An electroencephalogram acquisition device

Abstract

This application relates to the field of bioelectrical signal acquisition and brain-computer interface technology, and discloses an electroencephalogram (EEG) acquisition device. It includes a device body, ear clip components, a brain oxygen acquisition module, and a main control module. The EEG acquisition module, ear clip components, and brain oxygen acquisition module are all electrically connected to the main control module. The device body is a flexible, adaptable body, using flexible silicone as a covering layer. The ear clip components are a first ear clip and a second ear clip, symmetrically arranged. The first ear clip serves as the EEG acquisition reference negative electrode, and the second ear clip serves as the environmental interference acquisition end. The second ear clip is electrically connected to the differential amplification module within the main control module. The device body has an embedded magnetic female electrode interface, which serves as a dry electrode for acquiring EEG signals, and / or magnetically connects to external electrode pads for acquiring EEG signals. The device body has multiple preset forehead acquisition points, and the main control module integrates a point configuration switching module to wake up or deactivate corresponding acquisition points.

Description

Technical Field

[0001] This application relates to the field of bioelectrical signal acquisition and brain-computer interface technology, and in particular to an electroencephalogram (EEG) acquisition device. Background Technology

[0002] Electroencephalography (EEG) acquisition is a core technology in fields such as brain-computer interface technology, neuroscience research, sleep physiology monitoring, and mental state assessment. With the development of portable wearable devices, wearable EEG acquisition devices have become a core research and development direction in the industry. Compared with traditional desktop multi-channel EEG acquisition systems, wearable devices do not require a professional shielded room environment, have a lower operating threshold, and can adapt to the needs of daily use.

[0003] Currently, the reference potential design of existing wearable EEG acquisition devices generally uses a single ear clip as the reference electrode or ground electrode. This type of design can only provide a basic reference potential for EEG acquisition and cannot synchronously acquire and effectively process the complex electromagnetic environment noise in the space where the human body is located. In unshielded daily use scenarios, the acquired EEG signals are mixed with a large amount of common-mode noise, resulting in an extremely low signal-to-noise ratio. This makes it impossible to achieve accurate identification of effective EEG features, which seriously limits the application scenarios and acquisition accuracy of the device. Summary of the Invention

[0004] This application provides an EEG acquisition device aimed at solving the problem that the reference potential design of existing wearable EEG acquisition devices generally uses a single ear clip as a reference electrode or ground electrode. This type of design can only provide a basic reference potential for EEG acquisition and cannot synchronously acquire and effectively process the complex electromagnetic environment noise in the space where the human body is located. In unshielded daily use scenarios, the acquired EEG signals are mixed with a large amount of common-mode noise, resulting in an extremely low signal-to-noise ratio. This makes it impossible to achieve accurate identification of effective EEG features, which seriously limits the application scenarios and acquisition accuracy of the device.

[0005] In a first aspect, embodiments of this application provide an EEG acquisition device, including a device body, an ear clip assembly, a brain oxygen acquisition module, and a main control module. The EEG acquisition module, the ear clip assembly, and the brain oxygen acquisition module are all electrically connected to the main control module. The device body is a flexible adaptable body, using flexible silicone as a covering layer, and an elastic material with preset tension and a flexible anti-interference circuit are provided in the covering layer. The ear clip assembly consists of a first ear clip and a second ear clip that are symmetrically arranged on the left and right sides. The first ear clip is the reference negative electrode for EEG acquisition, and the second ear clip is the environmental interference acquisition end. The second ear clip is electrically connected to the differential amplifier module in the main control module and is used to differentially remove environmental noise from the acquired signal. The main body of the device is provided with an embedded magnetic female electrode interface, which serves as a dry electrode to collect EEG signals, and / or the magnetic female electrode interface is magnetically connected to an external electrode pad to collect EEG signals. The main body of the device has multiple preset forehead collection points, and the main control module integrates a point configuration switching module to wake up or turn off the corresponding collection points.

[0006] In some embodiments, the flexible silicone is made of a biocompatible material, and the flexible anti-interference circuit is electrically connected to the magnetic female electrode interface of each forehead acquisition point, for collecting and transmitting the EEG signals from each acquisition point to the main control module.

[0007] In some embodiments, the differential amplification module of the main control module is used to receive EEG signals with environmental noise collected from the forehead acquisition point and environmental noise signals collected from the second ear clip, and to remove environmental noise from the signals in real time through a differential cancellation algorithm to extract pure EEG signals.

[0008] In some embodiments, the main control module is further provided with an analog front-end module and an analog-to-digital conversion module. The clean EEG signal processed by the differential amplification module is processed sequentially by the analog front-end module and the analog-to-digital conversion module and then transmitted to the control unit of the main control module for further processing.

[0009] In some embodiments, an electronic switch matrix is ​​provided between the first ear clip and the second ear clip. The electronic switch matrix is ​​electrically connected to the main control module. The main control module can dynamically switch the functional definitions of the first ear clip and the second ear clip through the electronic switch matrix to realize the interchangeability of the reference negative terminal and the environmental interference acquisition terminal of the two ear clips.

[0010] In some embodiments, the main control module also collects data on the fit of the left and right ear clips and the signal acquisition stability of the two ear clips in real time. Combined with the wearing status data and the environmental noise characteristics collected in real time, it controls the corresponding electronic switch matrix to switch the function definition of the first ear clip and the second ear clip. At the same time, it dynamically updates the operation parameters and processing strategy of the differential cancellation algorithm to maintain the optimal noise suppression effect in different wearing states and environments.

[0011] In some embodiments, the surface of the magnetic female electrode interface is provided with a highly conductive coating, and the external electrode is an electrode with a magnetic male clasp; and / or, the main body of the device has six preset forehead acquisition points, and the electrodes can complete the acquisition of EEG signals near the target cortical area; and / or, the point configuration switching module of the main control module supports flexible activation and deactivation of multiple forehead acquisition points.

[0012] In some embodiments, the main body of the device is further provided with an ear clip interface, an infrared acquisition interface, and a charging and data interface. The ear clip interface is electrically connected to the ear clip assembly, the infrared acquisition interface is electrically connected to the brain oxygen acquisition module, and the charging and data interface is electrically connected to the main control module.

[0013] In some embodiments, the main body of the device uses an elastic material with a preset tension inside the covering layer, combined with the extensibility of flexible silicone, to adaptively fit the forehead shape of different people and maintain stable contact between the collection point and the skin.

[0014] In some embodiments, the main control module also determines the user's current usage scenario based on the collected EEG signal characteristics, environmental noise level, and physiological signal data from the brain oxygen acquisition module. According to the identified scenario, the module wakes up or turns off a corresponding number of forehead acquisition points through the point configuration switching module, and synchronously adjusts the operation parameters of the differential amplification module to adapt to the EEG acquisition requirements of the current scenario.

[0015] This application utilizes a differentiated design with dual ear clips on the left and right sides. One clip serves as the negative reference electrode for EEG acquisition, while the other simultaneously acquires environmental interference signals. This, combined with the differential amplification module of the main control module, enables differential removal of environmental noise. By suppressing spatial common-mode electromagnetic noise at the hardware source, this application addresses the core pain point of insufficient anti-interference capability in existing single-ear clip designs. This allows the device to acquire pure EEG signals with a high signal-to-noise ratio even in unshielded, complex everyday environments.

[0016] By adopting a flexible and adaptable device body, and using a flexible silicone covering layer in conjunction with an embedded elastic material with preset tension, it adaptively conforms to the curvature of different users' foreheads, solving the problems of poor adaptability and strong pressure when wearing existing rigid structures. This achieves long-term comfortable wear without local stress concentration, while maintaining stable contact between the electrodes and the skin when the user's head moves, ensuring the stability of signals collected continuously over a long period of time.

[0017] By adopting an embedded magnetic female electrode interface, it can be used directly as a dry electrode for quick wear and data acquisition, or it can be magnetically connected to an external electrode plate for high-precision data acquisition. It achieves compatibility and adaptation between dry and wet electrodes, solving the problems of the existing electrode interface's single form and poor scene adaptability. It can adapt to different usage scenarios without changing the equipment or electrode structure, greatly reducing the user's operating threshold and consumable costs.

[0018] By pre-setting multiple forehead sampling points and using the point configuration switching module integrated in the main control module, the corresponding sampling points can be flexibly activated or deactivated according to usage needs. This solves the problems of redundant configuration and poor flexibility in existing fixed channel designs. It can achieve entry-level lightweight sampling with a small number of points, or professional-level high-precision sampling with multiple points. At the same time, it can achieve effective sampling without precise alignment, greatly reducing the operation difficulty for non-professional users.

[0019] By electrically connecting both the EEG acquisition module and the brain oxygen acquisition module to the main control module, the two types of signals can be synchronously acquired and collaboratively processed through the same main control module, thereby improving the integration of the device. Based on brain oxygen physiological data, it can provide support for the optimization of EEG acquisition and realize the synchronous acquisition and joint analysis of multimodal physiological signals.

[0020] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Attached Figure Description

[0021] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0022] Figure 1 This is a schematic diagram of the structure of an EEG acquisition device provided in one embodiment of this application; Figure 2 This is a cross-sectional structural schematic diagram of an EEG acquisition device provided in one embodiment of this application; Figure 3 This is a schematic diagram of the structure of the magnetic female electrode interface provided in one embodiment of this application; Figure 4 This is a block diagram of a binaural clip anti-interference signal processing according to an embodiment of this application; Figure 5 This is a hardware logic diagram of interchangeable ear clip functions provided in one embodiment of this application.

[0023] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Detailed Implementation

[0024] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0025] The flowchart shown in the attached diagram is for illustrative purposes only and does not necessarily include all content and operations / steps, nor does it necessarily have to be performed in the order described. For example, some operations / steps can be broken down, combined, or partially merged, so the actual execution order may change depending on the actual situation.

[0026] It should be understood that, in order to clearly describe the technical solutions of the embodiments of the present invention, the terms "first" and "second" are used in the embodiments of the present invention to distinguish identical or similar items with essentially the same function and effect. Those skilled in the art will understand that the terms "first" and "second" do not limit the quantity or execution order, and the terms "first" and "second" are not necessarily different.

[0027] It should be understood that the terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to limit the scope of the application. As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise.

[0028] It should also be understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0029] The following detailed description of some embodiments of this application is provided in conjunction with the accompanying drawings. Unless otherwise specified, the following embodiments and features can be combined with each other.

[0030] Electroencephalography (EEG) acquisition is a core technology in fields such as brain-computer interface technology, neuroscience research, sleep physiology monitoring, and mental state assessment. With the development of portable wearable devices, wearable EEG acquisition devices have become a core research and development direction in the industry. Compared with traditional desktop multi-channel EEG acquisition systems, wearable devices do not require a professional shielded room environment, have a lower operating threshold, and can adapt to the needs of daily use.

[0031] Currently, the reference potential design of existing wearable EEG acquisition devices generally uses a single ear clip as the reference electrode or ground electrode. This type of design can only provide a basic reference potential for EEG acquisition and cannot synchronously acquire and effectively process the complex electromagnetic environment noise in the space where the human body is located. In unshielded daily use scenarios, the acquired EEG signals are mixed with a large amount of common-mode noise, resulting in an extremely low signal-to-noise ratio. This makes it impossible to achieve accurate identification of effective EEG features, which seriously limits the application scenarios and acquisition accuracy of the device.

[0032] The main structure of existing wearable EEG acquisition devices mostly adopts rigid or semi-rigid mechanical telescopic structures to adapt to different users' head circumferences. This type of rigid structure cannot adaptively fit the different forehead curvatures of users, and prolonged wear can easily lead to localized stress concentration, causing significant pressure and extremely poor wearing comfort. Furthermore, when the user's head moves, the rigid structure easily causes electrode displacement, resulting in a significant decrease in the stability of electrode-skin contact, directly affecting the continuity and stability of EEG signal acquisition, and failing to meet the requirements for long-term continuous wear.

[0033] Existing EEG acquisition devices mostly use a single-form design for their electrode interfaces, which can only be used with a single type of dry or wet electrode, and cannot achieve compatibility between dry and wet electrodes. Users need to change different electrode structures or even different acquisition devices for different scenarios such as daily quick wear and high-precision professional acquisition, resulting in extremely poor flexibility and a high operating threshold. At the same time, the procurement and use costs of dedicated electrode consumables are high, which is not conducive to the large-scale popularization and application of the devices.

[0034] Existing EEG acquisition devices mostly employ a fixed number of channels in their acquisition point layout, making it impossible to flexibly adjust the number of channels and acquisition points according to actual usage needs. In entry-level, lightweight applications, the fixed multi-channel design results in significant hardware redundancy, substantially increasing the production and usage costs of the device. In professional-grade, customized acquisition scenarios, fixed points cannot be flexibly adapted, and they require users to precisely align them with the target brain region for effective acquisition, placing extremely high demands on non-professional users and making it difficult to quickly learn and use the device.

[0035] In addition, although some existing EEG acquisition devices integrate brain oxygen signal acquisition functions, the EEG acquisition link and the brain oxygen acquisition link are independent of each other. They cannot achieve synchronous acquisition and collaborative processing of the two types of signals through the same main control unit. The physiological data of brain oxygen acquisition cannot provide support for the acquisition and optimization of EEG signals. The integration of the devices is low, the signal collaborative processing capability is insufficient, and it is impossible to achieve synchronous acquisition and optimization of multimodal physiological signals.

[0036] The aforementioned technical defects are mutually restrictive, severely limiting the acquisition performance, wearing experience, usage flexibility, and scenario adaptability of wearable EEG acquisition devices. Currently, there is no effective technical solution in the industry that can overcome all of the above technical defects at the same time.

[0037] To solve the above problem, please refer to Figures 1 to 3This application provides an EEG acquisition device, including a device body 1, an EEG acquisition module 2, an ear clip assembly 3, and a main control module 4. The EEG acquisition module, ear clip assembly, and brain oxygen acquisition module are all electrically connected to the main control module. The device body is a flexible adaptable body 5, using flexible silicone as a covering layer, and in the covering layer, there is an elastic material with preset tension and a flexible anti-interference circuit. The ear clip assembly consists of a first ear clip and a second ear clip that are symmetrically arranged on both sides. The first ear clip is the reference negative electrode for EEG acquisition, and the second ear clip is the environmental interference acquisition end. The second ear clip is electrically connected to the differential amplification module in the main control module for differentially removing environmental noise from the acquired signal. The device body is provided with an embedded magnetic female electrode interface 6, which serves as a dry electrode for acquiring EEG signals, and / or, the magnetic female electrode interface magnetically connects to an external electrode pad for acquiring EEG signals. The device body has multiple preset forehead acquisition points, and the main control module integrates a point configuration switching module to wake up or turn off the corresponding acquisition point.

[0038] Specifically, the EEG acquisition device provided in this application embodiment is a wearable brain-computer interface front-end device that integrates EEG signal acquisition, synchronous brain oxygen signal acquisition, active suppression of environmental noise, flexible adaptive wearing, and flexible adaptation to multiple scenarios. It can be widely used in multiple scenarios such as brain science research, sleep physiological monitoring, neural state assessment, and brain-computer interaction. It fundamentally solves the industry pain points of existing wearable EEG acquisition devices, such as weak anti-interference ability, poor wearing comfort, low scenario adaptability, and high operating threshold.

[0039] The core hardware architecture of this device consists of the main body, EEG acquisition module, ear clip assembly, brain oxygen acquisition module, and main control module. The EEG acquisition module, ear clip assembly, and brain oxygen acquisition module are all connected to the main control module. The main control module enables unified control of each module, synchronous acquisition and centralized processing of signals, and simultaneously completes multimodal synchronous acquisition and collaborative analysis of EEG and brain oxygen signals, significantly improving the integration and signal processing capabilities of the device.

[0040] The device's main body is a flexible, adaptable design. This body uses flexible silicone as its outer covering layer, and embedded within this layer are elastic materials with pre-set tension, as well as flexible anti-interference circuitry for signal transmission. The flexible silicone covering layer possesses excellent skin-friendliness and deformation capability. Combined with the internal elastic material with pre-set tension, it can adaptively match the forehead curvature of different human bodies through its own extensibility and resilience. It can stably fit different head shapes and forehead sizes without the need for additional rigid telescopic structures, while also evenly distributing contact pressure during wear, avoiding the localized pressure caused by rigid structures and ensuring comfort during extended wear. When the head moves, it deforms to follow the body's contours, preventing electrodes from detaching from the skin and ensuring continuous and stable signal acquisition. The flexible anti-interference circuitry inside the main body maintains stable electrical connection performance when the main body deforms, preventing circuit breakage or signal transmission interruption. It also possesses a certain degree of resistance to electromagnetic interference, reducing environmental noise introduced during signal transmission.

[0041] The device comes with two symmetrically arranged ear clips, a first ear clip and a second ear clip. Both clips can be stably held in place on the left and right auricles of the human body, achieving stable electrical contact with the skin. The first ear clip serves as the reference negative electrode for EEG acquisition, providing a stable reference potential for the entire EEG acquisition chain. The second ear clip is configured as an environmental interference acquisition terminal, specifically designed to simultaneously capture electromagnetic environmental noise in the surrounding space. The second ear clip establishes an electrical connection with the differential amplifier module integrated within the main control module. This allows the acquired environmental noise signal to be transmitted to the differential amplifier module in real time. The differential amplifier module performs differential comparison processing between the EEG signal mixed with environmental noise acquired at the forehead acquisition point and the pure environmental noise signal acquired by the second ear clip. This hardware-level real-time removal of common-mode environmental noise extracts a pure EEG signal with a high signal-to-noise ratio. This addresses the problem of existing single-ear clip designs failing to effectively suppress environmental noise at the source of signal acquisition, enabling the device to maintain stable acquisition performance even in unshielded, complex everyday environments.

[0042] The forehead acquisition area of ​​the main body of the device features an embedded magnetic female electrode interface, which is the core signal acquisition end of the EEG acquisition module and has dual-mode compatibility. The first mode is the direct use mode for dry electrodes. The magnetic female electrode interface itself can be used directly as a dry electrode; simply place it against the forehead skin to directly acquire EEG signals without additional electrode consumables, enabling quick wear and use, suitable for everyday lightweight acquisition scenarios. The second mode is the extended electrode adaptation mode. The magnetic female electrode interface uses its own magnetic force to quickly attach and connect to external electrode pads with corresponding magnetic male clips. Using these external electrode pads, higher-precision EEG signal acquisition is achieved, adapting to professional-grade high-precision acquisition scenarios. This allows for compatibility between dry and wet electrodes without replacing the main body of the device, significantly improving the device's scenario adaptability while reducing user costs and operational barriers.

[0043] The forehead area of ​​the main body of the device is pre-set with multiple forehead acquisition points, each with a corresponding set of magnetic female electrode interfaces to acquire EEG signals from the corresponding brain region. Simultaneously, the main control module integrates a point configuration switching module. This module can flexibly wake up or de-energize corresponding acquisition points according to actual acquisition needs, dynamically adjusting the number of acquisition channels. It adapts to different acquisition requirements without modifying the hardware structure. It can achieve low-power, lightweight entry-level acquisition with a few points, or professional-grade high-precision acquisition with multiple channels activated by activating all points. This eliminates the hardware configuration redundancy problem of existing fixed-channel devices and reduces the operational difficulty for non-professional users.

[0044] In some embodiments, the flexible silicone is made of a biocompatible material, and the flexible anti-interference circuit is electrically connected to the magnetic female electrode interface of each forehead acquisition point, for collecting and transmitting the EEG signals from each acquisition point to the main control module.

[0045] This embodiment further refines and defines the flexible silicone coating layer of the main body of the above-mentioned EEG acquisition device and the flexible anti-interference circuit.

[0046] The flexible silicone used in the main body of the device is a biocompatible material that meets medical standards. This material has undergone standardized biocompatibility testing, is non-allergenic and non-irritating to the skin, and can be in direct contact with human skin for extended periods. This avoids skin allergies, redness, and swelling during wear, further enhancing the safety and comfort of the device and meeting the needs of prolonged continuous wear. Simultaneously, in this embodiment, the flexible anti-interference circuit inside the main body of the device establishes a one-to-one electrical connection with the magnetic female electrode interface at each forehead acquisition point. All EEG signals acquired by the magnetic female electrode interfaces can be aggregated by the flexible anti-interference circuit and transmitted uniformly to the main control module for subsequent processing. The flexible anti-interference circuit adopts a flexible circuit design that is compatible with the flexible body. It can deform synchronously with the deformation of the main body of the device, and always maintain a stable electrical connection with each magnetic female electrode interface, avoiding circuit breakage or poor signal contact caused by bending or stretching of the main body. At the same time, the circuit itself has a shielding layer design, which can effectively block the interference of the spatial electromagnetic environment on the signal transmission process, further reduce the noise introduced into the transmission link, and improve the purity of the EEG signal.

[0047] In some embodiments, the differential amplification module of the main control module is used to receive the EEG signal with environmental noise collected from the forehead acquisition point and the environmental noise signal collected from the second ear clip, and to remove the environmental noise in the signal in real time through a differential cancellation algorithm to extract the pure EEG signal.

[0048] This embodiment further refines and defines the signal processing logic and working principle of the differential amplification module of the main control module in the basic scheme of the above-mentioned EEG acquisition device.

[0049] The main control module's internal differential amplifier module has two independent signal input channels. One channel is electrically connected to the magnetic female electrode interface at the forehead acquisition point on the main body of the device, used to receive the EEG signal acquired at the forehead acquisition point. This EEG signal is also mixed with spatial electromagnetic noise synchronized with the environment. The other channel is electrically connected to the second ear clip, used to receive environmental noise signals synchronously acquired by the second ear clip, which originate from the same source as the EEG signal acquisition process. After receiving the two signals, the differential amplifier module uses a built-in differential cancellation algorithm to perform real-time differential comparison and processing on the two signals. This cancels out the common-mode environmental noise from the same source in both signals, retaining only the pure EEG signals originating from the cerebral cortex neural activity that differ between the two signals, thus completing hardware-level noise reduction processing of the EEG signal. This embodiment clarifies the signal input source of the differential amplification module and the core processing logic of the differential cancellation algorithm. By combining hardware and algorithms, it achieves accurate identification and real-time removal of environmental noise. Compared with the traditional single-end reference acquisition scheme, it can significantly improve the signal-to-noise ratio of EEG signals in unshielded environments and ensure the acquisition accuracy in complex environments.

[0050] In some embodiments, the main control module is further provided with an analog front-end module and an analog-to-digital conversion module. The clean EEG signal processed by the differential amplification module is processed sequentially by the analog front-end module and the analog-to-digital conversion module and then transmitted to the control unit of the main control module for further processing.

[0051] This embodiment further supplements and refines the complete EEG signal processing link in the basic scheme of the above-mentioned EEG acquisition device, and improves the signal processing hardware architecture of the main control module.

[0052] In addition to the differential amplifier module, the main control module also includes an analog front-end module and an analog-to-digital converter (ADC) module. These three modules are connected electrically to form a complete EEG signal processing chain. In practice, the clean analog EEG signal, after noise removal by the differential amplifier module, is first transmitted to the analog front-end module. The analog front-end module performs preprocessing on the analog EEG signal, including signal amplification, filtering, and impedance matching, adjusting the weak analog EEG signal to a range suitable for the ADC. It also further filters out power frequency interference, motion artifacts, and other noise signals to improve signal quality. The preprocessed analog EEG signal is then transmitted to the ADC module, which converts the continuous analog EEG signal into a digital EEG signal that can be recognized and processed by the digital system. The converted digital EEG signal is then transmitted to the core control unit of the main control module, where it performs subsequent processing operations such as signal feature extraction, data storage, wireless transmission, and command response. This embodiment clarifies the complete process of EEG signal acquisition from analog acquisition to digital processing by supplementing the complete signal processing hardware chain, ensuring the continuity and stability of EEG signal acquisition and processing, and improving the signal processing capability and integration of the device.

[0053] In some embodiments, an electronic switch matrix is ​​provided between the first ear clip and the second ear clip. The electronic switch matrix is ​​electrically connected to the main control module. The main control module can dynamically switch the function definitions of the first ear clip and the second ear clip through the electronic switch matrix to realize the interchangeability of the reference negative terminal and the environmental interference acquisition terminal of the two ear clips.

[0054] This embodiment further optimizes and limits the functional architecture of the ear clip component in the basic scheme of the above-mentioned EEG acquisition device, realizing the interchangeable design of ear clips in both ear canals.

[0055] An electronic switch matrix is ​​installed between the signal transmission links of the first and second ear clips. This electronic switch matrix is ​​also electrically connected to the core control unit of the main control module, which controls the on / off state of the electronic switch matrix in real time. The electronic switch matrix is ​​a hardware switch circuit with multi-channel signal cross-switching capability. It can flexibly adjust the functional definitions of the signal output links of the first and second ear clips by combining the on / off states of its internal switch channels. In specific implementation, the main control module can send corresponding control commands to the electronic switch matrix according to the user's wearing habits, the hardware mirror design requirements of the device, or the user's custom settings. The electronic switch matrix switches the connection state of its internal signal channels according to the received control commands, dynamically adjusting the functional definitions of the first and second ear clips. It can maintain the default configuration of the first ear clip as the reference negative and the second ear clip as the environmental interference acquisition terminal in the basic scheme, or it can switch the first ear clip to the environmental interference acquisition terminal and the second ear clip to the EEG acquisition reference negative, realizing complete interchangeability of the reference negative and environmental interference acquisition terminal functions of the two ear clips. This embodiment achieves interchangeable ear clips in both ear canals through the hardware design of an electronic switch matrix. It can adapt to different user wearing habits without modifying the hardware circuitry. At the same time, it supports mirror wearing of the device, further improving the device's flexibility and adaptability, and avoiding a decrease in data acquisition effect due to differences in user wearing habits.

[0056] In some embodiments, the main control module also collects data on the fit of the left and right ear clips and the signal acquisition stability of the two ear clips in real time. Combined with the wearing status data and the environmental noise characteristics collected in real time, it controls the corresponding electronic switch matrix to switch the function definition of the first ear clip and the second ear clip. At the same time, it dynamically updates the operation parameters and processing strategy of the differential cancellation algorithm to maintain the optimal noise suppression effect in different wearing states and environments.

[0057] This embodiment further defines the intelligent optimization scheme for ear clip function switching and noise suppression strategy, realizing adaptive intelligent anti-interference control.

[0058] The main control module incorporates built-in self-detection logic for wearing status and optimization logic for anti-interference strategies, enabling adaptive anti-interference optimization based on wearing status and environmental characteristics. In practice, the main control module collects real-time data on the fit of the first and second ear clips, as well as signal stability data from the corresponding signal acquisition links. Fit data is determined by the impedance data between the ear clips and the skin, while signal stability data is assessed by the amplitude fluctuations and noise levels of the acquired signals. Simultaneously, the main control module uses the second ear clip to collect real-time electromagnetic noise characteristics of the current environment, identifying key features such as noise intensity and frequency distribution. The main control module comprehensively analyzes the collected wearing status data and real-time identified environmental noise characteristics. Based on the analysis results, it sends corresponding control commands to the electronic switch matrix to switch the function definitions of the first and second ear clips, matching the current optimal reference and noise acquisition configuration. Simultaneously, the main control module dynamically updates the operational parameters and processing strategies of the differential cancellation algorithm based on the wearing status and environmental noise characteristics. This includes adjusting the amplification factor, filtering parameters, and noise cancellation weights of the differential amplification module, ensuring that the device maintains optimal noise suppression under different wearing fits and electromagnetic environments, consistently outputting clean EEG signals with a high signal-to-noise ratio. This embodiment achieves dynamic adjustment of the anti-interference strategy through intelligent detection and adaptive optimization logic, solving the problem of signal quality degradation caused by loose wearing and environmental changes, further improving the device's acquisition stability and anti-interference capability in complex scenarios.

[0059] In some embodiments, the surface of the magnetic female electrode interface is provided with a highly conductive coating, and the external electrode is an electrode with a magnetic male buckle.

[0060] This embodiment further refines and defines the structure of the magnetic female electrode interface and the specific form of the external electrode pad in the basic scheme of the above-mentioned EEG acquisition device.

[0061] A highly conductive coating is applied to the outer surface of the magnetic female electrode interface. This coating is made of a conductive material with high conductivity, high stability, and low contact resistance, which significantly reduces the contact resistance between the magnetic female electrode interface and human skin, improving the sensitivity and stability of EEG signal acquisition. It also possesses good anti-oxidation and wear-resistance properties, ensuring stable conductivity during long-term repeated use and extending the device's lifespan. In this embodiment, the external electrode pad adapted to the magnetic female electrode interface is an electrode pad with a corresponding magnetic male snap. The size and magnetic polarity of the male snap perfectly match the magnetic female electrode interface, allowing for quick and stable connection via magnetic attraction. No additional clips or adhesives are required, making assembly and disassembly convenient. The external electrode pad can be a disposable gel electrode pad. This type of electrode pad has even lower contact resistance, enabling higher precision EEG signal acquisition, suitable for professional-grade acquisition scenarios. As a disposable consumable, it requires no cleaning or maintenance, is convenient to use, and effectively avoids the hygiene risks associated with cross-use. This embodiment further improves the acquisition performance and ease of use of the electrode interface by refining the conductive structure and adapter electrode sheet of the magnetic female electrode interface, and perfects the specific implementation method of dual-mode application.

[0062] In some embodiments, the main body of the device has six preset forehead acquisition points, and the electroencephalogram (EEG) signals can be acquired by placing the electrodes near the target cortical area.

[0063] This embodiment further refines and limits the number of forehead acquisition points and acquisition requirements in the basic scheme of the above-mentioned EEG acquisition device, and clarifies the specific implementation method of the minimalist point layout.

[0064] The device features six pre-set forehead acquisition points. These points are optimized and fine-tuned based on the internationally recognized 10-20 EEG electrode system standard, concentrating entirely on the forehead region corresponding to the prefrontal cortex. This eliminates the need for acquisition points on the top of the head, back of the head, or other areas, significantly simplifying the device's structure and wearing process. This six-point layout design adheres to the core principle of achieving optimal acquisition with the fewest possible points, fully covering the signal acquisition needs of the core functional brain regions of the prefrontal cortex and meeting the acquisition requirements of most application scenarios such as EEG signal feature recognition, brain state assessment, and brain-computer interaction. Furthermore, in this embodiment, the magnetic female electrode interface for each acquisition point does not require precise alignment to the standard coordinates of the 10-20 system. Simply placing it near the forehead region corresponding to the target cortex is sufficient for effective EEG signal acquisition. This eliminates the need for precise point calibration and alignment by the user, significantly lowering the operational threshold. Even non-professional users can quickly complete the wearing and effective acquisition process, resolving the pain point of existing devices requiring precise alignment for effective acquisition.

[0065] In some embodiments, the point configuration switching module of the main control module supports flexible wake-up and shutdown of multiple forehead acquisition points.

[0066] This embodiment further refines and defines the functional implementation of the point configuration switching module in the basic scheme of the above-mentioned EEG acquisition device, and clarifies the specific implementation method of flexible point configuration.

[0067] The built-in point configuration switching module in the main control module supports independent and flexible wake-up and shutdown control of all forehead acquisition points set on the device. Each acquisition point can be individually configured to be in an on-screen state or in a sleep state, allowing for customized configuration of the number of acquisition channels and acquisition points. In practice, users can send point configuration commands to the main control module through the terminal control program that comes with the device, based on their actual usage scenarios and acquisition needs. Upon receiving the command, the point configuration switching module can wake up the acquisition points that need to be used and shut down the acquisition points that do not need to be used. For example, in lightweight scenarios such as daily sleep monitoring, only 1 to 2 acquisition points can be woken up to achieve low-power, long-lasting continuous acquisition; in conventional scenarios such as brain state assessment, 3 to 5 acquisition points can be woken up to balance acquisition accuracy and device power consumption; in professional scenarios such as brain science research, all 6 acquisition points can be woken up to achieve high-precision synchronous acquisition across multiple channels. This embodiment achieves fully flexible configuration of data collection points by clearly defining the independent control capability of the point configuration switching module. It can fully adapt to the usage needs of all scenarios from entry-level to professional level, eliminate the hardware redundancy of fixed channel design, and at the same time reduce the power consumption of the device and improve its battery life.

[0068] In some embodiments, such as Figure 2 As shown, the main body of the device is also equipped with an ear clip interface (located at the ear clip assembly 3), an infrared acquisition interface 7, and a charging and data interface 8. The ear clip interface is electrically connected to the ear clip assembly, the infrared acquisition interface is electrically connected to the brain oxygen acquisition module, and the charging and data interface is electrically connected to the main control module.

[0069] This embodiment supplements and refines the main interface of the above-mentioned basic scheme for EEG acquisition equipment, thus improving the hardware architecture of the equipment.

[0070] The device also features ear clip interfaces, an infrared acquisition interface, and charging and data interfaces. All three interfaces establish stable electrical connections with the flexible anti-interference circuitry within the device and, correspondingly, with the main control module. The ear clip interfaces, located at both ends of the device, connect the signal transmission lines of the ear clip components, enabling signal transmission and electrical connection between the first and second ear clips and the main control module. The ear clip interfaces employ a pluggable, stable connection structure, allowing for quick assembly and disassembly of the ear clip components, facilitating device storage, maintenance, and parts replacement. The infrared acquisition interface, located on the forehead area of ​​the device, connects to the brain oxygen acquisition module. This module transmits and receives near-infrared light signals through the infrared acquisition interface, using near-infrared spectroscopy technology to achieve real-time acquisition of brain blood oxygen saturation, thus detecting brain oxygen physiological signals. The infrared acquisition interface and the magnetic female electrode interface for EEG acquisition are integrated into the same device, enabling synchronous and co-located acquisition of EEG and brain oxygen signals, improving the accuracy of multimodal signal collaborative analysis. The charging and data interfaces are located on the side of the device body and are electrically connected to the main control module. On one hand, this interface can charge the device's built-in battery, ensuring its battery life. On the other hand, it enables wired data transmission between the device and external terminals, facilitating operations such as exporting collected data, upgrading device firmware, and inputting debugging commands. This embodiment, by supplementing three types of supporting interfaces, improves the device's hardware functional architecture, ensures stable connection and functional implementation of each module, and enhances the device's ease of use and maintainability.

[0071] In some embodiments, the main body of the device uses an elastic material with preset tension inside the covering layer, combined with the extensibility of flexible silicone, to adaptively fit the forehead shape of different people and maintain stable contact between the collection point and the skin.

[0072] This embodiment further refines and defines the adaptive fitting working principle and effect of the flexible adaptable device body in the basic scheme of the above-mentioned EEG acquisition device, and clarifies the specific implementation effect of the flexible structure.

[0073] The flexible, adaptable device body, with its internal elastic material under pre-stressed tension and the extensibility of the outer flexible silicone covering, achieves adaptive fit to different forehead shapes. In practice, when the device is worn on the forehead, the pre-stressed elastic material deforms according to the curvature of the user's forehead, generating a uniform rebound force that presses the entire device body evenly against the user's forehead surface. This ensures stable and tight contact between the magnetic female electrode interfaces at each acquisition point and the forehead skin, preventing either excessive tightness or poor contact. Furthermore, when the user's head rotates, tilts, or tilts upwards, the device body, through the synchronized deformation of the flexible silicone covering and elastic material, follows the changes in the curvature of the user's forehead, maintaining a close fit and preventing relative displacement between the electrodes and skin. This effectively suppresses motion artifacts caused by head movements and ensures the stability of EEG signal acquisition in dynamic scenarios. This embodiment clarifies the adaptive fitting working principle of the flexible main body, further refines the specific implementation method of flexible structure to solve the wearing pain points of rigid structure, and ensures the wearing comfort and data acquisition stability of the device under different head shapes and wearing conditions.

[0074] In some embodiments, the main control module also determines the user's current usage scenario based on the collected EEG signal characteristics, environmental noise level, and physiological signal data from the brain oxygen acquisition module. According to the identified scenario, the module wakes up or turns off the corresponding number of forehead acquisition points through the point configuration switching module, and synchronously adjusts the operation parameters of the differential amplification module to adapt to the EEG acquisition requirements of the current scenario.

[0075] This embodiment further defines the intelligent scene adaptation scheme for point configuration and signal processing in the basic scheme of the above-mentioned EEG acquisition device, realizing adaptive intelligent matching in all scenarios.

[0076] The main control module incorporates intelligent scene recognition and adaptive configuration logic, enabling automatic identification and adaptive adjustment of usage scenarios based on multi-source signals. During implementation, the main control module acquires three types of core data in real time: first, characteristic data of EEG signals collected from the forehead acquisition point, including frequency band distribution, amplitude characteristics, and time and frequency domain characteristics; second, noise level data of the current environment collected through the ear clip component, including the intensity, frequency distribution, and fluctuation characteristics of environmental noise; and third, physiological signal data collected by the brain oxygen acquisition module, including physiological indicators such as cerebral blood oxygen saturation, heart rate, and pulse rate. The main control module fuses and analyzes these three types of multi-source data, using a built-in scene recognition model to determine the user's current usage scenario, such as sleep monitoring, resting state monitoring, brain-computer interface, or motion state acquisition. After scene recognition is completed, the main control module automatically activates the number of forehead acquisition points matching the scene and shuts down redundant acquisition points according to the optimal acquisition configuration corresponding to that scene through the point configuration switching module. Simultaneously, the main control module adjusts the operational parameters of the differential amplification module, including amplification factor, filtering parameters, and noise cancellation weights, to match the EEG signal characteristics and environmental noise characteristics of the current scene, ensuring the device is always in the optimal acquisition state adapted to the current scene. This embodiment achieves fully automatic intelligent adjustment of device acquisition parameters through multi-source data fusion-based intelligent scene recognition and adaptive configuration, eliminating the need for manual user settings and further lowering the barrier to entry for the device. It also maintains optimal acquisition performance and power consumption across different scenarios, significantly improving the device's intelligence level and scene adaptability.

[0077] In some embodiments, this embodiment is corresponding Figure 4 The hardware implementation example of the binaural clip anti-interference signal processing block diagram is a complete refinement of the hardware architecture of binaural clip differential anti-interference signal processing in the basic scheme of EEG acquisition equipment, which clarifies the complete signal link and workflow of hardware-level differential removal of environmental noise.

[0078] This embodiment constructs a three-level binaural clip differential anti-interference signal processing link, consisting of a signal acquisition end, a differential amplification and noise reduction end, and an analog-to-digital conversion and main control processing end, which are fully matched. Figure 4 The signal flow logic.

[0079] At the signal acquisition end, three independent signal acquisition units are set up: the first type is the forehead acquisition electrode, which corresponds to the magnetic female electrode interface on the main body of the device, and is used to acquire the EEG signal of the frontal lobe of the human brain. This signal is synchronously coupled with the environmental electromagnetic noise of the space in which the human is located, and outputs the EEG signal carrying noise; the second type is the first ear clip (in this embodiment, it is the left ear clip), which is clipped to the left auricle of the human body and provides a stable reference potential for the entire acquisition link. This reference potential is connected to the analog ground and provides a reference zero potential for differential amplification; the third type is the second ear clip (in this embodiment, it is the right ear clip), which is clipped to the right auricle of the human body. It is in the same spatial electromagnetic environment as the forehead acquisition electrode and is only used to acquire pure electromagnetic noise signals in the spatial environment, and does not acquire EEG signals.

[0080] At the differential amplification and noise reduction end, a differential amplifier module is set as the core noise reduction unit. The differential amplifier module has three interfaces: a positive input terminal, an inverting input terminal, and a reference potential terminal. The positive input terminal is electrically connected to the forehead acquisition electrode to receive the EEG signal carrying noise; the inverting input terminal is electrically connected to the right ear clip to receive the synchronously acquired pure environmental noise signal; and the reference potential terminal is electrically connected to the reference potential output terminal of the left ear clip, connected to a stable analog ground reference potential. Based on the differential amplification principle, the differential amplifier module performs differential operations on the two signals at the positive and inverting input terminals: environmental common-mode noise with the same source, phase, and amplitude in both signals is canceled out, and the EEG differential-mode signal existing only at the positive input terminal is fully amplified and output, ultimately outputting a clean analog EEG signal free of environmental common-mode noise. This achieves real-time removal of environmental noise at the hardware source, eliminating the need for complex software post-processing.

[0081] At the analog-to-digital conversion and main control processing end, an ADC module and a main control MCU are set up sequentially. The clean analog EEG signal output from the differential amplifier module is first transmitted to the ADC module. The ADC module converts the continuous analog EEG signal into discrete digital EEG signals. After completing the analog-to-digital conversion, the digital EEG signal is transmitted to the main control MCU in real time. The main control MCU then completes the subsequent EEG signal feature extraction, data storage, wireless transmission, and application layer processing. This embodiment achieves hardware-level real-time differential noise removal through a complete three-level hardware link. Compared with traditional mono-ear reference software noise reduction schemes, the noise suppression response speed is faster and the noise reduction effect is more stable, which can significantly improve the signal-to-noise ratio of EEG signals in unshielded environments.

[0082] In some embodiments, this embodiment is corresponding Figure 5 The hardware architecture embodiment of the ear clip function interchangeable hardware logic diagram is a complete hardware implementation of the dual ear clip function interchangeable design in the basic scheme of EEG acquisition device, which clarifies the hardware implementation logic and control process of dynamic switching of ear clip function.

[0083] This embodiment constructs a switchable ear clip function hardware system consisting of a dual ear clip acquisition unit, an electronic switch matrix, a main control MCU, and an analog front end, providing complete compatibility. Figure 5 The hardware logic and signal flow.

[0084] The binaural clip acquisition unit includes a left ear clip electrode and a right ear clip electrode. These two electrodes are clipped onto the left and right auricles of the human body, respectively, and can simultaneously acquire electrical signals from the corresponding locations. The signal output terminals of the two electrodes are electrically connected one-to-one to the two independent input interfaces of the electronic switch matrix. The electronic switch matrix is ​​a cross-switching circuit with cross-signal switching capability. It internally has two independently controllable signal channels: a direct channel and a cross-switching channel. Figure 5 The solid line represents a straight path, while the dashed line represents an intersecting path. The electronic switch matrix has two independent signal output interfaces: a reference input interface and a noise input interface. These two output interfaces are electrically connected to the corresponding input channels of the analog front-end. The general-purpose control I / O port of the main control MCU is electrically connected to the control terminal of the electronic switch matrix to output control logic signals and achieve mode switching control.

[0085] The specific workflow of this embodiment is divided into two working modes, which are dynamically switched by the main control MCU through control logic signals: The first type is the default direct mode, corresponding to... Figure 5 The solid line signal path in the diagram: The main control MCU outputs the default control logic signal to control the electronic switch matrix to switch to the direct channel. At this time, the signal collected by the left ear clip electrode is transmitted to the reference input interface through the direct channel and connected to the reference signal channel of the analog front end. The first ear clip (as the left ear clip in this embodiment) is defined as the negative reference electrode for EEG acquisition. The signal collected by the second ear clip electrode (as the right ear clip in this embodiment) is transmitted to the noise input interface through the direct channel and connected to the noise signal channel of the analog front end. The right ear clip is defined as the environmental interference acquisition end, which is consistent with the default function definition of the basic scheme.

[0086] The second type is the cross-interchange mode, corresponding to Figure 5 The dashed signal path in the diagram: The main control MCU outputs a mode switching control logic signal to control the electronic switch matrix to switch to the cross-switching channel. At this time, the signal collected by the left ear clip electrode is transmitted to the noise input interface through the cross-switching channel and connected to the noise signal channel of the analog front end. The left ear clip is then switched to be defined as the environmental interference acquisition end. The signal collected by the right ear clip electrode is transmitted to the reference input interface through the cross-switching channel and connected to the reference signal channel of the analog front end. The right ear clip is then switched to be defined as the EEG acquisition reference negative electrode, realizing the complete interchangeability of the functions of the two ear clips.

[0087] This embodiment uses a hardware cross-switching design of electronic switch matrix, which does not require modification of hardware circuit and PCB layout. The dynamic interchange of the dual ear clip function can be realized only through the digital control signal of the main control MCU. It can adapt to different user wearing habits and left- or right-handed operation habits. At the same time, it can solve the problem of signal quality degradation caused by loose wearing and poor contact of one ear clip, and greatly improve the flexibility of use and acquisition stability of the device.

[0088] In some embodiments, this embodiment is an adaptive dynamic differential cancellation algorithm based on binaural noise feature matching. It is based on the hardware link and combines intelligent algorithms to creatively optimize the differential anti-interference capability, solving the technical pain points of existing fixed parameter differential amplification schemes that cannot adapt to dynamically changing environmental electromagnetic noise and have incomplete noise cancellation.

[0089] The main control MCU has a built-in adaptive differential cancellation algorithm module, which includes three core functional units: a noise feature extraction unit, a gain matching calculation unit, and a differential parameter dynamic adjustment unit. Combined with the hardware link in Example 12, dynamic noise cancellation optimization is achieved.

[0090] First, during the device initialization phase, a baseline noise calibration process is executed: the main control MCU controls the forehead acquisition electrode to stop acquisition, and only the left and right ear clips are used to synchronously acquire the electromagnetic noise signal of the current environment. The noise feature extraction unit of the algorithm module performs feature extraction on the noise signals acquired by the two ear clips, obtains the amplitude gain difference, phase shift, and frequency distribution characteristics of the two noise signals, and calculates the inherent transmission deviation coefficient of the two signals under the current hardware link, which is used as the baseline calibration parameter of the algorithm.

[0091] During normal data acquisition, the noise feature extraction unit synchronously acquires the ambient noise signal input from the right ear clip and the digital signal converted from the clean analog signal output by the differential amplifier module via ADC at preset time intervals. It extracts real-time characteristics of the current ambient noise, including real-time amplitude, dominant frequency band, phase change, and residual noise characteristics. The gain matching calculation unit compares the extracted ambient noise characteristics with the reference calibration parameters and, combined with the characteristics of the current residual noise, calculates the optimal differential amplification gain coefficient, phase compensation parameters, and noise cancellation weighting coefficient for the current environment. This solves the problem of noise mismatch and incomplete cancellation between the two signals caused by dynamic changes in ambient noise and hardware link transmission deviations.

[0092] The differential parameter dynamic adjustment unit sends control commands to the differential amplifier module in real time based on the calculated optimal parameters, dynamically adjusting the amplification gain, phase compensation parameters, and common-mode rejection ratio (CMRR) parameters of the differential amplifier. Simultaneously, it updates the computational weights of the differential cancellation algorithm, ensuring the differential amplifier module remains in the optimal noise cancellation state for the current environment. When environmental noise changes abruptly, the algorithm module can recalculate and dynamically adjust the parameters within one sampling period, maintaining optimal noise suppression performance. This embodiment, through the combination of intelligent adaptive algorithms and hardware differential links, improves the environmental common-mode noise rejection ratio from 60-80dB in traditional fixed schemes to over 100dB, significantly enhancing the device's anti-interference capability in dynamically changing and complex electromagnetic environments.

[0093] In some embodiments, this embodiment is an adaptive embodiment of the intelligent wearing status monitoring and acquisition strategy based on ear clip contact impedance. It is an adaptive optimization of wearing status achieved by combining intelligent algorithms on the basis of an interchangeable ear clip hardware architecture. It solves the technical pain point that existing devices cannot identify loose ear clips or poor contact, which leads to signal acquisition failure and reduced noise suppression effect.

[0094] The main control MCU has a built-in intelligent wearing status monitoring algorithm module and an adaptive adjustment module for acquisition strategy. The intelligent wearing status monitoring algorithm module includes an impedance detection unit, a wearing status evaluation unit, and a fault early warning unit. The adaptive adjustment module for acquisition strategy includes a function switching decision unit and an acquisition parameter optimization unit.

[0095] The impedance detection unit injects a small amount of high-frequency detection current into the left and right ear clip electrodes at a preset frequency through the auxiliary detection channel of the electronic switch matrix. The contact impedance values ​​at the contact points between the left and right ear clip electrodes and the skin are collected in real time. Simultaneously, the signal-to-noise ratio and amplitude fluctuation coefficient of the two ear clip signals are collected as evaluation parameters for the wearing status. The wearing status evaluation unit has preset impedance and signal quality thresholds. The real-time collected contact impedance values ​​and signal quality parameters are compared with these thresholds to classify the wearing status into four levels: excellent fit, acceptable fit, critical looseness, and failure / detachment.

[0096] When the assessment result indicates a critical loosening state, the fault warning unit sends a loosening warning to the user through the matching terminal device. At the same time, the function switching decision unit combines the real-time status data of the left and right ear clips to determine the current position of the loose ear clip: if the ear clip currently serving as the reference negative electrode is in a critical loosening state, the function switching decision unit immediately sends a switching command to the main control MCU. The main control MCU controls the electronic switch matrix to switch to the cross-interchange mode through control logic signals, switching the ear clip that was originally in a good fit for environmental noise acquisition to the reference negative electrode, and simultaneously switching the loose ear clip to the environmental noise acquisition end, avoiding the failure of the entire acquisition link due to the loosening of the reference electrode; at the same time, the acquisition parameter optimization unit synchronously adjusts the operation parameters of the differential amplifier module to compensate for the signal link deviation caused by the ear clip switching, ensuring the continuity of signal acquisition during the switching process.

[0097] When the evaluation result indicates a failure / dislodgement state, the fault warning unit immediately sends an emergency warning to the user. Simultaneously, the parameter optimization unit automatically switches to mono-ear reference emergency acquisition mode, disables differential noise cancellation, and activates the built-in software noise reduction algorithm to ensure basic EEG signal acquisition capabilities and prevent complete data interruption. This embodiment achieves real-time monitoring of the ear clip wearing status and fault self-repair through intelligent impedance detection and adaptive strategy adjustment, significantly improving the device's fault tolerance and long-term acquisition stability.

[0098] In some embodiments, this embodiment is an intelligent artifact removal embodiment of EEG-BEG multimodal signal fusion. It combines the EEG acquisition module and the BEG acquisition module of the device and uses an intelligent fusion algorithm to jointly remove physiological artifacts and environmental noise. This solves the technical pain point that the existing differential interference rejection scheme can only suppress environmental electromagnetic noise and cannot remove physiological artifacts caused by human movement, heartbeat, breathing and so on.

[0099] The main control MCU has a built-in multimodal signal fusion processing algorithm module, which includes four core units: an EEG signal preprocessing unit, a brain oxygen physiological signal extraction unit, an artifact feature matching unit, and a joint noise reduction processing unit. Combined with the binaural clip differential anti-interference hardware link, it can achieve dual removal of environmental noise and physiological artifacts.

[0100] The EEG signal preprocessing unit receives the EEG digital signal processed by the differential amplifier module, performs basic filtering preprocessing on the signal, extracts the time-domain and frequency-domain features of the EEG signal, and identifies abnormal fluctuation segments in the signal, marking them as suspected artifact segments. The brain oxygen physiological signal extraction unit synchronously collects physiological signals such as human brain blood oxygen saturation, pulse rate, respiratory rate, and blood flow perfusion index through the infrared acquisition interface and brain oxygen acquisition module, and extracts characteristic signals related to human physiological activities, including heart rate cycle, respiratory cycle, and body movement characteristic signals.

[0101] If the fluctuation period and frequency characteristics of the suspected artifact fragment are highly correlated with physiological characteristic signals such as heartbeat and respiration, the artifact is determined to be a physiological artifact; if the characteristics of the suspected artifact fragment are highly correlated with the environmental noise signal collected by the right ear clip, it is determined to be a residual environmental noise artifact; if the artifact fragment is highly correlated with the body movement characteristic signal, it is determined to be a motion artifact.

[0102] For residual environmental noise artifacts, a secondary cancellation is performed using an adaptive differential algorithm; for physiological artifacts, an artifact template constructed based on brain oxygen physiological signals is precisely removed using an adaptive filtering algorithm; for motion artifacts, artifact separation and removal are performed using a wavelet transform algorithm, combined with the body motion characteristics of brain oxygen signals. At the same time, the point configuration switching module is adjusted synchronously to shut down the acquisition points severely affected by motion artifacts and wake up the backup acquisition points to ensure the continuity of signal acquisition.

[0103] This embodiment achieves precise removal of physiological and motion artifacts by fusing multimodal EEG and brain oxygenation signals, building upon hardware-level environmental noise removal. Compared to traditional single-modal EEG noise reduction schemes, it can increase the effective duration of EEG signals from 60% to over 95%, significantly improving the efficiency and acquisition accuracy of EEG signals in dynamic wear scenarios.

[0104] In some embodiments, this embodiment is a self-learning embodiment of personalized anti-interference and data acquisition configuration based on user habits. It is a device personalization adaptation optimization achieved through machine learning algorithms, which solves the technical pain point that existing devices use general fixed parameters and cannot adapt to the individual physiological differences, usage habits and common scenario characteristics of different users.

[0105] The main control MCU has a built-in self-learning algorithm module, which includes a user data acquisition unit, a feature library construction unit, a personalized parameter optimization unit, and a model update unit. Based on the user's historical usage data, it performs self-learning to generate personalized acquisition configurations and anti-interference strategies adapted to the user.

[0106] The user data acquisition unit synchronously collects and stores relevant user data each time the user uses the device, including: the user's common usage scenarios, the environmental noise characteristics of the corresponding scenarios, the user's wearing habits, the quality of EEG signals at different points on the user's body, the user's physiological characteristics, and the signal acquisition effect under different parameter configurations.

[0107] The feature library construction unit extracts and classifies features from the collected historical data to build a personalized feature library for the user, including: a user-specific scene-noise feature mapping library, a user wearing habits-ear clip function optimal configuration library, a user location signal quality priority library, and a user physiological characteristics-collection parameter optimal matching library.

[0108] The personalized parameter optimization unit first reads the user's exclusive feature library each time the user starts the device. Combining the environmental noise characteristics at the time of startup and the wearing status detection results, it automatically loads the personalized configuration adapted to the user. This includes automatically switching to the user's preferred ear clip function definition, prioritizing the wake-up of the sampling point with the best signal quality for the user, loading electrode excitation parameters adapted to the user's scalp impedance, and setting the optimal differential anti-interference parameters and noise reduction strategy adapted to the current scene. No manual configuration adjustment is required from the user.

[0109] The model update unit learns from newly added user data at preset intervals, updating the user-specific feature library and the optimal parameter model. As the number of times a user uses the device increases, the personalized adaptation effect is continuously optimized. At the same time, the algorithm module supports multi-user mode, which can build independent feature libraries for different users and automatically load the corresponding personalized configuration when switching users, adapting to usage scenarios where multiple people share the device.

[0110] This embodiment uses a self-learning machine learning algorithm to achieve personalized adaptive adaptation of the device to different users, solving the pain point that general fixed parameters cannot adapt to individual user differences, and greatly improving the device's user adaptability and long-term data collection effect.

[0111] It should be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the scope of the application. It should be understood that when an element or layer is referred to as “on,” “adjacent to,” “connected to,” or “coupled to” other elements or layers, it may be directly on, adjacent to, connected to, or coupled to other elements or layers, or there may be intervening elements or layers. Conversely, when an element is referred to as “directly on,” “directly adjacent to,” “directly connected to,” or “directly coupled to” other elements or layers, there are no intervening elements or layers. It should be understood that although the terms first, second, third, etc., may be used to describe various elements, components, areas, layers, and / or portions, these elements, components, areas, layers, and / or portions should not be limited by these terms. These terms are merely used to distinguish one element, component, area, layer, or portion from another element, component, area, layer, or portion. Therefore, without departing from the teachings of this application, the first element, component, area, layer, or portion discussed below may be referred to as a second element, component, area, layer, or portion.

[0112] Spatial relation terms such as “below,” “under,” “below,” “under,” “above,” “above,” etc., are used herein for convenience of description to describe the relationship between one element or feature shown in the figure and other elements or features. It should be understood that, in addition to the orientation shown in the figure, spatial relation terms are intended to also include different orientations of the device in use and operation. For example, if the device in the figure is flipped, then the element or feature described as “below,” “under,” or “below” other elements or features will be oriented “above” other elements or features. Therefore, the exemplary terms “below” and “under” can include both above and below orientations. The device may be otherwise oriented (rotated 90 degrees or otherwise) and the spatial descriptive terms used herein will be interpreted accordingly.

[0113] The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the scope of this application. When used herein, the singular forms “a,” “an,” and “the” are also intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the terms “comprising” and / or “including,” when used in this specification, identify the presence of the stated features, integers, steps, operations, elements, and / or components, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or groups. When used herein, the term “and / or” includes any and all combinations of the associated listed items.

[0114] It should also be understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0115] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and these modifications or substitutions should all be covered within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. An electroencephalogram (EEG) acquisition device, comprising a device body, an ear clip assembly, a brain oxygen acquisition module, and a main control module, characterized in that, The EEG acquisition module, ear clip assembly, and brain oxygen acquisition module are all electrically connected to the main control module. The main body of the device is a flexible adaptable body, using flexible silicone as a covering layer, and setting an elastic material with preset tension and a flexible anti-interference circuit in the covering layer. The ear clip assembly consists of a first ear clip and a second ear clip that are symmetrically arranged on the left and right sides. The first ear clip is the reference negative electrode for EEG acquisition, and the second ear clip is the environmental interference acquisition end. The second ear clip is electrically connected to the differential amplifier module in the main control module and is used to differentially remove environmental noise from the acquired signal. The main body of the device is provided with an embedded magnetic female electrode interface, which serves as a dry electrode to collect EEG signals, and / or the magnetic female electrode interface is magnetically connected to an external electrode pad to collect EEG signals. The main body of the device has multiple preset forehead collection points, and the main control module integrates a point configuration switching module to wake up or turn off the corresponding collection points.

2. The EEG acquisition device according to claim 1, characterized in that, The flexible silicone is made of biocompatible material. The flexible anti-interference circuit is electrically connected to the magnetic female electrode interface of each forehead acquisition point, and is used to collect and transmit the EEG signals of each acquisition point to the main control module.

3. The EEG acquisition device according to claim 1, characterized in that, The differential amplification module of the main control module is used to receive EEG signals with environmental noise collected from the forehead acquisition point and environmental noise signals collected from the second ear clip. The differential cancellation algorithm is used to remove environmental noise from the signals in real time and extract pure EEG signals.

4. The EEG acquisition device according to claim 3, characterized in that, The main control module is also equipped with an analog front-end module and an analog-to-digital conversion module. The clean EEG signal, after being processed by the differential amplification module, is processed sequentially by the analog front-end module and the analog-to-digital conversion module and then transmitted to the control unit of the main control module for further processing.

5. The EEG acquisition device according to claim 1, characterized in that, An electronic switch matrix is ​​provided between the first ear clip and the second ear clip. The electronic switch matrix is ​​electrically connected to the main control module. The main control module can dynamically switch the function definitions of the first ear clip and the second ear clip through the electronic switch matrix, so as to realize the interchange of the reference negative terminal and the environmental interference acquisition terminal of the two ear clips.

6. The EEG acquisition device according to claim 5, characterized in that, The main control module also collects real-time data on the fit of the left and right ear clips and the signal acquisition stability of the two ear clips. Combined with the wearing status data and the real-time collected environmental noise characteristics, it controls the corresponding electronic switch matrix to switch the function definition of the first and second ear clips. At the same time, it dynamically updates the operation parameters and processing strategy of the differential cancellation algorithm to maintain the optimal noise suppression effect under different wearing states and environments.

7. The EEG acquisition device according to claim 1, characterized in that, The surface of the magnetic female electrode interface is coated with a highly conductive coating, and the external electrode is an electrode with a magnetic male clasp; and / or, The main body of the device has six preset forehead acquisition points, and the electrodes can complete the acquisition of electroencephalogram (EEG) signals by placing the electrodes near the target cortical region; and / or, The point configuration switching module of the main control module supports flexible wake-up and shutdown of multiple forehead collection points.

8. The EEG acquisition device according to claim 1, characterized in that, The main body of the device is also provided with an ear clip interface, an infrared acquisition interface, and a charging and data interface. The ear clip interface is electrically connected to the ear clip assembly, the infrared acquisition interface is electrically connected to the brain oxygen acquisition module, and the charging and data interface is electrically connected to the main control module.

9. The EEG acquisition device according to claim 1, characterized in that, The main body of the device uses an elastic material with preset tension inside the covering layer, combined with the extensibility of flexible silicone, to adaptively fit the forehead shape of different people and maintain stable contact between the collection point and the skin.

10. The EEG acquisition device according to claim 1, characterized in that, The main control module also determines the user's current usage scenario based on the collected EEG signal characteristics, environmental noise level, and physiological signal data from the brain oxygen acquisition module. According to the identified scenario, it wakes up or turns off the corresponding number of forehead acquisition points through the point configuration switching module, and synchronously adjusts the operation parameters of the differential amplification module to adapt to the EEG acquisition requirements of the current scenario.

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