JP2015229046A - Electrocardiographic information acquisition device - Google Patents
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- 230000002159 abnormal effect Effects 0.000 claims description 5
- 238000001514 detection method Methods 0.000 claims description 5
- 230000005856 abnormality Effects 0.000 abstract description 11
- 210000000481 breast Anatomy 0.000 abstract 2
- 238000005259 measurement Methods 0.000 description 6
- 238000003745 diagnosis Methods 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 230000006854 communication Effects 0.000 description 3
- 238000004891 communication Methods 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 230000006870 function Effects 0.000 description 2
- 230000006698 induction Effects 0.000 description 2
- 210000000709 aorta Anatomy 0.000 description 1
- 230000007175 bidirectional communication Effects 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 210000005240 left ventricle Anatomy 0.000 description 1
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Abstract
Description
本発明は、被験者の心電情報を取得する心電情報取得装置に関する。 The present invention relates to an electrocardiogram information acquisition apparatus that acquires electrocardiogram information of a subject.
特許文献1は、人体に長時間、たとえば24時間、被験者の心電情報を取得する装置として本出願人が出願した心電情報を測定する装置として特許文献1が知られている。特許文献1は、被験者の心電を長時間測定し、長時間記録するモードと、心電の異常を自覚したとき、被験者また医師が認識したときに、イベントスイッチと称するスイッチを押し、押した時点から所定時間前後の心電を記録するものである。 Patent Document 1 is known as an apparatus for measuring electrocardiographic information filed by the present applicant as an apparatus for acquiring electrocardiographic information of a subject for a long time, for example, 24 hours, on the human body. Patent Document 1 is a mode in which a subject's electrocardiogram is measured and recorded for a long time, and when a subject or doctor recognizes an abnormality in the electrocardiogram, a switch called an event switch is pressed and pressed. The electrocardiogram is recorded about a predetermined time from the time.
特許文献2は、健康管理データ判定手段が異常と判定したときの前後の心電データを一定時間記憶する健康管理支援装置で、異常と判定されたときにはその旨を報知するものである。 Patent Document 2 is a health management support device that stores electrocardiographic data before and after when the health management data determination unit determines that there is an abnormality, and notifies that fact when it is determined to be abnormal.
以上に述べた特許文献1では、被験者の心電を長時間記録するが、心電の異常を感じた時に被験者または医師がイベントスイッチと称するスイッチを押すことによってその押した前後の心電を記録するものであるが、イベントスイッチを押さなければ心電を記録するには長時間記憶するメモリが必要となる。 In Patent Document 1 described above, the electrocardiogram of the subject is recorded for a long time, but when the electrocardiogram is felt abnormal, the subject or doctor presses a switch called an event switch to record the electrocardiogram before and after the press. However, if the event switch is not pressed, a memory for storing for a long time is required to record the electrocardiogram.
特許文献2では、心電が異常時に報知するものであるが、心電情報取得装置を胸に取り付けているときは心電を測定する。すなわち心電異常判定を検知すると自動的にその前後の所定時間の心電を記録するものである。特許文献2においてその心電情報取得装置を胸から取り外したときは外部からノイズが心電異常と同じような信号の場合には同じように心電異常と同じ報知をする恐れがあるが、その点について考慮されていない。その度に医師が駆けつけて診断をするようになる欠点を有する。また、心電情報取得装置を胸から外すときに、電源スイッチを設けて電源スイッチを切断することも考えられるが、電源スイッチの切断を忘れる場合があり、そのとき外部からノイズが侵入して上述のように心電異常と同じような信号の場合には同じように心電異常と同じ報知をする恐れがある。また、電源スイッチを必要としないのでコストダウンにつながる。また、ノイズパターンを多数記憶しておいてそのパターンに合致したらノイズと判断する方法もあるが、その方法もコストアップにつながる。 In Patent Document 2, an electrocardiogram is notified when an abnormality occurs, but the electrocardiogram is measured when the electrocardiogram information acquisition device is attached to the chest. That is, when an electrocardiogram abnormality determination is detected, electrocardiograms for a predetermined time before and after that are automatically recorded. In Patent Document 2, when the electrocardiogram information acquisition device is removed from the chest, there is a possibility that the same notification as the electrocardiogram abnormality may be made in the same manner when the noise is a signal similar to the electrocardiogram abnormality from the outside. The point is not considered. Each time a doctor rushes to make a diagnosis. Also, when removing the electrocardiogram information acquisition device from the chest, it is conceivable to disconnect the power switch by providing a power switch. In the case of a signal similar to an electrocardiographic abnormality as described above, there is a possibility that the same notification as the electrocardiographic abnormality is given. In addition, since no power switch is required, the cost is reduced. In addition, there is a method of storing a large number of noise patterns and determining that the noise is matched with the pattern, but this method also leads to an increase in cost.
本発明は、このような従来の構成が有していた問題を解決しようとするものであり、心電情報取得装置を被験者から取り外した時に、コストをかけずに心電異常と判断しないようにノイズと判定して心電異常信号の発生を防ぐことを目的とするものである。 The present invention is intended to solve the problem of such a conventional configuration, and when the electrocardiogram information acquisition device is removed from the subject, it is not determined to be an electrocardiogram abnormality without cost. The object is to prevent the occurrence of an electrocardiogram abnormal signal by determining it as noise.
請求項1は、少なくとも一対の電極を備えた電極部と、前記少なくとも一対の電極の間に発生した電位に基づいて心電波形およびノイズを検出する信号波形検出部と、装着ベルトまたは貼り付けることによって胸部に固定され、心電異常の時に警告信号を発生する心電情報取得装置であって、前記心電波形の第1の閾値を越えるピーク値(R波)と次のピーク値(R波)との間に発生するノイズのピーク値が所定の第2の閾値を越えるノイズの数を除して算出されるノイズ間隔が所定値よりも小さい時、前記警告信号を発生しないように制御する心電情報取得装置を提供するものである。 According to a first aspect of the present invention, there is provided an electrode portion including at least a pair of electrodes, a signal waveform detection portion for detecting an electrocardiogram waveform and noise based on a potential generated between the at least a pair of electrodes, and a wearing belt or affixing Is an electrocardiogram information acquisition device that is fixed to the chest and generates a warning signal when an electrocardiogram is abnormal, and includes a peak value (R wave) exceeding the first threshold value and the next peak value (R wave) of the electrocardiogram waveform. When the noise interval calculated by dividing the number of noises whose noise peak value exceeds a predetermined second threshold is smaller than the predetermined value, control is performed so that the warning signal is not generated. An electrocardiogram information acquisition apparatus is provided.
請求項2は、前記本ノイズが前記所定値を越えているときは利用者に報知部を制御してその旨を報知する請求項1に記載の心電情報取得装置を提供するものである。 According to a second aspect of the present invention, there is provided the electrocardiogram information acquiring apparatus according to the first aspect, wherein when the main noise exceeds the predetermined value, the user is notified by controlling a notification unit.
上述したように、本発明の心電情報取得装置は、身体から外したときには心電異常と同じような状況が生じない。また電源スイッチを設けないので、電源スイッチを操作し忘れもなく、コスト的にも安くすむ。 As described above, the electrocardiogram information acquisition apparatus of the present invention does not have the same situation as an electrocardiogram abnormality when removed from the body. In addition, since no power switch is provided, the power switch is not forgotten and the cost can be reduced.
図1は、本発明の心電計システムの概念図を示す。 FIG. 1 shows a conceptual diagram of an electrocardiograph system of the present invention.
1は、心電計を、2はコンピュータを示し、心電計1とコンピュータ2は双方向通信を行なうことができるよう1Cで示す通信部、2Cで示す通信アダプターを備えている。 Reference numeral 1 denotes an electrocardiograph, 2 denotes a computer, and the electrocardiograph 1 and the computer 2 include a communication unit indicated by 1C and a communication adapter indicated by 2C so that bidirectional communication can be performed.
3は、心電計1を不図示の固定部材で固定するためのベルトを示し、3L、3Rを示す孔を有し、不図示の背面ゴムベルトが取り付けられ、被診断者の胸に巻き回して固定できる。 Reference numeral 3 denotes a belt for fixing the electrocardiograph 1 with a fixing member (not shown), has holes 3L and 3R, is attached with a back rubber belt (not shown), and is wound around the chest of the subject. Can be fixed.
4Lは左胸部電極、4R1、4R2は右胸部電極を示し、被診断者の胸にそれぞれ接触し、心電信号を出力する。 Reference numeral 4L denotes a left chest electrode, and 4R1 and 4R2 denote right chest electrodes, which are in contact with the chest of the subject and output an electrocardiogram signal.
5R、5G、5Yはそれぞれ赤LED、緑LED、黄LEDを示し、動作状態を示す。 5R, 5G, and 5Y indicate red LED, green LED, and yellow LED, respectively, and indicate the operating state.
6はイベントスイッチを示し、イベントスイッチ6を押してオンしたときに、その前後の心電波形を記録する。 Reference numeral 6 denotes an event switch. When the event switch 6 is pressed and turned on, the electrocardiogram waveforms before and after the event switch 6 are recorded.
7は被診断者の名前等の被診断者情報等および心電波形を記録するメモリカードを示す。 Reference numeral 7 denotes a memory card that records diagnosis subject information such as the name of the diagnosis subject and an electrocardiographic waveform.
8は、誘導コードを接続する接続端子を示す。 Reference numeral 8 denotes a connection terminal for connecting the induction cord.
9は振動モータを示し、記録開始信号が出力されてもメモリカードに記録がされないと振動モータ9が駆動されて被診断者に振動を伝達して知らせる。 Reference numeral 9 denotes a vibration motor. If a recording start signal is output but no recording is made on the memory card, the vibration motor 9 is driven to transmit the vibration to the person to be diagnosed.
10はコンピュータ2のディスプレイ、11はコンピュータ2で被診断者の名前等の被診断者情報等を入力するキーボードを示す。 Reference numeral 10 denotes a display of the computer 2, and 11 denotes a keyboard for inputting diagnosis subject information such as the name of the diagnosis subject on the computer 2.
図2は、1つのチャネル、例えばCC5誘導データを出力する1チャネル心電測定モードを示す。 FIG. 2 shows a one-channel electrocardiographic measurement mode that outputs one channel, for example CC5 lead data.
Hは被診断者で心電計1を装着したベルト3を胸に巻いて例えばCC5誘導データを測定する1チャネル心電測定モードを示す。 H indicates a 1-channel electrocardiogram measurement mode in which a belt 3 with the electrocardiograph 1 is wound around the chest and the CC5 lead data is measured, for example.
図3は、2つのチャネル、例えばCC5とCM5誘導データを出力する2チャネル誘導データを出力する2チャネル心電測定モードを示す。 FIG. 3 shows a two-channel electrocardiographic measurement mode for outputting two channels, for example, two-channel lead data for outputting CC5 and CM5 lead data.
被診断者Hに心電計1を装着したベルト3を胸に巻くと共に2チャネル用接続端子8に一端を接続する12で示す2チャネル誘導コードの他端に13で示すディスポ電極を胸の中央上部に貼り付けてCC5とCM5誘導データを出力する2チャネル心電測定モードを示す。 A belt 3 with the electrocardiograph 1 attached to the subject H is wound around the chest and one end is connected to the two-channel connection terminal 8. A two-channel electrocardiogram measurement mode in which CC5 and CM5 lead data is output by pasting on the upper part is shown.
図4は、被験者の心電位を検出した心電波形図の基本的な例を示す。 FIG. 4 shows a basic example of an electrocardiogram waveform in which the subject's electrocardiogram is detected.
P、Q、R、S、Tで示された心電図部分のうち、血液を左心室から大動脈に送り出すときに生じるR波と次のR波であるR−R間隔を取り上げる。 Among the electrocardiogram portions indicated by P, Q, R, S, and T, the R wave generated when pumping blood from the left ventricle to the aorta and the RR interval that is the next R wave are taken up.
図5は、本発明の心電情報取得装置の作動の制御をつかさどるコンピュータの作動を示すフローチャートである。 FIG. 5 is a flowchart showing the operation of the computer that controls the operation of the electrocardiogram information acquisition apparatus of the present invention.
まず、S1でR波を検出し、S2で、その検出の基準となるR波の閾を設定し、S3で、その閾を越えるR波と次の同じく閾を越えるR波の間隔、R−R時間を検出する。 First, an R wave is detected at S1, a threshold of the R wave as a reference for the detection is set at S2, and an interval between the R wave exceeding the threshold and the next R wave exceeding the threshold at S3, R− R time is detected.
S4で、R波と同様にノイズの閾を設定し、S5でR−R間でノイズ閾を越えるノイズの数をカウントする。 In S4, a noise threshold is set in the same manner as in the R wave, and in S5, the number of noises exceeding the noise threshold is counted between RR.
S6でノイズの間隔Dを、R―R時間をノイズの数で除して求める。 In S6, the noise interval D is obtained by dividing the RR time by the number of noises.
S7でノイズ間隔Dが基準となるD0より大であるかどうかを判定し、ノイズ間隔Dが、D0より大きくない場合をノイズありと判定し、自動的に心電を記録するオートトリガ機能を阻止し、S8では次のステップに進み、ジドウトリガ機能の作動が可能になる。 In S7, it is determined whether or not the noise interval D is larger than the reference D0. If the noise interval D is not larger than D0, it is determined that there is noise, and an auto trigger function for automatically recording an electrocardiogram is prevented. In S8, the process proceeds to the next step, and the operation of the jido trigger function becomes possible.
図6は、心電波形とノイズの関係を示す図で、たとえば24時間のように長時間でかつ省電力で動作させるため心電波形のサンプリング間隔を8mmsecでサンプリングをした例を示す。ここではノイズが混入している場合の心電波形を示している。 FIG. 6 is a diagram showing the relationship between the electrocardiogram waveform and noise, and shows an example in which the electrocardiogram waveform is sampled at a sampling interval of 8 mmsec in order to operate for a long time and power saving, for example, 24 hours. Here, an electrocardiogram waveform when noise is mixed is shown.
R波検出のため、R波上限閾とR波下限閾を設定し、同様にノイズ検出のためのノイズ上限閾とノイズ下限閾を設定する。 For R wave detection, an R wave upper limit threshold and an R wave lower limit threshold are set, and similarly, a noise upper limit threshold and a noise lower limit threshold for noise detection are set.
R波はR波上限閾を越え、R波下限閾より下回ったR波を1つのR波と認識し、ノイズはノイズ上限閾を越え、ノイズ下限閾を下回った時点でカウントアップする。 The R wave exceeds the R wave upper limit threshold and the R wave below the R wave lower limit threshold is recognized as one R wave, and the noise is counted up when the noise exceeds the noise upper limit threshold and falls below the noise lower limit threshold.
2つのR波を検出するとR波とR波の間の時間、R−R時間が算出され、このR−R時間内にいくつのノイズが発生しているかを算出し、図6では番号でノイズカウンタ値を示している。 When two R waves are detected, the time between the R wave and the R wave is calculated, and how many noises are generated within this RR time. The counter value is shown.
R−R時間をノイズカウンタ値で除することにより平均ノイズ時間間隔を算出する。図5では、R−R時間は240msecで、カウンタ値が7であるので、240msecを7で除するので34.28msecとなる。ここではあらかじめノイズ間隔時間が1601msec以下ではノイズとして処理される。 The average noise time interval is calculated by dividing the RR time by the noise counter value. In FIG. 5, since the RR time is 240 msec and the counter value is 7, 240 msec is divided by 7, so that 34.28 msec is obtained. Here, if the noise interval time is 1601 msec or less, it is processed as noise in advance.
本発明の実施形として図1に示すような心電計1を不図示の固定部材で固定するためのベルトの形式で述べたが、本出願人が出願した特開2012−45195号公報の図9に示したようなベルトを使用せずに心電計測定部を被験者の被測定箇所に貼り付けるタイプで実施してもよい。 As an embodiment of the present invention, the electrocardiograph 1 as shown in FIG. 1 has been described in the form of a belt for fixing with an unillustrated fixing member, but the figure of Japanese Patent Application Laid-Open No. 2012-45195 filed by the present applicant. Instead of using a belt as shown in FIG. 9, the electrocardiograph measuring unit may be affixed to the subject to be measured.
1・・・・・・・・・・・・・心電計
2・・・・・・・・・・・・・コンピュータ
2C・・・・・・・・・・・・通信アダプター
3・・・・・・・・・・・・・ベルト
4L・・・・・・・・・・・・左胸部電極
4R1、4R2・・・・・・・右胸部電極
5R、5G、5Y・・・・・・LED
6・・・・・・・・・・・・・イベントスイッチ
7・・・・・・・・・・・・・メモリカード
8・・・・・・・・・・・・・2チャネル用接続端子
9・・・・・・・・・・・・・振動モータ
10・・・・・・・・・・・・ディスプレイ
11・・・・・・・・・・・・キー
12・・・・・・・・・・・・誘導コード
13・・・・・・・・・・・・ディスポ電極
1 ... Electrocardiograph 2 ... Computer 2C ... Communication adapter 3.・ ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ Belt 4L ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ Left chest electrode 4R1, 4R2 ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ Right chest electrode 5R, 5G, 5Y ・ ・ ・ ・..LED
6 ... event switch 7 ... memory card 8 ... 2 channel connection Terminal 9 ... vibrating motor 10 ... display 11 ... key 12 ...・ ・ ・ ・ ・ ・ ・ ・ Induction code 13 ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ ・ Disposable electrode
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JP2020174690A (en) * | 2019-04-15 | 2020-10-29 | 株式会社テクノ・コモンズ | Biological signal processing device |
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