JP3231283B2 - Multi-lead electrocardiogram transmitter and its receiver - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a telemeter system for simultaneously transmitting and receiving a plurality of electrocardiograms by radio, and more particularly to a multi-lead electrocardiogram transmitter for compressively transmitting an electrocardiogram and its receiver.

[0002]

2. Description of the Related Art Conventionally, in the radio transmission for an ECG monitor, electrocardiogram transmission of one or two channels has been mainly used mainly because of a relationship between a radio bandwidth used and a data amount required for the ECG transmission. To monitor multi-channel electrocardiograms, an expanded radio band is used, and radio monitors of multi-lead electrocardiograms are not widely used except for special research purposes.

[0003] On the other hand, there is an increasing demand for multi-lead wireless monitors due to the importance of arrhythmia monitors, but radio wave resources are limited and realization in a narrow band is desired. In order to reduce the bandwidth, it is necessary to improve the transmission capacity per band and simultaneously compress the electrocardiogram effectively to reduce the actual transmission volume.

Many methods for compressing an electrocardiogram have been devised on the premise of application to a Holter electrocardiograph. As compression techniques, a reversible compression method that can completely restore original data and an irreversible compression method that realizes high compression based on errors at the time of restoration are known. In the medical world, it is often difficult to evaluate a clinically acceptable error, so a lossless compression method is often selected.

As a reversible compression method, a method using a variable length code is generally known. This is to improve the compression ratio within a certain section by assigning a code having a short code length to data having a statistically high frequency of appearance. In the case of compression using a variable code length, it is important for the target data not to vary statistically in order to improve the compression ratio. When digitizing a waveform signal such as an electrocardiogram, if the signal is as flat as possible and has no change, the compression ratio is improved.

[0006] A typical electrocardiogram has a feature that a steep change seen in a QRS is periodically repeated, and a heartbeat removal method using a QRS template is known as a method for achieving high compression. In this method, substantially flat data excluding the QRS is created by using a difference between a QRS portion and a template prepared in advance. An outline of the operation of the method is shown in FIG. S2 is the original waveform of the electrocardiogram, T2 is the QRS template, S2-T2
Is a differential waveform, the data amplitude of which is smaller than that of the original waveform (S2), thereby improving the compression ratio.

[0007] As shown in JP-A-6-237909, a fixed template is used as a QRS template, and in JP-A-6-237909, the compression ratio is degraded by updating the QRS template when an arrhythmia occurs. Methods to prevent this have been proposed.

FIG. 6 shows a conventional technique using a QRS template. In the related art, electrocardiogram data is temporarily stored, a heartbeat is detected from the electrocardiogram data, and a process of reducing a template (T1, T2) value prepared in advance for the heartbeat portion is performed.

[0009]

However, the prior art has the following problems. The conventional compression method based on heartbeat removal is based on the premise that a heartbeat is detected, and compressed data cannot be determined until data necessary for heartbeat detection is accumulated. Assuming that the electrocardiogram is wirelessly transmitted and monitored, the time required for data storage increases the delay time of data transmission, and significantly impairs the real-time property which is a basic function of the patient monitor. In addition, incorporating the heartbeat detection function increases the circuit scale and the power consumption, so that it is difficult to achieve compatibility with portability when applied to a wireless device.

Further, when a fixed template is used as the QRS template, there is a problem that the compression ratio is deteriorated when the QRS pattern changes due to arrhythmia or the like. In the method of preventing the deterioration of the compression ratio by updating the QRS template when an arrhythmia occurs, in the real-time wireless transmission, the real-time transmission is temporarily suspended if the temporary increase in the transmission amount accompanying the template transmission cannot be absorbed Inevitably, it impairs continuity, which is a fundamental characteristic of a patient monitor.

The factor that actually lowers the ECG data compression rate is not limited to QRS, but includes various factors such as a pacemaker signal, noise due to electrode state and body movement, and the like.
In the prior art, when electrocardiogram data is temporarily stored, a heartbeat is detected from the data, and processing for reducing the template (T1, T2) value prepared in advance for the heartbeat portion is performed, as shown in FIG. ) Is noise, there is a problem that the difference (S1-T2) from the template increases the signal amplitude.

SUMMARY OF THE INVENTION The present invention has been made in view of the above problems, and has as its object to provide a telemeter system for transmitting and receiving electrocardiograms of a plurality of leads simultaneously by radio, thereby efficiently compressing electrocardiogram data without delay time. An object of the present invention is to provide a multi-lead ECG transmitter and a receiver for transmitting the same.

[0013]

SUMMARY OF THE INVENTION An object of the present invention is to provide a multi-lead electrocardiogram transmitter for simultaneously transmitting a plurality of lead electrocardiograms by radio, wherein a difference between a plurality of electrocardiogram signals is obtained. And a signal transmitting means for transmitting the compressed differential signal. According to a second aspect of the present invention, there is provided the multi-lead electrocardiogram transmitter according to the first aspect, wherein the difference calculating means calculates a difference between electrocardiogram signals induced from adjacent electrodes. The gist of the present invention according to claim 3 is a mounting abnormality detecting unit that detects an abnormal mounting of the electrode, an abnormal signal deleting unit that deletes an electrocardiogram signal derived from the electrode detected by the mounting abnormal detection unit, The multi-lead electrocardiogram transmitter according to claim 1 or 2, further comprising: Claim 4
According to the gist of the present invention, the difference calculation means outputs the reference guidance data input from the electrode as it is, calculates the difference between the guidance data output from the adjacent electrodes, and outputs the subtractor. It consists in a multi-lead electrocardiogram transmitter according to any one of claims 1 to 3, further comprising a. The gist of the present invention described in claim 5 is that the mounting abnormality detecting means includes an electrode abnormality detecting unit that detects an electrode abnormality by checking the amplitude of an electrode detection signal. It consists in a multi-lead electrocardiogram transmitter according to any one of 4. The gist of the present invention according to claim 6, wherein the abnormal signal deleting means includes an electrocardiogram data selecting section for deleting lead data from the electrode determined to be abnormal by the electrode abnormal detecting section. Claim 1
6. A multi-lead electrocardiogram transmitter according to any one of claims 1 to 5. The gist of the present invention as set forth in claim 7, is that the signal transmitting means encodes the data output from the subtractor, and modulates the encoded data into a radio signal by a digital modulation method. further comprising a modulation unit for applying a resides in a multi-lead electrocardiogram transmitter according to any one of claims 1 to 6, wherein. The gist of the present invention according to claim 8 is a multi-lead electrocardiogram transmitter that simultaneously transmits a plurality of lead electrocardiograms by wireless, wherein the limb electrode and the six chest electrodes and one of the limb electrodes are provided. A differential amplifier for removing noise by inputting a signal obtained by removing an RF electrode serving as a common ground from all electrodes including the limb electrode and the chest electrode, using an output from the LF electrode as a reference signal for a difference, An electrode abnormality detecting unit for detecting an electrode abnormality by checking the amplitude of a signal for use, an A / D converter for digitizing an output signal from the differential amplifier, and a chest electrode normally mounted based on the electrode abnormality detection information An electrocardiogram data selection unit for selecting and rearranging the lead data from, a subtractor that outputs the reference lead data as it is, calculates and outputs a difference between lead data from adjacent electrodes, and output data from the subtractor. The difference between the sample values is calculated and an encoding unit that assigns a variable length code,
A multi-lead electrocardiogram transmitter includes a transmission packet synthesizer that assembles encoded data into a packet together with electrode abnormality information, and a modulator that modulates a radio signal by a digital modulation method. The gist of the present invention according to claim 9 is a multi-lead electrocardiogram receiver for receiving a plurality of lead electrocardiograms transmitted simultaneously by radio, and demodulates a received signal into digital data by a demodulation method corresponding to a transmission side. A demodulator, a decoder for separating and extracting information on electrode abnormalities and encoded ECG data according to the packet structure, a decoder for restoring the extracted ECG data to 12-bit data, and an operation for each data By performing the processing, an induction synthesizing unit that synthesizes the standard 12-lead signal, and a D / A that converts the synthesized standard 12-lead signal into an analog waveform
A multi-lead electrocardiogram receiver characterized by comprising a converter and a recorder for recording data converted into an analog waveform by the D / A converter. The gist of the present invention according to claim 10 is an electrocardiogram data transmission method for simultaneously transmitting an electrocardiogram of a plurality of leads by radio, wherein a difference between electrocardiogram signals induced from the electrodes is taken as a difference signal. An ECG data transmission method for compressing a signal and transmitting the compressed difference signal. The gist of the present invention described in claim 11 is that the output of the differential amplifier is connected to an electrode abnormality detection unit, and the electrode abnormality detection unit detects the electrode abnormality by checking the amplitude of the electrode detection signal. The information is sent to the transmission packet synthesizer, and the information data relating to the electrode abnormality is used to control the selector and to delete the guidance data from the abnormal electrode, and encodes the II and III guidance data and the output data of the subtractor. Input to the encoding unit, the encoding unit calculates the difference from the value at the previous sampling, assigns a variable-length code for data compression, and encodes the encoded data with information on electrode anomalies etc. 2. A radio signal is modulated by a digital modulation system in a modulation unit and transmitted through an antenna.
0). The gist of the present invention according to claim 12 is an electrocardiogram data receiving method for receiving an electrocardiogram of a plurality of leads transmitted simultaneously by radio, wherein a received signal is converted into digital data in a demodulation method corresponding to a transmission side by a demodulation unit. The signal is demodulated and separated by a decoding unit into information relating to electrode abnormalities and encoded ECG data in accordance with the packet structure.
The data is restored to the bit data and output to the induction synthesizing unit.
An electrocardiogram data receiving method is characterized in that lead signals are combined, the combined standard 12 lead signal is converted into an analog waveform by a D / A converter, and recorded by a recorder.

[0014]

Embodiments of the present invention will be described below in detail with reference to the drawings. As shown in FIG. 1, a multi-lead electrocardiogram transmitter according to the present embodiment includes an electrode 1, a differential amplifier 2 for electrocardiographic lead, an A / D converter 3, an encoding section 4, and an electrocardiogram data selection section. 5, a subtractor 6, an electrode abnormality detector 7, a transmission packet synthesizer 8, a modulator 9, and an antenna 10.

As shown in FIG. 2, the multi-lead electrocardiogram receiver is roughly composed of a demodulator 11, a decoder 12, a decoder 13, a synthesizer 14, a DA 15, and a recorder 16.

FIG. 3 shows limb electrodes (RA, LA, RF, L
The state which is attached to a living body using six chest electrodes (C1 to C6) in addition to F) is shown.

[0017] In FIG. 1, the electrodes except the R F electrode 1
Is connected to the input of the differential amplifier 2 using the output from the LF electrode as a difference reference, and II and II are connected from the limb electrode.
The lead I is derived, and for the chest electrode, the deviation of each electrode 1 with respect to LF is derived. The output signal of the differential amplifier 2 is digitized by the A / D converter 3 at 12 bits and 300 Hz. The electrocardiogram is amplified by a differential amplifier. The frequency band of the electrocardiogram (up to 100 Hz) and the commercial AC power (50 or
(60 Hz) are close to each other, and if they are separated by frequency, they will affect the electrocardiogram waveform, and it is difficult to lower the impedance of the electrode 1 (skin impedance and electrode / skin contact impedance). Since it has to be received with a high input impedance, noise entering in the common mode is eliminated as a differential configuration.

In addition, since the electrocardiogram cannot be measured unless the electrode 1 is properly mounted, an electrode abnormality detecting function is provided.
A detection signal (CW of several kHz) out of the ECG band is injected, and the electrode 1 is determined based on the amplitude of the detection signal appearing at the output of the differential amplifier.
Are connected normally, and if the electrode 1 is disconnected, the signal amplitude becomes smaller. That is, the output of the differential amplifier 2 becomes an electrocardiogram to be measured.

The digitized II and III lead data is input to the encoding unit 4 as it is, and is encoded.
The lead data from the chest electrode passes through the electrocardiogram data selection unit 5, is rearranged into only electrodes that are normally mounted, and is input to the subtractor 6. The electrocardiogram data selector 5 has six input signals (S1, S2, S3, S4, S5, S
From 6), select data based on electrode abnormality detection information,
If all data is from a normal electrode, it is output as it is. For example, if the third input (S3) is from an abnormal electrode, this is deleted (S1, S2, S
4, S5, S6, S6). The subtractor 6 outputs the difference between the adjacent inputs, but outputs the reference one input as it is. That is, 6
Input signals (s1, s2, s3, s4, s5, s6)
With respect to (s1, s2-s1, s3-s2, s4-s
6, s5-s4, s6-s5) are output.

Further, the output of the differential amplifier 2 is connected to an electrode abnormality detecting section 7, and the electrode abnormality detecting section 7 examines the amplitude of the injected electrode detection signal of several kHz to several hundreds Hz, for example, to check the electrode abnormality. Is detected. The information on the electrode abnormality is sent to the transmission packet synthesizer 8 and used to control the electrocardiogram data selector 5 and delete the lead data from the abnormal electrode.

The II and III derivation data and the output data of the subtractor 6 are input to the encoder 4. The encoding unit 4 first calculates the difference from the value at the time of the previous sampling, and assigns a variable length code typified by, for example, a Huffman code used in general data compression. The encoded data is assembled into a packet shown in FIG. 5 together with information on the electrode abnormality and the like in the transmission packet combining unit 8, and after modulating the radio signal by a digital modulation method such as FSK or PSK in the modulation unit 9, It is transmitted through the antenna 10.

FIG. 2 shows the configuration of a receiver that receives transmission data from a standard 12-lead ECG transmitter and restores a 12-lead ECG. On the receiver side, the received signal is demodulated into digital data by the demodulation unit 11 in a demodulation method corresponding to the transmission side, and then information on the electrode abnormality and the encoded electrocardiogram are decoded by the decoding unit 12 according to the packet structure shown in FIG. Separate and extract data. The extracted electrocardiogram data is restored to 12-bit data by the decoder 13 and input to the lead synthesizing unit 14. The lead synthesizing unit 14 synthesizes a standard 12-lead signal by performing arithmetic processing on each data. The synthesized standard 12 guide signal is converted into an analog waveform by the D / A converter 15 and is recorded by the recorder 16 as appropriate.

Hereinafter, the operation of the multi-lead ECG telemeter system will be described with reference to FIG. FIG. 4 illustrates an example of an input signal to the electrocardiogram data selector 5 and an output signal of the subtractor 6 in the lead electrocardiogram transmitter according to the embodiment of the present invention shown in FIG. Actually, the input to the electrocardiogram data selector 5 is converted into digital data in the A / D converter 3, and the output signal of the electrocardiogram data selector 5 and the output signal of the subtracter 6 are also digital data. 4, it is expressed as waveform data for explanation. Although the number of inputs to the electrocardiogram data selector 5 is six in the configuration of FIG. 1, three of them are shown in FIG. In the example shown in FIG. 4, S1, S2, and S3 indicate signals input to the electrocardiogram data selector 5, and S3-S2 indicates output signals of the subtractor 6. In the input signal, S1 is assumed to be a case where the contact state of the electrode 1 is poor and the electrode 1 is in a noise state.

The electrode state controls the data selection in the electrocardiogram data selection unit 5, and in this example, S1 is deleted (S
, S3,...) Are input to the subtractor 6, and (S2, S3-S2,...) Are output from the subtractor 6. As shown in FIG. 4, the waveform of S3-S2 has a greatly reduced amplitude as compared with the waveform of S2 or S3. Although not shown in FIG. 4, other output data of the subtracter 6 whose amplitude is greatly reduced as compared with the original data can be obtained. This is because the correlation of the electrocardiogram waveform obtained from the adjacent electrode 1 is strong, and there is also an effect of removing noise having a high correlation between the adjacent electrodes such as body motion, electromyogram, and pacemaker, thereby suppressing an increase in amplitude due to the noise. Has the effect of

The difference between S3-S2, which is the output of the subtractor 6, from the data at the time of the previous sampling is 1% in the 95% section.
The difference is within a bit. The original data (S
In the section 3), the interval where the difference from the data at the previous sampling is within 1 bit is 65%, and a shorter code can be frequently used by encoding based on the subtractor output (S3-S2), and the compression ratio can be reduced. Can be improved.

The heartbeat component represented by QRS between adjacent electrodes has a very high correlation as shown in FIG. Therefore, by taking the difference, most of the heartbeat component can be removed as shown in FIG. 4, and the amplitude of the difference data is suppressed. By encoding this data, highly efficient encoding can be realized. In addition, the heartbeat removal according to the present invention does not require heartbeat detection unlike the conventional heartbeat removal using a template, and thus does not need to store data for that amount. Therefore, real-time wireless monitoring can be realized.

Further, by providing a means for skipping an abnormal electrode by referring to an electrode state detected separately in obtaining a difference between electrodes, it is possible to encode only data with a normal electrode having no noise. Become. As a result, even if an abnormal electrode exists, it is possible to reliably transmit data from the normal electrode.

The electrocardiogram shows the state of myocardial excitation.
QRS in particular shows ventricular excitement, which triggers the ventricle to contract and pump blood throughout the body. The ventricle, especially the left ventricle, is the part of the heart that produces the highest power, and its excitation waveform, QRS, has the highest amplitude in the electrocardiogram. When performing ECG compression, the key is how to reduce the effect of this QRS. In the present invention, the compression effect is increased by taking the difference between electrocardiograms obtained from a plurality of leads.

The multi-lead electrocardiogram transmitter and its receiver according to the embodiment are configured as described above, and have the following effects. Since the multi-lead ECG transmitter and the receiver of the present invention can effectively compress the data of the multi-lead ECG without sacrificing the real-time performance, the transmitter for the multi-lead ECG monitor can reduce the radio frequency band. Can be realized without spreading. This is because it has a basic configuration in which a difference is obtained with respect to a highly correlated electrocardiogram signal derived from the adjacent electrode 1, a time difference is obtained after the signal amplitude is reduced, and the time difference is encoded. . As a result, the data accumulation period can be shortened as compared with the heartbeat elimination method using the QRS template conventionally performed for the same purpose, and the real-time performance which is an important performance for the electrocardiogram monitor can be improved.

Further, a function of detecting an electrode state and eliminating a signal from an abnormal electrode is realized, and a stable ECG monitor can be realized without causing significant compression rate deterioration even when an electrode is abnormal. .

Further, since the heartbeat detection is not required, there is no need to accumulate the electrocardiogram data, and no delay occurs due to the data accumulation. For this reason, important real-time performance in the electrocardiogram monitor can be improved.

In the present embodiment, the difference is obtained after A / D conversion of the electrocardiogram signal. However, the difference may be obtained in the state of the analog signal by using a differential amplifier or the like. After reducing the signal amplitude, A / D
By performing the conversion and the encoding, the same effect as in the above embodiment can be obtained.

As described above, it is apparent that the present invention is not limited to the above-described embodiment, but can be appropriately modified within the scope of the technical idea of the present invention.

The number, position, shape, and the like of the above-mentioned constituent members are not limited to the above-described embodiment, but can be set to a number, position, shape, and the like suitable for carrying out the present invention.

[0035]

Since the present invention is configured as described above, the following effects can be obtained. The multi-lead ECG transmitter and the receiver of the present invention can effectively compress data of a multi-lead ECG without sacrificing real-time performance. This is because it has a basic configuration in which a difference is obtained for an electrocardiogram signal having a high correlation derived from an adjacent electrode, a time difference is obtained after the amplitude of the signal is reduced, and the time difference is encoded.

Further, according to the present invention, a function of detecting the state of the electrode and eliminating a signal from the abnormal electrode is realized.
A stable ECG monitor can be realized.

[Brief description of the drawings]

FIG. 1 is a configuration diagram of a multi-lead electrocardiogram transmitter according to an embodiment of the present invention.

FIG. 2 is a configuration diagram of a multi-lead ECG receiver according to the embodiment of the present invention.

FIG. 3 is an electrode mounting diagram of the multi-lead ECG transmitter shown in FIG. 1;

FIG. 4 is an operation explanatory diagram of the ECG data amplitude suppression of the multi-lead ECG transmitter shown in FIG. 1;

FIG. 5 is a configuration diagram of a transmission packet in the multi-lead ECG transmitter according to the embodiment of the present invention.

FIG. 6 is an explanatory diagram showing an example of an operation of suppressing electrocardiographic data amplitude according to a conventional method.

[Explanation of symbols] [Explanation of symbols]

 Reference Signs List 1 electrode 2 differential amplifier 3 A / D converter 4 encoding unit 5 electrocardiogram data selection unit 6 subtractor 7 electrode abnormality detection unit 8 transmission packet synthesis unit 9 modulation unit 10 antenna 11 demodulation unit 12 decoding unit 13 decoder 14 Induction synthesis unit 15 D / A converter 16 Recorder

────────────────────────────────────────────────── ─── Continuing on the front page (72) Inventor Masakazu Watanabe 5-7-1 Shiba, Minato-ku, Tokyo NEC Corporation (72) Inventor Hiroyuki Seki 5-7-1 Shiba, Minato-ku, Tokyo NEC (72) Inventor Kazuhiko Sudo 5-7-1 Shiba, Minato-ku, Tokyo NEC Corporation (56) References JP-A-58-183140 (JP, A) JP-A-6-237909 (JP) JP-A-5-37420 (JP, A) JP-A-5-161611 (JP, A) JP-A-7-51388 (JP, A) (58) Fields studied (Int. Cl. ⁷ , DB Name) A61B 5/0402

Claims (12)

(57) [Claims] 1. A multi-lead electrocardiogram transmitter for simultaneously transmitting a plurality of electrocardiograms by radio, comprising: a difference calculator for calculating a difference between a plurality of electrocardiogram signals to generate a difference signal; A multi-lead electrocardiogram transmitter, comprising: signal transmission means for transmitting. 2. The multi-lead ECG transmitter according to claim 1, wherein said difference calculating means calculates a difference between ECG signals derived from adjacent electrodes. 3. An abnormal mounting detecting means for detecting an abnormal mounting of the electrode, and an abnormal signal deleting means for deleting an electrocardiogram signal derived from the electrode detected by the abnormal mounting detecting means. The multi-lead ECG transmitter according to claim 1. 4. The subtraction device according to claim 1, wherein the difference calculating means includes a subtractor for outputting the reference guidance data input from the electrode as it is, calculating a difference between the guidance data output from the adjacent electrodes, and outputting the difference. 4. The method according to claim 1, wherein:
The multi-lead electrocardiogram transmitter according to any one of the above. Wherein said mounting abnormality detection means, to any one of claims 1 to 4, characterized in that with an electrode abnormality detector for detecting an electrode abnormal by examining the amplitude of the electrode signal for detecting A multi-lead ECG transmitter as described. 6. The apparatus according to claim 1, wherein the abnormal signal deleting unit includes an electrocardiogram data selecting unit that deletes lead data from the electrode determined to be abnormal by the electrode abnormality detecting unit. The multi-lead electrocardiogram transmitter according to any one of the above. 7. The signal transmission unit includes an encoding unit that encodes data output from the subtractor, and a modulation unit that modulates the encoded data to a radio signal by a digital modulation method. The multi-lead electrocardiogram transmitter according to claim 1, wherein: 8. A multi-lead electrocardiogram transmitter for simultaneously transmitting a plurality of lead electrocardiograms by radio, comprising: a limb electrode, six chest electrodes, and an output from an LF electrode that is one of the limb electrodes. As a reference signal, a signal is input from all electrodes including the limb electrode and the chest electrode excluding an RF electrode serving as a common ground, and a differential amplifier for removing noise, and an amplitude of an electrode detection signal is examined. An electrode abnormality detecting unit for detecting an electrode abnormality in the A / D, and an A / D for digitizing an output signal from the differential amplifier
A transducer, an electrocardiogram data selection unit that selects and rearranges lead data from normally mounted chest electrodes based on electrode abnormality detection information, and outputs the reference lead data as it is, and compares the lead data from adjacent electrodes A subtractor for calculating and outputting the difference between the output data from the subtractor and the sample value, and an encoding unit for assigning a variable length code; and transmitting the encoded data into a packet together with the electrode abnormality information. A multi-lead electrocardiogram transmitter, comprising: a packet synthesizer; and a modulator for modulating a radio signal by a digital modulation method. 9. A multi-lead electrocardiogram receiver for receiving a plurality of lead electrocardiograms transmitted simultaneously by radio, comprising: a demodulation section for demodulating a received signal into digital data by a demodulation method corresponding to a transmission side; A decoding unit that separates and extracts information related to electrode abnormalities and encoded ECG data, a decoder that restores the extracted ECG data to 12-bit data, and performs arithmetic processing on each data to perform standard processing An induction synthesizing unit for synthesizing the 12-lead signal; and a D / for converting the synthesized standard 12-lead signal into an analog waveform.
A multi-lead ECG receiver, comprising: an A converter; and a recorder for recording data converted into an analog waveform by the D / A converter. 10. An electrocardiogram data transmission method for simultaneous radio transmission of electrocardiograms of a plurality of leads, wherein a difference between electrocardiogram signals guided from electrodes is taken as a difference signal, and the difference signal is compressed. And transmitting the difference signal. 11. The output of the differential amplifier is connected to an electrode abnormality detection unit, and the electrode abnormality detection unit detects the electrode abnormality by examining the amplitude of the electrode detection signal, and transmits information on the electrode abnormality to the transmission packet synthesis unit. The information data relating to the electrode abnormalities is used to control the selection unit and to delete the guidance data from the abnormal electrode. The II and III guidance data and the output data of the subtractor are input to the encoding unit. The transmitter calculates the difference from the value at the previous sampling, assigns a variable-length code for data compression, and assembles the encoded data into a packet with information on electrode abnormalities in the transmission packet synthesizer, and modulates the data. The method for transmitting electrocardiogram data according to claim 10, wherein the wireless signal is modulated by a digital modulation method and transmitted through an antenna. 12. An electrocardiogram data receiving method for receiving an electrocardiogram of a plurality of leads simultaneously transmitted wirelessly, wherein a demodulation section demodulates a received signal into digital data by a demodulation method corresponding to a transmission side, and a decoding section Separate and extract information on electrode abnormalities and encoded ECG data according to the structure, restore the extracted ECG data to 12-bit data with a decoder, and output it to a lead synthesis unit. Perform arithmetic processing on the data,
A method for receiving electrocardiogram data, comprising: synthesizing a standard 12-lead signal; converting the synthesized standard 12-lead signal into an analog waveform by a D / A converter; and recording the analog waveform by a recorder.