JPH0490744A - Arrhythmia occurrence rhythm analyzer - Google Patents
Arrhythmia occurrence rhythm analyzerInfo
- Publication number
- JPH0490744A JPH0490744A JP2208471A JP20847190A JPH0490744A JP H0490744 A JPH0490744 A JP H0490744A JP 2208471 A JP2208471 A JP 2208471A JP 20847190 A JP20847190 A JP 20847190A JP H0490744 A JPH0490744 A JP H0490744A
- Authority
- JP
- Japan
- Prior art keywords
- interval
- section
- arrhythmia
- electrocardiogram
- wave
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 206010003119 arrhythmia Diseases 0.000 title claims abstract description 23
- 230000006793 arrhythmia Effects 0.000 title claims abstract description 22
- 230000033764 rhythmic process Effects 0.000 title claims abstract description 19
- 238000001514 detection method Methods 0.000 claims abstract description 7
- 238000006243 chemical reaction Methods 0.000 claims abstract description 6
- 208000000418 Premature Cardiac Complexes Diseases 0.000 claims description 16
- 230000008878 coupling Effects 0.000 abstract description 13
- 238000010168 coupling process Methods 0.000 abstract description 13
- 238000005859 coupling reaction Methods 0.000 abstract description 13
- 238000000034 method Methods 0.000 abstract description 7
- 230000006835 compression Effects 0.000 abstract 3
- 238000007906 compression Methods 0.000 abstract 3
- 238000010586 diagram Methods 0.000 description 11
- 230000008602 contraction Effects 0.000 description 8
- 230000002028 premature Effects 0.000 description 7
- 238000012545 processing Methods 0.000 description 7
- 230000000694 effects Effects 0.000 description 6
- 238000007796 conventional method Methods 0.000 description 3
- 239000007788 liquid Substances 0.000 description 3
- 239000003814 drug Substances 0.000 description 2
- 229940079593 drug Drugs 0.000 description 2
- 230000001939 inductive effect Effects 0.000 description 2
- 230000002159 abnormal effect Effects 0.000 description 1
- 238000009825 accumulation Methods 0.000 description 1
- 239000003416 antiarrhythmic agent Substances 0.000 description 1
- 230000003126 arrythmogenic effect Effects 0.000 description 1
- 239000003990 capacitor Substances 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 239000004973 liquid crystal related substance Substances 0.000 description 1
- 238000003754 machining Methods 0.000 description 1
- 238000003909 pattern recognition Methods 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
Landscapes
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は不整脈生起リズム分析装置に関し、特に心電図
アナログ信号による不整脈生起リズム分析装置に関する
。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to an arrhythmia-inducing rhythm analyzer, and particularly to an arrhythmia-inducing rhythm analyzer using an electrocardiogram analog signal.
従来、抗不整脈剤等の投与の効果を知るためには、ホル
タ−心電計により24時間程度の心電図信号を磁気テー
プに蓄積し、それを再生して不整脈(特に期外収縮)の
カウントを行うと共にその近傍のR波間隔(以下rRR
間隔」という)を計測して発生頻度の変化とRR間隔の
変化とを分析することにより、投与効果を確認していた
。Conventionally, in order to understand the effects of administering antiarrhythmic drugs, etc., electrocardiogram signals for about 24 hours were accumulated on magnetic tape using a Holter electrocardiograph, and the signals were played back to count arrhythmias (particularly premature contractions). At the same time as R-wave interval in the vicinity (rRR
The effects of administration were confirmed by measuring changes in the frequency of occurrence and changes in the RR interval.
上述した従来の方法によると、24時間程度に亘って記
録された長時間のテープを解析するためには、記録時の
240倍や720倍等の高速再生を行わないと短時間で
結果を得ることができないという問題点があった。According to the conventional method described above, in order to analyze a long tape recorded over about 24 hours, results cannot be obtained in a short time unless high-speed playback is performed, such as 240 times or 720 times the recording time. The problem was that it could not be done.
一方、より短時間に心電図を解析し、期外収縮の確認や
RR間隔の蓄積を行うためには、テープの走行速度を上
げる必要があり、さらに高速処理に適応できる高速処理
用のハードウェアが必要である。一方で、テープの再生
が高速になる程単位時間当りに処理できるデータ数や動
作し得るソフトウェアのステップ数が少なくなり、期外
収縮の認識精度や正確なRR間隔を求めるためのR波認
識精度を上げることができないと(八う問題点を有して
いた。On the other hand, in order to analyze electrocardiograms in a shorter time, check for premature contractions, and accumulate RR intervals, it is necessary to increase the tape running speed, and high-speed processing hardware that can adapt to high-speed processing is required. is necessary. On the other hand, as the tape playback speed becomes faster, the number of data that can be processed per unit time and the number of software steps that can be operated become smaller, which reduces the accuracy of recognizing premature contractions and R wave recognition for determining accurate RR intervals. There was a problem with not being able to raise the level of performance.
また、従来の磁気テープに心電図原信号を記憶させる方
式では、記録時に低速で記録を行1.’l、再生時に高
速で再生する為、記録時のワウフラッタ−により波形品
質を落としたり生起時刻ヘズレカイ生じるなどにより期
外収縮やR波の認識精度を低下することになり、正確な
不整脈生起リズム分析ができなかった。In addition, in the conventional method of storing the electrocardiogram original signal on a magnetic tape, recording is performed at low speed in rows 1. 'l, Because the playback is performed at high speed, the waveform quality is degraded due to wow and flutter during recording, and the recognition accuracy of extrasystles and R waves is reduced due to deviations in the time of occurrence, etc., making it difficult to accurately analyze arrhythmia-induced rhythms. I couldn't do it.
さらに、不整脈生起リズム分析の主な目的&よ、薬剤投
与後の薬効を期外収縮の発生頻度の変イヒ番こよって知
るものであるが、その分析の際ζこ利用されるパラメー
タは、期外収縮の総数の変化のみではなく、第2図に見
るように期外収縮が起こった時刻と直前のQR8波が生
起した時刻との間隔β(以下「カップリング間隔」とい
う)とその前の正常波形の発生間隔α(以降正常洞調律
間隔とt)う)との相関によって知る方法が臨床にて利
用されつつある。この方法を従来の方法である磁気テー
プにより実行しようとすると、前述のように1つの波形
に対する処理時間が短いため、起外収縮のパターン認識
とRR間隔を求める処理との同時処理が出来ず、テープ
を再度、再生し直すか、ハードディスク等にあらかじめ
波形をすべて蓄積しておき、後で時間をかけて解析を行
う必要があり、直ちに分析結果が得られないという問題
点を有していた。Furthermore, the main purpose of arrhythmogenic rhythm analysis is to determine the efficacy of a drug after administration by determining the frequency of occurrence of premature contractions, and the parameters used in this analysis are In addition to changes in the total number of extrasystole, as shown in Figure 2, the interval β between the time when an extrasystole occurs and the time when the immediately preceding QR8 wave occurs (hereinafter referred to as the "coupling interval") and the previous A method of determining this based on the correlation with the normal waveform occurrence interval α (hereinafter referred to as "normal sinus rhythm interval") is being used clinically. When this method is attempted to be carried out using the conventional method of magnetic tape, the processing time for one waveform is short as described above, so it is not possible to simultaneously process the pattern recognition of the lateral contraction and the process of calculating the RR interval. It is necessary to replay the tape again or to store all the waveforms in advance on a hard disk or the like, and then to analyze them later over time, which poses a problem in that analysis results cannot be obtained immediately.
本発明の不整脈生起リズム分析装置は、心電図アナログ
信号を入力する入力手段と、前記心電図アナログ信号を
ディジタル信号に変換するAD変換手段と、前記AD変
換手段によりディジタル化された信号から不整脈を検出
する不整脈検出手段と、前記不整脈検出手段により検出
された不整脈を期外収縮の形状毎に分類し分類された各
々に対応する不整脈検出時刻及び当該不整脈発生前のR
波間隔を蓄積する蓄積手段とを備えて構成される。The arrhythmia-causing rhythm analyzer of the present invention includes an input means for inputting an electrocardiogram analog signal, an AD conversion means for converting the electrocardiogram analog signal into a digital signal, and an arrhythmia is detected from the signal digitized by the AD conversion means. an arrhythmia detecting means, and classifying the arrhythmia detected by the arrhythmia detecting means according to the shape of extrasystole, and detecting the arrhythmia detection time corresponding to each classified and the R before the occurrence of the arrhythmia.
and storage means for storing wave intervals.
次に、本発明について図面を参照して説明する。 Next, the present invention will be explained with reference to the drawings.
第1図は本発明の一実施例の構成を示すブロック図であ
る。FIG. 1 is a block diagram showing the configuration of an embodiment of the present invention.
心電図信号入力部1は、生体信号入力用の電極17によ
り体表面より採取された微少信号を増幅する。アナログ
ディジタル変換部2は、マルチプレクサ−A/D変換器
等より構成され、心電図信号入力部1によって増幅され
た心電図アナログ信号をディジタル信号に変換する。The electrocardiogram signal input section 1 amplifies minute signals collected from the body surface by the electrodes 17 for biological signal input. The analog-to-digital converter 2 includes a multiplexer-A/D converter and the like, and converts the electrocardiogram analog signal amplified by the electrocardiogram signal input section 1 into a digital signal.
R液検出部3は、心電図信号の認識の基点となるQR8
波をP波、T波等の波形やノイズとの区別を行う。この
構成は、ディジタルフィルタ、加算回路等より構成され
る。RR間隔分析部4は、R液検出部3によって認識さ
れたR波の生起時刻の系列よりR波の生起間隔を求める
。The R liquid detection unit 3 uses QR8, which is the base point for recognizing electrocardiogram signals.
Distinguish waves from waveforms such as P waves and T waves, and from noise. This configuration includes a digital filter, an adder circuit, and the like. The RR interval analysis section 4 determines the occurrence interval of the R waves from the series of occurrence times of the R waves recognized by the R liquid detection section 3.
期外収縮認識部5は、R液検出部3で認識されたQR8
波についてその面積や高さから期外収縮と正常洞調律の
QR8波との識別を行う。ここにおいて期外収縮の形状
は必ずしも−通りではなく複数種類に亘るので、パター
ンマ・ノチンダ等において複数種類の分類を行いテンプ
レート作成を行う。カップリング間隔記憶部6は期外収
縮認識部5によって該当するQR8波が期外収縮と判定
された場合、RR間隔分析部4によって検出されたRR
間隔及び期外収縮の発生時刻の記憶を行う。The extrasystole recognition unit 5 detects QR8 recognized by the R liquid detection unit 3.
The area and height of the waves are used to distinguish between premature contractions and the QR8 wave of normal sinus rhythm. Here, since the shape of the extrasystole is not necessarily one-size-fits-all, but includes multiple types, templates are created by classifying the shapes into multiple types using pattern machining, etc. When the extra-systole recognition section 5 determines that the corresponding QR8 wave is an extra-systole, the coupling interval storage section 6 stores the RR detected by the RR interval analysis section 4.
The interval and time of occurrence of extrasystole are memorized.
正常洞調律間隔記憶部7は、RR間隔分析部6によって
カップリング間隔が記憶された場合、カップリング間隔
の直前のRR間隔を記憶する。クロック部8は、期外収
縮の発生実時刻を与えたり、中央処理部9にクロックパ
ルスを送り、AD変換器2の基準クロック信号を作り出
す。また、中央処理部9は、上述の各部の制御を行う。When the coupling interval is stored by the RR interval analysis unit 6, the normal sinus rhythm interval storage unit 7 stores the RR interval immediately before the coupling interval. The clock section 8 provides the actual time at which the extra systole occurs, sends a clock pulse to the central processing section 9, and generates a reference clock signal for the AD converter 2. Further, the central processing unit 9 controls each of the above-mentioned units.
このようにしてカップリング間隔記憶部6及び正常洞調
律間隔記憶部7に記憶されたカップリング間隔βと洞調
律間隔αとをID番号ごと期外収縮生起時刻ごとに、こ
れらの記憶部から外部へ読み出して各々のデータをそれ
ぞれX軸とY軸とにプロットすることで第3図に示すよ
うな相関図が完成する。一方、本方法では各カップリン
グ間隔記憶部に間隔と時刻の記憶に加え、期外収縮認識
部5において認識された期外収縮が既に記憶されている
、期外収縮と該当する期外収縮の形状のパターンが存在
する場合には、第4図のようなメモリレイアウトでその
パターンに付与された期外収縮の形状のIDの番号を記
憶しておく。The coupling interval β and sinus rhythm interval α stored in the coupling interval storage unit 6 and the normal sinus rhythm interval storage unit 7 in this way are exported from these storage units for each ID number and each premature contraction occurrence time. By reading out the data and plotting each data on the X axis and Y axis, a correlation diagram as shown in FIG. 3 is completed. On the other hand, in this method, in addition to storing the interval and time in each coupling interval storage unit, the extra-systole recognized by the extra-systole recognition unit 5 is already stored, and the extra-systole and the corresponding extra-systole are stored. If a shape pattern exists, the ID number of the shape of extrasystole assigned to that pattern is stored in a memory layout as shown in FIG.
本手法により相関図を作成する際に、各IDの番号に応
じた、つまり期外収縮の形状に応じたカップリング間隔
の相関図が第3図に示すように求められる。第3図はI
DIに関する相関図を示している。第5図は本発明の一
実施例の外観図である。When creating a correlation diagram using this method, a correlation diagram of coupling intervals corresponding to each ID number, that is, according to the shape of extrasystole, is obtained as shown in FIG. 3. Figure 3 is I
A correlation diagram regarding DI is shown. FIG. 5 is an external view of one embodiment of the present invention.
不整脈リズム分析装置11はマイクロプロセッサを内蔵
しており、電池によって駆動可能である。従って、被験
者は、本装置を携帯して日常活動中の心電図を分析・記
憶しながら日常の行動をとることができる。メモリカー
ドエ2はカップリング間隔や、正常洞調律間隔などの情
報を記憶する。メモリカード12は挿入部4に挿入され
、内部の中央処理部9のパスラインと直結する。液晶表
示部3は、時刻情報や、装置の異常状態、操作指示等を
表示する。電池収納部5は本装置の電源となる電池を収
納する部分であり、心電画人カケープル6は電極7と共
に心電図信号を体表面より本装置に入力している。The arrhythmia rhythm analyzer 11 has a built-in microprocessor and can be driven by a battery. Therefore, the subject can perform daily activities while carrying this device and analyzing and memorizing electrocardiograms during daily activities. The memory card 2 stores information such as coupling intervals and normal sinus rhythm intervals. The memory card 12 is inserted into the insertion section 4 and directly connected to the pass line of the internal central processing section 9. The liquid crystal display section 3 displays time information, an abnormal state of the device, operation instructions, and the like. The battery storage section 5 is a part that stores a battery that serves as a power source for this device, and the electrocardiogram capacitor 6 and the electrodes 7 input electrocardiogram signals into the device from the body surface.
以上説明したように本発明は、従来の方式に比較して次
の効果がある。As explained above, the present invention has the following effects compared to the conventional system.
すなわち、心電図の期外収縮の分類及び各間隔の分析が
装置携帯中にリアルタイムで行なわれるので、検査が終
わると同時に相関図等の不整脈リズム分析結果が短時間
で得られる。これにより投薬効果の情報を直ちに得られ
、次の処置への方針を迅速に決定できるという効果があ
る。また、磁気テープを介さないため、波形の周波数特
性やワウフラッタ−によるひずみが起こらず、全体の解
析精度も向上し、品質の良い波形が蓄積されるという効
果もある。That is, since the classification of premature contractions in the electrocardiogram and the analysis of each interval are performed in real time while the device is carried, arrhythmia rhythm analysis results such as correlation diagrams can be obtained in a short time as soon as the test is completed. This has the advantage that information on the effectiveness of medication can be obtained immediately, and the next course of treatment can be quickly determined. Furthermore, since no magnetic tape is used, distortion due to waveform frequency characteristics or wow and flutter does not occur, and overall analysis accuracy is improved, resulting in the accumulation of high-quality waveforms.
第1図は本発明の一実施例の構成を示すブロック図、第
2図はカップリング間隔を説明する模式図、第3図は本
発明の最終目的である相関図、第4図はメモリー内レイ
アウト構成とテンプレートの模式図、第5図は本実施例
の外観図である。
1・・・心電図信号入力部、2・・・AD変換部、3・
・・$3 回
洞調律間隔認識部、8・・・クロック部、9・・・中央
処理部、11・・・不整[IJズム分析装置、12・・
・メモリーカード、13・・・液晶表示部、14・・・
メモリカードそう入部、15・・・電池収納部、16・
・・心電画人カケープル、17・・・電極。Fig. 1 is a block diagram showing the configuration of an embodiment of the present invention, Fig. 2 is a schematic diagram explaining the coupling interval, Fig. 3 is a correlation diagram which is the final objective of the invention, and Fig. 4 is a diagram showing the internal memory of the memory. A schematic diagram of the layout configuration and template, and FIG. 5 is an external view of this embodiment. 1... Electrocardiogram signal input section, 2... AD conversion section, 3.
...$3 Sinus rhythm interval recognition unit, 8... Clock unit, 9... Central processing unit, 11... Irregularity [IJ rhythm analyzer, 12...
・Memory card, 13...LCD display section, 14...
Memory card compartment, 15...Battery compartment, 16.
・・Electrocardiogram person capeple, 17...electrode.
Claims (1)
アナログ信号をディジタル信号に変換するAD変換手段
と、前記AD変換手段によりディジタル化された信号か
ら不整脈を検出する不整脈検出手段と、前記不整脈検出
手段により検出された不整脈を期外収縮の形状毎に分類
し分類された各々に対応する不整脈検出時刻及び当該不
整脈発生前のR波間隔を蓄積する蓄積手段とを備えて成
ることを特徴とする不整脈生起リズム分析装置。an input means for inputting an electrocardiogram analog signal; an AD conversion means for converting the electrocardiogram analog signal into a digital signal; an arrhythmia detection means for detecting an arrhythmia from a signal digitized by the AD conversion means; Arrhythmia occurrence characterized by comprising: a storage means for classifying detected arrhythmias according to the shape of extrasystole and storing arrhythmia detection times corresponding to each classified and R-wave intervals before the arrhythmia occurrence. Rhythm analysis device.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2208471A JPH0490744A (en) | 1990-08-06 | 1990-08-06 | Arrhythmia occurrence rhythm analyzer |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2208471A JPH0490744A (en) | 1990-08-06 | 1990-08-06 | Arrhythmia occurrence rhythm analyzer |
Publications (1)
Publication Number | Publication Date |
---|---|
JPH0490744A true JPH0490744A (en) | 1992-03-24 |
Family
ID=16556727
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP2208471A Pending JPH0490744A (en) | 1990-08-06 | 1990-08-06 | Arrhythmia occurrence rhythm analyzer |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPH0490744A (en) |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
LT4756B (en) | 2000-01-11 | 2001-01-25 | Kauno Medicinos Universiteto Psichofiziologijos Ir Reabilitacijos Institutas | METHOD OF EXCLUSION OF SYNTHETIC AND ECTOPIC HEART RIT |
JP2007244531A (en) * | 2006-03-14 | 2007-09-27 | Nippon Koden Corp | Holter electrocardiographic monitor and electrocardiographic monitor system |
JP2008539987A (en) * | 2005-05-13 | 2008-11-20 | カーディオコア ラブ、インコーポレイテッド | Method and apparatus for sequentially extracting from electrocardiogram waveform |
WO2016125444A1 (en) * | 2015-02-03 | 2016-08-11 | ソニー株式会社 | Information processing device, information processing method, program, and observation system |
JP2018201800A (en) * | 2017-06-02 | 2018-12-27 | 日本電信電話株式会社 | Extrasystole discrimination device, extrasystole discrimination method, and program |
-
1990
- 1990-08-06 JP JP2208471A patent/JPH0490744A/en active Pending
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
LT4756B (en) | 2000-01-11 | 2001-01-25 | Kauno Medicinos Universiteto Psichofiziologijos Ir Reabilitacijos Institutas | METHOD OF EXCLUSION OF SYNTHETIC AND ECTOPIC HEART RIT |
JP2008539987A (en) * | 2005-05-13 | 2008-11-20 | カーディオコア ラブ、インコーポレイテッド | Method and apparatus for sequentially extracting from electrocardiogram waveform |
JP2007244531A (en) * | 2006-03-14 | 2007-09-27 | Nippon Koden Corp | Holter electrocardiographic monitor and electrocardiographic monitor system |
WO2016125444A1 (en) * | 2015-02-03 | 2016-08-11 | ソニー株式会社 | Information processing device, information processing method, program, and observation system |
JP2018201800A (en) * | 2017-06-02 | 2018-12-27 | 日本電信電話株式会社 | Extrasystole discrimination device, extrasystole discrimination method, and program |
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