JPH0531082A - Electronic blood pressure gauge - Google Patents
Electronic blood pressure gaugeInfo
- Publication number
- JPH0531082A JPH0531082A JP3194286A JP19428691A JPH0531082A JP H0531082 A JPH0531082 A JP H0531082A JP 3194286 A JP3194286 A JP 3194286A JP 19428691 A JP19428691 A JP 19428691A JP H0531082 A JPH0531082 A JP H0531082A
- Authority
- JP
- Japan
- Prior art keywords
- pressure
- cuff
- pulse wave
- pressurization
- systolic
- 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.)
- Granted
Links
Landscapes
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】この発明は、オシロメトリック式
血圧計に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an oscillometric blood pressure monitor.
【０００２】[0002]
【従来の技術】オシロメトリック式血圧計には、例えば
カフ圧を時間的に変化させ（図５のａ参照）、このカフ
圧上に重畳する脈波の振幅の変化（図５のｂ参照）から
血圧を算出するものがある。図５の（ｂ）は、このよう
な血圧計のカフ圧の減圧過程における脈波振幅の変化を
示したものであり、Ｐ点は最大振幅点（ＡMAX とする）
を示している。また、Ｄ点は、最大振幅点に対して０．
７ＡMAX の振幅を有する点であり、Ｓ点は、最大振幅点
に対して０．５ＡMAX の振幅を有する点である。そし
て、例えば図６のＳ点とＤ点に対応する図５の（ａ）の
点より、収縮期血圧（最高血圧）と拡張期血圧（最低血
圧）を決定していた。2. Description of the Related Art In an oscillometric sphygmomanometer, for example, the cuff pressure is temporally changed (see FIG. 5a), and the amplitude of the pulse wave superimposed on this cuff pressure is changed (see FIG. 5b). There is one that calculates blood pressure from. FIG. 5B shows a change in pulse wave amplitude in the process of reducing the cuff pressure of such a sphygmomanometer, and point P is the maximum amplitude point (denoted as A MAX ).
Is shown. Further, the point D is 0.
The point having an amplitude of 7A MAX , and the point S is a point having an amplitude of 0.5A MAX with respect to the maximum amplitude point. Then, for example, the systolic blood pressure (maximum blood pressure) and the diastolic blood pressure (minimum blood pressure) are determined from the points in FIG. 5A corresponding to the points S and D in FIG.
【０００３】オシロメトリック式血圧計では、以上のよ
うにして血圧値を決定するので、図５（ｂ）のＳ点が検
出できる程度の加圧が必要であるが、計測前には収縮期
血圧（最高血圧）を予測できないので加圧停止値を適切
な値に設定することは難しく、血圧変動の激しい高血圧
者においては特に困難である。また、加圧停止値を、む
やみに高い値に設定すると被測定者に苦痛を強いること
にもなる。In the oscillometric sphygmomanometer, since the blood pressure value is determined as described above, it is necessary to pressurize the blood vessel so that the point S in FIG. 5B can be detected. Since the (maximum blood pressure) cannot be predicted, it is difficult to set the pressurization stop value to an appropriate value, and it is particularly difficult for a hypertensive person with severe blood pressure fluctuations. Further, if the pressurization stop value is set to an unreasonably high value, the person to be measured will be in pain.
【０００４】そこで、従来は、カフ圧の加圧時におい
て、カフ圧信号を捕捉して、このカフ圧信号に重畳する
脈波の振幅の変化（脈波包絡線）を求めることによっ
て、簡易的に収縮期圧を推定していた。そして、この推
定した収縮期圧を基にして自動的に加圧停止点を設定し
ていた。Therefore, conventionally, when the cuff pressure is increased, the cuff pressure signal is captured and a change in the amplitude of the pulse wave (pulse wave envelope) superimposed on the cuff pressure signal is obtained, thereby simplifying the operation. Had estimated systolic pressure. Then, the pressurization stop point was automatically set based on this estimated systolic pressure.
【０００５】[0005]
【発明が解決しようとする課題】しかし、脈波の重畳し
たカフ圧信号から脈波を分離する為にハイパスフィルタ
を使用するので、加圧開始時などのように信号が急激に
変化する点で過渡応答と呼ばれる大きな変動が生じてし
まい、収縮期圧を算出する為の包絡線を正常に捕捉でき
ないという問題点があった。具体的には、カフ圧の低圧
領域で異常な***が生じる為に、非常に低い値が収縮期
圧と推定されてしまい、この推定値を基にして加圧停止
点を設定すると、加圧不足により血圧測定ができないと
いう問題点があった。However, since the high-pass filter is used to separate the pulse wave from the cuff pressure signal on which the pulse wave is superposed, the signal changes abruptly such as at the start of pressurization. There is a problem in that a large variation called a transient response occurs and the envelope for calculating the systolic pressure cannot be normally captured. Specifically, a very low value is estimated to be the systolic pressure because an abnormal bulge occurs in the low pressure region of the cuff pressure, and if the pressure stop point is set based on this estimated value, There was a problem that blood pressure could not be measured due to lack.
【０００６】この発明は、この問題点に着目してなされ
たものであって、過渡応答の影響を受けずに、カフ圧の
加圧過程で収縮期圧を推定することの出来る血圧計を提
供することを目的とする。The present invention has been made in view of this problem, and provides a sphygmomanometer capable of estimating the systolic pressure during the process of pressurizing the cuff pressure without being affected by the transient response. The purpose is to do.
【０００７】[0007]
【課題を解決するための手段】上記の目的を達成するた
め、この発明にかかる血圧計は、生体動脈を圧迫するカ
フと、このカフを加圧する加圧手段と、カフ内の圧力を
検出する圧力センサと、この圧力センサの検出したカフ
圧信号からこのカフ圧信号に重畳する脈波成分を抽出す
る脈波抽出手段と、加圧開始から所定時間が経過したこ
とを検出する時間経過検出手段と、及び若しくは、加圧
開始後カフ圧が所定値を越えたことを検出する所定カフ
圧検出手段と、前記所定時間及び若しくは所定カフ圧の
検出に応答して前記脈波抽出手段の動作を開始させる動
作開始制御手段と、カフ圧の加圧過程において収縮期圧
を推定する収縮期圧推定手段と、この収縮期圧推定手段
の推定した収縮期圧に基づいて定まる所定のカフ圧に達
すると前記加圧手段の動作を停止させる加圧停止手段
と、加圧停止後にカフ圧を徐々に減圧する減圧手段と、
カフ圧の減圧過程で脈波信号を抽出し、その脈波信号と
カフ圧に基づいて血圧を決定する血圧決定手段とで構成
されている。In order to achieve the above-mentioned object, a sphygmomanometer according to the present invention detects a cuff for pressing a living artery, a pressurizing means for pressurizing the cuff, and a pressure inside the cuff. A pressure sensor, a pulse wave extracting means for extracting a pulse wave component superimposed on the cuff pressure signal from the cuff pressure signal detected by the pressure sensor, and a time lapse detecting means for detecting that a predetermined time has elapsed from the start of pressurization. And / or a predetermined cuff pressure detecting means for detecting that the cuff pressure exceeds a predetermined value after the start of pressurization, and the operation of the pulse wave extracting means in response to the predetermined time and / or the detection of the predetermined cuff pressure. The operation start control means for starting, the systolic pressure estimation means for estimating the systolic pressure in the process of pressurizing the cuff pressure, and the predetermined cuff pressure determined based on the systolic pressure estimated by the systolic pressure estimation means are reached. Then the pressing hand A pressurizing stopping means for stopping the operation of the pressure reducing means for gradually depressurizing the cuff pressure after stopping pressurization,
The blood pressure determining means is configured by extracting a pulse wave signal in the process of reducing the cuff pressure and determining the blood pressure based on the pulse wave signal and the cuff pressure.
【０００８】[0008]
【作用】加圧手段はカフを加圧し、圧力センサはカフ内
の圧力（脈波の重畳したカフ圧信号）を検出する。そし
て、脈波抽出手段は、加圧時及び減圧時のカフ圧信号よ
りこの信号に重畳する脈波成分を抽出する。時間経過検
出手段は、加圧開始から所定の時間が経過したことを検
出する。また所定カフ圧検出手段は、加圧開始後カフ圧
が所定値を越えたことを検出する。そして、動作開始制
御手段は、この時間経過検出手段及びもしくは所定カフ
圧検出手段による所定時間及び若しくは所定カフ圧の検
出に応答して脈波抽出手段の動作の開始させる。従っ
て、過渡応答時には脈波が抽出されず、収縮期圧推定手
段は正確に収縮期圧を推定する。加圧停止手段は、前記
推定された収縮期圧の値に基づいて定まる加圧停止点で
加圧を停止し、その後、減圧手段がカフ圧を徐々に減圧
する。血圧決定手段は、このカフ圧減圧過程において、
脈波抽出手段によって抽出された脈波の振幅の変化に基
づいて血圧値を決定する。The pressurizing means pressurizes the cuff, and the pressure sensor detects the pressure in the cuff (cuff pressure signal on which the pulse wave is superimposed). Then, the pulse wave extracting means extracts the pulse wave component superimposed on this signal from the cuff pressure signal at the time of pressurization and depressurization. The time lapse detection means detects that a predetermined time has elapsed from the start of pressurization. Further, the predetermined cuff pressure detection means detects that the cuff pressure exceeds a predetermined value after the start of pressurization. Then, the operation start control means starts the operation of the pulse wave extracting means in response to the detection of the predetermined time and / or the predetermined cuff pressure by the time passage detection means and / or the predetermined cuff pressure detection means. Therefore, the pulse wave is not extracted during the transient response, and the systolic pressure estimation means accurately estimates the systolic pressure. The pressurization stop means stops pressurization at a pressurization stop point determined based on the estimated systolic pressure value, and then the depressurization means gradually reduces the cuff pressure. Blood pressure determination means, in this cuff pressure reduction process,
The blood pressure value is determined based on the change in the amplitude of the pulse wave extracted by the pulse wave extraction means.
【０００９】[0009]
【実施例】図１はこの発明の一実施例である電子血圧計
のブロック図である。この電子血圧計は、生体動脈を圧
迫するカフ１と、カフ１を加圧するポンプ２と、カフ１
の圧力（空気圧）を急速排気する急速排気弁３と、カフ
１の空気を徐々にに排気する微速排気弁４と、カフ１の
圧力を検出する圧力センサ５と、ローパスフィルタ６
と、圧力センサ５の出力をデジタル値に変換するＡ／Ｄ
変換器７と、Ａ／Ｄ変換器７からの信号を取り込み、後
述する種々の処理を行うＭＰＵ８と、測定した血圧値を
表示する表示器９を備えている。尚、ローパスフィルタ
６は加圧途上で脈波を抽出する場合において、カフ圧信
号上に混入する加圧ポンプ２の圧力ノイズを除去する為
に設けている。1 is a block diagram of an electronic sphygmomanometer according to an embodiment of the present invention. This electronic sphygmomanometer includes a cuff 1 that compresses a living artery, a pump 2 that pressurizes the cuff 1, and a cuff 1.
Quick exhaust valve 3 for rapidly exhausting the pressure (air pressure), a slow exhaust valve 4 for gradually exhausting the air of the cuff 1, a pressure sensor 5 for detecting the pressure of the cuff 1, and a low-pass filter 6
And an A / D that converts the output of the pressure sensor 5 into a digital value
It is provided with a converter 7, an MPU 8 that takes in signals from the A / D converter 7 and performs various processes described below, and a display 9 that displays the measured blood pressure value. The low-pass filter 6 is provided to remove the pressure noise of the pressurizing pump 2 mixed in the cuff pressure signal when the pulse wave is extracted during the pressurization.
【００１０】図２は図１に示す電子血圧計の全体動作を
示すゼェネラルフローチャートである。尚、脈波抽出
処理（ＳＴ５，ＳＴ１２）、脈波振幅算出処理（ＳＴ
６，ＳＴ１３）、血圧推定処理（ＳＴ７）および血
圧算出処理（ＳＴ１４）は、それぞれ以下の処理をする
部分である。 脈波抽出処理：カフ圧データから、カフ圧データに重
畳する脈波成分を抽出する処理である。 脈波振幅算出処理：脈波の起点と終点を１拍ごとに認
識して脈波の振幅を算出する処理である。 血圧推定処理：カフ圧の加圧過程における脈波振幅の
最大値ＡMAX を求め、この脈波振幅の最大値ＡMAX に基
づいて収縮期圧の推定値ＳＰを決定するサブルーチンで
ある（図３参照）。 血圧算出処理：脈波振幅による脈波の包短線の変化よ
り、最高血圧（収縮期圧）と最低血圧（拡張期圧）を算
出するサブルーチンである（図４参照）。FIG. 2 is a general flow chart showing the overall operation of the electronic blood pressure monitor shown in FIG. In addition, pulse wave extraction processing (ST5, ST12), pulse wave amplitude calculation processing (ST
6, ST13), the blood pressure estimation process (ST7), and the blood pressure calculation process (ST14) are parts that perform the following processes, respectively. Pulse wave extraction process: This is a process of extracting a pulse wave component superimposed on the cuff pressure data from the cuff pressure data. Pulse wave amplitude calculation process: This is a process of calculating the pulse wave amplitude by recognizing the start point and the end point of the pulse wave for each beat. Blood pressure estimation process: the maximum value A MAX of the pulse wave amplitude in pressurization process of the cuff pressure, a subroutine for determining an estimated value SP of systolic pressure based on the maximum value A MAX of the pulse wave amplitude (Figure 3 reference). Blood pressure calculation processing: This is a subroutine for calculating the systolic blood pressure (systolic pressure) and the diastolic blood pressure (diastolic pressure) from the change of the pulse wave envelope short line depending on the pulse wave amplitude (see FIG. 4).
【００１１】以下、図２のフローチャートに従って、図
１に示す電子血圧計の動作を説明する。スタートスイッ
チなどにより動作が開始されると、ＭＰＵ８はポンプ２
を駆動して加圧を開始する（ステップＳＴ（以下ＳＴと
略す）１）。次に、ＭＰＵ８は圧力センサ５からの信号
を検出して増加してゆく圧力を監視し（ＳＴ２）、カフ
圧が所定値に到達したか否かを判断する（ＳＴ３）。カ
フ圧が所定値に達していなければＳＴ２に戻るが、所定
値に達したら次の処理（ＳＴ４）に進む。そして、測定
開始時から所定の時間（τ）だけ経過しているか否か判
定して、所定の時間τを経過していなければＳＴ２に戻
って待機する（ＳＴ４）。つまり、ＳＴ３とＳＴ４の処
理があるので、カフ圧が所定値以上になり、かつ所定時
間τを経過した場合のみ次の処理ＳＴ５に移ることにな
る。The operation of the electronic sphygmomanometer shown in FIG. 1 will be described below with reference to the flowchart of FIG. When the operation is started by the start switch, etc., the MPU 8 turns the pump 2
To start pressurization (step ST (hereinafter abbreviated as ST) 1). Next, the MPU 8 detects the signal from the pressure sensor 5 and monitors the increasing pressure (ST2), and determines whether the cuff pressure has reached a predetermined value (ST3). If the cuff pressure has not reached the predetermined value, the process returns to ST2, but if it reaches the predetermined value, the process proceeds to the next process (ST4). Then, it is determined whether or not a predetermined time (τ) has elapsed from the start of measurement, and if the predetermined time τ has not elapsed, the process returns to ST2 and waits (ST4). That is, since the processes of ST3 and ST4 are performed, the process proceeds to the next process ST5 only when the cuff pressure exceeds the predetermined value and the predetermined time τ has elapsed.
【００１２】カフ圧が所定値を越え、加圧開始から所定
の時間が経過すると、脈波抽出処理に移り、ＭＰＵ８
は、カフ圧データから脈波成分を抽出する（ＳＴ５）。
その後、脈波振幅算出処理に移り１拍ごとの脈波振幅
を算出する（ＳＴ６）。そして、血圧推定処理を実行
する（ＳＴ７）。この処理では、最大振幅値ＡMAX が更
新される場合と収縮期圧推定値ＳＰが求まる場合がある
が（詳しくは後述する）、カフ圧の上昇が不十分で未だ
収縮期圧推定値ＳＰが求まっていない場合はＳＴ５に戻
ってＳＴ５〜ＳＴ７を繰り返す（ＳＴ８）。When the cuff pressure exceeds a predetermined value and a predetermined time elapses from the start of pressurization, the pulse wave extracting process is started and the MPU 8
Extracts the pulse wave component from the cuff pressure data (ST5).
After that, the process moves to the pulse wave amplitude calculation process to calculate the pulse wave amplitude for each beat (ST6). Then, the blood pressure estimation process is executed (ST7). In this process, the maximum amplitude value A MAX may be updated and the systolic pressure estimated value SP may be obtained (details will be described later), but the systolic pressure estimated value SP is still insufficient due to insufficient increase in the cuff pressure. If not found, the process returns to ST5 and repeats ST5 to ST7 (ST8).
【００１３】収縮期圧推定値ＳＰが求まった場合は、求
まった収縮期圧推定値ＳＰを基にして加圧停止点（目標
圧）を計算し、この加圧停止点に達するまで加圧を持続
する（ＳＴ９）。なお、この加圧停止点は、収縮期圧の
推定誤差や加圧停止直後から脈波の振幅測定開始時まで
の圧力降下なども考慮して、例えば収縮期圧推定値ＳＰ
に３０ｍｍＨｇを加算した値に設定される。加圧停止点
に達したら加圧をストップし（ＳＴ１０）、微速排気弁
４の動作による減圧を開始する（ＳＴ１１）。When the systolic pressure estimated value SP is obtained, the pressurization stop point (target pressure) is calculated based on the obtained systolic pressure estimated value SP, and pressurization is performed until the pressurization stop point is reached. Persist (ST9). Note that this pressurization stop point is, for example, the systolic pressure estimated value SP in consideration of the estimation error of the systolic pressure and the pressure drop immediately after the pressurization is stopped until the start of the pulse wave amplitude measurement.
Is set to a value obtained by adding 30 mmHg. When the pressurization stop point is reached, pressurization is stopped (ST10), and depressurization by the operation of the slow speed exhaust valve 4 is started (ST11).
【００１４】カフ圧の減圧過程に移行すると、先ず脈波
抽出処理によってカフ圧信号に重畳する脈波を抽出す
る（ＳＴ１２）。そして、脈波振幅算出処理によって
脈波の振幅を算出し（ＳＴ１３）、血圧算出処理をす
る（ＳＴ１４）。この血圧算出処理では、拡張期圧ＤＰ
の値が求まる場合とそうでない場合があるが（詳しくは
後述する）、カフ圧の減圧が不十分で未だ拡張期圧ＤＰ
の値が求まっていない場合はＳＴ１２に戻ってＳＴ１２
〜ＳＴ１５の処理を繰り返す（ＳＴ８）。この処理を繰
り返していると、やがて拡張期圧ＤＰが決定できるの
で、その後は急速排気弁３を動作させてカフ内の圧力を
排除して（ＳＴ１６）、血圧値を表示器９に表示して全
ての処理を終わる。When shifting to the process of reducing the cuff pressure, first, the pulse wave superimposed on the cuff pressure signal is extracted by the pulse wave extraction processing (ST12). Then, the amplitude of the pulse wave is calculated by the pulse wave amplitude calculation process (ST13), and the blood pressure calculation process is performed (ST14). In this blood pressure calculation process, the diastolic pressure DP
There are cases where the value of is obtained and cases where it is not (details will be described later), but the cuff pressure is not sufficiently reduced and the diastolic pressure DP is still
If the value of is not found, return to ST12 and ST12
~ The process of ST15 is repeated (ST8). If this process is repeated, the diastolic pressure DP can be determined in due course, and thereafter, the quick exhaust valve 3 is operated to eliminate the pressure in the cuff (ST16), and the blood pressure value is displayed on the display unit 9. All processing ends.
【００１５】図３は血圧推定処理（図２のＳＴ７）を
更に詳細に示すフローチャートである。なお、図３にお
いてＡＭＰ（ｎ）は抽出された脈波振幅を示しており、
ｎは抽出された脈波の順番を示す脈波番号である。ま
た、各脈波振幅ＡＭＰ（ｎ）に対する各カフ圧ＰＣ
（ｎ）は、この処理の直前に実行される脈波振幅算出処
理（ＳＴ６）で算出されている。尚、脈波番号ｎと、
脈波振幅の最大値を求める為の変数ＡMAX は、共に０に
初期設定されている。以下、図３に従って血圧推定処理
の内容を説明する。FIG. 3 is a flowchart showing the blood pressure estimation process (ST7 in FIG. 2) in more detail. In FIG. 3, AMP (n) indicates the extracted pulse wave amplitude,
n is a pulse wave number indicating the order of the extracted pulse waves. Also, each cuff pressure PC for each pulse wave amplitude AMP (n)
(N) is calculated in the pulse wave amplitude calculation process (ST6) executed immediately before this process. The pulse wave number n
The variables A MAX for obtaining the maximum value of the pulse wave amplitude are both initialized to 0. The contents of the blood pressure estimation process will be described below with reference to FIG.
【００１６】先ず、脈波の番号ｎを更新したうえで（Ｓ
Ｔ２１）、脈波振幅ＡＭＰ（ｎ）を脈波振幅最大値Ａ
MAX と比較する（ＳＴ２２）。ここでＡＭＰ（ｎ）≧Ａ
MAX である場合は、脈波の包絡線が上昇過程にあり、未
だ極大点に達していないと判断してＡMAX にＡＭＰ
（ｎ）の値を代入して（ＳＴ２３）、メインルーチンに
戻る。逆に、ＡＭＰ（ｎ）＜ＡMAX の場合には、脈波振
幅の包絡線が極大点を通過して減少過程にあると判断し
て、脈波振幅ＡＭＰ（ｎ）を収縮期圧決定の為のしきい
値と比較する（ＳＴ２４）。この実施例では、収縮期圧
決定の為のしきい値を例えば０．５ＡMAX に設定してお
り、ＡＭＰ（ｎ）≦０．５ＡMAX なら次の処理に移って
収縮期圧の推定値ＥＳＰを算出する（ＳＴ２５）。逆
に、ＡＭＰ（ｎ）＞０．５ＡMAX なら収縮期圧の推定値
を決定しないでメインルーチンに戻る。尚、加圧期間で
はカフ圧の変化が大きく、脈波間のカフ圧間隔が広い
為、脈波振幅がしきい値以下に減少した時点でのカフ圧
を、そのまま収縮期圧の推定値として採用すると精度が
悪い。そこで、本実施例では、以下の直線補完式を用い
て収縮期圧の推定値ＥＳＰを算出している。First, after updating the pulse wave number n (S
T21), the pulse wave amplitude AMP (n) is the pulse wave amplitude maximum value A
Compare with MAX (ST22). Where AMP (n) ≧ A
If it is MAX , it is judged that the envelope of the pulse wave is in the ascending process and it has not reached the maximum point yet, and AMP is applied to A MAX .
The value of (n) is substituted (ST23), and the process returns to the main routine. On the other hand, when AMP (n) <A MAX , it is determined that the envelope of the pulse wave amplitude has passed the maximum point and is in the process of decreasing, and the pulse wave amplitude AMP (n) is determined for the systolic pressure determination. (ST24). In this embodiment, the threshold value for determining the systolic pressure is set to, for example, 0.5 A MAX , and if AMP (n) ≦ 0.5 A MAX , the process proceeds to the next process and the estimated value ESP of the systolic pressure is set. Is calculated (ST25). Conversely, if AMP (n)> 0.5A MAX , the process returns to the main routine without determining the estimated systolic pressure value. Since the change in cuff pressure during the pressurization period is large and the cuff pressure interval between pulse waves is wide, the cuff pressure at the time when the pulse wave amplitude decreases below the threshold value is directly used as the estimated systolic pressure value. Then the accuracy is poor. Therefore, in this embodiment, the estimated value ESP of the systolic pressure is calculated using the following linear complementation formula.
【００１７】[0017]
【数１】 [Equation 1]
【００１８】尚、（数１）におけるＴＨS は、収縮期圧
決定の為のしきい値である。図４は、血圧算出処理
（図２のＳＴ１４）を詳細に示すフローチャートであ
る。尚、脈波振幅ＡＭＰ（ｎ）やカフ圧Ｐ（ｎ）は、脈
波抽出処理（ＳＴ１２）、脈波振幅算出処理（ＳＴ１
３）において既に算出されており、また、脈波の番号ｎ
や収縮期圧、拡張期圧の算出の為の変数ＳＰ、ＤＰ及び
脈波振幅の最大値を求める為の変数ＡMAX は全て０に初
期設定されている。Note that TH S in (Equation 1) is a threshold value for determining the systolic pressure. FIG. 4 is a flowchart showing in detail the blood pressure calculation process (ST14 in FIG. 2). In addition, the pulse wave amplitude AMP (n) and the cuff pressure P (n) are the pulse wave extraction process (ST12) and the pulse wave amplitude calculation process (ST1).
3) has already been calculated, and the pulse wave number n
The variables SP and DP for calculating the systolic pressure and the diastolic pressure, and the variable A MAX for obtaining the maximum value of the pulse wave amplitude are all initially set to zero.
【００１９】以下、図４のフローチャートに基づいて、
カフ圧の減圧過程で、どのようにして収縮期圧と拡張期
圧を算出するかを説明する。先ず、脈波の番号ｎの値が
更新された後（ＳＴ３１）、脈波振幅ＡＭＰ（ｎ）が最
大値ＡMAXと比較される（ＳＴ３２）。もしＡＭＰ
（ｎ）＞ＡMAX であれば脈波振幅の包絡線が未だ極大点
に達していないと判断してＳＴ４０に移ってＡＭＰ
（ｎ）の値をＡMAX に代入した後、メインルーチンに戻
る（ＳＴ４０）。Below, based on the flow chart of FIG.
How to calculate the systolic pressure and the diastolic pressure in the process of reducing the cuff pressure will be described. First, after the value of the pulse wave number n is updated (ST31), the pulse wave amplitude AMP (n) is compared with the maximum value A MAX (ST32). If AMP
If (n)> A MAX , it is judged that the envelope of the pulse wave amplitude has not reached the maximum point yet, and the process moves to ST40 and AMP.
After substituting the value of (n) into A MAX , the process returns to the main routine (ST40).
【００２０】一方、ＡＭＰ（ｎ）≦ＡMAX である場合に
は、脈波振幅の包絡線は既に極大点を通過して減少過程
にあると判断して、収縮期圧ＳＰが初期値０のままであ
るか否かを判定する（ＳＴ３３）。ここで、もしＳＰが
０以外であれば、収縮期圧ＳＰは既に決定されているの
であるからＳＴ３８にスキップし、逆にＳＰが０であれ
ば収縮期圧ＳＰを決定する為にＳＴ３４に移行する（Ｓ
Ｔ３３）。On the other hand, when AMP (n) ≤A MAX, it is determined that the envelope of the pulse wave amplitude has already passed the maximum point and is in the process of decreasing, and the systolic pressure SP has the initial value 0. It is determined whether or not there is still (ST33). Here, if SP is other than 0, the systolic pressure SP has already been determined, so skip to ST38, and conversely if SP is 0, proceed to ST34 to determine the systolic pressure SP. Do (S
T33).
【００２１】すなわち、ＳＴ３４以降は収縮期圧ＳＰの
決定を行う処理である。まず脈波のカウンタｊを現在の
脈波番号ｎにセットし（ＳＴ３４）、カウンタｊを１つ
づつ減算して（ＳＴ３５）、ｊで指定される脈波振幅Ａ
ＭＰ（ｊ）を、収縮期圧決定の為のしきい値と比較する
（ＳＴ３６）。この実施例では、収縮期圧ＳＰを決定す
る為のしきい値を、例えば０．５ＡMAX に設定している
ので、ＡＭＰ（ｊ）＞０．５ＡMAX である限りＳＴ３５
とＳＴ３６を繰り返す。そして、もしＡＭＰ（ｊ）≦
０．５ＡMAX の関係を満たす脈波番号ｊが見つかれば、
その番号ｊに対するカフ圧ＰＣ（ｊ）を収縮期圧ＳＰと
して採用する（ＳＴ３７）。That is, the process after ST34 is a process for determining the systolic pressure SP. First, the pulse wave counter j is set to the current pulse wave number n (ST34), the counter j is decremented by 1 (ST35), and the pulse wave amplitude A specified by j is set.
MP (j) is compared with a threshold value for determining systolic pressure (ST36). In this embodiment, the threshold value for determining the systolic pressure SP is set to, for example, 0.5A MAX , so ST35 is set as long as AMP (j)> 0.5A MAX.
And ST36 are repeated. And if AMP (j) ≦
If the pulse wave number j satisfying the relationship of 0.5A MAX is found,
The cuff pressure PC (j) for the number j is adopted as the systolic pressure SP (ST37).
【００２２】収縮期圧ＳＰの決定が終わると、次に拡張
期圧ＤＰの決定をする。先ず、ＡＭＰ(ｎ)の値が拡張期
圧ＤＰ決定の為のしきい値以下に減少したか否かを判定
する(ＳＴ３８)。この実施例では、拡張期圧ＤＰ決定の
為のしきい値を０．７ＡMAX に設定しているのでＡＭＰ
（ｎ）＞０．７ＡMAX なら何もしないでメインルーチン
に戻るが、ＡＭＰ（ｎ）≦０．７ＡMAX なら、その時の
脈波番号ｎに対するカフ圧ＰＣ（ｎ）を拡張期圧ＤＰと
して採用してメインルーチンに戻る（ＳＴ３９）。尚、
図４に示す血圧算出処理（ＳＴ１４）は、拡張期圧を
決定するための変数ＤＰが０である限り、繰り返し処理
されるので（ＳＴ１５参照）、最大振幅ＡMAX が決定さ
れた後、脈波抽出処理ＳＴ１２と脈波振幅算出処理ＳＴ
１３を何回か繰り返すことによって拡張期圧ＤＰ（０．
７ＡMAX ）を決定できる。After the systolic pressure SP has been determined, the diastolic pressure DP is then determined. First, it is determined whether or not the value of AMP (n) has decreased below a threshold value for determining the diastolic pressure DP (ST38). In this embodiment, since the threshold value for determining the diastolic pressure DP is set to 0.7 A MAX , the AMP
If (n)> 0.7A MAX, nothing is returned to the main routine, but if AMP (n) ≦ 0.7A MAX , the cuff pressure PC (n) for the pulse wave number n at that time is adopted as the diastolic pressure DP. Then, the process returns to the main routine (ST39). still,
The blood pressure calculation process (ST14) shown in FIG. 4 is repeatedly performed as long as the variable DP for determining the diastolic pressure is 0 (see ST15). Therefore, after the maximum amplitude A MAX is determined, the pulse wave is calculated. Extraction process ST12 and pulse wave amplitude calculation process ST
13 are repeated several times, the diastolic pressure DP (0.
7A MAX ) can be determined.
【００２３】[0023]
【発明の効果】以上説明したように、この発明にかかる
電子血圧計では、カフ圧の加圧開始付近では脈波の抽出
処理をしないので、血圧計の動作開始時に生じるノイズ
や体動などの影響などを受けにくく、従って確実に加圧
停止点を自動設定できる。As described above, in the electronic sphygmomanometer according to the present invention, the pulse wave is not extracted near the start of pressurization of the cuff pressure, so that noise or body movement generated at the start of the operation of the sphygmomanometer is prevented. It is unlikely to be affected, so that the pressure stop point can be set automatically with certainty.
【図１】この発明の一実施例である電子血圧計の回路ブ
ロック図である。FIG. 1 is a circuit block diagram of an electronic blood pressure monitor that is an embodiment of the present invention.
【図２】図１の電子血圧計の全体動作を説明する為のフ
ロー図である。FIG. 2 is a flow chart for explaining the overall operation of the electronic blood pressure monitor of FIG.
【図３】図１の電子血圧計の血圧推定処理を説明する為
のフロー図である。FIG. 3 is a flowchart for explaining blood pressure estimation processing of the electronic blood pressure monitor in FIG.
【図４】図１の電子血圧計の血圧算出処理を説明する為
のフロー図である。FIG. 4 is a flowchart for explaining a blood pressure calculation process of the electronic blood pressure monitor in FIG.
【図５】オシロメトリック方式の電子血圧計における血
圧決定方法を説明する為の図である。FIG. 5 is a diagram for explaining a blood pressure determination method in an oscillometric electronic blood pressure monitor.
１ カフ ２ ポンプ ３ 急速排気弁 ４ 微速排気弁 ５ 圧力センサ ８ ＭＰＵ 1 Cuff 2 Pump 3 Rapid exhaust valve 4 Fine speed exhaust valve 5 Pressure sensor 8 MPU
Claims (1)
圧する加圧手段と、カフ内の圧力を検出する圧力センサ
と、この圧力センサの検出したカフ圧信号からこのカフ
圧信号に重畳する脈波成分を抽出する脈波抽出手段と、
加圧開始から所定時間が経過したことを検出する時間経
過検出手段と、及び若しくは、加圧開始後カフ圧が所定
値を越えたことを検出する所定カフ圧検出手段と、前記
所定時間及び若しくは所定カフ圧の検出に応答して前記
脈波抽出手段の動作を開始させる動作開始制御手段と、
カフ圧の加圧過程において収縮期圧を推定する収縮期圧
推定手段と、この収縮期圧推定手段の推定した収縮期圧
に基づいて定まる所定のカフ圧に達すると前記加圧手段
の動作を停止させる加圧停止手段と、加圧停止後にカフ
圧を徐々に減圧する減圧手段と、カフ圧の減圧過程で脈
波信号を抽出し、その脈波信号とカフ圧に基づいて血圧
を決定する血圧決定手段とを備えることを特徴とする電
子血圧計。Claim: What is claimed is: 1. A cuff for compressing a biological artery, a pressurizing means for pressurizing the cuff, a pressure sensor for detecting the pressure in the cuff, and a cuff pressure signal detected by the pressure sensor. A pulse wave extracting means for extracting a pulse wave component superimposed on the cuff pressure signal,
Time lapse detection means for detecting that a predetermined time has elapsed from the start of pressurization, and / or predetermined cuff pressure detection means for detecting that the cuff pressure exceeds a predetermined value after the start of pressurization, and the predetermined time and / or Operation start control means for starting operation of the pulse wave extraction means in response to detection of a predetermined cuff pressure,
The systolic pressure estimation means for estimating the systolic pressure in the process of pressurizing the cuff pressure, and the operation of the pressurizing means when the predetermined cuff pressure determined based on the systolic pressure estimated by the systolic pressure estimation means is reached. Pressurization stopping means for stopping, pressure reducing means for gradually reducing the cuff pressure after the pressurization is stopped, pulse wave signals are extracted in the pressure reduction process of the cuff pressure, and blood pressure is determined based on the pulse wave signals and the cuff pressure. An electronic blood pressure monitor comprising: a blood pressure determining means.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3194286A JP3042051B2 (en) | 1991-08-02 | 1991-08-02 | Electronic sphygmomanometer |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3194286A JP3042051B2 (en) | 1991-08-02 | 1991-08-02 | Electronic sphygmomanometer |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH0531082A true JPH0531082A (en) | 1993-02-09 |
| JP3042051B2 JP3042051B2 (en) | 2000-05-15 |
Family
ID=16322077
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP3194286A Expired - Lifetime JP3042051B2 (en) | 1991-08-02 | 1991-08-02 | Electronic sphygmomanometer |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP3042051B2 (en) |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6602200B1 (en) | 1999-09-08 | 2003-08-05 | Omron Corporation | Electronic blood pressure meter |
| JP2004000422A (en) * | 2002-04-17 | 2004-01-08 | Nippon Colin Co Ltd | Sphygmomanometer having waveform analyzing function |
| US11759376B2 (en) | 2013-08-27 | 2023-09-19 | The Procter & Gamble Company | Absorbent articles with channels |
| US11911250B2 (en) | 2011-06-10 | 2024-02-27 | The Procter & Gamble Company | Absorbent structure for absorbent articles |
| US11944526B2 (en) | 2013-09-19 | 2024-04-02 | The Procter & Gamble Company | Absorbent cores having material free areas |
| US11957551B2 (en) | 2013-09-16 | 2024-04-16 | The Procter & Gamble Company | Absorbent articles with channels and signals |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH01256930A (en) * | 1988-04-08 | 1989-10-13 | Nec San-Ei Instr Co Ltd | Automatic setting of cuff pressure in tonometer |
| JPH03121045A (en) * | 1989-10-05 | 1991-05-23 | Terumo Corp | Electronic hemadynamometer |
-
1991
- 1991-08-02 JP JP3194286A patent/JP3042051B2/en not_active Expired - Lifetime
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH01256930A (en) * | 1988-04-08 | 1989-10-13 | Nec San-Ei Instr Co Ltd | Automatic setting of cuff pressure in tonometer |
| JPH03121045A (en) * | 1989-10-05 | 1991-05-23 | Terumo Corp | Electronic hemadynamometer |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6602200B1 (en) | 1999-09-08 | 2003-08-05 | Omron Corporation | Electronic blood pressure meter |
| JP2004000422A (en) * | 2002-04-17 | 2004-01-08 | Nippon Colin Co Ltd | Sphygmomanometer having waveform analyzing function |
| US11911250B2 (en) | 2011-06-10 | 2024-02-27 | The Procter & Gamble Company | Absorbent structure for absorbent articles |
| US11759376B2 (en) | 2013-08-27 | 2023-09-19 | The Procter & Gamble Company | Absorbent articles with channels |
| US11957551B2 (en) | 2013-09-16 | 2024-04-16 | The Procter & Gamble Company | Absorbent articles with channels and signals |
| US11944526B2 (en) | 2013-09-19 | 2024-04-02 | The Procter & Gamble Company | Absorbent cores having material free areas |
Also Published As
| Publication number | Publication date |
|---|---|
| JP3042051B2 (en) | 2000-05-15 |
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