JP2001095766A - Blood pressure measuring method - Google Patents
Blood pressure measuring methodInfo
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- JP2001095766A JP2001095766A JP27930499A JP27930499A JP2001095766A JP 2001095766 A JP2001095766 A JP 2001095766A JP 27930499 A JP27930499 A JP 27930499A JP 27930499 A JP27930499 A JP 27930499A JP 2001095766 A JP2001095766 A JP 2001095766A
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- blood pressure
- pat
- signal
- pulse wave
- sbp
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- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、血圧測定方法に係
り、特に、被測定者に無侵襲で連続的に血圧を計測する
血圧測定方法に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method for measuring blood pressure, and more particularly, to a method for measuring blood pressure continuously and noninvasively on a subject.
【０００２】[0002]
【従来の技術】従来より、血圧は、上腕の動脈が走って
いる場所に聴診器を置き、駆血帯に空気を送り込み聴診
器でコロトコフ音を聞くことにより測定を行っていた。
その他には、橈動脈等にカテーテルを挿し込むことによ
り、被測定者に対して侵襲的に血圧を計測していた。2. Description of the Related Art Conventionally, blood pressure has been measured by placing a stethoscope in a place where an artery of the upper arm is running, sending air into the tourniquet and listening to Korotkoff sounds with the stethoscope.
In addition, the blood pressure is measured invasively on the subject by inserting a catheter into the radial artery or the like.
【０００３】また、一般に、心拍毎の最高血圧である収
縮期血圧（systolic blood pressure,ＳＢＰ）と、心電
図のＲ波のピークから光電脈波の立ち上がり点までの時
間間隔である脈波伝播時間（pulse arrival time,ＰＡ
Ｔ）との間の関係は、理論的に動脈血管壁の粘弾性効果
として説明され、一定の関係があると考えられている。In general, systolic blood pressure (SBP), which is the maximum blood pressure for each heartbeat, and pulse wave transit time (SBP), which is the time interval from the peak of the R wave of the electrocardiogram to the rising point of the photoelectric pulse wave. pulse arrival time, PA
T) is theoretically described as the viscoelastic effect of the arterial vascular wall and is believed to have a certain relationship.
【０００４】[0004]
【発明が解決しようとする課題】しかしながら、上述の
ような従来のコロトコフ音による測定は、連続的な測定
ができず、また、カテーテルによる測定は、被測定者に
対して侵襲的となる。また、ＰＡＴの測定は非侵襲的で
あるが、ＳＢＰとＰＡＴとの関係には、多くの要因が関
連しているので、従来は、不明な点が山積していた。例
えば、人工呼吸装置が全身麻酔の手術の下で導入される
とき、ＳＢＰ及びＰＡＴの関係は変わってしまった。ま
た、実際の手術中に収集したＰＡＴ信号はＳ／Ｎが極め
て低く、且つ、電気メス等の影響が心電信号に入る場合
もあるため、ＰＡＴ信号とＳＰＢとの関係がはっきりし
ていない。However, the conventional measurement using the Korotkoff sound as described above cannot perform continuous measurement, and the measurement using a catheter is invasive to the subject. Further, although the measurement of PAT is non-invasive, there are many factors related to the relationship between SBP and PAT. For example, when a ventilator was introduced under general anesthesia surgery, the relationship between SBP and PAT changed. In addition, the PAT signal collected during the actual operation has an extremely low S / N ratio, and the influence of an electric scalpel or the like may be included in the electrocardiogram signal, so that the relationship between the PAT signal and SPB is not clear.
【０００５】本発明は、以上の点に鑑み、ＰＡＴの変化
が収縮期血圧の変化を反映することに注目し、非侵襲で
連続的に血圧を測定することを目的とする。また、本発
明は、ノイズに埋められているＰＡＴ信号に対して、適
当なディジタル処理を施し、有用な情報を抽出すること
で、正確な血圧の評価を行うことを目的とする。さら
に、本発明は、呼吸による影響を抑えて、ＳＢＰとＰＡ
Ｔとの相関関係を明確とした血圧測定方法を提供するこ
とを目的とする。In view of the above, it is an object of the present invention to measure continuously and non-invasively the blood pressure, noting that the change in PAT reflects the change in systolic blood pressure. Another object of the present invention is to perform accurate digital processing on a PAT signal embedded in noise to extract useful information, thereby performing accurate blood pressure evaluation. Further, the present invention suppresses the effects of respiration,
It is an object of the present invention to provide a blood pressure measurement method with a clear correlation with T.
【０００６】[0006]
【課題を解決するための手段】本発明の解決手段による
と、検出された脈波伝播時間信号からノイズを除去する
ことにより、修正脈波伝播時間信号を求める雑音除去処
理と、前記信号処理により求められた修正脈波伝播時間
信号の特定周波数成分を抽出し、抽出された特定周波数
成分と血圧校正値により求めた低周波数成分を合成する
ことにより、血圧を求める補正処理とを含む血圧測定方
法を提供する。According to the means of the present invention, noise is removed from a detected pulse wave transit time signal to thereby obtain a corrected pulse wave transit time signal. A blood pressure measurement method including: extracting a specific frequency component of the obtained corrected pulse wave transit time signal; and synthesizing the extracted specific frequency component and a low frequency component obtained by the blood pressure calibration value to obtain a blood pressure. I will provide a.
【０００７】[0007]
【発明の実施の形態】以下に、本発明の血圧測定方法に
ついて詳述する。図１に、本発明に係る血圧測定方法の
フローチャートを示す。まず、脈波伝播時間ＰＡＴを求
める（Ｓ１０）。図２に、脈波伝播時間ＰＡＴの説明図
を示す。図２中、上のグラフ(実線)は、ＥＣＧ（Electr
ocardiogram）とよばれる心電図信号を示す。下のグラ
フ(一点鎖線)は、ＰＰＧ（Photoplethysmogram）と呼ば
れる光電脈波信号を示す。測定では、心電図Ｒ波のピー
クを検出し、また、連続二つのＲ波ピークの間にある光
電脈波の立ち上がり点を検出する。心電図Ｒ波ピークか
ら光電脈波の立ち上がり点までの時間を求め、これを脈
波伝播時間ＰＡＴとする。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The blood pressure measuring method of the present invention will be described below in detail. FIG. 1 shows a flowchart of the blood pressure measurement method according to the present invention. First, the pulse wave propagation time PAT is determined (S10). FIG. 2 is an explanatory diagram of the pulse wave transit time PAT. In FIG. 2, the upper graph (solid line) shows the ECG (Electr
ocardiogram). The lower graph (dotted line) shows a photoplethysmographic signal called PPG (Photoplethysmogram). In the measurement, a peak of an electrocardiogram R wave is detected, and a rising point of a photoelectric pulse wave between two consecutive R wave peaks is detected. The time from the peak of the electrocardiogram R wave to the rising point of the photoelectric pulse wave is obtained, and this is defined as the pulse wave propagation time PAT.
【０００８】図３に、検出したＰＡＴ信号の説明図を示
す。上のグラフがＰＡＴ信号、下のグラフがＳＢＰ信号
をそれぞれ示す。このように、一般に、手術中等で長時
間にわたって収集したＰＡＴ信号は、Ｓ／Ｎが大変低
く、且つ、電気メス等の影響が心電信号に入る場合もあ
るため、検出したＰＡＴ信号は強いスパイク状ノイズに
埋もれてしまう。これでは、ＰＡＴとＳＢＰの関係を求
めることは極めて困難である。FIG. 3 is an explanatory diagram of the detected PAT signal. The upper graph shows the PAT signal, and the lower graph shows the SBP signal. As described above, in general, a PAT signal collected over a long period of time during an operation or the like has a very low S / N ratio, and the influence of an electric scalpel or the like sometimes enters the electrocardiogram signal. Is buried in the shape noise. In this case, it is extremely difficult to determine the relationship between PAT and SBP.
【０００９】そこで、つぎに、本発明では、ノイズに埋
められているＰＡＴ信号に対して、適当なディジタル処
理を施し、有用な情報を抽出して正確な評価をするため
に、ＰＡＴの雑音除去処理を実行する（Ｓ２０）。雑音
除去処理としては、例えば、スパイク状雑音除去、例外
値検出・除去と欠損値補間、呼吸成分除去等である。こ
れらのうち、全ての方法を用いてもよいし、必要に応じ
て適宜の方法を選択して用いて雑音除去を行ってもよ
い。Therefore, in the present invention, the PAT signal embedded in the noise is subjected to appropriate digital processing to extract useful information and accurately evaluate the PAT signal. The process is executed (S20). The noise removal processing includes, for example, spike noise removal, exceptional value detection / removal and missing value interpolation, respiratory component removal, and the like. Of these, all of the methods may be used, or an appropriate method may be selected and used to remove noise as needed.
【００１０】図４に、スパイク状雑音除去の説明図を示
す。画像のスパイク状ノイズ（Saltand Pepperノイズ)
を除去するために、例えばメディアンフィルタを使用す
る。これにより、孤立的なスパイク雑音を除去すること
ができる。なお、ＰＡＴとＳＢＰとの相関係数は、一例
として、−０．２５を示した。このようにして、幅の狭
いスパイクノイズが除去されたが、幅の広いスパイクは
まだ残っている。そこで、例外値検出・除去と欠損値補
間の処理を実行する。FIG. 4 is an explanatory diagram of spike noise removal. Image spike noise (Saltand Pepper noise)
For example, a median filter is used to remove the noise. As a result, isolated spike noise can be removed. The correlation coefficient between PAT and SBP is -0.25 as an example. In this way, narrow spike noise has been removed, but wide spikes still remain. Therefore, processing of exception value detection / removal and missing value interpolation is executed.
【００１１】図５に、例外値検出・除去と欠損値補間の
説明図を示す。この処理では、メディアンフィルタ等で
除去できない幅の広いスパイクノイズを微分フィルタで
検出して、その区間内のデータを削除する。さらに、ス
プライン関数等で該当区間前後のデータを用いて、削除
された欠損値を補間する。このような、非線形フィルタ
を使用することは、雑音除去に極めて有効である。この
処理により、有用信号に混入した雑音を有効に除去する
と同時に、細かな微妙の変化も再現できる。なお、ＰＡ
ＴとＳＢＰとの相関係数は、一例として、−０．８４を
示した。FIG. 5 is a diagram for explaining the detection and removal of outliers and the interpolation of missing values. In this process, a wide spike noise that cannot be removed by a median filter or the like is detected by a differential filter, and data in that section is deleted. Further, the missing value is interpolated by using data before and after the corresponding section using a spline function or the like. Use of such a nonlinear filter is extremely effective for noise removal. By this processing, noise mixed in the useful signal can be effectively removed, and at the same time, fine and subtle changes can be reproduced. In addition, PA
The correlation coefficient between T and SBP is, for example, -0.84.
【００１２】さらに、呼吸成分を除去する処理を実行す
る。図６に、呼吸成分除去についての説明図を示す。こ
の処理では、例えば、ウェーブレット(Wavelet)変換を
利用した、ウェーブレットフィルタを用いることができ
る。これにより、ＰＡＴ信号を平滑化することができ
る。なお、ＰＡＴとＳＢＰとの相関係数は、一例とし
て、−０．８７を示した。つぎに、雑音除去処理がほど
こされた修正ＰＡＴ信号について、さらにＳＢＰとの相
関を良くするように補正処理を実行する（Ｓ３０）。Further, a process for removing a respiratory component is executed. FIG. 6 is an explanatory diagram of respiratory component removal. In this processing, for example, a wavelet filter using a wavelet (Wavelet) transform can be used. Thereby, the PAT signal can be smoothed. The correlation coefficient between PAT and SBP is -0.87 as an example. Next, a correction process is performed on the modified PAT signal subjected to the noise removal process so as to further improve the correlation with the SBP (S30).
【００１３】図７に、補正処理の説明図を示す。また、
図８に、収縮期血圧推定プロセスの説明図を示す。ま
ず、修正ＰＡＴ信号（図８（ａ））の値を統一のサンプ
リング周波数（例えば、１Ｈｚ）にリスケールする。リ
スケールしたＰＡＴ（Rescaled Pulse Arrival Time,
ＲＰＡＴ）信号に基づき、バンドパスフィルタで帯域限
定成分ＢＬＣを生成する（図８（ｂ））。すなわち、リ
スケールした脈波伝播時間ＲＰＡＴが、バンドパスフィ
ルタ３１に入力される。収縮期血圧の推定精度はバンド
パスフィルタ３１のパラメータと校正間隔ＴＣに依存す
る。バンドパスフィルタ３１のパラメータの最適選択
は、例えば、ハイカットオフ周波数ＦＨ＝０．００４Ｈ
ｚ、ローカットオフ周波数ＦＬ＝０．０００５３Ｈｚで
あり、また、ＴＣ＝５minである。これらの値は、実際
応用時の目的、要求等により、適宜の値を用いることが
できる。バンドパスフィルタ３１から、帯域限定成分Ｂ
ＬＣが出力される。帯域限定成分ＢＬＣは、短時間内に
おける収縮期血圧の変化分を追跡する。FIG. 7 is an explanatory diagram of the correction process. Also,
FIG. 8 is an explanatory diagram of the systolic blood pressure estimation process. First, the value of the modified PAT signal (FIG. 8A) is rescaled to a uniform sampling frequency (for example, 1 Hz). Rescaled PAT (Rescaled Pulse Arrival Time,
Based on the (RPAT) signal, a band-pass filter generates a band-limited component BLC (FIG. 8B). That is, the rescaled pulse wave propagation time RPAT is input to the band-pass filter 31. Estimation accuracy of systolic blood pressure is dependent on the calibration interval T C as a parameter of the band pass filter 31. The optimal selection of the parameters of the bandpass filter 31 is, for example, the high cutoff frequency F H = 0.004H
z, a low cut-off frequency F L = 0.00053Hz, also a T C = 5min. As these values, appropriate values can be used depending on the purpose, requirements, and the like in actual application. From the band pass filter 31, the band limited component B
LC is output. The band-limited component BLC tracks a change in the systolic blood pressure in a short time.
【００１４】一方、例えば、線形補間方法等を用いた収
縮期血圧校正値より、低周波数成分ＬＦＣ（図８
（ｃ））を生成する。具体的には、まず、血圧校正値が
補間処理部３２に入力される。例えば、補間処理部３２
は、コロトコフ音を利用した間接的血圧測定等により所
定時間間隔で計測された収縮期血圧を用いて、測定間の
補間処理を行い連続した低周波成分を生成する。また
は、補間処理部３２は、脈波伝播信号又は修正脈波伝播
信号等を用いて、連続した低周波成分を生成するように
してもよい。なお、図８中、ＩＳＢＰ（Invasive Systo
lic blood pressure）信号は、侵襲的に測定したＳＢＰ
信号、即ち、観血式収縮期血圧を示す。補間処理部３２
は、このようにして、低周波数成分ＬＦＣを出力する。
低周波数成分ＬＦＣは、長時間の間に収縮期血圧ＳＢＰ
のトレンドを推定する。On the other hand, for example, a low frequency component LFC (FIG. 8) is obtained from a systolic blood pressure calibration value using a linear interpolation method or the like.
(C)) is generated. Specifically, first, the blood pressure calibration value is input to the interpolation processing unit 32. For example, the interpolation processing unit 32
Uses the systolic blood pressure measured at predetermined time intervals by indirect blood pressure measurement using the Korotkoff sound or the like, and performs interpolation processing between the measurements to generate a continuous low-frequency component. Alternatively, the interpolation processing unit 32 may generate a continuous low-frequency component using a pulse wave propagation signal, a corrected pulse wave propagation signal, or the like. In FIG. 8, ISBP (Invasive Systo
lic blood pressure) signal is SBP measured invasively
The signal is indicative of open systolic blood pressure. Interpolation processing unit 32
Outputs the low frequency component LFC in this manner.
The low-frequency component LFC is used to determine the systolic blood pressure SBP over a long period of time.
Estimate the trend of
【００１５】つぎに、ＢＬＣ成分とＬＦＣ成分を加算す
ることによって、収縮期血圧ＳＢＰを推定する。すなわ
ち、加算部３３は、脈波伝播時間の帯域限定成分ＢＬＣ
と、一定時間間隔で計測された校正値により求められた
低周波数成分ＬＦＣとを合成する。このようにして、連
続的に収縮期血圧ＳＢＰが推定され、推定した収縮期血
圧ＥＳＢＰ（図８（ｄ））を出力する（Ｓ４０）。Next, the systolic blood pressure SBP is estimated by adding the BLC component and the LFC component. That is, the adding unit 33 includes the band limited component BLC of the pulse wave transit time.
And a low-frequency component LFC obtained by a calibration value measured at regular time intervals. Thus, the systolic blood pressure SBP is continuously estimated, and the estimated systolic blood pressure ESBP (FIG. 8D) is output (S40).
【００１６】つぎに、実際の測定結果について説明す
る。測定された信号は、４歳から７７歳までの広い範囲
の年齢で、２０例（男１４例，女６例）を対象とした。
疾患は、狭心症，心房中隔欠損，解離性大動脈瘤，心室
中隔欠損，ファロー四徴症，等の心臓血管の病気を計測
対象とした。ＰＡＴ信号を求めるための測定信号は、胸
部Ｖ５誘導心電図の信号、指尖光電脈波（Photoplethys
mogram、ＰＰＧ）信号（左食指等）である。この他に、
肢誘導II心電図等を用いることもできる。解析データ長
として、測定時間４２時間２７分、心拍数２０６，５１
９である。また、推定した結果を評価するための血圧基
準値は、左橈動脈カテーテルより計測した。Next, actual measurement results will be described. The measured signals were for 20 cases (14 males and 6 females) at a wide range of ages from 4 to 77 years.
Diseases were measured for cardiovascular diseases such as angina, atrial septal defect, dissecting aortic aneurysm, ventricular septal defect, tetralogy of Fallot, and the like. Measuring signal for determining the PAT signal, chest V 5 lead ECG signal, fingertip photoelectric pulse wave (Photoplethys
mogram, PPG) signal (left finger, etc.). In addition,
Limb lead II electrocardiogram can also be used. As the analysis data length, the measurement time was 42 hours and 27 minutes, and the heart rate was 206, 51.
9 The blood pressure reference value for evaluating the estimated result was measured from the left radial artery catheter.
【００１７】図９に、推定した収縮期血圧ＥＳＢＰのサ
ンプルの説明図を示す。図より、観血式収縮期血圧ＩＳ
ＢＰは、推定した収縮期血圧ＥＳＢＰとよく相関してい
ることがわかる。この例では、推定誤差ＥｒｒＳＢＰ
は、ほぼ７％以内となっている。なお、推定誤差Ｅｒｒ
ＳＢＰは、以下の式で求めたものである。 ＥｒｒＳＢＰ＝１００＊（ＥＳＢＰ−ＩＳＢＰ）／ＩＳ
ＢＰFIG. 9 is an explanatory diagram of a sample of the estimated systolic blood pressure ESBP. From the figure, open systolic blood pressure IS
It can be seen that BP correlates well with the estimated systolic blood pressure ESBP. In this example, the estimation error ErrSBP
Is within approximately 7%. Note that the estimation error Err
SBP is obtained by the following equation. ErrSBP = 100 * (ESBP-ISBP) / IS
BP
【００１８】つぎに、図１０に、２０例について求めた
結果の誤差分布図を示す。この図では、誤差範囲とその
確率は、次の通りである。すなわち、誤差範囲±０％は
確率３８．８％、誤差範囲±１０％は確率９７．８％、
また、誤差範囲±１６％は確率９９．４％である。な
お、校正間隔ＴＣは、５分とした。このように、推定し
た収縮期血圧ＥＳＢＰの誤差特性は、平均誤差がゼロ
で、かなり良い正規分布となっている。Next, FIG. 10 shows an error distribution diagram of the results obtained for 20 examples. In this figure, the error ranges and their probabilities are as follows. That is, the error range ± 0% has a probability of 38.8%, the error range ± 10% has a probability of 97.8%,
In addition, the error range ± 16% has a probability of 99.4%. Note that the calibration interval T C was 5 minutes. As described above, the error characteristic of the estimated systolic blood pressure ESBP has a fairly good normal distribution with an average error of zero.
【００１９】以上のように、ＰＡＴ信号に混入された雑
音を除去した結果、有意で微妙なＰＡＴ信号の経時的変
化が明らかになった。また、比較的短期間又はＳＢＰが
安定している間では、血管特性の大きな変化が認められ
ないため、ＰＡＴが良くＳＢＰに追従していて、良好な
線形関係が見られる。As described above, as a result of removing the noise mixed in the PAT signal, a significant and subtle change with time of the PAT signal became apparent. In addition, during a relatively short period of time or when the SBP is stable, a large change in the blood vessel characteristics is not recognized, so that the PAT follows the SBP well and a good linear relationship is observed.
【００２０】[0020]
【発明の効果】本発明によると、以上のように、ＰＡＴ
の変化が収縮期血圧の変化を反映することに注目し、非
侵襲で連続的に血圧を測定することができる。また、本
発明によると、ノイズに埋められているＰＡＴ信号に対
して、適当なディジタル処理を施し、有用な情報を抽出
することで、正確な血圧の評価を行うことができる。さ
らに、本発明によると、呼吸による影響を抑えて、ＳＢ
ＰとＰＡＴとの相関関係を明確とした血圧測定方法を提
供することができる。According to the present invention, as described above, PAT
It is noted that changes in the blood pressure reflect changes in systolic blood pressure, and blood pressure can be measured non-invasively and continuously. Further, according to the present invention, an accurate evaluation of blood pressure can be performed by performing appropriate digital processing on a PAT signal embedded in noise and extracting useful information. Further, according to the present invention, the influence of respiration is suppressed and SB
A blood pressure measurement method that clarifies the correlation between P and PAT can be provided.
【図面の簡単な説明】[Brief description of the drawings]
【図１】本発明に係る血圧測定方法のフローチャート。FIG. 1 is a flowchart of a blood pressure measurement method according to the present invention.
【図２】脈波伝播時間ＰＡＴの説明図。FIG. 2 is an explanatory diagram of a pulse wave transit time PAT.
【図３】検出したＰＡＴ信号の説明図。FIG. 3 is an explanatory diagram of a detected PAT signal.
【図４】スパイク状雑音除去の説明図。FIG. 4 is an explanatory diagram of spike noise removal.
【図５】例外値検出・除去と欠損値補間の説明図。FIG. 5 is an explanatory diagram of exception value detection / removal and missing value interpolation.
【図６】呼吸成分除去についての説明図。FIG. 6 is an explanatory diagram of respiratory component removal.
【図７】補正処理の説明図。FIG. 7 is an explanatory diagram of a correction process.
【図８】収縮期血圧測定プロセスの説明図。FIG. 8 is an explanatory diagram of a systolic blood pressure measurement process.
【図９】推定した収縮期血圧ＥＳＢＰのサンプルの説明
図。FIG. 9 is an explanatory diagram of a sample of estimated systolic blood pressure ESBP.
【図１０】誤差分布図。FIG. 10 is an error distribution diagram.
Ｓ１０ ＰＡＴ検出処理 Ｓ２０ 雑音除去処理 Ｓ３０ 補正処理 Ｓ４０ 血圧出力処理 ３１ バンドパスフィルタ ３２ 補間処理部 ３３ 加算部 S10 PAT detection processing S20 Noise removal processing S30 Correction processing S40 Blood pressure output processing 31 Band pass filter 32 Interpolation processing unit 33 Addition unit
───────────────────────────────────────────────────── フロントページの続き Ｆターム(参考） 4C017 AA08 AA09 AA19 AB03 AC15 AC26 BC16 BD01 BD05 FF05 FF15 ──────────────────────────────────────────────────続 き Continued on the front page F term (reference) 4C017 AA08 AA09 AA19 AB03 AC15 AC26 BC16 BD01 BD05 FF05 FF15
Claims (6)
除去することにより、修正脈波伝播時間信号を求める雑
音除去処理と、 前記信号処理により求められた修正脈波伝播時間信号の
特定周波数成分を抽出し、抽出された特定周波数成分と
血圧校正値により求めた低周波数成分を合成することに
より、血圧を求める補正処理とを含む血圧測定方法。1. A noise removal process for obtaining a corrected pulse wave transit time signal by removing noise from a detected pulse wave transit time signal; and a specific frequency of the corrected pulse wave transit time signal obtained by the signal processing. A blood pressure measurement method comprising: extracting a component; and synthesizing the extracted specific frequency component and a low frequency component obtained from a blood pressure calibration value to obtain a blood pressure.
た血圧値を用いて、所定時間の間の補間処理を行い連続
した低周波成分を生成することを特徴とする請求項１に
記載の血圧測定方法。2. The method according to claim 1, wherein the correction process uses a blood pressure value measured at a predetermined time interval to perform an interpolation process for a predetermined time to generate a continuous low frequency component. Blood pressure measurement method.
号又は修正脈波伝播信号を用いて、連続した低周波成分
を生成することを特徴とする請求項１に記載の血圧測定
方法。3. The blood pressure measurement method according to claim 1, wherein the correction process generates a continuous low-frequency component using a blood pressure calibration value, a pulse wave propagation signal, or a corrected pulse wave propagation signal. .
去することを特徴とする請求項１乃至３のいずれかに記
載の血圧測定方法。4. The blood pressure measurement method according to claim 1, wherein said noise removal processing removes spike noise.
区間内の例外値を除去し、該当区間の前及び／又は後の
データを用いて除去された欠損値を補間することを特徴
とする請求項１乃至４のいずれかに記載の血圧測定方
法。5. The noise removal processing according to claim 1, wherein
The blood pressure measurement method according to any one of claims 1 to 4, wherein an exceptional value in the section is removed, and the missing value that has been removed is interpolated using data before and / or after the section.
ことを特徴とする請求項１乃至５のいずれかに記載の血
圧測定方法。6. The blood pressure measurement method according to claim 1, wherein the noise removal processing removes a respiratory component.
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| JP27930499A JP3631639B2 (en) | 1999-09-30 | 1999-09-30 | Blood pressure measurement method |
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|---|---|---|---|
| JP27930499A JP3631639B2 (en) | 1999-09-30 | 1999-09-30 | Blood pressure measurement method |
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| JP3631639B2 JP3631639B2 (en) | 2005-03-23 |
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| JP27930499A Expired - Fee Related JP3631639B2 (en) | 1999-09-30 | 1999-09-30 | Blood pressure measurement method |
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