated implantable structure, which is used to generate plasma active substances in the body and act on the surface of the interface electrode.

[0006] Optionally, in one embodiment, the plasma brain-computer interface further includes a control module for controlling the operating state of the plasma generating module.

[0007] Optionally, in one embodiment, a hollow cavity is provided inside the interface electrode along the axial direction, and multiple pores are distributed on the surface of the interface electrode. The control module controls the plasma generation module to produce plasma active material into the hollow cavity.

[0008] Optionally, in one embodiment, the interface electrode is composed of an array of multiple independent conductive contact units; The plasma generating module includes multiple plasma electrode plates, which are embedded between adjacent conductive contact units.

[0009] Alternatively, in one embodiment, the plasma electrode sheet includes a flexible conductive substrate, a dielectric material, and a plasma electrode.

[0010] Optionally, in one embodiment, the control module is further configured to detect the working status of the interface electrode and physiological signals in vivo, and adjust the generation parameters of the plasma generator according to the working status and physiological signals in vivo.

[0011] Optionally, in one embodiment, the control module is further configured to receive external communication information and control the working state of the plasma generating module according to the communication information.

[0012] Optionally, in one embodiment, the interface electrode surface is provided with a plurality of storage holes, each storage hole pre-stores plasma gel, the plasma gel being used to slowly release plasma active substances upon contact with body fluids.

[0013] Optionally, in one embodiment, the plasma gel includes a gel matrix and a plasma active substance, wherein the gel matrix is ​​any one of a pH-responsive gel, a ROS-responsive gel, or an enzyme-responsive gel.

[0014] Alternatively, in one embodiment, the surface of the storage hole is covered with a sealing film, which slowly degrades upon contact with bodily fluids.

[0015] As can be seen from the above technical solutions, the embodiments of this application have the following advantages: The plasma generation module is integrated with the brain-computer interface electrode assembly to form an integrated implantable structure. This allows the plasma generation module to directly generate plasma active substances in the body and act on the surface of the interface electrode to inhibit the growth of microorganisms around the electrode, reduce the probability of infection and inflammation, and the plasma generation module can activate the surface of the interface electrode in real time to improve the long-term anti-inflammatory stability of the brain-computer interface. Attached Figure Description

[0016] Figure 1 This is a schematic diagram of the plasma brain-computer interface provided in the embodiments of this application; Figure 2 This is a schematic diagram of the hollow electrode interlocking structure provided in the embodiments of this application; Figure 3 This is a schematic diagram of the plasma electrode sheet fitting method provided in the embodiments of this application; Figure 4 This is a schematic diagram of the plasma gel pre-storage method provided in the embodiments of this application. Detailed Implementation

[0017] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0018] It should be noted that although functional modules are divided in the device schematic diagram and a logical order is shown in the flowchart, in some cases, the steps shown or described may be performed in a different order than the module division in the device or the order in the flowchart. The terms "first," "second," etc., in the specification, claims, and the aforementioned drawings are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence.

[0019] The term “exemplary” as used herein means “serving as an example, embodiment, or illustration.” Any embodiment illustrated herein as “exemplary” is not necessarily to be construed as superior to or better than other embodiments.

[0020] In the embodiments of this application, the terms "module" or "unit" refer to a computer program or part of a computer program that has a predetermined function and works with other related parts to achieve a predetermined goal, and can be implemented wholly or partially using software, hardware (such as processing circuitry or memory), or a combination thereof. Similarly, a processor (or multiple processors or memory) can be used to implement one or more modules or units. Furthermore, each module or unit can be part of an overall module or unit that includes the functionality of that module or unit.

[0021] Furthermore, to better illustrate this application, numerous specific details are provided in the following detailed embodiments. Those skilled in the art should understand that this application can be implemented without certain specific details. In some instances, methods, means, components, and circuits well-known to those skilled in the art have not been described in detail in order to highlight the main points of this application.

[0022] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing embodiments of this application only and is not intended to limit this application.

[0023] First, let's analyze some of the terms used in this application: Implantable brain-computer interfaces (BCIs) are brain-computer interaction devices that involve surgically implanting electrode components directly into the brain (brain tissue or the surface of the cerebral cortex). Their core function is to directly collect electrical signals generated by the activity of brain neurons through the implanted electrodes, without relying on scalp contact. This results in higher signal acquisition accuracy and stronger resistance to interference, enabling direct information exchange between the brain and external devices. Compared to non-implantable BCIs, they avoid signal attenuation and interference from the scalp, making them suitable for long-term clinical applications and helping paralyzed patients and other groups achieve functions such as neural signal transmission and device control.

[0024] Plasma, also known as the fourth state of matter, is distinct from the solid, liquid, and gaseous states. It is a macroscopically neutral ionized gas composed of a large number of charged particles, neutral particles, and reactive free radicals. By applying external energy such as an electric field, electrons in gas molecules or atoms break free from the atomic nucleus, forming a mixed system containing ions, electrons, and highly reactive particles. Low-temperature plasma has wide applications in the biomedical field, as it is rich in reactive oxygen and nitrogen compounds and possesses strong redox capabilities.

[0025] Plasma anti-inflammatory technology primarily relies on cold atmospheric plasma (CAP) to generate reactive oxygen and nitrogen species (RONS) at ambient temperature and pressure, achieving efficient, broad-spectrum inactivation of microorganisms that are less likely to induce drug resistance. During plasma discharge, various key active substances are generated through the ionization and excitation of gases (such as air, argon, and oxygen), including hydroxyl radicals (•OH), singlet oxygen (¹O2), ozone (O3), and superoxide anions (O2•). - Hydrogen peroxide (H2O2), nitric oxide (NO), and peroxynitrite (ONOO) - These RONS exert their anti-inflammatory effects through multiple synergistic mechanisms: RONS, along with electric fields / ultraviolet light / charged particles, form "tunable redox and signal stimulation" on the tissue surface, thereby rapidly reducing microbial load and disrupting biofilms, reducing persistent sources of inflammation; on the other hand, they regulate host immune and tissue repair pathways through signal modulation (inhibiting excessive NF-κB and other pro-inflammatory axes, promoting macrophage transformation to a pro-repair phenotype, improving microcirculation and epithelial barrier, and promoting fibroblast / keratinocyte migration and angiogenesis), achieving a comprehensive anti-inflammatory effect from "anti-infection—immune remodeling—promoting healing".

[0026] Current implantable brain-computer interface (BCI) electrodes trigger acute inflammation and a foreign body reaction upon implantation. Microglia / macrophages rapidly aggregate and release inflammatory factors and reactive oxygen species. Subsequently, astrocytes proliferate, forming glial scars, accompanied by collagen deposition and extracellular matrix remodeling. This increases the effective distance between the electrode and neuron, restricts ion / molecular diffusion, and ultimately manifests as increased impedance, decreased signal amplitude, loss of activity per unit, and poor long-term stability. Current applications of plasma in BCI electrodes primarily focus on surface treatment and etching of electrode materials, i.e., activating the electrode surface to optimize its physicochemical properties and biocompatibility. However, the anti-inflammatory effect of plasma-activated electrode components decays over time after implantation, failing to maintain long-term stability.

[0027] Based on this, embodiments of this application provide a plasma brain-computer interface to solve the above problems.

[0028] Please see Figure 1 The diagram shows a structure of a plasma brain-computer interface, which includes a brain-computer interface electrode assembly and a plasma generation module. The brain-computer interface electrode assembly 11 includes interface electrodes for acquiring neural electrical signals; The plasma generating module 12 and the brain-computer interface electrode assembly 11 are integrated to form an integral implantable structure, which is used to generate plasma active substances in the body and act on the surface of the interface electrode.

[0029] Specifically, the brain-computer interface electrode assembly 11 collects neural electrical signals. That is, the interface electrode is in direct contact with brain tissue and can accurately capture the electrical signals generated by neuronal activity, converting the brain's thought commands and nerve impulses into recognizable electrical signals, providing raw data for subsequent signal processing and external device control.

[0030] The plasma generating module 12 generates highly active plasma-related substances, continuously producing active ingredients with anti-inflammatory and antibacterial effects. This plasma brain-computer interface integrates the plasma generating module 12 with the brain-computer interface electrode assembly 11 into a single, implantable structure, eliminating the need for separate components or external attachments. After implantation, the interface electrodes continuously collect brain nerve signals, enabling information transmission between the brain and external devices. Simultaneously, the plasma-related active substances act on the electrode surface and surrounding tissues, inhibiting bacterial growth, alleviating tissue inflammation, reducing glial scar formation, and preventing electrode performance degradation due to inflammation or tissue encapsulation. Compared to traditional unprotected implantable electrodes, this significantly improves long-term stability and safety, resolving issues such as susceptibility to infection, signal instability, and insufficient long-term reliability in existing implantable brain-computer interfaces.

[0031] For example, the plasma generation module can adopt a low-power, miniaturized design. When anti-inflammatory effects are needed, it uses corona discharge or radio frequency discharge to ionize trace amounts of gas in the surrounding environment (such as interstitial gas or pre-set inert gas), stably generating low-temperature plasma containing RONS (mainly ·OH, H2O2, NO, etc.), high-energy electrons, and active free radicals, thus avoiding damage to brain tissue from high temperatures. The active substances in the plasma can uniformly cover the electrode surface and contact interface. RONS, with its extremely strong redox properties, efficiently inactivates pathogenic microorganisms such as bacteria and viruses that may grow on the electrode surface, avoiding inflammatory responses caused by microbial infection, reducing the risk of immune rejection, and inhibiting glial scar hyperplasia.

[0032] In one embodiment, the plasma brain-computer interface further includes a control module for controlling the operating state of the plasma generation module.

[0033] In this embodiment, the required amount of plasma-active material varies depending on the implantation stage of the brain-computer interface and the different tissue microenvironments. Furthermore, it needs to be coordinated with the signal acquisition of the interface electrodes to avoid interference from plasma in the acquisition of neural electrical signals. Therefore, a control module can be incorporated to precisely regulate the plasma generation module, thereby achieving stability in both anti-inflammatory and electrode signal acquisition.

[0034] The control module features a miniaturized design adapted to the implantation environment, characterized by low power consumption and interference resistance. It can be integrated into a single implantable structure, eliminating the need for external control devices. Through electrical connection, it establishes signal transmission with the plasma generation module, enabling full control over the module's operation. The control module can control the plasma generation module's start-up and shutdown, and adjust its operating duration, discharge power, and action interval according to preset programs or external commands, thereby controlling the timing and amount of plasma-active substances generated. This allows for on-demand and controllable output of plasma-active substances, ensuring anti-inflammatory effects while reducing power consumption and avoiding excessive stimulation of brain tissue, making the plasma's action safer and more suited to the actual needs of the implantation environment.

[0035] In one embodiment, a hollow cavity is provided inside the interface electrode along the axial direction, and multiple pores are distributed on the surface of the interface electrode. The control module controls the plasma generation module to produce plasma active material into the hollow cavity.

[0036] In this embodiment, a hollow cavity is provided inside the interface electrode along its axial direction (i.e., the direction of electrode length extension). This hollow cavity is a pre-reserved, sealed hollow channel extending through the electrode's axial direction. Multiple apertures connected to the hollow cavity are distributed on the electrode surface. This structure provides a dedicated channel for the transport and uniform action of plasma active materials. The plasma generation module controls the generation of plasma active materials inside the hollow cavity. After the active materials form a stable distribution within the cavity, they can diffuse radially outward through the multiple apertures on the electrode surface, uniformly acting on the outer surface of the interface electrode and its surrounding tissue interface.

[0037] Because the plasma active material is delivered directionally through the internal chamber, excessive accumulation in non-target areas can be avoided. This ensures a stable and uniform effect of active material on all parts of the electrode surface while reducing unnecessary stimulation of surrounding normal nerve tissue. The control module can adjust the working intensity and output duration of the plasma generation module according to the actual needs of the implantation interface, thereby controlling the total amount of active material entering the hollow chamber. This allows the active material to be slowly released from the electrode surface pores at an appropriate concentration, achieving continuous antibacterial action on the electrode interface.

[0038] In one example, see Figure 2 The schematic diagram of the hollow interlocking electrode structure shown illustrates that the interface electrode 21 of the brain-computer interface electrode assembly can be made of conductive materials with excellent biocompatibility, such as platinum-iridium alloy or iridium oxide. The overall structure is columnar or needle-shaped, facilitating implantation into brain tissue. A hollow chamber 211 is machined along the length of the electrode 21, extending from one end to form a through-structure, while the other end is sealed to the plasma generation module 12. Several micrometer-sized pores are uniformly machined on the electrode surface, with pore sizes ranging from 1 to 10 μm and adjacent pore spacing ranging from 5 to 20 μm. Each micropore is connected to the internal hollow chamber 211, collectively forming a transport pathway for plasma active substances. This pore size parameter ensures stable outward release of plasma active substances while preventing backflow of brain tissue fluid into the chamber through a size effect.

[0039] The plasma generating module 12 is electrically connected to the power supply control module 22. The plasma generating module 12 employs a needle-type electrode structure, generating low-temperature plasma through corona discharge at the tip of the plasma electrode 121. This plasma can produce plasma-active substances containing reactive oxygen species (such as ·OH, ¹O2) and reactive nitrogen species (such as NO) at room temperature and pressure. The power supply control module 22 can adjust the intensity of the plasma generation to prevent thermal or electrochemical damage to surrounding nerve tissue caused by excessive discharge intensity.

[0040] In particular, at the connection between the plasma generating module 12 and the hollow chamber 211, and at the outer periphery of the micro-apertures on the electrode surface, biocompatible sealing materials such as silicone sealant and polyimide sealants can be used to construct sealing components, thereby ensuring the overall sealing performance of the device. This structural design can prevent plasma active substances from diffusing into non-target areas, while preventing tissue fluid from seeping into the device and preventing internal electronic components from being corroded and damaged.

[0041] The power supply control module 22 is based on a miniaturized pulse power supply design and can be deployed in two ways: subcutaneous implantation or external wearing. It supplies stable power to the plasma generation module through wires, with an operating voltage of 3-5V and an operating current of 10-50mA. This module can adjust the operating frequency and duration of the plasma generation module according to the actual anti-inflammatory needs of the implantation site, with an operating frequency range of 1-10kHz, thereby achieving continuous or intermittent release of plasma active substances.

[0042] Specifically, when the device is implanted in the human body and activated, the power supply control module provides a stable power supply to the plasma generation module. The plasma generation module generates low-temperature plasma in the hollow cavity inside the electrode. Active substances such as reactive oxygen and reactive nitrogen in the plasma accumulate in the cavity. Because the hollow cavity is connected to the tiny apertures on the electrode surface, and there is a slight positive pressure in the cavity (caused by trace amounts of gas generated during the plasma generation process), the active substances are slowly released into the electrode surface and surrounding brain and nerve tissue through the tiny apertures.

[0043] The released plasma active substances possess extremely strong bactericidal and anti-inflammatory effects. They can rapidly destroy the cell membranes and nucleic acid structures of bacteria on the electrode surface and surrounding tissues, inhibiting bacterial growth and reducing the inducing factors of inflammatory responses at their source. Simultaneously, the active substances can regulate the inflammatory microenvironment of surrounding tissues, inhibiting the release of inflammatory factors (such as interleukins and tumor necrosis factor), alleviating inflammatory manifestations such as tissue edema and adhesions, and achieving a sustained anti-inflammatory effect. Throughout the entire operation, the conductivity of the main electrodes of the brain-computer interface remains unaffected. The small pore size on their surface does not interfere with signal transmission between the electrodes and neural tissue, ensuring the normal operation of the brain-computer interface system. The power supply control module can flexibly adjust the plasma generation parameters based on clinical monitoring results to achieve personalized anti-inflammatory treatment, avoiding unnecessary energy consumption and tissue damage.

[0044] In one embodiment, the interface electrode is composed of an array of multiple independent conductive contact units. The plasma generating module includes multiple plasma electrode plates, which are embedded between adjacent conductive contact units.

[0045] In this embodiment, the conductive contact unit is the smallest signal acquisition unit constituting the brain-computer interface electrode, and is an independent block-shaped or sheet-shaped conductive structure. Each conductive contact unit is responsible for acquiring a single neural electrical signal. The units are insulated from each other and electrically disconnected, thereby achieving multi-channel, multi-point signal acquisition and avoiding signal crosstalk between channels. Multiple conductive contact units are arranged in a regular array, which can be arranged in a straight line along the same direction to form a linear array, or arranged in a multi-row, multi-column manner in a plane to form a planar array. After arrangement, a uniform gap is maintained between adjacent conductive contact units, and this gap is used to embed plasma electrode sheets.

[0046] Plasma electrode sheets can generate plasma-active substances by exciting the surrounding medium through micro-discharge. The control module controls the start and stop of the discharge, the discharge intensity, and the working sequence of the plasma electrode sheets by applying corresponding excitation electrical signals, thereby regulating the generation process of plasma-active substances. After the plasma electrode sheets are embedded between two adjacent conductive contact units, they can form distributed discharge sites on the surface of the conductive contact units, allowing the generated active substances to act more uniformly on the electrode interface and improving the antibacterial and anti-inflammatory effects.

[0047] In one embodiment, the plasma electrode sheet includes a flexible conductive substrate, a dielectric material, and a plasma electrode.

[0048] In this embodiment, the flexible conductive substrate has good flexibility and conductivity, and can be arranged to fit the gap between two adjacent conductive contact units, so that the plasma electrode sheet is closely fitted to the electrode structure, adapting to the slight deformation that may occur during implantation, and ensuring that the plasma electrode sheet can still work stably in the complex environment in the body.

[0049] Dielectric material is coated or filled between the flexible conductive substrate and the plasma electrode to achieve electrical isolation and electric field control, avoid short circuits or uneven electric field distribution during discharge, and improve the stability and uniformity of plasma discharge.

[0050] The plasma electrode can generate local micro-discharges under the excitation of electrical signals applied by the control module, thereby exciting the surrounding environment to generate plasma active materials.

[0051] In one example, a schematic diagram of the plasma electrode plate fitting method can be found by referring to... Figure 3As shown, the interface electrodes of the brain-computer interface electrode assembly are made of commonly used conductive materials. The interface electrodes are arranged in a linear array of multiple conductive contact units 212. Plasma electrode sheets 31 are embedded in the gaps between adjacent conductive contact units 212. Conductive connection structures such as conductive adhesive and metal contacts can be set in these gaps to ensure that the plasma electrode sheets 31 can achieve stable electrical contact after assembly.

[0052] The plasma electrode sheet 31 is based on flexible conductive materials such as flexible graphite and conductive polymer. Its surface is coated with a plasma generating layer composed of dielectric material and electrode material. The whole can be tightly embedded in the gap between adjacent conductive contact units 212 and reinforced by a fixing structure such as biocompatible adhesive, so that the electrode sheet 31 is firmly attached to the gap.

[0053] The power supply control module 22 adopts a miniaturized integrated design and supplies power to the plasma electrode sheet 31 through electrical circuits. It can be implanted under the skin or worn externally. It outputs 2-4V low-voltage DC power and controls the working current to 5-30mA to drive the plasma electrode sheet to generate low-temperature plasma and release corresponding active substances.

[0054] The outer surfaces of the conductive contact unit 212 and the plasma electrode sheet 31 can be completely covered with a biocompatible transparent protective coating 32 such as polyethylene glycol. This coating can effectively prevent the plasma electrode sheet from loosening and being corroded by body fluids, and will not hinder the diffusion and release of plasma active substances. At the same time, it has no significant impact on the nerve signal transmission performance of the electrode.

[0055] Specifically, after the device is implanted in the human body, the power supply control module provides a stable low-voltage power supply to the plasma electrode pads. Under the influence of an electric field, the plasma generation layer on the surface of the plasma electrode pads generates low-temperature plasma, producing active substances such as reactive oxygen species and reactive nitrogen species. Because the plasma electrode pads are directly embedded in the surface of the main electrode and in close contact with surrounding tissues, the generated active substances can be directly released into the electrode surface and surrounding tissues, rapidly destroying bacterial structures, inhibiting bacterial growth, and simultaneously regulating the inflammatory microenvironment to alleviate inflammatory responses. The power supply control module can adjust the power supply parameters according to anti-inflammatory needs, controlling the intensity and duration of plasma generation to achieve continuous or intermittent release of active substances. The protective coating protects the plasma electrode pads from corrosion by body fluids and tissue friction, extending the device's lifespan without affecting the electrode's signal transmission performance.

[0056] In one embodiment, the control module is also used to detect the working status of the interface electrode and physiological signals in vivo, and adjust the generation parameters of the plasma generator according to the working status and physiological signals in vivo.

[0057] In this embodiment, the working status of the interface electrode mainly includes indicators such as signal acquisition amplitude, contact impedance, and signal-to-noise ratio, which can reflect whether the electrode's performance is degraded due to tissue encapsulation or scar hyperplasia.

[0058] Physiological signals within the body include microenvironmental parameters such as local inflammation levels, pH value, and temperature, which are used to determine whether there is infection or immune rejection in the tissue.

[0059] After acquiring the working status and physiological signals within the body, the control module can adjust the generation parameters of the plasma generation module through internal logic, including discharge voltage, working duration, action interval, and output intensity, so that the generation and release of plasma active substances match the actual tissue state. For example, when an increase in electrode impedance or a local inflammatory trend is detected, the control module can automatically increase the plasma generation intensity; when the body state is stable and signal acquisition is normal, it reduces the output or enters standby mode, thereby achieving precise and adaptive regulation. This ensures both the antibacterial and anti-inflammatory effects and improved biocompatibility, while avoiding excessive discharge that could stimulate brain tissue, thus improving the safety and stability of the device during long-term use.

[0060] In one embodiment, the control module is also used to receive external communication information and control the working state of the plasma generating module according to the communication information.

[0061] In this embodiment, the control module can also be configured with an external communication function, which can receive communication information sent by external communication devices (such as external controllers and terminal devices). The communication information may include manual control commands, parameter setting commands, and working mode switching commands, such as specific commands to start / stop plasma generation, adjust discharge power, and set working time.

[0062] After receiving external communication information, the control module analyzes and processes the information, combining it with previously detected interface electrode operating status and in vivo physiological signals to comprehensively determine and control the working state of the plasma generator module, adjusting its generation parameters. For example, when medical personnel send a command to "increase plasma output intensity" via external devices, the control module can adjust the discharge voltage and current of the plasma generator module to increase the amount of active substances generated, provided that the current tissue condition allows it. When receiving a "standby" command, the control module stops the plasma generator module from working, maintaining only signal detection functionality. This achieves intelligent adaptive control of the plasma generator module while retaining the flexibility of manual intervention.

[0063] In one embodiment, the interface electrode surface is provided with a plurality of storage holes, each storage hole pre-stores plasma gel, which is used to slowly release plasma active substances after contact with body fluids.

[0064] In this embodiment, the interface electrode surface can be provided with multiple uniformly distributed storage holes. The storage holes are miniature accommodating structures opened on the electrode surface, which can be pre-filled and sealed with plasma gel.

[0065] Plasma gels can be biocompatible polymeric sustained-release carriers loaded with components that can be continuously excited to generate plasma-active factors.

[0066] After implantation, the plasma gel within the storage pores comes into contact with and is gradually activated by the body's tissue fluid and bodily fluids. Through its own slow degradation and diffusion, it continuously and steadily releases plasma-active substances to the interface electrode surface and surrounding tissues. This passive, sustained-release mechanism can inhibit the growth of microorganisms at the electrode interface, reduce local inflammation, and decrease glial scar hyperplasia, thereby maintaining a healthy interface between the electrode and brain tissue, ensuring the stability of neural signal acquisition. Simultaneously, it significantly simplifies the overall structure and improves the reliability and long-term lifespan of the implanted device.

[0067] In one embodiment, the plasma gel includes a gel matrix and a plasma-active substance, wherein the gel matrix is ​​any one of a pH-responsive gel, a ROS-responsive gel, or an enzyme-responsive gel.

[0068] In this embodiment, the plasma gel is composed of a gel matrix and plasma-active substances loaded thereon. The gel matrix is ​​a biocompatible polymer material with environmental responsive characteristics, specifically any one of pH-responsive gel, ROS-responsive gel, or enzyme-responsive gel.

[0069] Once the interface electrode is implanted, the gel matrix can sense changes in the surrounding tissue microenvironment. When abnormal states such as inflammation, infection, or immune response occur in the tissue, corresponding changes in pH, increased reactive oxygen species levels, or upregulation of specific enzyme expression trigger swelling, degradation, or structural loosening of the gel matrix, thereby gradually releasing the plasma-active substances loaded within it to the electrode interface. This responsive sustained-release method can adaptively adjust the release rate according to the actual physiological state of the tissue. When there is a risk of inflammation, it releases plasma-active substances in a timely manner to exert antibacterial and anti-inflammatory effects, while maintaining a low release or temporary storage state when the tissue condition is stable. This not only continuously improves the biocompatibility of the electrode interface and inhibits glial scar hyperplasia, but also avoids the ineffective consumption of plasma-active substances, enabling the interface electrode to maintain stable signal acquisition performance during long-term implantation.

[0070] In one embodiment, the surface of the storage hole is covered with a sealing film that slowly degrades upon contact with bodily fluids.

[0071] In this embodiment, each storage hole is covered with a sealing film. This sealing film provides a protective seal for the plasma gel, preventing premature leakage, inactivation, or contamination by external impurities before and during the initial implantation phase. The sealing film is made of a biodegradable medical polymer material. After the interface electrode is implanted, the sealing film gradually comes into contact with the surrounding tissue fluids and slowly degrades. As the sealing film gradually dissolves and breaks down, the plasma gel inside the storage hole is exposed and comes into contact with the body fluids. This delayed degradation of the sealing film allows for a delayed release of the plasma gel, avoiding premature release of active substances during the surgical implantation phase and ensuring that the antibacterial, anti-inflammatory, and biocompatibility-improving effects on the electrode interface are fully realized once the post-implantation tissue environment is stable, further enhancing the reliability and durability of long-term implantation.

[0072] In one example, a schematic diagram of the plasma gel pre-storage method can be found by referring to... Figure 4 As shown, the interface electrode 21 of the brain-computer interface electrode assembly is made of a medical material with good conductivity. Multiple storage holes 213 are machined on the surface of the end of the electrode intended for implantation. These storage holes 213 are used for pre-loading plasma gel 41. To improve loading stability, the inner wall of the storage hole 213 can be hydrophilically modified, allowing the gel to adhere tightly to the hole wall and preventing it from easily falling off or shifting during implantation and use.

[0073] Plasma gel 41 can use biocompatible polymer materials such as hyaluronic acid gel and chitosan gel as the gel matrix, internally loaded with plasma-active ingredients, and has an overall semi-solid state. This gel has stable sustained-release properties in the in vivo environment, and can gradually release plasma-active substance precursors; when the precursors come into contact with tissue fluid, a corresponding reaction will occur, generating in situ plasma-active substances with anti-inflammatory effects such as reactive oxygen species and reactive nitrogen species, thereby improving the microenvironment of the electrode implantation interface.

[0074] The fixation component employs a biodegradable sealing membrane 42, which covers the opening of the storage port 213. This membrane effectively blocks tissue contact during implantation, preventing premature gel loss. After implantation, the sealing membrane 42 is gradually degraded by bodily fluids without hindering the normal release of the active substance precursor. The entire surface of the electrode 21 and the exterior of the sealing membrane are also covered with a protective coating 43, further optimizing the device's biocompatibility and enhancing the overall stability and reliability of the structure during long-term use in vivo.

[0075] In the description of this invention, the terms "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of the invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

Claims

1. A plasma brain-computer interface, characterized in that, Includes brain-computer interface electrode components and plasma generation module; The brain-computer interface electrode assembly includes interface electrodes for acquiring neural electrical signals; The plasma generating module is integrated with the brain-computer interface electrode assembly to form an integral implantable structure, which is used to generate plasma active substances in the body and act on the surface of the interface electrode.

2. The plasma brain-computer interface according to claim 1, characterized in that, The plasma brain-computer interface also includes a control module, which is used to control the working state of the plasma generation module.

3. The plasma brain-computer interface according to claim 2, characterized in that, The interface electrode has a hollow cavity arranged along the axial direction inside, and the surface of the interface electrode has multiple holes of different diameters. The control module controls the plasma generating module to generate the plasma active material into the hollow cavity.

4. The plasma brain-computer interface according to claim 2, characterized in that, The interface electrode is composed of an array of multiple independent conductive contact units. The plasma generating module includes multiple plasma electrode plates, which are embedded between adjacent conductive contact units.

5. The plasma brain-computer interface according to claim 4, characterized in that, The plasma electrode sheet includes a flexible conductive substrate, a dielectric material, and a plasma electrode.

6. The plasma brain-computer interface according to claim 2, characterized in that, The control module is also used to detect the working status of the interface electrode and the physiological signals in vivo, and adjust the generation parameters of the plasma generator according to the working status and the physiological signals in vivo.

7. The plasma brain-computer interface according to claim 2, characterized in that, The control module is also used to receive external communication information and control the working state of the plasma generating module according to the communication information.

8. The plasma brain-computer interface according to claim 1, characterized in that, The interface electrode surface is provided with multiple storage holes, each storage hole pre-stores plasma gel, which is used to slowly release plasma active substances after contact with body fluids.

9. The plasma brain-computer interface according to claim 8, characterized in that, The plasma gel comprises a gel matrix and a plasma-active substance, wherein the gel matrix is ​​any one of a pH-responsive gel, a ROS-responsive gel, or an enzyme-responsive gel.

10. The plasma brain-computer interface according to claim 8, characterized in that, The surface of the storage hole is covered with a sealing film, which slowly degrades upon contact with bodily fluids.

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