Electrocardio monitoring equipment, charging equipment and electrocardiogram monitoring system

Abstract

The utility model relates to electrocardio monitoring equipment, charging equipment and electrocardio monitoring system.The electrocardio monitoring equipment is used for receiving physiological signals acquired by a signal collector, the electrocardio monitoring equipment comprises a first shell and a second shell which are designed in a split mode and detachably installed on the signal collector, and an NFC data collector is arranged in the second shell and detachably installed on the signal collector; the NFC data collector is used for identifying the NFC label of the signal collector, and the NFC label is used for storing the type of the signal collector; a circuit board is further arranged in the first shell, a control circuit and a signal switching circuit are arranged on the circuit board, a switch control end of the signal switching circuit is connected with the control circuit, and a signal output end of the signal switching circuit is connected with the signal acquisition circuit; the second shell is further provided with a conductive connecting piece, one end of the conductive connecting piece is in conductive connection with a conductive contact of the signal collector, and the other end of the conductive connecting piece is connected with the signal input end of the signal switching circuit. The electrocardiogram monitoring equipment can improve the collection efficiency of physiological signals.

Description

TECHNICAL FIELD

[0001] The utility model relates to medical equipment technical field especially, and it is a kind of electrocardiograph monitoring equipment, charging equipment and electrocardiograph monitoring system. BACKGROUND

[0002] With the continuous development of medical and health monitoring technology, real-time monitoring and collection of physiological signals have become an important part of modern medical and personal health management. The development of electrocardiograph monitoring equipment provides more convenient and accurate health monitoring means for doctors and patients, such as electrocardiogram (ECG). These devices not only can obtain the physiological data of users in real time, but also can play an important role in data analysis, disease warning and rehabilitation guidance.

[0003] In related technologies, electrocardiograph monitoring equipment is usually connected with electrocardiograph sensor / electrocardiograph lead, and physiological signals of patients are collected through electrocardiograph sensor / electrocardiograph lead. There are many types of electrocardiograph sensor / electrocardiograph lead, and when different types are replaced, complicated configuration is needed, thereby affecting data collection efficiency. SUMMARY

[0004] Therefore, it is necessary to provide an electrocardiograph monitoring equipment, charging equipment and electrocardiograph monitoring system to solve the above technical problem of low data collection efficiency.

[0005] In a first aspect, the utility model also provides an electrocardiograph monitoring equipment. The equipment is used for receiving physiological signals collected by signal collector; the equipment includes first shell and second shell of split design, the equipment can be detachably installed on the signal collector, the second shell is equipped with NFC data collector, the NFC data collector is used for identifying NFC tag of the signal collector, and the NFC tag is used for storing the type of the signal collector;

[0006] The first shell is also equipped with circuit board, the circuit board is equipped with control circuit and signal switching circuit, the switch control end of the signal switching circuit is connected with the control circuit, and the signal output end of the signal switching circuit is connected with signal collection circuit;

[0007] The second shell is also equipped with conductive connecting piece, one end of the conductive connecting piece is conductively connected with conductive contact of the signal collector, and the other end of the conductive connecting piece is connected with signal input end of the signal switching circuit.

[0008] In one of the embodiments, the signal switching circuit comprises a first analog switch, a second analog switch, a third analog switch and a fourth analog switch, and the signal acquisition circuit comprises a signal acquisition channel; the control circuit is configured to control the conduction of the first analog switch, the second analog switch, the third analog switch and the fourth analog switch to select the signal acquisition channel according to a signal acquisition instruction.

[0009] The control circuit is configured to control the selected signal acquisition channel to input the acquired at least one physiological signal to the signal acquisition circuit.

[0010] In one of the embodiments, the circuit board is further provided with a signal conditioning circuit configured to filter out interference components in the physiological signal.

[0011] In one of the embodiments, the signal acquisition device is further provided with an anti-fake label.

[0012] The ECG monitoring device is further provided with a label identification module configured to read the anti-fake label of the signal acquisition device to perform anti-fake identification on the signal acquisition device.

[0013] In one of the embodiments, the first shell is further provided with a respiration detection circuit configured to acquire a respiration signal.

[0014] In one of the embodiments, the ECG monitoring device is further provided with a motion detection sensor configured to detect the motion state of a human body.

[0015] In one of the embodiments, the circuit board is further provided with a defibrillation circuit; the defibrillation circuit is configured to perform voltage reduction processing on the physiological signal.

[0016] In one of the embodiments, the circuit board is provided with a charging interface; the second shell is mounted with a battery.

[0017] The battery is in conductive communication with an external power source through the charging interface.

[0018] In one of the embodiments, the battery is provided with a connecting structure, and the second shell is provided with a mounting groove; the battery is mounted in the mounting groove through the connecting structure.

[0019] In a second aspect, the utility model further provides a charging device, the charging device is equipped with a plurality of charging slots, the charging slot is used for charging the ECG monitoring device in any one of the above embodiments.

[0020] In a third aspect, the utility model further provides an ECG monitoring system, comprising the ECG monitoring device and the signal acquisition device in any one of the above embodiments; the ECG monitoring device is detachably mounted on the signal acquisition device and is in conductive connection with the signal acquisition device.

[0021] The aforementioned ECG monitoring device integrates an NFC data acquisition unit that can quickly identify the NFC tag on the signal acquisition unit. This allows users to automatically complete identification and configuration simply by bringing the device close to the signal acquisition unit, significantly reducing device preparation time and improving overall acquisition efficiency. Furthermore, the integrated signal switching circuit allows for real-time selection and switching of signal channels, enabling adjustments to the signal acquisition target based on real-time needs. This flexibility reduces manual adjustment time, quickly responding to different monitoring requirements and improving monitoring efficiency. Attached Figure Description

[0022] To more clearly illustrate the technical solutions in the embodiments of this utility model or the conventional technology, the drawings used in the description of the embodiments or the conventional technology will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0023] Figure 1 This is a schematic diagram of the electrocardiogram monitoring device in one embodiment;

[0024] Figure 2 This is a schematic diagram of the electrocardiogram monitoring device in another embodiment;

[0025] Figure 3 This is a schematic diagram of the electrocardiogram monitoring device in yet another embodiment;

[0026] Figure 4 This is a schematic diagram of the electrocardiogram monitoring device in another embodiment;

[0027] Figure 5 This is a schematic diagram of the internal structure of an electrocardiogram monitoring device in one embodiment;

[0028] Figure 6 This is a schematic diagram of the elastic sensing area and charging interface of an electrocardiogram monitoring device in one embodiment;

[0029] Figure 7 This is a schematic diagram of the charging method of an electrocardiogram monitoring device in one embodiment.

[0030] Reference numerals: 100, ECG monitoring device; 200, signal acquisition unit; 11, first housing; 12, second housing; 20, circuit board; 30, conductive connector; 220, conductive contact; 21, conductive point; 105, charging interface; 230, telescopic buckle; 210, base; 300, lead wire; 240, unlock button; 40, battery; 41, mounting part. Detailed Implementation

[0031] The technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only a part of the embodiments of the present invention, and not all of them. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0032] It should be noted that when a component is said to be "located on" another component, it can be directly located on the other component or may have an intervening component. When a component is considered to be "located on" another component, it can be directly located on the other component or may have an intervening component. When a component is considered to be "fixed to" another component, it can be directly fixed to the other component or may have an intervening component.

[0033] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0034] like Figures 1 to 4 The diagram shown is a structural schematic of the electrocardiogram (ECG) monitoring device 100 provided by this utility model. The ECG monitoring device 100 is used to receive physiological signals acquired by the signal acquisition unit 200; as shown... Figure 2 As shown, the ECG monitoring device 100 includes a split-design first housing 11 and a second housing 12, which together form a cavity (not shown). The ECG monitoring device 100 is detachably mounted on a signal acquisition device 200. An NFC data acquisition device is housed within the second housing 12. The NFC data acquisition device is used to identify the NFC tag of the signal acquisition device 200, and the NFC tag is used to store the type of the signal acquisition device 200. By identifying the type of the signal acquisition device 200 and receiving physiological signals collected by different types of signal acquisition devices 200, the ECG monitoring device 100 greatly improves its flexibility and adaptability.

[0035] The first housing 11 also contains a circuit board 20, which has a control circuit and a signal switching circuit. The switch control terminal of the signal switching circuit is connected to the control circuit, and the signal output terminal of the signal switching circuit is connected to the signal acquisition circuit.

[0036] The second shell 12 is further provided with a conductive connecting piece 30, one end of the conductive connecting piece 30 is in conductive connection with the conductive contact 220 of the signal collector 200, and the other end of the conductive connecting piece 30 is connected with the signal input end of the signal switching circuit.

[0037] In the embodiment, the NFC data collector integrated in the electrocardio monitoring device can quickly identify the NFC tag of the signal collector, so that the user only needs to approach the device to the signal collector when using the device to automatically complete the identification and configuration. This quick connection method greatly shortens the preparation time of the device, thereby improving the overall collection efficiency. Further, the signal switching circuit integrated in the device allows real-time selection and switching of the signal channel, so that the signal collection target can be adjusted according to the real-time demand. This flexibility reduces the time of manual adjustment, can quickly respond to different monitoring demands, and improves the monitoring efficiency.

[0038] In some embodiments, the first shell 11 is further provided with an NFC data collector; the NFC data collector is used to read the information of the type of the signal collector 200 stored in the NFC tag to identify the type of the signal collector 200. In some embodiments, before receiving the physiological signal, the control circuit performs in-place detection on the base 210 to confirm whether the signal collector 200 is in conductive connection with the electrocardio monitoring device 100. If so, the NFC data collector identifies the NFC tag configured by the signal collector 200 to identify the type information stored in the NFC tag, uploads the type information of the signal collector 200 to the central station, receives the signal collection instruction of the matching signal collector 200 issued by the central station, and executes the signal collection according to the signal collection instruction. In the embodiment, the NFC data collector automatically identifies different types of signal collectors 200, matches different types of signal collectors 200 to collect different physiological signals, and improves the flexibility and adaptability of the electrocardio monitoring device 100. Moreover, the NFC technology optimizes the hardware design of the electrocardio monitoring device 100, reduces the size of the device, and meets the requirement of receiving and storing physiological signals under the condition of limited size and area.

[0039] In some embodiments, the circuit board 20 is disposed within the cavity. A conductive connector 30 is fixedly mounted on the second housing 12. The base 210 has conductive contacts 220 corresponding to the conductive connector 30. One end of the conductive connector 30 extends into the cavity and is piezoelectrically connected to the conductive point 21 of the circuit board 20. The other end of the conductive connector 30 extends out of the outer surface of the second housing 12. When the ECG monitoring device 100 is mounted on the base 210, the conductive connector 30 abuts against the conductive contact 220 and is electrically connected. The conductive connector 30 is fixedly mounted on the second housing 12 and is piezoelectrically connected to the conductive point 21 of the circuit board 20. Specifically, the first housing 11 and the second housing 12 are fastened together, and the conductive connector 30 abuts against the circuit board 20 and is electrically connected, ensuring a stable electrical connection between the conductive connector 30 and the circuit board 20.

[0040] Since the ECG monitoring device 100 needs to transmit the collected physiological signals to a central station or ECG analysis system for disease analysis, and to meet the requirement of frequent disassembly and reassembly, the second housing 12 is integrated with the conductive connector 30 to fully consider the impact of frequent disassembly and reassembly of the ECG monitoring device 100 on the conductive connector 30. If the conductive connector 30 is damaged during use, the user can directly replace the second housing 12, which is convenient to install and cost-effective. During the replacement process, there is no need to disassemble the circuit board 20, thus avoiding destructive damage to the circuit board 20 and preventing the entire ECG monitoring device 100 from being scrapped due to the replacement of the conductive connector 30. The figure shows 14 conductive connectors 30, of which 10 conductive connectors are connected to a conductive signal acquisition unit 200, including 10 ECG leads or 10 patch ECG electrodes. The 10 ECG leads or 10 patch ECG electrodes include 4 limb leads LA+RA+LL+RL and 6 chest leads V1 to V6. Similarly, to meet the defibrillation function, the 10 ECG leads or 10 patch ECG electrodes are equipped with defibrillation resistors to support the defibrillation function.

[0041] like Figures 1 to 4 As shown, the electrocardiogram (ECG) monitoring device 100 includes a battery 40, which is mounted on a second housing 12. The battery 40 supplies power to the circuit board 20, meeting the power consumption requirements for the operation of the ECG monitoring device 100. The second housing 12 is provided with a mounting part 41 for housing the battery 40.

[0042] In some embodiments, the battery 40 is provided with a connection structure, and the second housing 12 is provided with a mounting groove. The battery 40 is installed in the mounting groove through the connection structure, thereby enabling the battery 40 to be installed on the second housing 12.

[0043] In some embodiments, such as Figure 1 and Figure 3As shown, the base 210 is equipped with a lead wire 300. One end of the lead wire 300 is mounted on the base 210 and exposed to form a conductive contact 220. The exposed conductive contact 220 of the second housing 12 contacts and conducts a conductive connection with the conductive connector 30. The conductive contact 220 is located in the circumferential direction of the base 210. Specifically, the conductive contact 220 can be arranged in the half-area on the base 210 where the telescopic buckle 230 is located. This ensures that when the ECG monitoring device 100 is mounted on the base 210 and flipped towards the base 210, the conductive connector 30 abuts against the corresponding conductive contact 220 on the base 210. This reduces the impact of the ECG monitoring device 100 on the conductive connector 30 when it is assembled on the base 210. At least one telescopic buckle 230 is provided on the base 210. The telescopic buckle 230 is used to limit and fix the ECG monitoring device 100 on the base 210. The telescopic buckle 230 is connected to the unlock button 240. When the user presses the unlock button 240, the telescopic buckle 230 can release the limiting function of the ECG monitoring device 100 on the ECG monitoring device 100, so that the ECG monitoring device 100 can be easily removed from the base 210.

[0044] refer to Figure 5 This is a schematic diagram of the internal structure of an electrocardiogram monitoring device 100 according to another embodiment. Figure 5 As shown, the ECG monitoring device 100 includes a signal switching circuit, a signal acquisition circuit, a tag identification module (NFC reader), a defibrillation circuit, and a signal conditioning circuit. The signal switching circuit uses various analog switches to switch between ECG and respiratory signals. The defibrillation circuit employs, but is not limited to, transient voltage suppression diodes (TVS diodes), anti-defibrillation chips, and gas discharge tubes to perform input signal conditioning, ESD electrostatic discharge protection, and anti-defibrillation protection. The signal conditioning circuit uses resistor-capacitor units to form a low-pass filter to filter out high-frequency interference components in the signal. The signal acquisition circuit has eight ECG signal input channels, an ADCA (analog-to-digital converter) module, built-in channel selection, and supports up to eight signal acquisition channels. The following provides a detailed description of each module.

[0045] It is understandable that different types of signal acquisition devices 200 support the acquisition of different physiological signals. Table 1 below illustrates the functions supported by different types of signal acquisition devices 200. The 3-electrode ECG lead is a single-lead device, with leads I, II, and III; lead III alone does not support respiratory signal acquisition. The 4-electrode patch ECG sensor and the 5-electrode ECG lead both support the acquisition of respiratory, pacing, and ECG signals. The 10-electrode ECG lead does not support respiratory signal acquisition but does support pacing and ECG signal acquisition.

[0046] Table 1 Signal collector 200 type example table

[0047]

[0048] In order to realize the signal acquisition function supported by the different types of signal collectors 200 in Table 1, the utility model proposes to adopt the method of signal switching circuit, in some embodiments, the electrocardiogram monitoring device 100 is configured with a signal switching circuit, the signal switching circuit includes a first analog switch, a second analog switch, a third analog switch and a fourth analog switch; the control circuit is used for controlling the conduction of the first analog switch, the second analog switch, the third analog switch and the fourth analog switch to select the signal acquisition channel; the selected signal acquisition channel inputs the collected at least one physiological signal to the signal acquisition circuit.

[0049] Among them, the physiological signal includes electrocardiogram signal, and can also include respiratory signal. The respiratory signal can include chest breathing (I lead, LA-RA) and abdominal breathing (II lead, LL-RA).

[0050] Specifically, the first analog switch, the second analog switch, the third analog switch and the fourth analog switch are all configurable analog switches, and the electrocardiogram monitoring device 100 is provided with a control circuit, which can control the switching of the first analog switch, the second analog switch, the third analog switch and the fourth analog switch according to the signal acquisition instruction through the control circuit, realize the selection of the corresponding signal acquisition channel, and dynamically adjust the collection of physiological signals.

[0051] The switching principle of the analog switch is as follows:

[0052] The first analog switch: double-pole double-throw switch, used for the selection of V6 signal of ten electrode leads and other lead respiratory feedback signals;

[0053] The second analog switch: double-pole double-throw switch, used for I lead respiration and II lead respiration signal selection except ten electrodes;

[0054] The third analog switch: double-pole double-throw switch, used for I lead electrocardiogram, II lead electrocardiogram and III lead electrocardiogram (three electrode case) selection;

[0055] The fourth analog switch: single-pole four-throw switch, used as the output of right leg drive signal in three electrode case or II lead signal input in other types of cases.

[0056] By setting the switching mechanism of multiple analog switches, the electrocardiogram monitoring device 100 switches the state of each analog switch according to the actual demand, and realizes the use scene of dynamically collecting physiological signals.

[0057] The switching principle of each analog switch under different signal collector 200 types is described below.

[0058] In some embodiments, when the NFC tag information identifies the signal collector 200 as a three-electrode lead, the three-electrode lead includes a left upper limb lead, a right upper limb lead, and a left leg lead. Therefore, the right leg drive signal RLD needs to control the switching of the fourth analog switch to select another limb lead as the output channel, specifically:

[0059] When the RLD is output through the other limb lead, the left leg lead, the I-lead respiration + I-lead pacing + I-lead ECG is supported.

[0060] When the RLD is output through the other limb lead, the left upper limb lead, the II-lead respiration + II-lead pacing + II-lead ECG is supported.

[0061] When the RLD is output through the other limb lead, the right upper limb lead, the III-lead pacing + III-lead ECG is supported.

[0062] Taking the II-lead respiration / ECG as an example (the I-lead signal is similar), the following is explained:

[0063] The first analog switch: switches to select the respiration signal collection channel, and inputs the respiration feedback signal of the human body to the signal collection circuit through the respiration signal collection channel.

[0064] The second analog switch: switches to select the respiration signal collection channel, first outputs the respiration excitation signal to the human body, generates the respiration feedback signal according to the impedance change of the human body, selects the II-lead respiration feedback signal input, and inputs it to the signal collection circuit through the first analog switch; at the same time, receives the respiration modulation signal output by the signal collection circuit.

[0065] The third analog switch: switches to select the ECG signal collection channel in the signal collection channel corresponding to two limb leads, and inputs the limb lead ECG signal to the signal collection circuit through the selected ECG signal collection channel, specifically, selects the II-lead ECG signal after filtering processing to input to the signal collection circuit for sampling.

[0066] The fourth analog switch: switches to select another limb lead as the output channel of the signal collection circuit, for example, connects the left upper limb lead, and the signal collection circuit obtains the right leg drive RLD signal through the right upper limb lead and the left leg lead, and the right leg drive RLD signal is output to the human body through the left upper limb lead channel as a common mode signal of the human body, thereby realizing the reduction of common mode interference and improving the common mode rejection ratio.

[0067] Among them, since the III-lead acquisition module closes the respiration modulation signal channel, the III-lead does not support the respiration function.

[0068] In some embodiments, when the signal collector 200 is identified as a four-electrode lead type, the four-electrode lead type includes a left upper limb lead, a right upper limb lead, a left leg lead, and a right leg lead; the left upper limb lead, the right upper limb lead, and the left leg lead are used to collect limb lead electrocardio signals.

[0069] It can be understood that when the signal collector 200 is of the four-electrode lead type, the right leg drive signal is no longer multiplexed to the left upper limb lead, the right upper limb lead, and the left leg lead for output, but an independent right leg lead is used. Taking II lead respiration / electrocardio as an example (other signals are similar), the switching principle of each analog switch in the four-electrode lead type is as follows:

[0070] The first analog switch: the position is downward, the respiration signal collection channel is selected, and the respiration feedback signal of the human body is input to the signal collection circuit through the respiration signal collection channel.

[0071] The second analog switch: the position is downward, the respiration signal collection channel is selected, the respiration excitation signal is first output to the human body, the respiration feedback signal is generated according to the impedance change of the human body, the II lead respiration feedback signal is selected for input, and is input to the signal collection circuit through the first analog switch; at the same time, the respiration modulation signal output by the signal collection circuit is received and output to the human body through the defibrillation protection circuit.

[0072] The third analog switch: the position is downward, the electrocardio signal collection channel in the signal collection channel corresponding to any two of the left upper limb lead, the right upper limb lead, and the left leg lead is selected, and the limb lead electrocardio signal is input to the signal collection circuit through the selected electrocardio signal collection channel. Specifically, the II lead electrocardio signal after filtering is selected for input to the signal collection circuit for sampling.

[0073] The fourth analog switch: the electrocardio signal collection channel in the signal collection channel corresponding to the other one of the left upper limb lead, the right upper limb lead, and the left leg lead is selected, and the limb lead electrocardio signal is input to the signal collection circuit through the selected electrocardio signal collection channel.

[0074] In some embodiments, when the signal collector 200 is of a five-electrode lead type, the five-electrode lead type includes a left upper limb lead, a right upper limb lead, a left leg lead, a right leg lead, and a chest lead; the left upper limb lead, the right upper limb lead, and the left leg lead are used to collect limb lead electrocardio signals, and the chest lead is used to collect chest lead electrocardio signals.

[0075] Specifically, the five-electrode lead type adds a chest lead compared to the four-electrode lead type, the chest lead can detect chest lead electrocardio signals of any part of the human body, and the position can be flexibly selected according to clinical needs. Taking II lead respiration / electrocardio as an example (other signals are similar), the following is explained:

[0076] The first analog switch: the position is downward, the respiratory signal acquisition channel is selected, and the respiratory feedback signal of the human body is input to the signal acquisition circuit through the respiratory signal acquisition channel.

[0077] The second analog switch: the position is downward, the respiratory signal acquisition channel is selected, the respiratory excitation signal is first output to the human body, the respiratory feedback signal is generated according to the impedance change of the human body, the II lead respiratory feedback signal is selected to be input, and is input to the signal acquisition circuit through the first analog switch; at the same time, the respiratory modulation signal output by the signal acquisition circuit is received, and is output to the human body through the defibrillation protection circuit.

[0078] The third analog switch: the position is downward, the electrocardio signal acquisition channel in the signal acquisition channel corresponding to any two of the left upper limb lead, the right upper limb lead, and the left leg lead is selected, and the electrocardio signal of the limb lead is input to the signal acquisition circuit through the selected electrocardio signal acquisition channel. Specifically, the II lead electrocardio signal after filtering processing is selected to be input to the signal acquisition circuit to complete sampling.

[0079] The fourth analog switch: the position is upward, the electrocardio signal acquisition channel in the signal acquisition channel corresponding to the other one of the left upper limb lead, the right upper limb lead, and the left leg lead is selected, and the electrocardio signal of the limb lead is input to the signal acquisition circuit through the selected electrocardio signal acquisition channel.

[0080] And, the right leg lead is controlled as an output channel of the signal acquisition circuit, and the right leg drive signal is applied to the human body through the output channel to reduce the common mode interference generated by the human body;

[0081] The chest lead is controlled as the electrocardio signal acquisition channel of the signal acquisition circuit to input the chest lead electrocardio signal to the signal acquisition circuit.

[0082] In some embodiments, when the signal acquisition device 200 is identified as a ten-electrode lead, the ten-electrode lead includes a left upper limb lead, a right upper limb lead, a left leg lead, a right leg lead, and six chest leads; the left upper limb lead, the right upper limb lead, and the left leg lead are used to acquire the electrocardio signal of the limb lead, and the six chest leads are used to acquire the electrocardio signal of the chest lead.

[0083] Specifically, the ten-electrode lead supports 12-lead input and does not support respiratory function. The analog switch is set as follows:

[0084] The first analog switch: the position is upward, the electrocardio signal acquisition channel in the signal acquisition channel corresponding to one of the six chest leads is selected, and the chest lead electrocardio signal is input to the signal acquisition circuit through the selected electrocardio signal acquisition channel. For example, the chest lead V6 signal is selected to be input to the signal acquisition circuit, and the respiratory monitoring function is closed.

[0085] The second analog switch: not in action due to the breathing monitoring function being turned off.

[0086] The third analog switch: in the down position, selects the ECG signal acquisition channel in the signal acquisition channel corresponding to any two of the left upper limb lead, the right upper limb lead and the left leg lead, and inputs the limb lead ECG signal to the signal acquisition circuit through the selected ECG signal acquisition channel. Specifically, the filtered II lead ECG signal is selected to be input to the signal acquisition circuit for sampling.

[0087] The fourth analog switch: in the up position, selects the ECG signal acquisition channel in the signal acquisition channel corresponding to the other of the left upper limb lead, the right upper limb lead and the left leg lead, and inputs the limb lead ECG signal to the signal acquisition circuit through the selected ECG signal acquisition channel.

[0088] In the above embodiment, the configuration of multiple analog switches is used to support the collection of different breathing waveforms and breathing rates of I lead (left arm lead-right arm lead) and II lead (left leg lead-right arm lead) through analog switch switching, meeting the needs of different populations for chest breathing (I lead) and abdominal breathing II lead.

[0089] In some embodiments, the circuit board 20 is also provided with a signal conditioning circuit for filtering out interference components in the physiological signal. Specifically, the signal low-pass filtering, such as RC filtering, is used to filter out high-frequency interference components in the ECG signal / pacing signal through a resistance-capacitance unit.

[0090] In some embodiments, the signal acquisition device 200 is provided with an anti-fake label; the ECG monitoring device is also provided with a label recognition module for reading the anti-fake label of the signal acquisition device 200 to perform anti-fake identification on the signal acquisition device 200.

[0091] It can be understood that the signal acquisition device 200 can also be divided into single-use signal acquisition device 200 and reusable signal acquisition device 200 according to the use case; when single-use, the signal acquisition device 200 can be identified for authenticity. It can be understood that the signal acquisition device 200 includes an ECG lead wire and a patch-type ECG sensor. Since the ECG lead wire is generally configured for reuse, the following will take the patch-type ECG sensor as an example to describe the anti-fake method.

[0092] In an example embodiment, the label identification module is further configured to identify the anti-counterfeit label in the patch-type electrocardio sensor, obtain identification information, production information and first ciphertext information in the anti-counterfeit label, and upload the identification information, the production information and the first ciphertext information to the central station; and the central station is configured to perform authenticity identification on the patch-type electrocardio sensor based on the identification information, the production information and the first ciphertext information. The first ciphertext information is encrypted by the identification information and the production information. The identification information is used to represent the uniqueness of the patch-type electrocardio sensor. The production information can include batch, manufacturing date, model and encryption information of the patch-type electrocardio sensor. The anti-counterfeit label is an NFC label.

[0093] In a specific implementation, in the manufacturing process of the patch-type electrocardio sensor, the manufacturer burns the production information to the anti-counterfeit label and uploads the corresponding information to the central station. The label identification module with an NFC antenna is configured in the electrocardio monitoring device 100, has an NFC card reader function, and can identify the anti-counterfeit label built-in the patch-type electrocardio sensor and obtain the unique identification UID of the patch-type electrocardio sensor, the production information and the first ciphertext information in the anti-counterfeit label. Then the obtained identification information, production information and first ciphertext information are uploaded to the central station. The central station decrypts the first ciphertext information to obtain the identification information and the production information, compares the decrypted identification information and production information with the identification information and production information identified from the anti-counterfeit label, and performs authenticity identification. Specifically, if one of the identification information and the production information is inconsistent, the patch-type electrocardio sensor is counterfeit; otherwise, it is real.

[0094] In this embodiment, by setting the anti-counterfeit label in the patch-type electrocardio sensor, the label identification module obtains the identification information, the production information and the first ciphertext information in the anti-counterfeit label, and uploads these information to the central station, so that the central station performs authenticity identification based on the identification information, the production information and the first ciphertext information, thereby ensuring the security of the patch-type electrocardio sensor.

[0095] In another example embodiment, the label identification module is further configured to identify the anti-counterfeit label in the patch-type electrocardio sensor, obtain identification information, production information and second ciphertext information in the anti-counterfeit label, and upload the identification information, the production information and the second ciphertext information to the central station; and the central station is further configured to obtain reserved information not contained in the anti-counterfeit label from a server in a networked state, perform authenticity identification on the patch-type electrocardio sensor based on the identification information, the production information, the second ciphertext information and the reserved information; and the second ciphertext information is encrypted by the identification information, the production information and the reserved information.

[0096] In a specific implementation, when the production information is burned into the anti-counterfeit label, the reserved information of a field is not burned into the label, but is only stored in the server. When encryption is performed, the second ciphertext information is obtained by jointly encrypting the identification information, the production information and the reserved information. Thus, after the central station decrypts the second ciphertext information to obtain the identification information, the production information and the reserved information, the identification information and the production information obtained by decryption can be compared with the identification information and the production information identified from the anti-counterfeit label. The reserved information needs to be obtained from the server through networking, and then the reserved information obtained by decryption is compared with the reserved information obtained from the server. According to the comparison results of the identification information, the production information and the reserved information, the authenticity identification result of the patch-type electrocardio sensor is determined. If one of the identification information, the production information and the reserved information is inconsistent, it indicates that the patch-type electrocardio sensor is fake. Otherwise, it is real.

[0097] In some embodiments, the encrypted information can also guarantee traceability and anti-counterfeiting effect through blockchain technology and regular cancellation. For example, after each patch-type electrocardio sensor is used, the related information of the patch-type electrocardio sensor is deleted from the server, and anti-counterfeiting is performed through cancellation.

[0098] In this embodiment, when the production information is burned into the anti-counterfeit label, the reserved information of a field is not burned into the label, but is only stored in the server. When encryption is performed, the second ciphertext information is obtained by jointly encrypting the identification information, the production information and the reserved information. When authenticity identification is performed, the reserved information in the server needs to be obtained through networking to complete the identification, and the anti-counterfeiting effect is further improved.

[0099] In some embodiments, the first housing 11 is further provided with a respiration detection circuit for collecting respiration signals. Specifically, the respiration detection circuit generates an excitation signal, applies the excitation signal to the collected object, and acquires respiration information of the collected object according to the respiration feedback signal of the collected object. In a specific implementation, the impedance method can be used for respiration monitoring. By giving a certain excitation signal to the human body, the excitation signal combines with the change of the chest volume during respiration to generate a respiration feedback electrical signal. By collecting the feedback information, the respiration rate and respiration waveform of the human body can be obtained, and the heart rate and waveform can be displayed through the host and remote central station software. The impedance method is used to detect respiration support I lead respiration LA-RA and II lead respiration LL-RA. Specifically, a high-frequency excitation square wave signal is first generated, and a high-frequency square wave modulation signal is generated through an internal circuit, such as 32 kHz. Through R1 and C1, the direct current waveform is converted into an alternating current waveform, and through the current limiting of R1, the current acting on the human body is reduced. In order to reduce the number of interfaces, the respiration channel excitation signal and the electrocardiogram signal / pacing signal share the same physical channel, such as the LA-RA channel. Then, the respiration feedback signal is modulated and demodulated. Due to the regular expansion and contraction of the chest volume during human respiration, corresponding to the human respiration action. When the excitation signal acts on the human body, the regular volume change of the chest appears as a regular change of the human body base resistance R3+ resistance δR. The regular voltage and current on δR reflect the change of the human respiration. After being conditioned by the anti-fibrillation resistance R2 and the 1-order HPF filter for alternating coupling and biasing to the intermediate power supply, it enters the internal circuit for demodulation processing, and finally obtains the real-time respiration waveform and respiration rate of the human body.

[0100] In some embodiments, the electrocardiogram monitoring device 100 is further provided with a motion detection sensor for detecting the motion state of the human body. Specifically, the motion state can include rest, sleep, motion, and fall. In actual application, the electrocardiogram monitoring device 100 can be equipped with a 6-axis motion sensor, including a 3-axis acceleration + 3-axis gyroscope, for monitoring the motion state of the human body.

[0101] In some embodiments, the circuit board 20 is also provided with a defibrillation circuit; the defibrillation circuit is used for voltage reduction processing of the physiological signal. Part of the defibrillation circuit is arranged in the signal collector 200, and a defibrillation resistance is arranged in the signal collector 200, which is used to dissipate the energy of defibrillation; another part is arranged in the electrocardiogram monitoring device 100, including a defibrillation chip and a protection circuit, and the defibrillation chip and the protection circuit combine to limit the current of the high-voltage pulse of defibrillation to a safe range. Specifically, the defibrillation function is mainly realized by two parts: the first part is located in the signal collector 200, and a defibrillation resistance is arranged therein to dissipate most of the energy of defibrillation in the form of heat; the second part is located in the electrocardiogram monitoring device 100, including a defibrillation chip and a secondary protection circuit, which combine to limit the current of the high-voltage pulse of defibrillation to a safe range. Among them, the defibrillation chip has the characteristics of small size, low leakage current and high repetition frequency, and its function is mainly used to quickly clamp the high-voltage pulse of 5000V defibrillation to about 10V ms level, and other voltages and energies are consumed through the defibrillation resistance of the first part; the secondary protection circuit further limits the current of the 10V signal to the acceptable range of the subsequent circuit according to the IO input range of the recorder internal chips, protects the normal work of the subsequent circuit, and can be realized by using ordinary resistance or anti-pulse resistance. In some embodiments, the defibrillation chip can be selected from lightning protection tubes or integrated chips. Considering the size requirement, an integrated chip can be used. It should be noted that the defibrillation function can only be realized in the repeatedly used electrocardiogram lead line. In this embodiment, in cooperation with the defibrillation resistance of the electrocardiogram signal collector 200, the electrocardiogram monitoring device 100 can realize the defibrillation function, protect the normal use of the electrocardiogram monitoring device 100, and at the same time not affect the defibrillation energy.

[0102] As shown in Figure 6 The electrocardiogram monitoring device 100 is also provided with an elastic touch area 104 and a charging interface 105, the elastic touch area 104 is used for receiving user pressing to realize event recording function, the charging interface 105 can support multiple charging modes, support flexible power supply during wearing, do not need to classify the electrocardiogram monitoring device 100 and the signal collector 200, and can realize super-long endurance of dynamic electrocardiogram acquisition.

[0103] In some embodiments, the circuit board 20 is provided with a charging interface; the shell is provided with a battery; and the battery is in conductive communication with an external power source through the charging interface.

[0104] In some embodiments, the charging is performed through the charging interface 105 by using an adapter and a customized USB Type-C data line.

[0105] In some embodiments, a charging device is also provided, which is provided with a plurality of charging slots, and the charging slots are used for charging the electrocardiogram monitoring device.

[0106] As shown in Figure 7As shown, the charging device includes a plurality of charger slots 90, and the charging slots 90 are adapted to the shape of the electrocardiogram monitoring device 100.

[0107] In practical applications, after the detachable battery assembly of the electrocardiogram monitoring device 100 is depleted, it can be detached and installed into the centralized charger slot for charging. The electrocardiogram monitoring device 100 can also be installed as a whole into the centralized charger slot, and the bottom patch-type electrocardiogram sensor interface can be used to charge the electrocardiogram monitoring device 100.

[0108] In some embodiments, the patch-type electrocardiogram sensor interface can adopt a pluggable design to support a variety of models of single-use and reusable patch-type electrocardiogram sensors and electrocardiogram lead wires, and can be designed to have an NFC wireless interface model identification function to support wireless NFC interface model identification and information management. This design can improve the compatibility of electrocardiogram lead wires and patch-type electrocardiogram sensors, and has the ability of wireless model identification and information management.

[0109] As shown in the Figure 1 The utility model also provides an electrocardiogram monitoring system 1, which comprises the electrocardiogram monitoring device 100 and the signal collector 200, realizes long-range acquisition and monitoring of electrocardiogram signals. The electrocardiogram monitoring device 100 is detachably installed on the signal collector 200 and is in conductive connection with the signal collector 200.

[0110] The technical features of the above embodiments can be combined in any way. To make the description concise, not all possible combinations of the technical features in the above embodiments are described, but as long as the combinations of the technical features do not exist contradictory, they should be considered as the scope of the present application.

[0111] The above embodiments only express several implementation manners of the utility model, and the description is more specific and detailed, but it should not be understood as a limitation on the scope of the utility model patent. It should be noted that for ordinary skilled persons in the art, without departing from the concept of the utility model, some modifications and improvements can be made, which are within the protection scope of the utility model. Therefore, the protection scope of the utility model patent should be subject to the appended claims.

Claims

1. An electrocardiographic monitoring device, characterized by The electrocardio monitoring device (100) is used for receiving physiological signals acquired by a signal collector (200); the electrocardio monitoring device (100) comprises a first shell (11) and a second shell (12) designed separately, the electrocardio monitoring device (100) is detachably installed on the signal collector (200), an NFC data collector is arranged in the second shell (12), the NFC data collector is used for identifying an NFC tag of the signal collector (200), and the NFC tag is used for storing a type of the signal collector (200); A circuit board (20) is further arranged in the first shell (11), a control circuit and a signal switching circuit are arranged on the circuit board (20), a switch control end of the signal switching circuit is connected with the control circuit, and a signal output end of the signal switching circuit is connected with a signal acquisition circuit; A conductive connecting piece (30) is further arranged on the second shell (12), one end of the conductive connecting piece (30) is conductively connected with a conductive contact (220) of the signal collector (200), and the other end of the conductive connecting piece (30) is connected with a signal input end of the signal switching circuit.

2. The electrocardiographic monitoring device of claim 1, wherein, The signal switching circuit comprises a first analog switch, a second analog switch, a third analog switch and a fourth analog switch, and the signal acquisition circuit comprises a signal acquisition channel; The control circuit is used for controlling the first analog switch, the second analog switch, the third analog switch and the fourth analog switch to select a signal acquisition channel; The control circuit is used for controlling the selected signal acquisition channel to input at least one acquired physiological signal to the signal acquisition circuit.

3. The electrocardiographic monitoring device of claim 2, wherein, The circuit board (20) further comprises a defibrillation circuit; and the defibrillation circuit is used for performing voltage reduction processing on the physiological signal.

4. The cardiac electrical monitoring device of claim 1, wherein, The circuit board (20) is provided with a charging interface; and a battery (40) is arranged on the second shell (12). The battery (40) is conductively communicated with an external power supply through the charging interface.

5. The electrocardiographic monitoring device of claim 4, wherein, The battery (40) is provided with a connecting structure, and the second shell (12) is provided with a mounting groove; and the battery (40) is mounted in the mounting groove through the connecting structure.

6. The cardiac electrical monitoring device of claim 1, wherein, The signal collector (200) is provided with an anti-fake label; The electrocardio monitoring device (100) further comprises a label identification module, which is used for reading the anti-fake label of the signal collector (200) to perform anti-fake identification on the signal collector (200).

7. The cardiac electrical monitoring device of claim 1, wherein, The first shell (11) is further provided with a respiration detection circuit, which is used for acquiring a respiration signal.

8. The cardiac electrical monitoring device of claim 1, wherein, The electrocardio monitoring device (100) is further provided with a motion detection sensor, which is used for detecting a motion state of a human body.

9. A charging device, characterized by The charging device is provided with a plurality of charging grooves (90), and the charging grooves (90) are used for charging the electrocardio monitoring device (100) according to any one of claims 1 to 8.

10. An electrocardiographic monitoring system characterized by, The electrocardio monitoring device (100) and the signal collector (200) are connected in conduction.

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