CN106562783B - Electrocardiogram measuring method and device - Google Patents
Electrocardiogram measuring method and device Download PDFInfo
- Publication number
- CN106562783B CN106562783B CN201610985835.6A CN201610985835A CN106562783B CN 106562783 B CN106562783 B CN 106562783B CN 201610985835 A CN201610985835 A CN 201610985835A CN 106562783 B CN106562783 B CN 106562783B
- Authority
- CN
- China
- Prior art keywords
- electrocardio
- signals
- signal
- activity
- charge signals
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0004—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the type of physiological signal transmitted
- A61B5/0006—ECG or EEG signals
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7225—Details of analog processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
Abstract
The invention discloses an electrocardio measuring method and device. The electrocardio-measuring method comprises the following steps: receiving at least two electrocardio-activity charge signals sent by at least two electrocardio-measuring probes in a wireless transmission mode; converting the at least two electrical charge signals into synchronized electrical charge signals; and calculating the electrocardiosignal of the human body according to the synchronous electrocardio-activity charge signal. According to the invention, the electrocardio-activity charge signals sent by the electrocardio-measuring probe in a wireless transmission mode are received, then the signals are synchronously processed to calculate and obtain real electrocardio signals, and a lead wire is not needed, so that the electrocardio signals with high quality can be obtained while the interference on the normal activity of human is reduced, no extra mechanical noise is generated, and the reliability is high.
Description
Technical Field
The invention relates to the field of medical instruments, in particular to an electrocardio measuring method and device.
Background
The electrocardiosignal is the projection of the electrophysiological activity of the heart on the surface of a human body, and specifically, K, Na and Ga ions enter or are discharged from a cell membrane in different activity periods of a cardiac pacing cell, so that potential differences are generated in different directions of the cell, which is the origin of electrocardio. All the cardiac pacemaking cells are superposed like small power supplies and show periodic potential variation along a specific direction, namely projections of electrocardiograms in different directions on the body surface. The projections in different directions are recorded, so that the change and conduction process of the electrocardio can be described.
The existing electrocardio measuring instrument converts the ion current of electrocardio into electron current through a body surface electrode, such as an Ag-AgCl electrode, thereby being suitable for measuring and recording by adopting the current electronic circuit technology. In order to better record electrocardiosignals, techniques such as Welson electrocardio and right leg driving are further developed, and the projection of the measurement signals corresponding to the electrocardio on the body surface is strictly defined through the arrangement of electrodes, so that a 'lead' system of the electrocardiosignals is formed. The most common electrocardiographic measurement lead system is the "conventional 12-lead". The connection mode of the conventional 12-lead electrocardiogram measurement is shown in fig. 1. Electrodes of four limbs (a left wrist LA, a right wrist RA, a left leg LL and a right leg RL) form limb leads, wherein signals of the left wrist LA, the right wrist RA and the left leg LL form a Welson central point through a specific resistance network after entering an electrocardio measuring instrument, and all measured electrode signals are potential differences of the electrodes and Welson electrocardio; correspondingly, the measurement signals are amplified, shaped and the like to synthesize a right leg driving signal which is loaded on the right leg RL, so that the influence of a common mode signal on the measurement is reduced; in addition, 6 electrodes positioned on the chest are arranged, and the projection and conduction conditions of the electrocardiosignals in the horizontal equal direction are correspondingly measured. These measurement signals described above together constitute the so-called "conventional 12-lead".
Similar to the conventional 12-lead, other lead systems for electrocardiographic measurement exist, but the ionic current of the electrocardiographic signal is converted into the electronic current of the measuring circuit by adopting the Ag-AgCl electrode and is invariable no matter how the ionic current is changed. And at least two electrode lines are required to form the measuring circuit. The two electrodes need to be distributed at the corresponding body surface tail ends of the two sides of the heart, and longer electrode signal wires are needed. For this reason, "resting" electrocardiographic measurement methods are used in situations such as exercise states or long-term monitoring, and there are many places where they are not suitable. The requirement of monitoring on electrocardio measurement signals is low, and when the conventional 12-lead connection is adopted, the electrode of the limb lead is not arranged at the tail end of the limb, but the tail end of the trunk is used; when measuring electrocardio under certain motion state, using electrode lead embedded in clothes; and so on.
Fig. 2 shows a weighing scale with an electrocardiographic measurement function. The measurement requires the person to be measured to hold the handle with his hand and step on a specific area with his bare foot. Fig. 3 shows the use mode of the intelligent terminal for measuring electrocardio through the back shell electrode. The electrode needs to be gripped by specific fingers of both hands of a person to be measured during the measurement.
The schemes can be used for measuring the electrocardio under specific conditions. But for the hands and even the limbs of the measured object in the liberation measurement process, no improvement is made. During the measurement, the two hands or the limbs of the tested person need to be fixed well according to the physical positions given by the instrument and equipment, and the tested person cannot move freely during the measurement. This is because these measurement principles all use the measurement principle of ion current-electron current conversion, and in order to obtain a stable measurement current, at least two electrode signal lines must be used: if the signal wire adopts a flexible wire, the long wire can obstruct the movement of the tested person; if the signal adopts the position of the fixed electrode, the limbs of the tested person are fixed by the relative position of the fixed electrode.
Disclosure of Invention
The invention aims to solve the technical problem that a lead wire used by the conventional electrocardiogram measuring equipment is easy to limit the normal activities of a person to be measured and is not suitable for long-term monitoring and measuring, thereby providing an electrocardiogram measuring method and a device.
In one aspect of the embodiments of the present invention, an electrocardiographic measurement method is provided, including: receiving at least two electrocardio-activity charge signals sent by at least two electrocardio-measuring probes in a wireless transmission mode; converting the at least two electrical charge signals into synchronized electrical charge signals; and calculating the electrocardiosignal of the human body according to the synchronous electrocardio-activity charge signal.
Optionally, converting the at least two electrical charge signals into synchronized electrical charge signals comprises: respectively extracting power frequency signals from the at least two electrocardio-activity charge signals; selecting a reference signal from the at least two electrocardio-activity charge signals, and calculating the time offset between a power frequency signal in other electrocardio-activity charge signals and a power frequency signal in the reference signal; and synchronizing the other electrocardio-activity charge signals with the reference signal according to the time offset to obtain the synchronized electrocardio-activity charge signals.
Optionally, selecting a reference signal from the at least two electrical charge signals, and calculating a time offset between a power frequency signal of the other electrical charge signals and a power frequency signal of the reference signal comprises: selecting the electrocardio-activity charge signal with the minimum initial phase of the power frequency signal as the reference signal; and calculating to obtain the time offset according to the phase offset of the power frequency signal in the other electrocardio-activity charge signals and the power frequency signal in the reference signal.
Optionally, before receiving at least two electrical charge signals of heart electrical activity sent by at least two electrocardiographic measurement probes by wireless transmission, the method comprises: and sending a starting acquisition signal to the at least two electrocardio measuring probes, wherein the starting acquisition signal is used for controlling the at least two electrocardio measuring probes to acquire electrocardio activity charge signals.
Optionally, the time interval from the receiving of the start acquisition signal to the start of signal acquisition by the at least two electrocardiographic measurement probes is less than or equal to one tenth of the period of the power frequency signal.
Optionally, the sampling rate of the at least two electrocardiographic measurement probes is 10 times of the power frequency.
In one aspect of the embodiments of the present invention, an electrocardiograph measurement apparatus is provided, including: the receiving unit is used for receiving at least two electrocardio-activity charge signals sent by at least two electrocardio-measuring probes in a wireless transmission mode; the conversion unit is used for converting the at least two electric charge signals of the heart electrical activity into synchronous electric charge signals of the heart electrical activity; and the calculating unit is used for calculating the electrocardiosignals of the human body according to the synchronous electrocardio-activity charge signals.
Optionally, the conversion unit comprises: the extraction module is used for respectively extracting power frequency signals from the at least two electrocardio-activity charge signals; the calculation module is used for selecting a reference signal from the at least two electrocardio-activity charge signals and calculating the time offset between a power frequency signal in other electrocardio-activity charge signals and a power frequency signal in the reference signal; and the synchronization module is used for synchronizing the other electrocardio-activity charge signals with the reference signal according to the time offset to obtain the synchronized electrocardio-activity charge signals.
Optionally, the calculation module comprises: the selection submodule is used for selecting the electrocardio-activity charge signal with the minimum initial phase of the power frequency signal as the reference signal; and the calculating submodule is used for calculating to obtain the time offset according to the phase offset of the power frequency signals in the other electrocardio-activity charge signals and the power frequency signals in the reference signals.
Optionally, the method further comprises: and the sending unit is used for sending a starting acquisition signal to the at least two electrocardio measuring probes, wherein the starting acquisition signal is used for controlling the at least two electrocardio measuring probes to acquire electrocardio activity charge signals.
According to the embodiment of the invention, the electrocardio-activity charge signals sent by the electrocardio-measuring probe in a wireless transmission mode are received and then are synchronously processed to calculate the real electrocardio-signals without adopting a lead wire, so that the electrocardio-signals with high quality can be obtained while the interference on the normal activity of human beings is reduced, no additional mechanical noise is generated, and the reliability is high.
Drawings
The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular descriptions of exemplary embodiments of the invention as illustrated in the accompanying drawings wherein like reference numbers generally represent like parts of exemplary embodiments of the invention.
FIG. 1 shows a conventional 12 lead electrocardiographic measurement connection;
FIG. 2 illustrates a weight scale with an electrocardiographic measurement function;
FIG. 3 shows the use of the intelligent terminal for measuring electrocardio through the back shell electrode;
FIG. 4 illustrates a smart wristband principle that can measure electrocardiograms;
FIG. 5 illustrates a schematic view of an electrocardiographic measurement probe in accordance with an embodiment of the present invention;
FIG. 6 shows a schematic of a charge sensing probe according to an embodiment of the present invention;
FIG. 7 is a schematic diagram of an amplifying circuit according to an embodiment of the present invention
FIG. 8 is a schematic view of another alternative ECG measurement probe in accordance with an embodiment of the invention;
FIG. 9 shows a schematic diagram of an electrocardiography measurement system in accordance with an embodiment of the present invention;
FIG. 10 is a flow chart of a method of measuring electrocardiography according to an embodiment of the present invention;
FIG. 11 shows a power frequency interference model for electrocardiographic measurements;
FIG. 12 is a schematic view of an electrocardiographic measurement device in accordance with an embodiment of the present invention;
FIG. 13 is a schematic diagram of an exemplary left wrist signal in accordance with an embodiment of the present invention;
FIG. 14 is a schematic diagram illustrating an exemplary left wrist signal in accordance with an embodiment of the present invention;
FIG. 15 is a schematic diagram showing the direct processing of the measurement signals to obtain "false" ECG signals;
FIG. 16 shows a power frequency signal extracted using an embodiment of the invention;
FIG. 17 shows the recovered ECG signal after synchronization with the power frequency signal.
Detailed Description
Preferred embodiments of the present invention will be described in more detail with reference to the accompanying drawings, in which preferred embodiments of the invention are shown. This invention may, however, be embodied in various forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
Before the embodiment of the present invention is introduced, an equivalent model of ion current-electron current of an electrocardiographic measurement electrode is introduced, as shown in fig. 4, in order to measure an electrocardiographic signal, in addition to a conversion mode of ion current-electron current, a charge sensor can be used to directly measure an ion charge signal of a specific part of a body, such as a limb end. The ion charge signal corresponding to the electrocardio measurement at any position of the limb tail does not depend on the measurement at any other position, so that the method has the basic condition of removing the electrocardio measurement lead wire.
Based on the above basic conditions, the electrocardiographic measurement method according to the embodiment of the present invention provides an electrocardiographic measurement probe and an electrocardiographic measurement system, but the electrocardiographic measurement method according to the embodiment of the present invention is not limited to be used in the electrocardiographic measurement probe and the electrocardiographic measurement system, and only one optional electrocardiographic measurement probe and system are provided here.
As shown in fig. 5, the electrocardiographic measurement probe includes: the charge induction detector 10 is used for detecting the corresponding electrocardio-activity charge signals of the human body part; the signal processor 20 is connected with the charge induction detector 10 and is used for processing the electrocardio-activity charge signal into a digital signal; the wireless transceiver 30 is used for transmitting the digital signals to the electrocardio processing terminal in a wireless transmission mode, wherein the electrocardio processing terminal generates human electrocardiosignals according to the received signals; and the microcontroller 40 is respectively connected with the signal processor 20 and the wireless transceiver 30 and is used for controlling the wireless transceiver 30 to transmit the digital signals to the electrocardio processing terminal in a wireless transmission mode.
When the electrocardiographic measurement probe according to the embodiment of the present invention is used, one side of the charge sensing probe 10 may be attached to a measurement portion of a human body, such as a wrist or an ankle. Each electrocardiograph measurement probe is used for measuring an electrocardiograph activity charge signal of a corresponding portion, and specifically, a charge sensing detector 10 is used for collecting signals, and then the collected electrocardiograph activity charge signals are transmitted to a signal processor 20 for signal processing, such as amplification, filtering, analog-to-digital conversion, and the like. The signal processor 20 sends the processed signal to the microcontroller 40, and the microcontroller 40 controls the wireless transceiver 30 to send the signal to the electrocardiograph processing terminal for generating an electrocardiograph signal.
In the embodiment of the invention, the electrocardio measuring probe and the electrocardio processing terminal carry out data transmission in a wireless transmission mode without adopting a lead wire, so that high-quality electrocardio signals can be obtained while the interference on the normal activities of human beings is reduced, no extra mechanical noise is generated, and the reliability is high.
It should be noted that the wireless transceiver of the embodiment of the present invention may be a self-contained antenna, or may also be an external antenna, so as to transmit a coded wireless signal.
Optionally, the signal processor 20 includes: the amplifying circuit is used for amplifying the electrocardio-activity charge signal; the filter is used for amplifying the electrocardio-activity charge signals; and the analog-to-digital converter is used for converting the electrocardio-activity charge signal into a digital signal.
The signal is amplified and filtered to improve the quality of the acquired signal and ensure the reliability of the electrocardio measurement. Since the acquired signal is usually an analog signal, the analog signal is converted into a digital signal by an analog-to-digital converter so that the microcontroller can recognize and process the digital signal.
In the above embodiments, before the electrical charge signal of cardiac activity is sent to the cardiac electrical processing terminal, the processed signal can still reflect the electrical signal of cardiac activity during each processing of the electrical charge signal of cardiac activity.
Alternatively, as shown in fig. 6, the charge induction probe 10 includes: the metal flat plate is connected with the amplifying circuit; and the shielding layer is covered on the metal flat plate and is used for shielding charges except the surface of the skin. For a metal plate with good shielding, when charges exist in a certain distance, the charges on the surface of the metal plate can be redistributed, so that the charges can be detected.
Alternatively, as shown in fig. 7, the amplifying circuit includes: and the same-direction input end of the operational amplifier is connected with the metal flat plate and is grounded through a resistor R3, and the reverse-direction input end of the operational amplifier is connected with the output end through a resistor R2 and is grounded through a capacitor C1. In order to have better charge detection sensitivity, instrumentation amplifiers with high input impedance and high amplification factor, i.e. operational amplifiers, are used. Corresponding to the configuration of fig. 7, the measurement of the human body's cardiac electrical charge, wherein the resistance R3 may be as high as 10G ohms. Optionally, the electrocardiographic measurement probe is disposed on a wrist strap or a wristwatch. The wrist band can be worn on the wrist or the ankle. The electric charge detection corresponding to the electrocardio-activities on the body surface is realized, and the electrocardio-signals can be measured by using two or more electric charge signals, such as two wrists and two ankles, to be synchronously measured.
In order to improve portability of the electrocardiographic measurement probe, as shown in fig. 8, the electrocardiographic measurement probe of the present embodiment further includes: a battery 50 for powering the charge sensing probe 10, the signal processor 20, the wireless transceiver 30 and the microcontroller 40.
In order to realize the purpose of removing the lead wire, the collected electrocardio-activity charge signals can be digitized, the charge measurement signals of two wrists, even two ankles and more positions can be sent to a receiver in a digitized form in a wireless transmission mode, and the receiver is placed on the body of a person to be measured or at some place with a reasonable communication distance from a patient, so that the lead wire between the charge measurement probes can be removed.
In another aspect of the embodiments of the present invention, there is also provided an electrocardiographic measurement system, as shown in fig. 9, the electrocardiographic measurement system includes: at least two electrocardio measuring probes 100 for detecting the corresponding electrocardio activity charge signals of the human body part; the electrocardio processing terminal 200 is wirelessly connected with the at least two electrocardio measuring probes 100 and is used for generating human electrocardiosignals according to the electrocardio activity charge signals detected by the at least two electrocardio measuring probes 100.
Further, the electrocardiogram processing terminal also comprises: the wireless transceiver is used for receiving an electrocardio-activity charge signal sent by the electrocardio measuring probe; the microcontroller is connected with the wireless transceiver and is used for generating a human body electrocardiosignal according to the electrocardio-activity charge signal received by the wireless transceiver.
Optionally, in order to ensure portability of the electrocardiograph measurement system, the electrocardiograph processing terminal further includes: and the battery is used for supplying power to the wireless transceiver and the microcontroller of the electrocardio measuring system.
The electrocardiograph measurement method provided by the embodiment of the present invention can be used in a leadless electrocardiograph measurement system, and is mainly executed by an electrocardiograph processing terminal, and specifically, as shown in fig. 10, the method includes:
step S101, at least two electrocardio-activity charge signals sent by at least two electrocardio-measuring probes in a wireless transmission mode are received.
The electrocardio-activity charge signals are acquired by the electrocardio-measuring probes, wherein each electrocardio-measuring probe acquires an electrocardio-activity charge signal and sends the electrocardio-activity charge signals to the electrocardio-processing terminal in a wireless transmission mode.
Step S102, at least two electric charge signals of the heart electrical activity are converted into synchronous electric charge signals of the heart electrical activity.
Because the electrocardio-activity charge signals collected by each electrocardio-measuring probe are asynchronous, after the electrocardio-activity charge signals are received by the electrocardio-processing terminal, the electrocardio-activity charge signals are synchronously processed and converted into synchronous electrocardio-activity charge signals, so that the electrocardio-signals can be obtained.
In the leadless electrocardio measuring system, the digitization of the signals collected by the electrocardio measuring probe depends on a local clock system, in other words, the charge signals of all parts of the body corresponding to the electrocardio activities sent to the leadless electrocardio processing terminal are asynchronous, the direct processing of the digitized signals is not meaningful, and the corresponding electrocardio signals cannot be obtained.
And step S103, calculating the electrocardiosignals of the human body according to the synchronous electrocardio-activity charge signals.
And calculating the synchronous electrocardio-activity charge signals by adopting subtraction processing and other modes to obtain electrocardio signals of the human body.
According to the embodiment of the invention, the electrocardio-activity charge signals sent by the electrocardio-measuring probe in a wireless transmission mode are received and then are synchronously processed to calculate the real electrocardio-signals without adopting a lead wire, so that the electrocardio-signals with high quality can be obtained while the interference on the normal activity of human beings is reduced, no additional mechanical noise is generated, and the reliability is high.
In order to obtain the synchronous electrocardial activity charge signal by the electrocardial processing terminal of the embodiment of the invention, a plurality of modes can be adopted. Such as:
1) the clock of the digital conversion of the electrocardio measuring probe is synchronized in a wireless mode instead of a local crystal oscillator. The mode can cause the power consumption of the wireless communication of the electrocardio measuring probe and the electrocardio processing terminal to be increased, the continuous working time is shortened, and even the measuring time can not meet the basic requirement, or the measured personnel is required to carry a battery with larger capacity; the circuit auxiliary circuit of the measuring probe is more auxiliary and at least needs a synchronous clock of KHz level; within a limited interval, it cannot be measured by allowing two or more persons to measure simultaneously, or a more complex system is required;
2) the clock for the digital conversion of the electrocardio measuring probe is solved by adopting a wireless synchronization and local phase-locked loop mode. The wireless synchronous clock signal of the electrocardio processing terminal does not need to exist all the time in the measuring process, but needs a certain time length, so that the clock of local digital conversion can be locked with high precision. Compared with the scheme 1), the requirement of wireless communication and power consumption are reduced, the problem of interference of measurement of a plurality of people in a limited interval can be solved in a time-sharing mode, but the digital clock of the charge measurement probe is very complex.
The normal environment in which human electrocardio measuring activities are positioned is considered to have power frequency interference (also called power line interference). Fig. 11 shows a power frequency interference model for electrocardiographic measurement, in which a 50Hz (our country, etc.) or 60Hz (us, japan, etc.) signal is present in the measured electrocardiographic signal. For the measurement in the same environment, the same human body and the same time period, the power frequency signal frequencies at different positions on the surface of the human body have high consistency. The power frequency signal in the charge electric signal of the electric charge and the electric activity can be separated, so that the electric charge signal of the electric charge and the electric activity can be synchronized with the lowest cost.
To this end, in an alternative embodiment, the step S102 of converting the at least two electrical charge signals into synchronized electrical charge signals includes: respectively extracting power frequency signals from at least two electrocardio-activity charge signals; selecting a reference signal from at least two electrocardio-activity charge signals, and calculating the time offset of a power frequency signal in other electrocardio-activity charge signals and a power frequency signal in the reference signal; and synchronizing the other electrocardio-activity charge signals with the reference signal according to the time offset to obtain synchronized electrocardio-activity charge signals.
Based on the consistency of the power frequency signals, in the embodiment, after the electrocardio-activity charge signals are received, the power frequency signals are extracted from the electrocardio-activity charge signals, so that the electrocardio-activity charge signals are synchronized by using time offset between the power frequency signals, and the power consumption is lower, so that the hardware cost is not required to be increased.
Further, selecting a reference signal from at least two electrical charge signals, and calculating the time offset between the power frequency signal of the other electrical charge signals and the power frequency signal of the reference signal comprises: selecting the electrocardio-activity charge signal with the minimum initial phase of the power frequency signal as a reference signal; and calculating to obtain time offset according to the phase offset of the power frequency signals in the other electrocardio-activity charge signals and the power frequency signals in the reference signals.
When the power frequency signal is used for synchronization, the electrocardio-active charge with the minimum initial phase of the power frequency signal is preferably used as a reference signal, and the reference signal is used as a synchronization reference, so that the actual acquisition time offset can be obtained according to the phase offset of the power frequency signal, and further, the signal synchronization is realized.
Optionally, in this embodiment, before step S101, the method includes: and sending a starting acquisition signal to the at least two electrocardio measuring probes, wherein the starting acquisition signal is used for controlling the at least two electrocardio measuring probes to acquire electrocardio activity charge signals.
Triggering of the electrocardio measuring probe is triggered by the electrocardio processing terminal, and particularly, a broadcast mode is adopted to send a starting acquisition signal to all charge measuring terminals; the electrocardio measuring probe starts measurement and collection according to the received collection starting signal, and for better synchronization signals, the time interval from the reception of the broadcast signal to the start of measurement and collection of the electrocardio measuring probe is required to be controlled within 1/10 of the power frequency signal period, for example, for 50Hz power, one tenth of the time is 2ms, which is easy to realize for the current microprocessor system. The electrocardio measuring probe starts measurement and acquisition and sends the digitized measuring result to the electrocardio processing terminal. The electrocardio measuring probe has high quantization precision, such as 21-24 bits, and for physiological signals, the analog-to-digital converter is commonly applied and has low power consumption.
And the electrocardio processing terminal extracts a power frequency signal from the received signals of the electrocardio measuring probes and fits the power frequency signal. In order to better realize the data processing, the signal sampling rate of the electrocardio measuring probe is 10 times of the power frequency, namely 500Hz or above. This is also a reasonable indicator for current analog-to-digital converters of physiological signals.
According to the extracted power frequency signal, a signal acquired by any electrocardio measuring probe can be selected as a reference, and the deviation of the power frequency signals of other charge detection terminal signals is calculated, wherein the deviation reflects the asynchrony between the signals of all paths. And selecting the charge detection terminal with the minimum initial phase as a reference, so that the signals of other charge detection terminals can obtain the actual acquisition time offset according to the phase offset of the power frequency signal. And (3) interpolating the data of other charge detection terminals by using the time point of the reference charge detection terminal to obtain a synchronous multi-channel charge measurement signal.
On the basis, a real signal can be obtained. Therefore, not only the lead wire between the electrocardio measuring probes is removed, but also the synchronous measurement is realized, thereby the electrocardio signals can be recovered by using the data of each charge measuring terminal.
An embodiment of the present invention further provides an electrocardiograph measurement apparatus, which may be used to execute the electrocardiograph measurement method according to the embodiment of the present invention, and specifically may be implemented by the above-mentioned electrocardiograph processing terminal, as shown in fig. 12, the apparatus includes: a receiving unit 121, a converting unit 122 and a calculating unit 123.
The receiving unit 121 is configured to receive at least two electrical charge signals of cardiac electrical activity sent by at least two cardiac electrical measurement probes in a wireless transmission manner.
The electrical charge signals of the electrocardiographic activity are acquired by the electrocardiographic measurement probes, wherein each electrocardiographic measurement probe acquires one electrical charge signal of the electrocardiographic activity and sends the electrical charge signal to the receiving unit 121 in a wireless transmission mode.
The converting unit 122 is configured to convert the at least two electrical charge signals into synchronized electrical charge signals.
Because the electrocardiographic activity charge signals acquired by the electrocardiographic measurement probes are asynchronous, after receiving a plurality of electrocardiographic activity charge signals, the conversion unit 122 performs synchronous processing on the electrocardiographic activity charge signals and converts the electrocardiographic activity charge signals into synchronous electrocardiographic activity charge signals so as to obtain electrocardiographic signals.
In the leadless electrocardio measuring system, the digitization of the signals collected by the electrocardio measuring probe depends on a local clock system, in other words, the charge signals of all parts of the body corresponding to the electrocardio activities sent to the leadless electrocardio processing terminal are asynchronous, the direct processing of the digitized signals is not meaningful, and the corresponding electrocardio signals cannot be obtained.
The calculating unit 123 is configured to calculate an electrocardiographic signal of the human body according to the synchronized electrocardiographic activity charge signal.
And calculating the synchronous electrocardio-activity charge signals by adopting subtraction processing and other modes to obtain electrocardio signals of the human body.
According to the embodiment of the invention, the electrocardio-activity charge signals sent by the electrocardio-measuring probe in a wireless transmission mode are received and then are synchronously processed to calculate the real electrocardio-signals without adopting a lead wire, so that the electrocardio-signals with high quality can be obtained while the interference on the normal activity of human beings is reduced, no additional mechanical noise is generated, and the reliability is high.
In an alternative embodiment, the conversion unit comprises: the extraction module is used for respectively extracting power frequency signals from the at least two electrocardio-activity charge signals; the calculation module is used for selecting a reference signal from at least two electrocardio-activity charge signals and calculating the time offset between a power frequency signal in other electrocardio-activity charge signals and a power frequency signal in the reference signal; and the synchronization module is used for synchronizing other electrocardio-activity charge signals with the reference signal according to the time offset to obtain synchronized electrocardio-activity charge signals.
Based on the consistency of the power frequency signals, in the embodiment, after the electrocardio-activity charge signals are received, the power frequency signals are extracted from the electrocardio-activity charge signals, so that the electrocardio-activity charge signals are synchronized by using time offset between the power frequency signals, and the power consumption is lower, so that the hardware cost is not required to be increased.
Further, the calculation module includes: the selection submodule is used for selecting the electrocardio-activity charge signal with the minimum initial phase of the power frequency signal as a reference signal; and the calculating submodule is used for calculating to obtain time offset according to the phase offset of the power frequency signals in the other electrocardio-activity charge signals and the power frequency signals in the reference signals.
When the power frequency signal is used for synchronization, the electrocardio-active charge with the minimum initial phase of the power frequency signal is preferably used as a reference signal, and the reference signal is used as a synchronization reference, so that the actual acquisition time offset can be obtained according to the phase offset of the power frequency signal, and further, the signal synchronization is realized.
Optionally, in this embodiment, the apparatus further includes: and the transmitting unit is used for transmitting a starting acquisition signal to the at least two electrocardio measuring probes, wherein the starting acquisition signal is used for controlling the at least two electrocardio measuring probes to acquire the electrocardio activity charge signals.
Triggering of the electrocardio measuring probe is triggered by a sending unit, and specifically, a broadcast mode is adopted to send a starting acquisition signal to all charge measuring terminals; the electrocardio measuring probe starts measurement and collection according to the received collection starting signal, and for better synchronization signals, the time interval from the reception of the broadcast signal to the start of measurement and collection of the electrocardio measuring probe is required to be controlled within 1/10 of the power frequency signal period, for example, for 50Hz power, one tenth of the time is 2ms, which is easy to realize for the current microprocessor system. The electrocardio measuring probe starts measurement and acquisition and sends the digitized measuring result to the electrocardio processing terminal. The electrocardio measuring probe has high quantization precision, such as 21-24 bits, and for physiological signals, the analog-to-digital converter is commonly applied and has low power consumption.
And the electrocardio processing terminal extracts a power frequency signal from the received signals of the electrocardio measuring probes and fits the power frequency signal. In order to better realize the data processing, the signal sampling rate of the electrocardio measuring probe is 10 times of the power frequency, namely 500Hz or above. This is also a reasonable indicator for current analog-to-digital converters of physiological signals.
Taking two electrocardiographic measurement probes as an example, fig. 13 to 17 show the process of recovering electrocardiographic signals by using the method of the present invention. FIG. 13 shows a left wrist signal using the charge measurement terminal of the present invention. FIG. 14 shows a right wrist signal using the charge measurement terminal of the present invention. FIG. 15 shows the direct processing of the measured signal using a charge measurement terminal to obtain a "false" ECG signal. By this processing, we can see that no meaningful electrocardiosignal is obtained for different measurements. Fig. 16 shows a power frequency signal extracted using the charge measurement terminal signal of the present invention. FIG. 17 shows the recovered ECG signal after synchronization with the power frequency signal.
All changes, equivalents, and modifications that come within the spirit and scope of the invention are desired to be protected by the following claims.
Claims (8)
1. An electrocardiographic measurement method, comprising:
receiving at least two electrocardio-activity charge signals sent by at least two electrocardio-measuring probes in a wireless transmission mode;
converting the at least two electrical charge signals into synchronized electrical charge signals; and
calculating an electrocardiosignal of the human body according to the synchronous electrocardio-activity charge signal;
wherein converting the at least two electrical charge signals into synchronized electrical charge signals comprises:
respectively extracting power frequency signals from the at least two electrocardio-activity charge signals;
selecting a reference signal from the at least two electrocardio-activity charge signals, and calculating the time offset between a power frequency signal in other electrocardio-activity charge signals and a power frequency signal in the reference signal;
and synchronizing the other electrocardio-activity charge signals with the reference signal according to the time offset to obtain the synchronized electrocardio-activity charge signals.
2. The method of claim 1, wherein selecting a reference signal from the at least two electrical charge signals for cardiac activity, and wherein calculating the time offset between a power frequency signal of the other electrical charge signals and a power frequency signal of the reference signal comprises:
selecting the electrocardio-activity charge signal with the minimum initial phase of the power frequency signal as the reference signal;
and calculating to obtain the time offset according to the phase offset of the power frequency signal in the other electrocardio-activity charge signals and the power frequency signal in the reference signal.
3. The electrocardiograph measurement method according to claim 1 or 2, wherein before receiving at least two electrocardial activity charge signals transmitted by at least two electrocardiograph measurement probes by wireless transmission, the method comprises:
and sending a starting acquisition signal to the at least two electrocardio measuring probes, wherein the starting acquisition signal is used for controlling the at least two electrocardio measuring probes to acquire electrocardio activity charge signals.
4. The electrocardiographic measurement method according to claim 3, wherein the time interval from the reception of the start signal to the start of signal acquisition by the at least two electrocardiographic measurement probes is less than or equal to one tenth of the period of the power frequency signal.
5. The electrocardiographic measurement method according to claim 3, wherein the sampling rate of the at least two electrocardiographic measurement probes is 10 times the power frequency.
6. An electrocardiographic measurement device, comprising:
the receiving unit is used for receiving at least two electrocardio-activity charge signals sent by at least two electrocardio-measuring probes in a wireless transmission mode;
the conversion unit is used for converting the at least two electric charge signals of the heart electrical activity into synchronous electric charge signals of the heart electrical activity; and
the computing unit is used for computing the electrocardiosignals of the human body according to the synchronous electrocardio-activity charge signals; wherein the conversion unit comprises:
the extraction module is used for respectively extracting power frequency signals from the at least two electrocardio-activity charge signals;
the calculation module is used for selecting a reference signal from the at least two electrocardio-activity charge signals and calculating the time offset between a power frequency signal in other electrocardio-activity charge signals and a power frequency signal in the reference signal;
and the synchronization module is used for synchronizing the other electrocardio-activity charge signals with the reference signal according to the time offset to obtain the synchronized electrocardio-activity charge signals.
7. The electrocardiographic measurement device of claim 6 wherein the computing module comprises:
the selection submodule is used for selecting the electrocardio-activity charge signal with the minimum initial phase of the power frequency signal as the reference signal;
and the calculating submodule is used for calculating to obtain the time offset according to the phase offset of the power frequency signals in the other electrocardio-activity charge signals and the power frequency signals in the reference signals.
8. The electrocardiographic measurement device according to claim 6 or 7, further comprising:
and the sending unit is used for sending a starting acquisition signal to the at least two electrocardio measuring probes, wherein the starting acquisition signal is used for controlling the at least two electrocardio measuring probes to acquire electrocardio activity charge signals.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610985835.6A CN106562783B (en) | 2016-11-09 | 2016-11-09 | Electrocardiogram measuring method and device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610985835.6A CN106562783B (en) | 2016-11-09 | 2016-11-09 | Electrocardiogram measuring method and device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106562783A CN106562783A (en) | 2017-04-19 |
| CN106562783B true CN106562783B (en) | 2020-05-15 |
Family
ID=58540783
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201610985835.6A Expired - Fee Related CN106562783B (en) | 2016-11-09 | 2016-11-09 | Electrocardiogram measuring method and device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN106562783B (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109581936A (en) * | 2018-12-31 | 2019-04-05 | 南京茂森电子技术有限公司 | A kind of multisensor multi channel signals synchronous and method |
| CN110327038B (en) * | 2019-05-08 | 2021-11-16 | 京东方科技集团股份有限公司 | Electrocardio acquisition circuit, equipment, method and system |
| CN116602643B (en) * | 2023-07-20 | 2023-11-17 | 成都晨电智能科技有限公司 | Sampling method and circuit for power frequency interference resistant signal and double-electrode heart rate sensor |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2437293Y (en) * | 2000-08-23 | 2001-07-04 | 广东省科学院自动化工程研制中心 | Electrocardial signal acquisition device |
| CN1820703A (en) * | 2006-01-26 | 2006-08-23 | 中国人民解放军空军航空医学研究所 | Measuring method and system for achieving blood pressure continuous measurement of pulse wave conduction time |
| CN104931782A (en) * | 2015-06-16 | 2015-09-23 | 江苏理工学院 | Remote asynchronous power frequency signal phase difference measurement method and system |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2007014541A (en) * | 2005-07-07 | 2007-01-25 | Toshiba Corp | Ultrasonic diagnostic equipment |
| US20080306348A1 (en) * | 2007-06-06 | 2008-12-11 | National Yang-Ming University | Miniature wireless apparatus for recording physiological signals of humans and use thereof |
-
2016
- 2016-11-09 CN CN201610985835.6A patent/CN106562783B/en not_active Expired - Fee Related
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2437293Y (en) * | 2000-08-23 | 2001-07-04 | 广东省科学院自动化工程研制中心 | Electrocardial signal acquisition device |
| CN1820703A (en) * | 2006-01-26 | 2006-08-23 | 中国人民解放军空军航空医学研究所 | Measuring method and system for achieving blood pressure continuous measurement of pulse wave conduction time |
| CN104931782A (en) * | 2015-06-16 | 2015-09-23 | 江苏理工学院 | Remote asynchronous power frequency signal phase difference measurement method and system |
Also Published As
| Publication number | Publication date |
|---|---|
| CN106562783A (en) | 2017-04-19 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| KR101448106B1 (en) | Analisys Method of Rehabilitation status using Electromyogram | |
| EP3038523B1 (en) | Contactless electrocardiography | |
| EP2670295B1 (en) | Health monitoring | |
| EP2676604B1 (en) | Real time QRS duration measurement in electrocardiogram | |
| CN110327038B (en) | Electrocardio acquisition circuit, equipment, method and system | |
| US20090048526A1 (en) | Apparatus for monitoring a person's heart rate and/or heart rate variation; wrist-watch comprising the same | |
| JP5889197B2 (en) | Body movement monitoring device | |
| WO2013155196A2 (en) | Ecard ecg monitor | |
| CA3021919C (en) | Systems, articles and methods for cardiology sensory technology | |
| WO2017090732A1 (en) | Respiratory estimation method and device | |
| US20140107501A1 (en) | Wireless multi-sensor platform for continuous real-time monitoring of cardiovascular respiratory dynamics | |
| CN210612114U (en) | Vibration sensing device, blood pressure measuring device and cardiopulmonary efficiency monitoring device | |
| CN106562783B (en) | Electrocardiogram measuring method and device | |
| CN101234016A (en) | Physiological parameter measuring apparatus | |
| Safronov et al. | Mobile ecg monitoring device with bioimpedance measurement and analysis | |
| EP2701587A1 (en) | Ecg mat | |
| JP2023099105A (en) | Electrocardiogram measurement method and system using wearable device | |
| JP2001299712A (en) | Long-time biological monitor | |
| Aboalseoud et al. | Wireless ECG monitoring system for telemedicine application | |
| Paukkunen et al. | A system for detection of three-dimensional precordial vibrations | |
| CN106308788B (en) | Portable electrocardio monitoring facilities | |
| KR20080084879A (en) | System for measuring physiological signal | |
| CN207101270U (en) | A kind of electrocardio measuring probe and system | |
| Gatouillat et al. | Evaluation of a real-time low-power cardiorespiratory sensor for the IoT | |
| Lim et al. | A Study on a Healthcare System Using Smart Clothes |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20200515 Termination date: 20211109 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |