Physiological signal monitoring device

Abstract

The embodiment of the invention provides a physiological signal monitoring device. The physiological signal monitoring device comprises a wearable body. The wearable body comprises an electrode configured to be in contact with human skin to collect human physiological signals, and the electrode is formed by printing conductive silica gel ink on a substrate; and the base body is configured to bear the electrode and fix the electrode on a target body part of a human body.

Description

TECHNICAL FIELD

[0001] The present application relates to the field of signal monitoring, in particular to a physiological signal monitoring device. BACKGROUND

[0002] The heart rate strap as a physiological signal monitoring device can be provided with two electrocardio electrodes, and the electrocardio signal is calculated based on the potential difference at the positions of the two electrocardio electrodes. However, in the heart rate strap product, the electrocardio electrodes for collecting the electrocardio signal are usually metal electrodes (for example, silver patch electrodes), which have poor corrosion resistance and tolerance, resulting in short product service life.

[0003] Therefore, it is necessary to provide a physiological signal monitoring device to improve the tolerance of the electrodes on the heart rate strap and prolong the service life thereof. SUMMARY

[0004] The physiological signal monitoring device provided by the embodiments of the present application includes a wearable body, which includes an electrode configured to be in contact with the skin of a human body to collect a physiological signal of the human body, the electrode being formed by printing conductive silicone ink on a substrate, and a base configured to carry the electrode and fix the electrode to a target body part of the human body. Since the conductive silicone ink has good chemical stability, the electrode formed by printing the conductive silicone ink on the substrate has strong corrosion resistance and a longer service life than the traditional metal electrode. Meanwhile, the preparation process of the conductive silicone ink can make the conductive particles more uniformly dispersed, so that the electrode has better conductivity.

[0005] In some embodiments, the substrate of the electrode is stacked on the surface of the base close to the skin of the human body. The substrate is stacked on the inner surface of the base, and the conductive silicone ink is printed on the surface of the substrate away from the base to form the electrode, so that the electrode can be attached to the skin of the human body to accurately measure the physiological signal of the human body.

[0006] In some embodiments, the substrate of the electrode is connected to the base by adhesion. The substrate of the electrode is connected to the base by adhesion, so that the electrode and the base can be separately processed and produced, and then adhesion is performed after the production of each is completed, thereby improving the production efficiency.

[0007] In some embodiments, the substrate of the electrode is connected to the base by adhesion. The substrate of the electrode is connected to the base by adhesion, so that the electrode and the base can be separately processed and produced, and then adhesion is performed after the production of each is completed, thereby improving the production efficiency.

[0008] In some embodiments, the base and the substrate are integrally knitted from one or more yarns. The integrally knitted base and substrate can improve the stability of the connection between the base and the substrate.

[0009] In some embodiments, the wearable body further includes a waterproof layer, through which at least a portion of the electrodes are connected to the substrate. By providing the waterproof layer, abnormal conductivity between the two electrodes due to liquid immersion can be prevented.

[0010] In some embodiments, the waterproof layer includes a first waterproof membrane, which is stacked on the surface of the substrate close to human skin, and its two sides are respectively bonded to the substrate and the electrode. By providing the first waterproof membrane, the electrode can be waterproofed, preventing abnormal conductivity between the two electrodes due to wetting.

[0011] In some embodiments, the waterproof layer further includes a second waterproof membrane, which is stacked on the side of the first waterproof membrane closest to the human skin, and is bonded to at least a portion of the outer periphery of the electrode. By providing the second waterproof membrane, abnormal conductivity between the two electrodes due to wetting can be further prevented.

[0012] In some embodiments, the waterproof layer comprises waterproof insulating yarn, and the substrate comprises elastic yarn; the waterproof layer and the substrate are integrally woven together. This integral weaving of the substrate and waterproof layer simplifies the manufacturing process and shortens the process time, thus facilitating the mass production of physiological signal monitoring devices. Furthermore, it improves the consistency of the physiological signal monitoring device fabrication, thereby enhancing the reliability of the device and the quality of the acquired signals.

[0013] In some embodiments, a waterproof layer is stacked on the surface of the substrate close to human skin, and the electrode substrate is located on the side of the waterproof layer away from the substrate. The substrate, waterproof layer, and electrode substrate are stacked sequentially, and the waterproof layer can prevent liquid on the substrate from spreading to the electrode, thereby achieving electrode waterproofing.

[0014] In some embodiments, the waterproof layer and the substrate are woven together in a parallel manner, with the substrate connected to the outer periphery of the waterproof layer, and the electrode substrate located on the surface of the waterproof layer close to the human skin. Weaving the waterproof layer and the substrate in a parallel manner simplifies the process and shortens the process time; it also reduces the thickness of the wearable body and improves flexibility.

[0015] In some embodiments, the electrode substrate comprises insulating yarn, and the substrate and waterproof layer are integrally woven together. This integral weaving of the substrate and waterproof layer simplifies the process and shortens the process time.

[0016] In some embodiments, the substrate, waterproofing layer, and base material are woven together in a parallel manner, with the waterproofing layer isolating the substrate from the base material. This parallel weaving of the substrate, waterproofing layer, and base material further simplifies the process and shortens the process time.

[0017] In some embodiments, the electrode further includes a substrate layer, at least partially located between the waterproof layer and a portion of the substrate. By providing the substrate layer, the surface of a portion of the electrode can be flush with or even protrude from the inner surface of the substrate, ensuring that the electrode can continuously contact the human body when the wearable device is worn on the user's body surface, thereby ensuring the quality of the physiological signals measured by the electrode.

[0018] In some embodiments, the electrodes include a first electrode and a second electrode, which are configured to measure electrocardiogram (ECG) signals. The first and second electrodes are located on opposite sides of the midsagittal plane of the human body. By positioning the two electrodes on opposite sides of the midsagittal plane, the quality of the acquired ECG signals can be effectively improved, which is beneficial for increasing the signal-to-noise ratio of the ECG signals.

[0019] In some embodiments, the electrodes include a first electrode and a second electrode, which are configured to acquire electromyographic signals from the same muscle. The first and second electrodes are arranged at intervals along the direction of the muscle fibers. In this configuration, the first and second electrodes can acquire the potential of the skin surface at their respective locations, and the potential difference between the acquired potentials is used to reflect the electromyographic signals of the muscle, thereby improving the accuracy of the acquired electromyographic signals.

[0020] In some embodiments, two metal buckles are fixedly disposed on the substrate. One of the metal buckles is electrically connected to a first electrode, and the other is electrically connected to a second electrode. The two metal buckles enable data transmission between the first and second electrodes and the processing circuit. The processing circuit is detachably connected to the two metal buckles via magnetic attraction. In this configuration, the processing circuit can acquire electrical signals (e.g., electromyographic and electrocardiographic signals) collected by the first and second electrodes through the two metal buckles, and determine the wearer's physiological signals based on these electrical signals.

[0021] In some embodiments, the wearable body further includes a conductive layer located between the metal buckle and the electrode, the metal buckle being electrically connected to the electrode through the conductive layer. By providing a conductive layer between the metal buckle and the electrode, the stability of the electrical connection between the metal buckle and the electrode can be improved.

[0022] In some embodiments, the substrate is roughened. Roughening the substrate can make the wearer fit the skin more comfortably.

[0023] In some embodiments, the conductivity of the electrodes is in the range of 0.1 S / cm to 0.3 S / cm. By setting the conductivity range of the electrodes, the wearable device can accurately and effectively acquire the user's physiological signals. Attached Figure Description

[0024] This application will be further described by way of exemplary embodiments, which will be described in detail with reference to the accompanying drawings. These embodiments are not limiting; in these embodiments, the same reference numerals denote the same structures, wherein:

[0025] Figure 1 These are schematic diagrams illustrating application scenarios of the physiological signal monitoring device according to some embodiments of this specification;

[0026] Figure 2A This is a structural diagram of the inner surface of a physiological signal monitoring device according to some embodiments of this specification;

[0027] Figure 2B This is a structural diagram of the outer surface of a physiological signal monitoring device according to some embodiments of this specification;

[0028] Figure 3 This is a front view of a physiological signal monitoring device shown in some embodiments of this specification;

[0029] Figure 4 This is a front view of a physiological signal monitoring device according to other embodiments shown in this specification;

[0030] Figure 5 This is a front view of a physiological signal monitoring device according to other embodiments shown in this specification;

[0031] Figure 6 This is a structural diagram of the inner surface of a physiological signal monitoring device according to other embodiments of this specification;

[0032] Figure 7 This is a front view of a physiological signal monitoring device according to other embodiments shown in this specification;

[0033] Figure 8 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification;

[0034] Figure 9 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification;

[0035] Figure 10 This is another structural diagram of the inner surface of the physiological signal monitoring device shown in other embodiments of this specification;

[0036] Figure 11 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification;

[0037] Figure 12 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification;

[0038] Figure 13 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification;

[0039] Figure 14 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification;

[0040] Figure 15 This is a schematic diagram showing the location of the electrodes on the human body according to some embodiments of this specification;

[0041] Figure 16 This is another front view of the physiological signal monitoring device shown in other embodiments of this specification. Detailed Implementation

[0042] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are merely some examples or embodiments of this application. For those skilled in the art, these drawings can be applied to other similar scenarios without creative effort. Unless obvious from the context or otherwise specified, the same reference numerals in the drawings represent the same structures or operations.

[0043] It should be understood that the terms “system,” “device,” “unit,” and / or “module” used herein are one way to distinguish different components, elements, parts, sections, or assemblies at different levels. However, if other terms can achieve the same purpose, they may be replaced by other expressions.

[0044] As indicated in this application and claims, unless the context clearly indicates otherwise, the words "a," "an," "an," and / or "the" do not specifically refer to the singular and may also include the plural. Generally speaking, the terms "comprising" and "including" only indicate the inclusion of explicitly identified steps and elements, which do not constitute an exclusive list, and the method or apparatus may also include other steps or elements.

[0045] In the description of this specification, it should be understood that the terms "first," "second," "third," "fourth," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Therefore, a feature defined as "first," "second," "third," or "fourth" may explicitly or implicitly include at least one of that feature. In the description of this specification, "a plurality of" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0046] In this specification, unless otherwise expressly specified and limited, the terms "connection," "fixed," etc., should be interpreted broadly. For example, the term "connection" can refer to a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium; it can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this specification according to the specific circumstances.

[0047] Figure 1 These are schematic diagrams illustrating application scenarios of the physiological signal monitoring device according to some embodiments of this specification. For example... Figure 1 As shown, in some embodiments, application scenario 100 of the physiological signal monitoring device (hereinafter referred to as application scenario 100) may include terminal device 110, network 120, storage device 130, monitoring object 140, and physiological signal monitoring device 150. In some embodiments, the various components in application scenario 100 (e.g., terminal device 110, storage device 130, physiological signal monitoring device 150) may be connected and / or communicate with each other via network 120 (e.g., wireless connection, wired connection, or a combination thereof).

[0048] Terminal device 110 refers to the device and / or software used by the user related to application scenario 100. Users related to application scenario 100 include, but are not limited to, the monitored object 140, physicians (e.g., clinicians, radiation oncologists), nurses, etc. For example, terminal device 110 can be a device or software that controls physiological signal monitoring device 150. The user issues control commands to physiological signal monitoring device 150 through terminal device 110, thereby controlling physiological signal monitoring device 150 to collect physiological signals from monitored object 140. For example, terminal device 110 can send user-input control commands to physiological signal monitoring device 150 via network 120 to control physiological signal monitoring device 150 to collect physiological signals from monitored object 140. In some embodiments, terminal device 110 can obtain physiological signals from monitored object 140 collected by physiological signal monitoring device 150 through network 120. In some embodiments, terminal device 110 can be one or any combination of mobile devices, tablet computers, laptop computers, desktop computers, and other devices with input and / or output functions.

[0049] Physiological signals refer to bioelectrical signals (e.g., electrocardiogram signals, electromyogram signals, etc.) of an object (e.g., monitoring object 140) acquired by a signal acquisition device (e.g., physiological signal monitoring device 150). Physiological signals can be a mixture of noise signals (e.g., motion artifact signals, electrostatic signals, etc.) and pure physiological signals. Pure physiological signals refer to the true physiological signals of the object (e.g., monitoring object 140) obtained after filtering out noise signals.

[0050] Network 120 can connect various components of application scenario 100 (e.g., terminal device 110, storage device 130, physiological signal monitoring device 150) and / or connect application scenario 100 with external resources. Network 120 enables communication between the various components of application scenario 100 and with other parts outside application scenario 100, facilitating the exchange of data and / or information. For example, terminal device 110 can acquire physiological signals of monitoring object 140 collected by physiological signal monitoring device 150 through network 120. As another example, storage device 130 can acquire and store physiological signal data of monitoring object 140 collected by physiological signal monitoring device 150 through network 120.

[0051] In some embodiments, network 120 can be any form of wired or wireless network, or any combination thereof. By way of example only, network 120 may include cable networks, wired networks, fiber optic networks, telecommunications networks, internal networks, the Internet, local area networks (LANs), wide area networks (WANs), wireless local area networks (WLANs), metropolitan area networks (MANs), public switch telephone networks (PSTNs), Bluetooth networks, ZigBee networks, near field communication (NFC) networks, etc., or any combination thereof. In some embodiments, network 120 may include at least one network access point, through which at least one component of application scenario 100 can connect to network 120 to exchange data and / or information. For example, data such as collected physiological signals can be transmitted through network 120.

[0052] Storage device 130 can store data, instructions, and / or any other information. In some embodiments, storage device 130 can store data obtained from physiological signal monitoring device 150 and / or terminal device 110. For example, storage device 130 can store physiological signals collected by physiological signal monitoring device 150. In some embodiments, storage device 130 may include mass storage, removable storage, volatile read-write storage, read-only storage (ROM), etc., or any combination thereof. Exemplary mass storage may include disks, optical disks, solid-state drives, etc. In some embodiments, storage device 130 can be implemented on a cloud platform. By way of example only, the cloud platform may include private cloud, public cloud, hybrid cloud, community cloud, distributed cloud, internal cloud, multi-layer cloud, etc., or any combination thereof.

[0053] In some embodiments, storage device 130 may be connected to network 120 to communicate with at least one other component in application scenario 100. At least one component in application scenario 100 may access data, instructions, or other information stored in storage device 130 via network 120. In some embodiments, storage device 130 may be directly connected to or communicate with one or more components in application scenario 100 (e.g., physiological signal monitoring device 150, terminal device 110). In some embodiments, storage device 130 may be part of physiological signal monitoring device 150 and / or terminal device 110.

[0054] The monitoring object 140 refers to the monitoring object of the physiological signal monitoring device 150, such as the user of the physiological signal monitoring device 150 or patients, athletes, experimental personnel, etc. who need to collect physiological signals.

[0055] The physiological signal monitoring device 150 refers to a device for collecting or monitoring physiological signals of the monitored object 140. The physiological signal monitoring device 150 can be fixed to at least one body part of the monitored object 140 (e.g., chest, back, waist, etc.) to collect physiological signals of the monitored object 140. In some embodiments, the physiological signal monitoring device 150 can be used to monitor the physiological signals of the monitored object 140 in a sports setting. For example, in a sports setting, the physiological signal monitoring device 150 can be fixed to the chest of the monitored object 140 to collect the electrocardiogram (ECG) signals of the monitored object 140 during exercise, thereby guiding the monitored object 140 to engage in scientific exercise based on the ECG signals and their changes. As another example, in a sports setting, the physiological signal monitoring device 150 can be fixed to a muscle of the monitored object 140 (e.g., pectoralis major, biceps brachii, etc.) to collect the electromyographic (EMG) signals of that muscle, thereby guiding the monitored object 140 to engage in scientific exercise (e.g., preventing muscle injury during exercise) based on the EMG signals and their changes. In some embodiments, the physiological signal monitoring device can also be used to monitor the physiological signals of the monitored subject 140 in other scenarios (e.g., sleep state, fetal heart rate monitoring of pregnant women, etc.). For example, in a sleep scenario, the physiological signal monitoring device 150 can be fixed to the chest of the monitored subject 140 to collect the electrocardiogram (ECG) signals of the monitored subject 140 during sleep, thereby determining the sleep quality of the monitored subject 140 based on the ECG signals and their changes. As another example, when the monitored subject 140 is a pregnant woman, the physiological signal monitoring device 150 can be used to monitor the fetal heart rate (i.e., fetal heart rate signal) of the pregnant woman, and determine the health status of the fetus based on the fetal heart rate signal and its changes.

[0056] In some embodiments, the physiological signal monitoring device 150 may be a strip-like structure (e.g., a heart rate monitor) including a substrate (e.g., a band that can be fixed to the body) and electrodes. The substrate can be used to fix the physiological signal monitoring device 150 to at least one body part of the monitored subject 140. The electrodes may be arranged on the inner surface of the substrate near the human skin for contact with at least one body part of the monitored subject 140 to collect physiological signals of the monitored subject 140 (e.g., the potential at the electrode location). In some embodiments, the physiological signal monitoring device 150 may be worn directly on at least one body part of the monitored subject 140, or it may be combined with a wearable device to fit on at least one body part of the monitored subject 140; for example, the physiological signal monitoring device 150 may be disposed on the inner surface of clothing.

[0057] In some embodiments, the physiological signal monitoring device 150 may have an independent power supply. The physiological signal monitoring device 150 can transmit the collected data (e.g., physiological signals) to other components (e.g., storage device 130, terminal device 110) via wired or wireless means (e.g., Bluetooth, WiFi, etc.). In some embodiments, one or more components in application scenario 100 may be part of the physiological signal monitoring device 150. For example, the physiological signal monitoring device 150 may include storage device 130, etc. Further description of the physiological signal monitoring device 150 can be found in [link to relevant documentation]. Figures 2A-14 And its related descriptions.

[0058] In some embodiments, application scenario 100 may further include processing circuitry. Figure 1 (Not shown, but can be configured within the physiological signal monitoring device 150 or terminal device 110). The processing circuit can calculate and acquire physiological data based on the electrical signals collected from multiple electrodes. Physiological data refers to data that reflects the bioelectrical characteristics of the monitored object (e.g., monitored object 140) based on physiological signals. For example, when the physiological signal is an electrocardiogram (ECG) signal, the physiological data can be ECG data. In some embodiments, the processing circuit can provide feedback to the monitored object 140 based on changes in physiological signals or physiological data. For example, it can remind the user (e.g., monitored object 140) to adjust the exercise mode or intensity based on the ECG signal or changes in the ECG signal during exercise to conduct scientific exercise. In some embodiments, the processing circuit can generate corresponding reminder information based on changes in physiological signals or physiological data and send it to the terminal device 110. For example, based on changes in physiological signals or physiological data, the terminal device 110 can provide voice prompts, generate vibrations, etc., to remind the user.

[0059] It should be noted that the above description of application scenario 100 is for illustrative purposes only and does not limit the scope of this specification. Those skilled in the art can make various modifications and changes to application scenario 100 under the guidance of this specification. However, these modifications and changes remain within the scope of this specification.

[0060] Figure 2A This is a structural diagram of the inner surface of a physiological signal monitoring device according to some embodiments of this specification; Figure 2B This is a structural diagram of the outer surface of a physiological signal monitoring device according to some embodiments of this specification; Figure 3 This is a front view of a physiological signal monitoring device shown in some embodiments of this specification; Figure 4 This is a front view of a physiological signal monitoring device according to other embodiments shown in this specification; Figure 5 This is a front view of a physiological signal monitoring device according to other embodiments shown in this specification.Figure 3 , Figure 4 and Figure 5 This is a front view of the physiological signal monitoring device when it is placed flat on a horizontal surface (e.g., when the outer or inner surface is parallel to the table / ground). Subsequent front views are similar.

[0061] In some embodiments, the physiological signal monitoring device may include a wearable body. The wearable body refers to the portion of the physiological signal monitoring device worn on a user's (e.g., monitoring object 140) body part (e.g., chest, waist, etc.). In some embodiments, the wearable body may be worn directly on the user's body part; for example, the wearable body may be worn on the user's body via a substrate (e.g., substrate 210 hereinafter referred to as substrate 210). In some embodiments, the wearable body may be combined with a wearable device to be worn on a user's body part; for example, the wearable body may be disposed on the inner surface of clothing, thereby being worn on the user's body.

[0062] In some embodiments, such as Figure 2A As shown, the wearable body 200 includes a base 210 and electrodes 220.

[0063] The substrate 210 is configured to carry the electrode 220, which is then fixed to a target body part of the human body. The target body part refers to the body part from which the physiological signal is to be measured. For example, when the physiological signal monitoring device is used to measure electrocardiogram (ECG) signals, the substrate 210 can fix the electrode 220 to the chest of the human body; in this case, the target body part corresponds to the chest. As another example, when the physiological signal monitoring device is used to measure electromyographic (EMG) signals, the substrate 210 can fix the electrode 220 to the muscle part to be measured (e.g., when measuring the EMG signal of the pectoralis major muscle, the electrode is fixed to the pectoralis major muscle); in this case, the target body part corresponds to the muscle part to be measured. As yet another example, when the physiological signal monitoring device is used to measure fetal heart rate signals, the substrate 210 can fix the electrode 220 to the abdomen of a pregnant woman; in this case, the target body part corresponds to the abdomen.

[0064] In some embodiments, such as Figure 2A As shown, the shape of the substrate 210 can be strip-shaped.

[0065] In some embodiments, such as Figure 2A As shown, the two ends of the base 210 along its length can be respectively provided with connectors 211 and 212. When connectors 211 and 212 are connected (e.g., fastened), the base 210 can surround and fit against the wearing part of the user (e.g., the monitoring object 140) (e.g., surround and fit against the user's chest, waist, etc.). In some embodiments, the connector can be a fastener, such as a button, snap fastener, magnetic clasp, etc.

[0066] In some embodiments, the material of the matrix 210 may include plant fibers (e.g., cotton fibers, hemp fibers, etc.), animal fibers (e.g., wool, etc.), synthetic fibers (e.g., acrylic fibers, polyester fibers, spandex fibers, etc.), modified chemical fibers, etc. For example, the matrix 210 may be woven from yarn made of plant fibers (e.g., cotton yarn).

[0067] In some embodiments, the substrate 210 may include elastic yarn (e.g., cotton yarn, spandex yarn, etc.), that is, the yarn used in the substrate 210 is elastic yarn, and the substrate 210 is woven from elastic yarn.

[0068] In some embodiments, the substrate 210 may be brushed to make the wearable body 200 fit the skin more comfortably.

[0069] Electrode 220 is configured to contact human skin to collect human physiological signals (e.g., electrocardiogram signals, electromyography signals). In some embodiments, such as Figure 2A As shown, electrode 220 includes a first electrode 221 and a second electrode 222. The first electrode 221 and the second electrode 222 are spaced apart along the length direction of the wearable body 200.

[0070] In some embodiments, electrode 220 may include a substrate and a coating. For example Figure 3 As shown, the first electrode 221 includes a substrate 2211 and a coating 2212, and the second electrode 222 includes a substrate 2221 and a coating 2222.

[0071] The substrate is configured to carry the coating. The coating is printed on the surface of the substrate facing away from the base. At this point, the base, substrate, and coating are stacked sequentially along the thickness direction of the wearable body 200. The coating is made of a conductive material used to collect physiological signals. In some embodiments, the substrate can be made of a low-elasticity textile, such as a low-elasticity fabric, woven fabric, etc. By making the substrate a low-elasticity textile, the substrate has better stability, thus facilitating the printing of the coating. In some embodiments, the substrate material can also be the same as or similar to the material of the base 210. For example, the substrate material can include plant fibers (e.g., cotton fibers, hemp fibers, etc.), animal fibers (e.g., wool, etc.), synthetic fibers (e.g., acrylic fibers, polyester, spandex, etc.), modified chemical fibers, etc.

[0072] In some embodiments, the coating may be conductive silicone ink. Electrodes are formed by printing a coating (e.g., conductive silicone ink) onto a substrate. That is, the first electrode 221 is formed by printing conductive silicone ink onto a substrate 2211, and the second electrode 222 is formed by printing conductive silicone ink onto a substrate 2221. In some embodiments, the electrode 220 may not include a substrate; in this case, the electrode 220 is formed by printing a coating directly onto a predetermined location on the surface of the substrate 210 near human skin (the predetermined area on the surface of the substrate 210 that carries the electrode). In some embodiments, the preparation process of the conductive silicone ink may be as follows: first, conductive particles are added to an organic solvent to fully disperse the conductive particles; then, silicone is added, and the silicone forms a network that encapsulates and binds the fully dispersed conductive particles, thereby forming conductive silicone ink. At this point, the conductive silicone ink is in a liquid or fluid state. This conductive silicone ink in this state is printed onto the substrate surface, and a solid electrode is formed after the organic solvent evaporates. The conductive particles here may include metal particles, carbon particles, or any combination thereof. In some embodiments, conductive silicone inks exhibit good chemical stability, resisting a variety of solvents and chemicals; and good biocompatibility, making physiological monitoring devices suitable for medical devices and biosensors. Furthermore, conductive silicone inks also enhance wettability, reducing sweat evaporation.

[0073] In some embodiments, compared to traditional metal electrodes (such as silver electrodes) which are completely exposed to air and susceptible to corrosion, the conductive particles in this case are bound within silicone, reducing contact with air. Therefore, the conductive silicone ink exhibits strong corrosion resistance and a longer service life than traditional metal electrodes. Furthermore, when the conductive particles are carbon particles, their greater stability and chemical inertness contribute to the strong corrosion resistance and extended service life of the conductive silicone ink. In some scenarios, electrodes can also be formed by molding solid conductive silicone, but this method results in thicker electrodes with higher hardness. In contrast, liquefying and then printing the conductive silicone ink onto a substrate allows for a thinner ink layer, resulting in better flexibility and elasticity for the wearable body 200. Moreover, the uniformity of conductive particle dispersion affects the conductivity of the conductive silicone ink. Traditional solid silicone has very high viscosity and poor particle dispersion uniformity, leading to poor conductivity. In contrast, the preparation process of conductive silicone ink allows for more uniform dispersion of conductive particles, resulting in better conductivity.

[0074] In some embodiments, to enable the wearable device 200 to accurately and effectively acquire the user's physiological signals, the conductivity of the electrodes formed by printing conductive silicone ink on the substrate is in the range of 0.1 S / cm to 0.3 S / cm. As an example, to improve the accuracy of the wearable device 200 in acquiring the user's physiological signals, the conductivity of the electrodes formed by printing conductive silicone ink on the substrate is 0.125 S / cm. In some embodiments, to improve the comfort of wearing the wearable device 200, the thickness of the conductive silicone ink printed on the substrate can be in the range of 200 micrometers to 1000 micrometers.

[0075] In some embodiments, electrodes are formed by printing conductive silicone ink onto a substrate, where the conductive silicone ink and the substrate are difficult to separate. Furthermore, the conductive silicone ink penetrates into the substrate and fuses with it after coating, thus giving the conductive silicone ink electrode higher strength.

[0076] In some embodiments, the electrode substrate is stacked on the surface of the substrate 210 near the human skin (i.e., the inner surface of the substrate), and the electrode coating is located on the side of the substrate facing away from the substrate 210. In this case, the substrate 210, the electrode substrate, and the electrode coating are stacked sequentially along the thickness direction of the wearable body 200. For example... Figure 3 As shown, the substrate 2211 of the first electrode 221 is stacked on the inner surface of the substrate 210 (i.e., the surface close to human skin), and the coating 2212 of the first electrode 221 is located on the side of the substrate 2211 facing away from the substrate 210. The substrate 210, the substrate 2211, and the coating 2212 are stacked sequentially along the thickness direction. Similarly, the substrate 2221 of the second electrode 222 is stacked on the inner surface of the substrate 210, and the coating 2222 of the second electrode 222 is located on the side of the substrate 2221 facing away from the substrate 210. The substrate 210, the substrate 2221, and the coating 2222 are stacked sequentially along the thickness direction.

[0077] In some embodiments, the electrode substrates (the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222) can be connected to the substrate 210 by adhesive bonding. For example, the side of the electrode substrate facing the substrate 210 can be provided with adhesive backing, and the substrate is bonded to the substrate 210 by the adhesive backing.

[0078] In some embodiments of this specification, the substrate is stacked on the inner surface of the base, and conductive silicone ink is printed on the surface of the substrate facing away from the base to form an electrode. This allows the electrode to adhere to human skin for accurate measurement of physiological signals. In some embodiments, the electrode substrate and the base are connected by adhesive bonding, allowing the electrode and base to be manufactured separately and then bonded together after each is completed, thereby improving production efficiency.

[0079] In some embodiments, the electrode substrate and the substrate 210 can be connected in a parallel manner. In this case, the electrode substrate is embedded in the substrate 210. In some embodiments, the electrode substrate can be completely embedded in the substrate 210 (i.e., the electrode penetrates the substrate 210 along the thickness direction). In this case, the surface of the substrate facing away from the coating is flush with the outer surface of the substrate 210 (the surface of the substrate 210 facing away from human skin), and the substrate 210 surrounds the outer periphery of the electrode. For example... Figure 4 As shown, the substrates 2211 of the first electrode 221 and 2221 of the second electrode 222 are spaced apart along the length direction, and the substrates 2211 and 2221 are completely embedded in the substrate 210. The surfaces of the substrates 2211 and 2221 facing away from the coating 2212 are flush with the outer surface of the substrate 210. The substrate 210 surrounds the outer periphery of the first electrode 221 and the second electrode 222. The substrate 210, the first electrode 221, and the second electrode 222 are joined side by side along the length direction. In some embodiments, the substrates of the electrodes may also be partially embedded in the substrate 210. For example... Figure 5 As shown, the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222 are partially embedded in the substrate 210. The substrate 210 surrounds the periphery of the substrate 2211 and the surface of the substrate 2211 facing away from the coating 2212, and the substrate 210 surrounds the periphery of the substrate 2221 and the surface of the substrate 2221 facing away from the coating 2222.

[0080] In some embodiments of this specification, by setting the substrate and the base body to be connected in a parallel manner, the overall thickness of the wearable body 200 can be reduced and the flexibility improved.

[0081] In some embodiments, the matrix and the substrate are formed by a mixture or integral weaving of one or more yarns.

[0082] Integrated weaving refers to the process of continuously weaving one or more yarns (e.g., cotton yarn, polyester yarn, etc.) to obtain a complete fabric. For example, the integrated weaving process for the matrix and substrate can be: based on the yarns contained in the matrix and substrate respectively (e.g., the matrix contains cotton yarn, and the substrate contains polyester yarn), according to a predetermined positional relationship between the matrix and substrate (e.g., ... Figure 3 or Figure 4 or Figure 5 (As shown in the positional relationship between the base and substrate), the base and substrate are continuously woven to obtain the shaped base and substrate. During the weaving process, a transition weaving technique (e.g., tuck weaving) is used when transitioning between the base and substrate. Furthermore, after obtaining the woven base and substrate based on the above integrated weaving process, a coating can be printed on the surface of the substrate facing the human skin (e.g., printing conductive silicone ink onto the substrate surface), thereby obtaining a complete wearable body.

[0083] In some embodiments of this specification, integrated weaving can improve the stability of the connection between the substrate and the matrix.

[0084] Figure 6 This is a structural diagram of the inner surface of a physiological signal monitoring device according to other embodiments of this specification; Figure 7 This is a front view of a physiological signal monitoring device according to other embodiments shown in this specification; Figure 8 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification; Figure 9 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification; Figure 10 This is another structural diagram of the inner surface of the physiological signal monitoring device shown in other embodiments of this specification; Figure 11 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification; Figure 12 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification; Figure 13 This is another front view of the physiological signal monitoring device shown in other embodiments according to this specification; Figure 14 This is another front view of the physiological signal monitoring device shown in other embodiments of this specification.

[0085] In some embodiments, the wearable body further includes a waterproof layer, through which at least a portion of the electrodes are connected to the substrate. For example, such as Figure 6 and Figure 7 As shown, the wearable body 200 also includes a waterproof layer 250, and the first electrode 221 and the second electrode 222 are connected to the substrate 210 through the waterproof layer 250.

[0086] When the substrate 210 is immersed in liquid (for example, when the user exercises, sweat soaks into the substrate 210), the substrate 210 will conduct electricity. At this time, in order to prevent abnormal conduction between the first electrode 221 and the second electrode 222 through the substrate 210, the first electrode 221 and the second electrode 222 need to be insulated from the substrate 210. Based on this, the waterproof layer 250 can be made of an insulating waterproof material, such as insulating rubber, silicone, etc.

[0087] In some embodiments, when the wearable body includes a waterproof layer, the electrodes may consist only of a coating (i.e., the electrodes do not include a substrate), which is directly printed onto the surface of the waterproof layer facing away from the substrate. For example, conductive silicone ink can be directly printed onto the portion of the waterproof layer facing away from the substrate. Figure 8As shown, coating 2212 is directly printed on the part of the waterproof layer 250 that is away from the substrate 210, and coating 2212 serves as the first electrode 221. Coating 2222 is directly printed on the part of the waterproof layer 250 that is away from the substrate 210 (coating 2212 and coating 2222 are printed alternately on the surface of the waterproof layer 250 along the length direction), and coating 2222 serves as the second electrode 222.

[0088] In some embodiments, the waterproof layer includes a first waterproof membrane, which is stacked on the surface of the substrate near human skin, and both sides of the first waterproof membrane are bonded to the substrate and the electrode, respectively. For example Figure 9 As shown, the waterproof layer 250 includes a first waterproof membrane 251, which is stacked on the surface of the substrate 210 near human skin. The two sides of the first waterproof membrane 251 are respectively bonded to the substrate 210 and the electrodes (first electrode 221 and second electrode 222). For example, the two surfaces of the first waterproof membrane 251 may be provided with adhesive backing, and the first waterproof membrane 251 is bonded to the substrate 210 and the electrodes (first electrode 221 and second electrode 222) through the adhesive backing.

[0089] The first waterproof membrane 251 is located between the substrate 210 and the electrodes (first electrode 221 and second electrode 222). The first waterproof membrane 251 can block liquid between the substrate 210 and the electrodes, thereby achieving waterproofing of the electrodes and preventing abnormal conduction between the first electrode 221 and the second electrode 222.

[0090] In some embodiments, the waterproof layer further includes a second waterproof membrane, which is stacked on the side of the first waterproof membrane closest to the human skin, and is bonded to at least a portion of the outer peripheral side of the electrode. For example Figure 9 As shown, the waterproof layer 250 also includes a second waterproof membrane 252, which is stacked on the side of the first waterproof membrane 251 closest to the human skin. The second waterproof membrane 252 is bonded to the outer periphery of the electrodes (including electrodes 221 and 222). One surface of the first waterproof membrane 251 faces the human skin, and at least a portion of the first waterproof membrane 251 may come into contact with the human skin. When there is sweat on the skin surface, the sweat will flow onto the first waterproof membrane 251. The sweat on the first waterproof membrane 251 (especially the portion located along the length direction between the first electrode 221 and the second electrode 222) may also cause abnormal communication between the first electrode 221 and the second electrode 222. In this case, by providing the second waterproof membrane 252, which surrounds the outer periphery of the first electrode 221 and the second electrode 222, the two electrodes can be further waterproofed.

[0091] In some embodiments, the waterproof membrane (including a first waterproof membrane and a second waterproof membrane) is made of a waterproof insulating film, such as a rubber film. In some embodiments, preferably, the waterproof membrane is made of polyurethane (PU) film.

[0092] In some embodiments of this specification, by setting a first waterproof membrane 251 and a second waterproof membrane 252, the electrodes can be waterproofed, preventing abnormal conduction between the two electrodes due to wetting; polyurethane membrane is selected as the material of the waterproof layer because polyurethane membrane has a high Young's modulus, which can form a more stable bond with the data interface and reduce noise during signal acquisition.

[0093] In some embodiments, the waterproof layer 250 includes waterproof insulating yarn (e.g., acrylic yarn, spandex yarn, etc.), and the substrate 210 includes elastic yarn (e.g., polyester yarn, nylon yarn, etc.), and the waterproof layer 250 and the substrate 210 are integrally woven together.

[0094] For example, the integrated weaving process of the waterproof layer and the substrate can be: based on the yarns contained in the substrate and the waterproof layer respectively (the substrate contains elastic yarns, and the waterproof layer contains waterproof insulating yarns), according to the positional relationship between the substrate and the waterproof layer (e.g., Figure 6 and Figure 7 The positional relationship between the substrate and the waterproof layer shown, or Figure 10 or Figure 11 (As shown in the diagram, the substrate and waterproof layer are positioned relative to each other.) The substrate and waterproof layer are woven together to obtain the formed substrate and waterproof layer. During the weaving process, a transition weaving technique (e.g., tuck weaving) is used to transition between the substrate and waterproof layer. Further, after obtaining the woven substrate and waterproof layer, the electrode can be fixed to a preset position on the inner surface of the waterproof layer to complete the bonding of the wearable body, including the substrate, electrode, and waterproof layer. Exemplarily, the fixing method can be: sewing the electrode to the surface of the waterproof layer using yarn (e.g., insulating yarn or waterproof insulating yarn, etc.) (e.g., sewing the fabric base of the electrode to the inner surface of the waterproof layer using yarn to achieve the connection between the electrode and the waterproof layer), or using an adhesive to attach the electrode to the surface of the waterproof layer.

[0095] In some embodiments, a waterproof layer is stacked on the surface of the substrate close to human skin, and the electrode substrate is located on the side of the waterproof layer away from the substrate. For example Figure 6 and Figure 7 As shown, the waterproof layer 250 is stacked on the surface of the substrate 210 close to human skin (i.e., the inner surface of the substrate), and the electrode substrates (including the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222) are located on the side of the waterproof layer 250 away from the substrate 210.

[0096] For example, such as Figure 6 and Figure 7 The integrated weaving process of the substrate 210 and the waterproof layer 250 shown may include: weaving the substrate 210 using elastic yarn; and weaving the waterproof layer 250 using waterproof insulating yarn in a predetermined waterproof area (the area where the predetermined waterproof layer is located) on the inner surface of the substrate 210. Further, in a predetermined electrode area (the area on the waterproof layer surface where the predetermined carrier electrode is located) on the inner surface of the waterproof layer 250, low-elasticity yarn can be used to weave the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222 onto the inner surface of the waterproof layer 250; a coating 2212 of the first electrode 221 is printed on the surface of the substrate 2211 facing away from the waterproof layer 250, and a coating 2222 of the second electrode 222 is printed on the surface of the substrate 2221 facing away from the waterproof layer 250, thereby obtaining a complete wearable body.

[0097] In some embodiments, the waterproof layer and the substrate are woven together in a parallel manner, with the substrate connected to the outer periphery of the waterproof layer, and the electrode substrate located on the surface of the waterproof layer close to human skin. For example Figure 10 and Figure 11 As shown, the waterproof layer 250 and the substrate 210 are woven together in a parallel manner (at this time, the waterproof layer 250 penetrates the substrate 210 along the thickness direction). The substrate 210 is connected to the outer periphery of the waterproof layer 250. The electrode substrate (including the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222) is located on the surface of the waterproof layer 250 close to human skin (i.e., the inner surface).

[0098] For example, such as Figure 10 and Figure 11 The integrated weaving process of the substrate 210 and the waterproof layer 250 shown may include: based on the yarns contained in the substrate 210 and the waterproof layer 250 respectively (e.g., the substrate 210 contains elastic yarns, and the waterproof layer 250 contains waterproof insulating yarns), according to... Figure 10 and Figure 11 The positional relationship between the substrate 210 and the waterproof layer 250 is shown. The substrate 210 and the waterproof layer 250 are continuously woven to obtain, as shown... Figure 10 and Figure 11 The substrate 210 and waterproof layer 250 are shown. During the weaving process, a transition weaving technique (e.g., tuck weaving) is used to transition between the substrate 210 and the waterproof layer 250. Furthermore, after the woven substrate 210 and waterproof layer 250 are obtained, electrodes (including a first electrode 221 and a second electrode 222) can be fixed to a preset electrode area on the inner surface of the waterproof layer 250 to complete the bonding of the wearable body 200 to the substrate 210, electrodes, and waterproof layer 250.

[0099] In some embodiments, the electrode substrate includes insulating yarn (e.g., cotton yarn, spandex yarn, etc.), and the substrate and waterproof layer are integrally woven together.

[0100] For example, with Figure 6 and Figure 7 ,or Figure 10 and Figure 11 Taking the structure of the wearable body shown as an example, the integrated weaving process of the electrode substrate (including the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222) and the waterproof layer 250 can be as follows: the waterproof layer 250 is formed by weaving waterproof insulating yarn; in the preset electrode area on the inner surface of the waterproof layer 250, the electrode substrate (including the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222) is woven onto the inner surface of the waterproof layer 250 using low-elasticity yarn. Furthermore, conductive silicone ink can be printed on the surfaces of the woven substrate 2211 and substrate 2221 to form the first electrode 221 and the second electrode 222.

[0101] In some embodiments, the substrate, waterproof layer, and base material are woven together in a parallel manner along the length direction, with the waterproof layer isolating the substrate from the base material. For example Figure 12 As shown, the substrate (including the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222), the waterproof layer 250 and the base 210 are woven together in a parallel manner along the length direction. In the length direction, the waterproof layer 250 isolates the substrate from the base 210.

[0102] For example, such as Figure 12 The integrated weaving process of the substrate (including the substrate 2211 of the first electrode 221 and the substrate 2221 of the second electrode 222), the waterproof layer 250, and the base 210 may include: based on the yarns contained in the substrate, the waterproof layer 250, and the base 210 (e.g., the substrate contains low-elasticity yarns, the waterproof layer 250 contains waterproof insulating yarns, and the base 210 contains elastic yarns), according to Figure 12 The positional relationship between the substrate, waterproof layer 250, and base material 210 is shown. The substrate, waterproof layer 250, and base material 210 are continuously woven together to achieve the desired result. Figure 12 The substrate, base 210, and waterproof layer 250 shown are described. During the weaving process, a transition weaving technique (e.g., tuck weaving) is used to transition between the base 210 and the waterproof layer 250, and between the waterproof layer 250 and the substrate. Furthermore, after obtaining the woven substrate, base 210, and waterproof layer 250, conductive silicone ink can be printed on the substrate to obtain a complete wearable body 200.

[0103] In some embodiments, the electrode further includes a substrate layer, at least partially located between the waterproof layer and a portion of the substrate. For example...Figure 13 As shown, the first electrode 221 includes a substrate layer 2213, and the second electrode 222 includes a substrate layer 2223; at least a portion of the substrate layer 2213 is located between the waterproof layer 250 and the substrate 2211, and at least a portion of the substrate layer 2223 is located between the waterproof layer 250 and the substrate 2221.

[0104] In some embodiments, such as Figure 14 As shown, when the waterproof layer 250 includes a first waterproof membrane 251 and a second waterproof membrane 252, the substrate layer 2213 is located between the first waterproof membrane 251 and a portion of the substrate 2211, and the substrate layer 2223 is located between the first waterproof membrane 251 and a portion of the substrate 2221. It is understood that the surface of the substrate that connects to the first waterproof membrane 251 is provided with adhesive, and the substrate is bonded to the first waterproof membrane 251 through the adhesive.

[0105] In some embodiments, the material of the substrate may be different from that of the base. For example, the base may be made of a woven fabric with low elasticity, while the substrate may be made of cotton yarn with high elasticity.

[0106] In some embodiments, the substrate layer may be made of the same material as the base. For example, both the base and the substrate layer may be made of woven fabric.

[0107] In some embodiments, when the electrode includes a substrate layer, the electrode, waterproof layer, and substrate can be integrally woven together. For example, using... Figure 13 Taking the structure of the wearable body shown as an example, the integrated weaving process of the electrodes, substrate, and waterproof layer can be as follows: A substrate 210 is formed by weaving elastic yarn; a waterproof layer 250 is formed by weaving waterproof insulating yarn in a predetermined waterproof area on the inner surface of the substrate 210; within the predetermined electrode area of ​​the waterproof layer 250, based on the yarns contained in the base (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222) and the substrate layer (including the substrate layer 2213 of the first electrode 221 and the substrate layer 2223 of the second electrode 222), the base and substrate are continuously woven to obtain the desired structure. Figure 13 The combination of the substrate, waterproof layer, and base material is shown. During the weaving process, a transition weaving technique (e.g., tuck weaving) is used to transition between the substrate and the base layer. Furthermore, a coating is printed on the surface of the substrate (conductive silicone ink is printed on the surfaces of substrates 2211 and 2221), thereby completing the bonding of the wearable body 200 to the base material 210, electrode 220, and waterproof layer 250.

[0108] In some embodiments of this specification, the surface of the electrode facing away from the waterproof layer may be recessed inward relative to the inner surface of the wearable body, causing the electrode to be unable to maintain continuous contact with the human skin, thereby affecting the measurement of physiological signals. Therefore, by providing a substrate layer, a portion of the electrode surface can be flush with or even protrude from the inner surface of the substrate, ensuring that the electrodes can maintain continuous contact with the human body when the wearable body is worn on the user's skin, thus guaranteeing the quality of the physiological signals measured by the electrodes.

[0109] Unlike the above-described method of forming electrodes by printing conductive silicone ink on a substrate, in some embodiments, the electrodes can also adopt other structural forms. In some embodiments, the electrodes can be fabricated using metallic materials, such as silver patches. The silver patch electrodes are adhered to the substrate (or waterproof layer) and come into contact with human skin to collect human physiological signals. To prevent corrosion and oxidation of the silver patch electrodes, conductive silicone ink can be coated on the surface of the silver patch electrodes near the human skin. In this case, the conductive silicone ink can both conduct electricity and protect the silver patch electrodes (e.g., prevent corrosion and oxidation).

[0110] Figure 15 This is a schematic diagram showing the location of the electrodes on the human body according to some embodiments of this specification.

[0111] In some embodiments, the first and second electrodes are configured to measure electrocardiogram (ECG) signals, and the first and second electrodes are located on opposite sides of the midsagittal plane of the human body. For example, with Figure 2A Taking electrode 220 as an example, the first electrode 221 and the second electrode 222 can be located on both sides of the midsagittal plane of the human body (for example, as shown). Figure 15 As shown, the first electrode 221 is located on the left side of the median sagittal plane 240 of the human body, and the second electrode 222 is located on the right side of the median sagittal plane 240 of the human body. The median sagittal plane of the human body refers to the sagittal plane located in the middle of the human body. This plane passes through the midline of the navel and vertically divides the body into two symmetrical parts.

[0112] In some embodiments, preferably, the positions of the two electrodes against the human body can be symmetrical about the midsagittal plane of the human body, that is, the distances between the two electrodes and the midsagittal plane of the human body are equal. For example, with... Figure 2A Taking the two electrodes shown as an example, the first electrode 221 is located on the body surface directly opposite the left iliac bone, and the second electrode 222 is located on the body surface directly opposite the right iliac bone.

[0113] In some embodiments of this specification, by placing the two electrodes on both sides of the midsagittal plane, the quality of the acquired electrocardiogram (ECG) signal can be effectively improved, which is beneficial to improving the signal-to-noise ratio of the ECG signal; by further placing the two electrodes at symmetrical positions on both sides of the midsagittal plane, the quality of the acquired ECG signal can be further improved.

[0114] In some embodiments, the first electrode 221 and the second electrode 222 are configured to acquire electromyographic (EMG) signals from the same muscle, and are spaced apart along the direction of the muscle fibers. The first electrode 221 and the second electrode 222 can acquire the electrical potential of the skin surface at their respective locations, and the potential difference between the acquired potentials can be used to reflect the EMG signal of the muscle. In some embodiments, the first electrode 221 and the second electrode 222 can be used to acquire the EMG signal of a target muscle of a user. The target muscle can refer to a single muscle or a group of muscles (e.g., the quadriceps femoris muscle group including the rectus femoris, vastus lateralis, vastus medialis, and vastus intermedius). For example, the first electrode 221 and the second electrode 222 can be spaced apart along the direction of the muscle fibers of the target muscle and extend in a direction perpendicular to the direction of the muscle fibers, thereby acquiring the electrical potential of the skin surface at their respective locations, and the potential difference between the acquired potentials can be used to reflect the EMG signal of the target muscle. In some embodiments, when the target muscle is a single muscle, since there are multiple other muscles surrounding the target muscle, the electromyographic (EMG) signal collected by electrode 220 may include the EMG signals of the target muscle and other surrounding muscles. Because the target muscle and other surrounding muscles are in the same muscle group, and the EMG signals generated by muscles in the same muscle group are relatively similar, the EMG signal actually collected by electrode 220 is close to the EMG signal of the target muscle, with a small error. That is, the EMG signal actually collected by electrode 220 can characterize the EMG signal of the target muscle. It should be noted that in other embodiments, the proportion of noise (i.e., the EMG signals of other muscles surrounding the target muscle) in the EMG signal collected by electrode 220 can be reduced by designing the shape of electrode 220 and using algorithmic processing, thereby improving the accuracy of the physiological signal monitoring device. As an example, the first electrode 221 and the second electrode 222 can be arranged alternately along the muscle fiber direction of the gastrocnemius muscle and extend respectively along an extension direction perpendicular to the muscle fiber direction. That is, the first electrode 221 and the second electrode 222 can be disposed on the gastrocnemius muscle, arranged at intervals along the user's height direction and extending along an extension direction perpendicular to the user's height direction respectively. The first electrode 221 and the second electrode 222 collect the potential of the skin surface at their respective locations, and the potential difference between the collected potentials can be used to reflect the electromyographic signal of the gastrocnemius muscle.

[0115] In some embodiments, two metal buckles are fixedly disposed on the substrate, one of which is electrically connected to the first electrode and the other of which is electrically connected to the second electrode.

[0116] In some embodiments, the two metal clips can be connected to an external processing circuit, enabling data transmission between the first and second electrodes and the processing circuit (e.g., transmitting acquired physiological signals to the processing circuit). In some embodiments, the processing circuit and the two metal clips can be detachably connected, for example, the processing circuit and the two metal clips can be detachably connected by magnetic attraction.

[0117] For example, such as Figures 2B-14 As shown, two metal clips (metal clip 231 and metal clip 232) are fixedly disposed on the substrate 210, wherein metal clip 231 is electrically connected to the first electrode 221, and metal clip 232 is electrically connected to the second electrode 222. In some embodiments, the metal clips may penetrate the substrate 210 (and at least part of the waterproof layer) along the thickness direction of the substrate 210 to electrically connect with the electrodes. For example Figure 14As shown, the metal buckle 231 penetrates the substrate 210, the first waterproof layer 251, and part of the second waterproof layer 252 along the thickness direction of the substrate 210 to be electrically connected to the first electrode 221; the metal buckle 232 penetrates the substrate 210, the first waterproof layer 251, and part of the second waterproof layer 252 along the thickness direction of the substrate 210 to be electrically connected to the second electrode 222. At this time, the metal buckles 231 and 232 do not protrude from the inner surface of the second waterproof layer 252. With this arrangement, the end of the metal buckle is wrapped in the second waterproof layer 252, which can prevent the metal buckle from contacting the human skin, thereby preventing the metal buckle from scratching the skin, and also improving wearing comfort. In other alternative embodiments, the metal buckle 231 may also penetrate completely through the substrate 210, the first waterproof layer 251, and the second waterproof layer 252 along the thickness direction of the substrate 210 to be electrically connected to the first electrode 221; the metal buckle 232 may also penetrate completely through the substrate 210, the first waterproof layer 251, and the second waterproof layer 252 along the thickness direction of the substrate 210 to be electrically connected to the second electrode 222. In this case, the metal buckles 231 and 232 are flush with or protrude from the inner surface of the second waterproof layer 252. In some embodiments, the metal buckle may be configured as a bent structure (e.g., an L-shaped structure). After penetrating the substrate 210 (and the waterproof layer), the metal buckle bends in the direction of the corresponding electrode to fit against the surface of the electrode facing the human skin, thereby achieving electrical connection between the metal buckle and the electrode. The bent portion of the metal buckle (i.e., the portion of the metal buckle that fits against the surface of the electrode facing the human skin) may be referred to as the buckle foot. In some embodiments, portions of the metal buckles 231 and 232 located on the outer surface of the substrate 210 may be connected to an external processing circuit (not shown in the figure). The processing circuit can acquire electrical signals (e.g., electromyographic signals and electrocardiogram signals) collected by the first electrode 221 and the second electrode 222 through the metal buckles 231 and 232, and determine the physiological signals (e.g., electrocardiogram signals) and / or physiological data (e.g., electrocardiogram) of the wearer (e.g., monitoring subject 140) based on the aforementioned electrical signals.

[0118] Figure 16 This is another front view of a physiological signal monitoring device according to other embodiments of this specification. In some embodiments, the wearable body may further include a conductive layer located between a metal clasp and an electrode, the metal clasp being electrically connected to the electrode through the conductive layer. For example, as... Figure 16As shown, the wearable body 200 may include conductive layers (conductive layer 261 and conductive layer 262), wherein conductive layer 261 is located between metal buckle 231 and first electrode 221, and metal buckle 231 is electrically connected to first electrode 221 through conductive layer 261; conductive layer 262 is located between metal buckle 232 and second electrode 222, and metal buckle 232 is electrically connected to second electrode 222 through conductive layer 262. In some embodiments, along the thickness direction of substrate 210, conductive layer 261 may be located between buckle pin of metal buckle 231 and coating 2212 of first electrode 221; conductive layer 262 may be located between buckle pin of metal buckle 232 and coating 2222 of second electrode 222. In some embodiments, conductive layer may include conductive yarn (e.g., silver yarn), and conductive layer is formed by weaving conductive yarn. The conductive layer is bonded to the electrode and / or metal buckle.

[0119] By placing a conductive layer between the metal buckle and the electrode, the stability of the electrical connection between the metal buckle and the electrode can be improved.

[0120] The basic concepts have been described above. Obviously, for those skilled in the art, the detailed disclosure above is merely illustrative and does not constitute a limitation of this application. Although not explicitly stated herein, those skilled in the art may make various modifications, improvements, and corrections to this application. Such modifications, improvements, and corrections are suggested in this application, and therefore remain within the spirit and scope of the exemplary embodiments of this application.

Claims

1. A physiological signal monitoring device, comprising: Wearable device, including: Electrodes, configured to contact human skin to collect human physiological signals, are formed by printing conductive silicone ink onto a substrate; and A substrate is configured to carry the electrode and fix the electrode to a target body part of the human body.

2. The physiological signal monitoring device according to claim 1, wherein, The electrode substrate is stacked on the surface of the substrate near human skin.

3. The physiological signal monitoring device according to claim 2, wherein, The electrode substrate is connected to the matrix by adhesive bonding.

4. The physiological signal monitoring device according to claim 1, wherein, The electrode substrate is connected to the matrix in a parallel manner.

5. The physiological signal monitoring device according to claim 2 or 4, wherein, The matrix and the substrate are integrally woven from one or more yarns.

6. The physiological signal monitoring device according to claim 1, wherein, The wearable body also includes a waterproof layer, through which at least a portion of the electrodes are connected to the substrate.

7. The physiological signal monitoring device according to claim 6, wherein, The waterproof layer includes a first waterproof membrane, which is stacked on the surface of the substrate near human skin, and the two sides of the first waterproof membrane are respectively bonded to the substrate and the electrode.

8. The physiological signal monitoring device according to claim 7, wherein, The waterproof layer further includes a second waterproof membrane, which is stacked on the side of the first waterproof membrane closest to the human skin, and the second waterproof membrane is bonded to at least a portion of the outer peripheral side of the electrode.

9. The physiological signal monitoring device according to claim 6, wherein, The waterproof layer includes waterproof insulating yarn, the substrate includes elastic yarn, and the waterproof layer and the substrate are integrally woven together.

10. The physiological signal monitoring device according to claim 9, wherein, The waterproof layer is stacked on the surface of the substrate close to human skin, and the base of the electrode is located on the side of the waterproof layer away from the substrate.

11. The physiological signal monitoring device according to claim 9, wherein, The waterproof layer and the substrate are woven together in a parallel manner, the substrate is connected to the outer periphery of the waterproof layer, and the base of the electrode is located on the surface of the waterproof layer close to human skin.

12. The physiological signal monitoring device according to claim 10 or 11, wherein, The electrode's substrate comprises insulating yarn, and the substrate and the waterproof layer are integrally woven together.

13. The physiological signal monitoring device according to claim 9, wherein, The substrate, the waterproof layer, and the base material are woven together in a parallel manner, and the waterproof layer isolates the substrate from the base material.

14. The physiological signal monitoring device according to claim 6, wherein, The electrode further includes a substrate layer, at least a portion of which is located between the waterproof layer and a portion of the substrate.

15. The physiological signal monitoring device according to claim 1, wherein, The electrodes include a first electrode and a second electrode, which are configured to measure electrocardiogram signals and are located on opposite sides of the midsagittal plane of the human body.

16. The physiological signal monitoring device according to claim 1, wherein, The electrode includes a first electrode and a second electrode, which are configured to acquire electromyographic signals from the same muscle, and are spaced apart along the direction of the muscle fibers.

17. The physiological signal monitoring device according to claim 15 or 16, wherein, Two metal buckles are fixedly disposed on the substrate. One of the two metal buckles is electrically connected to the first electrode, and the other of the two metal buckles is electrically connected to the second electrode. The two metal buckles enable data transmission between the first electrode, the second electrode and the processing circuit. The processing circuit is detachably connected to the two metal buckles by magnetic attraction.

18. The physiological signal monitoring device according to claim 17, wherein, The wearable body also includes a conductive layer, which is located between the metal buckle and the electrode, and the metal buckle is electrically connected to the electrode through the conductive layer.

19. The physiological signal monitoring device according to claim 1, wherein, The substrate is roughened.

20. The physiological signal monitoring device according to claim 1, wherein, The conductivity of the electrode is in the range of 0.1 S / cm to 0.3 S / cm.

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