JPS5975036A - Blood pressure measuring apparatus - Google Patents
Blood pressure measuring apparatusInfo
- Publication number
- JPS5975036A JPS5975036A JP57186384A JP18638482A JPS5975036A JP S5975036 A JPS5975036 A JP S5975036A JP 57186384 A JP57186384 A JP 57186384A JP 18638482 A JP18638482 A JP 18638482A JP S5975036 A JPS5975036 A JP S5975036A
- Authority
- JP
- Japan
- Prior art keywords
- pressure
- signal
- cuff
- blood
- blood pressure
- 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
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- 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】 本発明は、被験者への侵襲を軽減し、外部雑音。[Detailed description of the invention] The present invention reduces invasiveness to the subject and eliminates external noise.
足状雑音に対する問題を生体の応答性を考慮しながら解
決した血圧測定装置に関するものでおる。This invention relates to a blood pressure measuring device that solves the problem of foot noise while taking into consideration the responsiveness of the living body.
従来の超音波血圧測定装置は、上腕部にカフを巻き、カ
フ圧を血圧よシ十分高い位置に設定し、徐々に圧力を下
げドツプラ信号が発生したときの刀目圧外力を最高血圧
(収縮期血圧)とし、更に圧力を下げ信号が消滅したと
きの加圧外力を最低血圧(仏張期皿圧)として測定を行
なう。このように、減圧速屁が遅く加圧時間が長いため
加圧による圧迫感や腕がだるい、手の先がピリビリしび
れるなどの侵襲を伴う。特に楽中監視施設(工Cσ)。With conventional ultrasonic blood pressure measuring devices, a cuff is wrapped around the upper arm, the cuff pressure is set at a position sufficiently higher than the blood pressure, and the pressure is gradually lowered to calculate the external pressure force when the Dotsuplar signal is generated as the systolic blood pressure (systolic blood pressure). The pressure is further lowered and the external pressurizing force when the signal disappears is taken as the diastolic blood pressure (Bresch diastolic pressure) and measured. In this way, the decompression rate is slow and the pressure is applied over a long period of time, resulting in invasive symptoms such as a feeling of pressure, fatigue in the arms, and tingling in the tips of the hands. Especially the Rakuchu Monitoring Facility (Eng Cσ).
心疾息患者・監視装置(cctr) などの自rJd
J監視システムでは、数回に渡って測定を行なうため、
患者に大きな負担をかける二またこの装置では、測定時
間が長いため、外部雑音が血圧計測用変換器に混入する
確率が高くイ血f壁の運動以外から生じる足状雑音も大
きく、雑音と信号の周波数特性が同じでめるため識別が
困癲である。これは、最高最低血圧付近で多く見られ特
に最低血圧付近では大きな問題となる。Cardiac disease patients/monitoring equipment (CCTR), etc.
In the J monitoring system, measurements are taken several times, so
With this bifurcated device, which places a heavy burden on the patient, the measurement time is long, so there is a high probability that external noise will enter the blood pressure measurement transducer, and there is also a large foot-like noise caused by things other than the movement of the blood pressure wall. It is difficult to identify them because their frequency characteristics are the same. This is often seen near the systolic and diastolic blood pressures, and is especially a big problem near the diastolic blood pressure.
本発明は上記の点を考慮してなされたもので、被験者へ
の侵襲t@減し、雑音に強く信頼度の高い血圧測定を行
える装置を提供することを目的としたものである。The present invention has been made in consideration of the above points, and an object of the present invention is to provide an apparatus that can reduce the invasiveness to a subject, is resistant to noise, and can measure blood pressure with high reliability.
まずカフ圧を急速に変化させて侵襲の@$、を行ない外
部雑音の混入を防ぎ信号を検出しやすくすることを目的
とする最高血圧を測定する装置について述べる。First, we will describe a device for measuring systolic blood pressure that aims to rapidly change cuff pressure to perform invasive procedures to prevent external noise from entering and to make it easier to detect signals.
第1図は、圧力脈波、血圧、カフ圧、およびドツプラ信
号の関係を示したものである。任意の時刻に急速に初期
圧P・まで加圧し所定の時間待機した後ドツプラ信号の
有無の検出を行ない初期圧の増減により信号が無いこと
を確認した上で圧力脈波の立上9部分子、を基準に急速
に指数関数的に減圧させ信号を検出する。そしてこの時
のカフ圧を血圧とする。この結果を基にしながら減圧幅
を小さくし逐次近似的に繰り返すことで生体の応答性に
よる誤差を含まずに測定が可能となる。FIG. 1 shows the relationship among pressure pulse waves, blood pressure, cuff pressure, and Doppler signals. Rapidly pressurize to the initial pressure P at any time, wait for a predetermined time, then detect the presence or absence of a Doppler signal.After confirming that there is no signal due to an increase or decrease in the initial pressure, the rising 9-part molecule of the pressure pulse wave is detected. , the pressure is rapidly reduced exponentially based on , and a signal is detected. The cuff pressure at this time is defined as blood pressure. Based on this result, by reducing the width of the pressure reduction and repeating it in successive approximations, it becomes possible to measure without including errors due to the responsiveness of the living body.
第2図は、最高血圧測定装置のブロック図である。この
第2図において8はカン、9は圧力脈波計測用変換器1
0はドツプラ信号計測用変換器で、それぞれ上腕部11
の第2図示の位置に装着しである。そして1はドツプラ
信号検出装置、2はバンドパスフィルタ、3は圧力脈波
検出装置、4は圧力脈波波形整形回路、5は加圧減圧波
形形成回路、6はカフ圧計測用変換器である。12はド
ツプラ信号の出力端子、13はカフ圧計測用変換器6の
出力端子である。FIG. 2 is a block diagram of the systolic blood pressure measuring device. In this figure 2, 8 is a ring, and 9 is a pressure pulse wave measurement converter 1.
0 is a converter for measuring Doppler signals, and the upper arm 11
It is installed in the position shown in the second figure. 1 is a Doppler signal detection device, 2 is a bandpass filter, 3 is a pressure pulse wave detection device, 4 is a pressure pulse wave waveform shaping circuit, 5 is a pressurization/decompression waveform forming circuit, and 6 is a converter for cuff pressure measurement. . 12 is a Doppler signal output terminal, and 13 is an output terminal of the cuff pressure measuring converter 6.
かかる構成とすれば、カフ8の振動は、1心拍の任意の
時刻にポンプを用いて急速に加圧減圧波形形成回路5で
設定された血圧よシ十分高い位置まで加圧を行ない所定
の時間(10msec〜100111 BθC)待機さ
せ、端子12からの出力であるドツプラ信号の有無を判
定し、信号を検出した時は加圧(プラス5mHg)′に
行ない最終的に信号が検出されなくなるまで行ない変換
器9の出力を圧力脈波検出装置3.圧力脈波波形整形回
路4によシトリガ信号に変侠した後、この信号を基準に
時定#0.18θCで指数関数的に減圧させて行な、う
。この時、変換器10よ少入力されるドツプラ信号は、
ドツプラ信号検出装置1を通)バンドバスフィルり2で
一定周波数成分を取シ出し端子12よシ検出する。そし
て、その信号と対人6する時刻の端子13の出力1−擬
似血圧として1回目の測定が終る。次にこの結果を基に
2@目、2回目の結果を基に3回目の初期圧をそれぞれ
矢定し1回目と同じ方法で行なう。With such a configuration, the vibration of the cuff 8 is caused by rapidly pressurizing the cuff 8 using a pump at an arbitrary time of one heartbeat to a position sufficiently higher than the blood pressure set by the pressurization/decompression waveform forming circuit 5 for a predetermined period of time. (10 msec to 100111 BθC), and determines the presence or absence of the Doppler signal output from terminal 12. When a signal is detected, pressurize (plus 5 mHg)' until finally no signal is detected, and then convert. The output of the device 9 is detected by the pressure pulse wave detection device 3. After converting it into a trigger signal by the pressure pulse waveform shaping circuit 4, the pressure is reduced exponentially with a time setting of #0.18θC using this signal as a reference. At this time, the Doppler signal input to the converter 10 is
A certain frequency component is extracted by a bandpass filter 2 through a Doppler signal detection device 1 and detected at a terminal 12. Then, the first measurement is completed as the output 1 of the terminal 13 at the time when the signal corresponds to the person 6 - pseudo blood pressure. Next, based on this result, set the initial pressure for the second time, and set the initial pressure for the third time based on the result of the second time, and perform the same procedure as the first time.
2回目の初期圧P1は、擬似血圧にプラスlOs+ H
g s3回目P、はプラス5 rrs Hg とする
。このように3回減圧幅小さくしていきながら逐次近似
的に行ない3回目の結果を血圧として表示し測定が可能
となる。The second initial pressure P1 is the pseudo blood pressure plus lOs+H
g s3rd P, plus 5 rrs Hg. In this way, the pressure reduction width is reduced three times in a successive approximation manner, and the third result is displayed as blood pressure, allowing measurement.
次に、カフ圧を急速に変化させv襲の軽減を行ない外部
雑音の混入を防ぎ信号を検出しやすくすることを目的と
する最低血圧を測定する装置について述べる。Next, a device for measuring diastolic blood pressure will be described, which aims to rapidly change cuff pressure to reduce v-strokes, prevent external noise from entering, and facilitate signal detection.
第3図は、圧力脈波、血圧、カフ圧、およびドツプラ信
号の関係を示したものである。任意の時刻に急速に初期
圧P、まで加圧し所定の時間待機した後トップ2信号の
有無の検出を行ない初期圧の増減により信号があること
を確認した上で圧力脈波の立上シ部分子・を基準にTI
だけ遅延させ急速に指数間ぺ的に減圧させ信号を検出す
る。そしてこの時のカフ圧を血圧とする。この結果を基
にしながら減圧幅を小さくし逐次近似的に繰夛返すこと
で生体の応答性による誤差を含まずに測定が可能となる
。FIG. 3 shows the relationship between pressure pulse wave, blood pressure, cuff pressure, and Doppler signal. At an arbitrary time, the pressure is rapidly increased to the initial pressure P, and after waiting for a predetermined time, the presence or absence of the top 2 signal is detected.After confirming that there is a signal by increasing or decreasing the initial pressure, the rising part of the pressure pulse wave is detected. TI based on child
The signal is detected by rapidly decompressing the signal with an exponential delay. The cuff pressure at this time is defined as blood pressure. Based on this result, by reducing the width of the pressure reduction and repeating it in successive approximations, it becomes possible to measure without including errors due to the responsiveness of the living body.
第4図は、最低血圧測定装置のブロック図である。この
vJ4図において8はカフ、9は圧力脈波計測用変換器
JOはドッグ2信号計測用変換器で、それぞれ上腕部1
1の第4図示の位置に装置しである。そして1はドツプ
ラ信号検出装置、2はバンドパスフィルタ、3は圧力脈
波検出装置、4は圧力脈波波形整形回路、7は遅延回路
、5は加圧波形形成回路、6はカフ圧計測用変換器でお
る。12はドツプラ信号の出力端子、13はカフ圧計測
用変換器6の出力端子でめる。FIG. 4 is a block diagram of the diastolic blood pressure measuring device. In this vJ4 diagram, 8 is a cuff, 9 is a pressure pulse wave measurement transducer, and JO is a dog 2 signal measurement transducer.
1, the device is placed in the position shown in the fourth figure. 1 is a Doppler signal detection device, 2 is a bandpass filter, 3 is a pressure pulse wave detection device, 4 is a pressure pulse wave waveform shaping circuit, 7 is a delay circuit, 5 is a pressurization waveform forming circuit, and 6 is for cuff pressure measurement. Use a converter. 12 is an output terminal of the Doppler signal, and 13 is an output terminal of the cuff pressure measuring converter 6.
かかる構成とすれば、カフの振動は、1心拍の任意の時
刻にポンプをm−て急速に加圧減圧波形形成回路5で設
定された最低血圧よシ十分高い位置まで加圧を行ない所
定の時間(lQmsec〜100m5ec)待機させ、
端子12からの出力で委るトップ2信号の有無を判定し
、信号を検出出来ない時は゛加圧(プラス5關Hg)を
行ない最終的に信号が検出されるまで行ない変換器9の
出力を圧力脈波検出装置3、圧力脈波波形整形回路4に
よシトリガ信号に変換した後遅延回路7によJ T!(
500m1llθC〜8QQm8eO)だけ遅延し時定
70.1secで指数関数的に減圧させ行う。この時、
変換器1()よシ入力されるトップ2信号は、トップ2
信号検出装置lを通勺バンドパスフィルタ2で一定周波
数成分を取シ出し端子12よシ検出する。そして、その
信号と対応する時刻の端子13の出力を擬似血圧として
1回目の測定が終る。次にこの結果を基に2回目。With such a configuration, the vibration of the cuff can be controlled by rapidly increasing the pressure to a position sufficiently higher than the diastolic blood pressure set by the pressurization/decompression waveform forming circuit 5 by turning on the pump at an arbitrary time of one heartbeat. Wait for a time (lQmsec~100m5ec),
The presence or absence of the top 2 signal is determined by the output from the terminal 12, and if no signal is detected, pressurization (plus 5 degrees Hg) is applied until the signal is finally detected, and the output of the converter 9 is After the pressure pulse wave detection device 3 and the pressure pulse wave waveform shaping circuit 4 convert it into a trigger signal, the delay circuit 7 outputs the JT! (
The pressure is reduced exponentially with a delay of 500ml1llθC~8QQm8eO) and a time period of 70.1 seconds. At this time,
The top 2 signal input from converter 1() is
A signal detection device 1 passes through a bandpass filter 2 to pick up a constant frequency component and detects it at a terminal 12. Then, the first measurement is completed using the output of the terminal 13 at the time corresponding to the signal as a pseudo blood pressure. Next, based on this result, the second time.
2回目の結果を基に3回目の初期圧をそれぞれ決定し1
回目と同じ方法で行なう。21!−11目のW期圧PR
は、擬似血圧にプラス10tmHgs 3回目P、はプ
ラス5 m Hgとする。このように3回減圧幅を小さ
くしていきながら逐次近似的に行ない3回目の結果を血
圧として表示し血圧測定が可能となる。Determine the initial pressure for the third time based on the results of the second time.1
Do it the same way as the first time. 21! -11th W phase pressure PR
is 10 tmHgs plus the simulated blood pressure.The third P is plus 5 mHg. In this way, it is possible to perform blood pressure measurement by successively approximating the pressure reduction while decreasing the width of the pressure reduction three times and displaying the third result as blood pressure.
この装置は10〜15secという短かい時間にカフ圧
の初期値と最高又は最低血圧との減圧幅を5mHgづつ
少なくして逐次近似的に3回線シ返し測定を行なうため
加圧時間が短くな多加圧による圧迫感。This device performs three-circuit repeat measurements in a short period of 10 to 15 seconds by decreasing the decompression range between the initial value of the cuff pressure and the systolic or diastolic blood pressure by 5 mHg increments. Feeling of pressure.
腕がだるい2手の先がビリビリしびれるなどの侵襲が軽
減され、生体が粘弾性体であるために生じるカフ正に対
する生体の応答性の問題も解決する。Invasive effects such as numbness at the tips of two hands due to sluggish arms are alleviated, and the problem of the responsiveness of the living body to cuff correction, which occurs because the living body is a viscoelastic body, is also resolved.
又カフ圧の減圧時間が200m8θCとなるためドツプ
ラ信号計測用変換器の動作時間が4(1G−a=83士
造−−′ −竺1宵男1柵吐用4臼九器力暑昨待剥亦l
oomsθCと短くな)外部雑音が混入する確率が従来
の方式に比ベレ と小さくなる。In addition, since the cuff pressure reduction time is 200m8θC, the operating time of the converter for measuring the Dotsupler signal is 4 (1G-a = 83 Shizo--' Stripping
The probability that external noise (as short as oomsθC) will be mixed in is much smaller than in the conventional method.
00
さらに定状雑音の問題もドツプラ信号の振幅が血V壁の
変位に比例し周波数特性も血管壁の運動速度に比例する
ためカフ圧の減圧時間が上記200m5ecと短く、信
号の振幅が最高最低血圧とも従来の方式の10倍とな多
周波数特性は、定状雑音が25Hzをピークに1OHz
〜1oOHz と短かい範囲に示されるのに対して
信号は250 Hzをピークに2.5Hz〜1KHzと
広い範囲となり、今まで周波数分析による識別が行なえ
なかったものが可能となpBN比が同上し解決する。00 Furthermore, regarding the problem of constant noise, the amplitude of the Doppler signal is proportional to the displacement of the blood V wall, and the frequency characteristic is also proportional to the movement speed of the blood vessel wall, so the cuff pressure reduction time is as short as 200 m5ec, and the signal amplitude is the highest and lowest. The multi-frequency characteristic, which has 10 times higher blood pressure than the conventional method, has a constant noise of 1 OHZ with a peak of 25 Hz.
While the signal is shown in a short range of ~1oOHz, the signal peaks at 250 Hz and has a wide range of 2.5Hz to 1KHz, making it possible to identify things that were previously impossible to identify by frequency analysis. solve.
以上のように、短時間にカフ圧の初期値と血圧との落差
幅を小さくして逐次近似的に繰シ返すととによp1侵襲
の軽減がなされ、ドツプラ信号計測用変換器の動作時間
が短くなシ、外部雑音が混入する確率が小さくなること
に加え生体が粘弾性体であるために生じる誤差もなくな
る。またドツプラ信号の振幅が、血tmの変位に比ft
1L、周波数が運動速度に比例するためカフ圧′t−急
速に変化されることによ逆信号の振111が大きく、周
波数特性が雑音の特性に比べ高くなシ、周波数分析を用
いて信号と雑音の識別を行なうことで8N比が向上され
る。よって本発明は、雑音に強く極めて侵襲の少ない血
圧測定が可能となる。As described above, if the difference width between the initial value of the cuff pressure and the blood pressure is reduced in a short time and the steps are repeated in successive approximations, the p1 invasion can be reduced, and the operating time of the Doppler signal measurement converter can be reduced. Since the distance is short, the probability of external noise being mixed in is reduced, and errors caused by the viscoelastic body of the living body are also eliminated. Also, the amplitude of the Doppler signal is proportional to the displacement of blood tm.
1L, since the frequency is proportional to the movement speed, the amplitude of the reverse signal 111 is large due to the rapid change in cuff pressure 't-, and the frequency characteristics are higher than the noise characteristics. The 8N ratio is improved by identifying noise. Therefore, the present invention enables blood pressure measurement that is resistant to noise and extremely minimally invasive.
第1図は圧力脈波、血圧、方圧及びドツプジ信?
号の関係を示した波形図、第2図は本発明装置の第1実
施例の構成を示すブロック線図、第3図は圧力、脈波、
血圧、カフ圧及びドツプラ信号の関係を示した波形図、
第4図は第2実施例の構成を示すブロック線図である。
1・・・・・・・・・ドツプラ信号検出装置、2・・・
・・・・・・バンドパスフィルタ、3・・・・・・・・
・圧力脈波検出its 4・・・・・・・・・圧力脈波
波形整形回路、5・・・・・・・・・加圧減圧波形形成
回路、6・・・・・・・・・カフ圧計測用変換器、7・
・・・・・・・・遅延回路、8・・・・・・・・・カン
、9・・・・・・・・・圧力脈波計測用変換器、10・
・・・・・・・・ドツプラ信号計測用変換器、11・・
・・・・・・・上腕部、12・・・・・・・・・ドツプ
ラ信号の出力端子、13・・・・・・・・・カフ圧計測
用変換器の出力端子。Figure 1 shows pressure pulse wave, blood pressure, square pressure, and doppjishin? 2 is a block diagram showing the configuration of the first embodiment of the device of the present invention, and FIG. 3 is a waveform diagram showing the relationship between pressure, pulse waves,
A waveform diagram showing the relationship between blood pressure, cuff pressure, and Doppler signal,
FIG. 4 is a block diagram showing the configuration of the second embodiment. 1...Dotsupura signal detection device, 2...
...Band pass filter, 3...
・Pressure pulse wave detection its 4...... Pressure pulse wave waveform shaping circuit, 5...... Pressure/decompression waveform forming circuit, 6...... Cuff pressure measurement converter, 7.
......Delay circuit, 8...Kan, 9......Pressure pulse wave measurement converter, 10.
......Dotsupura signal measurement converter, 11...
...... Upper arm, 12... Output terminal of Doppler signal, 13... Output terminal of cuff pressure measurement converter.
Claims (1)
付けられ、心拍による血圧の変化を脈波として検出した
信号と一定時間の時間差かめる信号を検出する変換器と
、血管壁の運動に基づいて生じる血・aの下流側の信号
を検出する下流側の変換器と、1心拍の任意の時刻に、
カフへ急速に給気し加圧を行ない所定の時間待機した後
急速に減圧させる手段、上記カフの初期圧を増減させ心
拍による血圧の変化を脈波として検出した信号と一定時
間の時間差がある信号を基準にカフ圧を急速に変化させ
て行ったときに、下流側の変換器よシ得られる下流側の
信号を血圧信号として、その時刻に対応する圧力を血圧
として測定を行ない、この操作t−繰り返すごとに減圧
幅を小さくして逐次近似的に行なう手段とからなる血圧
を測定する血圧測定装置。 (2)上腕部に加圧のためのカフと、このカフに取り付
けられ、心拍炬よる血圧の変化を脈波として検出した信
号と一定時間の時間差がある信号を検出する変換器と、
血管壁の運動に基づいて生じる血管の下流側の信号を検
出する下流側′の変換器と、1心拍の任意の時刻に、カ
フへ急速に給気し加圧を行ない所定の時間待機した後急
速に減圧させる手段、上記カフの初期圧を増減させ心拍
による血圧の変化を脈波として検出した信号と一定時間
の時間渣がおる信号を基、準にカフ圧を急速に変化させ
て行ったときに、下流側の変換器よシ得られる下流側の
信号を血圧信号として、その時刻に対応する圧力を血圧
として測定を行ない、この操作を繰シ返すごとに減圧幅
を小さくして逐次近似的にイフなり手段と一定周波数の
血f壁の運動に基づいて生じる血管の下流側の信号を検
出する下流側の変換器よシ得られる下流側の信号を検出
するフィルタとからなる血圧測定装置。[Claims] (Li) A cuff for measuring pressure a on the upper arm, and a converter attached to this cuff that detects a signal that detects changes in blood pressure due to heartbeat as a pulse wave and a signal that detects a certain time difference. , a downstream transducer that detects the downstream signal of blood a generated based on the movement of the blood vessel wall, and at any time of one heartbeat,
A means of rapidly supplying air to the cuff, pressurizing it, waiting for a predetermined period of time, and then rapidly depressurizing the cuff.The initial pressure of the cuff is increased or decreased, and there is a certain time difference between the signal and the signal that detects the change in blood pressure caused by the heartbeat as a pulse wave. When the cuff pressure is rapidly changed based on the signal, the downstream signal obtained from the downstream converter is used as the blood pressure signal, and the pressure corresponding to that time is measured as the blood pressure. t-A blood pressure measuring device for measuring blood pressure comprising means for successively approximating the pressure reduction width by decreasing the pressure reduction width each time it is repeated. (2) a cuff for pressurizing the upper arm; a converter attached to the cuff that detects a signal that detects changes in blood pressure due to heartbeat as a pulse wave and a signal that has a certain time difference;
A transducer on the downstream side that detects signals on the downstream side of the blood vessel generated based on the movement of the blood vessel wall, and a transducer on the downstream side that detects signals on the downstream side of the blood vessel generated based on the movement of the blood vessel wall. The method of rapidly reducing the pressure was performed by increasing and decreasing the initial pressure of the cuff, and rapidly changing the cuff pressure based on a signal that detected changes in blood pressure due to heartbeat as a pulse wave and a signal that remained for a certain period of time. Sometimes, the downstream signal obtained from the downstream converter is used as the blood pressure signal, and the pressure corresponding to that time is measured as the blood pressure, and each time this operation is repeated, the width of the pressure reduction is decreased to make successive approximations. A blood pressure measuring device comprising a downstream transducer for detecting a signal on the downstream side of the blood vessel generated based on the movement of the blood wall at a constant frequency, and a filter for detecting the downstream signal obtained by the blood vessel. .
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP57186384A JPS5975036A (en) | 1982-10-22 | 1982-10-22 | Blood pressure measuring apparatus |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP57186384A JPS5975036A (en) | 1982-10-22 | 1982-10-22 | Blood pressure measuring apparatus |
Publications (1)
Publication Number | Publication Date |
---|---|
JPS5975036A true JPS5975036A (en) | 1984-04-27 |
Family
ID=16187442
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP57186384A Pending JPS5975036A (en) | 1982-10-22 | 1982-10-22 | Blood pressure measuring apparatus |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS5975036A (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2013517047A (en) * | 2010-01-12 | 2013-05-16 | ヘモディナミクス エセア デ セウベ | Arterial pressure measurement system and method for measuring arterial pressure under the influence of arterial pressure |
-
1982
- 1982-10-22 JP JP57186384A patent/JPS5975036A/en active Pending
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2013517047A (en) * | 2010-01-12 | 2013-05-16 | ヘモディナミクス エセア デ セウベ | Arterial pressure measurement system and method for measuring arterial pressure under the influence of arterial pressure |
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