JP5428889B2 - ECG measurement device - Google Patents
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Description
本発明は、心電計測装置に関するものである。 The present invention relates to an electrocardiograph.
心電図を得る発明としては、上腕での心電信号の計測に関して開示されている（例えば、特許文献１参照）。この発明では上腕で心電信号を取る際の電極として、電極アレイの中から最大の心電信号が得られるものを選択することが記載されている。 An invention for obtaining an electrocardiogram has been disclosed regarding the measurement of an electrocardiogram signal in the upper arm (see, for example, Patent Document 1). In this invention, it is described that an electrode for obtaining a maximum electrocardiogram signal is selected from the electrode array as an electrode for taking an electrocardiogram signal with the upper arm.
しかし、特許文献１では電極アレイの中から最大の心電信号を得る具体的な方法は開示されていない。また、電極アレイの数が多くなるにつれ組合せ数は多くなり、総当たりにより心電信号が大きく取れる信号を探していたのでは、時間がかかる虞がある。 However, Patent Document 1 does not disclose a specific method for obtaining the maximum electrocardiographic signal from the electrode array. In addition, as the number of electrode arrays increases, the number of combinations increases, and it may take time to search for a signal that can obtain a larger electrocardiogram signal by round robin.
本発明は、上述の課題の少なくとも一部を解決するためになされたものであり、以下の形態又は適用例として実現することが可能である。 SUMMARY An advantage of some aspects of the invention is to solve at least a part of the problems described above, and the invention can be implemented as the following forms or application examples.
［適用例１］生体の上腕に接触した複数の第１電極からなる電極アレイと、前記電極アレイより手首側の前記生体に接触した第２電極と、前記電極アレイの全ての前記第１電極について、前記第２電極との電位を差動検出することによって前記生体の心電波形のＲ波を計測する第１心電計測部と、前記第１心電計測部によるＲ波の計測結果に基づいて、最も大きな振幅で正の極性を持つＲ波を計測した前記電極アレイのうちの１つの第１電極と、最も大きな振幅で負の極性を持つＲ波を計測した前記電極アレイのうちの他の１つの第１電極とを特定する心電特定部と、前記心電特定部で特定された前記電極アレイのうちの１つの第１電極と他の１つの第１電極との電位を差動検出することによって前記生体の心電波形のＲ波を計測する第２心電計測部と、を含むことを特徴とする心電計測装置。 Application Example 1 Regarding an electrode array composed of a plurality of first electrodes in contact with the upper arm of a living body, a second electrode in contact with the living body on the wrist side from the electrode array, and all the first electrodes in the electrode array A first electrocardiogram measurement unit that measures an R wave of the electrocardiographic waveform of the living body by differentially detecting a potential with the second electrode, and a measurement result of the R wave by the first electrocardiogram measurement unit One of the electrode arrays that has measured the R wave having the largest amplitude and the positive polarity, and the other one of the electrode arrays that has measured the R wave having the largest amplitude and the negative polarity. An electrocardiogram specifying unit that specifies one first electrode of the first electrode; and a potential between one first electrode of the electrode array specified by the electrocardiogram specifying unit and the other first electrode is differentially differentiated A second heart for measuring the R wave of the electrocardiographic waveform of the living body by detecting Electrocardiograph which comprises a measuring unit.
これによれば、各第１電極と第２電極との間の心電波形のＲ波を最も大きく検出できる電極の組合せを選択することで、心電波形の検出に最適な電極の組合せを選ぶことができる。これにより、安定した心電波形を計測できるので、心電波形のＲ波の検出精度を高めることができる。 According to this, by selecting an electrode combination that can detect the R wave of the electrocardiogram waveform between each first electrode and the second electrode most greatly, an electrode combination that is optimal for the detection of the electrocardiogram waveform is selected. be able to. Thereby, since the stable electrocardiogram waveform can be measured, the detection accuracy of the R wave of the electrocardiogram waveform can be increased.
［適用例２］上記心電計測装置であって、前記電極アレイの複数の第１電極は、前記上腕の円周上に等間隔で置かれていることを特徴とする心電計測装置。 Application Example 2 In the electrocardiograph, the plurality of first electrodes of the electrode array are placed on the circumference of the upper arm at equal intervals.
これによれば、心電波形のＲ波の検出精度を容易に高めることができる。 According to this, the detection accuracy of the R wave of the electrocardiogram waveform can be easily increased.
［適用例３］上記心電計測装置であって、前記第２電極は、前記上腕に接触し該上腕を一周する長さであることを特徴とする心電計測装置。 Application Example 3 In the electrocardiogram measurement apparatus, the second electrode has a length that contacts the upper arm and goes around the upper arm.
これによれば、第２電極として、上腕を一周するような電極を用いることで、上腕の電位部分を加算したような中間電位を作り、その電位と各第１電極との電位を差動検出することができるので、心電波形のＲ波の検出精度をさらに高めることができる。 According to this, by using an electrode that goes around the upper arm as the second electrode, an intermediate potential is obtained by adding the potential portions of the upper arm, and the potential between the potential and each first electrode is differentially detected. Therefore, the detection accuracy of the R wave of the electrocardiographic waveform can be further increased.
［適用例４］上記心電計測装置であって、前記心電特定部は、各心電波形を該心電波形のＲ波の振幅と極性とでマッピングすることを特徴とする心電計測装置。 Application Example 4 In the electrocardiogram measurement apparatus, the electrocardiogram identification unit maps each electrocardiogram waveform with the amplitude and polarity of the R wave of the electrocardiogram waveform. .
これによれば、最も大きな振幅で正の極性を持つＲ波と、最も大きな振幅で負の極性を持つＲ波とを容易に特定することができる。 According to this, it is possible to easily identify the R wave having the largest amplitude and the positive polarity and the R wave having the largest amplitude and the negative polarity.
［適用例５］上記心電計測装置であって、２つの入力の電位を差動増幅する差動増幅部と、交流信号を出力するスイッチ制御部と、前記スイッチ制御部から出力された交流信号に応じて、前記差動増幅部に入力する１つの心電信号を前記第１電極と前記第２電極とのどちらか一方の心電信号に切り替える機械式のスイッチと、をさらに含むことを特徴とする心電計測装置。 Application Example 5 In the electrocardiogram measurement apparatus, a differential amplifier that differentially amplifies two input potentials, a switch controller that outputs an AC signal, and an AC signal output from the switch controller And a mechanical switch that switches one electrocardiographic signal input to the differential amplification unit to one of the first electrode and the second electrode. ECG measuring device.
これによれば、差動増幅部に入力する１つの心電信号を第１電極と第２電極とのどちらか一方の心電信号に容易に切り替えることができる。 According to this, one electrocardiographic signal input to the differential amplification unit can be easily switched to one of the first electrode and the second electrode.
（第１の実施形態）
図１は、本実施形態に係る心電計測装置のハードウェアの構成を示した図である。本実施形態に係る心電計測装置２は、第１電極としての電極１０ａ〜１０ｇからなる電極アレイ１０、電極アレイ１０の中から心電波形の計測に使用する電極を選択するために使用する第２電極としての電極Ｒ１２、電極アレイ１０の中から２つの電極を選択し、後段へ接続するマルチプレクサー（ＭＵＸ）１４、予め定められた周波数の交流信号を出力するスイッチ制御部１６、マルチプレクサー１４の一方の出力と電極Ｒ１２とのうちのどちらかを後段へ接続するスイッチ１８、２つの入力の電位の差動増幅を行う差動増幅部としての計装アンプ２０、心電信号から不要な高域成分を除去するＬＰＦ（低域通過フィルター）２２、心電信号を必要な振幅レベルまで増幅する増幅部２４、アナログ信号をデジタル信号に変換するＡ／Ｄ変換部２６、計測した心電信号をもとに種々の処理や電極選択のためのアルゴリズムを実行し、マルチプレクサー１４やスイッチ制御部１６を制御する制御部２８で構成される。
(First embodiment)
FIG. 1 is a diagram illustrating a hardware configuration of the electrocardiogram measurement apparatus according to the present embodiment. The electrocardiogram measuring apparatus 2 according to the present embodiment is used to select an electrode array 10 composed of electrodes 10a to 10g as first electrodes, and an electrode used for measuring an electrocardiographic waveform from the electrode array 10. Two electrodes are selected from the electrode R12 as the two electrodes and the electrode array 10, and a multiplexer (MUX) 14 connected to the subsequent stage, a switch control unit 16 for outputting an AC signal having a predetermined frequency, and the multiplexer 14 Switch 18 that connects either one of the output of electrode R12 and electrode R12 to the subsequent stage, instrumentation amplifier 20 as a differential amplification unit that differentially amplifies the potential of two inputs, an unnecessary high voltage from an electrocardiogram signal LPF (low-pass filter) 22 for removing band components, an amplifying unit 24 for amplifying an electrocardiogram signal to a required amplitude level, and A / D conversion for converting an analog signal into a digital signal 26, executes the algorithms for various processing and electrode selection based on the electrocardiographic signal measured, and a control unit 28 for controlling the multiplexer 14 and the switch controller 16.
電極アレイ１０は、人体（生体）Ａの上腕Ｂ（図４参照）に接触する複数の電極１０ａ〜１０ｇからなる。 The electrode array 10 includes a plurality of electrodes 10a to 10g that are in contact with an upper arm B (see FIG. 4) of a human body (living body) A.
電極１０ａ〜１０ｇは、心臓の活動に伴う人体Ａの電位の変化を検知する電極であり、心電波形を得る際に人体Ａに貼り付けられる電極である。電極１０ａ〜１０ｇは、上腕Ｂの円周上に等間隔に貼り付けられてもよい。電極１０ａ〜１０ｇはマルチプレクサー１４に接続されている。 The electrodes 10a to 10g are electrodes that detect a change in the potential of the human body A accompanying the activity of the heart, and are electrodes that are attached to the human body A when an electrocardiographic waveform is obtained. The electrodes 10a to 10g may be attached to the circumference of the upper arm B at equal intervals. The electrodes 10 a to 10 g are connected to the multiplexer 14.
電極Ｒ１２は、電極アレイ１０の電極１０ａ〜１０ｇとは異なる電極である。電極Ｒ１２は、上腕Ｂの電極アレイ１０より肘側（手首側）の上腕Ｂに貼り付けられる電極である。なお、電極Ｒ１２は、前腕あるいは手のひらに貼り付けつけてもよい。電極Ｒ１２はスイッチ１８に接続されている。 The electrode R12 is an electrode different from the electrodes 10a to 10g of the electrode array 10. The electrode R12 is an electrode attached to the upper arm B on the elbow side (wrist side) from the electrode array 10 of the upper arm B. The electrode R12 may be attached to the forearm or palm. The electrode R12 is connected to the switch 18.
マルチプレクサー１４は、機械的なスイッチと電子回路とがひとつのシリコン基板に形成されたＩＣ（Integrated Circuit）、即ちＭＥＭＳ（Micro Electro Mechanical Systems）である。マルチプレクサー１４は、電極１０ａ〜１０ｇ、スイッチ１８、及び計装アンプ２０に接続されている。 The multiplexer 14 is an IC (Integrated Circuit) in which a mechanical switch and an electronic circuit are formed on one silicon substrate, that is, a MEMS (Micro Electro Mechanical Systems). The multiplexer 14 is connected to the electrodes 10 a to 10 g, the switch 18, and the instrumentation amplifier 20.
スイッチ制御部１６は、スイッチ１８の開／閉を制御する信号を出力する電子回路を備えており、制御信号は、ＣＰＵ（Central Processing Unit）３０からの制御によりＨレベルかＬレベルの方形波の信号を出力する。スイッチ制御部１６は、スイッチ１８及び制御部２８に接続されている。 The switch control unit 16 includes an electronic circuit that outputs a signal for controlling opening / closing of the switch 18, and the control signal is a square wave of H level or L level under the control of a CPU (Central Processing Unit) 30. Output a signal. The switch control unit 16 is connected to the switch 18 and the control unit 28.
スイッチ１８は、導体の接触／非接触により電気信号の導通／遮断を行う機械式のスイッチあるいはトランジスター等を使用する電気的なスイッチである。スイッチ１８は、スイッチ制御部１６による制御の下、計装アンプ２０の入力端子の接続先を、マルチプレクサー１４と電極Ｒ１２とのいずれかの出力端子に切り替える。スイッチ１８の開／閉は、スイッチ制御部１６から出力される信号で制御され、スイッチ制御部１６から出力された方形波の信号の電圧が予め定められた閾値を超えたＨレベルとなると計装アンプ２０の入力端子の接続先がマルチプレクサー１４となり、スイッチ制御部１６から出力された信号のレベルが予め定められた閾値以下のＬレベルとなると計装アンプ２０の入力端子の接続先が電極Ｒ１２となる。スイッチ１８は、マルチプレクサー１４、電極Ｒ１２、計装アンプ２０、及びスイッチ制御部１６に接続されている。 The switch 18 is an electrical switch using a mechanical switch or a transistor that conducts / cuts off an electric signal by contact / non-contact of a conductor. The switch 18 switches the connection destination of the input terminal of the instrumentation amplifier 20 to one of the output terminals of the multiplexer 14 and the electrode R12 under the control of the switch control unit 16. The opening / closing of the switch 18 is controlled by a signal output from the switch control unit 16, and instrumentation is performed when the voltage of the square wave signal output from the switch control unit 16 becomes an H level exceeding a predetermined threshold. The connection destination of the input terminal of the amplifier 20 becomes the multiplexer 14, and when the level of the signal output from the switch control unit 16 becomes an L level equal to or lower than a predetermined threshold, the connection destination of the input terminal of the instrumentation amplifier 20 is the electrode R12. It becomes. The switch 18 is connected to the multiplexer 14, the electrode R 12, the instrumentation amplifier 20, and the switch control unit 16.
計装アンプ２０は、高い入力インピーダンスを持った差動増幅専用のオペアンプである。計装アンプ２０は、マルチプレクサー１４あるいはマルチプレクサー１４と電極Ｒ１２との２つの入力信号の差分を一定係数（差動利得）で増幅する差動増幅回路である。計装アンプ２０のゲインは例えば２１である。計装アンプ２０は、マルチプレクサー１４、スイッチ１８、及びＬＰＦ２２に接続されている。 The instrumentation amplifier 20 is an operational amplifier dedicated to differential amplification having a high input impedance. The instrumentation amplifier 20 is a differential amplifier circuit that amplifies the multiplexer 14 or the difference between the two input signals of the multiplexer 14 and the electrode R12 by a constant coefficient (differential gain). The gain of the instrumentation amplifier 20 is 21, for example. The instrumentation amplifier 20 is connected to the multiplexer 14, the switch 18, and the LPF 22.
ＬＰＦ２２は、フィルター回路の一種で、低周波を良く通し、ナイキスト周波数より高い周波数の帯域を通さないフィルターである。ＬＰＦ２２は、カットオフ周波数ｆｃ＝４０Ｈｚのローパスフィルターであり、計装アンプ２０から供給された心電信号の４０Ｈｚ以上の高周波成分を除去することでサンプリング時の折り返し雑音（エイリアス）を排除して増幅部２４に供給する。ＬＰＦ２２は、計装アンプ２０及び増幅部２４に接続されている。 The LPF 22 is a type of filter circuit, and is a filter that passes low frequencies well and does not pass a band of frequencies higher than the Nyquist frequency. The LPF 22 is a low-pass filter having a cut-off frequency fc = 40 Hz, and eliminates aliasing at the time of sampling by removing high-frequency components of 40 Hz or more of the electrocardiogram signal supplied from the instrumentation amplifier 20 to amplify. To the unit 24. The LPF 22 is connected to the instrumentation amplifier 20 and the amplification unit 24.
増幅部２４は、入力された心電信号を増幅する電子回路である。増幅部２４は、ＬＰＦ２２及びＡ／Ｄ変換部２６に接続されている。 The amplifying unit 24 is an electronic circuit that amplifies an input electrocardiogram signal. The amplification unit 24 is connected to the LPF 22 and the A / D conversion unit 26.
Ａ／Ｄ変換部２６は、増幅部２４で増幅されて出力されたアナログ信号をデジタル信号に変換する回路である。Ａ／Ｄ変換部２６は、高周波成分が除去された心電信号を所定のサンプリング周波数でデジタル信号に変換して制御部２８に供給する。Ａ／Ｄ変換部２６は、増幅部２４及び制御部２８に接続されている。 The A / D conversion unit 26 is a circuit that converts the analog signal amplified and output by the amplification unit 24 into a digital signal. The A / D converter 26 converts the electrocardiogram signal from which the high frequency component has been removed into a digital signal at a predetermined sampling frequency and supplies the digital signal to the controller 28. The A / D conversion unit 26 is connected to the amplification unit 24 and the control unit 28.
制御部２８は、ＣＰＵ３０、ＲＯＭ（Read Only Memory）３２、ＲＡＭ（Random Access Memory）３４などを備えたマイクロコンピューターである。制御部２８が、ＲＯＭ３２に記憶されているプログラムを実行すると、Ａ／Ｄ変換部２６から入力されるデジタル信号を解析して心電図を表示部３６に表示する機能や、求めた心電図を示すデータを生成し、生成したデータを記憶部３８に記憶させる機能が実現する。制御部２８では、取得した心電信号の保存、解析した心電波形のＲ波から心拍数の算出などが行われる。 The control unit 28 is a microcomputer including a CPU 30, a ROM (Read Only Memory) 32, a RAM (Random Access Memory) 34, and the like. When the control unit 28 executes the program stored in the ROM 32, the digital signal input from the A / D conversion unit 26 is analyzed and an electrocardiogram is displayed on the display unit 36, and data indicating the obtained electrocardiogram is displayed. A function of generating and storing the generated data in the storage unit 38 is realized. The controller 28 stores the acquired electrocardiogram signal, calculates the heart rate from the R wave of the analyzed electrocardiogram waveform, and the like.
本実施形態において、制御部２８では第１心電計測部、心電特定部、第２心電計測部が実現される。上記各部は、ＣＰＵ３０がＡ／Ｄ変換部２６からの心電信号を所定のプログラムを処理することで実現される。 In the present embodiment, the control unit 28 implements a first electrocardiogram measurement unit, an electrocardiogram identification unit, and a second electrocardiogram measurement unit. Each of the above units is realized by the CPU 30 processing a predetermined program on the electrocardiogram signal from the A / D conversion unit 26.
第１心電計測部では、電極アレイ１０の全ての電極１０ａ〜１０ｇについて、電極Ｒ１２との電位を差動検出することによって人体Ａの心電波形のＲ波を計測している。 The first electrocardiogram measurement unit measures the R wave of the electrocardiographic waveform of the human body A by differentially detecting the potential with the electrode R12 for all the electrodes 10a to 10g of the electrode array 10.
心電特定部では、第１心電計測部によって計測された各心電波形を心電波形のＲ波の振幅と極性とでマッピングしている。また、心電特定部では、マッピング結果に基づいて、最も大きな振幅で正の極性を持つＲ波を計測した電極アレイ１０のうちの１つの電極と、最も大きな振幅で負の極性を持つＲ波を計測した電極アレイ１０のうちの他の１つの電極とを特定している。 The electrocardiogram identification unit maps each electrocardiogram waveform measured by the first electrocardiogram measurement unit with the amplitude and polarity of the R wave of the electrocardiogram waveform. Also, the electrocardiogram identification unit, based on the mapping result, one electrode in the electrode array 10 that has measured the R wave having the largest amplitude and the positive polarity, and the R wave having the largest amplitude and the negative polarity. The other one electrode of the electrode array 10 that has measured is specified.
第２心電計測部では、心電特定部で特定された電極アレイ１０のうちの１つの電極と他の１つの電極との電位を差動検出することによって人体Ａの心電波形のＲ波を計測している。 In the second electrocardiogram measurement unit, the R wave of the electrocardiographic waveform of the human body A is detected by differentially detecting the potential between one electrode of the electrode array 10 specified by the electrocardiogram specifying unit and the other electrode. Is measured.
表示部３６は、画像を表示する表示デバイス（例えば、液晶ディスプレイや有機ＥＬ（Electro Luminescence）ディスプレイ）を有しており、制御部２８の制御の下、心電図の画像や、心電計測装置２を操作するための画面及び文字列などを表示する。 The display unit 36 has a display device (for example, a liquid crystal display or an organic EL (Electro Luminescence) display) that displays an image. Under the control of the control unit 28, an electrocardiogram image or the electrocardiograph 2 is displayed. Displays screens and character strings for operations.
記憶部３８は、不揮発性メモリーを有しており、制御部２８の制御の下、制御部２８が生成したデータを記憶する。 The storage unit 38 has a nonvolatile memory, and stores data generated by the control unit 28 under the control of the control unit 28.
操作部４０は、心電計測装置２を操作するためのボタン等の操作子を複数有しており、制御部２８に接続されている。操作子がユーザーによって操作されると、操作された操作子を示す信号が制御部２８へ供給される。制御部２８は、この信号をもとに操作者の行った操作や操作者からの指示を特定し、各部を制御する。 The operation unit 40 includes a plurality of operation elements such as buttons for operating the electrocardiograph 2, and is connected to the control unit 28. When the operator is operated by the user, a signal indicating the operated operator is supplied to the control unit 28. The control unit 28 specifies an operation performed by the operator and an instruction from the operator based on this signal, and controls each unit.
本実施形態では、上腕Ｂにおいて、心電信号には２つの異なる信号が伝わってきており、計測部位により信号の大きさが異なる。上腕Ｂを円周上に一周覆うような電極アレイ１０を配置させ、最適な電極アレイ１０の電極を選択することにより、安定した心電波形のＲ波を計測することができる。 In the present embodiment, in the upper arm B, two different signals are transmitted to the electrocardiogram signal, and the magnitude of the signal differs depending on the measurement site. A stable electrocardiographic R wave can be measured by arranging the electrode array 10 so as to cover the upper arm B on the circumference and selecting an electrode of the optimal electrode array 10.
ここで、心電波形におけるＲ波について説明する。
図２は、心電波形、すなわち心臓の活動電位の時間的変化の正常波形を示した図である。典型的な正常波形は、心拍１回ごとに大きくＰ、Ｑ、Ｒ、Ｓ、Ｔの５つの波で構成され、中でも目立つＱ、Ｒ、Ｓ波は一括してＱＲＳ波と呼ばれる。図にはないが、これ以外にもＵ波という波が存在する。Ｐ波は、心房の興奮により起こる活動電位の波であり、ＱＲＳ波は、心室の興奮により起こる活動電位の波であり、Ｔ波は、興奮した心室の心筋細胞が再分極する過程で起こる活動電位の波である。心房に溜まった血液を心室に送るために心室が収縮する。このときの活動電位がＰ波であり、このとき心室が膨張状態になる。次に、心室が激しく収縮し、心室の血液を全身に送り出す。このときの活動電位がＲ−Ｔ波となる。
Here, the R wave in the electrocardiogram waveform will be described.
FIG. 2 is a diagram showing an electrocardiogram waveform, that is, a normal waveform of a temporal change in the action potential of the heart. A typical normal waveform is largely composed of five waves of P, Q, R, S, and T for each heartbeat, and conspicuous Q, R, and S waves are collectively referred to as QRS waves. Although not shown in the figure, there are other waves called U waves. P wave is an action potential wave caused by atrial excitation, QRS wave is an action potential wave caused by ventricular excitation, and T wave is an activity that occurs in the process of repolarization of excited ventricular cardiomyocytes. It is a wave of potential. The ventricle contracts to send blood accumulated in the atria to the ventricle. The action potential at this time is a P wave, and the ventricle is in an inflated state at this time. Next, the ventricle contracts violently, sending ventricular blood to the whole body. The action potential at this time is an RT wave.
図３は、左腕の正面図であり、本実施形態に係る１つの局面による電極アレイ１０及び電極Ｒ１２の配置場所を示した図である。図３に示すように、電極Ｒ１２を上腕Ｂの肘側へ、電極アレイ１０の電極１０ａを上腕Ｂの肩側へ配置し、電極Ｒ１２と電極１０ａとの電位を差動検出し、上記構成を通すことにより心電波形のＲ波が計測できる。一方、電極アレイ１０の電極１０ｂを電極１０ａと異なる位置へ配置した場合、電極１０ｂで計測した心電波形のＲ波の極性が電極１０ａで計測した心電波形のＲ波の極性と異なる信号を計測することができる。これは上腕Ｂに２つの異なる心電信号が伝わってきており、上腕Ｂを伝播する際に混ざりながら信号が伝わっていると考えられる。肘側の上腕Ｂに配置された電極Ｒ１２は、混ざった信号を検出しており、電位的には中間点を表している。一方、電極１０ａ，１０ｂは上腕Ｂにおいて完全に混ざった信号となる前の別々の信号を検出している。 FIG. 3 is a front view of the left arm, and is a view showing the arrangement location of the electrode array 10 and the electrode R12 according to one aspect according to the present embodiment. As shown in FIG. 3, the electrode R12 is arranged on the elbow side of the upper arm B, the electrode 10a of the electrode array 10 is arranged on the shoulder side of the upper arm B, and the potential of the electrode R12 and the electrode 10a is differentially detected. The R wave of the electrocardiogram waveform can be measured by passing it through. On the other hand, when the electrode 10b of the electrode array 10 is arranged at a position different from the electrode 10a, a signal in which the polarity of the R wave of the electrocardiographic waveform measured by the electrode 10b is different from the polarity of the R wave of the electrocardiographic waveform measured by the electrode 10a. It can be measured. It is considered that two different electrocardiographic signals are transmitted to the upper arm B, and the signals are transmitted while being mixed when propagating through the upper arm B. The electrode R12 disposed on the upper arm B on the elbow side detects a mixed signal and represents an intermediate point in terms of potential. On the other hand, the electrodes 10a and 10b detect separate signals before the signals are completely mixed in the upper arm B.
本実施形態では上記特徴に注目し、以下の手順により電極アレイ１０の中から差動検出に好適な２つの電極を選択する。 In the present embodiment, paying attention to the above features, two electrodes suitable for differential detection are selected from the electrode array 10 by the following procedure.
図４及び図５は、左腕の正面図であり、本実施形態に係る１つの局面による電極アレイ１０及び電極Ｒ１２の配置場所を示した図である。図４に示すように、まず、心電図を計測される被計測者（生体）に電極１０ａ〜１０ｇ、電極Ｒ１２が貼り付けられる。具体的には、上腕Ｂには、導電性を有するジェルが塗られ、このジェルを介して電極１０ａ〜１０ｇは上腕Ｂの肩側、電極Ｒ１２は上腕Ｂの肘側に貼り付けられる。また、電極１０ａ〜１０ｇは上腕Ｂの円周上に等間隔に貼り付けられる。 4 and 5 are front views of the left arm, and are diagrams showing the arrangement locations of the electrode array 10 and the electrode R12 according to one aspect of the present embodiment. As shown in FIG. 4, first, the electrodes 10a to 10g and the electrode R12 are attached to the measurement subject (biological body) whose electrocardiogram is measured. Specifically, a conductive gel is applied to the upper arm B, and the electrodes 10a to 10g are attached to the shoulder side of the upper arm B and the electrode R12 is attached to the elbow side of the upper arm B through the gel. The electrodes 10a to 10g are attached to the circumference of the upper arm B at equal intervals.
次に、被計測者が心臓の計測の開始を指示する操作を操作部４０において行うと、制御部２８は、スイッチ制御部１６を動作させる信号を出力する。この信号をスイッチ制御部１６が受け取ると、制御信号がＬレベルの方形波の信号をスイッチ１８へ出力する。そして、この信号がスイッチ１８に供給されると計装アンプ２０の入力端子の接続先が電極Ｒ１２に接続される。 Next, when the measurement subject performs an operation for instructing the start of heart measurement in the operation unit 40, the control unit 28 outputs a signal for operating the switch control unit 16. When the switch control unit 16 receives this signal, it outputs a square wave signal whose control signal is L level to the switch 18. When this signal is supplied to the switch 18, the connection destination of the input terminal of the instrumentation amplifier 20 is connected to the electrode R12.
マルチプレクサー１４により選択された電極１０ａ〜１０ｇのうちの１つの電極とスイッチ１８により選択された電極Ｒ１２とから出力される信号、つまり心臓の活動に伴う電位の変化を示す信号は、計装アンプ２０で差動増幅される。計装アンプ２０で差動増幅された信号は、ＬＰＦ２２で高周波成分が除去された後、増幅部２４に入力される。増幅部２４で増幅された信号は、Ａ／Ｄ変換部２６でデジタル信号に変換された後、制御部２８に入力される。 A signal output from one of the electrodes 10a to 10g selected by the multiplexer 14 and the electrode R12 selected by the switch 18, that is, a signal indicating a change in potential accompanying the activity of the heart is an instrumentation amplifier. 20 is differentially amplified. The signal differentially amplified by the instrumentation amplifier 20 is input to the amplifier 24 after the high frequency component is removed by the LPF 22. The signal amplified by the amplifier 24 is converted into a digital signal by the A / D converter 26 and then input to the controller 28.
制御部２８は、Ａ／Ｄ変換部２６から出力されたデジタル信号を受け取ると、第１心電計測部で受け取ったデジタル信号から電極の電位を計測し、この信号に基づいて電極１０ａ〜１０ｇのうちの１つの電極と電極Ｒ１２とにおける電位の変化の波形、即ち心電図を求め、各電極の波形の画像が表示部３６に表示されるように表示部３６を制御する。なお、制御部２８は、Ａ／Ｄ変換部２６から供給されたデジタル信号を記憶部３８に記憶させる処理も行う。 When the control unit 28 receives the digital signal output from the A / D conversion unit 26, the control unit 28 measures the potential of the electrode from the digital signal received by the first electrocardiogram measurement unit, and based on this signal, the electrodes 10a to 10g. A waveform of a change in potential at one of the electrodes and the electrode R12, that is, an electrocardiogram is obtained, and the display unit 36 is controlled so that an image of the waveform of each electrode is displayed on the display unit 36. The control unit 28 also performs processing for storing the digital signal supplied from the A / D conversion unit 26 in the storage unit 38.
次に、電極１０ａ〜１０ｇで計測された心電波形から、Ｒ波が最も大きく極性がプラスのものと極性がマイナスのものをそれぞれ選択する。例えば、図５の丸で囲んだ部分４２に示すように、電極１０ｇがプラス極性のＲ波、また、丸で囲んだ部分４４に示すように、電極１０ｄがマイナス極性のＲ波として選択される。 Next, from the electrocardiogram waveforms measured by the electrodes 10a to 10g, one having the largest R wave and having a positive polarity and one having a negative polarity are selected. For example, as shown in a circled portion 42 in FIG. 5, the electrode 10g is selected as a positive polarity R wave, and as shown in a circled portion 44, the electrode 10d is selected as a negative polarity R wave. .
具体的には、心電特定部で第１心電計測部によって計測された心電波形の最大ピークのＲ波の振幅と極性とがマッピングされる。また、心電特定部では、マッピング結果に基づいて、最も大きな振幅で正の極性を持つＲ波を計測した電極アレイ１０のうちの１つの電極と、最も大きな振幅で負の極性を持つＲ波を計測した電極アレイ１０のうちの他の１つの電極とが特定される。ここで、ピーク検出には一般的なピーク検出方法や特定の波形パターン（例えば心電波形のＲ波）との相関演算による相関値などを用いることができる。 Specifically, the amplitude and polarity of the R wave of the maximum peak of the electrocardiogram waveform measured by the first electrocardiogram measurement unit are mapped by the electrocardiogram identification unit. Also, the electrocardiogram identification unit, based on the mapping result, one electrode in the electrode array 10 that has measured the R wave having the largest amplitude and the positive polarity, and the R wave having the largest amplitude and the negative polarity. The other one electrode of the electrode array 10 that has measured is specified. Here, for peak detection, a general peak detection method or a correlation value obtained by correlation calculation with a specific waveform pattern (for example, an R wave of an electrocardiogram waveform) can be used.
次に、上記で選択された２つの電極１０ｄ，１０ｇを用いて、その電極間の電位を差動検出することにより、上記同様に心電波形のＲ波を検出する。このとき、図１に示すように、マルチプレクサー１４は上記で選択された２つの電極１０ｄ，１０ｇの心電信号を計装アンプ２０へ出力するように制御され、スイッチ１８はマルチプレクサー１４の心電信号を計装アンプ２０へ接続するように制御される。 Next, by using the two electrodes 10d and 10g selected above and differentially detecting the potential between the electrodes, the R wave of the electrocardiographic waveform is detected as described above. At this time, as shown in FIG. 1, the multiplexer 14 is controlled to output the electrocardiographic signals of the two electrodes 10 d and 10 g selected above to the instrumentation amplifier 20, and the switch 18 is controlled by the heart of the multiplexer 14. The electric signal is controlled to be connected to the instrumentation amplifier 20.
本実施形態では、電極アレイ１０の電極１０ｄ，１０ｇを選択することで、上腕Ｂの円周上において振幅を大きく取れる電極の組合せ候補を、少ない演算で特定することができる。なお、電極アレイ１０を７つの電極１０ａ〜１０ｇとして説明を行ったが、電極アレイ１０の電極が増えれば増えるほど組合せが増えるため、特定の２つを選択することが困難となり、本実施形態のアルゴリズムにより選択を簡略化できる効果は大きくなる。 In the present embodiment, by selecting the electrodes 10d and 10g of the electrode array 10, it is possible to identify electrode combination candidates that can have a large amplitude on the circumference of the upper arm B with a small number of calculations. The electrode array 10 has been described as having seven electrodes 10a to 10g. However, as the number of electrodes in the electrode array 10 increases, the number of combinations increases. Therefore, it is difficult to select a specific two. The effect that the selection can be simplified by the algorithm is increased.
（第２の実施形態）
第１の実施形態では、電極Ｒ１２を２つの心電信号が混ざった信号を検出するために上腕Ｂの電極アレイ１０より肘側の上腕Ｂへ配置する構成を説明した。
(Second Embodiment)
In the first embodiment, the configuration in which the electrode R12 is arranged in the upper arm B on the elbow side from the electrode array 10 of the upper arm B in order to detect a signal in which two electrocardiographic signals are mixed has been described.
図６は、左腕の正面図であり、本実施形態に係る１つの局面による電極アレイ１０及び電極Ｒ４６の配置場所を示した図である。本実施形態では、図６に示すように、第２電極としての電極Ｒ４６を上腕Ｂに配置された電極アレイ１０より肘側の上腕Ｂへ配置し、上腕Ｂを一周するような１つの電極として用いる。電極アレイ１０は上腕Ｂの付け根周辺（脇の下）に装着されている。本実施形態に係る心電計測装置の電極Ｒ４６は、上腕Ｂに接触し、上腕Ｂを一周する長さの電極で構成されている。電極Ｒ４６では、電極Ｒ４６が設けられた上腕Ｂの電位部分を加算したような中間電位が作られる。その電位と各電極１０ａ〜１０ｇとの差動検出を行うことで、第１の実施形態と同様なアルゴリズムを実行する。 FIG. 6 is a front view of the left arm, and is a view showing an arrangement place of the electrode array 10 and the electrode R46 according to one aspect according to the present embodiment. In the present embodiment, as shown in FIG. 6, the electrode R46 as the second electrode is arranged on the upper arm B on the elbow side from the electrode array 10 arranged on the upper arm B, and as one electrode that goes around the upper arm B. Use. The electrode array 10 is mounted around the base (armpit) of the upper arm B. The electrode R46 of the electrocardiograph according to the present embodiment is configured with an electrode having a length that contacts the upper arm B and goes around the upper arm B. In the electrode R46, an intermediate potential is created such that the potential portion of the upper arm B provided with the electrode R46 is added. By performing differential detection between the potential and each of the electrodes 10a to 10g, an algorithm similar to that of the first embodiment is executed.
本実施形態では、２つの心電信号の混合が十分でない上腕Ｂの位置において、電極Ｒ４６を用いることにより、第１の実施形態と同様の効果を得ることができる。 In the present embodiment, the same effect as in the first embodiment can be obtained by using the electrode R46 at the position of the upper arm B where mixing of two electrocardiographic signals is not sufficient.
なお、電極Ｒ４６は、厳密に上腕Ｂを一周する必要はなく、両方の心電信号が混ざる長さの電極とすればよい。また、一枚の電極ではなく、複数の電極を導線でつなぐ構成としてもよい。 The electrode R46 does not need to go around the upper arm B strictly, and may be an electrode having a length in which both electrocardiographic signals are mixed. Moreover, it is good also as a structure which connects several electrodes with a conducting wire instead of one electrode.
２…心電計測装置 １０…電極アレイ １０ａ〜１０ｇ…電極（第１電極） １２…電極Ｒ（第２電極） １４…マルチプレクサー １６…スイッチ制御部 １８…スイッチ ２０…計装アンプ ２２…ＬＰＦ ２４…増幅部 ２６…Ａ／Ｄ変換部 ２８…制御部 ３０…ＣＰＵ ３２…ＲＯＭ ３４…ＲＡＭ ３６…表示部 ３８…記憶部 ４０…操作部 ４２，４４…部分 ４６…電極Ｒ（第２電極）。 DESCRIPTION OF SYMBOLS 2 ... Electrocardiograph 10 ... Electrode array 10a-10g ... Electrode (1st electrode) 12 ... Electrode R (2nd electrode) 14 ... Multiplexer 16 ... Switch control part 18 ... Switch 20 ... Instrumentation amplifier 22 ... LPF 24 ... Amplifier 26 ... A / D converter 28 ... Control part 30 ... CPU 32 ... ROM 34 ... RAM 36 ... Display part 38 ... Storage part 40 ... Operating part 42, 44 ... Part 46 ... Electrode R (second electrode).
Claims (5)
前記電極アレイより手首側の前記生体に接触した第２電極と、
前記電極アレイの全ての前記第１電極について、前記第２電極との電位を差動検出することによって前記生体の心電波形のＲ波を計測する第１心電計測部と、
前記第１心電計測部によるＲ波の計測結果に基づいて、最も大きな振幅で正の極性を持つＲ波を計測した前記電極アレイのうちの１つの第１電極と、最も大きな振幅で負の極性を持つＲ波を計測した前記電極アレイのうちの他の１つの第１電極とを特定する心電特定部と、
前記心電特定部で特定された前記電極アレイのうちの１つの第１電極と他の１つの第１電極との電位を差動検出することによって前記生体の心電波形のＲ波を計測する第２心電計測部と、
を含むことを特徴とする心電計測装置。 An electrode array comprising a plurality of first electrodes in contact with the upper arm of a living body;
A second electrode in contact with the living body closer to the wrist than the electrode array;
A first electrocardiogram measurement unit that measures an R wave of the electrocardiographic waveform of the living body by differentially detecting a potential with respect to the second electrode for all the first electrodes of the electrode array;
Based on the measurement result of the R wave by the first electrocardiogram measurement unit, the first electrode of the electrode array that has measured the R wave having the largest amplitude and the positive polarity, and the negative with the largest amplitude. An electrocardiograph identifying unit that identifies the other first electrode of the electrode array that has measured the R wave with polarity;
The R wave of the electrocardiographic waveform of the living body is measured by differentially detecting the potential of one first electrode and the other first electrode of the electrode array specified by the electrocardiogram specifying unit. A second electrocardiogram measurement unit;
An electrocardiogram measuring device comprising:
前記電極アレイの複数の第１電極は、前記上腕の円周上に等間隔で置かれていることを特徴とする心電計測装置。 The electrocardiograph according to claim 1,
A plurality of first electrodes of the electrode array are placed at equal intervals on the circumference of the upper arm.
前記第２電極は、前記上腕に接触し該上腕を一周する長さであることを特徴とする心電計測装置。 The electrocardiograph according to claim 1 or 2,
2. The electrocardiograph according to claim 1, wherein the second electrode has a length that contacts the upper arm and makes a round of the upper arm.
前記心電特定部は、各心電波形を該心電波形のＲ波の振幅と極性とでマッピングすることを特徴とする心電計測装置。 In the electrocardiograph according to any one of claims 1 to 3,
The electrocardiograph specifying unit maps each electrocardiogram waveform with the amplitude and polarity of an R wave of the electrocardiogram waveform.
２つの入力の電位を差動増幅する差動増幅部と、
交流信号を出力するスイッチ制御部と、
前記スイッチ制御部から出力された交流信号に応じて、前記差動増幅部に入力する１つの心電信号を前記第１電極と前記第２電極とのどちらか一方の心電信号に切り替える機械式のスイッチと、
をさらに含むことを特徴とする心電計測装置。 In the electrocardiograph according to any one of claims 1 to 4,
A differential amplifier for differentially amplifying the potentials of the two inputs;
A switch controller that outputs an AC signal;
A mechanical system that switches one electrocardiogram signal input to the differential amplifier to one of the first electrode and the second electrode in accordance with an AC signal output from the switch controller. And the switch
An electrocardiogram measuring apparatus further comprising:
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| US11000219B2 (en) | 2015-10-21 | 2021-05-11 | Nec Corporation | Electrocardiogram measurement apparatus and electrocardiogram measurement method |
| DE112021000615T5 (en) | 2020-03-31 | 2022-11-10 | Omron Healthcare Co., Ltd. | CUFF AND ELECTROCARDIOGRAPHIC MEASUREMENT DEVICE |
| DE112021000590T5 (en) | 2020-03-31 | 2022-12-01 | Omron Healthcare Co., Ltd. | CUFF AND ELECTROCARDIOGRAPHIC MEASUREMENT DEVICE |
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| JP5445263B2 (en) * | 2010-03-24 | 2014-03-19 | セイコーエプソン株式会社 | Biological information acquisition device |
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| SE0302746D0 (en) * | 2003-10-17 | 2003-10-17 | Uppsala Laekarkonsult Ab | multielectrode |
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| US11000219B2 (en) | 2015-10-21 | 2021-05-11 | Nec Corporation | Electrocardiogram measurement apparatus and electrocardiogram measurement method |
| US11963778B2 (en) | 2018-07-06 | 2024-04-23 | Omron Healthcare Co., Ltd. | Belt and electrocardiogrameasurement device |
| DE112021000615T5 (en) | 2020-03-31 | 2022-11-10 | Omron Healthcare Co., Ltd. | CUFF AND ELECTROCARDIOGRAPHIC MEASUREMENT DEVICE |
| DE112021000590T5 (en) | 2020-03-31 | 2022-12-01 | Omron Healthcare Co., Ltd. | CUFF AND ELECTROCARDIOGRAPHIC MEASUREMENT DEVICE |
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