Non-contact electrocardiosignal collection clothes and electrocardiosignal detection method

Abstract

The application provides a non-contact ECG signal acquisition clothes and an ECG signal detection method. The acquisition clothes comprises a clothes body, a sensing electrode and a control box arranged on the clothes body, the sensing electrode 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 electrically connecting with the control box, the second electrode is arranged in suspension, and the electromagnetic shielding layer is grounded. The sensing electrode on the acquisition clothes 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 therefore has high dielectric performance, can effectively improve the coupling capacitance between the skin and the electrode, and further reduce the capacitive reactance and the 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) detection technology, and more specifically, to a non-contact ECG signal acquisition garment and an ECG signal detection method. Background Technology

[0002] Current ECG sensors primarily acquire ECG signals through contact. Prolonged use of contact-based acquisition patches can cause skin sensitivity and other problems. Even the most skin-friendly patches can only guarantee good contact for 14 consecutive days; beyond that time, adverse reactions such as rashes may occur. Furthermore, existing ECG monitoring systems often restrict movement due to the wiring harness.

[0003] To address the aforementioned issues, non-contact ECG detection technology has emerged that couples ECG signals from the skin to electrodes based on capacitive coupling, and then outputs the signal through processing circuitry. However, since human ECG signals are weak electrical signals with low signal-to-noise ratios, they are easily attenuated by external interference. Furthermore, the coupling capacitance between the current non-contact ECG sensing electrodes and the skin is relatively small, resulting in a large total impedance, which further increases the signal attenuation and affects the quality of ECG signal acquisition. Summary of the Invention

[0004] The problem that this invention aims to solve is that existing non-contact ECG detection methods have small coupling capacitance, large capacitive reactance and total impedance between the sensing electrode and human skin, which causes severe attenuation of the ECG signal during coupling, resulting in poor detection quality and effect of the already weak ECG signal.

[0005] To address the aforementioned problems, this invention provides a non-contact ECG signal acquisition garment, comprising a garment body and sensing electrodes and a control box disposed on the garment body. The sensing electrodes comprise an electrode composite layer, a first insulating layer, an electromagnetic shielding layer, and a second insulating layer disposed sequentially. The electrode composite layer comprises a first electrode, a second electrode, and a polar layer disposed between the first electrode and the second electrode. The polar layer comprises a polar material, barium titanate and / or calcium titanate. The first electrode is used for electrical connection with the control box, the second electrode is suspended, and the electromagnetic shielding layer is grounded.

[0006] Preferably, the electrode composite layer is prepared by the following method:

[0007] A polar solvent is obtained by uniformly mixing 50%-74% by weight of liquid PDMS resin material, 25%-45% of the polar material, 1%-5% of curing agent, and 1%-2% of catalyst.

[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 sensing electrode is disposed on the inner side of the garment body, which is one of the following: a bodysuit, a back-tight strap type, or a side-tight strap type.

[0011] Preferably, the garment body is provided with multiple contact points, and each contact point is provided with a sensing electrode. The number and position of the contact points are set according to the connection points of single or multiple leads.

[0012] Preferably, the garment body is provided with multiple contact points, the number and position of which are set according to the connection points of a single or multiple leads, and multiple sensing electrodes are arranged around the contact points, and the multiple sensing electrode arrays are distributed.

[0013] Preferably, the non-contact ECG signal acquisition clothing also includes a communication module, which includes a WiFi module or a Bluetooth module, and the control box is used to connect to a terminal through the communication module.

[0014] Preferably, the control box includes a power supply, a signal acquisition and processing circuit, and a transmission circuit. The signal acquisition and processing circuit is used to process the bioelectric signal detected by the first electrode (211), and the transmission circuit is used to send the processed signal to the terminal for display or upload it to the cloud for storage.

[0015] The advantages of the non-contact ECG signal acquisition clothing of the present invention compared with the prior art are as follows:

[0016] This invention relates to a non-contact ECG signal acquisition garment. By incorporating sensing electrodes on the garment itself, it allows for uninterrupted ECG signal detection simply by the user wearing the garment, making it convenient to use. The sensing electrodes of this invention include 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. Furthermore, due to the high dielectric properties of the intermediate polar layer of the electrode composite layer, when the human signal coupled from the first electrode is transmitted to the second electrode through the polar layer, the charge is amplified. 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. In addition, the increased coupling capacitance between the skin and electrode composite layer also reduces the cutoff frequency of the high-pass filter formed by the human skin, the insulating medium, and the capacitive coupling electrode, thereby improving the detection effect of electrical signals.

[0017] The present invention also provides a method for detecting electrocardiogram (ECG) signals, based on the non-contact ECG signal acquisition clothing described above, comprising:

[0018] Bioelectrical signals are acquired using the non-contact electrocardiogram signal acquisition sensor electrodes on clothing;

[0019] The control box on the non-contact ECG signal acquisition clothing is used to process the bioelectrical signals, and the processed signals are sent to a terminal or uploaded to the cloud.

[0020] The advantages of the electrocardiogram signal detection method of the present invention compared with the prior art are as follows:

[0021] This invention acquires bioelectrical signals by sensing electrodes on clothing through non-contact electrocardiogram (ECG) signal acquisition. The signals are then processed by a control box and sent to a terminal or uploaded to the cloud for display on the terminal or storage in the cloud. This achieves non-contact, non-disturbing detection of ECG signals. The advantages of non-contact ECG signal acquisition through clothing are the same as those mentioned above and will not be repeated here. Attached Figure Description

[0022] Figure 1 This is a schematic diagram of the electrode composite layer in an embodiment of the present invention;

[0023] Figure 2 This is a flowchart illustrating the preparation method of the electrode composite layer in an embodiment of the present invention;

[0024] Figure 3These are schematic diagrams of different styles of vests in embodiments of the present invention;

[0025] Figure 4 This is a schematic diagram of a single-lead data acquisition vest in an embodiment of the present invention;

[0026] Figure 5 This is a schematic diagram showing the distribution of the 18 lead connection sites in an embodiment of the present invention;

[0027] Figure 6 This is a customized multi-electrode bodysuit in an embodiment of the present invention;

[0028] Figure 7 This is a general-purpose multi-electrode bodysuit as described in the embodiments of the present invention;

[0029] Figure 8 This is a full-body ECG monitoring bodysuit as described in this embodiment of the invention.

[0030] Explanation of reference numerals in the attached figures:

[0031] 1. Control box; 2. Sensing electrode; 21. Electrode composite layer; 22. First insulating layer; 23. Electromagnetic shielding layer; 24. Second insulating layer; 211. First electrode; 212. Second electrode; 213. Polar layer; 100. Human skin; 200. Underwear; 300. Clothing body. Detailed Implementation

[0032] 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.

[0033] Please see Figure 1 , Figure 4 As shown, this embodiment of the invention provides a non-contact ECG signal acquisition garment (hereinafter referred to as acquisition garment), including a garment body 300 and a sensing electrode 2 and a control box 1 disposed on the garment body 300. The sensing electrode 2 includes an electrode composite layer 21, a first insulating layer 22, an electromagnetic shielding layer 23 and a second insulating layer 24 disposed 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 for electrical connection with the control box 1, the second electrode 212 is suspended, and the electromagnetic shielding layer 23 is grounded.

[0034] The clothing collected in this embodiment, such as Figure 1As shown within the dashed box, a sensing electrode 2 and a control box 1 are integrated on the garment body 300. Typically, multiple sensing electrodes 2 are integrated on a single garment body 300, and a control box 1 is also located on the garment body 300. The connections of each sensing electrode 2 are concentrated in the control box 1. The sensing electrodes 2 are used to collect bioelectrical signals, and the control box 1 is used to process the collected signals and transmit the processed signals to a terminal via Bluetooth or WiFi. The terminal displays electrocardiogram curves, or uploads the data to the cloud for storage. It should be noted that when a right leg drive signal is present, to reduce computational complexity and improve efficiency, the signal collected in this embodiment and the right leg drive signal can be uploaded to the terminal for processing and display simultaneously.

[0035] The sensing electrode 2 in this embodiment includes an electrode composite layer 21, such as Figure 1 As 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 control box 1, and the surface of the first electrode 211 is gold-plated to improve the service life of the sensing electrode 2. 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.

[0036] The principle of non-contact ECG detection is that after the electric charge travels from the dermis to the epidermis, the movement of the 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 property of like charges repelling and unlike charges attracting, 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.

[0037] Therefore, when the electrode composite layer 21 of this embodiment 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 aspects: Firstly, the electrode composite layer 21 of this embodiment is equivalent to a capacitor. According to the capacitance value calculation formula, increasing the dielectric constant of the medium between the plates can effectively improve the capacitance value. On the other hand, the first electrode 211 is connected to the external circuit through the control box 1. Therefore, after the charge is polarized on the surface of the human skin 100, according to the principle of non-contact ECG signal detection, 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 will be collected. 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 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, from this perspective, the increased coupling capacitance between the skin and the electrodes reduces the cutoff frequency, thus enabling effective detection of the ECG signal.

[0038] In this embodiment, the sensing electrode 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 can be made of PI material to isolate the electrode composite layer 21 from the electromagnetic shielding layer 23, preventing contact between the two layers and thus avoiding circuit continuity. Preferably, as shown in the example... Figure 1As shown, the area of ​​the first insulating layer 22 can be set to be relatively large to improve the isolation effect. The electromagnetic shielding layer 23 is grounded to shield against external electromagnetic interference. The second insulating layer 24 is used to protect the electromagnetic shielding layer 23 and prevent it from being worn. Thus, in this embodiment, the sensing electrode consists of an electrode composite layer 21, a first insulating layer 22, an electromagnetic shielding layer 23, and a second insulating layer 24 from top to bottom, and the lower surface of the electrode composite layer 21 can be bonded to the first insulating layer 22, the electromagnetic shielding layer 23, and the second insulating layer 24 with an adhesive to form a single piece.

[0039] In some embodiments, the preparation method of the electrode composite layer 21 is described to better understand its structure. For example... Figure 2 As shown, the preparation method of the electrode composite layer 21 is as follows:

[0040] A polar solvent is obtained by uniformly mixing 50%-74% by weight of liquid PDMS resin material, 25%-45% of the polar material, 1%-5% of curing agent, and 1%-2% of catalyst.

[0041] 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.

[0042] 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, making the collected clothing in this embodiment breathable and helping to expel body moisture when used to detect human electrocardiogram signals.

[0043] The substrate can be a carbon fiber board or a glass fiber board, and the first electrode 211 and the second electrode 212 can be copper foil. The prepared polar solvent is applied to the upper and lower surfaces of the carbon fiber board or glass fiber board, and then a flat copper foil is applied to the two surfaces. The entire structure is then fed into a press and cured under high temperature (120-180℃) and high pressure (2h).

[0044] 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, thereby increasing the coupling capacitance between the skin and the electrode composite layer 21.

[0045] In some embodiments, the sensing electrode 2 is disposed on the inner side of the garment body 300 and can be fixed to the garment body 300 by means of adhesive or sewing. The garment body is one of the following: a bodysuit, a back-tight strap type, or a side-tight strap type. Therefore, when wearing the garment, the user wears the undergarment 200 beforehand; the undergarment 200 can be a pure cotton vest, etc., so that the first electrode 211 of the sensing electrode 2 comes into contact with the pure cotton vest. Furthermore, this method facilitates the maintenance of the garment when performing multiple tests. Since the surface of the sensing electrode 2 is gold-plated, daily maintenance can be achieved by wiping with alcohol, and the undergarment 200 can be directly replaced, further extending the service life of the garment.

[0046] In this embodiment, the style of the clothing body 300 is not limited; it can be a vest, long-sleeved shirt, long pants, or other clothing for the subject to wear, thus obtaining various styles of clothing such as vests and long-sleeved shirts for collecting electrocardiogram signals. For example, as... Figure 3 As shown, several different styles of vests are displayed, including bodysuit style ( Figure 3 (a) shown), back strap type ( Figure 3 (b) shown), double-sided strap type ( Figure 3 (c) As shown, each type of vest has its own advantages and disadvantages, allowing for targeted selection. For example, belted vests have a longer lifespan and better fit. Of course, if the belt affects the detection effect at the points, a one-piece compression garment can be chosen. For instance, for 18-lead detection, a compression garment style is preferred because the detection points under the left armpit and on the left back may be affected by the belt. For single-lead detection, which is used more frequently, the belted style can improve product lifespan and is more cost-effective.

[0047] In some embodiments, the garment body 300 is provided with multiple contact points, and each contact point is provided with a sensing electrode 2. The number and position of the contact points are set according to the connection points of single or multiple leads.

[0048] A lead is a technical term in electrocardiography (ECG), referring to the placement of electrodes on the body surface and the connection between the electrodes and the amplifier during ECG recording. ECG leads can be single-lead or multi-lead. A single-lead ECG machine is a type of ECG machine with only one amplification channel. The ECG waveforms of each lead are recorded individually, so it cannot reflect the changes in the ECG in each lead at the same time. Single-lead ECG machines can examine arrhythmias, providing preliminary screening for premature beats, atrial fibrillation, and various irregularities. Their main significance lies in early detection and postoperative follow-up. Given the often transient and immediate nature of heart disease, timely capture of abnormal electrical signals is crucial for subsequent medical judgment. Therefore, single-lead ECGs can serve as a preliminary screening for arrhythmias and an early warning system for heart disease, enabling early detection, treatment, and control. Figure 4 As shown, this is a data collection vest obtained by setting sensing electrode 2 on a tight-fitting vest based on a single-lead detection site.

[0049] Multi-lead systems are categorized into two-lead, three-lead, 12-lead, 15-lead, and 18-lead systems, and are generally selected based on the specific needs. The 18-lead system is currently a relatively comprehensive lead connection method. For example, the distribution of the sensing electrodes 2 for collecting data from the clothing is determined according to the 18-lead connection method. Figure 5 This is a schematic diagram of 18 leads, including: limb leads (4): right upper limb, left upper limb, left lower limb, right lower limb; chest leads (12): V1 is located at the 4th intercostal space on the right sternal border; V2 is located at the 4th intercostal space on the left sternal border; V3 is located at the midpoint of the line connecting V2 and V4; V4 is located at the 5th intercostal space on the left midclavicular line; V5 and V6 are at the same level as V4, located on the left anterior axillary line and the left mid axillary line respectively; V7 is located at the same level as V4 on the left posterior axillary line; V8 is located at the same level as V4 on the left scapular line; V9 is located at the same level as V4 on the left paravertebral line; V3R, V4R, and V5R are located at the corresponding positions of V3, V4, and V5 on the right anterior chest.

[0050] In this embodiment, contact points are set on the garment body 300 according to the lead connection points, and a sensing electrode 2 is set on each contact point. For example... Figure 6 As shown, it is a tight-fitting vest, in which, Figure 6 (a) is the front of the vest. Figure 6(b) shows the back of the vest. The distribution of sensing electrodes 2 on the garment body 300 is the same as the distribution of the 18 lead connection points in the diagram, satisfying all points on the torso. This setup allows for accurate detection, with each sensing electrode 2 precisely detecting the ECG signal at its corresponding location. Since the lead connection points vary between different users, they cannot perfectly match, resulting in slight differences in garment size. Therefore, this type of garment is suitable for customized production, i.e., private customization.

[0051] To achieve widespread use of the same size, it can be designed as follows: Figure 7 As shown, specific leads can be configured when selecting them, either manually or through intelligent settings. Figure 7 (a) is the front of the vest. Figure 7 (b) The back of the vest. In this embodiment, the garment body 300 is provided with multiple contact points. The number and position of the contact points are set according to the connection points of a single or multiple leads. Multiple sensing electrodes 2 are arranged around the contact points, and the multiple sensing electrodes 2 are distributed in an array. Therefore, since multiple sensing electrodes 2 are provided near the same contact point on the garment, the number of detection points increases. Thus, when different users wear the garment, the correct lead contact points can be matched manually or automatically.

[0052] like Figure 8 As shown, this is a long-sleeved full-body compression garment designed for full-body ECG monitoring based on an 18-lead configuration. Figure 8 (a) shows the front of the bodysuit, with sensing electrodes 2 positioned at the limb lead detection sites and the chest lead detection sites, respectively. Figure 8 (b) is the back of the bodysuit.

[0053] In some embodiments, the clothing being collected also includes a communication module, which may include a WiFi module or a Bluetooth module. The control box 1 is used to connect to a terminal via the communication module. In some embodiments, the collected signals can be processed directly in the control box. Of course, if a right leg drive circuit exists, signal processing can also be performed on the terminal. When signal processing is performed at the control box, the control box 1 includes a power supply, a signal acquisition and processing circuit, and a transmission circuit. The signal acquisition and processing circuit is used to process the bioelectrical signals detected by the first electrode 211. The transmission circuit is used to send the processed signals to the terminal for display or upload them to the cloud for storage, for example, by converting them into an electrocardiogram (ECG) curve. In this embodiment, after receiving the ECG signal, the control box 1 wirelessly transmits the data to the terminal via Bluetooth or WiFi. All collected information will be displayed on the terminal. Of course, the data can be stored in the terminal or simultaneously uploaded to the cloud and to the monitoring physician for easy viewing later. Later, the ECG data can even be analyzed using artificial intelligence. If a problem occurs with the ECG, an alarm can be triggered immediately, and the family doctor can also be notified.

[0054] This invention also provides a method for detecting electrocardiogram (ECG) signals, based on the non-contact ECG signal acquisition method described above, comprising:

[0055] Bioelectrical signals are acquired using the non-contact electrocardiogram signal acquisition sensor 2 on the clothing;

[0056] The control box 1 on the non-contact electrocardiogram signal acquisition clothing is used to process the bioelectric signal, and the processed signal is sent to the terminal or uploaded to the cloud.

[0057] The process of collecting clothing in this embodiment is as follows:

[0058] At work, such as Figure 1 As shown, the user should wear appropriate undergarments, such as a vest or long-sleeved shirt; thinner fabrics are more comfortable. Then, put on the collection garment, ensuring a good fit. After starting the system, the user should rest in bed as usual, ensuring that the control box 1 does not compress the abdomen.

[0059] While the disclosure is as stated above, its scope of protection is not limited thereto. Those skilled in the art can make various changes and modifications without departing from the spirit and scope of this disclosure, and all such changes and modifications will fall within the protection scope of this invention.

Claims

1. A non-contact ECG signal acquisition garment, characterized in that, The device includes a garment body (300) and a sensing electrode (2) and a control box (1) disposed on the garment body (300). The sensing electrode (2) includes an electrode composite layer (21), a first insulating layer (22), an electromagnetic shielding layer (23), and a second insulating layer (24) disposed 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 electrically connect to the control box (1), the second electrode (212) is suspended, and the electromagnetic shielding layer (23) is grounded.

2. The non-contact ECG signal acquisition clothing according to claim 1, characterized in that, The electrode composite layer (21) is prepared by the following method: A polar solvent is obtained by uniformly mixing 50%-74% by weight of liquid PDMS resin material, 25%-45% of the polar material, 1%-5% of curing agent, and 1%-2% of catalyst. 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 clothing 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 clothing according to claim 1, characterized in that, The sensing electrode (2) is disposed on the inner side of the garment body (300), which is one of the following: bodysuit, back strap type, or side strap type.

5. The non-contact ECG signal acquisition clothing according to claim 1, characterized in that, The garment body (300) is provided with multiple contact points, and each contact point is provided with a sensing electrode (2). The number and position of the contact points are set according to the connection points of single or multiple leads.

6. The non-contact ECG signal acquisition clothing according to claim 1, characterized in that, The garment body (300) is provided with multiple contact points. The number and position of the contact points are set according to the connection points of single or multiple leads. Multiple sensing electrodes (2) are arranged around the contact points, and the multiple sensing electrodes (2) are distributed in an array.

7. The non-contact ECG signal acquisition clothing according to claim 1, characterized in that, It also includes a communication module, which may include a WiFi module or a Bluetooth module, and the control box (1) is used to connect to the terminal through the communication module.

8. The non-contact ECG signal acquisition clothing according to claim 7, characterized in that, The control box (1) includes a power supply, a signal acquisition and processing circuit, and a transmission circuit. The signal acquisition and processing circuit is used to process the bioelectric signal detected by the first electrode (211), and the transmission circuit is used to send the processed signal to the terminal for display or upload it to the cloud for storage.

9. A method for detecting electrocardiogram (ECG) signals, characterized in that, The non-contact ECG signal acquisition clothing as described in any one of claims 1-8 includes: Bioelectric signals are obtained by using the non-contact electrocardiogram signal acquisition sensor electrode (2) on the clothing; The bioelectric signal is processed by the control box (1) on the non-contact electrocardiogram signal acquisition clothing, and the processed signal is sent to the terminal or uploaded to the cloud.

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