A minimally invasive intracerebral passive-attached brain-computer interface system based on neuroendoscope

Abstract

The application provides a minimally invasive intracerebral passive adhering brain-computer interface system based on a neuroendoscope, a minimally invasive neuroendoscope implanting module provides a channel and a visual field, and is an operation entrance of the system; a flexible passive chip is a function execution core, signal acquisition, stimulation or drug release are realized; a fixing and adhering module provides structural stability, and reliable long-term operation is ensured; and an external energy / signal coupling module constitutes an energy and information interaction interface, and closed loop control and feedback of the system are realized. Through space position, energy transmission and signal channels, the four modules form a multi-layer cooperative system, and finally precise implantation, stable work and remote control of the intracerebral flexible function chip are realized. The application adopts the above-mentioned minimally invasive intracerebral passive adhering brain-computer interface system based on a neuroendoscope, has good clinical operability and engineering expandability, and provides a reliable implementation path for local precise treatment, neural regulation and brain-computer interface application of central nervous system diseases.

Description

Technical Field

[0001] This invention relates to the field of neurointervention and brain-computer interface, and in particular to a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy. Background Technology

[0002] Currently, intracranial implantable devices are mainly divided into two categories: one is puncture-type catheters or electrode systems, such as ventricular drainage tubes, deep brain stimulators (DBS), and drug infusion pumps; the other is surface-attached or flexible membrane sensors used for recording signals on the brain surface or in the sulci. While both types of devices have their advantages, they also have significant limitations. Puncture-type devices require penetrating the brain parenchyma to reach the target area, which can easily cause tissue tearing, vascular damage, and chronic inflammation. Long-term implantation can also lead to glial scarring, resulting in electrode signal attenuation or drug flow obstruction. While surface-attached devices can reduce tissue damage, they are limited by the implantation channel and fixation method, making stable deployment on the surface or deep regions of the ventricles difficult. Especially in the fluid environment of flowing cerebrospinal fluid, the chip is prone to drift or detachment, severely affecting its functional stability and data reliability.

[0003] On the other hand, traditional intracranial implantable devices generally rely on external leads or internal batteries for power. The presence of leads increases the risk of infection and mechanical traction, while also restricting the patient's freedom of movement; internal power sources are limited by size and lifespan, making long-term use difficult. To address this issue, passive implantable microsystems based on mechanisms such as magnetothermal, photothermal, and electromagnetic induction have emerged in recent years, enabling wireless power supply and functional triggering under the influence of external physical fields. However, the application of such systems is still limited by the design of the implantation location and energy transfer path; their operational stability, heat dissipation safety, and packaging reliability all depend on precise implantation methods and fixation strategies.

[0004] Therefore, developing a minimally invasive implantation pathway that can achieve precise positioning and is compatible with the functions of multiple passive chips is a key step in promoting the clinical application of intracranial therapy and brain-computer interface technology. Summary of the Invention

[0005] The purpose of this invention is to provide a minimally invasive passive intracranial attachment brain-computer interface system based on neuroendoscopy, which enables the attachment and stable fixation of various types of micro-devices such as drug-loaded chips, passive EEG acquisition chips, or passive stimulation chips on the surface of the ventricles or the superficial layer of the brain parenchyma. It is applicable to scenarios such as local intracranial treatment, monitoring, and regulation.

[0006] To achieve the above objectives, the present invention provides a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy, comprising: The minimally invasive neuroendoscopic implantation module is used to establish a safe implantation channel, provide a visual operating environment, and achieve precise chip delivery and positioning. A flexible passive functional chip is used to realize the local release of drugs in the brain, the acquisition of electrical signals, the sensing and regulation of nerve stimulation or other physiological parameters; the flexible passive functional chip includes, but is not limited to, one or more of the following: drug-carrying chip, passive EEG signal acquisition chip, and passive stimulation chip. A fixation and adhesion module is used to ensure that flexible passive functional chips can maintain long-term stable adhesion even under cerebrospinal fluid flow and slight displacement of brain tissue. The external energy / signal coupling module provides non-contact energy excitation and signal interaction for the flexible passive functional chip, enabling remote control and data acquisition.

[0007] Preferably, the minimally invasive neuroendoscopic implantation module includes a cranial microbone window unit, a flexible endoscope unit, an imaging device unit, and a delivery sheath unit; The cranial microbone window unit provides a fixed channel for flexible endoscopes and delivery sheaths to enter the ventricles by creating a microbone window in the target brain region. The microbone window not only serves as the entry point for endoscope insertion but also provides a stable support surface, allowing the endoscope and delivery instruments to maintain a fixed angle and orientation during insertion. The flexible endoscope unit, including fiber optic bundles, imaging channels, and flexible guide structures, moves flexibly within the curved ventricles or sulci of the brain. The flexible endoscope tip is responsible for acquiring real-time images of the brain tissue and can adjust its direction in narrow spaces, entering the ventricles through the cranial micro-bone window unit. The imaging unit includes a high-definition camera, a cold light source, and an image processing interface. It is connected to the flexible endoscope unit via a fiber optic link to transmit the ventricle images acquired by the endoscope to an external control terminal in real time. The imaging unit can provide stable brightness, clear images, and real-time feedback with extremely low latency. The delivery sheath unit is coaxially arranged along the outside of the flexible endoscope unit to stably advance the flexible passive functional chip along the sheath without folding, twisting or shifting; the front port of the sheath is designed with a compliant structure to provide flexible support when the flexible passive functional chip is pushed out, helping the flexible passive functional chip to unfold smoothly in the ventricle or target area and attach to the target surface.

[0008] Preferably, the fixation and adhesion module includes a mechanical support unit, a bio-adhesion unit, and a suture fixation unit; The mechanical support unit designs micro-bumps, grooves, or micro-flexible needles on the bottom of the flexible passive functional chip to provide friction or micro-scale embedding effect when the flexible passive functional chip is first attached to brain tissue. The bioadhesion unit provides durable chemical adhesion on the basis of mechanical fixation, enabling the flexible passive functional chip to remain stable in the long-term cerebrospinal fluid flushing environment; in the part of the flexible passive functional chip that contacts the tissue, bioadhesion materials such as dopamine or catechol-based modified hydrogels are used. The suture fixation unit has suture holes pre-drilled at the edge of the flexible passive functional chip. By connecting with absorbable sutures, the edge of the flexible passive functional chip is lightly sutured in the early stage of implantation, which enhances the overall mechanical stability and prevents the flexible passive functional chip from shifting due to small movements of brain tissue.

[0009] Preferably, the external energy / signal coupling module includes: The alternating magnetic field coil unit generates a high-frequency magnetic field that couples with the magnetocaloric material in the flexible passive functional chip, causing the thermally driven film to heat up and generate mechanical driving force, thereby realizing thermally triggered drug release. The alternating magnetic field coil achieves deep energy transfer in a non-contact manner, enabling remote control. The near-infrared light source unit uses tissue-penetrable NIR light to excite the photothermal layer in the flexible passive functional chip through direct irradiation or fiber optic transmission, causing it to generate local heating or deformation, thereby triggering drug release or regulating functional elements. Radio frequency transmitting coil unit: The radio frequency transmitting coil unit forms an electromagnetic coupling with the LC resonant unit or spiral induction coil in the flexible passive functional chip to realize wireless power supply and signal feedback; the unit remotely drives the flexible passive functional chip to work by tuning the radio frequency, field strength and modulation mode, and receives its feedback signal. Control terminal unit: The control terminal unit is responsible for adjusting the output of all external energy modules, including power, frequency, mode and duration; at the same time, the control terminal unit can also receive signals back from the flexible passive functional chip in real time for functional verification, status monitoring and closed-loop control.

[0010] A method for using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy includes the following steps: Preoperative preparation and establishment of microbone windows: First, the operator determines the target implantation location based on imaging data and establishes a cranial microbone window in the area of ​​the target implantation location; the microbone window serves as the access channel for the endoscope and provides an initial fixation point for the flexible endoscope, enabling the endoscope to enter the ventricle or sulcus at a controlled angle and direction; Flexible laparoscope insertion and visual navigation: The flexible laparoscope is slowly inserted into the brain through a micro-bone window. The optical fiber at the front end of the laparoscope is connected to the imaging device, which displays images of the ventricular structure, blood vessel distribution and target tissue area in real time on the operating terminal. The operator adjusts the direction and depth of the laparoscope through visual navigation and fixes the position of the laparoscope when it approaches the target area, providing a stable guide path for the delivery of the sheath. Delivery sheath advancement and chip introduction: The delivery sheath is advanced coaxially along the endoscope guide sleeve. The flexible passive functional chip is pre-loaded in the front chamber of the sheath. After the sheath enters the target area, the flexible chip is smoothly released by the control push rod. The sheath and endoscope maintain a coaxial structure to ensure that the chip can unfold in the expected posture and adhere to the tissue surface. Chip Deployment and Fixation: After deployment, the chip's flexible structure automatically unfolds to conform to the surface of the brain tissue. The mechanical support structure at the bottom of the chip generates initial friction or microscale interlocking with the tissue surface, providing the first layer of fixation force. Simultaneously, the bioadhesive hydrogel in the bioadhesion unit rapidly solidifies in a wet state, forming chemical bonds with the brain tissue surface, thereby enhancing the chip's adhesion stability. Light absorbable sutures are performed using pre-reserved suture holes to ensure that the chip does not shift with tissue movement in the early stages. External energy source positioning and coupling matching: After implantation, the operator places the external energy module in the corresponding body surface area. The alternating magnetic field coil unit and the near-infrared light source unit are set with power, frequency and excitation mode through the control terminal, and then the energy output is started. The energy is conducted to the implanted chip through the tissue and coupled with the thermo-driven membrane, spiral coil or LC resonant unit inside the chip, thereby triggering drug release, signal acquisition or generation of stimulation pulses. Functional Triggering and Closed-Loop Monitoring: When external stimulation is initiated, the thermodynamic driving membrane of the drug-loaded chip heats up and deforms, thereby driving the drug solution in the storage cavity to be precisely released to the target tissue through the microfluidic channel and hollow microneedle array, realizing local on-demand drug delivery; the passive acquisition chip receives external energy through a spiral induction coil and activates the signal modulator to collect EEG or local field potentials and transmit them wirelessly; the passive stimulation chip outputs stimulation pulses through a bipolar electrode array under radio frequency coupling to achieve local neural modulation; the external control terminal monitors the transmitted signals in real time and can adjust the stimulation parameters as needed to achieve closed-loop control; Long-term use and follow-up: The mechanical support, chemical adhesion and suture structure of the fixation and adhesion system ensure that the chip remains stably attached under long-term cerebrospinal fluid flushing and tissue pulsation; the external energy / signal coupling module can be reactivated as needed in subsequent treatment or monitoring cycles; the passive chip does not require an internal battery and can also operate for a long time, thereby meeting the actual needs of disease monitoring, local treatment or neuromodulation.

[0011] Therefore, the present invention employs the above-mentioned minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy, and the technical effects are as follows: By creating a micro-bone window of about 1 cm in diameter at the top of the skull and operating under direct vision using a neuroendoscopy, the flexible chip was precisely attached to the surface of the ventricle or the area adjacent to the lesion without penetrating the brain parenchyma. This significantly reduced the risk of tissue trauma and bleeding, and improved the accuracy and safety of implantation positioning.

[0012] The microstructures at the bottom of the chip, together with the catechol-based or dopamine-modified hydrogel and surgical sutures, can form a high-strength bioadhesion in the continuously flowing cerebrospinal fluid wet environment, ensuring that the chip is stably anchored to the target area for a long time, preventing drift or detachment, and ensuring the stability and reliability of long-term in vivo signal acquisition, stimulation or drug release.

[0013] The standardized implantation pathway proposed by this method can be applied to three types of functional modules: drug-loaded chips, passive EEG signal acquisition chips, and passive stimulation chips. This constructs a multifunctional implantation platform that is both universal and scalable, and can simultaneously support multiple biomedical functions such as quantitative release of local drugs in the brain, monitoring of neural electrical activity, and electromagnetic stimulation modulation, significantly improving the integration and practicality of the brain implantation system.

[0014] This method is compatible with multi-mode coupling power supply mechanisms that utilize magnetic fields, optical fields, and radio frequency energy, achieving completely passive wireless drive and avoiding the problems of infection, traction, and lifespan limitations associated with traditional wire or battery power supply.

[0015] The chip is made of flexible, bio-inert materials, which are mechanically highly compatible with brain tissue. It also features temperature- and pressure-limiting and leak-proof encapsulation designs, which can maintain signal stability and biosafety in long-term implantation environments.

[0016] This invention achieves systematic innovation in minimally invasive pathway design, interface anchoring, energy coupling, and functional compatibility, providing a safe, reliable, and scalable engineering approach for local precision treatment of central nervous system diseases, neuromodulation, and brain-computer interface applications. Attached Figure Description

[0017] Figure 1 This is a flowchart of a minimally invasive passive intracerebral attachment brain-computer interface method based on neuroendoscopy according to the present invention; Figure 2 This is a schematic diagram of a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to the present invention. Detailed Implementation

[0018] The technical solution of the present invention will be further described below with reference to the accompanying drawings and embodiments.

[0019] Unless otherwise defined, the technical or scientific terms used in this invention shall have the ordinary meaning as understood by one of ordinary skill in the art to which this invention pertains.

[0020] Example 1 like Figure 2 As shown, a minimally invasive, passively attached brain-computer interface system based on neuroendoscopy comprises four core modules: a minimally invasive neuroendoscopic implantation module, a flexible passive functional chip, a fixation and adhesion module, and an external energy / signal coupling module. These four modules work together organically through mechanical transmission paths, imaging vision links, energy coupling channels, and signal feedback loops to achieve precise implantation, stable fixation, remote stimulation, and functional execution of the flexible passive chip.

[0021] The minimally invasive neuroendoscopic implantation module is used to establish a safe implantation channel, provide a visual operating environment, and achieve precise chip delivery and positioning.

[0022] Skull micro-bone window unit: By creating a micro-bone window in the target brain region, a fixed channel is provided for the flexible endoscope and delivery sheath to enter the ventricle. This bone window not only serves as the entry point for endoscope insertion but also provides a stable support surface, allowing the endoscope and delivery instruments to maintain a fixed angle and orientation during insertion, thereby reducing operational deviation and laying the foundation for precise chip positioning.

[0023] The flexible endoscope unit, composed of fiber optic bundles, imaging channels, and flexible guiding structures, allows for flexible movement within the curved pathways of the ventricles or sulci. The endoscope's tip is responsible for acquiring real-time images of the brain tissue's interior and can adjust its orientation within confined spaces. It enters the ventricles through the cranial micro-bone window unit and is the core component of the system for achieving internal visualization and operational guidance.

[0024] The imaging unit includes a high-definition camera, a cold light source, and an image processing interface. It is connected to the flexible endoscope unit via a fiber optic link to transmit real-time images of the brain ventricles acquired by the endoscope to an external control unit. This unit provides stable brightness, clear images, and real-time feedback with extremely low latency, enabling operators to make accurate judgments and avoid damaging brain tissue. It also provides reliable visual support for chip deployment and attachment.

[0025] Delivery sheath unit: Coaxially arranged along the outer side of the flexible endoscope unit, it is used to stably advance the flexible passive functional chip along the sheath without folding, twisting, or shifting. The front port of the sheath is designed with a compliant structure to provide flexible support when the chip is pushed out, ensuring that the chip can be smoothly deployed and attached to the target surface in the ventricle or target area.

[0026] Flexible passive functional chips (implanted devices) serve as the core execution unit of the system, enabling local drug release in the brain, electrical signal acquisition, and the sensing and regulation of neural stimulation or other physiological parameters. Flexible passive functional chips include, but are not limited to, one or more of the following: drug-loaded chips, passive EEG signal acquisition chips, and passive stimulation chips. Depending on clinical needs, one of the following types can be selected or used in combination: Drug delivery chip Drug storage chamber unit: The drug storage chamber unit adopts a flexible closed cavity structure to accommodate solution, colloidal, or suspension drugs. Its material can achieve leakage prevention and stability through flexible polymers or multi-layer composite structures, and it is directly connected to the microfluidic channel unit to ensure that the internal drug solution can be effectively driven into the delivery path.

[0027] Microfluidic channel unit: The microfluidic channel unit consists of several micrometer-level channels, connecting the drug storage chamber unit to the hollow microneedle array unit. This unit is used for quantitative output of drug solution by designing the channel width, length, and flow resistance.

[0028] Hollow microneedle array unit: Located on the side of the chip attached to the tissue, the hollow microneedle array unit allows drugs to directly enter the target area by slightly penetrating the ventricular epithelium or tissue surface through its micro-tip. Each microneedle corresponds one-to-one with a microfluidic channel, forming a closed "drug storage-channel-microneedle" path for rapid and precise local drug delivery and fixation.

[0029] Thermo-driven membrane unit: Located behind the drug storage chamber unit, the thermo-driven membrane unit is composed of magnetocaloric material, photothermal film, or electrothermal element. When an external alternating magnetic field, near-infrared light, or radio frequency energy enters the body, the membrane can rapidly heat up or deform, thereby increasing the pressure inside the drug storage chamber and pushing the drug solution into the microfluidic channel for on-demand and quantitatively driven closed-loop release.

[0030] Passive EEG signal acquisition chip Flexible electrode array unit: Constructed of highly flexible conductive material, arranged in a multi-channel grid, it can closely adhere to the surface of brain tissue and acquire local EEG signals or field potentials. Due to its ultra-thin and flexible properties, it maintains stable contact even when the brain tissue undergoes slight deformation, improving signal quality and biocompatibility. Used for acquiring local EEG signals or field potentials.

[0031] The helical induction coil unit, connected to the flexible electrode array unit, forms electromagnetic coupling with an external radio frequency coil through an optimized helical structure, enabling the chip to obtain operating power through external energy excitation without the need for a battery. Simultaneously, this coil can wirelessly transmit modulated EEG signals back externally, providing a stable data pathway for closed-loop monitoring.

[0032] Signal modulation unit: Located between the electrode array unit and the helical coil unit, it is used to perform amplitude modulation, frequency modulation, or impedance modulation on the acquired signal to enhance anti-interference and signal recognition. The electrical signal modulated by this unit will be transmitted through the helical coil to establish a stable wireless communication link with the external receiving module.

[0033] Passive Stimulation Chip Miniature LC resonant unit: Composed of a resonant structure consisting of capacitors and inductors, it is coupled to an external RF transmitting coil. This unit is used to absorb external RF energy and generate an induced electric field locally, and is the main energy harvesting component of the passive stimulation chip.

[0034] Bipolar electrode array unit: Connected to the output of the LC resonant unit, it converts the induced voltage into local stimulation pulses for targeted stimulation of brain regions or neural structures. Its fine wiring and flexible substrate allow it to conform to the tissue surface, ensuring the precision of stimulation.

[0035] Current limiting and protection circuit unit: Composed of a current-limiting resistor, impedance regulator, or temperature protection structure, it is used to limit the stimulation intensity, prevent local overheating, and ensure tissue safety. This unit plays a protective role in the stimulation path, ensuring that stimulation is performed within a safe range.

[0036] The fixation and adhesion module ensures that the chip can maintain stable long-term adhesion even under the flow of cerebrospinal fluid and slight displacement of brain tissue.

[0037] Mechanical support unit: Microbumps, grooves or micro-flexible needles are designed on the bottom of the chip. These structures provide friction or microscale embedding when the chip is first attached to brain tissue, making the chip less prone to slippage and serving as the mechanical basis for subsequent chemical adhesion.

[0038] Bioadhesion Unit: At the contact point between the chip and tissue, bioadhesive materials such as dopamine or catechol-modified hydrogels are used. These materials can rapidly solidify in a wet state and form a tight bond with the tissue surface. This unit provides durable chemical adhesion on top of mechanical fixation, enabling the chip to remain stable in long-term cerebrospinal fluid flushing environments.

[0039] Suture fixation unit: Suture holes are reserved at the edge of the chip. By connecting with absorbable sutures, the edge of the chip can be lightly sutured in the early stage of implantation, which can enhance the overall mechanical stability and prevent the chip from shifting due to small movements of brain tissue.

[0040] The external energy / signal coupling unit provides non-contact energy excitation and signal interaction for the passive chip, enabling remote control and data acquisition.

[0041] Alternating Magnetic Field (AMF) Coil Unit: This unit generates a high-frequency magnetic field that couples with the magnetocaloric material in the chip, causing the thermally driven film to heat up and generate a mechanical driving force, thereby achieving thermally triggered drug release. This unit achieves deep energy transfer in a non-contact manner and features remote controllability.

[0042] Near-infrared light source unit: Utilizing tissue-penetrating NIR light, it excites the photothermal layer in the chip through direct irradiation or fiber optic transmission, causing localized heating or deformation, thereby triggering drug release or regulating functional elements. Its advantages lie in precise activation, controllable timing, and strong localization.

[0043] Radio frequency (RF) transmitting coil unit: This unit forms an electromagnetic coupling with the LC resonant unit or spiral induction coil within the chip, enabling wireless power supply and signal feedback. By tuning the RF frequency, field strength, and modulation method, this unit can remotely drive the passive functional chip and receive its feedback signals.

[0044] Control terminal unit: Responsible for regulating the output of all external energy modules, including power, frequency, mode, and duration. Simultaneously, this terminal can receive signals from the chip in real time for functional verification, status monitoring, and closed-loop control, serving as the command center of the entire system.

[0045] like Figure 1 As shown, a method for using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy includes the following steps: Preoperative preparation and establishment of microbone windows: First, the operator determines the target implantation location based on imaging data and establishes a cranial microbone window in the area of ​​the target implantation location; the microbone window serves as the access channel for the endoscope and provides an initial fixation point for the flexible endoscope, enabling the endoscope to enter the ventricle or sulcus at a controlled angle and direction; Flexible laparoscope insertion and visual navigation: The flexible laparoscope is slowly inserted into the brain through a micro-bone window. The optical fiber at the front end of the laparoscope is connected to the imaging device, which displays images of the ventricular structure, blood vessel distribution and target tissue area in real time on the operating terminal. The operator adjusts the direction and depth of the laparoscope through visual navigation and fixes the position of the laparoscope when it approaches the target area, providing a stable guide path for the delivery of the sheath. Delivery sheath advancement and chip introduction: The delivery sheath is advanced coaxially along the endoscope guide sleeve. The flexible passive functional chip is pre-loaded in the front chamber of the sheath. After the sheath enters the target area, the flexible chip is smoothly released by the control push rod. The sheath and endoscope maintain a coaxial structure to ensure that the chip can unfold in the expected posture and adhere to the tissue surface. Chip Deployment and Fixation: After deployment, the chip's flexible structure automatically unfolds to conform to the surface of the brain tissue. The mechanical support structure at the bottom of the chip generates initial friction or microscale interlocking with the tissue surface, providing the first layer of fixation force. Simultaneously, the bioadhesive hydrogel in the bioadhesion unit rapidly solidifies in a wet state, forming chemical bonds with the brain tissue surface, thereby enhancing the chip's adhesion stability. Light absorbable sutures are performed using pre-reserved suture holes to ensure that the chip does not shift with tissue movement in the early stages. External energy source positioning and coupling matching: After implantation, the operator places the external energy module in the corresponding body surface area. The alternating magnetic field coil unit and the near-infrared light source unit are set with power, frequency and excitation mode through the control terminal, and then the energy output is started. The energy is conducted to the implanted chip through the tissue and coupled with the thermo-driven membrane, spiral coil or LC resonant unit inside the chip, thereby triggering drug release, signal acquisition or generation of stimulation pulses. Functional Triggering and Closed-Loop Monitoring: When external stimulation is initiated, the thermodynamic driving membrane of the drug-loaded chip heats up and deforms, thereby driving the drug solution in the storage cavity to be precisely released to the target tissue through the microfluidic channel and hollow microneedle array, realizing local on-demand drug delivery; the passive acquisition chip receives external energy through a spiral induction coil and activates the signal modulator to collect EEG or local field potentials and transmit them wirelessly; the passive stimulation chip outputs stimulation pulses through a bipolar electrode array under radio frequency coupling to achieve local neural modulation; the external control terminal monitors the transmitted signals in real time and can adjust the stimulation parameters as needed to achieve closed-loop control; Long-term use and follow-up: The mechanical support, chemical adhesion and suture structure of the fixation and adhesion system ensure that the chip remains stably attached under long-term cerebrospinal fluid flushing and tissue pulsation; the external energy / signal coupling module can be reactivated as needed in subsequent treatment or monitoring cycles; the passive chip does not require an internal battery and can also operate for a long time, thereby meeting the actual needs of disease monitoring, local treatment or neuromodulation.

[0046] Before the operation, the target implantation area and approach angle are determined by the image navigation system. A micro bone window with a diameter of about 1 cm is established in the top of the skull or frontoparietal region, and a flexible neuroendoscope is placed after the dura mater incision.

[0047] The endoscopic channel is pre-loaded with a passive functional chip (including any one of a drug-loaded chip, a passive EEG signal acquisition chip, or a passive radiofrequency stimulation chip). Under direct vision, the operator slowly delivers the chip along the endoscopic working channel to the surface of the ventricle or the area adjacent to the lesion.

[0048] Upon reaching the target area, the chip's flexible structure allows it to unfold and adhere to the ventricular wall or ependymal surface. Simultaneously, catechol-based or dopamine-modified hydrogels are injected into the interface between the chip's bottom microstructure and brain tissue, rapidly forming high-strength bioadhesion in a humid environment.

[0049] To further enhance the fixation effect, 1–2 points of slight suturing are performed at the chip edge using a laparoscopic micromanipulation hook, enabling the chip to achieve dual mechanical and chemical anchoring.

[0050] After implantation, the endoscope and sheath are removed, and the dura mater and bone window are closed layer by layer. Postoperatively, the chip's energy supply and functional control are achieved through an external magnetic field, light field, or radio frequency emission module.

[0051] Drug-loaded chips can release drugs on demand and in quantitative quantities under magnetothermal or photothermal excitation; passive EEG signal acquisition chips can wirelessly acquire and transmit EEG signals using electromagnetic induction; passive radiofrequency stimulation chips can generate local electrical stimulation under external radiofrequency energy excitation, achieving wireless neuromodulation.

[0052] The entire procedure is minimally invasive, safe, and visualized. After implantation, the chip exhibits high stability and excellent interface compatibility, maintaining stable functional output over a long period. In terms of materials, the chip body utilizes flexible, bio-inert polymers (such as Parylene C, PDMS, or medical-grade silicone rubber), while the electrodes and conductors are made of highly conductive, low-resistance materials such as Au, Pt, or PEDOT:PSS. Combined with multi-layer encapsulation and temperature-limiting protection design, this ensures that leakage, corrosion, or performance degradation does not occur during long-term exposure to cerebrospinal fluid.

[0053] Therefore, the present invention employs the aforementioned minimally invasive passive intracranial attachment brain-computer interface system based on neuroendoscopy, which can achieve universal implantation operation for different types of cores, while also taking into account the safety, biocompatibility and signal stability of long-term use. It has good clinical operability and engineering scalability, and provides a reliable implementation path for the local precision treatment, neuromodulation and brain-computer interface application of central nervous system diseases.

[0054] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and not to limit them. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can still be made to the technical solutions of the present invention, and these modifications or equivalent substitutions cannot cause the modified technical solutions to deviate from the spirit and scope of the technical solutions of the present invention.

Claims

1. A minimally invasive, passively attached brain-computer interface system based on neuroendoscopy, characterized in that, include: The minimally invasive neuroendoscopic implantation module is used to establish a safe implantation channel, provide a visual operating environment, and achieve precise chip delivery and positioning. A flexible passive functional chip is used to realize the local release of drugs in the brain, the acquisition of electrical signals, the sensing and regulation of nerve stimulation or other physiological parameters; the flexible passive functional chip includes, but is not limited to, one or more of the following: drug-carrying chip, passive EEG signal acquisition chip, and passive stimulation chip. A fixation and adhesion module is used to ensure that flexible passive functional chips can maintain long-term stable adhesion even under cerebrospinal fluid flow and slight displacement of brain tissue. The external energy / signal coupling module provides non-contact energy excitation and signal interaction for the flexible passive functional chip, enabling remote control and data acquisition.

2. The minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 1, characterized in that, The minimally invasive neuroendoscopic implantation module includes a skull micro-bone window unit, a flexible endoscope unit, an imaging device unit, and a delivery sheath unit; The cranial microbone window unit provides a fixed channel for flexible endoscopes and delivery sheaths to enter the ventricles by creating a microbone window in the target brain region. The microbone window not only serves as the entry point for endoscope insertion but also provides a stable support surface, allowing the endoscope and delivery instruments to maintain a fixed angle and orientation during insertion. The flexible endoscope unit, including fiber optic bundles, imaging channels, and flexible guide structures, moves flexibly within the curved ventricles or sulci of the brain. The flexible endoscope is responsible for acquiring real-time images of the brain tissue and can be oriented in narrow spaces, entering the ventricle through the cranial micro-bone window unit; The imaging unit includes a high-definition camera, a cold light source, and an image processing interface. It is connected to the flexible endoscope unit via a fiber optic link to transmit the ventricle images acquired by the endoscope to an external control terminal in real time. The imaging unit can provide stable brightness, clear images, and real-time feedback with extremely low latency. The delivery sheath unit is coaxially arranged along the outside of the flexible endoscope unit to stably advance the flexible passive functional chip along the sheath without folding, twisting or shifting; the front port of the sheath is designed with a compliant structure to provide flexible support when the flexible passive functional chip is pushed out, helping the flexible passive functional chip to unfold smoothly in the ventricle or target area and attach to the target surface.

3. The minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 1, characterized in that, The fixation and adhesion module includes a mechanical support unit, a bio-adhesion unit, and a suture fixation unit; The mechanical support unit designs micro-bumps, grooves, or micro-flexible needles on the bottom of the flexible passive functional chip to provide friction or micro-scale embedding effect when the flexible passive functional chip is first attached to brain tissue. The bioadhesion unit provides durable chemical adhesion on top of mechanical fixation, enabling the flexible passive functional chip to remain stable in a long-term cerebrospinal fluid flushing environment. In the contact area between the flexible passive functional chip and the tissue, bioadhesive materials such as dopamine or catechol-based modified hydrogels are used. The suture fixation unit has suture holes pre-drilled at the edge of the flexible passive functional chip. By connecting with absorbable sutures, the edge of the flexible passive functional chip is lightly sutured in the early stage of implantation, which enhances the overall mechanical stability and prevents the flexible passive functional chip from shifting due to small movements of brain tissue.

4. The minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 1, characterized in that, External energy / signal coupling module, including: The alternating magnetic field coil unit generates a high-frequency magnetic field that couples with the magnetocaloric material in the flexible passive functional chip, causing the thermally driven film to heat up and generate mechanical driving force, thereby realizing thermally triggered drug release. The alternating magnetic field coil achieves deep energy transfer in a non-contact manner, enabling remote control. The near-infrared light source unit uses tissue-penetrable NIR light to excite the photothermal layer in the flexible passive functional chip through direct irradiation or fiber optic transmission, causing it to generate local heating or deformation, thereby triggering drug release or regulating functional elements. Radio frequency transmitting coil unit: The radio frequency transmitting coil unit forms an electromagnetic coupling with the LC resonant unit or spiral induction coil in the flexible passive functional chip to realize wireless power supply and signal feedback; by tuning the radio frequency, field strength and modulation mode, it remotely drives the flexible passive functional chip to work and receives its feedback signal. Control terminal unit: The control terminal unit is responsible for adjusting the output of all external energy modules, including power, frequency, mode and duration; at the same time, the control terminal unit can also receive signals back from the flexible passive functional chip in real time for functional verification, status monitoring and closed-loop control.

5. A method of using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy, characterized in that, To implement the minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy as described in any one of claims 1-4, the system comprises the following steps: Preoperative preparation and microbone window establishment: First, the operator determines the target implantation location based on imaging data and establishes a cranial microbone window in the area of ​​the target implantation location; Delivery sheath advancement and chip introduction: The delivery sheath is advanced coaxially along the endoscope guide sleeve. The flexible passive functional chip is pre-installed in the front chamber of the sheath. After the sheath enters the target area, the flexible chip is smoothly released by controlling the push rod. Chip Deployment and Fixation: After deployment, the chip's flexible structure automatically unfolds to conform to the surface of the brain tissue. The mechanical support structure at the bottom of the chip generates initial friction or microscale interlocking with the tissue surface, providing the first layer of fixation force. Simultaneously, the bioadhesive hydrogel in the bioadhesion unit rapidly solidifies in a wet state, forming chemical bonds with the brain tissue surface, thereby enhancing the chip's adhesion stability. Light absorbable sutures are performed using pre-reserved suture holes to ensure that the chip does not shift with tissue movement in the early stages. External energy source positioning and coupling matching: The output energy is conducted to the implanted chip through the tissue and coupled with the thermo-driven membrane, spiral coil or LC resonant unit inside the chip, thereby triggering drug release, signal acquisition or generating stimulation pulses; Functional Triggering and Closed-Loop Monitoring: When external stimulation is initiated, the thermodynamic driving membrane of the drug-loaded chip heats up and deforms, thereby driving the drug solution in the storage cavity to be precisely released to the target tissue through the microfluidic channel and hollow microneedle array, realizing local on-demand drug delivery; the passive acquisition chip receives external energy through a spiral induction coil and activates the signal modulator to collect EEG or local field potentials and transmit them wirelessly; the passive stimulation chip outputs stimulation pulses through a bipolar electrode array under radio frequency coupling to achieve local neural modulation; the external control terminal monitors the transmitted signals in real time and can adjust the stimulation parameters as needed to achieve closed-loop control; Long-term use and follow-up: The mechanical support, chemical adhesion and suture structure of the fixation and adhesion system ensure that the chip remains stably attached under long-term cerebrospinal fluid flushing and tissue pulsation.

6. The method of using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 5, characterized in that, The microbone window serves as an access channel for the endoscope and also provides an initial fixation point for the flexible endoscope, enabling the endoscope to enter the ventricle or sulcus at a controlled angle and direction.

7. The method of using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 5, characterized in that, Flexible laparoscope insertion and visual navigation: The flexible laparoscope is slowly inserted into the brain through a micro-bone window. The optical fiber at the front end of the laparoscope is connected to the imaging device, which displays images of the ventricular structure, blood vessel distribution and target tissue area in real time on the operating terminal. The operator adjusts the direction and depth of the laparoscope through visual navigation and fixes the position of the laparoscope when approaching the target area, providing a stable guide path for the delivery of the sheath.

8. The method of using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 5, characterized in that, When locating and coupling the external energy source, after implantation, the operator places the external energy module in the corresponding body surface area. The alternating magnetic field coil unit and the near-infrared light source unit set the power, frequency and excitation mode through the control terminal, and then start the energy output.

9. The method of using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 5, characterized in that, The sheath and endoscope are kept coaxial to ensure that the chip can unfold in the expected orientation and adhere to the tissue surface.

10. The method of using a minimally invasive passive intracerebral attachment brain-computer interface system based on neuroendoscopy according to claim 5, characterized in that, The external energy / signal coupling module is reactivated as needed during subsequent treatment or monitoring cycles. The passive chip does not require an internal battery and can operate for a long time, thus meeting the actual needs of disease monitoring, local treatment, or neuromodulation.

Images