JPH0545257B2 - - Google Patents

Description

[Detailed Description of the Invention] [Industrial Application Field] The present invention relates to a device that amplifies and automatically recognizes electrocardiogram signals obtained from the body surface, and in particular, a device that automatically recognizes P waves and detects body surface electrocardiogram signals. In addition to improving the accuracy of automatic analysis regarding P waves, it is also possible to detect His bundle waves by executing the averaging method using the automatically recognized P waves as a synchronization signal, thereby improving the quality of body surface His bundle electrocardiograms. The present invention relates to an electrocardiogram P wave recognition application device designed to achieve the following.

[Conventional technology]

(1) Background of the Invention There are two types of electrocardiogram processing devices: those for body surface electrocardiograms and those for body surface His bundle electrocardiograms.

Of these, the former is a device that automatically recognizes electrocardiogram signals obtained from the patient's body surface and is used to automatically analyze the patient's heart condition.

The electrocardiogram obtained from the body surface is composed of P waves, QRS complexes, and T waves, as shown in Figure 9A.
The vertical axis represents the intensity of electrical stimulation of the heart, and the horizontal axis represents the time it takes for the electrical stimulation to travel through the heart.

The above-mentioned P wave can be explained using the cardiac stimulation conduction system shown in FIG.
This refers to the state in which the atrioventricular node 206 spreads until it gathers at the atrioventricular node 206, that is, the process of excitation of the atrium.

The QRS complex consists of the ventricular septum 208 and the left and right ventricular muscles 20
9,210, in other words, the electrical stimulation passing through the atrioventricular node 206 spreads to the right ventricle 203 and the left ventricle 204 via the His bundle 207, that is, the ventricular excitatory process. do.

Furthermore, in FIG. 9A, the T wave means the electrical recovery process after the ventricular excitation process is completed.

After the T wave, the heart enters a resting state,
A straight baseline B (FIG. 9) is drawn.

Among these, the P wave indicates the initial excitement process of the heart, so by looking at the body surface electrocardiogram (Figure 9A), we can determine at what intervals this P wave, the subsequent QRS complex, and the T wave occur. By observing this, you can determine the state of your heart disease.

Therefore, when performing automatic analysis, first
Being able to automatically recognize waves is essential.

On the other hand, the latter is a device for detecting the hiss bundle wave H (FIG. 9B) in the above-mentioned body surface electrocardiogram (FIG. 9A).

This latter device is used when automatic analysis based on the former device shows that there is a serious heart disease and it is particularly necessary to confirm the His bundle wave H.

For example, as a result of automatic analysis of body surface electrocardiograms,
PR interval (Fig. 9A), that is, the conduction time between the excitatory process in the atrium and the conduction time in the atrioventricular node 206 (Fig. 10) from the His bundle 207 to the upper ventricular septum 211 is abnormally long, which may cause arrhythmia. You may be judged and want to know the reason.

In that case, if you carefully observe the appearance of the His bundle wave H in the body surface His bundle electrocardiogram (Fig. 9B), you can see that the electrical excitation is in front of the His bundle 207 (Fig. 10).
You can tell if it ends after (mark) or after (x mark). Therefore, it is clear which abnormality in the stimulus conduction system is the cause of this arrhythmia, and how to treat it accordingly.

However, this His bundle wave H occurs only at a minute potential even lower than the P wave, which has a low potential, even in the body surface electrocardiogram (FIG. 9A) (FIG. 9B). For this reason, in the former electrocardiogram automatic analyzer, the hiss bundle wave H is often not recorded because its amplification sensitivity is low. Furthermore, even if the degree of amplification is simply increased, noise and the like will also be amplified, so it is difficult to immediately extract only the hiss bundle wave H within one cardiac cycle t (FIG. 9B).

Therefore, in order to detect the hiss bundle wave H, the so-called averaging method is used, in which only the noise is removed by averaging the hiss bundle waves H for each of multiple cardiac cycles using the P wave that appears immediately before as a synchronizing signal. A processing device for body surface His bundle ECG becomes effective.

(2) Conventional example The conventional P wave recognition device for body surface electrocardiogram is
As shown in FIG. 1A, it is composed of an electrocardiogram amplification section 101 and a P wave recognition section 103.

The electrocardiogram signal E1 obtained from the body surface is amplified approximately 1000 times by the electrocardiogram amplifier 101, and an amplified electrocardiogram signal E2 is output.

This amplified electrocardiogram signal E2 is input to the P wave recognition unit 103 in order to automatically recognize P waves.

The P wave E4 automatically recognized by the P wave recognition unit 103 is sent to an automatic analysis unit (not shown) and is used to automatically analyze the body surface electrocardiogram.

On the other hand, some conventional body surface His bundle electrocardiogram processing devices employ an R-wave synchronized averaging method.

Generally, the average method is used in [industrial applications]
As outlined in the ``Background of the Invention'' column and ``Background of the Invention'' column (1) of [Prior Art], this is a means for detecting the His bundle wave H, which has the lowest action potential among the electrocardiogram signals (Fig. 11). be.

The principle of this averaging method is that if the hiss bundle wave, which is a synchronous signal that appears in each cardiac cycle, and the asynchronous noise that occurs around it are averaged in synchronization with the cardiac cycle, the hiss bundle wave remains unchanged. is based on the fact that noise changes and therefore becomes smaller.
In other words, the purpose of the averaging method is to remove noise and detect only hiss bundle waves.

There is no general standard for how many times the above averaging should be performed, but when n hiss bundle waves are averaged, the SN ratio is √ of the SN ratio of one hiss bundle wave.
Since it is well known that the number of averaging operations increases, it is certain that the noise decreases and it becomes easier to detect only the hiss bundle wave, which is a signal, as the number of averaging operations increases.

Conventionally, when executing the above average method,
The R wave (Fig. 9A) was used as the synchronization signal.

This is because the R wave has the highest action potential among the electrocardiogram signals (Fig. 9A), so it is easy to detect as a synchronous signal, and in a normal heart, the His bundle should be averaged with the R wave, which is the synchronous signal. Since the PR interval, which is the interval between the P wave that appears immediately before the wave H (B in Figure 9), is constant, the hiss bundle wave always occurs at the same temporal position (A (1) in Figure 12), and as described above. This is because it is easier to achieve the purpose of the averaging method.

However, in the case of an abnormal heart, for example, if there is a heart disease such as arrhythmia, the PR interval may become abnormally long (Fig. 12 A (2)) or short (Fig. 12 A (n)). There are things to do.

In such a case, the temporal position of the hiss bundle wave H is R
There is a problem in that the temporal position of the hiss bundle wave H shifts during the execution process of the averaging method, making it impossible to achieve the purpose of the averaging method, which is to leave only the hiss bundle wave and remove noise. Figure 12 A(n+1)).

In order to solve this problem, P
This is a wave synchronous averaging method.

This P-synchronized averaging method uses the P-wave as a synchronizing signal and takes the average of the hiss bundle wave H that appears immediately after the P-wave.As mentioned above, the R-wave synchronized averaging method that had been used until then did not detect arrhythmia as a cause.
This method was proposed because the PR interval changes and the time position of the hiss bundle wave H becomes unstable with respect to the R wave, making it impossible to achieve the purpose of the averaging method.

That is, in the R-wave synchronous averaging method, the hiss bundle wave and R
In the case of arrhythmia where the interval between waves changes, the purpose of the averaging method cannot be achieved, but according to the P-wave synchronous averaging method, the purpose of the averaging method can be achieved in diseases where the temporal positional relationship between the His bundle wave and the R wave changes. Based on the idea.

As shown in FIG. 12B, the body surface His bundle electrocardiogram detection device using such a P-wave synchronized averaging method has a His bundle wave dedicated amplifier 104 and a His bundle wave in addition to an electrocardiogram amplification section 101 and a P wave recognition section 103. Wave detection section 1
05.

The electrocardiogram signal E1 obtained from the body surface is input and amplified by the hiss bundle wave dedicated amplifying section 104 in order to extract the hiss bundle wave with the lowest action potential included therein, and the amplified hiss bundle wave E5 is output. .

The hiss bundle wave detection unit 105 receives the automatically confirmed P wave E4 from the above-mentioned P wave recognition unit 103 as well as the amplified hiss bundle wave E5.

The hiss bundle wave detection unit 105 inputs the amplified hiss bundle wave E5 a plurality of times, for example, every n cardiac cycles, and (12th
In order to remove the noise generated before and after the hiss bundle wave, the hiss bundle wave E6 is detected by the averaging method by taking the average of these with the P wave E4 as a synchronization signal (Figure C). Figure 12 (n+
1)).

[Problem that the invention seeks to solve]

According to the configuration shown in the conventional example of the automatic analysis device for body surface electrocardiogram (FIG. 11A), the P wave recognition unit 10
3, the amplified electrocardiogram signal E2 is input.
However, the conventional electrocardiogram signal amplifying section 101 does not particularly emphasize and amplify P waves, but amplifies the entire electrocardiogram. Therefore, the P wave E4 included in the amplified electrocardiogram signal E2 (FIG. 11B) input to the P wave recognition unit 103 has a low voltage and is mixed with a fluctuating baseline and noise, as shown in the figure. .

Therefore, the P wave recognition unit 103 may not be able to automatically recognize P waves compared to other QRS complexes or T waves. In this case, in the conventional example (Fig. 11A), the measurement of the part related to P waves is not satisfactory, and the accuracy of automatic analysis decreases, resulting in the inability to provide accurate data useful for discovering heart disease. It has points.

On the other hand, according to the configuration shown in the conventional example (FIG. 12B) of the body surface His bundle electrocardiogram processing device, the P wave E4 recognized by the P wave recognition unit 103 is input to the His bundle wave detection unit 105. It's becoming like that.

This is because the P wave E4 is used as a synchronization signal for the averaging method performed by the hiss bundle wave recognition unit 105.

However, as explained in the conventional example of an automatic recognition device for a body surface electrocardiogram (FIG. 11), the P wave E4 itself, which should be a synchronization signal, may not be automatically recognized (FIG. 11B).

In such a case, as shown in FIGS. 12C, (2) and n, the P wave E4, which is a synchronizing signal, cannot be aligned with the common time reference axis TR.

Therefore, even if the PH interval remains unchanged for all cardiac cycles (Fig. 12C(1)-n), the P wave E4
The temporal position of the hiss bundle wave E5 that appears immediately after becomes indeterminate (Fig. 12 C(2) and n), and the hiss bundle wave E5 (with the same cardiac cycle as the automatically recognized P wave E4 (Fig. 12 C1)) Compared to FIG. 12 C(1)), the temporal position is shifted (FIG. 12 C(2) and n).

For this reason, as in the case of the R-wave periodic averaging method described above, the objective of the averaging method, which is to remove noise while leaving the hiss bundle wave, cannot be achieved (first
Figure 2C(n+1)).

For this reason, the His bundle wave detection unit 105 cannot accurately recognize the His bundle waves, and the quality of the body surface His bundle electrocardiogram deteriorates.

That is, the conventional example of a processing device for body surface His bundle electrocardiogram (FIG. 12A) also has the problem that it cannot provide accurate data useful for discovering heart diseases.

[Means for solving problems]

In view of the problem that the above-mentioned conventional technology cannot provide accurate data useful for discovering heart diseases, the present invention firstly provides a dedicated P-wave amplification section to provide a P-wave recognition section with an emphasis on P-waves. By inputting P waves, automatic recognition of P waves is enabled and automatic analysis accuracy regarding P waves is improved.Secondly, this automatically recognized P wave is used as a synchronization signal to execute the P wave synchronized averaging method to calculate histograms. The present invention aims to improve the quality of the body surface His bundle electrocardiogram by making it possible to detect waves, thereby solving the above-mentioned problems.

[Effect]

Therefore, the effect of the configuration of the first invention shown in FIG. 1 is to branch the electrocardiogram signal S1 obtained from the body surface and input one to the electrocardiogram amplification section 1 and the other to the P-wave dedicated amplification section 2. Generates an amplified electrocardiogram signal wave S2 and an amplified P wave S3, and a P wave recognition unit 3
First, the threshold value TH of S3 to be detected is set using both the amplified electrocardiogram signal S2 and the amplified P wave S3,
Next, the preset threshold TH is used to detect the amplified P wave S3, which has a large amplitude and is steeper, thereby detecting the P wave S4.
enables automatic recognition of

Further, the operation of the configuration of the second invention shown in FIG.
Input the amplified hiss bundle wave S5 obtained through
First, the hiss bundle wave recognition unit 5 automatically recognizes the P wave S.
4 as a synchronization signal to the time reference axis TR (Fig. 2B), and then, in order to remove noise, the hiss bundle wave S5 of each cardiac cycle is averaged and the averaging method is performed to calculate the hiss bundle wave. Detect S6.

〔Example〕

(1) First invention Hereinafter, the configuration and operation of the first invention will be explained by way of embodiments with reference to the accompanying drawings.

Configuration FIG. 3 is a diagram showing an embodiment of the first invention.

In the figure, electrodes (conductors) LA, RA...C6 that are in close contact with the body surface, a buffer amplifier 6, a network 7, and a lead selector 8 are connected in sequence, and the lead selector 8 is connected to an electrocardiogram amplifier The electrocardiogram amplifying section 1 and the P-wave amplifying section 2 are connected to a P-wave recognizing section 3, respectively.

In this embodiment, the lead selector 8 selects the standard
2nd lead of 12 leads, i.e. left foot electrode LF
The action potentials at two points on the heart taken from the right-hand electrode RA and RA are selected.

Therefore, the electrocardiogram signal S1 (FIG. 4) from the second lead appears at the two output terminals of the lead selector 8, and the output terminals are connected to the input terminal of the electrocardiogram amplifier 1. .

The electrocardiogram amplifying section 1 includes a preamplifier 1A similar to that used in conventional electrocardiographs.
It is a device that amplifies the entire electrocardiogram signal S1 from the second lead output from the lead selector 8 and outputs the amplified electrocardiogram signal S2, and the output terminal is connected to the P wave recognition unit 3. is connected to the input terminal of

The P-wave dedicated amplifier section 2 includes a preamplifier 2A, a low-cut filter 2B, an amplifier 2C, a hum filter 2D, and a high-cut filter amplifier 2E.
and the second output from the lead selector 8
The electrocardiogram signal S1 from the lead is input, the P wave is emphasized, extracted and amplified, and the amplified P wave S3
(FIG. 4C), and its output terminal is connected to the other input terminal of the P-wave recognition section 3.

The P-wave recognition unit 3 includes an A/D converter 3A, a storage unit 3B, and a CPU 3C, and sets a threshold TH based on the amplified electrocardiogram signal S2 and the amplified P-wave S2, and detects the amplified P-wave S3 at this set threshold TH. This is a device that recognizes and outputs P waves S4.

Operation (i) Operation from the electrode to the lead selector The electrocardiogram signal derived from each electrode passes through the buffer amplifier 6 and the network 7,
The second lead is selected by the lead selector 8.

Therefore, the two output terminals of the lead selector 8 output the electrocardiogram signal SI from the second lead.

(ii) Operation of the electrocardiogram amplifying section The electrocardiogram signal S1 (FIG. 4A) is input to the differential amplifier constituting the preamplifier 1A, and the potential difference therebetween is amplified and input to the low-cut filter 1B.

The low-frequency band is removed by the low-cut filter 1B, and the signal is further amplified by the amplifier 1C to output an amplified electrocardiogram signal S2 (FIG. 4B), which is input to the P-wave recognition unit 3.

(iii) Operation of the P-wave dedicated amplifier section The electrocardiogram signal S1 (Fig. 4A) output from the lead selector 8 is also input to the differential amplifier constituting the preamplifier 2A of the P-wave dedicated amplifier section 2. The difference between the two potentials of LF and RA is taken by the differential amplifier, and first stage amplification is performed.

Next, the low frequency of the electrocardiogram signal amplified by the differential amplifier is cut by a low-cut filter 2B. That is, low cut filter 2B
If the cutoff frequency of is f ₀ , waves with frequencies lower than f ₀ are removed.

The electrocardiogram signal from which the low frequency has been cut is subjected to second stage amplification by an amplifier 2C, and a wave of frequency _f2 mixed in from the power supply is removed by a hum filter 2D.

The electrocardiogram signal that has passed through the hum filter 2D is finally sent to the high-cut filter amplifier 2.
At E, high frequency noise is removed and a third stage amplification is performed.

In this way, in the P-wave dedicated amplifying section 3, low-frequency, high-frequency and power supply noises are cut, and the amplified P-wave S3 is extracted and outputted with emphasis (FIG. 4C).

This P-wave dedicated amplification section 2 is provided according to the present invention to emphasize and extract the P-wave from the body surface electrocardiogram signal S1, and the lower limit f ₀ of its frequency characteristics f ₀ to _{f 1} is as follows. P
higher than the lower limit of the wave frequency band. This means that even if some P waves leak, low frequency noise is completely cut out, the output amplified P wave S3 has a steep waveform (Fig. 5), and the P wave is detected by the P wave recognition unit 3. This is to facilitate P-wave synchronization in the hiss bundle wave recognition unit 5 of the second invention, which will be described later, which is related to the first invention.

(iv) Operation of P wave recognition unit (1) Setting of P wave detection threshold Amplified electrocardiogram signal S2 and amplified P wave S3
The signals (B and C in FIG. 4) are input to the A/D converter 3A, converted from analog to digital, and then temporarily stored in the storage section 3B.

Here, the CPU 3C inputs the digitized amplified electrocardiogram signal S2 stored in the storage section 3B. This is the threshold value for detecting the amplified P wave S3, which will be described later.
This is for setting TH, and the input time only takes a few seconds.

Next, the CPU 3C detects the R wave of the input digital amplified electrocardiogram signal S2 (FIG. 5). At this time, the wave of ventricular premature contraction (VPC), which is known to have no P wave, is removed. Using the detected R wave, set the detection interval of S3, determine the most effective threshold of S, and set the threshold
Let it be TH.

(2) Detection of amplified P wave The CPU 3C inputs the digital amplified P wave S3 stored in the storage section 3B, and detects the P wave S4 included in the electrocardiogram signal S2 according to the set threshold TH.
(Fig. 4D) is detected.

In this case, the amplified P wave S3 has
As shown in FIG. 5, since several peaks are included, P waves are detected based on an effective procedure.

Among the information regarding this amplified P wave S3, the trigger point also serves as a time reference point for the P wave synchronous averaging method performed by the hiss bundle wave recognition unit 5 of the second invention described later. In other words, the trigger point becomes a time phase matching point in the P-wave synchronous averaging method.

As described above, according to the first invention, P
By providing a dedicated P-wave amplification section 2 that emphasizes and amplifies the waves, low-voltage P waves can be easily recognized.

Therefore, this recognized P wave S4 is sent to CPU3.
When C outputs and sends it to an automatic analysis unit (not shown), the accuracy of automatic analysis of P waves in body surface electrocardiograms improves, providing accurate data useful for discovering heart diseases.

(3) Second invention Hereinafter, the configuration and operation of the second invention will be explained by way of embodiments with reference to the accompanying drawings.

Configuration FIG. 6 is a diagram showing an embodiment of the second invention.

Since the structure from the electrode to the P-wave recognition section 3 is completely the same as that of the first invention, the explanation will be omitted, and the hiss bundle wave dedicated amplification section 4 and the hiss bundle wave recognition section 5 will be explained below.

The hiss bundle wave dedicated amplification section 4 is a preamplifier 4A.
It consists of a low-cut filter 4B, an amplifier 4C, a high-cut filter 4D, and an amplifier 4E, which inputs the second lead electrocardiogram signal S1 (FIG. 7A) selected by the lead selector 8, amplifies the potential difference, and generates an amplified histogram. This is a device that emphasizes and outputs the bundle wave S5 (FIG. 7B).

The configuration of this dedicated hiss bundle wave amplifier 4 is the same as that of the conventional one, and the outputted amplified hiss bundle wave S5 is sent to the hiss bundle wave recognition unit 5, and P-wave synchronization is performed to remove surrounding noise. The average is taken.

The hiss bundle wave recognition unit 5 is composed of an A/D converter 5A, a storage unit 5B, and a CPU 5C, and receives the amplified hiss bundle wave S5 as an input, and detects the hiss bundle wave S6 by taking the average using the P wave S4 as a synchronization signal. This is a device that outputs images.

In this case, it is also possible to combine the hiss bundle wave recognition section 5 and the P wave recognition section 3 into one.

Operation The operation from the electrode to the P wave recognition unit 3 is as follows:
Since it is exactly the same as the invention, the explanation will be omitted, and the above-mentioned hiss bundle wave dedicated amplification section 4 and hiss bundle wave recognition section 5 will be explained.

Electrocardiogram signal S output from lead selector 8
1 is input to the differential amplifier constituting the preamplifier 4A, and the potential difference between RA and LA is amplified, and then passes through the low-cut filter 4B, amplifier 4C, high-cut filter 4D, and amplifier 4E to the amplified hiss bundle wave S5 (the first 7B) is output.

Since this amplified hiss bundle wave S5 is mixed with noise, the A/D converter 5 of the hiss bundle wave recognition unit 5 is used for the P-wave synchronized averaging method.
It is input to A. Here, the amplified hiss bundle wave S5
is converted into digital data and temporarily stored in the storage section 5B.

On the other hand, the CPU 5C receives the P wave S4 (FIG. 4D) output from the P wave recognition section 3.
This is to align the time phase matching point t ₀ of the automatically recognized information regarding the P wave to the time reference axis TR (FIG. 8) of the P wave synchronous averaging method, which will be described later.

Next, the CPU 5C inputs the amplified hiss bundle wave S5 stored in the storage unit 5B (the eighth
Figure) For each cardiac cycle, align the above time phase matching point t ₀ with the time reference axis TR, and then
(Figure 8). Finally, the addition result is divided by the number of amplified hiss bundle waves S5 to take an average and remove noise.

This means that the P-wave synchronous averaging method has been executed, and the hiss bundle wave S6 from which noise has been removed has been detected (FIGS. 8 and 7C).

In this way, according to the second invention, automatic recognition of P waves has become possible due to the related first invention, so the PH interval is always constant and the temporal positions of the hiss bundle waves are all added in the same state. By executing the P-wave synchronous averaging method that allows averaging, the purpose of the averaging method of detecting hiss bundle waves while removing noise has been achieved, and it has become possible to detect hiss bundle waves. Therefore, the quality of body surface His bundle electrocardiograms has improved, providing accurate data useful for discovering heart diseases.

〔Effect of the invention〕

As described above, according to the first invention, by emphasizing and amplifying the P wave of the electrocardiogram signal obtained from the body surface, and by configuring the amplified P wave to be detectable, the P wave to be recognized can be detected. It has become possible to automatically recognize P waves despite the presence of low voltage, fluctuating baselines, and noise, making it possible to satisfactorily measure areas related to P waves. According to the second invention, the automatically recognized P wave is used as a synchronization signal to take the average of the hiss bundle waves generated immediately after the P wave. As a result, the purpose of the averaging method, which is to remove noise and detect the hiss bundle waves, can be taken by averaging the temporal positions of all the hiss bundle waves at the same time, making it possible to detect the hiss bundle waves. As a result, the quality of the body surface His bundle electrocardiogram also improved, and in the end, both inventions had the effect of providing accurate data useful for discovering heart diseases such as arrhythmia.

[Brief explanation of drawings]

FIG. 1 is a diagram showing the principle of the first invention, FIG. 2 is a diagram showing the principle of the second invention, and FIG. 3 is a diagram showing an embodiment of the first invention.
Fig. 4 is a waveform diagram of each part of the first invention, Fig. 5 is an explanatory diagram of P wave recognition operation, Fig. 6 is a diagram showing an embodiment of the second invention, and Fig. 7 is a waveform diagram of each part of the second invention. Figure, 8th
The figure is an explanatory diagram of the operation of His bundle wave recognition, Figure 9 is a body surface electrocardiogram and a body surface His bundle electrocardiogram, Figure 10 is a schematic diagram showing the cardiac stimulation conduction system, and Figure 11 is an explanatory diagram of the conventional technology (body surface electrocardiogram). FIG. 12 is an explanatory diagram of the prior art (for body surface His bundle electrocardiogram). 1... Electrocardiogram amplification unit, 2... P wave dedicated amplification unit,
3... P wave recognition section, 4... Hiss bundle wave dedicated amplification section,
5... Hiss bundle wave recognition unit.

Claims (1)

[Claims] 1. An electrocardiogram amplification unit 1 that inputs an electrocardiogram signal S1 obtained from the body surface, amplifies the entire electrocardiogram signal S1, and outputs an amplified electrocardiogram signal S2; Input,
A preamplifier 2A that performs first-stage amplification, a low-cut filter 2B that removes low-frequency noise, and a second
It is composed of an amplifier 2C that performs stage amplification, a hum filter 2D that removes power supply noise, and a high-cut filter amplifier 2E that removes high-frequency noise and performs third-stage amplification. A P-wave dedicated amplifier 2 that emphasizes and amplifies the wave and outputs the amplified P-wave S3, and a threshold value (TH) that inputs the amplified electrocardiogram signal S2 and the amplified P-wave S3 and sets it based on the amplified electrocardiogram signal S2. By detecting the amplified P wave S3 at
P wave recognition unit 3 that recognizes P wave S4 included in amplified electrocardiogram signal S2 and outputs the recognized P wave S4
An electrocardiogram P wave recognition device comprising: 2. An electrocardiogram amplification unit 1 that inputs an electrocardiogram signal S1 obtained from the body surface, amplifies the entire electrocardiogram signal S1, and outputs an amplified electrocardiogram signal S2;
A preamplifier 2A that performs first-stage amplification, a low-cut filter 2B that removes low-frequency noise, and a second
It is composed of an amplifier 2C that performs stage amplification, a hum filter 2D that removes power supply noise, and a high-cut filter amplifier 2E that removes high-frequency noise and performs third-stage amplification. A P-wave dedicated amplifier 2 that emphasizes and amplifies the wave and outputs the amplified P-wave S3, and a threshold value (TH) that inputs the amplified electrocardiogram signal S2 and the amplified P-wave S3 and sets it based on the amplified electrocardiogram signal S2. By detecting the amplified P wave S3 at
P wave recognition unit 3 that recognizes P wave S4 included in amplified electrocardiogram signal S2 and outputs the recognized P wave S4
and input the electrocardiogram signal S1 obtained from the body surface,
A hiss bundle wave dedicated amplifier 4 which emphasizes and amplifies the hiss bundle wave and outputs an amplified hiss bundle wave S5, and inputs the recognized P wave S4 and amplified hiss bundle wave S5, and a hiss bundle wave recognition unit 5 which attenuates the noise contained in the amplified hiss bundle wave S5 by taking an average of the amplified hiss bundle wave S5 using the synchronization signal as a synchronization signal, and outputs a hiss bundle wave S6. Electrocardiogram P wave recognition application device.