A portable physiological parameter assessment system

Abstract

This application discloses a portable physiological parameter assessment system, comprising: a portable case, multiple physiological parameter detection devices, a central data processing device, and a data output device. The portable case has a receiving slot for housing the physiological parameter detection devices. The central data processing device collects the detection data from each physiological parameter detection device and outputs health assessment data through the data output device. Multiple physiological parameter detection devices corresponding to multiple different bodily functions are integrated with the central data processing device and the data output device within the portable case. Through the integrated design of the portable case, multiple physiological parameter detection devices corresponding to at least three bodily functions are centrally housed, avoiding the inconvenience of carrying multiple independent consumer-grade devices and solving the shortcomings of professional-grade devices such as large size and poor portability. This system can be flexibly adapted to mobile scenarios such as home-based monitoring, community health screening, and in-home health services.

Description

Technical Field

[0001] This application relates to the field of health management technology, and in particular to a portable physiological parameter assessment system. Background Technology

[0002] Currently, families and communities have become core scenarios for daily health management. These scenarios demand that physiological parameter monitoring devices not only be easy to operate and suitable for non-professional users, but also highly portable. They must meet the needs of families for on-the-go monitoring and also be compatible with mobile usage scenarios such as community health screenings and in-home health services. However, current physiological parameter monitoring devices on the market fail to meet the comprehensive usage requirements of family and community scenarios, exhibiting numerous technical deficiencies. They struggle to support the comprehensive testing needs of multiple bodily functions in these scenarios, and cannot provide users with intuitive overall health indices, making it difficult to achieve a comprehensive assessment of overall health status.

[0003] In daily health monitoring at home and in communities, most mainstream consumer-grade monitoring devices are isolated products with single functions, such as scales, smart bracelets, electronic blood pressure monitors, and portable blood glucose meters. These devices can only collect and detect single physiological parameters and cannot achieve comprehensive monitoring of multiple bodily functions, including circulatory, metabolic, and muscular systems. Although these devices are portable and easy to operate, making them suitable for home and community use, the monitoring data from different devices are stored separately within the devices themselves or in their own independent applications. This lack of effective unified data management and integration mechanisms leads to serious data fragmentation. Furthermore, each device can only output isolated parameter values ​​without a unified overall health index. Even if users manually collect various data, it is difficult to extract intuitive overall health assessment results from multi-dimensional parameters, making it impossible to form a comprehensive understanding of their own health status.

[0004] While professional-grade medical testing equipment, such as electrocardiographs, body composition analyzers, and professional blood pressure monitors, can achieve high-precision physiological parameter detection, and some devices can cover parameter collection for multiple bodily functions, the collected data has higher reference value and can provide professional support for health management in families and communities. However, these devices are generally expensive and have complex operating procedures, requiring a high level of professional knowledge and skills from operators. More importantly, most professional-grade devices are not portable, being bulky, requiring specialized auxiliary equipment, and having high power supply requirements. This makes them unsuitable for mobile and portable use in non-professional settings such as homes and communities, and difficult to adapt to the needs of community-based health testing and home-based professional monitoring. Furthermore, the test results of these devices are mostly lists of professional data, without outputting overall health indices for the general public. Ordinary users cannot directly understand the overall health meaning behind the data, creating a significant gap between consumer-grade daily monitoring and professional-grade accurate testing in home and community settings. This fails to effectively connect the detection of multiple bodily functions and cannot provide ordinary users with an easily understandable overall health assessment.

[0005] It is evident that existing health monitoring devices struggle to meet the demands for both high portability and comprehensive testing, making them unsuitable for applications in homes and communities. This has become a key issue hindering the deep implementation of physiological parameter monitoring technology in daily health management within families and communities. Summary of the Invention

[0006] This manual provides a portable physiological parameter assessment system to address the problem that existing health monitoring devices struggle to meet the requirements of high portability and comprehensive testing, making them unsuitable for application scenarios such as homes and communities.

[0007] To address the aforementioned technical problems, this specification provides a portable physiological parameter assessment system, comprising: a portable housing with a receiving slot for housing physiological parameter detection devices; multiple physiological parameter detection devices, each capable of being stored in a corresponding receiving slot; the physiological parameter detection devices are used to detect the user's physiological health data, and the detection data from the multiple physiological parameter detection devices correspond to multiple different bodily function systems; a central data processing device is disposed within the portable housing; the central data processing device is used to collect the detection data from each physiological parameter detection device and output the user's physical health assessment data. A data output device is disposed in the portable housing and electrically connected to the central data processing device; the data output device includes a local presentation module and / or an external communication module; the local presentation module is used to present the user's physical health assessment data; the external communication module is used to transmit the user's physical health assessment data to an external presentation terminal; wherein, multiple physiological parameter detection devices corresponding to multiple different bodily function systems are integrated with the central data processing device and the data output device in the portable housing, making the portable housing a single integrated portable device.

[0008] In some embodiments, a first power supply contact is provided on the inner side of each receiving slot, and a second power supply contact is provided on the outer wall surface of each physiological parameter detection device. The inner wall surface of the receiving slot at the first power supply contact and the outer wall surface of the device at the second power supply contact are adapted to each other, so that when the physiological parameter detection device is placed in the receiving slot, the positions of the first power supply contact and the second power supply contact match and naturally achieve electrical connection; the first power supply contact is electrically connected to the pre-embedded wiring in the portable case.

[0009] In some embodiments, the first power supply contact and the second power supply contact are magnetic contacts.

[0010] In some embodiments, a storage battery is integrated into the portable housing, and the storage battery is electrically connected to each first power supply contact inside each receiving slot.

[0011] In some embodiments, the multiple physiological parameter detection devices integrated in the portable housing include a body composition scale; a battery powering the body composition scale is electrically connected as an energy storage battery to each first power supply contact inside each receiving slot.

[0012] In some embodiments, a second charging interface is provided on the outside of the portable case, and the second charging interface is electrically connected to the energy storage battery for charging the energy storage battery.

[0013] In some embodiments, the physiological parameter detection device includes a body composition scale and at least one of an electroencephalogram (EEG) signal detection device, a heart rate detection device, a grip strength detection device, and a lung function detection device.

[0014] In some embodiments, each physiological parameter detection device that can be housed in the receiving tank has an independent power supply unit, signal acquisition unit and data storage unit, and can independently complete the acquisition and local storage of physiological parameters.

[0015] In some embodiments, the physiological parameter detection device includes an electroencephalogram (EEG) signal detection device; the EEG signal detection device includes: a first fixing part and a second fixing part for setting detection electrodes, the first fixing part corresponding to the circumferential direction of the head, and the second fixing part corresponding to the midline position of the head; the second fixing part is rotatably fixed on the first fixing part; when the EEG signal detection device is housed in a receiving slot, the second fixing part is rotated to overlap with the first fixing part.

[0016] In some embodiments, the electrodes on the EEG signal detection device can be symmetrically distributed in the prefrontal and central regions of the head, and distributed along the midline in the parietal and occipital lobes. Correspondingly, the central data processing device can be configured to perform the following operations: acquire multi-channel EEG signals from the prefrontal, central, parietal, and occipital lobes of the brain detected by the EEG signal detection device; determine a four-parameter feature set from the multi-channel EEG signals, the four-parameter feature set including the following four feature parameters: peak alpha frequency, 1 / f spectral slope, alpha wave relative power, and theta wave relative power; calculate a quantitative index value of brain functional state based on a preset mapping relationship according to the four-parameter feature set, and use the quantitative index value of brain functional state as functional system evaluation data of the nervous system; wherein, the mapping relationship is determined by training through a sample dataset, and the mapping relationship ensures that when the input four-parameter feature set is the same, a unique quantitative index value of brain functional state is output.

[0017] In some embodiments, the detection electrodes in the EEG signal detection device are adsorption-type conductive electrodes; the adsorption-type conductive electrode includes: an elastic conductive body having a skin contact surface and a device bonding surface disposed opposite to each other; the device bonding surface is integrally formed with a microstructure adsorption fixing layer, which, through physical adsorption, allows the device bonding surface to be detachably fixed to the surface of the bioelectric signal acquisition device in a surface contact form, forming a conductive contact area of ​​the bonding interface; the elastic conductive body has an integrally formed through-type continuous conductive structure, one end of which extends directly to the outer surface of the skin contact surface to form a signal acquisition end, and the other end extends directly to the bonding interface of the microstructure adsorption fixing layer of the device bonding surface, forming a signal output end that is directly connected to the bioelectric signal acquisition device, thus constructing a continuous bioelectric signal transmission path from the skin contact surface to the device bonding surface.

[0018] In some embodiments, the skin contact surface is provided with a conductive microneedle structure array, which is electrically connected to the through-type continuous conductive structure for passing through hair to contact the scalp.

[0019] In some embodiments, the elastic modulus of the elastic conductive body varies in a gradient from the skin contact surface to the device bonding surface; wherein the elastic modulus of the skin contact surface region is lower than that of the device bonding surface region, so that the skin contact surface conforms to the microstructure of the skin, while the device bonding surface maintains stable surface contact with the surface of the bioelectric signal acquisition device.

[0020] In some embodiments, the physiological parameter detection device includes a body composition scale; the body composition scale includes: a scale body, in which a weighing module and a body composition detection module are disposed; a display module, which includes a display screen and a wireless communication unit; and a connecting mechanism having a first state and a second state; in the first state, the connecting mechanism maintains a mechanical connection between the display module and the scale body, and allows the display module to rotate relative to the scale body and hover within a rotation range; in the second state, the connecting mechanism allows the display module to be mechanically separated from the scale body; when the display module is mechanically separated from the scale body, the display module establishes a communication connection with the scale body through the wireless communication unit.

[0021] In some embodiments, the multiple physiological parameter detection devices integrated in the portable case include a body composition scale; the portable case includes a cover and a base that can be opened and closed relative to each other, the body composition scale is embedded in the base, and when the cover is opened relative to the base, the detection surface of the body composition scale is exposed for user detection; the cover and the base are connected by a connecting component.

[0022] In some embodiments, the system further includes: a shielding portion disposed on the cover portion, and at least one side of the shielding portion being connected to a side of the cover portion; the shielding portion having a first structural position and a second structural position; when in the first structural position, the shielding portion can cover a receiving groove on the inner side of the cover portion; when in the second structural position, the shielding portion avoids the receiving groove on the inner side of the cover portion, thereby exposing the receiving groove.

[0023] In some embodiments, the shielding portion is connected to the side of the cover portion via a hinge axis and can rotate around the hinge axis to switch between a first structural position and a second structural position.

[0024] In some embodiments, a locking assembly is provided on a second side opposite to and / or adjacent to the first side of the portable case, the locking assembly being used to restrict the cover and base from rotating about the pivot of the connecting assembly when closed.

[0025] In some embodiments, the housing of the cover and the base is made of conductive composite material, forming a conductive shielding closed loop when closed; and / or, the inner wall of the receiving groove is provided with a conductive buffer layer, so that each receiving groove forms an independent shielding cavity; and / or, the connecting assembly is provided with a conductive spring, so that the cover and the base maintain shielding continuity in any open or closed state.

[0026] In some embodiments, at least one side of the shielding portion is provided with a conductive shielding layer; when in the first structural position, the shielding portion and the cover portion constitute a complete shielding space.

[0027] In some embodiments, the central data processing device acquires detection data from various physiological parameter detection devices that can be housed in a receiving tank via a wireless connection.

[0028] In some embodiments, the system further includes: a remote health management platform communicatively connected to the central data processing device, and / or a health management application for a mobile terminal communicatively connected to the remote health management platform and / or the central data processing device to obtain and present the data processing results of the central data processing device.

[0029] In some embodiments, the data output device presents radar charts of functional system assessment data for each bodily function system and / or overall physiological health assessment data, which are calculated based on the assessment data for each bodily function system.

[0030] In some embodiments, the central data processing device is configured to perform the following method: acquiring detection data output by a multimodal physiological parameter detection device that has established a communication connection with the central data processing device; the physiological parameter detection device is an independently operating physical detection device, and the detection data of each modality of the physiological parameter detection device corresponds to at least one bodily function system; processing the detection data output by the multimodal physiological parameter detection device according to a matched target data processing flow to generate functional system evaluation data for at least two bodily function systems; and generating overall physiological health evaluation data for the user based on the at least two functional system evaluation data according to the matched target data processing flow.

[0031] The portable physiological parameter assessment system provided in this manual integrates multiple physiological parameter detection devices corresponding to at least three bodily functions through the integrated design of the portable case. This avoids the inconvenience of carrying multiple independent consumer-grade devices and solves the shortcomings of professional-grade devices, such as large size and poor portability. It can be flexibly adapted to mobile scenarios such as home monitoring, community health screening, and door-to-door health services, enabling comprehensive detection of multiple bodily functions in grassroots settings to be carried out in a portable manner, breaking the technical bottleneck that "comprehensive detection and high portability cannot be achieved at the same time".

[0032] By integrating multi-dimensional detection devices into a portable enclosure and coordinating with a central data processing device to acquire all detection data, isolated physiological data that was originally scattered across different devices and independent applications can be collected and managed, completely solving the "data silo" problem of traditional consumer-grade devices. This provides a complete and coherent data source for the comprehensive evaluation of multiple bodily functions, avoiding evaluation bias caused by partial data.

[0033] The portable device integrates three core functions: detection, data processing, and result presentation. Users do not need to switch between multiple independent devices or manually collect and organize data. The entire process of "detection-processing-viewing results" can be completed through the integrated system. It not only meets the self-monitoring needs of family users, but also significantly reduces the operational complexity for community health service personnel, improves the efficiency of grassroots health screening and door-to-door services, and promotes the deep implementation of health monitoring technology in home and community settings.

[0034] The system retains the advantages of easy operation and high portability of consumer-grade devices, while also achieving professional-level health assessment depth through comprehensive detection of multiple body function systems and professional data processing by the central data processing device. It effectively fills the technological gap between existing consumer-grade and professional-grade monitoring devices, allowing ordinary users to enjoy integrated health monitoring services of "convenient operation + comprehensive detection + professional assessment" in home and community settings. Attached Figure Description

[0035] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this application. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0036] Figure 1 This is a schematic diagram of the portable physiological parameter assessment system provided in this manual; Figure 2 A three-dimensional structural diagram of an electroencephalogram (EEG) signal detection device; Figure 3 This is a top view schematic diagram of an electroencephalogram (EEG) signal detection device; Figure 4 This is a schematic diagram of the EEG signal detection device in its retracted and folded state. Figure 5 A flowchart illustrating the process of calculating quantitative indicators of brain functional status for central data processing devices; Figure 6 This is a schematic diagram of the cross-sectional structure of an adsorption-type conductive electrode. Figure 7 A schematic cross-sectional view of an adsorption-type conductive electrode with an antibacterial coating, anti-slip texture, and / or hydrophobic layer. Figure 8 This is a schematic diagram of an adsorption-type conductive electrode with an array of conductive microneedles. Figure 9 A schematic diagram illustrating the working state of conductive microneedles penetrating hair and contacting the scalp. Figure 10 A schematic diagram of the overall structure of a body composition scale; Figure 11 This is a schematic diagram of another state of the overall structure of the body composition scale; Figure 12 A schematic diagram of the body composition scale display module separated from the scale body; Figure 13 This is a schematic diagram showing the lid and base of the portable case in the closed state. Figure 14 This is a schematic diagram showing the lid and base of the portable case in the open position. Figure 15 A schematic diagram showing the structure in which the shielding part is in the second structural position (avoiding the inner receiving groove of the cover part); Figure 16 A schematic diagram showing the shielding part in the first structural position (the receiving groove inside the cover part); Figure 17 A schematic diagram of the internal storage compartments of a portable case; Figure 18 This is a schematic diagram showing the unfolded shape of the shielding section and the portable case. Figure 19 A schematic diagram of an interface presented to the user by a data output device; Figure 20 A schematic diagram of the process for generating physical health assessment data for a central data processing device. Detailed Implementation

[0037] To enable those skilled in the art to better understand the technical solutions in this application, the technical solutions in the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of this application.

[0038] This manual provides a portable physiological parameter assessment system, such as... Figure 1 As shown, it includes a portable housing A, multiple physiological parameter detection devices B, a central data processing device C, and a data output device D.

[0039] The portable case A has a compartment for storing the physiological parameter detection device.

[0040] Physiological parameter detection device B is used to detect the user's physiological health data. Multiple physiological parameter detection devices B can be stored in their respective receiving slots. In some embodiments, all physiological parameter detection devices B and their accompanying accessories can be stored inside the portable case A, forming a closed, portable structure without exposed accessories.

[0041] In some embodiments, the physiological parameter detection device in the portable physiological parameter assessment system includes at least two of the following: a body composition scale, an electroencephalogram (EEG) signal detection device, a heart rate detection device, a grip strength detection device, and a lung function detection device.

[0042] The detection data from the multiple physiological parameter detection devices installed in the portable housing A correspond to multiple different bodily functional systems, which may include at least two of the following functional systems: circulatory system (or cardiovascular system), respiratory system, nervous system, musculoskeletal system, and metabolic system.

[0043] The physiological parameter detection device corresponding to the circulatory system (or cardiovascular system) may include at least one of the following: heart rate detection device (which can detect heart rate rhythm) and HRV (Heart Rate Variability) detection device (which can detect HRV index).

[0044] The physiological parameter detection device corresponding to the respiratory system is an indirect detection type lung function detection device. The detection indicators corresponding to the respiratory system include at least one of the following: vital capacity, peak expiratory / inspiratory flow rate, resting ventilation, respiratory rate, etc.

[0045] The physiological parameter detection device corresponding to the nervous system may include at least one of the following: electroencephalogram (EEG) signal detection device and deep sleep detection device. The detection indicators corresponding to the nervous system may include at least one of the following: EEG signal rhythm, deep sleep quality (duration / percentage / cycle, etc.), autonomic nervous function balance, and the rest and repair state of the central nervous system.

[0046] The physiological parameter detection devices corresponding to the musculoskeletal system may include: grip strength detection devices and / or body composition scales, etc. The detection indicators corresponding to the musculoskeletal system include at least one of the following: hand muscle strength, total muscle mass / muscle rate, muscle fat ratio, etc.

[0047] The physiological parameter detection device corresponding to the metabolic system can be a body composition scale. The detection indicators corresponding to the metabolic system include at least one of the following: body fat percentage, muscle mass, body water percentage, bone mass, basal metabolic rate (derived), etc.

[0048] Each physiological parameter detection device is an independent physical detection device. That is, each physiological parameter detection device has an independent power supply unit, signal acquisition unit and data storage unit. It can complete the acquisition and local storage of physiological parameters independently without relying on other devices. It can be used independently of the system it belongs to, or it can establish a communication connection with the central data processing device in its system and work together with other components of the system to realize the system's functions.

[0049] The central data processing device C is housed within the portable casing A. The central data processing device C collects data from the physiological parameter detection devices B and outputs the user's health assessment data.

[0050] Data output device D is housed within portable casing A. Data output device D is electrically connected to the central data processing unit. Data output device D includes a local presentation module and / or an external communication module. The local presentation module is used to present the user's health assessment data. The external communication module is used to transmit the user's health assessment data to an external presentation terminal.

[0051] Multiple physiological parameter detection devices B, corresponding to multiple different bodily functional systems, are integrated with central data processing device C and data output device D in a portable case A, making the portable case A a single integrated portable device.

[0052] The portable physiological parameter assessment system provided in this manual integrates multiple physiological parameter detection devices corresponding to at least three bodily functions through the integrated design of the portable case. This avoids the inconvenience of carrying multiple independent consumer-grade devices and solves the shortcomings of professional-grade devices, such as large size and poor portability. It can be flexibly adapted to mobile scenarios such as home monitoring, community health screening, and door-to-door health services, enabling comprehensive detection of multiple bodily functions in grassroots settings to be carried out in a portable manner, breaking the technical bottleneck that "comprehensive detection and high portability cannot be achieved at the same time".

[0053] By integrating multi-dimensional detection devices into a portable enclosure and coordinating with a central data processing device to acquire all detection data, isolated physiological data that was originally scattered across different devices and independent applications can be collected and managed, completely solving the "data silo" problem of traditional consumer-grade devices. This provides a complete and coherent data source for the comprehensive evaluation of multiple bodily functions, avoiding evaluation bias caused by partial data.

[0054] The portable device integrates three core functions: detection, data processing, and result presentation. Users do not need to switch between multiple independent devices or manually collect and organize data. The entire process of "detection-processing-viewing results" can be completed through the integrated system. It not only meets the self-monitoring needs of family users, but also significantly reduces the operational complexity for community health service personnel, improves the efficiency of grassroots health screening and door-to-door services, and promotes the deep implementation of health monitoring technology in home and community settings.

[0055] The system retains the advantages of easy operation and high portability of consumer-grade devices, while also achieving professional-level health assessment depth through comprehensive detection of multiple body function systems and professional data processing by the central data processing device. It effectively fills the technological gap between existing consumer-grade and professional-grade monitoring devices, allowing ordinary users to enjoy integrated health monitoring services of "convenient operation + comprehensive detection + professional assessment" in home and community settings.

[0056] It is important to note that current technologies typically do not integrate physiological parameter detection devices, central data processing devices, and data output devices corresponding to multiple different bodily functions into a portable case. This is partly because electromagnetic interference from cross-modal sensors cannot be resolved, and partly because integration would inevitably result in an exponential increase in size and weight, making it difficult to achieve the portability requirements of home and community settings. Specifically: I. Electromagnetic Interference: The higher the integration, the more exponentially the interference worsens. In existing technologies, electromagnetic interference problems of single-function devices are relatively easy to solve. However, when a cross-modal detection device, a high-speed data processing device, and a high-frequency display output device are concentrated in a confined space of less than 10L, the electromagnetic interference evolves from a "single interference source" to "multi-source coupled intermodulation interference," with its intensity increasing exponentially rather than linearly superimposed. Specifically, 1. Intrinsic intermodulation interference from cross-modal detection devices. Detection devices for different bodily functions operate across a wide range of frequency bands (from DC to hundreds of kHz). When integrated into a confined space, signals from different frequency bands can intermodulate, generating new interference frequencies that happen to fall within the detection frequency band of weak bioelectrical signals. For example, the 50kHz carrier wave of a body composition scale intermodulates with the 660nm infrared light modulation signal of a pulse oximeter, producing interference signals that overlap with the ECG QRS complex (0.05Hz-100Hz). This intermodulation interference cannot be eliminated by conventional filtering methods and will directly lead to complete distortion of the ECG waveform.

[0057] 2. The central processing unit and data output devices themselves are strong sources of interference. Current technology generally overlooks the fact that the high-speed processor (clock frequency above 1GHz) of the central data processing unit and the backlight driving circuit of the LCD / OLED display of the data output device are themselves extremely strong sources of electromagnetic radiation. When the distance between them and the ECG and EMG modules that collect microvolt-level signals is less than 5cm, the intensity of their radiation interference can exceed 100 times that of the bioelectrical signals themselves. Furthermore, in portable cases with a capacity of less than 10L, it is impossible to provide sufficient safety clearance to isolate these sources of interference.

[0058] 3. The irreconcilable contradiction between shielding solutions and portability. To address the aforementioned interference, the only existing technology involves adding metal shielding covers, shielding wires, and absorbing materials. However, each additional layer of shielding increases the weight of the enclosure by 15%-20% and its volume by 10%-15%. If the enclosure is to simultaneously shield three strong interference sources—a scale, a processor, and a display screen—the shielding structure itself would weigh over 1 kg, directly compromising the device's portability. This creates a vicious cycle: "Add shielding → increased weight → loss of portability; no shielding → insufficient accuracy → unusable."

[0059] II. Cabinet Size: Existing stacked integration solutions have extremely low integration levels and significant space waste, inevitably resulting in excessively large cabinet sizes that fail to meet portability requirements. There is a clear industry consensus on the portability of portable health devices in home and community settings. However, the existing "planar stacking" integration method, due to its extremely low space utilization, struggles to meet this requirement. The core issues are reflected in three aspects: 1. The foot area of ​​the body composition scale is an incompressible hard constraint, directly occupying most of the bottom space of the enclosure. Body composition detection needs to meet the requirements of human feet standing, and its effective foot area has a fixed physical limitation. When using a planar stacking solution, the body composition scale alone will occupy most of the bottom space of the enclosure, leaving no extra space for other detection devices, central control and data output devices, and can only increase the volume of the enclosure.

[0060] 2. The multi-module independent structure results in severe space redundancy and low integration. In the existing technology, each physiological parameter detection device has an independent shell, battery compartment and interface. When these independent devices are simply stacked into the box, the gaps between the devices, the thickness of the shell of each device and the redundant structure of the independent battery will generate a lot of ineffective space, resulting in extremely low space utilization of the box and a significant increase in the overall volume.

[0061] 3. Inappropriate integration methods further exacerbate the size expansion. The centralized power supply design and scattered stacking layout of existing technologies cannot achieve compact adaptation of each module. They can only accommodate all components by increasing the size of the enclosure, which ultimately results in the enclosure size far exceeding the portability requirements and failing to meet the needs of home and community mobile use scenarios.

[0062] In summary, in the existing technology, the unsolvable nature of electromagnetic interference and the rigid constraints of volume are intertwined and form a vicious cycle. This means that any attempt to integrate multiple system detection devices, central data processing devices, and data output devices into a single portable enclosure will either sacrifice detection accuracy or portability, and will never be able to simultaneously meet the comprehensive needs of home and community scenarios for "comprehensive detection + high accuracy + high portability".

[0063] The portable physiological parameter assessment system provided in this manual features a receiving slot within the portable casing to house multimodal physiological parameter detection devices corresponding to different bodily functional systems. The shape of the receiving slot matches the shape of the corresponding physiological parameter detection device, thus solving the problems of low integration, large space waste, and excessive size in existing technologies. Specifically, 1. Solve the problem of space redundancy caused by independent shells of multiple modules: In the existing technology, each detection device is an independent structure (with an independent shell and battery compartment), and simple stacking can easily generate a lot of ineffective space; the receiving slot can accurately position and store each detection device without the need to reserve gaps between devices, reduce the space waste caused by independent shells, improve the utilization rate of the cabinet space, and avoid the expansion of the cabinet volume due to space redundancy.

[0064] 2. Solve the problem of excessive space occupation by planar stacking: In the existing planar stacking solution, the volumetric scale occupies most of the bottom space, leaving no space for other detection devices; the storage slot can realize the layered / partitioned storage of multiple detection devices (instead of planar stacking), making full use of the internal space of the box, without having to significantly increase the volume of the box to accommodate multiple detection devices, and helping the box meet the portability requirements.

[0065] In some embodiments, the physiological parameter detection device integrated into the portable housing A includes a body composition scale, and at least one of an electroencephalogram (EEG) signal detection device, a heart rate detection device, a grip strength detection device, and a lung function detection device.

[0066] An electroencephalogram (EEG) signal detection device is a sensor-based detection device that collects brainwave bioelectrical signals through contact with the human head, processes and transmits these signals, and then detects and analyzes them. An EEG signal detection device may include a support carrier, EEG sensing components, a signal processing module, and a power supply module.

[0067] The heart rate detection device uses a non-invasive photoelectric detection method to achieve real-time acquisition, data processing, and wireless transmission of human heart rate. It is adaptable to detection on multiple body parts such as the wrist and fingers. The heart rate detection device includes a PPG photoelectric sensor component, a signal processing module, and a power supply module.

[0068] Grip force detection devices collect mechanical signals from the human hand's grip through pressure sensors and convert them into precise grip force values. A grip force detection device may include a grip structure, pressure sensing components, a data display module, and a power supply module.

[0069] The pulmonary function testing device employs a non-invasive, indirect detection method. It collects related physical signals during human respiration, such as airflow velocity, respiratory pressure, and chest rise and fall, through sensing components. After analysis and conversion of these signals by a built-in algorithm, core pulmonary function indicators such as vital capacity, resting ventilation, respiratory rate, and peak expiratory / inspiratory flow rate are indirectly derived. The device includes a support carrier, indirect sensing components (including miniature airflow sensors, thin-film pressure sensors, and flexible displacement sensors), a signal processing and algorithm module, and a power supply module.

[0070] In addition to the detection devices mentioned above, it may also include devices for detecting physiological parameters corresponding to the aforementioned bodily functional systems.

[0071] Each physiological parameter detection device is an independently operating physical detection device. That is, each device has its own independent power supply unit, signal acquisition unit, and data storage unit. It can independently complete the acquisition and local storage of physiological parameters without relying on other devices. It can be used independently of its system, or it can establish a communication connection with the central data processing device within its system to collaboratively achieve the system's functions. This design addresses the problem of "the incompatibility between multi-detection device integration and electromagnetic compatibility" from three dimensions: interference source isolation, interference generation mechanism blocking, and decoupling shielding costs and portability. A detailed explanation follows: 1. Eliminate the fatal interference of strong interference sources on weak bioelectrical signals at the source.

[0072] In existing technologies, the central high-speed processor (1GHz+ clock) and LCD / OLED backlight driving circuit are extremely strong sources of electromagnetic radiation. When the distance between them and the ECG, EEG, and EMG modules that collect microvolt-level signals is small, the intensity of radiation interference exceeds 100 times that of the bioelectrical signals themselves and cannot be eliminated by conventional filtering. This design allows the detection device to operate independently of the enclosure. During detection, it can maintain any safe distance from strong interference sources such as the central data processing device and data output devices (such as displays), completely isolating strong radiation interference from physical space. There is no need to reserve an expensive and space-consuming shielding isolation area inside the enclosure, ensuring the original accuracy of bioelectrical signal detection.

[0073] 2. Completely block intrinsic intermodulation interference of cross-modal detection devices.

[0074] In existing integrated solutions, the operating frequency bands of detection devices for different bodily functions span a wide range (DC to hundreds of kHz). When operating simultaneously, these devices generate multi-source coupling intermodulation interference, producing noise that falls precisely within the bioelectrical detection frequency band (0.05Hz~100Hz). For example, the intermodulation between the 50kHz carrier wave of a body composition scale and the infrared modulation signal of a pulse oximeter can completely mask the QRS complex of an electrocardiogram. This new setup supports a single-device independent detection mode, allowing only one detection device to operate at a time. This mechanism fundamentally eliminates the intermodulation of signals from different frequency bands, thus solving the problem of intermodulation interference that conventional filtering methods cannot eliminate.

[0075] 3. Break the vicious cycle of "increased weight due to shielding → loss of portability".

[0076] Existing technologies require multiple layers of metal shielding and absorbing materials to address interference from multiple modules within the enclosure. Each additional layer increases the enclosure's weight by 15%-20% and its volume by 10%-15%, ultimately compromising portability. This new design only requires lightweight single-module shielding for each independent testing device, eliminating the need for complex multi-module partitioned shielding structures. During testing, the device is detached from the enclosure, eliminating the need for high-strength shielding between the central data processing unit and the testing modules. Overall, the amount of shielding material used is reduced by over 70%. While ensuring electromagnetic compatibility, this significantly reduces system weight and volume, meeting the portability requirements of home and community settings.

[0077] 4. Eliminate conducted coupling interference from the common power supply circuit.

[0078] In existing centralized power supply schemes, all detection devices share the same power circuit. The operating currents of different devices couple with each other through the internal resistance of the power supply, generating conducted interference (for example, the large current pulse of the volume fractionation scale will generate spike noise on the power line, crosstalking to the EEG detection circuit). This setup uses independent power supply units for each detection device, completely cutting off the power conduction interference path between detection devices, reducing the power supply noise level by more than an order of magnitude, and significantly improving the signal-to-noise ratio of weak signals.

[0079] 5. Avoid self-interference in wireless communication during the detection process.

[0080] Existing integrated physiological parameter assessment systems generally employ real-time wireless transmission of detection data. The radio frequency signals themselves significantly interfere with the detection of microvolt-level bioelectrical signals. Furthermore, simultaneous parallel transmission by multiple devices exacerbates channel congestion and signal crosstalk, severely reducing the accuracy and reliability of high-precision detection results. This new setup addresses this by configuring independent data storage units for each physiological parameter detection device, supporting local data caching and batch synchronization mechanisms during non-detection periods. During high-precision bioelectrical detection such as EEG and ECG, the device's wireless communication module can be completely shut down, eliminating electromagnetic interference from radio frequency signals and ensuring an absolutely pure electromagnetic environment during the detection period. Once all detection tasks are completed, the locally stored complete detection data is then uniformly synchronized to the central data processing device.

[0081] Meanwhile, the local storage mechanism also has the ability to protect against data transmission failures: when the central data processing device is interrupted, loses signal or has abnormal transmission, all detection data will be completely stored locally on the detection device and automatically retransmitted after communication is restored, effectively avoiding the loss of detection data due to transmission failure and ensuring the integrity and continuity of data collection.

[0082] In some embodiments, a first power supply contact is provided on the inner side of each receiving slot, and a second power supply contact is provided on the outer wall surface of each physiological parameter detection device. The inner wall surface of the receiving slot at the first power supply contact is adapted to the shape of the outer wall surface of the (physiological parameter detection) device at the second power supply contact, so that the positions of the first power supply contact and the second power supply contact match when the physiological parameter detection device is placed in the receiving slot, thereby naturally achieving electrical connection. The first power supply contact is electrically connected to the pre-embedded wiring in the portable housing A.

[0083] The embedded wiring is hidden inside the portable case. Users cannot see the embedded wiring when using the portable case for normal testing. This ensures the neatness of the case's appearance and provides good protection for the wiring, avoiding problems such as wear and interference caused by exposed wiring.

[0084] The pre-embedded wiring can be flexibly set according to actual structural requirements. It can be a circuit on a printed circuit board (PCB) or a flexible wire. Both forms can achieve a stable electrical connection between the first power supply contact and other electrical components in the enclosure, adapting to different internal layouts and production process requirements of the enclosure.

[0085] The corresponding surface shapes of the first power supply contact and the second power supply contact are adapted to form a charging guide groove, which has the following multiple technical effects: 1. Automatic alignment and error prevention: No need for manual precise alignment of the contact points. Users only need to roughly place the detection device into the receiving groove, and the inclined surface of the guide groove will guide the two contacts to automatically and accurately align and make tight contact, realizing blind insertion automatic electrical connection. This greatly improves the operation convenience for non-professional users and avoids poor contact problems caused by reverse or incorrect placement.

[0086] 2. Ultra-thin, compact, and space-saving: This shape-adaptive surface contact connection method eliminates the need for complex connection structures such as plugs, sockets, and clips. The connection thickness can be controlled within 1mm, effectively saving the space between the receiving slot and the physiological parameter detection device. This further optimizes the utilization rate of the internal space of the case and helps to achieve miniaturization and lightweight design of portable cases.

[0087] 3. Reliable contact and long service life: The limiting function of the guide groove ensures that the contact pressure and contact area of ​​the contact point are consistent each time it is placed, avoiding problems such as excessive contact resistance and overheating caused by point contact, thus improving the stability of power supply; at the same time, it reduces the lateral friction and wear of the contact point during insertion and removal, significantly extending the service life of the power supply contact.

[0088] 4. Enhanced protection performance: The shape-fitting design significantly reduces the gap between the receiving groove and the detection device, effectively preventing dust and moisture from entering the contact area, reducing the risk of contact oxidation and short circuits, and improving the reliability of the equipment in complex usage environments such as homes and communities.

[0089] The first and second power supply contacts mentioned above can be magnetic contacts. Using magnetic contacts with a shape-adaptive contact surface allows for a thinner connection structure and higher space utilization. It eliminates the need for the insertion depth, snap-fit ​​structure, and clearance space required by traditional plug-in connectors, resulting in a thinner overall contact area and a more compact fit between the housing and the detection device, further reducing overall size and weight. Simultaneously, the magnetic force assists in the automatic adsorption and alignment of the contacts, further improving contact reliability based on the guide groove structure, preventing poor contact due to loosening or displacement, and ensuring stable charging and data transmission.

[0090] In some embodiments, a storage battery is integrated into the portable housing A, and the storage battery is electrically connected to each first power supply contact inside each receiving slot. This arrangement has the following technical advantages: 1. Significantly reduce the size and weight of the detection device: Each physiological parameter detection device does not need to have a built-in large-capacity independent battery, which can reduce its size and weight by 40%-60%, further freeing up internal storage space and fundamentally solving the problem of space redundancy and weight accumulation caused by multiple independent batteries.

[0091] 2. Enables integrated power supply for on-demand charging: The detection device can be automatically charged when placed in the receiving slot and used immediately when taken out. Users do not need to charge or manage the power of each detection device separately, which completely eliminates the pain point of charging multiple devices and greatly improves the convenience of use.

[0092] 3. Further enhance the integrated design: All power supply links are hidden inside the cabinet, with no exposed charging interfaces and cables, which not only ensures the integrity of the appearance, but also avoids the risk of dust and water ingress caused by exposed interfaces.

[0093] Furthermore, in some embodiments, the multiple physiological parameter detection devices integrated in the portable housing A include a body composition scale; the battery powering the body composition scale acts as an energy storage battery and is electrically connected to each of the first power supply contacts inside each receiving slot. This reusable power supply configuration has the following technical advantages: 1. Reduce the number of batteries at the source, significantly reducing weight and volume: There is no need to set up an additional independent energy storage battery. The large-capacity power supply battery required by the body composition scale itself is reused, which directly reduces the volume and weight of a set of batteries and matching battery compartments, further freeing up internal space and helping the system achieve ultimate miniaturization and lightweighting.

[0094] 2. Significantly improve battery capacity utilization: The body composition scale is an intermittent working device with short single working time and long standby time, leaving its battery capacity idle for a long time. Reusing it as a system energy storage battery can make full use of the idle battery capacity to power other detection devices, avoiding waste of battery capacity and extending the overall system's total operating time.

[0095] 3. Simplified circuit structure, reduced cost and failure rate: The elimination of the need to design two independent battery management, charging protection and power supply circuits greatly simplifies the electrical wiring and circuit complexity inside the enclosure, which reduces production costs, reduces circuit failure points, and improves the overall operational reliability of the system.

[0096] 4. Naturally compatible power supply: The body composition scale requires the output of a large current pulse when it is working. Its matching battery itself has a large current discharge capacity, which can fully meet the charging needs of other low-power physiological parameter detection devices. No additional battery specifications need to be adjusted, and the compatibility is excellent.

[0097] In some embodiments, a second charging interface is provided on the outside of the portable case, and the second charging interface is electrically connected to the energy storage battery for charging the energy storage battery.

[0098] In some embodiments, the physiological parameter detection device includes an electroencephalogram (EEG) signal detection device. The EEG signal detection device includes a first fixing portion and a second fixing portion for setting detection electrodes, the first fixing portion corresponding to the circumferential direction of the head, and the second fixing portion corresponding to the midline position of the head.

[0099] The second fixing part is rotatably fixed to the first fixing part. When the EEG signal detection device is housed in the receiving slot, the second fixing part rotates to overlap with the first fixing part.

[0100] Furthermore, in some embodiments, the circumferential length of the first fixing part is adjustable to accommodate different head circumferences; the fixing position on at least one side of the second fixing part is detachably adjustable to accommodate different cranial heights.

[0101] By rotating the second fixing part to overlap with the first fixing part, the portable head-mounted device can be stored, making its use and storage more convenient and simple. Through the storage method of "rotating the second fixing part to overlap with the first fixing part", the lightweight brain function status assessment device can be stored in a flat shape, which can not only greatly improve the utilization of storage space, but also effectively compress the storage volume, making it more suitable for daily home storage scenarios (such as drawers, small storage boxes), further enhancing the convenience of the device in daily home use.

[0102] Figure 2 This is a three-dimensional structural diagram of the electroencephalogram (EEG) signal detection device provided in this specification. Figure 3 This is a top view schematic diagram of the electroencephalogram (EEG) signal detection device provided in this instruction manual. Figure 4 This is a schematic diagram showing the EEG signal detection device provided in this specification in its stored state. In the diagram, 10 represents the EEG signal detection device, 11 represents the detection electrode, 12 represents the reference electrode, 13 represents the ground electrode, M represents the first fixing part, and N represents the second fixing part.

[0103] The aforementioned rotatable and stackable EEG signal detection device addresses the pain points of existing head-mounted EEG detection devices, such as large storage volume, low integration, easy damage during carrying, and cumbersome operation for non-professional users. It also balances detection accuracy and wearability, as detailed below: 1. Extremely compressed storage volume, significantly improving system integration and portability. When stored, the second fixing part can rotate to completely overlap with the first fixing part, transforming the original T-shaped / cross-shaped three-dimensional structure into a flat and regular planar structure, reducing the storage volume of the device by more than 40%. It can perfectly fit the customized small storage slot in the portable case without reserving extra space, significantly improving the utilization rate of the internal space of the case, and helping the entire physiological parameter assessment system to achieve miniaturization and lightweight design, meeting the needs of portable scenarios such as community door-to-door service and outdoor mobile detection.

[0104] 2. Simplified operation process, lowering the barrier to entry for non-professional users. Adopting an integrated rotating connection design, no parts need to be disassembled. Users can easily unfold and store the device with just one hand, completely avoiding the problems of easily lost parts and complex assembly steps associated with traditional split EEG devices. Furthermore, after unfolding, the second fixing part naturally aligns with the midline of the head, enabling rapid and accurate electrode positioning. Users do not need to manually adjust the electrode arrangement, significantly shortening test preparation time and making it suitable for home-based self-testing and community-based batch screening scenarios.

[0105] 3. Improved structural reliability and equipment protection. The second fixing part is permanently rotatably connected to the first fixing part, with no easily lost independent parts. The structural stability is far superior to that of detachable designs. When stacked and stored, the originally protruding center electrode is completely wrapped and protected, avoiding the risk of electrode bending or damage during transportation. At the same time, it prevents dust and moisture from contaminating the electrode contact surface, extending the service life of the equipment.

[0106] 4. Balancing fit and signal stability: The rotatable second fixing part can be finely adjusted to fit different users' head circumference and head shape, ensuring uniform and stable contact pressure between the midline electrode and the scalp, reducing signal drift and interference caused by improper wearing; combined with the adsorption conductive electrode, it can further improve the accuracy and consistency of EEG signal acquisition.

[0107] 5. Deeply integrated with the system design. The neat shape formed after stacking can precisely fit the inner wall of the receiving slot, ensuring that when the device is placed in the receiving slot, the magnetic power supply contacts and data transmission contacts automatically and accurately align, realizing blind-plug automatic charging and data synchronization without manual adjustment. This perfectly matches the system's integrated design concept of "storage-charging-data transmission". The electrodes on the EEG signal detection device can be symmetrically distributed in the prefrontal and central lobes of the head, and distributed along the midline in the parietal and occipital lobes. The central data processing device can be configured to perform actions such as... Figure 5 The operation shown. Figure 5 The operations shown include the following steps S110 to S130.

[0108] S110: Acquire multi-channel EEG signals from the prefrontal, central, parietal, and occipital lobes of the brain detected by the EEG signal detection device.

[0109] S120: Determine a four-parameter feature set from the multi-channel EEG signal. The four-parameter feature set includes the following four feature parameters: peak α frequency, 1 / f spectral slope, α wave relative power, and θ wave relative power.

[0110] S130: Based on the four-parameter feature set, calculate the quantitative index value of brain functional state based on the preset mapping relationship, and use the quantitative index value of brain functional state as the functional system evaluation data of the nervous system; wherein, the mapping relationship is determined by training through sample dataset, and the mapping relationship ensures that when the input four-parameter feature set is the same, a unique quantitative index value of brain functional state is output.

[0111] Quantitative indicators of brain function can be reflected in brain age assessment values, brain activation status values, etc.

[0112] The "mapping relationship that outputs a unique quantitative index value of brain functional state when the four input parameter feature sets are the same" mentioned in this application refers to the fact that under ideal technical conditions, such as no data processing errors, the detection equipment being in a standard working environment and rated working state, and no external uncontrollable interference factors, the mapping relationship itself has the uniqueness of the output result. This is the core technical characteristic and design goal of the mapping relationship, and also the key feature of the technical solution protected by this application.

[0113] The four feature parameter set can consist of only four feature parameters: peak α frequency, 1 / f spectral slope, α wave relative power, and θ wave relative power. Alternatively, it can include other feature parameters based on these four feature parameters. These feature parameters can be calculated from the EEG signals detected by the detection electrodes in four brain regions: the prefrontal cortex, central cortex, parietal cortex, and occipital cortex.

[0114] The above four characteristic parameters, approached from three core technical dimensions—rhythmic characteristics, power distribution, and network coordination—form a non-redundant and highly complementary scientific evaluation system. This avoids the one-sidedness and limitations of single-parameter evaluation, and the evaluation results of each technical dimension accurately correspond to the five core evaluation dimensions of brain functional status defined by the applicant. Specifically, peak alpha frequency focuses on arousal level and energy state, corely characterizing the inherent stability of brain neural rhythms, and is a core rhythmic characteristic indicator reflecting brain alertness and basic vitality; alpha wave relative power quantifies relaxation state and stress regulation ability, reflecting the balance of resting-activated brain resource allocation through power ratio, and is a core power distribution indicator for assessing stress regulation and resting quality; theta wave relative power assesses cognitive load and attention concentration ability, memory processing and cognitive reserve ability, reflecting the load intensity and memory processing activity of the brain during task processing through power ratio, and is a core power distribution indicator suitable for all age groups; 1 / f spectrum slope characterizes the stability of neural rhythm and network coordination, accurately reflecting the complexity of whole-brain neuronal network coordination and the basic health status of brain development and aging, and is a core network coordination indicator for monitoring long-term brain health.

[0115] These four characteristic parameters, when combined, comprehensively cover the entire chain of brain function from "basic health → dynamic state → task processing," enabling both real-time assessment (such as current focus or fatigue) and monitoring long-term health trends (such as cognitive decline risk and developmental maturity), achieving a "three-dimensional assessment" rather than a "single-point judgment." This addresses the core pain points of existing technologies while achieving a balance between professionalism and practicality.

[0116] The combination of the above four characteristic parameters follows the principle of necessity and sufficiency, and can meet the needs of portable home use.

[0117] The method of assessing brain functional status by using a combination of four feature parameters has the following advantages: 1. High computational efficiency: It does not require complex nonlinear feature extraction (such as multi-scale entropy and higher-order statistics), and can be calculated using only FFT, linear regression, and power integral, which has low requirements for device computing power (consumer-grade microprocessors can support it), enabling real-time assessment; 2. Low data requirements: It only requires 4-8 channels of data, eliminating the need for 16-64 channels of whole-brain coverage in professional-grade equipment, reducing the size, weight, and cost of the device, and meeting the portability needs of daily monitoring for families and individuals; 3. Avoidance of redundant interference: It does not introduce parameters that are weakly correlated with brain function (such as absolute power of delta waves and instantaneous amplitude of a single brain region), reducing the interference of irrelevant factors on the assessment results and solving the pain points of "redundant feature parameters and unstable accuracy" in existing technologies.

[0118] The evaluation results using four characteristic parameters can be directly applied to different usage scenarios, satisfying both the daily status management needs of ordinary people and providing effective references for health monitoring. Specifically: 1. Daily scenarios: α / θ relative power determines whether it is suitable for work, study, or rest, and peak α frequency assesses energy status, enabling personalized time management (e.g., breaking down tasks when α waves are too high, and meditating when α waves are too low); 2. Health monitoring scenarios: Long-term trends in 1 / f spectrum slope monitor the risk of cognitive decline (e.g., a persistently steep slope in the elderly) and the developmental maturity of children (a gradually flattening slope in adolescents); abnormal combinations of peak α frequency and θ wave relative power provide early warning of attention deficit disorders, mild cognitive impairment, and other problems; 3. Cross-population adaptability: Applicable to different populations such as children and adolescents (developmental monitoring), adults (work efficiency management), and the elderly (brain health maintenance), without the need to adjust parameter combinations for specific populations, making it highly versatile.

[0119] The proprietary quantization mapping relationship in this application forms a one-to-one closed-loop technical solution with the four-parameter feature set and the 4-8 channel lightweight hardware structure, which is irreplaceable. The core of this solution is reflected in the following two aspects: 1. Without this mapping relationship, it is impossible to achieve a balance between lightweight hardware and professional-grade precision.

[0120] If the proprietary quantization mapping relationship of this application is not adopted, there are only two alternative solutions in the prior art, neither of which can meet the core inventive purpose of this application.

[0121] The two alternatives are: (1) Using a professional-grade full-band multi-parameter complex model: This type of model requires input of more than 10 EEG feature parameters and more than 16 channels of whole-brain EEG data, which has extremely high computing power requirements. The calculation time for a single frame of data is ≥4.8 seconds, which cannot achieve real-time evaluation on the consumer-grade low-computing-power microprocessor of this application, and is completely inconsistent with the lightweight design goal of portable devices; (2) Using a conventional simplified linear regression model: Although this type of model can be adapted to low-computing-power hardware, under the condition of 4-8 channels and four parameters of the small amount of data input in this application, it cannot fit the nonlinear relationship between the four parameters and the brain functional state. The relative error of the evaluation in the home unshielded environment is ≥22%, which cannot meet the core requirements of accurate evaluation.

[0122] Only the proprietary quantization mapping relationship of this application can achieve an evaluation relative error of ≤5% comparable to that of professional-grade 64-channel devices, while meeting the real-time response requirement of ≤1 second, under the premise of only inputting a four-parameter feature set and adapting to consumer-grade low-computing-power hardware. This is an irreplaceable core technology in the lightweight solution of this application.

[0123] 2. Without this mapping relationship, it is impossible to achieve a full-dimensional evaluation of the value of the four-parameter combination.

[0124] The four-parameter feature set of this application corresponds to the five core assessment dimensions of brain functional state. There is a non-linear complementary relationship between the parameters, rather than a simple linear superposition relationship. Conventional general-purpose algorithm models cannot specifically fit the complementary characteristics of the four parameters, resulting in either dimensional redundancy or dimensional missingness, failing to fully cover the five assessment dimensions. In contrast, the proprietary quantitative mapping relationship of this application is specifically trained and optimized based on the complementary characteristics of the four parameters and the correspondence of the five assessment dimensions. It can accurately fit the non-linear relationship between the four parameters and brain functional state, achieving the core invention objective of "completing accurate assessment of all dimensions with the fewest parameters," forming an inseparable technical whole with the four-parameter feature set.

[0125] The detection electrodes in the aforementioned electroencephalogram (EEG) signal detection device can be adsorption-type conductive electrodes. Figure 6 A schematic cross-sectional view of the adsorption-type conductive electrode in this embodiment is shown. Figure 6 As shown, the adsorption-type conductive electrode includes an integrally formed elastic conductive body 25. The elastic conductive body 25 has a skin contact surface 21 and a device contact surface 27 that are disposed opposite to each other.

[0126] In some embodiments, the elastic conductive body 25 can be made of a flexible conductive polymer material, such as conductive silicone, conductive rubber, or flexible conductive polyurethane, giving it good deformation capability and biocompatibility. The elastic conductive body 25 has a sheet-like or arc-shaped structure (which can be designed to fit the signal acquisition site, such as an arc-shaped fit structure for the wrist, chest, etc.). In some embodiments, the elastic conductive body 25 can be integrally formed from an elastic matrix and conductive fillers doped in the elastic matrix through injection molding or compression molding. The elastic matrix can be selected from liquid silicone (LSR), thermoplastic polyurethane (TPU), or other polymer materials with good flexibility and resilience (e.g., conductive fabric). Liquid silicone is suitable for skin contact scenarios, with good biocompatibility and high softness. Thermoplastic polyurethane is suitable for acquisition sites that need to be repeatedly bent, with high toughness. Conductive fabric is suitable for large-area signal acquisition, with good breathability. It can be flexibly selected according to actual usage requirements.

[0127] The conductive filler can be selected from carbon nanotubes, graphene, carbon black, or other microparticles or fibrous materials with good conductivity. By uniformly dispersing the conductive filler in a liquid or molten elastic matrix and then injecting it into a mold for curing, a single, seamless elastic conductive body 25 is formed.

[0128] The device bonding surface 27 is integrally formed with a microstructure adsorption and fixing layer 28. This microstructure adsorption and fixing layer 28 can be formed directly by transferring a microstructure pattern from the mold cavity surface during injection molding, or it can be formed on the device bonding surface 27 after molding through processes such as laser etching, micro-imprinting, or chemical etching. In one embodiment, the microstructure adsorption and fixing layer 28 can be a micro-suction cup array, a micro / nano-convex structure, or a flexible bonding microstructure. In one embodiment, the microstructure adsorption and fixing layer 28 includes a large number of micron-sized protrusions, pits, or suction cup-like structures.

[0129] The microstructures in the microstructure adsorption and fixation layer 28 can generate adsorption and adhesion forces through physical interactions such as van der Waals forces with the adsorbed surface. Through physical adsorption, the microstructure adsorption and fixation layer 28 allows the device contact surface 27 to be detachably fixed to the surface of the bioelectric signal acquisition device in a surface contact manner, forming a conductive contact area at the contact interface. Because it is a physical adsorption process, disassembly will not damage the device surface and the device can be reused.

[0130] The elastic conductive body 25 has an integrally formed continuous conductive structure 26. This continuous conductive structure 26 can be formed by a continuous network of conductive fillers doped in the elastic matrix overlapping each other during the molding process, or it can be formed by embedding conductive fibers, conductive films, or metal mesh inside the elastic conductive body 25. One end of the continuous conductive structure 26 extends directly to the outer surface of the skin contact surface 21, forming a signal acquisition end exposed to the skin contact surface 21 for contacting the skin of the subject to pick up bioelectric signals. The other end of the continuous conductive structure 26 extends directly to the bonding interface of the microstructure adsorption and fixation layer 28 of the device bonding surface 27, forming a signal output end directly connected to the bioelectric signal acquisition device. Since the entire conductive path from the skin contact surface 21 to the device bonding surface 27 is an integrally formed, continuous, and uninterrupted structure, there are no physical interfaces or welding points between different material layers in traditional multi-component electrodes, thus constructing a continuous bioelectric signal transmission path from the skin contact surface 21 to the device bonding surface 27.

[0131] In this embodiment, the adsorption-type conductive electrode is used by pressing the microstructure adsorption fixing layer 28 of the device bonding surface 27 against the surface of the bioelectric signal acquisition device (e.g., the metal panel of a fitness equipment handle, the glass surface of a body composition scale, the plastic shell of an ECG patch, etc.). Physical adsorption forces are generated between the microstructure and the adsorbed surface, causing the module to adhere firmly to the device surface and forming a tight planar conductive contact. At this time, the signal acquisition end of the through-type continuous conductive structure 26 contacts the skin of the test subject, and the signal output end is electrically connected to the device signal input end through the conductive contact area of ​​the bonding interface. The bioelectric signal is directly transmitted from the skin to the bioelectric signal acquisition device via the through-type continuous conductive structure 26, without the need for additional wires, solder joints, or conductive adhesive.

[0132] In the above embodiments, the microstructure adsorption and fixation layer 28 of the conductive module enables the conductive module to be detachably fixed to the native surface of the bioelectric signal acquisition device in a surface contact manner through purely physical adsorption. No pre-installed installation structure, mechanical interface, or adhesive coating is required on the device, and disassembly does not damage the device surface, achieving true plug-and-play and non-destructive assembly / disassembly. The continuous conductive structure 26 extends directly from the outer surface of the skin contact surface 1 to the bonding interface of the device bonding surface 27, eliminating the macroscopic physical interfaces such as fabric / sponge, sponge / wire, and wire / solder joint in traditional multi-component electrodes. This avoids problems such as poor interface contact, resistance drift, and signal loss, ensuring high-fidelity transmission of bioelectric signals from the skin to the acquisition device. The conductive module does not rely on any modifications to the device and can be adapted to various native surfaces such as metal, plastic, glass, and composite materials. The same module can be freely transferred and used between different types of fitness equipment, body composition scales, ECG patches, EEG caps, etc., significantly reducing the overall cost for equipment manufacturers and end users. The conductive module can be easily disassembled for cleaning or replacement, effectively addressing the risk of cross-infection in shared environments such as gyms and rehabilitation centers.

[0133] In some embodiments, such as Figure 7 As shown, the skin contact surface 21 is provided with an antibacterial coating 22, an anti-slip texture 23, and / or a hydrophobic layer 24. One or more of the following treatments are applied to the skin contact surface 21. In one embodiment, an antibacterial coating 22 can be applied to the skin contact surface 21, using silver ion-based, zinc oxide-based, or organic antibacterial materials to inhibit bacterial growth. In another embodiment, an anti-slip texture 23, such as raised dots, mesh patterns, or stripes, can be formed on the skin contact surface 21 to increase friction with the skin and prevent slippage. In yet another embodiment, a hydrophobic layer 24 can be applied to reduce the adhesion of sweat and bodily fluids, facilitating cleaning and maintaining signal stability. The above treatments can be achieved through coating, blending, or molding, improving the hygiene and signal acquisition reliability of the adsorption-type conductive electrode in multi-user shared environments.

[0134] Please refer to Figure 8 and Figure 9 The diagrams show structural schematics of the adsorption-type conductive electrode in the embodiments of this specification and application scenario diagrams of the adsorption-type conductive electrode. In some embodiments, such as Figure 8 As shown, the skin contact surface 21 is provided with a conductive microneedle structure array 29, which is electrically connected to a through-type continuous conductive structure 26 for penetrating hair to contact the scalp. Figure 9As shown, the microneedle structure on the skin contact surface 21 of the adsorption conductive electrode can penetrate the hair and contact the scalp, effectively avoiding the interference of hair on signal transmission, reducing contact impedance, and thus improving the reliability and accuracy of EEG signal acquisition. This solves the problem of weak and unstable signals caused by hair obstruction during EEG detection in traditional adsorption conductive electrodes.

[0135] Specifically, the conductive microneedle structure array 29 is composed of multiple microneedles arranged at predetermined intervals. The shape of the microneedles can be selected from at least one of a square pyramid, a cone, a triangular pyramid, or a frustum. In one embodiment, the tip of the microneedle is rounded to avoid scratching the scalp. In one embodiment, the height of the microneedles ranges from 200 μm to 800 μm, preferably from 300 μm to 500 μm, to ensure sufficient contact area and low contact resistance.

[0136] The conductive microneedle structure array 29 can be integrally formed with the elastic conductive body 25. During manufacturing, an injection molding process can be used. A microneedle cavity is set within the mold at the position corresponding to the skin contact surface 1. A conductive composite material (such as liquid silicone doped with carbon nanotubes) is injected into the mold, integrally forming the elastic conductive body 25 and the conductive microneedle structure array 29 on its surface. In this case, the material of the conductive microneedle structure array 29 is the same as that of the elastic conductive body 25, and the conductive filler inside the microneedles and the continuous conductive structure 26 in the elastic conductive body 25 naturally form a continuous conductive network, achieving a low-impedance electrical connection from the microneedle tip to the signal output terminal. Optionally, after injection molding, a microneedle array can also be formed on the skin contact surface 21 by laser etching or chemical etching, and then a conductive layer (such as silver, gold, or titanium nitride) can be deposited on the microneedle surface by sputtering, evaporation, or chemical plating to further reduce contact impedance.

[0137] Furthermore, the conductive microneedle array 29 can coexist with the antibacterial coating 22, anti-slip texture 23, and hydrophobic layer 24 on the aforementioned skin contact surface 21. For example, after the microneedle array is formed, the antibacterial coating 22 and hydrophobic layer 24 can be applied only in the flat areas between the microneedles by selective spraying or vapor deposition, while keeping the microneedle tips exposed to ensure low-impedance contact; or an ultrathin (<1μm) conductive hydrophobic coating can be applied to the entire skin contact surface 21 (including the microneedle surface) to balance hair penetration contact with sweat and stain resistance.

[0138] In some embodiments of this specification, the elastic modulus of the elastic conductive body 25 varies in a gradient along the direction from the skin contact surface 21 to the device bonding surface 27. Specifically, the elastic modulus of the skin contact surface 21 region is lower than that of the device bonding surface 27 region, so that the skin contact surface 21 conforms to the skin's microstructure, while the device bonding surface 27 maintains stable surface contact with the surface of the bioelectric signal acquisition device.

[0139] In one embodiment, the elastic modulus of the skin contact surface 21 is set to a Shore A hardness of 10-25 (approximately 0.5-2 MPa). This low-modulus area can fully conform to the micro-texture of the skin, increase the effective contact area, reduce contact resistance, and improve wearing comfort, avoiding local discomfort or indentations caused by prolonged pressure. In another embodiment, the elastic modulus of the device contact surface 27 is set to a Shore A hardness of 40-70 (approximately 5-20 MPa). This high-modulus area can provide rigid support for the microstructure adsorption and fixation layer 28, ensuring that the micro-suction cup or micro-protrusion maintains shape stability during adsorption, thereby achieving greater adsorption adhesion and resisting shear forces during use, preventing the module from accidentally falling off.

[0140] In some embodiments, the physiological parameter detection device includes a body composition scale, such as... Figure 10 , Figure 11 and Figure 12 As shown, the body composition scale may include: scale body 31, display module 32 and connecting mechanism 33.

[0141] The scale body 31 is equipped with a weighing module and a body composition detection module. As the main measuring body, the scale body 31 integrates common weighing modules (such as strain gauge sensors) to acquire weight signals, and a body composition detection module (e.g., a circuit based on the principle of bioelectrical impedance analysis (BIA)) to measure human body impedance through electrodes and calculate composition data such as body fat percentage and muscle mass.

[0142] The scale body 31 has a detection surface with detection electrodes, which can be the aforementioned adsorption-type conductive electrodes. When the user places both feet on the detection electrodes, the electrodes contact the skin on the soles of the feet, releasing a weak, safe current into the body. The body composition is analyzed by detecting the conduction resistance of this current within the body.

[0143] The display module 32 includes a display screen and a wireless communication unit. Specifically, the display module 32 is a module that integrates information presentation and communication functions. The display screen (such as an LCD or OLED screen) of the display module 32 is used to visualize data. The display module 32 also integrates at least one wireless communication unit (e.g., a Bluetooth module or a WiFi module) for establishing a wireless data link.

[0144] The connecting mechanism 33 has a first state and a second state. In the first state, the connecting mechanism 33 maintains a mechanical connection between the display module 32 and the scale body 31, allowing the display module 32 to rotate relative to the scale body 31 and hover within its rotation range. In the second state, the connecting mechanism 33 allows the display module 32 to be mechanically separated from the scale body 31. The connecting mechanism 33 is used to rotatably connect the display module 32 to the scale body 31. The preset angle range can refer to the angle between the display module 32 and the scale body 31. For example, the preset angle range can be an interval from near 0° to a certain maximum angle. Another example is that the preset angle range can be 0° to 180°. Yet another example is that the preset angle range can be 0° to 170°. The connecting mechanism 33 integrates a damping or locking mechanism (such as a friction damper, ratchet mechanism, etc.) to ensure that the display module 32 can be stably held at at least a few specific angles within the preset angle range, eliminating the need for continuous hand-holding and facilitating user viewing.

[0145] When the display module 32 is mechanically separated from the scale body 31, the display module 32 establishes a communication connection with the scale body 31 via a wireless communication unit. In one embodiment, after the display module 32 is mechanically separated from the scale body 31, its built-in wireless communication unit is activated, and a wireless communication connection is automatically established with the corresponding communication unit inside the scale body 31 (e.g., Bluetooth pairing connection). Through this wireless communication link, the scale body 31 can send real-time detected or stored body composition data to the separated display module 32 for user viewing.

[0146] The aforementioned component scale adopts an integrated design that combines functionality, in-situ storage, and a flattened form. By using a foldable embedded display module in conjunction with the scale body's fitting groove, the overall thickness in the folded state is reduced by more than 30%. There is no need to reserve a separate storage slot for the display module and other components in the portable case; all components can be stored in their original positions using the scale body's own space.

[0147] In some embodiments, the connection mechanism 33 further includes a contact conductive structure. When the display module 32 is mechanically connected to the scale body 31, the contact conductive structure charges the display module 32, and / or the display module 32 and the scale body 31 establish a wired communication connection through the contact conductive structure. When the display module 32 and the scale body 31 are mechanically separated, the contact conductive structure automatically disconnects. When the display module 32 and the scale body 31 are mechanically connected through the connection mechanism 33, the contact conductive structure automatically establishes an electrical connection. Current flows from the scale body 31 to the power supply unit (such as a battery) of the display module 32 through the contact conductive structure to replenish its power. Data can be transmitted wiredly between the display module 32 and the scale body 31 through the contact conductive structure. When the user operates the connection mechanism 33 to mechanically separate the display module 32 from the scale body 31, the contact conductive structure automatically and physically disconnects the electrical connection. By incorporating a contact-type conductive structure, charging and / or data communication functions can be integrated into the physical connection process. Users only need to complete the assembly to automatically obtain a continuous power supply and a reliable data channel, greatly simplifying user operation and enhancing convenience. Simultaneously, the automatic disconnection mechanism ensures safety and allows the body composition scale to seamlessly switch to wireless operating mode when disconnected.

[0148] In some embodiments, the wireless communication unit includes a first wireless communication unit and a second wireless communication unit. When the display module 32 is mechanically separated from the scale body 31, the display module 32 establishes a communication connection with the scale body 31 through the first wireless communication unit, and also establishes a communication connection with the central data processing device through the second wireless communication unit.

[0149] In some embodiments, the display screen includes a main display screen located on the front of the display module 32 and an auxiliary display screen located on the back. When the display module 32 is folded over the scale body 31 via the connecting mechanism 33, the auxiliary display screen displays the weight information detected by the weighing module.

[0150] The front of the display module 32 refers to the surface of the display module 32 that is positioned opposite the scale body 31. When the user rotates and folds the display module 32 via the connecting mechanism 33, so that it covers the scale body 31 (i.e., in the stored or standby state), the main display screen on the front will be obscured from the surface of the scale body 31. At this time, the auxiliary display screen on the back automatically faces outward and becomes visible. This auxiliary display screen is configured to display the baseline weight information detected by the weighing module. This setup enables rapid measurement in the stored state. The user does not need to unfold or separate the display module 32; they only need to stand on the scale body 31 to directly read real-time weight data through the outward-facing auxiliary screen in the folded state. This simplifies the daily high-frequency weighing process and provides a burden-free and rapid measurement experience.

[0151] In some embodiments, the upper surface of the scale body 31 is provided with a groove adapted to the display module 32. When the display module 32 is folded over and covers the scale body 31, at least a portion of the display module 32 is embedded in the groove.

[0152] When the user rotates and folds the display module 32 onto the scale body 31 via the connecting mechanism 33, the groove can accommodate the display module 32, allowing at least a portion of the display module 32 (especially the main body containing the display screen) or all of the display module 32 to be embedded in the groove, rather than simply stacked on the surface of the scale body 31. By embedding the display module 32 at least partially into the scale body 31, the overall thickness in the folded state is effectively reduced, making the product appear flatter when stored. The groove structure also provides circumferential restraint and protection for the embedded display module 32 (especially its screen and edges), reducing the risk of scratches or damage to the display module 32 during movement, storage, or accidental bumps. In the folded state, the display module 32 is restrained by the groove, making it less likely to slide or shift on the surface of the scale body 31, thus improving the overall structural stability of the device.

[0153] In some embodiments, an electrode handle is also provided on the upper surface of the scale body 31. In addition to the measurement area for standing, the upper surface of the scale body 31 also includes an electrode handle and a corresponding connecting cable groove. The electrode handle is a component for the user to hold, and its surface integrates hand electrodes for bioelectrical impedance measurement. When performing body composition measurements, the user can hold this handle, which, together with the foot electrodes (usually integrated into the standing area of ​​the scale surface), forms a complete current loop to obtain more accurate and stable body composition data. The electrode handle provides a more ergonomic grip, improving the comfort of the measurement process and the reliability of electrode contact.

[0154] In some embodiments, the portable housing A includes a cover 100 and a base 200 that can be opened and closed relative to each other. The body composition scale 210 is embedded in the base. When the cover 100 is opened relative to the base 200, the detection surface of the body composition scale is exposed for user detection.

[0155] like Figure 13 This is a schematic diagram showing the cover 100 and the base 200 in the closed state. Figure 14 This is a schematic diagram showing the cover 100 and the base 200 in the open state. The cover 100 and / or the base 200 are provided with receiving grooves on their inner sides. The receiving grooves on the inner side of the cover 100 are adapted to the shape of other physiological parameter detection devices, and the receiving grooves on the inner side of the base 200 are adapted to the shape of the body composition scale 210.

[0156] The cover 100 and the base 200 can be split open. A connecting assembly 300 is disposed on the first side of the portable housing for connecting the cover 100 and the base 200. For example, as... Figure 14 As shown, the cover 100 and the base 200 are connected by a connecting assembly 300, which allows them to rotate and unfold up to 180° around the pivot of the connecting assembly 300. The connecting assembly 300 may also integrate a damping structure to ensure a smoother unfolding process for the cover 100 and the base 200. The connecting assembly 300 may be a hinged structure.

[0157] The portable housing provided in this application adopts this embedded structure, allowing the entire portable housing to be placed directly on the ground. The user can complete the test by standing on the body composition scale's detection surface at the base, without needing to remove the body composition scale from the housing. This design has the following technical advantages: 1. More stable structure and higher integration: The body composition scale and the base form an integrated whole structure, with a connection strength far exceeding that of detachable installations. It can stably withstand the load of a standing human body, avoiding the problems of loosening and displacement of independent modules. At the same time, it eliminates the need for the shell, disassembly and assembly buckles, and storage clearance required for independent body composition scales, transforming the body composition scale itself into a structural component of the cabinet, greatly improving the system integration and further reducing the overall volume of the cabinet. 2. More convenient operation and higher testing efficiency: The operation steps of taking out, putting away and returning the body composition scale are completely eliminated. Users can directly perform body composition testing by opening the box. The operation is completed in one step, which significantly simplifies the usage process. It is especially suitable for high-frequency and rapid testing scenarios such as community batch health screening and door-to-door services by medical staff.

[0158] A locking assembly may be provided on a second side opposite to and / or adjacent to the first side of the portable housing to restrict the cover 100 and the base 200 from rotating about the pivot of the connecting assembly 300 when closed.

[0159] A handle can also be provided on the side of the portable case opposite to the first side to improve the portability of the portable physiological parameter assessment system and make it suitable for scenarios such as family health management and community health services.

[0160] In some embodiments, the thickness of the cover portion 100 can be 45 mm, and the thickness of the base portion 200 can be 24-25 mm, that is, the cover portion 100 and the base portion 200 can have a thickness difference.

[0161] The receiving groove can be integrally formed with the rigid shell of the cover 100 and the base 200 through injection molding and stamping processes; or it can be pre-installed in the inner side of the box, and the prefabricated groove can be separately fixed by snap-fitting, bonding or other methods.

[0162] To better buffer and protect the various physiological parameter detection devices, the interior and bottom of the receiving tank can be lined with flexible buffer layers such as silicone or sponge. The tank body of the Body Composition Scale 210 can adopt a double-layer buffer structure; the tank opening can be designed as an arc shape, and the bottom of the receiving tank can be equipped with silicone anti-slip and shock-absorbing protrusions; the tank walls can be equipped with symmetrical elastic locking protrusions to achieve flexible limiting of the physiological parameter detection devices. The tank body of the Body Composition Scale 210 provides suspended positioning protection for the detection electrode area, and is equipped with an ultra-thin silicone pad to prevent compression and wear. All protective structures are integrated into the tank body design, without occupying additional space.

[0163] The body composition scale 210 is located inside the base 200. When the base 200 and the cover 100 are opened relative to each other, the detection surface of the body composition scale 210 is exposed for user testing. In other words, when the base 200 and the cover 100 are opened, the scale body of the body composition scale 210 can be used directly without being removed from the base 200. If accessories are provided, the full functionality of the body composition scale 210 can be used after removing the accessories.

[0164] like Figure 15 As shown, 101 can be a receiving slot for a heart rate detection device with a depth of 38mm; 102 can be a receiving slot for a deep sleep module that integrates EEG signal detection and heart rate detection functions with a depth of 38mm; 103 can be a receiving slot for an EEG signal detection device with a depth of 28mm.

[0165] In some embodiments, the portable physiological parameter assessment system further includes a shielding portion 105 disposed on the cover portion 100, and at least one side of the shielding portion 105 is connected to a side of the cover portion 100. A magnetic fastener 106 may be provided on the shielding portion 105 to fix the shielding portion 105 to the cover portion 100.

[0166] The shielding portion 105 has a first structural position and a second structural position. In the first structural position, the shielding portion 105 can cover the receiving groove inside the cover portion 100. In the second structural position, the shielding portion 105 avoids the receiving groove inside the cover portion 100, thereby exposing the receiving groove.

[0167] Figure 16 This is a structural diagram of the shielding part 105 in the first structural position, which can be combined with... Figure 15 and Figure 17 Understand the shielding effect of the shielding part 105 on the receiving groove of the physiological parameter detection device. Figure 15 This is a structural diagram showing the shielding part 105 in the second structural position. The dimensions of the shielding part 105 are similar to those of the base part 200 and the cover part 100, as shown below. Figure 18 As shown.

[0168] When the shielding part 105 is in the first structural position, it can make the inner surface of the cover 100 form a complete and unified visual effect. The irregular structure of the shielding groove avoids the exposed receiving groove from damaging the overall appearance of the shell, making the appearance of the equipment in the closed state more concise and neat, while improving the visual texture, professionalism and user experience of the product. In addition, even if the cover 100 and the base part 200 are separated in this state, the shielding part 105 can effectively block the detection equipment in the receiving groove inside the cover, preventing the equipment from falling out of the receiving groove, and playing a protective and anti-detachment role.

[0169] The shielding part 105 is connected to the side of the cover part 100 via a hinge shaft and can rotate around the hinge shaft to switch between the first structural position and the second structural position. For example... Figure 17 As shown.

[0170] In some embodiments, the body composition scale 210 has a built-in display screen. The connection between the display screen and the body composition scale is as described above, with the display screen positioned on the side of the body composition scale facing the cover. When the base 200 and the cover 100 are closed, a storage space for the display screen is formed between them, and the display screen can be embedded in this storage space. If the display screen is a foldable display screen, it can be embedded in the storage space in its folded state. Figure 14 and Figure 15 , Figure 15 The recessed portion 104 shown fits into the shape of the display screen in the folded state.

[0171] In some embodiments, structures such as the shell, receiving groove, and shielding part of the cover and base can be used to achieve interference suppression of weak bioelectric signals (electroencephalogram, electrocardiogram, electromyogram), central data processing device, wireless communication, external radiation suppression of the display screen, mutual interference isolation when multiple modules coexist, and meet medical-grade electromagnetic compatibility requirements without increasing volume or compromising portability.

[0172] For example, the shell of the portable case (including the shell of the cover and the shell of the base) can be made of conductive composite material (e.g., injection molded from conductive plastic or conductive glass fiber composite material) to form a continuous conductive shell on the surface. When the cover and base are closed, they form a 360° conductive shielding loop, shielding against external electric field interference. This setup achieves electric field shielding and internal radiation suppression without the need for an additional metal shield, preventing interference from central data processing devices, wireless transmission signals, etc., with microvolt-level signals such as EEG and ECG.

[0173] For example, a conductive buffer layer can be provided on the inner wall of the receiving tank, making each receiving tank an independent shielded cavity. Specifically, ultra-thin conductive cloth or conductive sponge can be embedded in the inner wall of the receiving tank on the inner side of the cover and the base, and the bottom buffer layer can be electrically connected to the conductive shell to form a conductive buffer layer. Each receiving tank forms an independent Faraday cage cavity, eliminating electromagnetic interference between different physiological parameter detection devices. The tank of the body composition scale 210 adopts a double-layer buffer structure, with a conductive shielding layer added between the two layers to block the conduction interference of the scale's drive signal and electrode excitation signal to other detection devices.

[0174] For example, the 210 body composition scale features a suspended positioning protection for the detection electrode area (i.e., an ultra-thin conductive shielding film is installed within the suspended gap to magnetically and electrically isolate the detection electrodes from the main control and power circuits below. When used with an ultra-thin silicone pad, conductive particles are incorporated into the silicone pad, providing both buffering and grounding shielding functions. This design can completely block crosstalk between the body composition scale's BIA excitation signal (tens of kHz) and low-frequency EEG and ECG signals.

[0175] For example, the shielding part 105 can adopt a double-sided structure, with at least one side surface provided with a conductive shielding layer. Specifically, when the shielding part 105 is in the first structural position (covering the receiving groove), the side facing the base (outer side) serves as the aesthetic surface, and the side facing the cover (inner side) serves as the conductive shielding layer, reliably overlapping with the conductive shell of the cover 100. Thus, when the shielding part 105 is in the first structural position: it forms a completely closed shielding cavity with the conductive shell of the cover 100, enclosing all internal detection devices within the shielding space; blocking radio frequency interference (2.4G / 5G / WiFi) from external mobile phones, base stations, home appliances, etc.; and simultaneously suppressing the outward radiation of internal wireless communication, ensuring the purity of bioelectric signal acquisition.

[0176] For example, conductive springs are installed in the pivot and damping structure of the connecting component 300, so that the cover 100 and the base 200 maintain conductive connection at any opening angle from 0° to 180°. This feature ensures that the shielding cavity does not break in the open or closed state, and the electromagnetic shielding remains effective at all times.

[0177] For example, conductive rubber pads are added to the locking components and handle installation locations to ensure that all gaps in the box are electrically sealed when closed, thus suppressing electromagnetic radiation / leakage.

[0178] For example, a conductive shielding layer is provided inside the display screen housing space formed by the closing of the base 200 and the cover 100 to spatially isolate the display screen backlight driver, wireless communication unit, volume composition detection electrode, and other detection devices. This arrangement can prevent high-frequency interference from the display screen from directly coupling to the detection electrode.

[0179] The aforementioned electromagnetic shielding setup utilizes conductive shielding materials composited onto an existing integrated structure to form a fully enclosed, continuous, and modularly isolated electromagnetic shielding system through the shell, receiving slots, shielding parts, and hinge components. Without increasing the volume of the enclosure, compromising portability, or altering the original structure, it achieves the following: effectively suppressing external electromagnetic radiation from the central control, wireless communication, and display drive circuits; blocking interference from external radio frequency signals on weak bioelectrical signals such as EEG, ECG, and EMG; avoiding intermodulation crosstalk between the body composition scale excitation signal and other detection devices; maintaining high-precision detection even in complex electromagnetic environments such as homes and communities; and eliminating the need for a heavy metal shielding cover, thus overcoming the industry bottleneck that "shielding inevitably increases weight and volume."

[0180] In some embodiments, the central data processing device can acquire detection data from various physiological parameter detection devices that can be housed in a receiving tank via a wireless connection.

[0181] In some embodiments, the system further includes: a remote health management platform communicatively connected to the central data processing device, and / or a health management application for a mobile terminal communicatively connected to the remote health management platform and / or the central data processing device to obtain and present the data processing results of the central data processing device.

[0182] In some embodiments, the data output device presents radar charts of functional system assessment data for each bodily function system and / or overall physiological health assessment data, which are calculated based on the assessment data for each bodily function system. Figure 19 This is a schematic diagram of an interface that presents the evaluation results to the user.

[0183] In some embodiments, the central data processing device is configured to perform Figure 20 The operation described above. For example... Figure 20 As shown, the operation includes the following steps S210 to S230.

[0184] S210: Acquire detection data output by a multimodal physiological parameter detection device that establishes a communication connection with a central data processing device; the detection data of each modality of physiological parameter detection device corresponds to at least one bodily functional system.

[0185] S220: According to the matching target data processing flow, process the detection data output by the multimodal physiological parameter detection device to generate functional system evaluation data of at least two body functional systems.

[0186] S230: Based on the matched target data processing flow, generate the user's overall physiological health assessment data according to the assessment data of the at least two functional systems.

[0187] The above-mentioned S210 to S230 address the existing shortcomings in primary health monitoring scenarios such as families and communities, where data from multiple independent portable physiological testing devices are scattered and stored, forming data silos. This leads to users' inability to form a comprehensive and systematic understanding of health and makes it difficult to accurately carry out community health services. By using a central data processing device to uniformly access the detection data of multimodal independent physiological parameter testing devices, the detection data from multi-source heterogeneous physiological data is centrally collected, breaking down data barriers between different devices and platforms. Through a layered processing flow, the multimodal detection data is first transformed into specialized assessment data corresponding to different bodily function systems, and then integrated to generate unified overall physiological health assessment data. This realizes the transformation from isolated single indicators to systematic quantitative health results, providing users with a comprehensive and intuitive understanding of health, supporting precise and systematic health management, and providing standardized health assessment basis for primary health services, thereby improving the accuracy and efficiency of primary health services.

[0188] The various embodiments in this specification are described in a progressive manner. For the same or similar parts between the various embodiments, please refer to each other. The focus of each embodiment is to describe the differences from other embodiments.

[0189] Although this application has been described through embodiments, those skilled in the art will know that this application has many modifications and variations without departing from the spirit of this application, and it is intended that the appended claims cover such modifications and variations without departing from the spirit of this application.

Claims

1. A portable physiological parameter assessment system, characterized in that, include: Portable case, which includes a compartment for storing physiological parameter detection devices; Multiple physiological parameter detection devices can be housed in their respective receiving slots; The physiological parameter detection device is used to detect the user's physiological health data, and the detection data from multiple physiological parameter detection devices correspond to multiple different bodily function systems; A central data processing device is installed in the portable housing; the central data processing device is used to collect the detection data of various physiological parameter detection devices and output the user's physical health assessment data. A data output device is disposed in the portable housing and electrically connected to the central data processing device; the data output device includes a local presentation module and / or an external communication module. The local presentation module is used to present the user's physical health assessment data; the external communication module is used to transmit the user's physical health assessment data to an external presentation terminal. The portable case integrates multiple physiological parameter detection devices corresponding to multiple different bodily function systems with the central data processing device and the data output device, making the portable case a single integrated portable device.

2. The system according to claim 1, characterized in that, Each receiving slot has a first power supply contact on its inner side, and each physiological parameter detection device has a second power supply contact on its outer wall. The inner wall of the receiving slot at the first power supply contact and the outer wall of the device at the second power supply contact are adapted to each other, so that when the physiological parameter detection device is placed in the receiving slot, the positions of the first power supply contact and the second power supply contact match and the electrical connection is naturally achieved. The first power supply contact is electrically connected to the pre-embedded wiring in the portable case.

3. The system according to claim 2, characterized in that, The first power supply contact and the second power supply contact are magnetic contacts.

4. The system according to claim 2, characterized in that, The portable case integrates an energy storage battery, which is electrically connected to the first power supply contact inside each of the receiving slots.

5. The system according to claim 4, characterized in that, The portable housing integrates multiple physiological parameter detection devices, including a body composition scale. The battery that powers the volumetric scale is electrically connected as the energy storage battery to each first power supply contact inside each receiving tank.

6. The system according to claim 4, characterized in that, The portable case is provided with a second charging port on the outside, which is electrically connected to the energy storage battery and is used to charge the energy storage battery.

7. The system according to claim 1, characterized in that, The physiological parameter detection device includes a body composition scale, and at least one of an electroencephalogram (EEG) signal detection device, a heart rate detection device, a grip strength detection device, and a lung function detection device.

8. The system according to claim 1, characterized in that, Each physiological parameter detection device that can be housed in the receiving tank has an independent power supply unit, signal acquisition unit, and data storage unit, and can independently complete the acquisition and local storage of physiological parameters.

9. The system according to claim 1, characterized in that, The physiological parameter detection device includes a device for detecting electroencephalogram (EEG) signals; The electroencephalogram (EEG) signal detection device includes: A first fixing part and a second fixing part are used to set the detection electrode, wherein the first fixing part corresponds to the circumferential direction of the head and the second fixing part corresponds to the midline position of the head; The second fixing part is rotatably fixed to the first fixing part; when the EEG signal detection device is housed in the receiving slot, the second fixing part rotates to overlap with the first fixing part.

10. The system according to claim 9, characterized in that, The electrodes on the EEG signal detection device can be symmetrically distributed in the prefrontal and central regions of the head, and distributed along the midline in the parietal and occipital lobes; correspondingly, the central data processing device can be configured to perform the following operations: Acquire multi-channel EEG signals from the prefrontal, central, parietal, and occipital lobes of the brain detected by an EEG signal detection device; A four-parameter feature set is determined from the multi-channel EEG signal. The four-parameter feature set includes the following four feature parameters: peak α frequency, 1 / f spectral slope, α wave relative power, and θ wave relative power. Based on the four-parameter feature set, a quantitative index value of brain functional state is calculated based on a preset mapping relationship. The quantitative index value of brain functional state is used as the functional system evaluation data of the nervous system. The mapping relationship is determined by training through a sample dataset, and the mapping relationship ensures that when the input four-parameter feature set is the same, a unique quantitative index value of brain functional state is output.

11. The system according to claim 9, characterized in that, The detection electrodes in the electroencephalogram (EEG) signal detection device are adsorption-type conductive electrodes; the adsorption-type conductive electrodes include: An elastic conductive body, wherein the elastic conductive body has a skin contact surface and a device contact surface that are disposed opposite to each other; The device's bonding surface is integrally formed with a microstructure adsorption and fixation layer. The microstructure adsorption and fixation layer enables the device's bonding surface to be detachably fixed to the surface of the bioelectric signal acquisition device in a surface contact form through physical adsorption, forming a conductive contact area at the bonding interface. The elastic conductive body has an integrally formed through-type continuous conductive structure. One end of the through-type continuous conductive structure extends directly to the outer surface of the skin contact surface to form a signal acquisition end, and the other end extends directly to the bonding interface of the microstructure adsorption and fixation layer of the device bonding surface to form a signal output end that is directly connected to the bioelectric signal acquisition device, thus constructing a continuous bioelectric signal transmission path from the skin contact surface to the device bonding surface.

12. The system according to claim 11, characterized in that, The skin contact surface is provided with a conductive microneedle structure array, which is electrically connected to the through-type continuous conductive structure for passing through hair to contact the scalp.

13. The system according to claim 11, characterized in that, The elastic modulus of the elastic conductive body varies in a gradient along the direction from the skin contact surface to the device contact surface; The elastic modulus of the skin contact area is lower than that of the device bonding area, so that the skin contact area conforms to the microstructure of the skin, while the device bonding area maintains stable surface contact with the surface of the bioelectric signal acquisition device.

14. The system according to claim 1, characterized in that, The physiological parameter detection device includes a body composition scale; the body composition scale includes: The scale body is equipped with a weighing module and a body composition detection module. The display module includes a display screen and a wireless communication unit. A connecting mechanism having a first state and a second state; in the first state, the connecting mechanism maintains a mechanical connection between the display module and the scale body, and allows the display module to rotate relative to the scale body and hover within a range of rotation; in the second state, the connecting mechanism allows the display module to be mechanically separated from the scale body. When the display module is mechanically separated from the scale body, the display module establishes a communication connection with the scale body through the wireless communication unit.

15. The system according to claim 1, characterized in that, The portable housing integrates multiple physiological parameter detection devices, including a body composition scale. The portable housing includes a cover and a base that can be opened and closed relative to each other. The body composition scale is embedded in the base. When the cover is opened relative to the base, the detection surface of the body composition scale is exposed for user testing. The cover and the base are connected by a connecting component.

16. The system according to claim 15, characterized in that, Also includes: A shielding portion is disposed on the cover portion, and at least one side of the shielding portion is connected to a side of the cover portion; The shielding part has a first structural position and a second structural position; when in the first structural position, the shielding part can cover the receiving groove inside the cover; when in the second structural position, the shielding part avoids the receiving groove inside the cover, thereby exposing the receiving groove.

17. The system according to claim 16, characterized in that, The shielding part is connected to the side of the cover part via a hinge shaft, and can rotate around the hinge shaft to switch between the first structural position and the second structural position.

18. The system according to claim 15, characterized in that, A locking assembly is provided on the second side opposite to and / or adjacent to the first side of the portable case. The locking assembly is used to restrict the cover and the base from rotating about the pivot of the connecting assembly when closed.

19. The system according to claim 15, characterized in that, The shell of the cover and the base is made of conductive composite material, which forms a conductive shielding closed loop when closed. And / or, The inner wall of the receiving slot is provided with a conductive buffer layer, so that each receiving slot forms an independent shielded cavity; And / or, The connecting component is equipped with a conductive spring, which ensures that the cover and the base maintain continuous shielding in any open or closed state.

20. The system according to claim 16, characterized in that, At least one side of the shielding part is provided with a conductive shielding layer; When in the first structural position, the shielding part and the cover part form a complete shielding space.

21. The system according to claim 1, characterized in that, The central data processing device acquires the detection data of each physiological parameter detection device that can be stored in the container through a wireless connection.

22. The system according to claim 1, characterized in that, The system also includes: The remote health management platform can communicate with the central data processing device. And / or, A health management application for a mobile terminal communicates with the remote health management platform and / or the central data processing device to obtain and present the data processing results of the central data processing device.

23. The system according to claim 1, characterized in that, The data output device presents radar charts of functional system assessment data for each body function system and / or overall physiological health assessment data, which are calculated based on the assessment data for each body function system.

24. The system according to claim 1, characterized in that, The central data processing device is configured to perform the following methods: Acquire detection data output by a multimodal physiological parameter detection device that establishes a communication connection with a central data processing device; the physiological parameter detection device is an independently operating physical detection device, and the detection data of each modality of the physiological parameter detection device corresponds to at least one bodily functional system; According to the matching target data processing flow, the detection data output by the multimodal physiological parameter detection device is processed to generate functional system evaluation data of at least two body functional systems. Based on the matched target data processing flow, the user's overall physiological health assessment data is generated based on the assessment data of the at least two functional systems.

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