Physiological signal monitoring device

Abstract

Disclosed is a physiological signal monitoring device (150), comprising a wearable body (200). The wearable body comprises: an electrode (220) configured to be in contact with the skin of a human body so as to acquire a physiological signal of the human body, the electrode being formed by printing conductive silicone ink on substrates (2211, 2221); and a matrix (210) configured to carry the electrode and fix the electrode to a target body part of the human body.

Description

Physiological signal monitoring device 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 between 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, there is a need 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.

[0004] SUMMARY

[0005] The physiological signal monitoring device provided by the embodiments of the present application includes a wearable body, which includes electrodes configured to be in contact with the skin of a human body to collect physiological signals of the human body, and a substrate configured to carry the electrodes and fix the electrodes to a target body part of the human body, wherein the electrodes are formed by printing conductive silicone ink on a base.

[0006] In some embodiments, the base of the electrodes is stacked on the surface of the substrate close to the skin of the human body.

[0007] In some embodiments, the base of the electrodes is connected to the substrate by adhesion.

[0008] In some embodiments, the base of the electrodes is connected to the substrate in a parallel manner.

[0009] In some embodiments, the substrate and the base are integrally knitted by one or more yarns.

[0010] In some embodiments, the wearable body further includes a waterproof layer, and at least part of the electrodes are connected to the substrate through the waterproof layer.

[0011] In some embodiments, the waterproof layer includes a first waterproof film, the first waterproof film is stacked on the surface of the substrate close to the skin of the human body, and the two sides of the first waterproof film are adhesively connected to the substrate and the electrodes, respectively.

[0012] In some embodiments, the waterproof layer further includes a second waterproof film, the second waterproof film is stacked on the side of the first waterproof film close to the skin of the human body, and the second waterproof film is adhesively connected to the outer circumferential side of at least part of the electrodes.

[0013] In some embodiments, the waterproof layer comprises waterproof insulating yarns, the base body comprises elastic yarns, and the waterproof layer and the base body are formed by integrated weaving.

[0014] In some embodiments, the waterproof layer is stacked on the surface of the base body close to the human skin, and the base of the electrode is located on the side of the waterproof layer away from the base body.

[0015] In some embodiments, the waterproof layer and the base body are woven in a side-by-side manner, the base body is connected to the outer circumferential side of the waterproof layer, and the base of the electrode is located on the surface of the waterproof layer close to the human skin.

[0016] In some embodiments, the base of the electrode comprises insulating yarns, and the base and the waterproof layer are formed by integrated weaving.

[0017] In some embodiments, the base, the waterproof layer and the base body are woven in a side-by-side manner, and the waterproof layer insulates the base from the base body.

[0018] In some embodiments, the electrode further comprises a substrate layer, at least part of the substrate layer is located between the waterproof layer and part of the base.

[0019] In some embodiments, the electrode comprises a first electrode and a second electrode, the first electrode and the second electrode are configured to measure electrocardiogram signals, and the first electrode and the second electrode are located on both sides of the median plane of the human body.

[0020] In some embodiments, the electrode comprises a first electrode and a second electrode, the first electrode and the second electrode are configured to collect electromyogram signals of the same muscle, and the first electrode and the second electrode are arranged in a spaced-apart manner along the direction of muscle fibers of the muscle.

[0021] In some embodiments, two metal buckles are fixedly arranged on the base body, one of the two metal buckles is electrically connected to the first electrode, the other of the two metal buckles is electrically connected to the second electrode, the two metal buckles realize data transmission between the first electrode, the second electrode and the processing circuit, and the processing circuit is detachably connected to the two metal buckles by magnetic attraction.

[0022] In some embodiments, the wearable body further comprises a conductive layer, the conductive layer is located between the metal buckle and the electrode, and the metal buckle is electrically connected to the electrode through the conductive layer.

[0023] In some embodiments, the base body is sandblasted.

[0024] In some embodiments, the electrical conductivity of the electrode is in the range of 0.1 S / cm to 0.3 S / cm. BRIEF DESCRIPTION OF DRAWINGS

[0025] The present application will be further described in the way of example embodiments, which will be described in detail with reference to the accompanying drawings. These embodiments are not limiting, in these embodiments, the same reference numbers represent the same structures, wherein:

[0026] Fig. 1 is a schematic diagram of an application scenario of a physiological signal monitoring device according to some embodiments of the present specification;

[0027] Fig. 2A is a structure diagram of an inner surface of a physiological signal monitoring device according to some embodiments of the present specification;

[0028] Fig. 2B is a structure diagram of an outer surface of a physiological signal monitoring device according to some embodiments of the present specification;

[0029] Fig. 3 is a front view of a physiological signal monitoring device according to some embodiments of the present specification;

[0030] Fig. 4 is a front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0031] Fig. 5 is a front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0032] Fig. 6 is a structure diagram of an inner surface of a physiological signal monitoring device according to some other embodiments of the present specification;

[0033] Fig. 7 is a front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0034] Fig. 8 is another front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0035] Fig. 9 is another front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0036] Fig. 10 is another structure diagram of an inner surface of a physiological signal monitoring device according to some other embodiments of the present specification;

[0037] Fig. 11 is another front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0038] Fig. 12 is another front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0039] Fig. 13 is another front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0040] Fig. 14 is another front view of a physiological signal monitoring device according to some other embodiments of the present specification;

[0041] FIG. 15 is a schematic illustration of a human body position with electrodes positioned thereon, according to some embodiments of the present specification;

[0042] FIG. 16 is another front view of a physiological signal monitoring device, according to some other embodiments of the present specification. DETAILED DESCRIPTION

[0043] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following will briefly introduce the drawings needed to be used in the embodiment description. Obviously, the drawings in the following description are only some examples or embodiments of the present application, and for those skilled in the art, the present application can also be applied to other similar scenarios without paying creative labor, according to the drawings. Unless it is clear from the language context or otherwise indicated, the same reference numbers in the drawings represent the same structures or operations.

[0044] It should be understood that the "system", "device", "unit" and / or "module" used herein is a method for distinguishing different components, elements, parts, sections or assemblies at different levels. However, if other words can achieve the same purpose, the words can be replaced by other expressions.

[0045] As shown in the present application and claims, unless the context clearly indicates otherwise, the words "one", "a", "an", and / or "the" do not mean to specify a single number, but also include a plurality. Generally speaking, the terms "include" and "contain" only indicate that the steps and elements explicitly identified are included, and these steps and elements do not constitute an exclusive list, and the method or device can also include other steps or elements.

[0046] In the description of the present specification, it should be understood that the terms "first", "second", "third", "fourth" and the like are only for the purpose of description, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, the features defined with "first", "second", "third", "fourth" can explicitly or implicitly include at least one of the features. In the description of the present specification, the meaning of "a plurality of" is at least two, for example, two, three, etc., unless otherwise specifically limited.

[0047] In the present specification, unless otherwise specifically defined and limited, the terms "connection", "fixing" and the like should be understood broadly. For example, the term "connection" can mean fixed connection, or detachable connection, or integral; can be mechanical connection, or electrical connection; can be direct connection, or indirect connection through intermediate medium; can be internal connection of two elements or interaction relationship between two elements, unless otherwise specifically limited. For those skilled in the art, the specific meaning of the above terms in the present specification can be understood according to the specific circumstances.

[0048] FIG. 1 is a schematic diagram of an application scenario of a physiological signal monitoring apparatus according to some embodiments of the present specification. As shown in FIG. 1, in some embodiments, an application scenario 100 of a physiological signal monitoring apparatus (hereinafter referred to as application scenario 100) can include a terminal device 110, a network 120, a storage device 130, a monitoring object 140, and a physiological signal monitoring apparatus 150. In some embodiments, each component (e.g., terminal device 110, storage device 130, physiological signal monitoring apparatus 150) in application scenario 100 can be connected and / or communicate with each other via network 120 (e.g., wireless connection, wired connection, or a combination thereof).

[0049] The terminal device 110 refers to a device and / or software used by a user related to the application scenario 100. The user related to the application scenario 100 includes but is not limited to the monitoring object 140, a physician (e.g., a clinician, a radiotherapist), a nurse, and the like. For example, the terminal device 110 can be a device or software for controlling the physiological signal monitoring apparatus 150, and the user can issue a control instruction to the physiological signal monitoring apparatus 150 through the terminal device 110, so as to control the physiological signal monitoring apparatus 150 to collect the physiological signal of the monitoring object 140. For example, the terminal device 110 can send the control instruction input by the user to the physiological signal monitoring apparatus 150 through the network 120, so as to control the physiological signal monitoring apparatus 150 to collect the physiological signal of the monitoring object 140. In some embodiments, the terminal device 110 can obtain the physiological signal of the monitoring object 140 collected by the physiological signal monitoring apparatus 150 through the network 120. In some embodiments, the terminal device 110 can be one or any combination of a mobile device, a tablet computer, a laptop computer, a desktop computer, and other devices with input and / or output functions.

[0050] The physiological signal refers to the bioelectric signal (e.g., electrocardiogram signal, electromyogram signal, and the like) of an object (e.g., monitoring object 140) collected based on a signal collection device (e.g., physiological signal monitoring apparatus 150). The physiological signal can be a mixed signal mixed with a noise signal (e.g., motion artifact signal, electrostatic signal, and the like) and a pure physiological signal. The pure physiological signal refers to the true physiological signal of the object (e.g., monitoring object 140) obtained by filtering out the noise signal.

[0051] The network 120 can connect various components of the application scenario 100 (e.g., the terminal device 110, the storage device 130, the physiological signal monitoring apparatus 150) and / or connect the application scenario 100 with external resource parts. The network 120 can enable communication between various components of the application scenario 100 and / or between the application scenario 100 and other parts outside the application scenario 100, and facilitate exchange of data and / or information. For example, the terminal device 110 can obtain physiological signals of the monitoring object 140 collected by the physiological signal monitoring apparatus 150 through the network 120. For another example, the storage device 130 can obtain physiological signal data of the monitoring object 140 collected by the physiological signal monitoring apparatus 150 and store the data through the network 120.

[0052] In some embodiments, the network 120 can be any form of wired or wireless network, or any combination thereof. For example only, the network 120 can include a cable network, a wireline network, a fiber-optic network, a telecommunications network, an intranet, the Internet, a local area network (LAN), a wide area network (WAN), a wireless local area network (WLAN), a metropolitan area network (MAN), a public switched telephone network (PSTN), a Bluetooth network, a ZigBee network, a near-field communication (NFC) network, and / or the like, or any combination thereof. In some embodiments, the network 120 can include at least one network access point through which at least one component of the application scenario 100 can connect to the network 120 to exchange data and / or information. For example, data such as collected physiological signals can be transmitted through the network 120.

[0053] The storage device 130 can store data, instructions, and / or any other information. In some embodiments, the storage device 130 can store data obtained from the physiological signal monitoring apparatus 150 and / or the terminal device 110. For example, the storage device 130 can store physiological signals collected by the physiological signal monitoring apparatus 150. In some embodiments, the storage device 130 can include a mass storage, a removable storage, a volatile read-write memory, a read-only memory (ROM), and / or the like, or any combination thereof. An exemplary mass storage can include a magnetic disk, an optical disk, a solid-state disk, and / or the like. In some embodiments, the storage device 130 can be implemented on a cloud platform. For example only, the cloud platform can include a private cloud, a public cloud, a hybrid cloud, a community cloud, a distributed cloud, an on-premises cloud, a multi-cloud, and / or the like, or any combination thereof.

[0054] In some embodiments, the storage device 130 can be connected to the network 120 to communicate with at least one other component in the application scenario 100. At least one component in the application scenario 100 can access data, instructions or other information stored in the storage device 130 through the network 120. In some embodiments, the storage device 130 can be directly connected or in communication with one or more components in the application scenario 100 (e.g., the physiological signal monitoring apparatus 150, the terminal device 110). In some embodiments, the storage device 130 can be part of the physiological signal monitoring apparatus 150 and / or the terminal device 110.

[0055] The monitoring subject 140 refers to a monitoring subject of the physiological signal monitoring apparatus 150, for example, a user of the physiological signal monitoring apparatus 150 or a patient, an athlete, an experimental subject, etc. who needs to collect physiological signals.

[0056] The physiological signal monitoring apparatus 150 refers to an apparatus for collecting or monitoring physiological signals of the monitoring subject 140. The physiological signal monitoring apparatus 150 can be fixed to at least one body part (e.g., chest, back, waist, etc.) of the monitoring subject 140 to collect physiological signals of the monitoring subject 140. In some embodiments, the physiological signal monitoring apparatus 150 can be used for physiological signal monitoring of the monitoring subject 140 in a sports scenario. For example, in a sports scenario, the physiological signal monitoring apparatus 150 can be fixed to the chest of the monitoring subject 140 to collect electrocardiogram signals of the monitoring subject 140 during exercise, so as to guide the monitoring subject 140 to exercise scientifically according to the electrocardiogram signals and changes in the electrocardiogram signals. For another example, in a sports scenario, the physiological signal monitoring apparatus 150 can be fixed to a position of a muscle (e.g., pectoralis major, biceps, etc.) of the monitoring subject 140 to collect electromyogram signals of the muscle of the monitoring subject 140, so as to guide the monitoring subject 140 to exercise scientifically (e.g., to prevent muscle injury during exercise) according to the electromyogram signals and changes in the electromyogram signals. In some embodiments, the physiological signal monitoring apparatus can also be used for physiological signal monitoring of the monitoring subject 140 in other scenarios (e.g., sleep state, fetal heart monitoring of a pregnant woman, etc.). For example, in a sleep scenario, the physiological signal monitoring apparatus 150 can be fixed to the chest of the monitoring subject 140 to collect electrocardiogram signals of the monitoring subject 140 during sleep, so as to judge the sleep quality of the monitoring subject 140 according to the electrocardiogram signals and changes in the electrocardiogram signals. For another example, when the monitoring subject 140 is a pregnant woman, the physiological signal monitoring apparatus 150 can be used to monitor the fetal heart rate (i.e., fetal heart signals) of the pregnant woman, and to judge the health condition of the fetus according to the fetal heart signals and changes in the fetal heart signals.

[0057] In some embodiments, the physiological signal monitoring device 150 can be a band structure (e.g., a heart rate band for measuring heart rate), including a substrate (e.g., a band that can be wrapped and fixed on 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 monitoring subject 140. The electrodes can be arranged on the inner surface of the substrate close to the human skin, for conforming to at least one body part of the monitoring subject 140 to collect the physiological signal (e.g., the electric potential at the position of the electrodes) of the monitoring subject 140. In some embodiments, the physiological signal monitoring device 150 can be directly worn on at least one body part of the monitoring subject 140, or can be combined with a wearable device to conform to at least one body part of the monitoring subject 140, for example, the physiological signal monitoring device 150 can be arranged on the inner surface of the clothing.

[0058] In some embodiments, the physiological signal monitoring device 150 can have an independent power supply. The physiological signal monitoring device 150 can send the collected data (e.g., physiological signal) to other components (e.g., the storage device 130, the terminal device 110) through wired or wireless (e.g., Bluetooth, WiFi, etc.) manner. In some embodiments, one or more components in the application scenario 100 can be part of the physiological signal monitoring device 150. For example, the storage device 130, etc. can be included in the physiological signal monitoring device 150. More information about the physiological signal monitoring device 150 can be found in FIGS. 2A-14 and their related descriptions.

[0059] In some embodiments, the application scenario 100 can further include a processing circuit (not shown in FIG. 1, which can be configured in the physiological signal monitoring device 150 or the terminal device 110). The processing circuit can calculate and obtain physiological data based on the electrical signals collected by the plurality of electrodes. The physiological data refers to data determined based on the physiological signal, reflecting the biological electrical characteristics of the monitoring subject (e.g., the monitoring subject 140), for example, when the physiological signal is an electrocardiogram signal, the physiological data can be electrocardiogram data. In some embodiments, the processing circuit can provide feedback to the monitoring subject 140 based on the changes in the physiological signal or the physiological data. For example, according to the electrocardiogram signal or the changes in the electrocardiogram signal during exercise, the user (e.g., the monitoring subject 140) can be reminded to adjust the exercise method or intensity for scientific exercise. In some embodiments, the processing circuit can generate corresponding reminder information based on the changes in the physiological signal or the physiological data and send it to the terminal device 110. For example, based on the changes in the physiological signal or the physiological data, the terminal device 110 can provide voice prompts, produce vibrations, etc., to remind the user.

[0060] It should be noted that the above description of the application scenario 100 is merely for illustration and explanation, and does not limit the scope of the present specification. Various modifications and changes can be made to the application scenario 100 under the guidance of the present specification. However, these modifications and changes are still within the scope of the present specification.

[0061] FIG. 2A is a structure diagram of an inner surface of a physiological signal monitoring device according to some embodiments of the present specification;

[0062] FIG. 2B is a structure diagram of an outer surface of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 3 is a front view of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 4 is a front view of a physiological signal monitoring device according to some other embodiments of the present specification; and FIG. 5 is a front view of a physiological signal monitoring device according to some other embodiments of the present specification. Among them, FIG. 3, FIG. 4 and FIG. 5 are front views of the physiological signal monitoring device when it is placed horizontally (for example, when the outer surface or the inner surface is placed parallel to the desktop / ground), and the subsequent front views are the same.

[0063] In some embodiments, the physiological signal monitoring device can include a wearing body. The wearing body refers to the part of the physiological signal monitoring device worn on the body part (for example, chest, waist, etc.) of the user (for example, the monitoring object 140). In some embodiments, the wearing body can be directly worn on the body part of the user, for example, the wearing body is worn on the user's body through the base body (for example, the base body 210 described later). In some embodiments, the wearing body can be combined with a wearable device to be worn on the body part of the user, for example, the wearing body can be arranged on the inner surface of the clothes, so as to be worn on the user's body.

[0064] In some embodiments, as shown in FIG. 2A, the wearing body 200 includes a base body 210 and an electrode 220.

[0065] The base body 210 is configured to carry the electrode 220 and fix the electrode 220 to the target body part of the human body. The target body part refers to the body part to be measured for the physiological signal. For example, when the physiological signal monitoring device is used to measure the electrocardiogram signal, the base body 210 can fix the electrode 220 to the chest of the human body, and at this time, the target body part corresponds to the chest. For another example, when the physiological signal monitoring device is used to measure the electromyogram signal, the base body 210 can fix the electrode 220 to the muscle part to be measured (for example, the electromyogram signal of the pectoralis major muscle is measured, and the electrode is fixed to the pectoralis major muscle), and at this time, the target body part corresponds to the muscle part to be measured. For another example, when the physiological signal monitoring device is used to measure the fetal heart signal, the base body 210 can fix the electrode 220 to the abdomen of the pregnant woman, and at this time, the target body part corresponds to the abdomen.

[0066] In some embodiments, as shown in FIG. 2A, the base body 210 can have a shape of a strip.

[0067] In some embodiments, as shown in FIG. 2A, the base body 210 can be provided with a connecting member 211 and a connecting member 212 at two ends along the length direction of the base body 210, respectively. When the connecting member 211 and the connecting member 212 are connected (e.g., buckled), the base body 210 can be wrapped around and fitted to a wearing part of a user (e.g., a user’s chest, waist, etc.). In some embodiments, the connecting member can be a connecting buckle, such as a button, a snap, a magnetic buckle, etc.

[0068] In some embodiments, the material of the base body 210 can include plant fibers (e.g., cotton fibers, hemp fibers, etc.), animal fibers (e.g., wool, etc.), synthetic fibers (e.g., acrylic, polyester, spandex, etc.), modified chemical fibers, etc. For example, the base body 210 can be knitted from yarns made of plant fibers (e.g., cotton yarns).

[0069] In some embodiments, the base body 210 can include elastic yarns (e.g., cotton yarns, spandex yarns, etc.), i.e., the yarns used for the base body 210 are elastic yarns, and the base body 210 is knitted from the elastic yarns.

[0070] In some embodiments, the base body 210 can be brushed to make the wearing of the body 200 more comfortable against the skin.

[0071] The electrodes 220 are configured to be in contact with the skin of a human body to collect physiological signals (e.g., electrocardiogram signals, electromyogram signals) of the human body. In some embodiments, as shown in FIG. 2A, the electrodes 220 include a first electrode 221 and a second electrode 222. The first electrode 221 and the second electrode 222 are arranged at intervals along the length direction of the wearing body 200.

[0072] In some embodiments, the electrodes 220 can include a substrate and a coating layer. For example, as shown in FIG. 3, the first electrode 221 includes a substrate 2211 and a coating layer 2212, and the second electrode 222 includes a substrate 2221 and a coating layer 2222.

[0073] The substrate is configured to carry the coating. The coating is printed on the surface of the substrate away from the base. At this time, the base, the substrate and the coating are sequentially stacked in the thickness direction of the wearing body 200. The material of the coating is a conductive material for collecting physiological signals. In some embodiments, the material of the substrate can be a low-elasticity textile, for example, the material of the substrate can be a low-elasticity cloth, a woven cloth, etc. By setting the material of the substrate as a low-elasticity textile, the substrate can have better stability, thereby facilitating the printing of the coating. In some embodiments, the material of the substrate can also be the same as or similar to the material of the base 210, for example, the material of the substrate can include plant fibers (for example, cotton fibers, hemp fibers, etc.), animal fibers (for example, wool, etc.), synthetic fibers (for example, acrylic, polyester, spandex, etc.), modified chemical fibers, etc.

[0074] In some embodiments, the coating can be a conductive silicone ink. The electrode is formed by printing the coating (for example, the conductive silicone ink) on the substrate. That is, the first electrode 221 is formed by printing the conductive silicone ink on the substrate 2211, and the second electrode 222 is formed by printing the conductive silicone ink on the substrate 2221. In some embodiments, the electrode 220 can also not include a substrate, at this time, the electrode 220 is formed by directly printing the coating on the predetermined position (the surface of the base 210 is predetermined to carry the electrode area) on the surface of the base 210 close to the human skin. In some embodiments, the preparation process of the conductive silicone ink can be as follows: first, conductive particles are added to an organic solvent, and the conductive particles are dispersed in the organic solvent, then silica gel is added, and the silica gel forms a network to wrap and bind the dispersed conductive particles, thereby forming a conductive silicone ink; at this time, the conductive silicone ink is in a liquid or fluid state, and the conductive silicone ink in this state is printed on the surface of the substrate, and after the organic solvent volatilizes, a solid electrode is formed. The conductive particles herein can include metal particles, carbon particles, etc. or any combination thereof. In some embodiments, the conductive silicone ink has good chemical stability and can resist various solvents and chemicals; and the conductive silicone ink has good biocompatibility, so that the physiological monitoring device can be applied to medical equipment and biosensors. In addition, the conductive silicone ink also has the function of improving the wetness, that is, it can reduce the evaporation of sweat.

[0075] In some embodiments, compared to a traditional metal electrode (such as a silver electrode) that is completely exposed to air and is susceptible to corrosion, the conductive particles in the present case are bound in the silicone, which can reduce the contact with air, so that the conductive silicone ink has strong corrosion resistance and a longer service life than the traditional metal electrode. In addition, when the conductive particles are carbon particles, the carbon particles are more stable and chemically inert, so that the conductive silicone ink has strong corrosion resistance and a longer service life. In some scenarios, the electrode can also be formed by molding a solid conductive silicone, but the electrode obtained in this way has a thicker thickness and higher hardness. In contrast, the conductive silicone ink is liquefied and then printed on the substrate, which can make the thickness of the conductive silicone ink thinner, so that the wearable body 200 has better flexibility and elasticity. Furthermore, since the uniformity of the dispersion of the conductive particles affects the conductivity of the conductive silicone ink, the viscosity of the traditional solid silicone is very high, and the uniformity of the dispersion of the conductive particles is poor, so the conductivity is poor. In contrast, the preparation process of the conductive silicone ink can make the conductive particles more uniformly dispersed, and have better conductivity.

[0076] In some embodiments, in order to enable the wearable body 200 to accurately and effectively collect the physiological signals of the user, the electrical conductivity of the electrode formed by printing the conductive silicone ink on the substrate is within the range of 0.1 S / cm to 0.3 S / cm. As an example, in order to improve the accuracy of the wearable body 200 in collecting the physiological signals of the user, the electrical conductivity of the electrode formed by printing the conductive silicone ink on the substrate is 0.125 S / cm. In some embodiments, in order to improve the comfort of wearing the wearable body 200, the thickness of the conductive silicone ink printed on the substrate can be within the range of 200 microns to 1000 microns.

[0077] In some embodiments, by printing the conductive silicone ink on the substrate to form the electrode, the conductive silicone ink and the substrate are difficult to separate. At the same time, the conductive silicone ink penetrates into the substrate after being applied and is fused with the substrate, so that the conductive silicone ink electrode has higher strength.

[0078] In some embodiments, the substrate of the electrode is stacked on the surface of the base body 210 close to the human skin (i.e. the inner surface of the base body), and the coating of the electrode is located on the side of the substrate away from the base body 210. At this time, the base body 210, the substrate of the electrode, and the coating of the electrode are sequentially stacked in the thickness direction of the wearing body 200. For example, as shown in FIG. 3, the substrate 2211 of the first electrode 221 is stacked on the inner surface of the base body 210 (i.e. the surface close to the human skin), the coating 2212 of the first electrode 221 is located on the side of the substrate 2211 away from the base body 210, and the base body 210, the substrate 2211 and the coating 2212 are sequentially stacked in the thickness direction; similarly, the substrate 2221 of the second electrode 222 is stacked on the inner surface of the base body 210, the coating 2222 of the second electrode 222 is located on the side of the substrate 2221 away from the base body 210, and the base body 210, the substrate 2221 and the coating 2222 are sequentially stacked in the thickness direction.

[0079] In some embodiments, the substrate of the electrode (the substrate 2211 of the first electrode 221, the substrate 2221 of the second electrode 222) and the base body 210 can be connected by adhesion. For example, the side of the substrate of the electrode facing the base body 210 can be provided with a back adhesive, and the substrate is adhered to the base body 210 by the back adhesive.

[0080] In some embodiments of the present specification, the substrate is stacked on the inner surface of the base body, and the conductive silicone ink is printed on the surface of the substrate away from the base body to form the electrode, which can enable the electrode to conform to the human skin to accurately measure the physiological signals of the human body. In some embodiments, the substrate of the electrode and the base body are connected by adhesion, so that the electrode and the base body can be processed and produced separately, and then adhered after the production is completed, thereby improving the production efficiency.

[0081] In some embodiments, the base of the electrode and the base body 210 can be connected in a side-by-side manner. At this time, the base of the electrode is embedded in the base body 210. In some embodiments, the base of the electrode can be completely embedded in the base body 210 (i.e., the electrode penetrates the base body 210 along the thickness direction), at this time, the surface of the base away from the coating is flush with the outer surface of the base body 210 (the surface of the base body 210 away from the human skin), and the base body 210 surrounds the outer peripheral side of the electrode. For example, as shown in FIG. 4, the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222 are spaced apart along the length direction, and the base 2211 and the base 2221 are completely embedded in the base body 210, the surface of the base 2211 away from the coating 2212 and the surface of the base 2221 away from the coating 2222 are flush with the outer surface of the base body 210, and the base body 210 surrounds the outer peripheral side of the first electrode 221 and the second electrode 222. The base body 210, the first electrode 221 and the second electrode 222 are connected in a side-by-side manner along the length direction. In some embodiments, the base of the electrode can also be partially embedded in the base body 210. For example, as shown in FIG. 5, the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222 are partially embedded in the base body 210, and the base body 210 surrounds the peripheral side of the base 2211 and the surface of the base 2211 away from the coating 2212, and the base body 210 surrounds the peripheral side of the base 2221 and the surface of the base 2221 away from the coating 2222.

[0082] In some embodiments of the present specification, by connecting the base and the base body in a side-by-side manner, the overall thickness of the wearable body 200 can be reduced, and the flexibility can be improved.

[0083] In some embodiments, the base body and the base are formed by mixed weaving or integrated weaving of one or more yarns.

[0084] Integrated weaving refers to a process of continuously weaving an overall fabric using one or more yarns (e.g., cotton yarn, polyester yarn, etc.). For example, based on the yarns contained in the base body and the base (e.g., the base body contains cotton yarn and the base contains polyester yarn), the base body and the base are continuously woven according to the predetermined positional relationship between the base body and the base (e.g., the positional relationship between the base body and the base shown in FIG. 3 or FIG. 4 or FIG. 5) to obtain a shaped base body and base. During the weaving process, a transition weaving method (e.g., tuck knitting) is used when transitioning between the base body and the base. Further, after the base body and the base are woven based on the above integrated weaving process, the coating can be printed on the surface of the base facing the human skin (e.g., conductive silicone ink is printed on the surface of the base), thereby obtaining a complete wearable body.

[0085] In some embodiments of the present specification, by integrated weaving, the stability of the connection between the base and the base body can be improved.

[0086] FIG. 6 is a structure diagram of an inner surface of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 7 is a front view of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 8 is another front view of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 9 is another front view of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 10 is another structure diagram of an inner surface of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 11 is another front view of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 12 is another front view of a physiological signal monitoring device according to some embodiments of the present specification; FIG. 13 is another front view of a physiological signal monitoring device according to some embodiments of the present specification; and FIG. 14 is another front view of a physiological signal monitoring device according to some embodiments of the present specification.

[0087] In some embodiments, the wearable body further comprises a waterproof layer, and the at least one electrode is connected to the base body through the waterproof layer. For example, as shown in FIG. 6 and FIG. 7, the wearable body 200 further comprises a waterproof layer 250, and the first electrode 221 and the second electrode 222 are connected to the base body 210 through the waterproof layer 250.

[0088] When the base body 210 is immersed in liquid (for example, when the user moves, sweat is immersed in the base body 210), the base body 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 base body 210, the first electrode 221, the second electrode 222 and the base body 210 need to be insulated, based on this, the waterproof layer 250 can be made of insulating waterproof material, for example, the waterproof layer 250 can be made of insulating rubber, silicone and the like.

[0089] In some embodiments, when the wearable body comprises a waterproof layer, the electrode can only comprise a coating (i.e., the electrode does not comprise a substrate), and the coating is directly printed on the surface of the waterproof layer away from the base body. For example, conductive silicone ink is directly printed on part of the surface of the waterproof layer away from the base body. For example, as shown in FIG. 8, the coating 2212 is directly printed on part of the surface of the waterproof layer 250 away from the base body 210, and the coating 2212 serves as the first electrode 221; the coating 2222 is directly printed on part of the surface of the waterproof layer 250 away from the base body 210 (the coating 2212 and the coating 2222 are printed on the surface of the waterproof layer 250 in a length direction), and the coating 2222 serves as the second electrode 222.

[0090] In some embodiments, the waterproof layer comprises a first waterproof film, the first waterproof film is stacked on the surface of the base body close to the human skin, and the two sides of the first waterproof film are respectively bonded to the base body and the electrode. For example, as shown in FIG. 9, the waterproof layer 250 comprises a first waterproof film 251, the first waterproof film 251 is stacked on the surface of the base body 210 close to the human skin, and the two sides of the first waterproof film 251 are respectively bonded to the base body 210 and the electrode (the first electrode 221 and the second electrode 222). For example, the two surfaces of the first waterproof film 251 can be respectively provided with adhesive, and the first waterproof film 251 is bonded to the base body 210 and the electrode (the first electrode 221 and the second electrode 222) through the adhesive.

[0091] The first waterproof film 251 is located between the base body 210 and the electrode (the first electrode 221 and the second electrode 222), and the first waterproof film 251 can block the liquid between the base body 210 and the electrode, thereby achieving waterproof of the electrode and avoiding abnormal conduction between the first electrode 221 and the second electrode 222.

[0092] In some embodiments, the waterproof layer further comprises a second waterproof film, the second waterproof film is stacked on the side of the first waterproof film close to the human skin, and the second waterproof film is bonded to the outer circumferential side of at least part of the electrode. For example, as shown in FIG. 9, the waterproof layer 250 further comprises a second waterproof film 252, the second waterproof film 252 is stacked on the side of the first waterproof film 251 close to the human skin, and the second waterproof film 252 is bonded to the outer circumferential side of the electrode (including the first electrode 221 and the second electrode 222). One surface of the first waterproof film 251 faces the human skin, and at least part of the first waterproof film 251 can be in contact with the human skin. When the skin surface has sweat, the sweat can flow onto the first waterproof film 251, and the sweat on the first waterproof film 251 (especially the part corresponding to the length direction between the first electrode 221 and the second electrode 222) can also cause abnormal conduction between the first electrode 221 and the second electrode 222. At this time, by providing the second waterproof film 252, the second waterproof film 252 is arranged around the outer circumferential side of the first electrode 221 and the second electrode 222, thereby further achieving waterproof of the two electrodes.

[0093] In some embodiments, the waterproof film (including the first waterproof film and the second waterproof film) is made of a waterproof and insulating film, for example, a rubber film, etc. In some embodiments, preferably, the waterproof film can be made of a polyurethane (PU) film.

[0094] In some embodiments of the present specification, by arranging the first waterproof film 251 and the second waterproof film 252, the electrodes can be waterproofed, and abnormal conduction caused by infiltration between the two electrodes can be prevented; the polyurethane film is selected as the material of the waterproof layer, and because the Young's modulus of the polyurethane film is relatively high, a more stable combination with the data interface can be formed, and noise in the signal acquisition process can be reduced.

[0095] In some embodiments, the waterproof layer 250 includes waterproof and insulating yarns (for example, acrylic yarns, spandex yarns, etc.), the base body 210 includes elastic yarns (for example, polyester yarns, nylon yarns, etc.), and the waterproof layer 250 and the base body 210 are formed by integrated knitting.

[0096] For example, the integrated knitting process of the waterproof layer and the base body can be as follows: based on the yarns contained in the base body and the waterproof layer (the base body contains elastic yarns, and the waterproof layer contains waterproof and insulating yarns), the base body and the waterproof layer are knitted according to the positional relationship between the base body and the waterproof layer (for example, the positional relationship between the base body and the waterproof layer shown in FIGS. 6 and 7, or the positional relationship between the base body and the waterproof layer shown in FIGS. 10 or 11), to obtain a shaped base body and waterproof layer. During the knitting process, a transition knitting method (for example, tuck knitting) is used to transition between the base body and the waterproof layer. Further, after the base body and the waterproof layer are knitted, the electrodes can be fixed to the predetermined positions on the inner surface of the waterproof layer, to complete the combination of the base body, the electrodes, and the waterproof layer included in the wearable body. For example, the above-mentioned fixing method can be that the electrodes are sewn to the surface of the waterproof layer using yarns (for example, insulating yarns or waterproof and insulating yarns, etc.) (for example, the fabric base of the electrodes is sewn to the inner surface of the waterproof layer using yarns, to realize the connection between the electrodes and the waterproof layer), or the electrodes are adhered to the surface of the waterproof layer using adhesives.

[0097] In some embodiments, the waterproof layer is stacked on the surface of the base body close to the human skin, and the base of the electrode is located on the side of the waterproof layer away from the base body. For example, as shown in FIGS. 6 and 7, the waterproof layer 250 is stacked on the surface of the base body 210 close to the human skin (i.e., the inner surface of the base body), and the base of the electrode (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222) is located on the side of the waterproof layer 250 away from the base body 210.

[0098] For example, the integrated knitting process of the base 210 and the waterproof layer 250 shown in FIGS. 6 and 7 can include: knitting the base 210 using the elastic yarn; knitting the waterproof layer 250 on the preset waterproof region (the region where the waterproof layer is preset) of the inner surface of the base 210 using the waterproof insulating yarn. Further, the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222 can be knitted on the inner surface of the waterproof layer 250 in the preset electrode region of the inner surface of the waterproof layer 250 (the region where the electrodes are preset on the surface of the waterproof layer) using the low-elasticity yarn; the coating 2212 of the first electrode 221 is printed on the surface of the base 2211 away from the waterproof layer 250, and the coating 2222 of the second electrode 222 is printed on the surface of the base 2221 away from the waterproof layer 250, thereby obtaining the complete wearable body.

[0099] In some embodiments, the waterproof layer and the base are knitted in a parallel manner, the base is connected to the outer circumferential side of the waterproof layer, and the base of the electrode is located on the surface of the waterproof layer close to the human skin. For example, as shown in FIGS. 10 and 11, the waterproof layer 250 and the base 210 are knitted in a parallel manner (at this time, the waterproof layer 250 penetrates the base 210 in the thickness direction), the base 210 is connected to the outer circumferential side of the waterproof layer 250, and the base of the electrode (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222) is located on the surface (i.e., the inner surface) of the waterproof layer 250 close to the human skin.

[0100] For example, the integrated knitting process of the base 210 and the waterproof layer 250 shown in FIGS. 10 and 11 can include: based on the yarns contained in the base 210 and the waterproof layer 250 (for example, the base 210 contains the elastic yarn, and the waterproof layer 250 contains the waterproof insulating yarn), continuously knitting the base 210 and the waterproof layer 250 according to the positional relationship of the base 210 and the waterproof layer 250 shown in FIGS. 10 and 11, to obtain the base 210 and the waterproof layer 250 shown in FIGS. 10 and 11, wherein during the knitting process, a transition knitting method (for example, tuck knitting) is used when transitioning between the base 210 and the waterproof layer 250. Further, after obtaining the knitted base 210 and the waterproof layer 250, the electrodes (including the first electrode 221 and the second electrode 222) can be fixed on the preset electrode region of the inner surface of the waterproof layer 250, to complete the combination of the base 210, the electrodes, and the waterproof layer 250 included in the wearable body 200.

[0101] In some embodiments, the base of the electrode includes an insulating yarn (for example, cotton yarn, spandex yarn, etc.), and the base and the waterproof layer are integrally knitted.

[0102] For example, referring to the structures of the wearable body shown in FIGS. 6 and 7, or FIGS. 10 and 11, the integrated knitting process of the electrode base (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222) and the waterproof layer 250 can be as follows: knitting the waterproof layer 250 using waterproof and insulating yarns; knitting the electrode base (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222) on the inner surface of the waterproof layer 250 in the preset electrode area of the inner surface of the waterproof layer 250 using low-elasticity yarns. Further, the conductive silicone ink can be printed on the surfaces of the knitted base 2211 and base 2221 to form the first electrode 221 and the second electrode 222.

[0103] In some embodiments, the base, the waterproof layer, and the substrate are knitted in a parallel manner along the length direction, and the waterproof layer separates the base from the substrate. For example, referring to FIG. 12, the base (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222), the waterproof layer 250, and the substrate 210 are knitted in a parallel manner along the length direction, and the waterproof layer 250 separates the base from the substrate 210 along the length direction.

[0104] For example, referring to the structure of the wearable body shown in FIG. 12, the integrated knitting process of the base (including the base 2211 of the first electrode 221 and the base 2221 of the second electrode 222), the waterproof layer 250, and the substrate 210 can include: based on the yarns contained in the base, the waterproof layer 250, and the substrate 210 (for example, the base contains low-elasticity yarns, the waterproof layer 250 contains waterproof and insulating yarns, and the substrate 210 contains elastic yarns), and according to the positional relationship between the base, the waterproof layer 250, and the substrate 210 shown in FIG. 12, the base, the waterproof layer 250, and the substrate 210 are continuously knitted to obtain the base, the substrate 210, and the waterproof layer 250 shown in FIG. 12, wherein during the knitting process, transition knitting methods (for example, tuck knitting) are used when transitioning between the substrate 210 and the waterproof layer 250, and between the waterproof layer 250 and the base. Further, after the base, the substrate 210, and the waterproof layer 250 are knitted, the conductive silicone ink can be printed on the base to obtain the complete wearable body 200.

[0105] In some embodiments, the electrode further includes a substrate layer, and at least part of the substrate layer is located between the waterproof layer and part of the base. For example, referring to FIG. 13, the first electrode 221 includes a substrate layer 2213, and the second electrode 222 includes a substrate layer 2223; at least part of the substrate layer 2213 is located between the waterproof layer 250 and the base 2211, and at least part of the substrate layer 2223 is located between the waterproof layer 250 and the base 2221.

[0106] In some embodiments, as shown in FIG. 14, when the waterproof layer 250 includes the first waterproof film 251 and the second waterproof film 252, the substrate layer 2213 is located between the first waterproof film 251 and the partial substrate 2211, and the substrate layer 2223 is located between the first waterproof film 251 and the partial substrate 2221. It can be understood that the surface of the substrate connected with the first waterproof film 251 is provided with an adhesive, and the substrate is connected with the first waterproof film 251 by the adhesive.

[0107] In some embodiments, the material of the substrate layer can be different from the material of the substrate. For example, the material of the substrate can be a woven fabric with small elasticity, and the material of the substrate layer can be cotton yarn with large elasticity.

[0108] In some embodiments, the material of the substrate layer can be the same as the material of the substrate. For example, the material of the substrate and the material of the substrate layer can both be a woven fabric.

[0109] In some embodiments, when the electrode includes the substrate layer, the electrode, the waterproof layer, and the base body can be formed by integrated weaving. For example, in the structure of the wearable body shown in FIG. 13, the integrated weaving process of the electrode, the base body, and the waterproof layer can be as follows: the base body 210 is woven by using elastic yarn; the waterproof layer 250 is woven on the inner surface of the base body 210 in the predetermined waterproof area by using waterproof and insulating yarn; and in the predetermined electrode area of the waterproof layer 250, the base body (including the substrate 2211 of the first electrode 221 and the substrate 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) are continuously woven based on the yarn contained in each of the base body and the substrate layer, so as to obtain the combination of the base body, the waterproof layer, and the base body as shown in FIG. 13. In the weaving process, a transition weaving method (for example, tuck knitting) is used when the base body and the substrate layer are transitioned. Further, the surface of the base body is printed with a coating (the surface of the substrate 2211 and the substrate 2221 is printed with conductive silicone ink), so as to complete the combination of the base body 210, the electrode 220, and the waterproof layer 250 included in the wearable body 200.

[0110] In some embodiments of the present disclosure, the surface of the electrode away from the waterproof layer can be recessed inwardly relative to the inner surface of the wearable body, which can cause the electrode to fail to continuously adhere to the human skin, thereby affecting the measurement of the physiological signal. Based on this, by providing the substrate layer, the substrate layer can make the surface of part of the electrode flush with or protrude from the inner surface of the base body, so as to ensure that the electrode can continuously contact the human body when the wearable body is worn on the surface of the user, and thereby ensure the quality of the physiological signal measured by the electrode.

[0111] In some embodiments, the electrodes can also have other structural forms. In some embodiments, the electrodes can be made of metal materials, such as silver patches. The silver patch electrodes are attached to the substrate (or waterproof layer), and the silver patch electrodes are in contact with the human skin to collect the physiological signals of the human body. In order to prevent the silver patch electrodes from being corroded and oxidized, the conductive silicone ink can be coated on the surface of the silver patch electrodes close to the human skin. At this time, the conductive silicone ink can not only play a conductive role, but also can protect the silver patch electrodes (such as preventing the silver patch electrodes from being corroded and oxidized).

[0112] FIG. 15 is a schematic diagram of the position of the electrodes on the human body according to some embodiments of the present specification.

[0113] In some embodiments, the first electrode and the second electrode are configured to measure the electrocardiogram signals, and the first electrode and the second electrode are located on both sides of the median plane of the human body. For example, taking the electrodes 220 shown in FIG. 2A as an example, the first electrode 221 and the second electrode 222 can be located on both sides of the median plane of the human body (for example, as shown in FIG. 15, the first electrode 221 is located on the left side of the median plane 240 of the human body, and the second electrode 222 is located on the right side of the median plane 240 of the human body). The median plane of the human body refers to the plane located at the median position of the human body, which passes through the navel and vertically divides the body into two symmetrical parts.

[0114] In some embodiments, preferably, the positions of the human body where the two electrodes are attached are symmetrical about the median plane of the human body, that is, the distances of the two electrodes from the median plane of the human body are equal. For example, taking the two electrodes shown in FIG. 2A as an example, the first electrode 221 is located on the position of the body surface directly opposite the left ilium, and the second electrode 222 is located on the position of the body surface directly opposite the right ilium.

[0115] In some embodiments of the present specification, by configuring the two electrodes on both sides of the median plane, the quality of the collected electrocardiogram signals can be effectively improved, and the signal-to-noise ratio of the electrocardiogram signals can be improved. By further configuring the two electrodes on the symmetrical positions on both sides of the median plane, the quality of the collected electrocardiogram signals can be further improved.

[0116] In some embodiments, the first electrode 221 and the second electrode 222 are configured to collect the electromyography signals of the same muscle, and the first electrode 221 and the second electrode 222 are arranged along the direction of the muscle fibers of the muscle. The first electrode 221 and the second electrode 222 can collect the electric potentials of the skin surface at the positions where the first electrode 221 and the second electrode 222 are respectively located, and the potential difference between the collected electric potentials can be used to reflect the electromyography signals of the muscle. In some embodiments, the first electrode 221 and the second electrode 222 can be used to collect the electromyography signals of the target muscle of the user, and the target muscle can refer to a single muscle or a same muscle group (for example, the quadriceps femoris muscle group including the rectus femoris muscle, the vastus lateralis muscle, the vastus medialis muscle, and the vastus intermedius muscle). For example, the first electrode 221 and the second electrode 222 can be arranged along the direction of the muscle fibers of the target muscle and respectively extend along the extension direction perpendicular to the direction of the muscle fibers, so as to collect the electric potentials of the skin surface at the positions where the first electrode 221 and the second electrode 222 are respectively located, and the potential difference between the collected electric potentials can be used to reflect the electromyography signals of the target muscle. In some embodiments, when the target muscle is a single muscle, the electromyography signals collected by the electrode 220 can include the electromyography signals of the target muscle and other muscles around the target muscle, because there are multiple other muscles around the target muscle. Since the target muscle and the other muscles around the target muscle are in the same muscle group, and the electromyography signals generated by the muscles in the same muscle group are relatively close, the electromyography signals actually collected by the electrode 220 are close to the electromyography signals of the target muscle, and the error is small. That is, the electromyography signals actually collected by the electrode 220 can represent the electromyography signals of the target muscle. It should be noted that in other embodiments, the proportion of noise (i.e., the electromyography signals of the other muscles around the target muscle) in the electromyography signals collected by the electrode 220 can be reduced by means of shape design of the electrode 220, algorithm processing, and the like, so as to improve the accuracy of the physiological signal monitoring device. As an example, the first electrode 221 and the second electrode 222 can be arranged along the direction of the muscle fibers of the gastrocnemius muscle and respectively extend along the extension direction perpendicular to the direction of the muscle fibers. That is, the first electrode 221 and the second electrode 222 can be arranged at the gastrocnemius muscle, arranged along the height direction of the user and respectively extend along the extension direction perpendicular to the height direction of the user, the first electrode 221 and the second electrode 222 can collect the electric potentials of the skin surface at the positions where the first electrode 221 and the second electrode 222 are respectively located, and the potential difference between the collected electric potentials can be used to reflect the electromyography signals of the gastrocnemius muscle.

[0117] In some embodiments, two metal buckles are fixedly arranged on the base, one of the two metal buckles is electrically connected with the first electrode, and the other of the two metal buckles is electrically connected with the second electrode.

[0118] In some embodiments, the two metal buckles can be connected with an external processing circuit, and the two metal buckles realize data transmission (for example, transmission of collected physiological signals to the processing circuit) between the first electrode and the second electrode and the processing circuit. In some embodiments, the processing circuit can be detachably connected with the two metal buckles, for example, the processing circuit can be detachably connected with the two metal buckles through magnetic attraction.

[0119] Exemplarily, as shown in FIGS. 2B-14, the base body 210 is fixedly provided with two metal buckles (metal buckle 231 and metal buckle 232), wherein the metal buckle 231 is electrically connected with the first electrode 221, and the metal buckle 232 is electrically connected with the second electrode 222. In some embodiments, the metal buckle can penetrate through the base body 210 (and at least part of the waterproof layer) in the thickness direction of the base body 210 to be electrically connected with the electrode. For example, as shown in FIG. 14, the metal buckle 231 penetrates through the base body 210, the first waterproof layer 251 and part of the second waterproof layer 252 in the thickness direction of the base body 210 to be electrically connected with the first electrode 221; the metal buckle 232 penetrates through the base body 210, the first waterproof layer 251 and part of the second waterproof layer 252 in the thickness direction of the base body 210 to be electrically connected with the second electrode 222. At this time, the metal buckle 231 and the metal buckle 232 do not protrude from the inner surface of the second waterproof layer 252, and in this arrangement, the end of the metal buckle is wrapped in the second waterproof layer 252, which can avoid the metal buckle from contacting the human skin, thereby avoiding the metal buckle from scratching the human skin, and at the same time, improving the wearing comfort. In other alternative embodiments, the metal buckle 231 can also completely penetrate through the base body 210, the first waterproof layer 251 and the second waterproof layer 252 in the thickness direction of the base body 210 to be electrically connected with the first electrode 221; the metal buckle 232 can also completely penetrate through the base body 210, the first waterproof layer 251 and the second waterproof layer 252 in the thickness direction of the base body 210 to be electrically connected with the second electrode 222. At this time, the metal buckle 231 and the metal buckle 232 are flush with the inner surface of the second waterproof layer 252, or protrude from the inner surface of the second waterproof layer 252. In some embodiments, the metal buckle can be provided in a bent structure (for example, an L-shaped structure), and after the metal buckle penetrates through the base body 210 (and the waterproof layer), the metal buckle is bent towards the direction of the corresponding electrode to be attached to the surface of the electrode facing the human skin, thereby realizing the electrical connection between the metal buckle and the electrode. The bent part of the metal buckle (that is, the part of the metal buckle attached to the surface of the electrode facing the human skin) can be referred to as a buckle foot. In some embodiments, the metal buckle 231 and the metal buckle 232 located on the outer surface of the base body 210 can be connected with an external processing circuit (not shown in the figure). The processing circuit can obtain the electrical signals (for example, electromyographic signals and electrocardiographic signals) collected by the first electrode 221 and the second electrode 222 through the metal buckle 231 and the metal buckle 232, and determine the physiological signals (for example, electrocardiographic signals) and / or physiological data (for example, electrocardiogram) of the wearer (for example, the monitoring object 140) based on the above-mentioned electrical signals.

[0120] Fig. 16 is another front view of a physiological signal monitoring device according to some embodiments of the present specification. In some embodiments, the wearing body can further comprise a conductive layer between the metal buckle and the electrode, through which the metal buckle is electrically connected with the electrode. For example, as shown in Fig. 16, the wearing body 200 can comprise a conductive layer (conductive layer 261 and conductive layer 262), wherein the conductive layer 261 is between the metal buckle 231 and the first electrode 221, and the metal buckle 231 is electrically connected with the first electrode 221 through the conductive layer 261; the conductive layer 262 is between the metal buckle 232 and the second electrode 222, and the metal buckle 232 is electrically connected with the second electrode 222 through the conductive layer 262. In some embodiments, along the thickness direction of the base body 210, the conductive layer 261 can be between the buckle foot of the metal buckle 231 and the coating 2212 of the first electrode 221; the conductive layer 262 is between the buckle foot of the metal buckle 232 and the coating 2222 of the second electrode 222. In some embodiments, the conductive layer can comprise a conductive yarn (for example, silver yarn), and the conductive layer is formed by weaving the conductive yarn. The conductive layer is adhesively connected between the electrode and / or the metal buckle.

[0121] By arranging the 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.

[0122] The foregoing merely illustrates the principles of the application. It will thus be appreciated that those skilled in the art will be able to devise various arrangements that, although not explicitly described or shown herein, embody the principles of the application and are thus within its spirit and scope. In addition, it will be appreciated that those skilled in the art will be able to devise various modifications of the described or illustrated examples, which, though not explicitly described or shown, embody the principles of the application and are thus within its spirit and scope.

Claims

1. A physiological signal monitoring device, comprising: a wearable body, comprising: an electrode configured to contact with human skin to collect human physiological signals, 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 a human body.

2. The physiological signal monitoring apparatus of claim 1, wherein, the substrate of the electrode is stacked on a surface of the base close to human skin.

3. The physiological signal monitoring apparatus of claim 2, wherein, the substrate of the electrode is connected to the base by adhesion.

4. The physiological signal monitoring apparatus of claim 1, wherein, the substrate of the electrode is juxtaposed with the base.

5. The physiological signal monitoring apparatus as defined in claim 2 or 4, wherein the base and the substrate are integrally knitted by one or more yarns.

6. The physiological signal monitoring apparatus of claim 1, wherein, the wearable body further comprises a waterproof layer, at least part of the electrode is connected to the base through the waterproof layer.

7. The physiological signal monitoring apparatus of claim 6, wherein, the waterproof layer comprises a first waterproof film, the first waterproof film is stacked on a surface of the base close to human skin, and the first waterproof film is adhesively connected to the base and the electrode.

8. The physiological signal monitoring apparatus of claim 7, wherein, the waterproof layer further comprises a second waterproof film, the second waterproof film is stacked on a side of the first waterproof film close to human skin, and the second waterproof film is adhesively connected to at least part of the outer circumferential side of the electrode.

9. The physiological signal monitoring apparatus of claim 6, wherein, the waterproof layer comprises waterproof and insulating yarns, the base comprises elastic yarns, and the waterproof layer and the base are integrally knitted.

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

11. The physiological signal monitoring apparatus of claim 9, wherein, the waterproof layer is juxtaposed with the base and is knitted to the base, the waterproof layer is adhesively connected to the outer circumferential side of the base, and the substrate of the electrode is located on a surface of the waterproof layer close to human skin.

12. The physiological signal monitoring apparatus as defined in claim 10 or 11, wherein the substrate of the electrode comprises insulating yarns, and the substrate and the waterproof layer are integrally knitted.

13. The physiological signal monitoring apparatus of claim 9, wherein, the substrate, the waterproof layer and the base are juxtaposed and knitted, and the waterproof layer separates the substrate and the base.

14. The physiological signal monitoring apparatus of claim 6, wherein, the electrode further comprises a substrate layer, at least part of the substrate layer is located between the waterproof layer and part of the substrate.

15. The physiological signal monitoring apparatus of claim 1, wherein, the electrode comprises a first electrode and a second electrode, the first electrode and the second electrode are configured to measure electrocardiogram signals, and the first electrode and the second electrode are located on both sides of the median plane of the human body.

16. The physiological signal monitoring apparatus of claim 1, wherein, the electrode comprises a first electrode and a second electrode, the first electrode and the second electrode are configured to collect electromyogram signals of the same muscle, and the first electrode and the second electrode are arranged in a spaced-apart manner along the direction of muscle fibers of the muscle.

17. The physiological signal monitoring apparatus as defined in claim 15 or 16, wherein two metal buckles are fixedly arranged on the base, one of the two metal buckles is electrically connected to the first electrode, the other of the two metal buckles is electrically connected to the second electrode, the two metal buckles realize data transmission between the first electrode, the second electrode and a processing circuit, and the processing circuit is detachably connected to the two metal buckles by magnetic attraction.

18. The physiological signal monitoring apparatus of claim 17, wherein, the wearable body further comprises a conductive layer 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 apparatus of claim 1, wherein, the base is brushed.

20. The physiological signal monitoring apparatus of 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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