JPH08581A - Electronic sphygmomanometer - Google Patents
Electronic sphygmomanometerInfo
- Publication number
- JPH08581A JPH08581A JP6217108A JP21710894A JPH08581A JP H08581 A JPH08581 A JP H08581A JP 6217108 A JP6217108 A JP 6217108A JP 21710894 A JP21710894 A JP 21710894A JP H08581 A JPH08581 A JP H08581A
- Authority
- JP
- Japan
- Prior art keywords
- pressure
- cuff
- blood vessel
- pulse wave
- volume
- 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、血管容積を一定保持
することで、血圧を自動的に測定する容積補償式の電子
血圧計に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a volume-compensating electronic blood pressure monitor for automatically measuring blood pressure by keeping a blood vessel volume constant.
【０００２】[0002]
【従来の技術】従来、電子血圧計には、光電容積脈波や
インピーダンス（ＩＰＧ）脈波から得られる血管容積が
一定値になるようにカフ圧を制御して、血圧を測定する
ようにした容積補償式血圧計がある。2. Description of the Related Art Conventionally, in an electronic blood pressure monitor, the cuff pressure is controlled so that the blood vessel volume obtained from the photoelectric plethysmogram or the impedance (IPG) pulse wave becomes a constant value, and the blood pressure is measured. There is a volume compensation blood pressure monitor.
【０００３】[0003]
【発明が解決しようとする課題】上記した従来の容積補
償式の電子血圧計では、制御カフ圧の全範囲を通じて固
定の血管容積の目標値を使用しているが、実際の光電容
積脈波や、インピーダンス（ＩＰＧ）脈波の直流成分の
波形では、カフ圧によって血管が完全に圧閉している点
や、血圧とカフ圧が平衡している点など、血管容積が変
化していないはずの点で血管容積の増加傾向を示し、組
織変形の影響を受けている。そのため、固定の制御目標
値を使用した場合には、生体組織の影響が小さい指部で
しか測定ができず、また、実際の血圧値より最高血圧と
最低血圧の差（脈圧）が小さく出力されるという問題点
があった。In the conventional volume-compensated electronic blood pressure monitor described above, a fixed target value of the blood vessel volume is used throughout the entire range of the control cuff pressure. In the waveform of the DC component of the impedance (IPG) pulse wave, the blood vessel volume should not change, such as the point where the blood vessel is completely closed by the cuff pressure, or the point where the blood pressure and the cuff pressure are in equilibrium. The points show an increasing tendency of the blood vessel volume and are affected by the tissue deformation. Therefore, when a fixed control target value is used, measurement can be performed only on the finger part where the influence of living tissue is small, and the difference between the systolic blood pressure and the diastolic blood pressure (pulse pressure) is smaller than the actual blood pressure value and output. There was a problem that was done.
【０００４】この発明は、上記問題点に着目してなされ
たものであって、組織変形の影響を受けない、高精度に
測定をなし得る電子血圧計を提供することを目的として
いる。The present invention has been made in view of the above problems, and an object thereof is to provide an electronic sphygmomanometer that is not affected by tissue deformation and can perform highly accurate measurement.
【０００５】[0005]
【課題を解決するための手段及び作用】この出願の特許
請求の範囲の請求項１に係る電子血圧計は、カフと、こ
のカフ内の圧力を検出するカフ圧検出手段と、カフ圧を
制御するカフ圧制御手段と、カフ下の血管容積を検出す
る血管容積検出手段とを備え、カフ下血管容積が所定の
血管容積値と常に一致するようにカフ圧を制御すること
で前記カフ圧から血圧を測定するものにおいて、血管容
積脈波信号の振幅が最大となるカフ圧時の血管容積脈波
の脈波一拍区間の平均値を検出する血管容積脈波平均値
検出手段と、前記カフ圧が所定血圧値よりも大きい時の
血管容積信号の１脈波内の最小点を検出する脈波最小点
検出手段と、前記脈波最小点検出手段で検出される複数
個の最小点を補間する補間手段と、この補間手段によっ
て得られる補間曲線が前記脈波一拍区間の平均値を通過
するように、前記補間曲線に所定値を加算する演算手段
とを備え、前記演算手段によって得られる血管容積値を
制御目標値とするようにしている。An electronic sphygmomanometer according to claim 1 of the present application claims a cuff, a cuff pressure detecting means for detecting a pressure in the cuff, and a cuff pressure control. From the cuff pressure by controlling the cuff pressure and the blood vessel volume detecting means for detecting the blood vessel volume under the cuff, and controlling the cuff pressure so that the blood volume under the cuff always matches a predetermined blood vessel volume value. In measuring blood pressure, a vascular volume pulse wave average value detecting means for detecting an average value of one pulse section of the vascular volume pulse wave at the time of the cuff pressure at which the amplitude of the vascular volume pulse wave signal is maximum, and the cuff. A pulse wave minimum point detecting means for detecting a minimum point in one pulse wave of a blood vessel volume signal when the pressure is higher than a predetermined blood pressure value, and a plurality of minimum points detected by the pulse wave minimum point detecting means are interpolated. Interpolation means and the interpolation music obtained by this interpolation means So as to pass the average value of the pulse wave one beat section, there is provided a calculating means for adding a predetermined value to the interpolation curve, and the blood vessel volume value obtained by the calculating means is set as a control target value. .
【０００６】この発明の採用原理について説明する。図
１は、本発明を実施するための電子血圧計の装置構成を
示したブロック図である。この電子血圧計は、カフ１と
カフ１の圧力を検出する圧力センサ２と、コロトコフ音
マイク３と、血管容積センサ（インピーダンスプレチス
モグラフ、光電法、ストレンゲージなど）４と、血圧測
定のための処理を実行するＣＰＵ５と、加減圧ポンプ６
及び測定血圧値を表示する表示器７を備えている。そし
て、圧力センサ２によって、図２に示すカフ圧、コロト
コフ音マイク３によって図２に示すコロトコフ音信号、
血管容積センサ４によって、図２に示す血管容積信号
（交流、直流成分）が検出される。The principle of adoption of the present invention will be described. FIG. 1 is a block diagram showing a device configuration of an electronic sphygmomanometer for implementing the present invention. This electronic sphygmomanometer includes a cuff 1 and a pressure sensor 2 for detecting the pressure of the cuff 1, a Korotkoff sound microphone 3, a blood vessel volume sensor (impedance plethysmograph, photoelectric method, strain gauge, etc.) 4, and processing for blood pressure measurement. CPU 5 for executing the process, and pressurizing / depressurizing pump 6
And a display 7 for displaying the measured blood pressure value. Then, the pressure sensor 2 causes the cuff pressure shown in FIG. 2, the Korotkoff sound microphone 3 causes the Korotkoff sound signal shown in FIG.
The blood vessel volume sensor 4 detects the blood vessel volume signals (AC and DC components) shown in FIG.
【０００７】図１の加減圧ポンプ６でカフ圧を最高血圧
より数十ｍｍＨｇ高くまで加圧後、一定速度で微速減圧
する過程において、血管容積直流成分の１心拍周期毎の
容積最小点とカフ圧を検出し、それぞれＶｓｏ（ｎ）、
Ｐｓｏ（ｎ）（ｎ＝１、２、…）とし、図３に示した血
管容積信号交流成分のプラトー部分が消失するまで記録
する。また、血管容積交流成分の振幅が最大の時の同一
心拍周期内の血管容積直流成分の平均容積点とカフ圧を
Ｖｍ、Ｐｍとする。In the process of pressurizing the cuff pressure to several tens of mmHg higher than the systolic blood pressure by the pressurizing / depressurizing pump 6 in FIG. 1 and then depressurizing the blood pressure at a constant speed, the volume minimum point and the cuff of the DC component of the blood vessel volume for each cardiac cycle. The pressure is detected and Vso (n),
Pso (n) (n = 1, 2, ...) Is recorded until the plateau portion of the blood vessel volume signal AC component shown in FIG. 3 disappears. Further, the average volume points and cuff pressures of the blood vessel volume DC component within the same heartbeat cycle when the amplitude of the blood vessel volume AC component is maximum are set to Vm and Pm.
【０００８】図６の（ａ）に示したように、前記処理で
得られた血管容積とカフ圧のデータをカフ圧−血管容積
のグラフにプロットし、Ｖｓｏ（ｎ）（ｎ＝１、２、
…）をそれぞれ任意の曲線で補間し、補間曲線ｌｓｏを
算出する。本来曲線１ｓｏは血管容積が一定である場所
を連結しているので、Ｘ軸に平行な直線とならなければ
ならないが、実際はそうならない。これは、それぞれの
カフ圧に対応して、カフ下の生体組織が変形している為
と考えられる。そこで、図６の（ｂ）に示したように曲
線ｌｓｏが（Ｐｍ、Ｖｍ）の点を通るように血管容積大
の方向へ平行移動して曲線ｌｓｏ’を算出すると、この
曲線ｌｓｏ’は、それぞれのカフ圧でのカフ下生体組織
の変形の影響を含んだ制御目標値を示すことになる。As shown in FIG. 6A, the blood vessel volume and the cuff pressure data obtained by the above-mentioned treatment are plotted on a cuff pressure-vessel volume graph, and Vso (n) (n = 1, 2). ,
...) is interpolated by an arbitrary curve to calculate an interpolated curve lso. Originally, the curve 1so connects the places where the blood vessel volume is constant, so it must be a straight line parallel to the X-axis, but this is not the case. It is considered that this is because the living tissue under the cuff is deformed corresponding to each cuff pressure. Therefore, as shown in FIG. 6 (b), when the curve lso is translated in the direction of the volume of the blood vessel so as to pass through the point (Pm, Vm), and the curve lso 'is calculated, the curve lso' becomes The control target value including the influence of the deformation of the living tissue under the cuff at each cuff pressure is shown.
【０００９】また、図７に示した従来の制御目標値であ
るＬｏと本法を比較すると、従来の測定方法では、脈圧
が本来より小さめに評価され、誤差となっていたことが
わかる。特許請求の範囲の請求項４に係る電子血圧計
は、カフと、このカフ内の圧力を検出するカフ圧検出手
段と、カフ圧を制御するカフ圧制御手段と、カフ下の血
管容積を検出する血管容積検出手段とを備え、カフ下血
管容積が所定の血管容積値と常に一致するようにカフ圧
を制御することで前記カフ圧から血圧を測定するものに
おいて、カフ圧が最高血圧と一致した時の血管容積脈波
信号の脈波の一拍区間の最大点を検出する血管容積脈波
最大点検出手段と、カフ圧が最低血圧と一致した時の血
管容積脈波信号の脈波の一拍区間の最小点を検出する血
管容積脈波最小点検出手段と、血管容積脈波信号の振幅
が最大になるカフ圧時の血管容積脈波の脈波の脈波一拍
期区間の平均値を検出する血管容積脈波平均値検出手段
と、前記検出点の２点又は３点を補間する演算手段と、
を備え、前記演算手段によって得られる血管容積値を制
御目標値とするようにしている。Further, by comparing the conventional control target value Lo shown in FIG. 7 with this method, it can be seen that in the conventional measuring method, the pulse pressure was evaluated to be smaller than it should be, resulting in an error. An electronic sphygmomanometer according to claim 4 of the claims includes a cuff, a cuff pressure detecting means for detecting the pressure in the cuff, a cuff pressure control means for controlling the cuff pressure, and a blood vessel volume under the cuff. The blood pressure is measured from the cuff pressure by controlling the cuff pressure so that the blood volume under the cuff always matches a predetermined blood vessel volume value, and the cuff pressure matches the systolic blood pressure. The maximum point of the plethysmogram of the plethysmogram of the plethysmogram signal of the vascular volume pulse wave signal at the time of detection, and the pulse wave of the plethysmogram of the vascular volume pulse wave when the cuff pressure matches the minimum blood pressure. Vessel volume pulse wave minimum point detection means for detecting the minimum point of one pulse section and pulse wave of the pulse wave of the blood vessel volume pulse wave at the time of the cuff pressure at which the amplitude of the blood vessel volume pulse wave signal becomes maximum, and the average of one pulse period section Vascular volume pulse wave average value detection means for detecting the value, and two or three of the detection points Calculating means for interpolating,
And the blood vessel volume value obtained by the calculation means is set as the control target value.
【００１０】次に、この発明の電子血圧計の採用原理に
ついて説明する。この発明を実施するための電子血圧計
の装置構成は、図１に示したものと同様である。図１の
圧力センサ２、コロトコフ音マイク３、血管容積センサ
４（インピーダンスプレチスモグラフ、光電法、ストレ
ンゲージなどのいずれか）から、それぞれ図８のカフ圧
信号、コロトコフ音信号、血管容積信号（交流、直流成
分）を検出する。図１の加減圧ポンプ６でカフ圧を最高
血圧より数十ｍｍＨｇ高くまで加圧後、一定速度で微速
減圧する過程において、コロトコフ音が最初に発生した
ときの同一心拍周期内の血管容積直流成分の容積最大点
とカフ圧をＶS 、ＰS とし、コロトコフ音が最後に発生
したときの同一心拍周期内の血管容積直流成分の容積最
小点とカフ圧をＶD 、ＰD とし、血管容積交流成分の振
幅が最大のときの同一心拍周期内の血管容積直流成分の
平均容積点とカフ圧をＶM 、ＰM とする。Next, the principle of adoption of the electronic blood pressure monitor of the present invention will be described. The device configuration of the electronic sphygmomanometer for implementing the present invention is the same as that shown in FIG. From the pressure sensor 2, Korotkoff sound microphone 3, and blood vessel volume sensor 4 (any one of impedance plethysmograph, photoelectric method, strain gauge, etc.) of FIG. 1, the cuff pressure signal, Korotkoff sound signal, and blood vessel volume signal (AC, DC component) is detected. In the process of pressurizing the cuff pressure to several tens of mmHg higher than the systolic blood pressure by the pressurizing / depressurizing pump 6 in FIG. The maximum volume point and the cuff pressure of V S and P S are defined as V S and P S, and the volume minimum point of the DC component and the cuff pressure of the DC component within the same heartbeat cycle when the Korotkoff sound last occurs are defined as V D and P D. Let V M and P M be the average volume points and cuff pressures of the DC component of the blood vessel volume within the same heartbeat cycle when the amplitude of the AC component is maximum.
【００１１】図１１に示したように、前記処理で得られ
た血管容積とカフ圧のデータをカフ圧−血管容積のグラ
フにプロットし、ＶD 、ＶM 、ＶS をそれぞれ任意の曲
線で補間して曲線ＬSMD を算出する。本来曲線ＬSMD に
おいて、血管容積は一定であるので、Ｘ軸に平行な直線
とならなければならないが、実際はそうならない。これ
は、それぞれのカフ圧に対応してカフ下の生体組織が変
形している為と考えられる。そこで、曲線ＬSMD は、そ
れぞれのカフ圧でのカフ下生体組織の変形の影響を含ん
だ制御目標値を示すことになる。As shown in FIG. 11, the data of the blood vessel volume and the cuff pressure obtained by the above-mentioned processing are plotted on a graph of the cuff pressure-the blood vessel volume, and V D , V M and V S are respectively represented by arbitrary curves. The curve L SMD is calculated by interpolation. Originally, in the curve L SMD , since the blood vessel volume is constant, it must be a straight line parallel to the X axis, but it is not the case. It is considered that this is because the living tissue under the cuff is deformed corresponding to each cuff pressure. Therefore, the curve L SMD shows the control target value including the influence of the deformation of the living tissue under the cuff at each cuff pressure.
【００１２】また、図１２に示した従来の制御目標値で
あるＬ0 と本法を比較すると、従来の方法では脈圧が実
際より小さく評価されて誤差となっていたことがわか
る。Further, by comparing the conventional control target value L 0 shown in FIG. 12 with this method, it can be seen that in the conventional method, the pulse pressure was evaluated to be smaller than the actual value, resulting in an error.
【００１３】[0013]
【実施例】以下、実施例により、この発明をさらに詳細
に説明する。一実施例電子血圧計の構成は図１に示すも
のが使用される。また、この実施例電子血圧計では、図
４に示したジェネルフロー図の手順により、容積補償法
による連続血圧測定が行われる。The present invention will be described in more detail with reference to the following examples. The configuration of the electronic blood pressure monitor shown in FIG. 1 is used as one embodiment. Further, in the electronic blood pressure monitor of this embodiment, continuous blood pressure measurement by the volume compensation method is performed according to the procedure of the general flow chart shown in FIG.
【００１４】先ず、ステップＳＴ（以下、ＳＴと略す）
１で被験者に血管容積検出センサ４を内蔵した上腕カフ
１を装着する。ＳＴ２でカフ圧の制御目標値を算出す
る。ＳＴ３、ＳＴ４でカフ圧を検出し、リアルタイムの
血圧波形、あるいは最高血圧値、最低血圧値を表示す
る。次に、血管容積センサ４により、血管容積を検出し
て（ＳＴ５）、制御目標値との誤差を算出し（ＳＴ
６）、その誤差からカフ圧の制御量を算出する（ＳＴ
７）。そして、ＳＴ８で制御量に応じてカフ圧を制御
し、ＳＴ９で終了を確認して、非選択の場合はＳＴ３に
戻る。First, step ST (hereinafter abbreviated as ST)
At 1, the subject wears an upper arm cuff 1 having a built-in blood vessel volume detection sensor 4. In ST2, the control target value of the cuff pressure is calculated. The cuff pressure is detected in ST3 and ST4, and the real-time blood pressure waveform, or the maximum blood pressure value and the minimum blood pressure value are displayed. Next, the blood vessel volume sensor 4 detects the blood vessel volume (ST5) and calculates the error from the control target value (ST
6) Calculate the control amount of the cuff pressure from the error (ST
7). Then, in ST8, the cuff pressure is controlled according to the control amount, in ST9, the end is confirmed, and in the case of non-selection, the process returns to ST3.
【００１５】図５は、本発明の要部に相当する図５のＳ
Ｔ２のカフ圧の制御目標値の算出処理ルーチンの詳細フ
ロー図である。このルーチンに入ると、先ず、ＳＴ２０
１で最高血圧より数十ｍｍＨｇ高くまで加圧後、ＳＴ２
０２で微速減圧を開始して、ＳＴ２０３でカフ圧を検出
し、ＳＴ２０４で減圧目標値に達したかチェックして、
減圧目標値に達するまでＳＴ２１３で微速減圧を行いな
がら、ＳＴ２０３からＳＴ２１３のステップに戻り、Ｓ
Ｔ２０３、…、ＳＴ２１３の処理を繰り返す。ＳＴ２０
５で血管容積の直流成分と交流成分をそれぞれ検出し
て、さらに脈波成分が最大か否かを判別して（ＳＴ２０
６）、最大でない場合は、次のＳＴ２０７、ＳＴ２０８
をスキップするが、血管容積交流成分が最大時には、同
一脈拍周期内の血管容積直流成分の平均容積Ｖｍをメモ
リに記憶する（ＳＴ２０７）とともに、カフ圧Ｐｍを同
じくメモリに保存記憶する（ＳＴ２０８）。FIG. 5 shows an S of FIG. 5 corresponding to the main part of the present invention.
It is a detailed flow chart of a calculation processing routine of the control target value of the cuff pressure of T2. When entering this routine, first, ST20
In step 1, pressurize to several tens of mmHg higher than systolic blood pressure, then ST2
At 02, the slow decompression is started, the cuff pressure is detected at ST203, and it is checked at ST204 whether the decompression target value is reached,
While performing slow decompression in ST213 until the decompression target value is reached, the process returns from ST203 to ST213, where S
The processing of T203, ..., ST213 is repeated. ST20
In step 5, the DC component and the AC component of the blood vessel volume are detected, and it is further determined whether or not the pulse wave component is the maximum (ST20
6) If it is not the maximum, the next ST207, ST208
However, when the blood vessel volume AC component is maximum, the average volume Vm of the blood vessel volume DC component within the same pulse cycle is stored in the memory (ST207), and the cuff pressure Pm is also stored and stored in the memory (ST208).
【００１６】ＳＴ２０９で脈拍一周期内の血管容積最小
点の波形形状を検出し、ＳＴ２１０でプラトー部分（平
坦部分）があるかないかチェックし、プラトー部分が無
くなったら次に続くＳＴ２１１、ＳＴ２１２のステップ
を飛ばす。プラトー部分が存在する間は、ＳＴ２１１で
脈拍一周期内の血管容積最小点を検出してＶｓｏ（ｎ）
（ｎ＝１、２、…）に保存し、ＳＴ２１２でその時のカ
フ圧Ｐｓｏ（ｎ）（ｎ＝１、２、…）を保存する。In ST209, the waveform shape of the minimum point of the blood vessel volume within one cycle of the pulse is detected. In ST210, it is checked whether or not there is a plateau portion (flat portion). If the plateau portion disappears, the following steps of ST211, ST212 are performed. Fly. While the plateau portion is present, Vso (n) is detected by detecting the blood vessel volume minimum point in one pulse cycle in ST211.
(N = 1, 2, ...) And the cuff pressure Pso (n) (n = 1, 2, ...) At that time is stored in ST212.
【００１７】ＳＴ２０４でカフ圧が減圧目標に到達した
ことが確認されたら、ＳＴ２１４に移り、メモリ上の圧
−容積グラフにＰｓｏ（ｎ）、Ｖｓｏ（ｎ）（ｎ＝１、
２、…）をプロットし、任意の曲線で補間して曲線ｌｓ
ｏを算出する。ＳＴ２１５で曲線ｌｓｏが（Ｐｍ、Ｖ
ｍ）の点を通るように曲線ｌｓｏを血管容積大の方向へ
平行移動して曲線ｌｓｏ’を算出し、制御目標血管容積
曲線とする。そして、リターンする。When it is confirmed in ST204 that the cuff pressure has reached the decompression target, the process proceeds to ST214, and Pso (n), Vso (n) (n = 1,
2, ...) are plotted and interpolated with an arbitrary curve to obtain the curve ls
Calculate o. In ST215, the curve lso is (Pm, V
The curve lso is translated in the direction of the large blood vessel volume so as to pass through the point m), and the curve lso ′ is calculated to be the control target blood vessel volume curve. And it returns.
【００１８】図７は、本発明の上記実施例による制御目
標値と、従来の制御目標値を使用したときの容積補償式
血圧測定値の相違を概念的に示した図である。Ｐ−Ｖ
SYS は、ある最高血圧値の時の、１脈拍周期内の血管容
積最大点を任意のカフ圧に対してプロットしたもので、
Ｐ−ＶDIA はある最低血圧値の時の、１心拍周期内の血
管容積最小点を任意のカフ圧に対してプロットしたもの
である。容積補償式血圧測定において、本発明による組
織変形の影響を考慮したカフ圧依存の制御目標値ｌｓ
ｏ’を使用した場合は、前記最高血圧をＰｓと評価する
のに対して、従来の固定された制御目標値Ｌｏの場合で
は、前記最高Ｐｓ’と評価される。つまり、本発明の上
記実施例による組織変形の影響を考慮した制御目標値を
使用することにより、従来の固定された制御目標値を使
用した場合に発生していた測定誤差（ｅＰｓ）を取り除
くことができる。FIG. 7 is a diagram conceptually showing the difference between the control target value according to the embodiment of the present invention and the volume-compensated blood pressure measurement value when the conventional control target value is used. PV
SYS is a plot of the maximum point of vascular volume within one pulse cycle at a certain systolic blood pressure value against an arbitrary cuff pressure.
P-V DIA is a plot of the minimum point of the blood vessel volume within one heartbeat cycle with respect to an arbitrary cuff pressure at a certain minimum blood pressure value. In the volume-compensated blood pressure measurement, the cuff pressure-dependent control target value ls considering the effect of tissue deformation according to the present invention
When o'is used, the systolic blood pressure is evaluated as Ps, whereas in the case of the conventional fixed control target value Lo, it is evaluated as the maximal Ps'. That is, by using the control target value in consideration of the influence of the tissue deformation according to the above-described embodiment of the present invention, the measurement error (ePs) that occurs when the conventional fixed control target value is used is removed. You can
【００１９】次に、他の実施例電子血圧計〔請求項４に
係る実施例〕を説明する。図９、図１０は、図４のＳＴ
２のカフ圧の制御目標値を算出する処理の他の例を詳細
に示すフロー図である。概略的な全体フローは図４と同
様である。図５の場合と同様に、先ず、カフを最高血圧
よりも数十ｍｍＨｇ高い値、つまり加圧目標圧まで加圧
し（ＳＴ２１）、その後、微速減圧を開始し（ＳＴ２
２）、カフ圧を検出しつつ、減圧目標値に達したかをチ
ェックし（ＳＴ２３、ＳＴ２４）、減圧目標値となるま
では、ＳＴ２５、…、ＳＴ３６の処理を繰り返す。Next, another embodiment of an electronic blood pressure monitor [an embodiment according to claim 4] will be described. 9 and 10 show ST of FIG.
It is a flowchart which shows in detail another example of the process which calculates the control target value of the cuff pressure of 2. The schematic overall flow is the same as in FIG. As in the case of FIG. 5, first, the cuff is inflated to a value that is several tens of mmHg higher than the systolic blood pressure, that is, the inflating target pressure (ST21), and then the slow depressurization is started (ST2).
2) While detecting the cuff pressure, it is checked whether the pressure reduction target value is reached (ST23, ST24), and the processes of ST25, ..., ST36 are repeated until the pressure reduction target value is reached.
【００２０】ステップＳＴ２５で、血管容積の直流成分
と交流成分をそれぞれ検出して、次に血管容積の交流成
分の振幅が最大か？をチェックし（ＳＴ２６）、振幅最
大の場合に、振幅最大時の一周期内の血管容積直流成分
の平均容積を検出し、メモリＶM に記憶するとともに
（ＳＴ２７）、その時のカフ圧をメモリＰM に記憶する
（ＳＴ２８）。ＳＴ２６で、振幅最大でない場合は、ス
テップＳＴ２７、ＳＴ２８をスキップして、ステップＳ
Ｔ２９に移る。In step ST25, the DC component and the AC component of the blood vessel volume are respectively detected, and is the amplitude of the AC component of the blood vessel volume the maximum? Check the (ST26), when the maximum amplitude, to detect the average volume of the vessel volume the DC component in one period of time the maximum amplitude, as well as stored in the memory V M (ST27), the memory P cuff pressure at that time Store in M (ST28). If the amplitude is not the maximum in ST26, steps ST27 and ST28 are skipped and step S
Move to T29.
【００２１】ステップＳＴ２９でコロトコフ（Ｋ）音を
検出し、検出したコロトコフ音が最初の場合は、対応す
るカフ圧が最高血圧であるから、ステップＳＴ３０のＳ
ＹＳか？の判定がＹＥＳとなり、同一振幅周期内の振幅
最大点の血管容積を検出し、メモリＶS に記憶する（Ｓ
Ｔ３１）とともに、この時のカフ圧をメモリＰS に記憶
する（ＳＴ３２）。検出されたコロトコフ音が最初でな
い場合、あるいはコロトコフ音が検出されていない場合
は、ステップＳＴ３０の判定ＮＯで、ステップＳＴ３
１、ＳＴ３２をスキップし、ステップＳＴ３３に移る。When the Korotkoff (K) sound is detected in step ST29 and the detected Korotkoff sound is the first, the corresponding cuff pressure is the systolic blood pressure, and therefore, step S30 S
YS? Is YES, the blood vessel volume at the maximum amplitude point within the same amplitude cycle is detected and stored in the memory V S (S
Along with T31), the cuff pressure at this time is stored in the memory P S (ST32). If the detected Korotkoff sound is not the first, or if the Korotkoff sound is not detected, the determination result in step ST30 is NO, and step ST3
1, ST32 is skipped, and the process proceeds to step ST33.
【００２２】ステップＳＴ３３では、検出されたコロト
コフ音が最後の（消滅する）場合、その対応するカフ圧
が最低血圧ＤＩＡであるから、ステップＳＴ３３のＤＩ
Ａか？の判定がＹＥＳとなり、同一脈拍周期内の振幅最
小点の血管容積を検出し、メモリＶD に記憶するととも
に（ＳＴ３５）、その時点のカフ圧をメモリＰD に記憶
する（ＳＴ３６）。コロトコフが最後の時点でない場
合、ステップＳＴ３３の判定ＮＯで、ステップＳＴ３
４、ＳＴ３５をスキップし、ステップＳＴ３６に移る。
ステップＳＴ３６では、微速減圧してステップＳＴ２４
に戻る。In step ST33, when the detected Korotkoff sound is the last (disappears), the corresponding cuff pressure is the diastolic blood pressure DIA.
Is it A? Is YES, the blood vessel volume at the minimum amplitude point in the same pulse cycle is detected and stored in the memory V D (ST35), and the cuff pressure at that time is stored in the memory P D (ST36). If Korotkoff is not the final time point, the determination is NO in step ST33, and step ST3
4, ST35 is skipped, and the process proceeds to step ST36.
In step ST36, the pressure is depressurized at a very low speed and then step ST24
Return to
【００２３】以上の処理を経て、ステップＳＴ２４にお
いて、カフ圧が減圧目標に到達したことが確認されると
ステップＳＴ３７に移り、メモリ上の圧−容積グラフに
（Ｐ S 、ＶS ）（ＰM 、ＶM ）（ＰD 、ＶD ）の３点を
プロットし、任意の曲線で補間して曲線ＬSMD を算出し
て図１１のようにカフ圧に対する制御血管容積曲線とす
る。After the above processing, step ST24
And it is confirmed that the cuff pressure has reached the decompression target.
Move to step ST37, and display the pressure-volume graph on the memory.
(P S, VS) (PM, VM) (PD, VD) 3 points
Plot and interpolate with any curve to obtain curve LSMDAnd calculate
As shown in FIG. 11, a control vessel volume curve with respect to the cuff pressure is shown.
It
【００２４】図１２は、図９の実施例の場合の制御目標
値と、従来の制御目標値を使用したときの容積補償式血
圧測定値の相違を概念的に示した図である。Ｐ−ＶSYS
は、ある最高血圧値の時の一脈拍周期内の血管容積最大
点を任意のカフ圧に対してプロットしたもので、Ｐ−Ｖ
DIA は、ある最低血圧値の時の一脈拍周期内の血管容積
最小点を任意のカフ圧に対してプロットしたものであ
る。容積補償式血圧測定において、本発明による組織変
形の影響を考慮したカフ圧依存の制御目標ＬSMDを使用
した場合は、前記最高、最低血圧をそれぞれＰS 、ＰD
と評価するのに対して、従来の固定された制御目標値Ｌ
0 の場合では、前記最高、最低血圧はそれぞれＰS ' 、
ＰD ' と評価される。つまり、本発明による組織変形の
影響を考慮した制御目標値を使用することにより、従来
の固定された制御目標値を使用したた場合に発生してい
た測定誤差（最低血圧側ではカフ圧大の方へｅＰD 、最
高血圧側ではカフ圧小の方へｅＰS ）を取り除くことが
できる。FIG. 12 is a diagram conceptually showing the difference between the control target value in the case of the embodiment of FIG. 9 and the volume-compensated blood pressure measurement value when the conventional control target value is used. PV SYS
Is a plot of the maximum point of the blood vessel volume within one pulse cycle at a certain systolic blood pressure value with respect to an arbitrary cuff pressure, and P-V
DIA is a plot of the minimum point of vascular volume in one pulse cycle at a certain minimum blood pressure value with respect to an arbitrary cuff pressure. In the volume-compensated blood pressure measurement, when the cuff pressure-dependent control target L SMD in consideration of the influence of tissue deformation according to the present invention is used, the maximum and minimum blood pressures are respectively P S and P D.
In contrast to the conventional fixed control target value L
In the case of 0, the maximum and minimum blood pressures are P S 'and
It is evaluated as P D '. That is, by using the control target value in consideration of the influence of the tissue deformation according to the present invention, the measurement error (when the cuff pressure is large on the lowest blood pressure side is generated when the conventional fixed control target value is used. It is possible to remove eP D toward the person and eP S toward the person with low cuff pressure on the systolic side.
【００２５】[0025]
【発明の効果】請求項１に記載の発明によれば、血管容
積脈波信号の振幅が最大となるカフ圧時の血管容積脈波
の脈波一拍区間の平均値を検出する血管容積脈波平均値
検出手段と、前記カフ圧が所定血圧値よりも大きい時の
血管容積信号の１脈波内の最小点を検出する脈波最小点
検出手段と、前記脈波最小点検出手段で検出される複数
個の最小点を補間する補間手段と、この補間手段によっ
て得られる補間曲線が前記脈波一拍区間の平均値を通過
するように、前記補間曲線に所定値を加算する演算手段
とを特徴的に備え、前記演算手段によって得られる血管
容積値を制御目標値とするようにしたので、また、請求
項４に記載の発明によれば、カフと、このカフ内の圧力
を検出するカフ圧検出手段と、カフ圧を制御するカフ圧
制御手段と、カフ下の血管容積を検出する血管容積検出
手段とを備え、カフ下血管容積が所定の血管容積値と常
に一致するようにカフ圧を制御することで前記カフ圧か
ら血圧を測定する電子血圧計において、カフ圧が最高血
圧と一致した時の血管容積脈波信号の脈波の一拍区間の
最大点を検出する血管容積脈波最大点検出手段と、カフ
圧が最低血圧と一致した時の血管容積脈波信号の脈波の
一拍区間の最小点を検出する血管容積脈波最小点検出手
段と、血管容積脈波信号の振幅が最大になるカフ圧時の
血管容積脈波の脈波の脈波一拍期区間の平均値を検出す
る血管容積脈波平均値検出手段と、前記検出点の２点又
は３点を補間する演算手段と、を備え、前記演算手段に
よって得られる血管容積値を制御目標値とするようにし
ているので、容積補償式の血圧測定の過程で血圧とバラ
ンスするようにカフ圧を大きく変化させても組織変形に
よる影響を受けないので、より正確な血圧測定ができる
という効果が得られる。According to the first aspect of the present invention, the vascular volume pulse for detecting the average value of one pulse wave section of the vascular volume pulse wave at the cuff pressure at which the amplitude of the vascular volume pulse wave signal is maximized. A wave average value detecting means, a pulse wave minimum point detecting means for detecting a minimum point in one pulse wave of a blood vessel volume signal when the cuff pressure is larger than a predetermined blood pressure value, and the pulse wave minimum point detecting means. An interpolating means for interpolating a plurality of minimum points, and an arithmetic means for adding a predetermined value to the interpolating curve so that the interpolating curve obtained by the interpolating means passes the average value of the pulse wave one beat section. Since the blood vessel volume value obtained by the calculation means is set as the control target value, the cuff and the pressure in the cuff are detected. A cuff pressure detecting means, a cuff pressure control means for controlling the cuff pressure, An electronic sphygmomanometer comprising a blood vessel volume detecting means for detecting the blood vessel volume, and measuring the blood pressure from the cuff pressure by controlling the cuff pressure so that the blood volume under the cuff always matches a predetermined blood vessel volume value, Vessel volume pulse wave maximum point detection means for detecting the maximum point of one pulse section of the pulse wave of the plethysmographic signal when the cuff pressure matches the systolic blood pressure, and vascular volume when the cuff pressure matches the diastolic blood pressure A vascular volume pulse wave minimum point detecting means for detecting the minimum point of one pulse section of the pulse wave of the pulse wave signal, and the pulse wave pulse of the vascular volume pulse wave at the time of the cuff pressure at which the amplitude of the vascular volume pulse wave signal becomes maximum. The blood vessel volume pulse wave average value detecting means for detecting the average value of the wave one-beat period section and the calculating means for interpolating two or three of the detection points are provided, and the blood vessel volume value obtained by the calculating means is calculated. Since it is set to the control target value, volume compensation type blood pressure measurement Since not influenced by tissue deformation even significant changes the cuff pressure so as to balance the blood pressure in the process, effect that more can accurate blood pressure measurements.
【図１】この発明の実施例電子血圧計の構成を示すブロ
ック図である。FIG. 1 is a block diagram showing a configuration of an electronic blood pressure monitor according to an embodiment of the present invention.
【図２】同実施例電子血圧計におけるカフ圧を変化させ
た場合の、コロトコフ音、血管容積直流成分、及び血管
容積交流成分の関係を示す図である。FIG. 2 is a diagram showing a relationship between a Korotkoff sound, a blood vessel volume direct current component, and a blood vessel volume alternating current component when the cuff pressure is changed in the electronic blood pressure monitor of the embodiment.
【図３】同実施例電子血圧計におけるカフ圧を減圧した
場合の、血管容積交流成分のプラトー部分の消失を説明
する図である。FIG. 3 is a diagram for explaining disappearance of a plateau portion of a blood vessel volume AC component when the cuff pressure is reduced in the electronic blood pressure monitor of the embodiment.
【図４】同実施例電子血圧計の全体動作を説明するため
のフロー図である。FIG. 4 is a flowchart for explaining the overall operation of the electronic blood pressure monitor of the embodiment.
【図５】同フロー図におけるカフ圧の制御目標値の算出
処理を、さらに詳説するためのフロー図である。FIG. 5 is a flowchart for further explaining the calculation process of the control target value of the cuff pressure in the same flowchart.
【図６】同実施例電子血圧計の血管容積の複数の最小
点、及びその補間と、オフセット成分の加算を説明する
図である。FIG. 6 is a diagram illustrating a plurality of minimum points of a blood vessel volume of the electronic blood pressure monitor of the embodiment, interpolation of the minimum points, and addition of an offset component.
【図７】従来の容積補償式の電子血圧計と、上記実施例
電子血圧計の測定精度の差を説明するための図である。FIG. 7 is a diagram for explaining a difference in measurement accuracy between a conventional volume-compensated electronic blood pressure monitor and the electronic blood pressure monitor of the above-described embodiment.
【図８】他の実施例電子血圧計におけるカフ圧を変化さ
せた場合のコロトコフ音、血管容積直流成分、及び血管
容積交流成分の関係を示す図である。FIG. 8 is a diagram showing a relationship among a Korotkoff sound, a blood vessel volume direct current component, and a blood vessel volume alternating current component when the cuff pressure is changed in the electronic blood pressure monitor of another embodiment.
【図９】同実施例電子血圧計のカフ圧の制御目標値の算
出処理の詳細を示すフロー図である。FIG. 9 is a flowchart showing the details of the calculation processing of the control target value of the cuff pressure of the electronic blood pressure monitor of the embodiment.
【図１０】図９のフロー図とともに、同実施例電子血圧
計のカフ圧の制御目標値の算出処理を詳細に示すフロー
図である。10 is a flow chart showing in detail the calculation process of the control target value of the cuff pressure of the electronic blood pressure monitor of the embodiment together with the flow chart of FIG. 9.
【図１１】同実施例電子血圧計におけるカフ圧と血管容
積の関係を説明する図である。FIG. 11 is a diagram illustrating the relationship between cuff pressure and blood vessel volume in the electronic blood pressure monitor of the same embodiment.
【図１２】従来の容積補償式の電子血圧計と、上記実施
例電子血圧計の測定精度の差を説明する図である。FIG. 12 is a diagram illustrating a difference in measurement accuracy between a conventional volume-compensated electronic blood pressure monitor and the electronic blood pressure monitor of the above-described embodiment.
１ カフ ２ 圧力センサ ３ コロトコフ音マイク ４ 血管容積センサ ５ ＣＰＵ ６ 加減圧ポンプ ７ 表示器 1 cuff 2 pressure sensor 3 Korotkoff sound microphone 4 blood vessel volume sensor 5 CPU 6 pressurizing / depressurizing pump 7 indicator
Claims (4)
圧検出手段と、カフ圧を制御するカフ圧制御手段と、カ
フ下の血管容積を検出する血管容積検出手段とを備え、
カフ下血管容積が所定の血管容積値と常に一致するよう
にカフ圧を制御することで前記カフ圧から血圧を測定す
る電子血圧計において、 血管容積脈波信号の振幅が最大となるカフ圧時の血管容
積脈波の脈波一拍区間の平均値を検出する血管容積脈波
平均値検出手段と、 前記カフ圧が所定血圧値よりも大きい時の血管容積信号
の１脈波内の最小点を検出する脈波最小点検出手段と、 前記脈波最小点検出手段で検出される複数個の最小点を
補間する補間手段と、 この補間手段によって得られる補間曲線が前記脈波一拍
区間の平均値を通過するように、前記補間曲線に所定値
を加算する演算手段とを備え、 前記演算手段によって得られる血管容積値を制御目標値
とするようにしたことを特徴とする電子血圧計。1. A cuff, a cuff pressure detecting means for detecting a pressure in the cuff, a cuff pressure control means for controlling a cuff pressure, and a blood vessel volume detecting means for detecting a blood vessel volume under the cuff,
An electronic sphygmomanometer that measures blood pressure from the cuff pressure by controlling the cuff pressure so that the volume under the cuff always matches the predetermined blood vessel volume value. Blood vessel plethysmogram average value detecting means for detecting an average value of the plethysmogram of the blood vessel plethysmogram, and the minimum point in one pulse wave of the vascular volume signal when the cuff pressure is larger than a predetermined blood pressure value. Pulse wave minimum point detection means, an interpolation means for interpolating a plurality of minimum points detected by the pulse wave minimum point detection means, and an interpolation curve obtained by this interpolation means is An electronic sphygmomanometer comprising: a calculation unit that adds a predetermined value to the interpolation curve so as to pass an average value, and a blood vessel volume value obtained by the calculation unit is set as a control target value.
フ圧を最高血圧より充分加圧後徐々に減圧する過程にお
いて、血管容積脈波の各脈波内の最小点部分からプラト
ーな形状が消失することによって決定されるものである
請求項１記載の電子血圧計。2. The predetermined blood pressure of the pulse wave minimum point detecting means has a plateau from the minimum point portion in each pulse wave of the blood vessel volume pulse wave in the process of sufficiently reducing the cuff pressure from the systolic blood pressure and then gradually decreasing it. The electronic sphygmomanometer according to claim 1, wherein the shape is determined by disappearance of the shape.
の血圧測定手段によって得られた最低血圧値である請求
項１記載の電子血圧計。3. The electronic sphygmomanometer according to claim 1, wherein the predetermined blood pressure of the pulse wave minimum point detecting means is a minimum blood pressure value obtained by another blood pressure measuring means.
圧検出手段と、カフ圧を制御するカフ圧制御手段と、カ
フ下の血管容積を検出する血管容積検出手段とを備え、
カフ下血管容積が所定の血管容積値と常に一致するよう
にカフ圧を制御することで前記カフ圧から血圧を測定す
る電子血圧計において、 カフ圧が最高血圧と一致した時の血管容積脈波信号の脈
波の一拍区間の最大点を検出する血管容積脈波最大点検
出手段と、 カフ圧が最低血圧と一致した時の血管容積脈波信号の脈
波の一拍区間の最小点を検出する血管容積脈波最小点検
出手段と、 血管容積脈波信号の振幅が最大になるカフ圧時の血管容
積脈波の脈波の脈波一拍期区間の平均値を検出する血管
容積脈波平均値検出手段と、 前記検出点の２点又は３点を補間する演算手段と、を備
え、 前記演算手段によって得られる血管容積値を制御目標値
とするようにしたことを特徴とする電子血圧計。4. A cuff, a cuff pressure detecting means for detecting a pressure in the cuff, a cuff pressure control means for controlling a cuff pressure, and a blood vessel volume detecting means for detecting a blood vessel volume under the cuff,
In an electronic sphygmomanometer that measures blood pressure from the cuff pressure by controlling the cuff pressure so that the sub-cuff blood vessel volume always matches a predetermined blood vessel volume value, a vascular volume pulse wave when the cuff pressure matches the systolic blood pressure The maximum point of the pulse wave of the pulse wave of the signal is detected, and the minimum point of the pulse wave of the pulse wave signal of the blood vessel is detected when the cuff pressure matches the minimum blood pressure. Vessel volume pulse minimum point detecting means for detecting, and vascular volume pulse for detecting the average value of the pulse wave of the pulse wave of the plethysmogram at cuff pressure at which the amplitude of the plethysmogram signal is maximum An electronic device comprising: a wave average value detection means; and a calculation means for interpolating two or three of the detection points, wherein the blood vessel volume value obtained by the calculation means is used as a control target value. Sphygmomanometer.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP21710894A JP3211130B2 (en) | 1994-04-21 | 1994-09-12 | Electronic sphygmomanometer |
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP8281394 | 1994-04-21 | ||
| JP6-82813 | 1994-04-21 | ||
| JP21710894A JP3211130B2 (en) | 1994-04-21 | 1994-09-12 | Electronic sphygmomanometer |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH08581A true JPH08581A (en) | 1996-01-09 |
| JP3211130B2 JP3211130B2 (en) | 2001-09-25 |
Family
ID=26423828
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP21710894A Expired - Fee Related JP3211130B2 (en) | 1994-04-21 | 1994-09-12 | Electronic sphygmomanometer |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP3211130B2 (en) |
Cited By (5)
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|---|---|---|---|---|
| WO2008014725A2 (en) * | 2006-07-31 | 2008-02-07 | Univerzita Karlova 3. lékarská fakulta | Device for generation of a triggering signal |
| WO2011122116A1 (en) * | 2010-03-30 | 2011-10-06 | オムロンヘルスケア株式会社 | Blood pressure measurement device, and method for controlling blood pressure measurement device |
| WO2011122117A1 (en) * | 2010-03-30 | 2011-10-06 | オムロンヘルスケア株式会社 | Blood pressure measurement device, and method for controlling blood pressure measurement device |
| JP2016032488A (en) * | 2014-07-30 | 2016-03-10 | 日本光電工業株式会社 | Biological information measurement device, biological information measurement method, and program |
| JP2018108404A (en) * | 2018-02-15 | 2018-07-12 | 日本光電工業株式会社 | Biological information measuring device, biological information measuring method, and program |
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| KR20220069273A (en) | 2020-11-20 | 2022-05-27 | 삼성전자주식회사 | Apparatus and method for detecting body component |
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1994
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Cited By (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2008014725A2 (en) * | 2006-07-31 | 2008-02-07 | Univerzita Karlova 3. lékarská fakulta | Device for generation of a triggering signal |
| WO2008014725A3 (en) * | 2006-07-31 | 2008-03-13 | Univerzita Karlova 3 Lekarska | Device for generation of a triggering signal |
| WO2011122116A1 (en) * | 2010-03-30 | 2011-10-06 | オムロンヘルスケア株式会社 | Blood pressure measurement device, and method for controlling blood pressure measurement device |
| WO2011122117A1 (en) * | 2010-03-30 | 2011-10-06 | オムロンヘルスケア株式会社 | Blood pressure measurement device, and method for controlling blood pressure measurement device |
| JP2011206296A (en) * | 2010-03-30 | 2011-10-20 | Omron Healthcare Co Ltd | Blood pressure measurement device, and method for controlling the same |
| JP2011206320A (en) * | 2010-03-30 | 2011-10-20 | Omron Healthcare Co Ltd | Blood pressure measurement device, and method for controlling the same |
| DE112011101145T5 (en) | 2010-03-30 | 2013-01-10 | Omron Healthcare Co., Ltd. | Blood pressure measuring device and control method for blood pressure measuring device |
| US9364156B2 (en) | 2010-03-30 | 2016-06-14 | Omron Healthcare Co., Ltd. | Blood pressure measurement device and control method for blood pressure measurement device |
| JP2016032488A (en) * | 2014-07-30 | 2016-03-10 | 日本光電工業株式会社 | Biological information measurement device, biological information measurement method, and program |
| US10165952B2 (en) | 2014-07-30 | 2019-01-01 | Nihon Kohden Corporation | Biological information measuring apparatus and biological information measuring method |
| JP2018108404A (en) * | 2018-02-15 | 2018-07-12 | 日本光電工業株式会社 | Biological information measuring device, biological information measuring method, and program |
Also Published As
| Publication number | Publication date |
|---|---|
| JP3211130B2 (en) | 2001-09-25 |
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