Electrocardiogram monitoring accessory and device

Abstract

An electrocardiogram monitoring accessory and device, comprising: a lead, which contacts a user's body to detect and obtain an electrocardiogram signal, a wire, which is used to transmit the electrocardiogram signal obtained by the lead to a data processing end, and the data processing end obtains and processes the electrocardiogram signal into an electrocardiogram detection result. A collection unit is arranged at the proximal end of the wire communication connected to the lead in a manner of a parallel wire communication line, and the electrocardiogram signal is divided into a first electrocardiogram signal and a second electrocardiogram signal containing equal information in parallel. The collection unit converts the first electrocardiogram signal into a first processing signal according to an analog-to-digital conversion process based on a first sampling frequency, and the data processing end converts the second electrocardiogram signal into a second processing signal according to an analog-to-digital conversion process based on a second sampling frequency, wherein the first sampling frequency is configured to be less than the second sampling frequency, the first electrocardiogram signal and the second electrocardiogram signal are analog signals, and the first processing signal and the second processing signal are digital signals.

Description

Technical Field

[0001] The present invention relates to the field of electrocardiogram detection, and in particular to an electrocardiogram monitoring accessory and device. Background Art

[0002] CN205094431U relates to a home portable electrocardiograph, wherein a display screen is installed on the outer wall of a shell, and a detection button is installed on the left side of the display screen; an electrode detector is installed on the right end of the shell, and a processor and an electrocardiogram detection module are installed inside the shell; the signal output end of the electrode detector is connected to the electrocardiogram detection module, and the signal output end of the electrocardiogram detection module is connected to the processor, and a wireless transmitter is installed on the signal output end of the processor; a detection terminal is arranged outside the shell, and a wireless receiver for information transmission with the wireless transmitter is installed on the detection terminal. The home portable electrocardiograph is small in size and easy to carry. It can be used as a portable medical instrument, and it is convenient to measure and check the pacing electrocardiogram in time. The processor can perform multiple functions such as data acquisition and waveform display, alarm, storage, transmission, analysis, etc., and can complete multiple inspections in the shortest time, thereby saving time and knowing the inspection results in real time.

[0003] Common civilian equipment generally adopts a single-lead method, which has less data volume and less calculation required to eliminate interference, so it has become a conventional choice. However, the test results of general single-lead ECG detection contain the least amount of information, and can only realize some of the most basic ECG detection items, and cannot reflect all or further symptoms of the user. Equipment with 3 leads, 8 leads or even 12 leads is often used in hospitals. Such equipment is generally expensive and has thoughtful anti-interference protection. Thanks to the signal shielding effect of the dedicated detection room and the guidance of professional doctors, the signal interference of multi-lead detection can be limited to a more reasonable range. However, for the civilian field, due to the uncertainty of the use environment and the lack of guidance for user actions, the signal interference generated by multi-lead detection is very serious. If the clutter signal is to be eliminated or prevented, a larger device is required, which is tantamount to increasing the cost and is not convenient for users to carry.

[0004] In addition, on the one hand, there are differences in understanding among those skilled in the art; on the other hand, the inventor studied a large number of documents and patents when making the present invention, but due to space limitations, not all details and contents are listed in detail. However, this does not mean that the present invention does not have the characteristics of these prior arts. On the contrary, the present invention already has all the characteristics of the prior art, and the applicant reserves the right to add relevant prior art to the background technology. Summary of the invention

[0005] In order to solve at least part of the problems existing in the above-mentioned prior art, the present invention provides an electrocardiogram monitoring accessory, which is used to work with a data processing end having data processing and computing functions and a power supply, and comprises: a lead, which contacts the user's body to detect and obtain an electrocardiogram signal, a wire, which is used to transmit the electrocardiogram signal obtained by the lead to the data processing end, and a collection unit is arranged at the proximal end of the wire communication connected to the lead in the form of a parallel wire communication line, and the electrocardiogram signal is divided into a first electrocardiogram signal and a second electrocardiogram signal containing equal information in parallel, and the collection unit converts the first electrocardiogram signal into a first processing signal according to an analog-to-digital conversion process based on a first sampling frequency. Through the setting, the data processing end can convert the second electrocardiogram signal into a second processing signal according to an analog-to-digital conversion process based on a second sampling frequency, wherein the first sampling frequency is configured to be less than the second sampling frequency, the first electrocardiogram signal and the second electrocardiogram signal are analog signals, and the first processing signal and the second processing signal are digital signals.

[0006] This embodiment achieves the effect of performing low-frequency sampling on the wire near the lead end and using it for signal noise evaluation and / or signal noise elimination in the subsequent formal ECG signal processing. The advantage is that the ECG signal is not subjected to high noise interference when it is just generated from the lead, and low-frequency sampling is used to obtain a first processing signal in a digital format that can better reflect the real and correct ECG signal. Not only does the first processing signal used as a reference become a digital form that can be stable and anti-interference to ensure the stability of the reference, but the digital encryption feature can also be used to achieve the anti-counterfeiting effect of the line. In addition, due to the use of the analog-to-digital conversion process of low-frequency sampling, the acquisition part near the lead end of the wire has low working power consumption, low data processing volume, and low data storage throughput. A better reference signal can be obtained under the premise of greatly reducing the volume and power consumption of the related components of the acquisition part. In particular, for the lead part type with more leads, the acquisition part is set on the wire of each lead, and its overall volume, data processing volume and power consumption will not increase significantly, and the wire manufacturing cost will also be controlled within a reasonable range. In particular, in this case, the energy supply of the low-power acquisition unit may not come from the data processing end, but may be autonomously powered by a micro-battery, thereby further avoiding additional interference caused by the power supply of the data processing end.

[0007] Preferably, the first processed signal is configured to be transmittable to a data processing terminal and to be compared with the second processed signal to obtain a noise evaluation value and / or to eliminate inter-point noise in the second processed signal based on the comparison of the first processed signal.

[0008] This solution uses the first processed signal with less interference near the lead in the form of a digital signal to judge or remove the clutter of the second processed signal with richer details, so that the smaller part of the processing work can be placed on the wire closer to the lead, and the accurate data can be collected without causing a large increase in the cost, power consumption and volume of the lead part. The work that requires a lot of calculations is placed on the data processing end, making the circuit division more reasonable, and eliminating or predicting the interference of subsequent wires and interface parts by reference, which is convenient for users to replace corresponding wires or obtain more accurate data. In the case of eliminating the noise between points, the signal interference problem caused by the movement of the wire can be quantified, allowing users to perform slight movements and limit their own behavior based on the noise evaluation value. Generally speaking, users can use this device during slight movements in daily life without having to remain completely still.

[0009] Preferably, the acquisition unit is provided with a first memory, which stores the first processing signal with a timestamp within a first preset time period to form a first processing data packet, and sends the first processing data packet to the data processing end via a wire after the preset time period.

[0010] The collection unit is provided with a storage device so that data within a preset time can be temporarily stored therein. Due to the use of a low-frequency sampling method, the capacity, throughput and volume of the storage device can be realized as a smaller option, which has little impact on the overall structural complexity, volume and weight of the conductor, and will not cause a significant increase in the use and manufacturing costs, which is beneficial to user use.

[0011] Preferably, the data processing end is provided with a second memory, and the data processing end stores the second processing signal with a timestamp according to a second preset time length to form a second processing data packet, wherein the second preset time length is configured to be greater than the first preset time length.

[0012] This setting method is to place the part with larger data processing volume and storage demand on the data processing end with more powerful computing and power supply functions so that the second processing signal can contain more content. In addition, by configuring the second preset time length to be greater than the first preset time length, the time difference between the generation time and transmission time of the first processing signal and the time formed by the second processing signal of the same content is taken into account, so that the second processing signal at least includes the entire range of the first processing signal.

[0013] Preferably, after the data processing end obtains the first processing data packet, the sampling data in the first data processing packet and the sampling data in the second data processing packet are respectively expanded according to their respective timestamps and the time difference between the first processing data packet and the second processing data packet is eliminated by time shifting to achieve a comparison in the same domain.

[0014] Preferably, the value of each first processed signal in the first processed data packet after eliminating the time difference is used as a sampling point, and the second processed signal matching the sampling point in the second processed data packet is formed as a reference point, and other data obtained based on the second sampling frequency are provided between adjacent reference points.

[0015] Preferably, the portion of other data that exceeds the reference point values ​​on both sides thereof is classified as clutter data, and the spike waves that produce sudden amplitude changes in other data are classified as clutter data, and the quality of the clutter data is judged to form a noise evaluation value.

[0016] Preferably, the variation trend of the reference point is used as a template, and after removing the clutter data, a curve that conforms to the description of the first processed signal and has more data details is restored by data fitting to eliminate the noise between points.

[0017] Preferably, the collection unit contains a micro battery as a power supply, and the collection unit is configured to obtain energy only from the micro battery.

[0018] A cardiotoc monitoring device comprises: a lead, which contacts a user's body to detect and obtain cardiotoc signals; a wire, which is used to transmit the cardiotoc signals obtained by the lead to a data processing end; the data processing end obtains and processes the cardiotoc signals into cardiotoc detection results; a collection unit is arranged at the proximal end of the wire communication connected to the lead in a manner of parallel wire communication lines; the cardiotoc signals are divided into a first cardiotoc signal and a second cardiotoc signal containing equal information in parallel; the collection unit converts the first cardiotoc signal into a first processing signal according to an analog-to-digital conversion process based on a first sampling frequency; the data processing end converts the second cardiotoc signal into a second processing signal according to an analog-to-digital conversion process based on a second sampling frequency, wherein the first sampling frequency is configured to be less than the second sampling frequency, the first cardiotoc signal and the second cardiotoc signal are analog signals, the first processing signal and the second processing signal are digital signals, and the data processing end is constructed to at least be able to receive the first processing signal, and to be able to compare the second processing signal with the first processing signal in the same domain to obtain a noise evaluation value and / or eliminate inter-point noise in the second processing signal based on the first processing signal. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] Figure 1 This is a schematic diagram of data flow conversion of the present invention;

[0020] Figure 2 It is a schematic diagram of the structure of the pin part of the present invention;

[0021] Figure 3 It is a schematic diagram of the structure of the present invention;

[0022] In the figure: 100, data processing end; 200, access interface; 300, lead unit; 310, socket; 320, wire tube; 330, wire; 340, lead; 350, mark; 400, pin; 500, acquisition unit; 001, first ECG signal; 002, second ECG signal; 003, first processed signal; 004, second processed signal; 005, first processed data packet; 006, second processed data packet; 007, ECG signal. DETAILED DESCRIPTION

[0023] In the description of the present invention, it should be noted that, in the absence of other special explanations or limitations, the terms "installation", "connection" and "connection" mentioned in the specification should be understood in a broad sense, for example, it can be a fixed connection, or a detachable connection or an integrated connection; it can be a mechanical connection or an electrical connection, or a combination of a mechanical connection and an electrical connection; it can be a direct connection, or it can be an indirect connection through an intermediate switching component. For electronic components, it can be a circuit installation using wires, or it can be a simplified circuit board design using integration and other methods. For those skilled in the art, the specific meanings of the above terms in the present invention can be understood according to specific application situations.

[0024] Figure 3 Provided is an electrocardiogram monitoring accessory and device, which at least includes a data processing end 100, an access interface 200 and a lead unit 300. The data processing end at least includes a power supply and a processor with strong processing capabilities. The access interface 200 is used to connect the lead unit 300 to obtain an externally input electrocardiogram signal 007. Preferably, the access interface 200 of the present invention adopts a TYPE-C interface structure and related interface protocols.

[0025] As can be seen from the above, the access interface 200 adopts the TYPE-C structure and communication protocol, which has at least a plurality of different pins 400 ( Figure 2As shown, not all pins are shown in the figure), the common and standard number is 12. The present invention specifically defines each pin 400, especially the pin 400 of the access interface 200, so that it corresponds to the twelve detection points of the electrocardiogram detection one by one. For example, the pin 400 numbered 1 can only be connected to the lead 340 for detecting the potential of the left arm of the human body, and the pin 400 numbered 2 can only be connected to the lead 340 for detecting the potential of the right arm of the human body. By analogy, the positions of the 12 leads 340 of the human electrocardiogram detection are respectively divided into 6 limb leads 340 (Ⅰ, Ⅱ, Ⅲ, aVR, aVL, aVF) And 6 chest leads 340 (V1~V6), they all have different connection positions on the human body, and the combination of different numbers of leads 340 can detect different ECG parameters. Common detection modes include 3-lead 340, 6-lead 340 and other detection modes. Each different lead 340 is connected to the outside of the human body through a wire 330, and the wire 330 is used to conduct human body potential signals. According to the above-mentioned pin 400 regulations for the access interface 200, only one of the wires 330 led out from each lead 340 is a corresponding pin 400 with signal connectivity feedback among all the pins 400. Therefore, by making a fixed arrangement of the pins 400 of the access interface 200, the position of each pin 400 and the lead 340 corresponding thereto can be fixed, and then by assembling 1-12 leads 340 according to the requirements of ECG detection to form different lead sections 300, for example, the wires 330 of 3 leads 340 are assembled into one lead section 300, and the lead section 300 also includes a socket 310, which is configured to at least be able to be plugged with the access interface 200 to form data communication and physical connection, so the relationship between the socket 310 and the access interface 200 can be configured as the relationship between the male and female heads of the TPYE-C interface. Accordingly, when assembling several wires 330, the wires 330 are connected to the socket 310 accordingly according to the position of the pins 400 corresponding to the wires 330 on the access interface 200. Specifically, the pins 400 between the access interface 200 and the socket 310 are in one-to-one correspondence, for example, pin 400 No. 1 of the access interface 200 corresponds to pin 400 No. 1 of the socket 310, and when the connection is made to form data transmission, the pins 400 of the two are also connected correspondingly. Therefore, the present invention achieves an anti-counterfeiting function, that is, by specially defining the pins 400 of the access interface 200, and when manufacturing the lead part 300, the position of the wire 330 of the lead 340 is correspondingly assembled to the corresponding interface pin 400 according to the above-mentioned specially defined pin 400 position, so that only the correctly manufactured lead part 300 can generate a communication signal connection with the access interface 200, otherwise, the wrong corresponding pin 400 will not generate information interaction, thereby achieving the effect of preventing counterfeiting.

[0026] Preferably, in order to facilitate the user to distinguish the lead parts 300 composed of different leads 340, a mark 350 indicating the composition of the lead 340 is provided on each lead part 340 composed of different numbers of different types of leads 340. Specifically, the multiple strands of wires 330 of the assembled leads 340 are all collected into the same wire tube 320 ( Figure 3 As shown in FIG. 1 , the mark 350 can be set on the line tube 320 by printing, hot stamping, engraving, etc. The content of the mark 350 is mainly the composition of the lead 340, for example, indicating that a certain lead part 300 is a combination of V1-V3 leads 340 of the chest lead 340. This design allows the user to easily identify the composition and function of the lead 340 of each lead part 300, and basically can achieve the effect of being able to use it as soon as the mark 350 is seen, which greatly reduces the learning cost of the user. The lead part 300 formed by any number and any type of arrangement and combination of all 12 leads 340 manufactured in the factory can be directly selected by the user for use, avoiding the problem of misoperation and increased learning cost caused by the user's own wiring according to the lead 340 used.

[0027] Preferably, the interface supports a customized mode in some non-standard connection situations. Specifically, by reallocating pin 400 definitions to certain positions and types of pins 400, the pins 400 can be reorganized to perform functions. For example, the pins 400 used for USB 3.0 can be reassigned to transmit other data signals or to supply power. In this embodiment, the definitions of several pins 400 need to be reallocated to realize the function of transmitting different ECG lead 340 signals.

[0028] Preferably, the pin 400 definition arrangement of the access interface 200 adopted in this embodiment is implemented by simultaneously defining the pins 400 corresponding to the leads 340 that can be combined with each other to form the required number of complete leads 340 in a distributed manner at the asymmetric pin 400 positions of the two pin 400 combinations. Specifically, in this embodiment, the lead 340 connection interface with a maximum of 12 bits is defined on the first pin 400 combination and the second pin 400 combination, and each pin 400 combination has at least a portion of defined pins 400 corresponding to the 12-bit leads 340. Such defined pins 400 corresponding to the leads 340 can be called lead 340 pins, and undefined pins 400 can be called vacant pins. It should be noted that the difference between the lead 340 pin and the vacant pin in the pin 400 structure is whether it has a corresponding wire 330 welded thereto. There is no welded wire 330 on the vacant pin, so it cannot meet the connection requirements of circuits and communications. The above statement can also be described as that the lead 340 pins corresponding to the number of required leads 340 are distributed on at least one of the first pin 400 combination and the second pin 400 combination. Preferably, when the number of required leads 340 is the largest number of 12 leads 340, the lead 340 pins are respectively distributed on the two pin 400 combinations. For example, as shown in the figure, the pin 400 numbered A1 is defined as receiving the N (RL) lead 340, A4 is defined as corresponding to the F (LL) lead 340, B4 is defined as corresponding to the C2 lead 340, and so on. According to the lead 340 of this embodiment, the definition of a group of symmetrical pins 400 in the combination of two pins 400 that are symmetrical about the center will be set to be different. For example, the pin 400 numbered A4 is defined as F(LL), and the corresponding pin 400 B4 is defined as corresponding to the C2 lead 340, and is different from the definition of the pin 400 numbered A4, that is, the socket 310 used in the lead 340 part in this embodiment can only be connected to the access interface 200 in one connection direction to obtain a correct communication connection. For example, the F(LL) and C2 leads 340 are respectively connected to the A4 and B4 positions of the socket 310 through the wire 330. Through the connection between the socket 310 and the access interface 200, the A4 position of the socket 310 corresponds to the A4 position of the access interface 200, and correspondingly the B4 position corresponds. Only then can correct data connectivity be formed for these two leads 340. If the socket 310 is inserted into the access interface 200 in reverse, the A4 position of the socket 310 corresponds to the B4 position of the access interface 200, and the B4 of the socket 310 corresponds to the A4 pin 400 of the access interface 200. This is equivalent to the F (LL) lead 340 of the lead 340 being connected to the pin 400 of the access interface 200 defined as receiving the C2 lead 340. In this case, a data mismatch or signal will be generated, and the ECG detection cannot be performed.

[0029] Specifically, this embodiment uses the current relatively complete and more efficient TYPE-C interface as the basis for improvement, adopts a full-port C port to meet the needs of the 12-bit ECG wire 330, and randomly or selects 12 pins 400 from the full 24 pins 400 as the data transmission interface. Theoretically, there is only a C port in the process of selecting the pins 400. 24 12 = 2704156 options. If the type of corresponding lead 340 accepted is defined for each selected pin 400, then theoretically there are A 12 12 = 479001600 kinds of arrangement schemes. In general, when designing or manufacturing this interface, there are a total of C from selecting pins 400 to defining each pin 400 according to leads 340. 24 12 *A 12 12 =1295295050649600 kinds, these possible choices can be called pin 400 pool, it can be seen that the selection base of pin 400 pool is very large, and the pin 400 selection at the trillion level is enough for the manufacturer to select one of the pin 400 combinations as the production template of the interface during production, so that the wire 330 and the interface produced will be difficult to be copied by other imitators, because the probability of overlapping with the pin 400 combination selected by the manufacturer after random imitation is very small. Therefore, the pin 400 produced by the pin 400 production scheme selected by this implementation will be difficult to imitate, and the wire 330 produced by the imitator cannot be connected to the product produced according to this embodiment and form a data connection.

[0030] A long-standing problem with ECG detection is that ECG signal 007 is usually very weak. The strength of ECG signal 007 detected at lead 340 is not high in itself. In the process of transmission through the line to the interface and then to the host, it is affected by various electromagnetic interferences, power frequency interferences, etc., which greatly increases the difficulty of the host to process the noise. Sometimes it is difficult to distinguish the correct ECG signal 007 from the complex signal noise, which may cause the ECG detection to fail or the detection results to deviate significantly from the normal level.

[0031] At present, the wire 330 connected to the lead 340 used in the ECG equipment has undergone a period of development and has some relatively mature designs. In terms of anti-interference, certain improvements are usually made in the design and manufacture of the line. For example, the lead 340 line produced by Yongkangda Company, which can be adapted to ECG instruments such as Nihon Kohden, Coman, and Sanrui, adopts an ABS-PVC alloy-wrapped line design, which greatly reduces the influence of external electromagnetic and power frequency interference on the signal transmission inside the line. The above-mentioned wires are suitable for large ECG equipment in medical facilities, and are similar for civilian equipment, with certain anti-interference measures on the wires. However, due to the physical or penetrating electromagnetic disturbances of the line, the quality or aging of the wire itself, and the mutual interference between the pins 400 at the interface, the quality of signal transmission is still affected to a certain extent. At present, the process of ECG detection usually teaches users to remain silent when the ECG detection is officially implemented. This silent state requires the user to remain basically still, breathe steadily, and be calm, so as to reduce the interference of the ECG detection signal transmission caused by the user. However, the specific impact of the user's slight movement on the ECG detection signal has not been quantitatively analyzed. Some slight movements do not have much effect on the results of the ECG detection. If the user is forced to remain silent, it will cause the user to have negative emotions about the inconvenience of use, which is not conducive to improving the comfort of using the ECG detection equipment.

[0032] Therefore, preferably, the present invention is provided with a collection unit 500 on the wire 330 of each lead 340, and the collection unit 500 is close to the lead 340 connected to the user's body on the communication link. Specifically, starting from the ECG signal 007 detected by the lead 340, the transmission of the signal in the wire 330 until entering the access interface 200 through the socket 310 to the data processing end is the communication link. As can be seen from the above, in the process of signal transmission in the line, the longer the line is, the more parts of the information contained in the signal are lost and interfered. In particular, the interference and noise generated by the switching part through the socket 310 and the access interface 200 can easily drown out the weak ECG signal 007. The signal received by the collection unit 500 close to the lead 340 on the communication link receives less interference, and can obtain clearer ECG data except for the background noise. Therefore, by transmitting the copied ECG data to the collection unit 500, the effect of attached listening can be achieved in the collection unit 500. Specifically, the acquisition unit 500 is arranged in parallel on the communication link of the wire 330 in a parallel manner. Here, the signal input end of the acquisition unit 500 and one end of the wire 330 parallel thereto form two signal collection ends, which can be referred to as the first signal end and the second signal end. The ECG signal 007 generated on the lead 340 is an analog signal. The ECG signal 007 is transmitted to the wire 330 through the lead 340 and is divided into two ECG signals 007 containing the same information at the position of the acquisition unit 500. One flows to the acquisition unit 500 via the first signal end, and the other flows normally to the remaining wire 330 via the second signal end and enters the data processing end. The two signals can be referred to as the first ECG signal 001 and the second ECG signal 002, respectively. Figure 1 shown.

[0033] The acquisition unit 500 is configured to process the first ECG signal 001 input therein into a first processed signal 003 containing ECG information in digital form according to the process of analog-to-digital conversion, wherein the process of analog-to-digital conversion is realized based on the subdivision process of amplification, filtering, sampling and quantization. The amplification step is to amplify the analog signal so that the ECG signal 007 originally fluctuating in a small range is amplified to a range that can be detected by the module conversion circuit. Filtering is to filter the bandwidth of the amplified first signal to a limited bandwidth that can be accepted by the subsequent sampling step. In principle, the sampling process is to collect the continuously changing signal of the first ECG signal 001 according to a certain specified time through the analog-to-digital conversion circuit, so as to obtain one by one continuous data points arranged in time, wherein the sampling frequency design of the specified time or the sampling process is a more critical issue. According to the calculation formula of sampling frequency Fs=N*df, where Fs is the sampling frequency, N is the number of sampling points, and df is the frequency resolution. The frequency resolution represents the minimum interval for distinguishing two signals of different frequencies in the application. In the desired case, the smaller the value, the better. The more sampling points, the better. The more sampling points, the more information in the analog signal is retained. However, this will cause a lot of calculation and energy consumption of the analog-to-digital conversion circuit, which is unacceptable for the acquisition unit 500 used in the present invention. Therefore, this embodiment adopts a lower sampling frequency for analog-to-digital conversion, and the sampling frequency can be called the first sampling frequency. Quantization is to compare and transform the sampled data points according to the coding table set in the circuit, and finally convert the data of each data point into a digital form described by binary. This signal after analog-to-digital conversion is called the first processed signal 003. Due to the use of a lower first sampling frequency, the generated first processed signal 003 contains less information, but because it is close to the position of lead 340 for detecting the ECG signal 007, it can be considered that the information it contains is less affected by interference such as noise and clutter. If the entire first processed signal 003 is restored, the restored ECG information will be closer to the ECG information collected at lead 340.

[0034] Therefore, in this embodiment, the first processed signal 003 is output to the wire 330 through the output end of the acquisition unit 500, and is simultaneously transmitted to the position of the socket 310 with the second ECG signal 002 in the wire 330 and then finally enters the data processing end. The first processed signal 003 is a digital signal, and the second ECG signal 002 is an analog signal, so the scheme of transmitting both in the wire 330 requires the use of a modem, which can be made into a tiny chip level, such as the AD5700-1BCPZ-R5 modem patch chip, which is only about 4*4mm in size and can be embedded in the acquisition unit 500 and / or the wire 330. Or in other embodiments, the signal output end of the acquisition unit 500 is directly communicatively coupled to one of the pins 400 of the socket 310 that is not occupied by the wire 330. According to a situation where there are a maximum of leads 340, 12 pins 400 of the full-port socket 310 are occupied, and the wires 330 connected to these 12 leads 340 respectively have the acquisition unit 500 occupying the remaining 12 pins 400. Compared with analog signals, digital signals have a discrete characteristic obtained by sampling, and their tolerance to noise will be greatly improved. The digital signal can also be restored losslessly by using the decision regeneration method at the signal receiving end, so the first processed signal 003 can be transmitted to the data processing end in an almost lossless state. In some other embodiments, an encryption chip is added before the signal output of the acquisition unit 500 to encrypt the output first processing signal 003, and the encrypted first processing signal 003 is received at the data processing end and decoded using a preset decryption program to obtain the correct first processing signal 003, wherein the encryption and decryption key can be used as judgment data to prevent outsiders from counterfeiting the lead 340. Due to the use of a digital signal mode, the first processing signal 003 can be easily encrypted, and the encryption process is used to achieve a further anti-counterfeiting effect. Similarly, the size of the encryption chip used above is very small, for example, the size of the ATSHA204A-SSHDA-B chip is at the millimeter level, and it can also be buried in the circuit.

[0035] Through the docking of the socket 310 and the access interface 200, the first processed signal 003 and the second ECG signal 002 can be communicated into the data processing end. The component that performs data processing on the ECG signal 007 to obtain the final required complete ECG detection result is called the data processing end 100. The data processing end 100 is constructed to at least receive the first processed signal 003 and the second ECG signal 002, and can convert the second ECG signal 002 into a second processed signal 004 in the form of a digital signal and then compare it with the first processed signal 003 in the same domain to obtain a noise evaluation value and / or eliminate the point-to-point noise in the second processed signal 004 based on the first processed signal 003 acquisition point comparison. The process of generating the second processed signal 004 by the data processing end 100 is similar to the process of generating the first processed signal 003 by the analog-to-digital conversion process described above, but the difference is that in order to obtain a signal with a larger amount of information from the original ECG data, that is, the second ECG signal 002, when sampling the second ECG signal 002, a second sampling frequency with a higher sampling frequency is selected, that is, the second sampling frequency is higher or much higher than the first sampling frequency. This design is because, firstly, when processing ECG data, it is necessary to obtain original data with more detailed information to ensure the integrity and credibility of the ECG detection data; secondly, the data processing end 100 can be equipped with a processor with powerful data processing capabilities and a power supply that can provide stable and high-throughput power.

[0036] Since the transmission of the wire 330 and the conversion of the first ECG signal 001 into the first processed signal 003 by the acquisition unit 500 have a delay, the first processed signal 003 and the second ECG signal 002 that arrive at the data processing end 100 at the same time are not equal in timing, but the first processed signal 003 is slightly delayed from the second ECG signal 002. Therefore, memories are provided on both the acquisition unit 500 and the data processing end 100, which can be respectively referred to as the first memory and the second memory. The first memory stores the first processed signal 003 with a timestamp within a first preset time period to form a first processed data packet 005, and sends the first processed data packet 005 to the data processing end 100 via the wire 330 after the preset time period ends. The data processing end 100 stores the converted second processed signal 004 with a timestamp according to the second preset time length to form a second processed data packet 006. After the data processing end 100 obtains a first processed data packet 005, the sampled data in the first data processing packet and the sampled data in the second data processing packet are respectively expanded according to their respective timestamps and the time difference formed by the first processed data packet 005 and the second processed data packet 006 is eliminated by time shifting. The solution for eliminating the time difference is to arrange the sampled data in the first processed data packet 005 with the change of timestamp as a vector. At this time, the time change is equivalent to the independent variable, and the sampled data corresponding to the timestamp is equivalent to the dependent variable. Similarly, the second processed data packet 006 is expanded in the same way, and the second preset time length is set to be longer than the first preset time length. Therefore, the second processed data packet 006 collected in the second preset time length theoretically contains all the contents of the sampled data in the first processed data packet 005. Therefore, by shifting the sampled data in the first processed data packet 005 by time, the corresponding points with the same value can be found in the second processed data packet 006. Or in the case of certain interference, the displacement matching on the image can also be performed by fitting the waveform curve. After matching, reference points are formed in the second processing data packet 006. These reference points are the sampling points in the first processing data packet 005. These reference points and sampling points refer to the values ​​of single data of the first processing signal 003 and the second processing signal 004 or their point system expressions in the coordinate diagram. After matching or correspondence is generated, the second processing data packet 006 is divided into several sections according to each reference point of the time stamp interval. In addition to the reference point data consistent with the sampling point data in the first processing data packet 005, each section also has more refined other data obtained based on a higher sampling frequency. According to the continuous and non-mutated change trend of the curve during the electrocardiogram change process, the part of the other data that exceeds the reference point values ​​at both ends of the section where it is located can be classified as clutter data, and the spike waves that produce a large number of mutations in the amplitude of the other data can be classified as clutter data. The noise evaluation value is obtained by evaluating the quality of the clutter data.Specifically, the good and bad value is obtained by taking into account the number of spike waves, the amplitude of spike waves, and the number and distribution of other data points beyond the reference point and performing differential analysis with the preset reference value. The evaluation of the good and bad value can come from the preset score standard. If the differential good and bad value is not higher than the preset unqualified standard, it indicates that at least the noise anti-interference level of the signal transmission is basically qualified. Preferably, a variety of score standards can also be set, such as unqualified, qualified, good, excellent and other scores. Such scores and judgment schemes can be obtained by experiments or by professionals after judgment and weighing, and finally a noise evaluation value is given. By analogy, by comparing the entire second processing data packet 006 and the first processing data packet 005, an overall evaluation of the interference of the communication line where the wire 330 is located can be obtained, that is, the above-mentioned noise evaluation value, which can be used to guide the user to choose whether to replace the wire 330, repair the interface part or replace the reference source of the use environment. The above-mentioned elimination of the inter-point noise in the second processed signal 004 based on the comparison of the first processed signal 003 acquisition points is to use the change trend of the reference point as a template, and after marking and removing the clutter data in the above-mentioned manner, restore the curve that conforms to the description of the first processed signal 003 and has more data details by data fitting. This curve can be used for subsequent ECG signal 007 processing to obtain an ECG curve with strong anti-interference and high restoration. The above-mentioned first preset time length can be set to 1 minute, and the second preset time length can be set to 1 minute delayed by several seconds. The delay seconds can be determined according to the transmission delay of the wire 330 and the formation and transmission delay time of the first processed data packet 005, and at least greater than the sum of the above-mentioned delay times.

[0037] Preferably, this embodiment also provides another solution for automatically aligning the timestamps of the first processing data packet 005 and the second processing data packet 006. Specifically, when the ECG signal 007 is divided into two by the acquisition unit 500, a marker is used to mark a first timestamp at the ends of the first ECG signal 001 and the second ECG signal 002, respectively, and the first timestamp indicates that the signal segment is intercepted from this time. A timing crystal oscillator is provided inside the marker, and a second timestamp is marked at the end of the first ECG signal 001 and the second ECG signal 002 at the end of the timing, and the second timestamp indicates that the signal segment is stopped from this time. The first timestamp and the second timestamp can be transmitted together with the first ECG signal 001 and the second ECG signal 002 streams in the form of parallel data packets, so that the first ECG signal 001 and the second ECG signal 002 segments respectively intercepted by the first timestamp and the second timestamp are consistent. When the acquisition unit 500 and the data processing end 100 process the first ECG signal 001 and the second ECG signal 002 and store them to form the first processing data packet 005 and the second processing data packet 006, the first timestamp and the second timestamp are retained to determine the start and end time of the two data packets. Even if the first processing data packet 005 is delayed in the time of being delivered to the data processing end 100, according to the markings of the first timestamp and the second timestamp, the data processing end 100 can still align the data in the two data packets at the correct time. Preferably, the marker may not use the method of sending a timestamp, but may send two marking data with a time difference, such as a character, a definition instruction, etc. Since the collection unit 500 and the data processing end 100 both use the method of attaching a timestamp when collecting data, the marking data is only used to mark the start and end of the data segment. The specific timestamp can be implemented by the timestamps of the first processing data packet 005 and the second processing data packet 006 formed as described above. The marking data is used to mark the data used for a certain timestamp as the start or end data.

[0038] This embodiment realizes the effect of performing low-frequency sampling on the wire 330 near the end of the lead 340 and using it for signal noise evaluation and / or signal noise elimination in the subsequent formal ECG signal 007 processing. The advantage is that the ECG signal 007 is not subject to high noise interference when it is just generated from the lead 340, and a first processing signal 003 in a digital format that can better reflect the real and correct ECG signal 007 is obtained by low-frequency sampling. Not only does the first processing signal 003 used as a reference become a digital form that can be stable and anti-interference to ensure the stability of the reference, but it can also use the digital encryption feature to achieve The anti-counterfeiting effect of the circuit is achieved. In addition, due to the use of the analog-to-digital conversion process with low frequency sampling, the collection unit 500 at the end of the wire 330 close to the lead 340 has low working power consumption, low data processing volume, and low data storage throughput. A better reference signal can be obtained under the premise of greatly reducing the volume and power consumption of the related components of the collection unit 500. In particular, for the lead 340 type with more leads 340, the collection unit 500 is set on the wire 330 of each lead 340, and its overall volume, data processing volume and power consumption will not be significantly increased, and the manufacturing cost of the wire 330 will also be controlled within a more reasonable range. In particular, in this case, the energy supply of the low-power collection unit 500 does not come from the data processing end 100, but is autonomously powered by a micro battery, thereby further avoiding additional interference caused by the power supply of the data processing end 100.

[0039] The accessories involved in this embodiment refer to accessories composed of lead parts, which can be sold as a separate product, and the functions of the data processing end can be realized by injecting programs, such as using programs built into devices such as mobile phones, tablets, or computers with corresponding interfaces. The device involved in this embodiment refers to a device formed by combining the lead part with components that can complete the functions of the above-mentioned data processing end.

[0040] It should be noted that the above specific embodiments are exemplary, and those skilled in the art can come up with various solutions inspired by the disclosure of the present invention, and these solutions also belong to the disclosure scope of the present invention and fall within the protection scope of the present invention. Those skilled in the art should understand that the present invention description and its drawings are illustrative and do not constitute a limitation of the claims. The protection scope of the present invention is defined by the claims and their equivalents.

Claims

1. An electrocardiogram monitoring accessory, which is used to work with a data processing terminal (100) having data processing and computing functions and a power supply, comprising: Lead (340), which contacts the user's body to detect and obtain the electrocardiogram signal (007), A wire (330) is used to transmit the electrocardiographic signal (007) obtained by the lead (340) to a data processing terminal (100), It is characterized by: At the proximal end of the wire (330) connected to the lead (340), a collection unit (500) is provided in parallel with the wire (330) communication link, which is close to the lead (340) connected to the user's body on the communication link, wherein the communication link is a path for the signal starting from the electrocardiogram signal (007) detected and obtained by the lead (340) to be transmitted in the wire (330) to enter the access interface (200) through the socket (310) of the lead unit (300) to the data processing end. The electrocardiogram signal (007) is divided into a first electrocardiogram signal (001) and a second electrocardiogram signal (002) containing the same information at the location of the parallel acquisition unit (500), and the acquisition unit (500) converts the first electrocardiogram signal (001) into a first processed signal (003) according to an analog-to-digital conversion process based on a first sampling frequency. The data processing end (100) is capable of converting the second electrocardiogram signal (002) into a second processed signal (004) according to an analog-to-digital conversion process based on a second sampling frequency, wherein the first sampling frequency is configured to be less than the second sampling frequency, the first electrocardiogram signal (001) and the second electrocardiogram signal (002) are analog signals, and the first processed signal (003) and the second processed signal (004) are digital signals. The first processed signal (003) is configured to be transmitted to the data processing terminal (100) and to be compared with the second processed signal (004) to obtain a noise evaluation value and / or to eliminate inter-point noise in the second processed signal (004) based on the comparison of the first processed signal (003). The acquisition unit (500) is provided with a first memory, which stores the first processed signal (003) with a timestamp according to a first preset time length to form a first processed data packet (005), and sends the first processed data packet (005) to the data processing end (100) via a wire (330) after the preset time length ends. The data processing end (100) is provided with a second memory, and the data processing end (100) stores the second processed signal (004) with a timestamp according to a second preset time length to form a second processed data packet (006), wherein the first preset time length is configured to be less than the second preset time length. The sampling data in the first processing data packet (005) is configured to be able to be expanded with the sampling data in the second processing data packet (006) according to their respective timestamps and to eliminate the time difference between the first processing data packet (005) and the second processing data packet (006) by using a time shift method, so as to achieve a comparison in the same domain. The value of each first processed signal (003) in the first processed data packet (005) after eliminating the time difference is used as a sampling point, and the second processed signal (004) in the second processed data packet (006) that matches the sampling point is formed as a reference point, and other data obtained based on the second sampling frequency are located between adjacent reference points. Classifying the portion of the other data that exceeds the reference point values ​​on both sides as clutter data, classifying the spike waves with sudden amplitude changes in the other data as clutter data, and judging the quality of the clutter data to form the noise evaluation value. Using the variation trend of the reference point as a template, after removing the clutter data, a curve that conforms to the description of the first processed signal (003) and has more data details is restored by data fitting to eliminate the noise between the points. The access interface (200) has at least a plurality of different pins (400), each of the pins (400) corresponding to a detection point of electrocardiogram detection. The definition and arrangement of the pins (400) of the access interface (200) are achieved by simultaneously defining the pins (400) corresponding to the leads (340) that can be combined with each other to form a complete number of leads in a distributed manner at the positions of the asymmetric pins (400) of the two pins (400) combined.

2. The monitoring accessory according to claim 1, characterized in that: The collection part (500) contains a micro battery as a power supply, and the collection part (500) is configured to obtain energy only from the micro battery.

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