Non-contact electrocardiosignal collection foot ring sensor

Abstract

The application provides a non-contact ECG signal collection foot ring sensor, which comprises a foot ring body and an ECG signal sensor arranged on the foot ring body, wherein the ECG signal sensor comprises an electrode composite layer, a first insulating layer, an electromagnetic shielding layer and a second insulating layer arranged in sequence, the electrode composite layer comprises a first electrode, a second electrode and a polarity layer arranged between the first electrode and the second electrode, the polarity layer comprises a polarity material of barium titanate and / or calcium titanate, the first electrode is used for being connected to an ECG collection circuit, the second electrode is arranged in suspension, and the electromagnetic shielding layer is grounded. The foot ring sensor of the application comprises the electrode composite layer, the electrode composite layer contains the polarity material of barium titanate and / or calcium titanate with high dielectric constant, and thus has high dielectric performance, can effectively improve the coupling capacitance between the skin and the electrode, and further reduce the capacitive reactance and total impedance, reduce the attenuation degree of the ECG signal in the coupling process, and improve the electric signal detection effect.

Description

Technical Field

[0001] This invention relates to the field of electrocardiogram (ECG) signal acquisition technology, and more specifically, to a non-contact ECG signal acquisition ankle bracelet sensor. Background Technology

[0002] Electrocardiography (ECG) is a common clinical diagnostic tool for cardiovascular diseases, assisting medical professionals in identifying the nature and severity of heart lesions and arrhythmias. During testing, electrodes are typically placed on a localized area of ​​the body to record the weak electrical signals generated during cardiac activity. These signals are amplified and transmitted to the machine for recording. ECG signals are differential-mode voltages between specific points on the body, with amplitudes typically in the millivolt (mV) range. However, the amplitude of the human body's power frequency signal is generally in the volt (V) range, making ECGs susceptible to strong power frequency interference, usually in common-mode form. To detect these weak ECG signals amidst such strong interference, operational amplifiers with high common-mode rejection ratios (CMRR) are generally required. ECG machines commonly employ cancellation drive circuits (also known as right leg drive circuits) to improve the CMR. However, current ECG machines are contact devices, requiring electrodes to contact the skin, which can be irritating and may cause adverse reactions such as rashes. Non-contact ECG signal detection offers a non-intrusive approach, avoiding irritating skin contact and providing a better user experience. However, existing non-contact ECG sensing electrodes have a small coupling capacitance with the skin, resulting in a large capacitive reactance and consequently a high total impedance. Furthermore, human ECG signals are weak signals with a low signal-to-noise ratio, easily affected by external factors such as clothing materials, motion artifacts, static electricity, and electromyographic signals from the skin surface. This leads to significant attenuation of the already weak ECG signal during coupling, severely impacting the quality of ECG signal acquisition. Increasing the conditioning circuitry and digital algorithms, on the other hand, presents challenges due to processing difficulties. Summary of the Invention

[0003] The problem that this invention aims to solve is that the coupling capacitance between the existing non-contact ECG sensing electrodes and the skin is small, resulting in a large capacitive reactance, which causes the ECG signal to attenuate significantly during the coupling process and leads to poor signal detection.

[0004] To address the aforementioned problems, this invention provides a non-contact ECG signal acquisition ankle bracelet sensor, comprising: an ankle bracelet body and an ECG signal sensor disposed on the ankle bracelet body. The ECG signal sensor includes an electrode composite layer, a first insulating layer, an electromagnetic shielding layer, and a second insulating layer disposed sequentially. The electrode composite layer includes a first electrode, a second electrode, and a polar layer disposed between the first electrode and the second electrode. The polar layer includes polar materials barium titanate and / or calcium titanate. The first electrode is used to connect to an ECG acquisition circuit, the second electrode is suspended, and the electromagnetic shielding layer is grounded.

[0005] Preferably, the electrode composite layer is prepared by the following method:

[0006] The following raw materials are taken by weight percentage: 50%-74% liquid PDMS resin material, 25%-45% polar material, 1%-5% curing agent, and 1%-2% catalyst.

[0007] The above raw materials are mixed evenly to obtain a polar solvent.

[0008] The polar solvent is applied to the upper and lower surfaces of the substrate, and the first electrode and the second electrode are respectively applied to the upper and lower surfaces of the polar solvent. After curing, the electrode composite layer is obtained.

[0009] Preferably, the curing agent comprises a hydrogen-containing siloxane, and the catalyst comprises a platinum catalyst.

[0010] Preferably, the non-contact ECG signal acquisition ankle sensor further includes one or more of a blood oxygen saturation sensor, a pulse sensor, and a body temperature sensor disposed on the ankle body.

[0011] Preferably, the non-contact ECG signal acquisition ankle sensor further includes a communication module, which is disposed on the ankle body. The ECG signal sensor, blood oxygen saturation sensor, pulse sensor, and body temperature sensor on the ankle body are used to communicate with a terminal through the communication module.

[0012] Preferably, the communication module includes a Bluetooth module or a WiFi module.

[0013] Preferably, the non-contact ECG signal acquisition ankle sensor further includes an ECG acquisition circuit, which is used to send the skin electrical signals acquired by the electrode composite layer to the terminal.

[0014] Preferably, the non-contact ECG signal acquisition ankle sensor further includes a fixing strap, one end of which is connected to the ankle body, and the other end of which is detachably connected to the ankle body.

[0015] Preferably, the non-contact ECG signal acquisition ankle sensor further includes a protective sleeve. The protective sleeve and the fixing strap are both made of silicone and are integrally molded. The protective sleeve is disposed on the surface of the ankle body other than the contact surface. The contact surface is the surface for contact with the skin. The fixing strap is provided with Velcro for connecting with the protective sleeve.

[0016] The advantages of the non-contact ECG signal acquisition ankle sensor of the present invention compared with the prior art are as follows:

[0017] This invention relates to a non-contact ECG signal acquisition ankle bracelet sensor. An ECG signal sensor is mounted on the ankle bracelet body. The ECG signal sensor includes an electrode composite layer. The multi-layered composite structure of the electrode composite layer is equivalent to a capacitor. Because the electrode composite layer contains high-dielectric-constant polar materials such as barium titanate and / or calcium titanate, it possesses high dielectric properties, effectively increasing the capacitance value. Simultaneously, due to the high dielectric properties of the intermediate polar layer of the electrode composite layer, the human signal coupled to the first electrode is amplified when it acts on the second electrode through the polar layer. Since the second electrode is suspended and not connected to any signal, the charge on the second electrode, in turn, amplifies the charge on the first electrode through conduction by the polar layer. Because the first electrode is connected to an external circuit, a stronger signal can be detected, thereby increasing the coupling capacitance between the skin and the electrode, reducing capacitive reactance and total impedance, and decreasing the attenuation of the ECG signal during coupling. Furthermore, the increased coupling capacitance between the skin and the electrode composite layer also lowers the cutoff frequency of the high-pass filter formed by the human skin, the insulating medium, and the capacitive coupling electrode, thereby improving the electrical signal detection effect. Attached Figure Description

[0018] Figure 1 This is a schematic diagram of the anklet body in an embodiment of the present invention. Figure 1 ;

[0019] Figure 2 This is a schematic diagram of the electrode composite layer in an embodiment of the present invention;

[0020] Figure 3 This is a schematic diagram of the anklet body in an embodiment of the present invention. Figure 2 ;

[0021] Figure 4 This is a schematic diagram of the ankle bracelet sensor in an embodiment of the present invention;

[0022] Figure 5 This is a schematic diagram of the ankle bracelet sensor in use according to an embodiment of the present invention;

[0023] Figure 6 for Figure 5 A top view of the ankle strap body of the ankle strap sensor in a horizontal position;

[0024] Figure 7 This is a functional diagram of the ankle bracelet sensor in an embodiment of the present invention;

[0025] Figure 8 This is a schematic diagram of the ankle sensor being worn on the ankle in an embodiment of the present invention.

[0026] Explanation of reference numerals in the attached figures:

[0027] 1. Ankle band body; 2. ECG signal sensor; 21. Electrode composite layer; 22. First insulating layer; 23. Electromagnetic shielding layer; 24. Second insulating layer; 211. First electrode; 212. Second electrode; 213. Polarity layer; 3. Blood oxygen saturation sensor; 4. Pulse sensor; 5. Body temperature sensor; 6. Fixing strap; 7. Protective cover; 8. Power button; 9. Status indicator light; 10. Signal transmission light; 100. Human skin; 200. Clothing and / or bed sheet. Detailed Implementation

[0028] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings.

[0029] like Figure 1 As shown, an embodiment of the present invention provides a non-contact ECG signal acquisition ankle bracelet sensor, comprising an ankle bracelet body 1 and an ECG signal sensor 2 disposed on the ankle bracelet body 1, as follows: Figure 2 As shown, the electrocardiogram (ECG) signal sensor 2 includes an electrode composite layer 21, a first insulating layer 22, an electromagnetic shielding layer 23, and a second insulating layer 24 arranged sequentially. The electrode composite layer 21 includes a first electrode 211, a second electrode 212, and a polar layer 213 disposed between the first electrode 211 and the second electrode 212. The polar layer 213 includes polar materials barium titanate and / or calcium titanate. The first electrode 211 is used to connect to the ECG acquisition circuit, the second electrode 212 is suspended, and the electromagnetic shielding layer 23 is grounded.

[0030] The principle of non-contact ECG detection is that after electric charge travels from the dermis to the epidermis, the movement of charge is hindered by the pajamas and sheets, preventing direct contact with the sensor electrodes. This causes the charge to accumulate on the skin, creating polarization. Due to the repulsion of like charges and the attraction of unlike charges, opposite charges accumulate on the electrode surface. When the charge on the skin surface opposite the electrode changes, the charge on the electrode also changes accordingly, thus enabling non-contact detection of ECG signals.

[0031] This embodiment uses a non-contact ECG signal acquisition ankle sensor (hereinafter referred to as the ankle sensor). The ankle body 1 is fixed to the ankle of the human body. An ECG signal sensor 2 is installed on the ankle body 1 to achieve real-time detection of ECG signals. The ECG signal sensor 2 mainly consists of an electrode composite layer 21, a first insulating layer 22, an electromagnetic shielding layer 23, and a second insulating layer 24. The first insulating layer 22 isolates the electrode composite layer 21 from the electromagnetic shielding layer 23, preventing them from contacting and thus avoiding circuit continuity. The first insulating layer 22 can be made of PI material. The electromagnetic shielding layer 23 shields against external electromagnetic interference and is grounded. The second insulating layer 24 protects the electromagnetic shielding layer 23 from wear. Therefore, the sensor in this embodiment consists of, from top to bottom, an electrode composite layer 21, a first insulating layer 22, an electromagnetic shielding layer 23, and a second insulating layer 24. The lower surface of the electrode composite layer 21, the first insulating layer 22, the electromagnetic shielding layer 23, and the second insulating layer 24 can be bonded together with an adhesive.

[0032] like Figure 2As shown, the electrode composite layer 21 has a multi-layer structure, including a first electrode 211, a polar layer 213, and a second electrode 212 arranged sequentially. The first electrode 211 is used to connect to the ECG acquisition circuit, and the second electrode 212 is suspended. The polar layer 213 has a high dielectric constant because it includes barium titanate and / or calcium titanate, which are polar materials with high dielectric constants. Therefore, when the electrode composite layer 21 is used as a capacitive coupling electrode for non-contact ECG signal detection, its high dielectric constant increases the capacitance value of the coupling capacitance formed between the skin and the electrode. This can be understood from the following three aspects: First, the electrode composite layer 21 in this embodiment can be understood as a capacitor. According to the capacitance value calculation formula, increasing the dielectric constant of the medium between the electrodes can effectively increase the capacitance value. On the other hand, since the external ECG acquisition circuit is connected to the first electrode 211, according to the principle of non-contact ECG signal detection, after the charge is polarized on the surface of the human skin 100, opposite charges that attract the electrical signal of the human skin 100 will be coupled out on the plate of the first electrode 211. When this charge passes through the polar layer 213 between the first electrode 211 and the second electrode 212, the dielectric constant in the polar layer 213 increases significantly. Under the charge conduction of the polar layer 213, the charge on the plate of the second electrode 212 is enhanced. Since the second electrode 212 is suspended, that is, the pin of the second electrode 212 is not connected to any signal, neither to a high level nor to a low level, the charge on the second electrode 212 will also enhance the charge on the first electrode 211 under the conduction of the polar layer 213. Thus, under the charge enhancement effect of the polar layer 213, the enhanced ECG signal on the first electrode 211 can be detected by the ECG acquisition circuit. Therefore, this embodiment increases the coupling capacitance between the skin and the electrode composite layer 21 by setting an electrode composite layer 21 containing a polarity layer 213, thereby reducing the capacitive reactance and the total impedance, thus reducing the attenuation of the ECG signal during coupling and improving the detection quality of the ECG signal. Furthermore, in the non-contact ECG signal detection system, the structure formed by the human skin 100, insulating clothing and / or bed sheet 200, and capacitive coupling electrodes functions as a first-order high-pass filter. Because the coupling capacitance between the skin and the electrode composite layer 21 is increased, the cutoff frequency of the high-pass filter is reduced. Since a high-pass filter has the characteristic of passing high frequencies and blocking low frequencies, the reduced cutoff frequency also allows for effective detection of the ECG signal.

[0033] To facilitate understanding of the structure of the electrode composite layer 21 in this embodiment, some embodiments provide a method for preparing the electrode composite layer 21, including the following steps: taking the following raw materials by weight percentage: 50%-74% liquid PDMS resin material, 25%-45% polar material, 1%-5% curing agent, and 1%-2% catalyst, wherein the polar material includes barium titanate and / or calcium titanate; mixing the above raw materials uniformly to obtain a polar solvent; covering the upper and lower surfaces of the substrate with the polar solvent, and covering the first electrode 211 and the second electrode 212 on the upper and lower surfaces of the polar solvent, respectively, and obtaining the electrode composite layer 21 after curing treatment.

[0034] In this embodiment, the polar solvent forms a cured layer on the substrate surface during the curing process, which together with the substrate constitutes the polar layer 213. Since the polar solvent contains high dielectric constant polar materials such as barium titanate and calcium titanate, and the electrode composite layer 21 is prepared using a mixing and curing process, which is a physical change, the original material properties can be maintained. Therefore, the resulting mixed polar solvent also has a high dielectric constant, and the cured polar layer 213 also has a high dielectric constant. Furthermore, in this embodiment, the electrode composite layer 21 is formed by coating the upper and lower surfaces of the substrate with a polar solvent, covering the first electrode 211 and the second electrode 212 respectively, and then curing and shaping it in equipment such as a press, forming a multi-layered composite layer. Because the distance between the two electrodes is small, it also helps to increase the capacitance value, i.e., increase the coupling capacitance between the skin and the electrode composite layer 21.

[0035] In some embodiments, the curing agent in the polar solvent accounts for 1%-5% of the total weight, preferably 2%, and the specific content can be adjusted according to temperature and humidity. The curing agent is preferably a hydrogen-containing siloxane. The catalyst accounts for 1%-2% of the total weight, preferably 1.5%, and is used to accelerate the curing speed. The catalyst is preferably a platinum catalyst. Liquid PDMS (polydimethylsiloxane) resin material is used to adjust the flexibility of the finished product, which determines the extensibility of the finished product. This allows the sensor prepared in this embodiment to have air permeability, which helps to expel moisture when used to detect human electrocardiogram signals.

[0036] To facilitate understanding of the structure of ECG signal sensor 2, its fabrication steps are described below through a specific example.

[0037] Step S1: Prepare a substrate, which can be a carbon fiber board or a glass fiber substrate.

[0038] Step S2: Prepare a polar solvent, the ingredients of which include: PDMS: 50%-74%; barium titanate and / or calcium titanate: 25%-45%; curing agent: 1%-5%; catalyst: 1-2%.

[0039] Step S3: The polar solvent prepared in step S2 is applied to the upper and lower surfaces of the carbon fiber plate, and then a flat thin copper sheet is applied to the two surfaces. The copper sheet serves as the first electrode 211 and the second electrode 212.

[0040] Step S4: The aforementioned integral structure is fed into a press machine and kept under high temperature (120-180℃) and high pressure for 2 hours. After curing and molding, it is taken out to obtain the electrode composite layer 21.

[0041] Step S5: Cover the electrode composite layer 21 with a first insulating layer 22, an electromagnetic shielding layer 23, and a second insulating layer 24 to obtain the electrocardiogram signal sensor 2.

[0042] In some of these implementations, such as Figure 3 As shown, the ankle bracelet sensor also includes one or more of a blood oxygen saturation sensor 3, a pulsation sensor 4, and a body temperature sensor 5 disposed on the ankle bracelet body 1. Therefore, the ankle bracelet sensor of this embodiment can detect blood oxygen saturation, pulsation signals, body temperature, and skin conductance signals. These signals provide information about human physiological conditions, all of which are important parameters reflecting the body's state. Specifically, blood oxygen saturation and pulsation are typically acquired using photoelectric sensors, while body temperature can be acquired using thermocouples or similar devices.

[0043] In electrocardiogram (ECG) signal detection, it is usually necessary to incorporate a right leg drive to improve the common-mode rejection ratio (CMRR) in order to detect weak ECG signals amidst strong power frequency interference. Since the ankle is far from the heart, the obtained skin conductance signal receives less interference, which can effectively suppress common-mode noise. Therefore, in this embodiment, the ankle sensor is fixed to the right ankle or instep to acquire the skin conductance signal in that area. This signal is then combined with the signal from the chest leads to reduce common-mode noise interference and obtain a more stable ECG signal quality. To enrich the functionality of the ankle sensor, more sensors can be integrated into the ankle body 1 to detect different signals, such as blood pressure, blood oxygen, and heart rate signals as described in the above embodiment. Thus, this embodiment can detect multiple signals, including skin conductance signals, blood oxygen, and body temperature, using only the ankle sensor, eliminating the need for the wristband sensor used in the prior art to detect blood pressure, blood oxygen, and heart rate.

[0044] like Figure 1 As shown, this is a front view of the ankle bracelet body 1 in a horizontal state. Since the ankle bracelet sensor in this embodiment is mainly used to detect electrocardiogram (ECG) signals, other sensors besides the ECG signal sensor 2 can be integrated together to form an integrated sensor. This simplifies the interface of the ankle bracelet body 1, avoids multiple sensors being cluttered, and improves the aesthetics of the ankle bracelet body 1.

[0045] In some embodiments, the ankle bracelet sensor further includes a communication module disposed on the ankle bracelet body 1. The ECG signal sensor 2, blood oxygen saturation sensor 3, pulse sensor 4, and body temperature sensor 5 on the ankle bracelet body 1 can communicate with an external terminal through this communication module. The communication module may include a Bluetooth module or a WiFi module. Figure 7 As shown, the various sensors integrated on the ankle bracelet body 1 are connected to the terminal via a Bluetooth module. The terminal processes the right leg drive signal, blood oxygen saturation, pulse, body temperature and other signals detected by the ankle bracelet sensors.

[0046] In some of these implementations, such as Figure 4 , Figure 5 As shown, the ankle sensor also includes a fixing strap 6. One end of the fixing strap 6 is connected to the ankle body 1, and the other end of the fixing strap 6 is used for detachable connection to the ankle body 1. This design facilitates user wear; in use, the ankle body 1 is wrapped around the ankle once, and then the other end of the fixing strap 6 is fixed to the ankle body 1. For example, as... Figure 8 As shown, Velcro is provided on the fixing strap 6, which makes it convenient for users to adjust the size and wear the garment.

[0047] In some of these implementations, such as Figure 4 As shown, the ankle sensor also includes a protective sleeve 7, which is made of a flexible material, such as a flexible plastic film or silicone. The protective sleeve 7 is disposed on the surface of the ankle body 1 other than the contact surface, which is the surface for contact with the skin. In a preferred embodiment, the fixing strap 6 and the protective sleeve 7 are integrally molded silicone products. The protective sleeve 7 is fitted onto the ankle body 1, one end of the fixing strap is integrally connected to the protective sleeve 7, and the other end is detachably fixed to the protective sleeve 7 by Velcro or the like, forming a ring-shaped body for fitting around the ankle. Figure 4 The image shows a front view of the ankle sensor with a silicone sleeve. The black parts in the image are the silicone fixing strap 6 and the protective sleeve 7. The use of silicone improves the user experience when in contact with the skin. The protective sleeve 7 prevents damage to the ankle sensor body 1, and by wrapping the ankle sensor body 1 with the protective sleeve 7, all-round protection can be achieved for the ankle sensor body 1.

[0048] In some embodiments, the ankle bracelet sensor also includes an electrocardiogram (ECG) acquisition circuit, which transmits the skin conductance signal acquired by the electrode composite layer 21 to a terminal. In this embodiment, the acquired right leg drive signal is directly transmitted to the terminal via the ECG acquisition circuit. The terminal performs unified signal processing, such as combining the received right leg drive signal and the received chest ECG signal and then performing filtering, amplification, and other processing to reduce redundant calculations and errors.

[0049] In some implementations, flexible circuit boards are used to integrate and encapsulate the various sensing components. A flexible silicone strap is used to mount the circuit board and fix it to the ankle, maintaining contact between the sensors and the ankle skin. The collected information is transmitted to a terminal for data synthesis and display. The data can be stored on the terminal or simultaneously uploaded to the cloud and to monitoring physicians for later review. Later, ECG data can even be analyzed using artificial intelligence; if an ECG problem occurs, an alarm can be triggered immediately, and a family doctor can be notified.

[0050] In some of these implementations, such as Figure 5 , Figure 6 As shown, the ankle sensor also includes a power button 8, a status indicator light 9, and a signal transmission light 10, all located on the ankle sensor body 1. The power button 8 is touch-operated, and charging is wireless, preventing the main body from contacting water. The exterior is wrapped and secured with silicone. The status indicator light 9 indicates whether the ankle sensor is powered on; for example, a green light indicates power on, and the light turns off when powered off. The signal transmission light 10 indicates whether the ankle sensor is connected to a terminal.

[0051] The above description is merely a specific embodiment of the present invention, enabling those skilled in the art to understand or implement the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the invention. Therefore, the present invention is not to be limited to the embodiments shown herein, but is to be accorded the widest scope consistent with the principles and novel features of the invention herein.

Claims

1. A non-contact ECG signal acquisition ankle bracelet sensor, characterized in that, include: The ankle bracelet body (1) and the electrocardiogram (ECG) signal sensor (2) disposed on the ankle bracelet body (1) are provided. The ECG signal sensor (2) includes an electrode composite layer (21), a first insulating layer (22), an electromagnetic shielding layer (23), and a second insulating layer (24) disposed in sequence. The electrode composite layer (21) includes a first electrode (211), a second electrode (212), and a polar layer (213) disposed between the first electrode (211) and the second electrode (212). The polar layer (213) includes polar materials barium titanate and / or calcium titanate. The first electrode (211) is used to connect to the ECG acquisition circuit, the second electrode (212) is suspended, and the electromagnetic shielding layer (23) is grounded.

2. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 1, characterized in that, The electrode composite layer (21) is prepared by the following method: The following raw materials are taken by weight percentage: 50%-74% liquid PDMS resin material, 25%-45% polar material, 1%-5% curing agent, and 1%-2% catalyst. The above raw materials are mixed evenly to obtain a polar solvent. The polar solvent is applied to the upper and lower surfaces of the substrate, and the first electrode (211) and the second electrode (212) are respectively applied to the upper and lower surfaces of the polar solvent. After curing, the electrode composite layer (21) is obtained.

3. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 2, characterized in that, The curing agent includes a hydrogen-containing siloxane, and the catalyst includes a platinum catalyst.

4. The non-contact ECG signal acquisition ankle bracelet sensor according to any one of claims 1-3, characterized in that, It also includes one or more of the following: a blood oxygen saturation sensor (3), a pulse sensor (4), and a body temperature sensor (5) disposed on the ankle bracelet body (1).

5. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 4, characterized in that, It also includes a communication module, which is disposed on the ankle bracelet body (1). The electrocardiogram signal sensor (2), the blood oxygen saturation sensor (3), the pulse sensor (4) and the body temperature sensor (5) on the ankle bracelet body (1) are used to communicate with the terminal through the communication module.

6. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 5, characterized in that, The communication module includes a Bluetooth module or a WiFi module.

7. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 5, characterized in that, It also includes an electrocardiogram (ECG) acquisition circuit, which is used to send the skin electrical signals acquired by the electrode composite layer (21) to the terminal.

8. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 1, characterized in that, It also includes a fixing strap (6), one end of which is connected to the ankle ring body (1), and the other end of which is used for detachable connection to the ankle ring body (1).

9. The non-contact ECG signal acquisition ankle bracelet sensor according to claim 8, characterized in that, It also includes a protective sleeve (7), the protective sleeve (7) and the fixing strap (6) are both made of silicone and are integrally molded. The protective sleeve (7) is set on the surface of the ankle ring body (1) other than the contact surface. The contact surface is the surface for contact with the skin. The fixing strap (6) is provided with Velcro for connecting with the protective sleeve (7).

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