JPS58149731A - Non-observing type hemomanometer apparatus - Google Patents
Non-observing type hemomanometer apparatusInfo
- Publication number
- JPS58149731A JPS58149731A JP57030502A JP3050282A JPS58149731A JP S58149731 A JPS58149731 A JP S58149731A JP 57030502 A JP57030502 A JP 57030502A JP 3050282 A JP3050282 A JP 3050282A JP S58149731 A JPS58149731 A JP S58149731A
- Authority
- JP
- Japan
- Prior art keywords
- cuff
- blood pressure
- pressure
- amplifier
- sensor
- 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
(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】
本願は非観血式の血圧測定装置に関し、更に詳しくは、
カフ内勤脈波の差分を算出し、そのピーク値を検出して
最高血圧および最低血圧を測定する装置に関する。DETAILED DESCRIPTION OF THE INVENTION The present application relates to a non-invasive blood pressure measuring device, and more specifically,
The present invention relates to a device that calculates the difference between in-cuff pulse waves, detects its peak value, and measures systolic blood pressure and diastolic blood pressure.
血圧の測定は、一般に、観点式と非観血式との二種類に
分けられる。Blood pressure measurement is generally divided into two types: a viewpoint method and a non-invasive method.
観点式とは、血管を切開あるいは針を血管に刺して血圧
とその変動を直接圧力計に導き測定するものである。具
体的には、液体を満たしたカテーラル(中空管)あるい
はセンサを測定部位にまで挿入し、血圧およびその変動
を体外に置かれた圧カドランスジューサまで導き、該ト
ランスジューサの出力信号を増幅、記録表示する。The viewpoint method is one in which blood pressure and its fluctuations are measured directly by cutting the blood vessel or inserting a needle into the blood vessel and leading it to a pressure gauge. Specifically, a catheter (hollow tube) or sensor filled with liquid is inserted into the measurement site, blood pressure and its fluctuations are guided to a pressure transducer placed outside the body, and the output signal of the transducer is amplified. Record and display.
しかしながら、この方式による血圧測定は針等を直接血
管に刺すわけであるから、患者に負担を与え、血圧を容
易に測定するというわけにはいかない。However, blood pressure measurement using this method involves directly inserting a needle or the like into a blood vessel, which places a burden on the patient and does not allow easy measurement of blood pressure.
そこで現在では、特別の場合を除き、非観血式つまシ体
外から間接的に血圧を測定する方法が広く行われている
。Therefore, except in special cases, non-invasive methods of measuring blood pressure indirectly from outside the body are widely used.
現在、この間接法として最も一般的なものは、聴診法と
呼ばれる方法で、次の手順に従って行なわれる。Currently, the most common indirect method is called the auscultation method, which is performed according to the following steps.
まず、上腕部にカフ(圧迫帯)を巻き、該カフの内圧を
加圧ポンプで上昇させた後、徐々に圧力を減じながら、
肘の動脈上に聴診器を置いて聴診し、カフ内圧が最高血
圧値に一致すると心拍に同期して発生するコロトコフ音
(カフ下の動脈を通過する血流が末梢側の静止した動脈
血と衝突し、血管壁を振動させる音)を聴きとり、また
カフ内圧が最低血圧値と一致するとコロトコフ音が消滅
することを確認して、最高血圧と最低血圧とを測定する
。First, a cuff (compression band) is wrapped around the upper arm, and after increasing the internal pressure of the cuff with a pressure pump, the pressure is gradually reduced while
Place a stethoscope over the elbow artery and auscultate. When the internal cuff pressure matches the systolic blood pressure value, a Korotkoff sound occurs in synchronization with the heartbeat (the blood flow passing through the artery under the cuff collides with stationary arterial blood on the distal side). The systolic blood pressure and diastolic blood pressure are measured by listening to the sound that vibrates the blood vessel wall and confirming that the Korotkoff sound disappears when the cuff internal pressure matches the diastolic blood pressure value.
また、現在電気血圧計として使用されているものも、上
記聴診法の原理を応用したもので、マイクロフォンでコ
ロトコフ音を集音し判別確認後、メータ等によって表示
する。Furthermore, the electric blood pressure monitors currently in use apply the principle of the auscultation method described above, and the Korotkoff sounds are collected with a microphone and, after discrimination and confirmation, are displayed on a meter or the like.
しかしながら、この血圧計で特に難かしい・ のは、
通常人間が行なう、最高、最低血圧値め判定基準となる
コロトコフ音の確認判定を機械が行なわなければならな
いことである。However, what is particularly difficult about this blood pressure monitor is:
This means that the machine must perform the confirmation and judgment of Korotkoff sounds, which are the standard for determining systolic and diastolic blood pressure values, which is normally performed by humans.
最高、最低血圧値の決定には、コロトコフ音の発現ある
いは消滅を確認判定する必要があるが、その音量は非常
に微弱であるため、カフ圧制御時、腕を動かしたときに
発生するマイクロホンと皮膚の摩擦雑音の影響を受は易
く、血圧の測定を困難にしている。In order to determine the maximum and diastolic blood pressure values, it is necessary to confirm and judge the appearance or disappearance of Korotkoff sounds, but since the volume is very weak, it is difficult to determine whether the Korotkoff sounds appear or disappear. They are susceptible to skin friction noise, making blood pressure measurement difficult.
本発明は、従来の血圧計のかかる欠陥を消却するために
開発されたもので、これまでとは全く異なる原理、すな
わちカフ内勤脈波の差分を算出し、そのピーク値を検出
して最高血圧および最低血圧を測定する方法を考案した
ものである。The present invention was developed to eliminate such defects in conventional blood pressure monitors, and uses a completely different principle from the previous ones, that is, it calculates the difference between cuff pulse waves, detects its peak value, and measures the systolic blood pressure. and devised a method for measuring diastolic blood pressure.
以下、本発明を図示実施例に基づいて詳説する。Hereinafter, the present invention will be explained in detail based on illustrated embodiments.
図面牙1図は、本発明に係る血圧計の一実施例を示す構
成図である。図示において、センサ(4)(マイクロフ
ォン、圧トランスジューサ、光センサ等を含む)は、カ
フ(1)から中空管(6)を介し外部に引き出しである
。FIG. 1 is a configuration diagram showing an embodiment of a blood pressure monitor according to the present invention. In the illustration, sensors (4) (including microphones, pressure transducers, optical sensors, etc.) are drawn out from the cuff (1) via a hollow tube (6).
ポンプ(2)は該カフに流体を供給し加圧する。センサ
の出力は、カフ内圧成分についてはDC増幅器(5)で
増幅し、カフ内勤脈波成分はAC増幅器(7)で増幅す
る。AC増幅器の出力はそのまま、またDC増幅器の出
力はA/Dコンバータ(6)を介し演算処理回路(8)
(実施例ではマイクロコンピュータを使用)に送られる
。また、図示実施例では、マイクロコンピュータの周辺
に、タイマ(10)、メモリ(9)を設けである。これ
らの機能、作用については後述する。A pump (2) supplies fluid to and pressurizes the cuff. In the output of the sensor, the cuff internal pressure component is amplified by a DC amplifier (5), and the cuff internal pulse wave component is amplified by an AC amplifier (7). The output of the AC amplifier is sent as is, and the output of the DC amplifier is sent to the arithmetic processing circuit (8) via the A/D converter (6).
(a microcomputer is used in the embodiment). In the illustrated embodiment, a timer (10) and a memory (9) are provided around the microcomputer. These functions and actions will be described later.
なお、図示実施例では、カフを巻装する個所を、従来の
聴診法のごとく上腕部に限定されることのないよう(例
えば指にカフを巻装することのできるよう)、センサを
中空管(3)でカフの外部に引き出し、該中空管、カフ
および該カフとポンプとを結ぶ中空管(12)に、血液
と同じ比重の液体で満たし、センサを心臓と同じ高さに
取シ付けることのできるように構成しである。ただし、
本発明ではセンサをカフに内臓し、従来と同じく該カフ
を上腕部に巻装して測定するものであっても何ら支障は
ない。In the illustrated embodiment, the sensor is made hollow so that the cuff is not limited to the upper arm as in conventional auscultation methods (for example, the cuff can be wrapped around a finger). The tube (3) is pulled out of the cuff, and the hollow tube, the cuff, and the hollow tube (12) connecting the cuff and the pump are filled with liquid having the same specific gravity as blood, and the sensor is placed at the same height as the heart. It is configured so that it can be installed. however,
In the present invention, there is no problem even if the sensor is built into the cuff and the measurement is carried out by wrapping the cuff around the upper arm as in the conventional case.
いまポンプで流体をカフに供給し加圧すると、カフ内の
圧力は増大し、カフ内圧は矛2図(イ)のごとく順次増
大する。なお、とのカフ内圧波形は正確には矛2図(ロ
)のカフ内勤脈波形が重じょうしだものであるが、簡単
のため図示の如く直線で示しである。Now, when fluid is supplied and pressurized to the cuff with a pump, the pressure inside the cuff increases, and the internal pressure of the cuff gradually increases as shown in Figure 2 (a). Although the cuff internal pressure waveform shown in Figure 2 (b) is more accurately the cuff internal pressure waveform, it is shown as a straight line for simplicity.
次に、カフ内勤脈波形は順次増大し、あるピーク値(こ
のときのカフ内圧が平均血圧(BP )を境に漸次減少
する。次いで、この力a■
フ内勤脈波形の差分をとると牙2図(ハ)のごとくなる
。図中圧のピーク値が最高血圧(BP )に対応し
、負のピーク値が最低血圧ax
(BPmin )に対応する。Next, the cuff pulse waveform increases sequentially, and the cuff pressure at this time gradually decreases after reaching a certain peak value (the mean blood pressure (BP)). The result is as shown in Fig. 2 (c). In the figure, the peak value of the pressure corresponds to the systolic blood pressure (BP), and the negative peak value corresponds to the diastolic blood pressure ax (BPmin).
マイクロコンピュータは動脈波が正しく検出されている
かを認識し、波形エネルギの差分計算を行ない、差のピ
ーク2点を血圧値と認識し、そのピーク点の圧力値をメ
モリ(9)することとし、その他のコントロールを制御
するプログラムを備えている。なお、タイマ(10)は
測定のインターバルを設定するためのものである。The microcomputer recognizes whether the arterial wave is correctly detected, calculates the difference in waveform energy, recognizes the two peak points of the difference as the blood pressure value, and stores the pressure value at the peak point in memory (9). It has a program that controls other controls. Note that the timer (10) is for setting the measurement interval.
動脈波の差分のピークを測定することにより最高血圧の
測定が可能であるのは次の理由に依る。The reason why systolic blood pressure can be measured by measuring the peak of the difference in arterial waves is as follows.
牙3図(イ)は、ポンプ(2)でカフ(1)内の血管(
11)を押しつぶした状態を示すもので、血流(三角波
)は管壁(図中斜線を施しである部分)に衝突し、その
衝撃波がカフ内の流体および中空管(3)を介しセンサ
(4)に伝達する。Diagram 3 (a) shows that the pump (2) is used to pump the blood vessels (1) inside the cuff (1).
11), the blood flow (triangular wave) collides with the tube wall (the shaded area in the figure), and the shock wave passes through the fluid in the cuff and the hollow tube (3) to the sensor. (4).
牙6図(ロ)は、ポンプの加圧を停止し、印加圧力の減
少に伴ない、押しつぶされた血管がだんだん膨らんで血
流が流れ出したときの状態を示すもので、このときはカ
フ内圧と血管内の圧力が等しい。血管は図示斜線で示す
部分、すなわちカフ内全体で振動するから、オ・6図(
イ)における衝撃波とは明瞭に区別することのできる圧
脈波が発生する。牙2図(ロ)の上点がこれに対応し、
矛2図(ハ)では差分の正のピーク値に該当する。Figure 6 (b) shows the state when the pump pressurization is stopped and as the applied pressure decreases, the crushed blood vessel gradually expands and blood begins to flow.At this time, the cuff internal pressure and the pressure inside the blood vessels are equal. The blood vessel vibrates in the shaded area, that is, the entire inside of the cuff.
A pressure pulse wave is generated that can be clearly distinguished from the shock wave in (a). The upper point of Fang 2 (b) corresponds to this,
In Figure 2 (c), this corresponds to the positive peak value of the difference.
矛4図に、本発明装置による最高血圧(SEP)の実測
値を従来の間接法(RIvA−ROCICI法)と比較
して示す。標本数は30゜単位はmm Hgである。図
から両者の実測値がよく一致するのがわかる。Figure 4 shows the actual measured value of systolic blood pressure (SEP) by the device of the present invention in comparison with the conventional indirect method (RIvA-ROCICI method). The number of samples is 30° in mm Hg. It can be seen from the figure that the actual measured values of the two coincide well.
差分のピーク値が最低血圧値に対応する根拠は実測に依
るものである。j/−5図に本発明装置による最低血圧
(DBP)の実測値を従来の間接法(RIVA−ROO
OI法)と比較して示す。標本数は30、単位はmmH
gである。図かられかるように、本願装置による最低血
圧の測定値は従来法による数値とよく一致している。The reason why the peak value of the difference corresponds to the diastolic blood pressure value is based on actual measurements. Figure j/-5 shows the actual measured value of diastolic blood pressure (DBP) by the device of the present invention compared to the conventional indirect method (RIVA-ROO).
A comparison with the OI method) is shown below. Number of samples is 30, unit is mmH
It is g. As can be seen from the figure, the measured values of diastolic blood pressure by the device of the present invention are in good agreement with the values obtained by the conventional method.
以上、本発明に係る血圧測定装置につき、その構成およ
び測定原理につき詳説したが、その構成から次のような
特有の効果が奏する。The configuration and measurement principles of the blood pressure measuring device according to the present invention have been described in detail above, and the configuration provides the following unique effects.
すなわち、従来のコロトコフ音を検出して血圧を測定す
る場合と違って、本発明はセンサで容易に検出できるカ
フ内圧と動脈波とを観測すればよいから、測定条件は緩
和され、従って測定は容易で、且つ雑音に影響されるこ
とは少ないから測定精度が高い。That is, unlike the conventional method of measuring blood pressure by detecting Korotkoff sounds, the present invention only requires observing the intracuff pressure and arterial wave, which can be easily detected with a sensor, so the measurement conditions are relaxed, and therefore the measurement is easy. It is easy to use and is less affected by noise, so the measurement accuracy is high.
しかも、コンピュータを利用してデータ処理を行なって
いるから、長時間にわたる血圧の測定、監視が可能とな
る。例えば、睡眠中に、タイマとポンプの制御に依り断
続的な血圧測定が可能となる等、従来のものに比しその
用途の拡大は著るしい。Moreover, since data processing is performed using a computer, blood pressure can be measured and monitored over a long period of time. For example, it has become possible to measure blood pressure intermittently during sleep by controlling a timer and pump, and its uses have expanded significantly compared to conventional ones.
図面は本発明の一実施例を示すもので、矛1図は測定回
路の構成図、矛2図は観測された血圧波形のモデル化し
た説明図、矛3図は本発明に依る血圧測定の原理を説明
する図、矛4図および牙5図は本発明装置と従来法との
測定値を比較したグラフである。
〔主要部分の符号の説明〕
カ 7 −−−−−−−−−−−−−−−
−−−−一−−−−−−−−−−−−−−−iポンプ
−−−−−−−−−−−−−−−−−一−−−−−−−
−−−−−−−−−2中空管 −一−−−−−−−−−
−−−−−−−−−−−−−−−−−−−m−−−3セ
ンサ −−−−−−−−−−−−−−−−−−−−−−
−−−−−−−m−−−−−4DC増幅器 −−−−−
−−−−−−−−−一−−−−−−−−−−−−−−−
−−−= 5A/Dコンバータ −−−−−−−−−
−−−−−−−−−−−−−−−−−−−−−6AC増
幅器 ・−−−−−−−−一一−−−−−−−−−−
−−−−−一一一−−−・7演算処理回路 −−−−−
−−−−−−一−−−−−−−−−−−−−−−−−−
−= 8O
帛4図
AP
R1νA−ROCCIThe drawings show one embodiment of the present invention. Figure 1 is a configuration diagram of a measurement circuit, Figure 2 is an explanatory diagram of an observed blood pressure waveform modeled, and Figure 3 is an illustration of blood pressure measurement according to the present invention. Figures explaining the principle, Figure 4 and Figure 5, are graphs comparing the measured values of the device of the present invention and the conventional method. [Explanation of symbols of main parts] F 7 −−−−−−−−−−−−−−−
−−−−−−−−−−−−−−−−−−−i pump
−−−−−−−−−−−−−−−−−−−−−−−−−−
−−−−−−−−−2 Hollow tube −1−−−−−−−−−
−−−−−−−−−−−−−−−−−−−m−−−3 sensor −−−−−−−−−−−−−−−−−−−
----------m----4DC amplifier -------
−−−−−−−−−−−−−−−−−−−−−−−−−
---= 5A/D converter ---------
−−−−−−−−−−−−−−−−−−−−6 AC amplifier
−−−−−111−−−・7 Arithmetic processing circuit −−−−−
−−−−−−−−−−−−−−−−−−−−−−−−−
-= 8O Figure 4 AP R1νA-ROCCI
Claims (1)
ンプ(2)と、該カフに若しくは該カフに連通ずる中空
管(3)に設けたセンサ(4)と、該センサの出力信号
のうちカフ内圧成分を増幅するDC増幅器(5)と、カ
フ内勤脈波成分を増幅するAC増幅器(7)と、該DC
増幅器に連設するA/Dコンバータ(6)と、該コンバ
ータの出力と前記AC増幅器(7)の出力とを人力デー
タとし動脈波の差分を算出しその正および負のピーク値
を検出しかつ該ピーク値に対応するカフ内圧を検出する
演算処理回路(8)とから成る、非観血式血圧測定装置
。1. A cuff (1), a pump (2) that supplies and pressurizes fluid to the cuff, a sensor (4) installed in the cuff or in a hollow tube (3) communicating with the cuff, and a sensor (4) for the sensor. A DC amplifier (5) that amplifies the cuff internal pressure component of the output signal, an AC amplifier (7) that amplifies the cuff internal pulse wave component, and the DC
An A/D converter (6) connected to the amplifier, the output of the converter and the output of the AC amplifier (7) are used as manual data to calculate the difference in arterial waves, and detect the positive and negative peak values thereof. A non-invasive blood pressure measuring device comprising an arithmetic processing circuit (8) that detects the cuff internal pressure corresponding to the peak value.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP57030502A JPS58149731A (en) | 1982-03-01 | 1982-03-01 | Non-observing type hemomanometer apparatus |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP57030502A JPS58149731A (en) | 1982-03-01 | 1982-03-01 | Non-observing type hemomanometer apparatus |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS58149731A true JPS58149731A (en) | 1983-09-06 |
JPS6216096B2 JPS6216096B2 (en) | 1987-04-10 |
Family
ID=12305588
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP57030502A Granted JPS58149731A (en) | 1982-03-01 | 1982-03-01 | Non-observing type hemomanometer apparatus |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS58149731A (en) |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS6238138A (en) * | 1985-08-12 | 1987-02-19 | オムロン株式会社 | Electronic hemomanometer |
JPS6297531A (en) * | 1985-10-24 | 1987-05-07 | オムロン株式会社 | Electronic hemomanometer |
JPS63246137A (en) * | 1988-01-26 | 1988-10-13 | 松下電工株式会社 | Electronic hemomanometer |
JPH01232933A (en) * | 1988-03-15 | 1989-09-18 | Omron Tateisi Electron Co | Electronic hemomanometer |
US5140991A (en) * | 1989-08-22 | 1992-08-25 | Colin Electronics, Co., Ltd. | Heartbeat synchronous pulse wave detecting apparatus |
Families Citing this family (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
TWI245064B (en) | 1998-12-28 | 2005-12-11 | Idemitsu Kosan Co | Organic electroluminescence device |
-
1982
- 1982-03-01 JP JP57030502A patent/JPS58149731A/en active Granted
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS6238138A (en) * | 1985-08-12 | 1987-02-19 | オムロン株式会社 | Electronic hemomanometer |
JPS6297531A (en) * | 1985-10-24 | 1987-05-07 | オムロン株式会社 | Electronic hemomanometer |
JPH06113B2 (en) * | 1985-10-24 | 1994-01-05 | オムロン株式会社 | Electronic blood pressure monitor |
JPS63246137A (en) * | 1988-01-26 | 1988-10-13 | 松下電工株式会社 | Electronic hemomanometer |
JPH0431255B2 (en) * | 1988-01-26 | 1992-05-26 | ||
JPH01232933A (en) * | 1988-03-15 | 1989-09-18 | Omron Tateisi Electron Co | Electronic hemomanometer |
US5140991A (en) * | 1989-08-22 | 1992-08-25 | Colin Electronics, Co., Ltd. | Heartbeat synchronous pulse wave detecting apparatus |
Also Published As
Publication number | Publication date |
---|---|
JPS6216096B2 (en) | 1987-04-10 |
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