JPH0538332A - Device for measuring degree of arteriosclerosis - Google Patents
Device for measuring degree of arteriosclerosisInfo
- Publication number
- JPH0538332A JPH0538332A JP22100191A JP22100191A JPH0538332A JP H0538332 A JPH0538332 A JP H0538332A JP 22100191 A JP22100191 A JP 22100191A JP 22100191 A JP22100191 A JP 22100191A JP H0538332 A JPH0538332 A JP H0538332A
- Authority
- JP
- Japan
- Prior art keywords
- pressure
- compression
- degree
- pulse wave
- arteriosclerosis
- 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.)
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/107—Measuring physical dimensions, e.g. size of the entire body or parts thereof
- A61B5/1073—Measuring volume, e.g. of limbs
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Dentistry (AREA)
- Physics & Mathematics (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】本発明は生体内の動脈の硬化度を
測定することができる動脈硬化度測定装置に関するもの
である。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an arteriosclerosis degree measuring apparatus capable of measuring the degree of arteriosclerosis in a living body.
【０００２】[0002]
【従来の技術および課題】動脈硬化状態は生体の循環器
や神経の状態に密接に関連しており、重要な医学情報で
あることから、動脈硬化度を測定することが望まれる。
しかし、動脈硬化度は動脈血管壁の硬さの程度を表すも
のであるから、皮膚の上から容易に測定することは困難
であった。2. Description of the Related Art The arteriosclerosis state is closely related to the states of the circulatory organs and nerves of the living body and is important medical information, so it is desirable to measure the degree of arteriosclerosis.
However, since the degree of arteriosclerosis represents the degree of hardness of the arterial blood vessel wall, it was difficult to easily measure it from above the skin.
【０００３】本発明者等は以上の事情を背景として種々
研究を重ねた結果、たとえば、生体内の動脈を圧迫する
カフ等の圧迫装置の圧迫圧力を目標圧迫圧力まで昇圧し
た後降圧させる過程で逐次検出される脈波に基づいて血
圧値を測定する場合において、その脈波の振幅は漸増し
た後漸減するのであるが、脈波振幅の増加状態、脈
波振幅の変化曲線の高さと幅との割合、脈波振幅の最
大値と平均血圧値との比は、被検者の動脈硬化度にそれ
ぞれ密接に関連することを見い出した。本発明はかかる
知見に基づいて為されたものである。As a result of various researches conducted by the present inventors against the background described above, for example, in the process of increasing the compression pressure of a compression device such as a cuff for compressing an artery in a living body to a target compression pressure and then decreasing the pressure. When measuring the blood pressure value based on the sequentially detected pulse wave, the amplitude of the pulse wave gradually increases and then gradually decreases, but the increase state of the pulse wave amplitude, the height and width of the change curve of the pulse wave amplitude, and It was found that the ratio of the pulse wave amplitude and the ratio of the maximum value of the pulse wave amplitude to the average blood pressure value were respectively closely related to the arteriosclerosis degree of the subject. The present invention was made based on such findings.
【０００４】[0004]
【課題を解決するための第１の手段】すなわち、第１発
明の要旨とするところは、生体内の動脈の硬化度を測定
するための装置であって、(a) 前記動脈を圧迫する圧迫
装置と、(b) その圧迫装置の圧迫圧力を検出し、その圧
迫圧力を表す圧力信号を出力する圧力センサと、(c)前
記圧迫装置の圧迫圧力を前記生体の最高血圧値より高い
目標圧迫圧力まで昇圧した後予め定められた速度で降圧
させる圧迫圧力調節手段と、(d) 前記圧迫圧力の降圧過
程で逐次得られる前記圧力信号に基づいて前記動脈から
脈波を検出する脈波検出手段と、(e) 前記圧迫圧力の降
圧過程で前記動脈から発生し且つ逐次検出される脈波の
振幅の増加状態に基づいて前記動脈硬化度を決定する動
脈硬化度決定手段とを含むことにある。[Means for Solving the Problems] That is, the gist of the first invention is a device for measuring the degree of hardening of an artery in a living body, comprising: (a) a compression for compressing the artery. A device, (b) a pressure sensor that detects the compression pressure of the compression device and outputs a pressure signal that represents the compression pressure, and (c) the compression pressure of the compression device that is higher than the maximum blood pressure value of the living body. A compression pressure adjusting means for increasing the pressure and then decreasing the pressure at a predetermined rate, and (d) a pulse wave detecting means for detecting a pulse wave from the artery based on the pressure signal sequentially obtained in the step of decreasing the compression pressure. And (e) includes arteriosclerosis degree determining means for determining the degree of arteriosclerosis based on the increasing state of the amplitude of the pulse wave generated from the artery in the process of reducing the compression pressure and sequentially detected. ..
【０００５】[0005]
【作用および第１発明の効果】かかる構成の第１発明の
動脈硬化度測定装置においては、生体内の動脈を圧迫す
る圧迫装置の圧迫圧力を圧迫圧力調節手段によりその生
体の最高血圧値より高い目標圧迫圧力まで昇圧した後予
め定められた速度で降圧させる過程で、動脈硬化度決定
手段により、前記動脈から発生し且つ脈波検出手段にて
逐次検出される脈波の振幅の増加状態に基づいて動脈硬
化度が決定されるので、動脈硬化度を皮膚の上から容易
に測定することができるのである。これにより、循環器
の健康状態を表す重要な指標である動脈硬化度が容易に
測定されるばかりでなく、たとえば、麻酔の深さと動脈
硬化度との関係から麻酔深度の測定に利用され得るとと
もに、交感神経と動脈硬化度との関係から精神状態の測
定に利用され得る。In the arteriosclerosis degree measuring device of the first aspect of the present invention having such a configuration, the compression pressure of the compression device for compressing the artery in the living body is higher than the maximum blood pressure value of the living body by the compression pressure adjusting means. Based on the increase state of the amplitude of the pulse wave generated from the artery by the arteriosclerosis determination means and successively detected by the pulse wave detection means in the process of increasing the pressure to the target compression pressure and then decreasing the pressure at a predetermined rate. Since the degree of arteriosclerosis is determined by the method, the degree of arteriosclerosis can be easily measured from above the skin. As a result, not only can the degree of arteriosclerosis, which is an important indicator of the health status of the circulatory organ, be easily measured, but it can also be used to measure the depth of anesthesia from the relationship between the depth of anesthesia and the degree of arteriosclerosis. , It can be used to measure the mental state from the relationship between the sympathetic nerve and the degree of arteriosclerosis.
【０００６】[0006]
【課題を解決するための第２の手段】次に、第２発明の
要旨とするところは、生体内の動脈の硬化度を測定する
ための装置であって、(a) 前記動脈を圧迫する圧迫装置
と、(b) その圧迫装置の圧迫圧力を検出し、その圧迫圧
力を表す圧力信号を出力する圧力センサと、(c) その圧
迫装置の圧迫圧力を前記生体の平均血圧値より高い目標
圧迫圧力まで昇圧した後予め定められた速度で降圧させ
る圧迫圧力調節手段と、(d) 前記圧迫圧力の降圧過程で
逐次得られる前記圧力信号に基づいて前記動脈から脈波
を検出する脈波検出手段と、(e) 前記圧迫圧力の降圧過
程で逐次検出される脈波の振幅の最大値を決定する振幅
最大値決定手段と、(f) 前記圧迫圧力の降圧過程で逐次
検出される脈波の振幅の変化を表す振幅変化曲線の、前
記振幅の最大値の予め定められた比率以上の部分の曲線
幅を決定する曲線幅決定手段と、(g) 前記振幅の最大値
と前記曲線幅との比に基づいて、その比と前記動脈硬化
度との間の予め記憶された関係から前記生体の動脈硬化
度を決定する動脈硬化度決定手段とを含むことにある。[Second Means for Solving the Problems] Next, the gist of the second invention is a device for measuring the degree of hardening of an artery in a living body, which comprises (a) compressing the artery. A compression device, and (b) a pressure sensor that detects the compression pressure of the compression device and outputs a pressure signal that represents the compression pressure, and (c) the compression pressure of the compression device is higher than the average blood pressure value of the living body. A compression pressure adjusting means for increasing the pressure to a compression pressure and then reducing the pressure at a predetermined rate, and (d) pulse wave detection for detecting a pulse wave from the artery based on the pressure signal sequentially obtained in the pressure reduction step. Means, (e) amplitude maximum value determining means for determining the maximum value of the amplitude of the pulse wave that is sequentially detected in the step of reducing the compression pressure, and (f) pulse wave that is sequentially detected in the step of reducing the compression pressure. Of the maximum value of the amplitude of the amplitude change curve representing the change of the amplitude of Curve width determining means for determining the curve width of a portion having a ratio greater than or equal to, and (g) based on the ratio between the maximum value of the amplitude and the curve width, pre-stored between the ratio and the arteriosclerosis degree. And an arteriosclerosis degree determining means for determining the arteriosclerosis degree of the living body from the established relationship.
【０００７】[0007]
【作用および第２発明の効果】かかる構成の第２発明の
動脈硬化度測定装置においては、生体内の動脈を圧迫す
る圧迫装置の圧迫圧力を圧迫圧力調節手段によりその生
体の平均血圧値より高い目標圧迫圧力まで昇圧した後予
め定められた速度で降圧させる過程で脈波検出手段によ
りその動脈から脈波が逐次検出され、その脈波の振幅の
最大値が振幅最大値決定手段により決定されるととも
に、その脈波の振幅の変化を表す振幅変化曲線の、前記
振幅の最大値の予め定められた比率以上の部分の曲線幅
が曲線幅決定手段により決定される。そして、動脈硬化
度決定手段により、前記振幅の最大値と前記曲線幅との
比に基づいて、その比と動脈硬化度との間の予め記憶さ
れた関係から生体の動脈硬化度が決定されるので、動脈
硬化度を皮膚の上から容易に測定できる。In the arteriosclerosis degree measuring device of the second aspect of the present invention having such a configuration, the compression pressure of the compression device for compressing the artery in the living body is higher than the average blood pressure value of the living body by the compression pressure adjusting means. The pulse wave is sequentially detected from the artery by the pulse wave detecting means in the process of increasing the pressure to the target compression pressure and then decreasing the pressure at a predetermined rate, and the maximum value of the amplitude of the pulse wave is determined by the amplitude maximum value determining means. At the same time, the curve width determining means determines the curve width of a portion of the amplitude change curve representing the change in the amplitude of the pulse wave that is equal to or greater than a predetermined ratio of the maximum value of the amplitude. Then, the arteriosclerosis degree determination means determines the arteriosclerosis degree of the living body based on the ratio between the maximum value of the amplitude and the curve width from the prestored relationship between the ratio and the arteriosclerosis degree. Therefore, the degree of arteriosclerosis can be easily measured from above the skin.
【０００８】[0008]
【課題を解決するための第３の手段】また、第３発明の
要旨とするところは、生体内の動脈の硬化度を測定する
ための装置であって、(a) 前記動脈を圧迫する圧迫装置
の圧迫圧力を予め定められた目標圧迫圧力まで昇圧した
後予め定められた速度で降圧させる過程で逐次得られる
脈波に基づいて前記生体の平均血圧値を測定する血圧測
定手段と、(b) 前記圧迫圧力の降圧過程で逐次得られる
脈波の振幅の最大値と前記平均血圧値との比に基づい
て、その比と前記動脈硬化度との間の予め記憶された関
係から前記生体の動脈硬化度を決定する動脈硬化度決定
手段とを含むことにある。[Third Means for Solving the Problem] The gist of the third invention is a device for measuring the degree of hardening of an artery in a living body, comprising: (a) a compression for compressing the artery. Blood pressure measuring means for measuring the average blood pressure value of the living body based on the pulse wave sequentially obtained in the process of increasing the compression pressure of the device to a predetermined target compression pressure and then decreasing the pressure at a predetermined rate, and (b ) Based on the ratio between the maximum value of the amplitude of the pulse wave and the average blood pressure value that are sequentially obtained in the step of reducing the compression pressure, based on a pre-stored relationship between the ratio and the degree of arteriosclerosis of the living body. And arteriosclerosis degree determining means for determining the degree of arteriosclerosis.
【０００９】[0009]
【作用および第３発明の効果】かかる構成の第３発明の
動脈硬化度測定装置においては、血圧測定手段により、
生体内の動脈を圧迫する圧迫装置の圧迫圧力を予め定め
られた目標圧迫圧力まで昇圧した後予め定められた速度
で降圧させる過程で逐次得られる脈波に基づいてその生
体の平均血圧値が測定されるとともに、動脈硬化度決定
手段により、圧迫圧力の降圧過程で逐次得られる脈波の
振幅の最大値と前記平均血圧値との比に基づいて、その
比と動脈硬化度との間の予め記憶された関係から生体の
動脈硬化度が決定されるので、動脈硬化度を皮膚の上か
ら容易に測定できる。In the arteriosclerosis degree measuring device of the third aspect of the present invention having such a configuration, the blood pressure measuring means allows
The average blood pressure value of the living body is measured based on the pulse wave that is sequentially obtained in the process of increasing the compression pressure of the compression device that compresses the artery in the living body to the predetermined target compression pressure and then decreasing the pressure at the predetermined speed With the arteriosclerosis degree determining means, based on the ratio between the maximum value of the amplitude of the pulse wave and the average blood pressure value that are successively obtained in the step of reducing the compression pressure, the ratio and the arteriosclerosis degree are calculated in advance. Since the degree of arteriosclerosis of the living body is determined from the stored relationship, the degree of arteriosclerosis can be easily measured from above the skin.
【００１０】[0010]
【実施例】以下、本発明の一実施例を図面に基づいて詳
細に説明する。DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An embodiment of the present invention will be described in detail below with reference to the drawings.
【００１１】図２は、第１発明の動脈硬化度測定装置の
一構成例を示す図である。図２において、１０はゴム製
袋状のカフであって、たとえば人体の上腕部１２に巻回
された状態で取り付けられる。カフ１０には、圧力セン
サ１４、切換弁１６、および空気ポンプ１８が配管２０
を介して接続されている。切換弁１６は、カフ１０内へ
の圧力の供給を許容する圧力供給状態と、カフ１０内を
徐々に排気する徐速排気状態と、カフ１０内を急速に排
気する急速排気状態とに切り換えられるように構成され
ている。圧力センサ１４は、カフ１０内の圧力を検出し
てその圧力を表す圧力信号ＳＰを静圧弁別回路２２およ
び脈波弁別回路２４にそれぞれ供給する。静圧弁別回路
２２はローパスフィルタを備えており、圧力信号ＳＰに
含まれる定常的な圧力（カフ圧Ｐ）を表すカフ圧信号Ｓ
Ｋを弁別してそのカフ圧信号ＳＫをＡ／Ｄ変換器２６を
介して制御装置２８へ供給する。脈波弁別回路２４はバ
ンドパスフィルタを備えており、圧力信号ＳＰに含まれ
る脈波を表す脈波信号ＳＭを弁別してその脈波信号ＳＭ
をＡ／Ｄ変換器３０を介して制御装置２８へ供給する。
この脈波信号ＳＭが表す脈波は、被測定者の心拍に同期
して上腕動脈から発生してカフ１０に伝達される圧力振
動波である。本実施例においては、上記カフ１０が圧迫
装置を構成するとともに、上記脈波弁別回路２４が脈波
検出手段として機能する。FIG. 2 is a diagram showing an example of the construction of the arteriosclerosis degree measuring device of the first invention. In FIG. 2, reference numeral 10 denotes a rubber bag-like cuff, which is attached to the upper arm 12 of a human body in a wound state. A pressure sensor 14, a switching valve 16, and an air pump 18 are connected to the cuff 10 through a pipe 20.
Connected through. The switching valve 16 is switched between a pressure supply state that allows the pressure to be supplied into the cuff 10, a slow exhaust state in which the cuff 10 is gradually exhausted, and a rapid exhaust state in which the cuff 10 is rapidly exhausted. Is configured. The pressure sensor 14 detects the pressure in the cuff 10 and supplies a pressure signal SP representing the pressure to the static pressure discrimination circuit 22 and the pulse wave discrimination circuit 24, respectively. The static pressure discrimination circuit 22 includes a low-pass filter, and the cuff pressure signal S representing the steady pressure (cuff pressure P) included in the pressure signal SP.
K is discriminated and the cuff pressure signal SK is supplied to the control device 28 via the A / D converter 26. The pulse wave discrimination circuit 24 includes a band pass filter, discriminates the pulse wave signal SM representing the pulse wave included in the pressure signal SP, and then the pulse wave signal SM.
Is supplied to the control device 28 via the A / D converter 30.
The pulse wave represented by the pulse wave signal SM is a pressure vibration wave generated from the brachial artery in synchronization with the heartbeat of the measurement subject and transmitted to the cuff 10. In the present embodiment, the cuff 10 constitutes a compression device, and the pulse wave discrimination circuit 24 functions as a pulse wave detecting means.
【００１２】上記制御装置２８は、ＣＰＵ、ＲＯＭ、Ｒ
ＡＭ、およびＩ／Ｏポート等を備えた所謂マイクロコン
ピュータにて構成されており、ＣＰＵは、ＲＯＭに予め
記憶されたプログラムに従ってＲＡＭの記憶機能を利用
しつつ信号処理を実行することにより、Ｉ／Ｏポートか
ら駆動信号を出力して図示しない駆動回路を介して切換
弁１６および空気ポンプ１８を制御することによりカフ
圧Ｐを調節し、カフ圧Ｐを被測定者の予想される最高血
圧値より高い所定の目標カフ圧Ｐm まで昇圧した後、そ
のカフ圧Ｐを予め定められた緩やかな速度で降圧させる
過程で逐次採取される脈波に基づいて、最高血圧値，最
低血圧値，および平均血圧値等の血圧値を決定するため
の良く知られたオシロメトリック方式の血圧値決定アル
ゴリズムに従ってたとえば最高血圧値ＳＹＳ，最低血圧
値ＤＩＡ，および平均血圧値ＭＥＡＮを決定してその決
定した血圧値を表示器３２に表示させる。徐速降圧過程
で逐次採取される脈波の振幅がそれぞれ求められ且つそ
れらの振幅の最大値が決定されて、その最大振幅の脈波
が採取された時点のカフ圧Ｐが平均血圧値ＭＥＡＮとし
て決定され、この平均血圧値ＭＥＡＮより高圧側におけ
る脈波振幅の変曲点に対応するカフ圧Ｐが最高血圧値Ｓ
ＹＳとして決定されるとともに、その平均血圧値ＭＥＡ
Ｎより低圧側における脈波振幅の変曲点に対応するカフ
圧Ｐが最低血圧値ＤＩＡとして決定されるのである。本
実施例においては、上記圧力センサ１４、切換弁１６、
空気ポンプ１８、静圧弁別回路２２、Ａ／Ｄ変換器２
６、および制御装置２８等が圧迫圧力調節手段を構成す
る。The control device 28 includes a CPU, ROM, R
It is configured by a so-called microcomputer having an AM, an I / O port, etc., and the CPU executes I / O by performing signal processing while utilizing the storage function of the RAM in accordance with a program stored in advance in the ROM. The cuff pressure P is adjusted by outputting a drive signal from the O port and controlling the switching valve 16 and the air pump 18 via a drive circuit (not shown) so that the cuff pressure P is higher than the maximum blood pressure value expected by the subject. After the pressure is raised to a high predetermined target cuff pressure P m , the systolic blood pressure value, the diastolic blood pressure value, and the average are obtained based on the pulse wave that is sequentially collected in the process of decreasing the cuff pressure P at a predetermined slow speed. According to a well-known oscillometric blood pressure value determining algorithm for determining a blood pressure value such as a blood pressure value, for example, a maximum blood pressure value SYS, a minimum blood pressure value DIA, and It determines the average blood pressure value MEAN displays the blood pressure value thus determined to the display 32. The amplitudes of the pulse waves that are sequentially sampled in the gradual depressurization process are obtained, and the maximum values of these amplitudes are determined. The cuff pressure P at the time when the pulse waves of the maximum amplitude are sampled is the average blood pressure value MEAN. The cuff pressure P that is determined and corresponds to the inflection point of the pulse wave amplitude on the higher pressure side than the mean blood pressure value MEAN is the systolic blood pressure value S.
Determined as YS and its mean blood pressure value MEA
The cuff pressure P corresponding to the inflection point of the pulse wave amplitude on the lower pressure side than N is determined as the minimum blood pressure value DIA. In the present embodiment, the pressure sensor 14, the switching valve 16,
Air pump 18, static pressure discriminating circuit 22, A / D converter 2
6, the control device 28 and the like constitute a compression pressure adjusting means.
【００１３】また、制御装置２８は、予め記憶されたプ
ログラムに従って、カフ圧Ｐの徐速降圧過程で上腕動脈
から逐次検出される脈波の振幅の増加状態に基づいて被
測定者の動脈硬化度を決定し、その決定された動脈硬化
度を表示器３２に逐次表示させる。したがって、本実施
例においては、制御装置２８が動脈硬化度決定手段を構
成する。Further, the control device 28, according to a program stored in advance, based on the increasing state of the amplitude of the pulse wave sequentially detected from the brachial artery in the process of gradually decreasing the cuff pressure P, the degree of arteriosclerosis of the subject. Is determined, and the determined degree of arteriosclerosis is sequentially displayed on the display 32. Therefore, in the present embodiment, the control device 28 constitutes an arteriosclerosis degree determining means.
【００１４】ここで、図３は、上腕動脈を圧迫するカフ
１０内の目標カフ圧Ｐm からの徐速降圧過程における種
々のカフ圧Ｐでの脈波の発生状況を説明するための概要
図であって、実線にて示す図形は心臓の拡張時における
上腕動脈の内壁面を表しており、心臓の収縮時において
は、カフ１０にて圧迫される上腕動脈がカフ圧Ｐに抗し
て破線で示すように拡張して斜線にて示す容積に対応す
る大きさの脈波が発生する。すなわち、たとえば図４の
振幅変化曲線に示すように、カフ圧Ｐが最高血圧値ＳＹ
Ｓより大きいとき（図４中Ｉ）には血流が阻止された状
態で極小さい脈波が発生するだけであるが、カフＰが最
高血圧値ＳＹＳに達する（図４中II）と血液の流動が再
開されて脈波の振幅Ａが漸増し、カフ圧Ｐが平均血圧値
ＭＥＡＮに達したとき（図４中III ）に最大振幅Ａmax
の脈波が発生するとともに、カフ圧Ｐが平均血圧値ＭＥ
ＡＮより更に小さくなる（図４中IV）と脈波の振幅Ａが
漸減するのである。この場合において、上腕動脈の血管
壁が硬くなる程、その上腕動脈のカフ１０よりも上流側
に位置する部分の心臓収縮時における弾性変形は小さく
なるため、カフ圧Ｐの降圧過程で逐次検出される脈波の
振幅は上腕動脈の血管壁が硬くなる程急激に立ち上がる
と考えられる。第１発明の動脈硬化度測定装置の測定原
理はかかる基本原理に基づいているのである。なお、上
記図４の振幅変化曲線は、降圧過程で逐次得られた脈波
の振幅の大きさを表す点（図示せず）を結ぶ包絡線を示
す。Here, FIG. 3 is a schematic diagram for explaining the state of generation of pulse waves at various cuff pressures P in the gradual pressure reduction process from the target cuff pressure P m in the cuff 10 that compresses the brachial artery. The solid line represents the inner wall surface of the brachial artery when the heart is dilated, and when the heart is deflated, the brachial artery compressed by the cuff 10 resists the cuff pressure P and is broken. A pulse wave having a size corresponding to the volume indicated by diagonal lines is generated by expanding as indicated by. That is, for example, as shown in the amplitude change curve of FIG. 4, the cuff pressure P is the systolic blood pressure value SY.
When it is larger than S (I in FIG. 4), only a minimal pulse wave is generated in a state where blood flow is blocked, but when the cuff P reaches the systolic blood pressure value SYS (II in FIG. 4), When the flow is restarted and the amplitude A of the pulse wave gradually increases, and the cuff pressure P reaches the mean blood pressure value MEAN (III in FIG. 4), the maximum amplitude A max.
Pulse wave is generated and the cuff pressure P changes to the average blood pressure value ME.
When it becomes smaller than AN (IV in FIG. 4), the amplitude A of the pulse wave gradually decreases. In this case, as the blood vessel wall of the brachial artery becomes harder, the elastic deformation of the portion of the brachial artery located upstream of the cuff 10 at the time of cardiac contraction becomes smaller. It is considered that the amplitude of the pulse wave increases rapidly as the vascular wall of the brachial artery becomes harder. The measurement principle of the arteriosclerosis degree measuring device of the first invention is based on this basic principle. The amplitude change curve of FIG. 4 shows an envelope connecting points (not shown) representing the magnitude of the amplitude of the pulse wave sequentially obtained in the step of lowering pressure.
【００１５】以下、本実施例の動脈硬化度測定装置の作
動を図１のフローチャートに従って説明する。The operation of the arteriosclerosis measuring device of this embodiment will be described below with reference to the flow chart of FIG.
【００１６】電源が投入されると、図示しない初期処理
が実行された後、ステップＳ１が実行されて図示しない
起動スイッチがＯＮ操作されたか否かが判断される。こ
の判断が否定された場合にはステップＳ１が繰り返し実
行されて待機状態とされるが、肯定された場合にはステ
ップＳ２が実行されることにより、切換弁１６が圧力供
給状態に切り換えられ且つ空気ポンプ１８が駆動されて
カフ１０内が被測定者の予想される最高血圧値より高い
所定の目標カフ圧Ｐｍ（たとえば１８０mmHg程度の圧
力）まで昇圧された後空気ポンプ１８が停止させられる
とともに、ステップＳ３が実行されて、切換弁１６が徐
速排気状態に切り換えられることにより、カフ１０内の
徐速降圧が開始される。When the power is turned on, after initial processing (not shown) is executed, step S1 is executed to determine whether or not the start switch (not shown) is turned on. If this determination is negative, step S1 is repeatedly executed to enter the standby state, but if affirmative, step S2 is executed, so that the switching valve 16 is switched to the pressure supply state and the air is supplied. After the pump 18 is driven to increase the pressure inside the cuff 10 to a predetermined target cuff pressure Pm (for example, a pressure of about 180 mmHg) higher than the systolic blood pressure value expected by the subject, the air pump 18 is stopped and the step is performed. When S3 is executed and the switching valve 16 is switched to the gradual exhaust state, the gradual pressure reduction in the cuff 10 is started.
【００１７】次に、ステップＳ４が実行されることによ
り、脈波信号ＳＭが読み込まれて脈波が１拍検出された
か否かが判断される。この判断が否定された場合にはス
テップＳ４が繰り返し実行されるが、肯定された場合に
はステップＳ５が実行されて、検出された脈波の振幅Ａ
が算出され且つそのときのカフ圧Ｐと共に記憶された
後、ステップＳ６の血圧値決定ルーチンが実行される。
この血圧値決定ルーチンにおいては、逐次検出される脈
波の振幅Ａの最大値Ａmax が決定されて、その最大振幅
Ａmax の脈波が採取された時点のカフ圧Ｐが平均血圧値
ＭＥＡＮとして決定されるとともに、この平均血圧値Ｍ
ＥＡＮより高圧側における脈波振幅の変曲点に対応する
カフ圧Ｐが最高血圧値ＳＹＳとして決定され且つその平
均血圧値ＭＥＡＮより低圧側における脈波の振幅の変曲
点に対応するカフ圧Ｐが最低血圧値ＤＩＡとして決定さ
れる。次に、ステップＳ７が実行されて、血圧測定が完
了したか否かが判断され、未だ完了していない場合には
ステップＳ４乃至ステップＳ７が繰り返し実行される。Next, by executing step S4, it is determined whether the pulse wave signal SM is read and one pulse wave is detected. If this determination is negative, step S4 is repeatedly executed, but if the determination is positive, step S5 is executed to detect the amplitude A of the detected pulse wave.
Is calculated and stored together with the cuff pressure P at that time, the blood pressure value determination routine of step S6 is executed.
In this blood pressure value determination routine, the maximum value A max of the amplitude A of the pulse wave that is sequentially detected is determined, and the cuff pressure P at the time when the pulse wave of the maximum amplitude A max is sampled is the average blood pressure value MEAN. Once determined, this mean blood pressure value M
The cuff pressure P corresponding to the inflection point of the pulse wave amplitude on the high pressure side of EAN is determined as the systolic blood pressure value SYS, and the cuff pressure P corresponding to the inflection point of the amplitude of the pulse wave on the low pressure side of the mean blood pressure value MEAN. Is determined as the minimum blood pressure value DIA. Next, step S7 is executed to determine whether or not the blood pressure measurement is completed. If not completed, steps S4 to S7 are repeatedly executed.
【００１８】血圧測定が完了して上記ステップＳ７の判
断が肯定された場合には、ステップＳ８が実行されるこ
とにより、切換弁１６が急速排気状態に切り換えられて
カフ１０内が急速に排圧される。続くステップＳ９にお
いては、たとえば時定数の考え方に基づいて、最大振幅
Ａmax の６３．２％値（０．６３２Ａmax ）が算出され
るとともに、ステップＳ１０においては、図４に示すよ
うに、振幅変化曲線の最高血圧値ＳＹＳに対応する変曲
点ａと前記０．６３２Ａmax に対応する点ｂとを結ぶ直
線ｃの傾斜角度θが決定される。次に、ステップＳ１１
が実行されて、たとえば図５に示すような傾斜角度θと
動脈硬化度との間の予め記憶された関係から、ステップ
Ｓ１０で決定された実際の傾斜角度θに基づいて被測定
者の動脈硬化度が決定されるとともに、ステップＳ１２
が実行されて、その動脈硬化度が最高血圧値ＳＹＳ，最
低血圧値ＤＩＡ，および平均血圧値ＭＥＡＮと共に表示
器３２に表示された後終了させられる。When the blood pressure measurement is completed and the determination in step S7 is affirmative, step S8 is executed to switch the switching valve 16 to the rapid exhaust state, so that the pressure inside the cuff 10 is rapidly exhausted. To be done. In the subsequent step S9, a 63.2% value (0.632A max ) of the maximum amplitude A max is calculated based on the concept of the time constant, and in step S10, as shown in FIG. The inclination angle θ of the straight line c connecting the inflection point a corresponding to the systolic blood pressure value SYS of the change curve and the point b corresponding to 0.632A max is determined. Next, step S11
Is executed, and based on the pre-stored relationship between the inclination angle θ and the degree of arteriosclerosis as shown in FIG. 5, the arteriosclerosis of the measurement subject is determined based on the actual inclination angle θ determined in step S10. The degree is determined and step S12
Is executed, the degree of arteriosclerosis is displayed on the display 32 together with the systolic blood pressure value SYS, the diastolic blood pressure value DIA, and the mean blood pressure value MEAN, and then the processing is terminated.
【００１９】このように本実施例によれば、カフ１０内
の徐速降圧過程で上腕動脈から逐次検出される脈波の振
幅の増加状態がその振幅の変化曲線における前記直線ｃ
の傾斜角度θとして検出され、動脈硬化度と密接に関連
するその傾斜角度θに基づいて予め記憶された関係から
実際の動脈硬化度が決定されるので、被測定者の動脈硬
化度を皮膚の上から容易に測定することができる。As described above, according to the present embodiment, the increasing state of the amplitude of the pulse wave sequentially detected from the brachial artery in the process of gradually decreasing the pressure in the cuff 10 is represented by the straight line c in the change curve of the amplitude.
Is detected as the inclination angle θ, and the actual degree of arteriosclerosis is determined from the relationship stored in advance based on the inclination angle θ that is closely related to the degree of arteriosclerosis. It can be easily measured from above.
【００２０】また、本実施例によれば、従来のオシロメ
トリック型血圧測定装置をそのまま流用できるため、動
脈硬化度測定装置を容易に構成できる利点がある。Further, according to this embodiment, since the conventional oscillometric blood pressure measuring device can be used as it is, there is an advantage that the arteriosclerosis measuring device can be easily constructed.
【００２１】次に、第１発明の他の実施例を説明する。Next, another embodiment of the first invention will be described.
【００２２】たとえば、前記実施例では、振幅の増加状
態を表す直線ｃの傾斜角度θと動脈硬化度との間の予め
記憶された関係から実際の傾斜角度θに基づいて被測定
者の動脈硬化度が決定されるように構成されているが、
必ずしもその必要はなく、たとえば、前記振幅変化曲線
における最高血圧値ＳＹＳに対応する変曲点ａから０．
６３２Ａmax に対応する点ｂに達するまでの到達時間ｔ
（図４参照）に基づいて脈波振幅の増加状態を検出し、
その到達時間ｔと動脈硬化度との間のたとえば図６に示
すような予め記憶された関係から実際の到達時間ｔに基
づいて被測定者の動脈硬化度を決定するようにしてもよ
いし、あるいは、カフ圧Ｐの徐速降圧が開始されてから
逐次検出される脈波の振幅の、カフ圧Ｐの降圧割合に対
する増加率に基づいて脈波振幅の増加状態を検出し、そ
の増加率と動脈硬化率との間のたとえば図７に示すよう
な予め記憶された関係から実際の増加率に基づいて被測
定者の動脈硬化度を決定するようにしてもよい。For example, in the above embodiment, the arteriosclerosis of the person to be measured is based on the actual inclination angle θ from the prestored relationship between the inclination angle θ of the straight line c representing the increasing state of the amplitude and the degree of arteriosclerosis. It is configured to determine the degree,
This is not always necessary, for example, from the inflection point a corresponding to the systolic blood pressure value SYS in the amplitude change curve to 0.
Arrival time t until reaching the point b corresponding to 632A max
(See FIG. 4) to detect the increase state of the pulse wave amplitude,
The degree of arteriosclerosis of the subject may be determined based on the actual time of arrival t from the relationship stored in advance between the arrival time t and the degree of arteriosclerosis, for example, as shown in FIG. Alternatively, the increasing state of the pulse wave amplitude is detected based on the increasing rate of the amplitude of the pulse wave that is sequentially detected after the cuff pressure P is gradually decreased, and the increasing rate is detected as the increasing rate. The degree of arteriosclerosis of the subject may be determined based on the actual rate of increase from the prestored relationship with the rate of arteriosclerosis as shown in FIG. 7, for example.
【００２３】以上、第１発明の一実施例を図面に基づい
て詳細に説明したが、本発明はその他の態様で実施する
こともできる。Although one embodiment of the first invention has been described in detail with reference to the drawings, the present invention can be implemented in other modes.
【００２４】たとえば、麻酔時においては動脈の硬化度
（柔軟度）が変化することが知られているとともに、交
感神経が興奮すると動脈が硬くなることが知られている
ことから、前記実施例において、被測定者の動脈硬化度
を所定時間毎に測定できるように構成すれば、麻酔の深
さと動脈硬化度との関係から手術中における患者の麻酔
深度をモニタしたり、あるいは交感神経の興奮と動脈硬
化度との関係から病棟などにおける患者の精神状態をモ
ニタしたりすることも可能である。For example, it is known that the degree of arterial stiffness (flexibility) changes during anesthesia and that the arteries become harder when the sympathetic nerve is excited. If it is configured so that the degree of arteriosclerosis of the subject can be measured at predetermined time intervals, the depth of anesthesia of the patient during surgery can be monitored from the relationship between the depth of anesthesia and the degree of arteriosclerosis, or sympathetic excitement It is also possible to monitor the patient's mental condition in a ward or the like from the relationship with the degree of arteriosclerosis.
【００２５】また、前記実施例では、傾斜角度θと動脈
硬化度との間の予め記憶された関係は直線状の関係とさ
れているが、曲線状や階段状の関係とすることもでき
る。In the above embodiment, the pre-stored relationship between the inclination angle θ and the degree of arteriosclerosis is a linear relationship, but it may be a curved or stepwise relationship.
【００２６】また、前記実施例では、脈波の振幅の増加
状態を表す傾斜角度θを求めるために、振幅変化曲線の
最大値の６３．２％値が用いられているが、振幅最大値
の６３．２％以外の比率の値を用いてもよい。Further, in the above-mentioned embodiment, 63.2% of the maximum value of the amplitude change curve is used to obtain the inclination angle θ representing the increase state of the amplitude of the pulse wave. A value of a ratio other than 63.2% may be used.
【００２７】また、前記実施例では、脈波検出手段は脈
波弁別回路２４にて構成されているが、制御装置２８の
マイクロコンピュータによるデジタルフィルタにて構成
されてもよい。Further, in the above-mentioned embodiment, the pulse wave detecting means is constituted by the pulse wave discriminating circuit 24, but it may be constituted by a digital filter by the microcomputer of the control device 28.
【００２８】また、前記実施例において、血圧値を測定
することなく動脈硬化度のみを測定するようにしてもよ
い。Further, in the above embodiment, only the degree of arteriosclerosis may be measured without measuring the blood pressure value.
【００２９】次に、第２発明の実施例を説明する。第２
発明の一実施例である動脈硬化度測定装置は、たとえ
ば、第１発明の実施例の図２と同様の構成を備えている
とともに、図１のフローチャートにおけるステップＳ９
乃至ステップＳ１１以外は同様に構成されているため、
そのステップＳ９乃至ステップＳ１１に替えて設けられ
る図８に示すステップＳＡ９乃至ステップＳＡ１１につ
いてのみ説明する。Next, an embodiment of the second invention will be described. Second
An arteriosclerosis degree measuring device that is an embodiment of the invention has, for example, the same configuration as that of the embodiment of the first invention shown in FIG. 2, and step S9 in the flowchart of FIG.
The steps other than step S11 have the same configuration,
Only steps SA9 to SA11 shown in FIG. 8 provided in place of steps S9 to S11 will be described.
【００３０】まず、ステップＳＡ９が実行されて、脈波
振幅の最大値Ａmax の９０％値（０．９Ａmax ）が決定
され且つ振幅変化曲線の０．９Ａmax 以上の部分の曲線
幅Ｗ（図９参照）が決定される。次に、ステップＳＡ１
０が実行されて、振幅最大値Ａmax と曲線幅Ｗとの比
（Ａmax ／Ｗ）が求められる。次いで、ステップＳＡ１
１が実行されて、比（Ａmax ／Ｗ）と動脈硬化度との間
のたとえば図１０に示すような予め記憶された関係から
ステップＳＡ１０にて決定された実際の比（Ａmax ／
Ｗ）に基づいて被測定者の動脈硬化度が決定される。こ
れにより、第１発明の実施例と同様の効果が得られる。
この場合においては、制御装置２８が振幅最大値決定手
段、曲線幅決定手段、および動脈硬化度決定手段として
機能する。[0030] First, step SA9 and is executed, 90% of the maximum value A max of the pulse wave amplitude (0.9 A max) is determined and the amplitude change curve 0.9 A max or more portions of the curve width W ( (See FIG. 9) is determined. Next, step SA1
0 is executed to obtain the ratio (A max / W) between the maximum amplitude value A max and the curve width W. Then, step SA1
1 is performed, the ratio (A max / W) and the actual ratio is determined from a pre-stored relationship shown in FIG. 10 for example between arterial stiffness in step SA10 (A max /
The degree of arteriosclerosis of the subject is determined based on W). As a result, the same effect as that of the first embodiment is obtained.
In this case, the control device 28 functions as an amplitude maximum value determination means, a curve width determination means, and an arteriosclerosis degree determination means.
【００３１】なお、上記第２発明の実施例においては、
目標カフ圧Ｐm は必ずしも最高血圧値より高い圧力まで
昇圧する必要はなく平均血圧値より所定量高い圧力まで
昇圧されておれば第２発明の効果を得ることが可能であ
る。In the embodiment of the second invention described above,
The target cuff pressure P m does not necessarily have to be increased to a pressure higher than the systolic blood pressure value, and the effect of the second invention can be obtained if the target cuff pressure P m is increased to a pressure higher than the average blood pressure value by a predetermined amount.
【００３２】次に、第３発明の実施例を説明する。第３
発明の一実施例である動脈硬化度測定装置は、たとえ
ば、第１発明の実施例の図２と同様の構成を備えている
とともに図１のフローチャートにおけるステップＳ９乃
至ステップＳ１１以外は同様に構成されているため、そ
のステップＳ９乃至ステップＳ１１に替えて設けられる
図１１に示すステップＳＢ９およびステップＳＢ１０に
ついてのみ説明する。Next, an embodiment of the third invention will be described. Third
An arteriosclerosis degree measuring device according to an embodiment of the invention has, for example, the same configuration as that of the embodiment of the first invention shown in FIG. 2 and is configured similarly except steps S9 to S11 in the flowchart of FIG. Therefore, only steps SB9 and SB10 shown in FIG. 11, which are provided in place of steps S9 to S11, will be described.
【００３３】まず、ステップＳＢ９が実行されて、ステ
ップＳ６にて決定された振幅最大値Ａmax と平均血圧値
ＭＥＡＮとの比（Ａmax ／ＭＥＡＮ）が決定される。次
に、ステップＳＢ１０が実行されて、比（Ａmax ／ＭＥ
ＡＮ）と動脈硬化度との間のたとえば図１２に示すよう
な予め記憶された関係からステップＳＢ９にて決定され
た実際の比（Ａmax／ＭＥＡＮ）に基づいて被測定者の
動脈硬化度が決定される。これにより、第１発明の実施
例と同様の効果が得られる。この場合においては、圧力
センサ１４、切換弁１６、空気ポンプ１８、静圧弁別回
路２２、脈波弁別回路２４、Ａ／Ｄ変換器２６，３０、
および制御装置２８等が血圧測定手段を構成するととも
に、制御装置２８が動脈硬化度決定手段として機能す
る。First, step SB9 is executed to determine the ratio (A max / MEAN) between the maximum amplitude value A max determined in step S6 and the mean blood pressure value MEAN. Next, step SB10 is executed to execute the ratio (A max / ME
AN) and the degree of arteriosclerosis based on the actual ratio (A max / MEAN) determined in step SB9 from the relationship stored in advance as shown in FIG. It is determined. As a result, the same effect as that of the first embodiment is obtained. In this case, the pressure sensor 14, the switching valve 16, the air pump 18, the static pressure discrimination circuit 22, the pulse wave discrimination circuit 24, the A / D converters 26 and 30,
The control device 28 and the like constitute blood pressure measuring means, and the control device 28 functions as arteriosclerosis degree determining means.
【００３４】なお、上記第３発明の実施例においては、
血圧測定手段は少なくとも平均血圧値を測定するもので
あればよく、最高血圧値および最低血圧値は測定されな
くてもよい。In the embodiment of the third invention described above,
The blood pressure measuring means only needs to measure at least the average blood pressure value, and the systolic blood pressure value and the diastolic blood pressure value may not be measured.
【００３５】以上、第１発明，第２発明，および第３発
明を一実施例に基づいて説明したが、これらはあくまで
も一例であり、本発明はその趣旨を逸脱しない範囲にお
いて種々変更を加えた態様で実施し得ることは勿論であ
る。The first invention, the second invention, and the third invention have been described above based on the embodiments, but these are merely examples, and the present invention has been modified in various ways without departing from the spirit thereof. As a matter of course, the present invention can be carried out in various modes.
【図１】図２の装置の第１発明による作動を説明するた
めのフローチャートである。1 is a flow chart for explaining the operation of the apparatus of FIG. 2 according to the first invention.
【図２】第１発明，第２発明，および第３発明の動脈硬
化度測定装置の一構成例を示すブロック線図である。FIG. 2 is a block diagram showing a configuration example of an arteriosclerosis degree measuring device of the first invention, the second invention, and the third invention.
【図３】目標カフ圧からの徐速降圧過程における種々の
カフ圧Ｐでの脈波の発生状況を説明するための概要図で
ある。FIG. 3 is a schematic diagram for explaining a generation state of a pulse wave at various cuff pressures P in a process of gradually reducing pressure from a target cuff pressure.
【図４】徐速降圧過程で逐次検出される脈波の振幅の変
化曲線の一例を示す図であって、その振幅の増加状態を
それぞれ表す傾斜角度θおよび到達時間ｔを示す図であ
る。FIG. 4 is a diagram showing an example of a change curve of the amplitude of a pulse wave that is sequentially detected in a gradual depressurization process, and is a diagram showing a tilt angle θ and an arrival time t that respectively represent the increasing state of the amplitude.
【図５】図１のフローチャートのステップＳ１１で用い
られる脈波振幅増加状態を表す傾斜角度θと動脈硬化度
との間の予め記憶された関係の一例を示す図である。5 is a diagram showing an example of a pre-stored relationship between an inclination angle θ and a degree of arteriosclerosis, which represents a pulse wave amplitude increasing state used in step S11 of the flowchart of FIG.
【図６】脈波振幅増加状態を表す到達時間ｔと動脈硬化
度との間の予め記憶された関係の一例を示す図である。FIG. 6 is a diagram showing an example of a pre-stored relationship between an arrival time t representing a pulse wave amplitude increasing state and an arteriosclerosis degree.
【図７】脈波振幅増加状態を表す増加率と動脈硬化度と
の間の予め記憶された関係の一例を示す図である。FIG. 7 is a diagram showing an example of a pre-stored relationship between an increase rate representing a pulse wave amplitude increasing state and an arteriosclerosis degree.
【図８】第２発明の実施例を説明するためのフローチャ
ートの要部を示す図である。FIG. 8 is a diagram showing a main part of a flowchart for explaining an embodiment of the second invention.
【図９】図８のステップＳＡ９にて決定される曲線幅等
を説明するための図である。9 is a diagram for explaining the curve width and the like determined in step SA9 of FIG.
【図１０】図８のステップＳＡ１１にて用いられる関係
の一例を示す図である。10 is a diagram showing an example of a relationship used in step SA11 of FIG.
【図１１】第３発明の実施例を説明するためのフローチ
ャートの要部を示す図である。FIG. 11 is a diagram showing a main part of a flow chart for explaining an embodiment of the third invention.
【図１２】図１１のステップＳＢ１０にて用いられる関
係の一例を示す図である。12 is a diagram showing an example of a relationship used in step SB10 of FIG.
１０ カフ（圧迫装置） ｛１４ 圧力センサ、１６ 切換弁、１８ 空気ポン
プ、２２ 静圧弁別回路、２６ Ａ／Ｄ変換器、２８
制御装置｝圧迫圧力調節手段 ２４ 脈波弁別回路（脈波検出手段） ２８ 制御装置（動脈硬化度決定手段，振幅最大値決定
手段，曲線幅決定手段） ｛１４ 圧力センサ、１６ 切換弁、１８ 空気ポン
プ、２２ 静圧弁別回路、２４ 脈波弁別回路、２６，
３０ Ａ／Ｄ変換器、２８ 制御装置｝血圧測定手段10 cuff (compression device) {14 pressure sensor, 16 switching valve, 18 air pump, 22 static pressure discriminating circuit, 26 A / D converter, 28
Control device} Compression pressure adjusting means 24 Pulse wave discriminating circuit (pulse wave detecting means) 28 Control device (arteriosclerosis degree determining means, maximum amplitude value determining means, curve width determining means) {14 pressure sensor, 16 switching valve, 18 air Pump, 22 static pressure discrimination circuit, 24 pulse wave discrimination circuit, 26,
30 A / D converter, 28 control device} Blood pressure measuring means
Claims (3)
装置であって、 前記動脈を圧迫する圧迫装置と、 該圧迫装置の圧迫圧力を検出し、該圧迫圧力を表す圧力
信号を出力する圧力センサと、 前記圧迫装置の圧迫圧力を前記生体の最高血圧値より高
い目標圧迫圧力まで昇圧した後予め定められた速度で降
圧させる圧迫圧力調節手段と、 前記圧迫圧力の降圧過程で逐次得られる前記圧力信号に
基づいて前記動脈から脈波を検出する脈波検出手段と、 前記圧迫圧力の降圧過程で前記動脈から発生し且つ逐次
検出される脈波の振幅の増加状態に基づいて前記動脈硬
化度を決定する動脈硬化度決定手段とを含むことを特徴
とする動脈硬化度測定装置。1. A device for measuring the degree of hardening of an artery in a living body, which comprises a compression device for compressing the artery, a compression pressure of the compression device is detected, and a pressure signal representing the compression pressure is output. A pressure sensor, compression pressure adjusting means for increasing the compression pressure of the compression device to a target compression pressure higher than the systolic blood pressure value of the living body, and then reducing the pressure at a predetermined rate, and successively obtaining the pressure in the pressure reduction process. Pulse wave detecting means for detecting a pulse wave from the artery based on the pressure signal, and the artery based on an increasing state of the amplitude of the pulse wave generated from the artery in the process of reducing the compression pressure and sequentially detected. An arteriosclerosis degree measuring device comprising: an arteriosclerosis degree determining means for determining a degree of hardening.
装置であって、 前記動脈を圧迫する圧迫装置と、 該圧迫装置の圧迫圧力を検出し、該圧迫圧力を表す圧力
信号を出力する圧力センサと、 前記圧迫装置の圧迫圧力を前記生体の平均血圧値より高
い目標圧迫圧力まで昇圧した後予め定められた速度で降
圧させる圧迫圧力調節手段と、 前記圧迫圧力の降圧過程で逐次得られる前記圧力信号に
基づいて前記動脈から脈波を検出する脈波検出手段と、 前記圧迫圧力の降圧過程で逐次検出される脈波の振幅の
最大値を決定する振幅最大値決定手段と、 前記圧迫圧力の降圧過程で逐次検出される脈波の振幅の
変化を表す振幅変化曲線の、前記振幅の最大値の予め定
められた比率以上の部分の曲線幅を決定する曲線幅決定
手段と、 前記振幅の最大値と前記曲線幅との比に基づいて、該比
と前記動脈硬化度との間の予め記憶された関係から前記
生体の動脈硬化度を決定する動脈硬化度決定手段とを含
むことを特徴とする動脈硬化度測定装置。2. A device for measuring the degree of hardening of an artery in a living body, which comprises a compression device for compressing the artery, a compression pressure of the compression device, and outputs a pressure signal representing the compression pressure. A pressure sensor, compression pressure adjusting means for increasing the compression pressure of the compression device to a target compression pressure higher than the average blood pressure value of the living body, and then reducing the pressure at a predetermined rate, and sequentially obtaining the compression pressure in the step of reducing the compression pressure. A pulse wave detecting means for detecting a pulse wave from the artery based on the pressure signal, an amplitude maximum value determining means for determining a maximum value of the amplitude of the pulse wave sequentially detected in the step of reducing the compression pressure, and A curve width determining means for determining a curve width of a portion of the amplitude change curve representing the change of the amplitude of the pulse wave sequentially detected in the step of reducing the compression pressure, which is equal to or greater than a predetermined ratio of the maximum value of the amplitude, and Maximum amplitude An arteriosclerosis degree determining means for determining an arteriosclerosis degree of the living body based on a pre-stored relationship between the ratio and the arteriosclerosis degree based on a ratio with the curve width. Hardness measuring device.
装置であって、 前記動脈を圧迫する圧迫装置の圧迫圧力を予め定められ
た目標圧迫圧力まで昇圧した後予め定められた速度で降
圧させる過程で逐次得られる脈波に基づいて前記生体の
平均血圧値を測定する血圧測定手段と、 前記圧迫圧力の降圧過程で逐次得られる脈波の振幅の最
大値と前記平均血圧値との比に基づいて、該比と前記動
脈硬化度との間の予め記憶された関係から前記生体の動
脈硬化度を決定する動脈硬化度決定手段とを含むことを
特徴とする動脈硬化度測定装置。3. A device for measuring the degree of hardening of an artery in a living body, the pressure being increased by a compression device for compressing the artery to a predetermined target compression pressure, and then at a predetermined speed. Blood pressure measuring means for measuring the average blood pressure value of the living body based on the pulse wave sequentially obtained in the step of reducing the pressure, the maximum value and the average blood pressure value of the amplitude of the pulse wave sequentially obtained in the step of reducing the compression pressure An arteriosclerosis degree measuring device comprising: an arteriosclerosis degree determining unit that determines an arteriosclerosis degree of the living body based on a pre-stored relationship between the ratio and the arteriosclerosis degree based on the ratio.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3221001A JP2938238B2 (en) | 1991-08-05 | 1991-08-05 | Atherosclerosis measuring device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3221001A JP2938238B2 (en) | 1991-08-05 | 1991-08-05 | Atherosclerosis measuring device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH0538332A true JPH0538332A (en) | 1993-02-19 |
| JP2938238B2 JP2938238B2 (en) | 1999-08-23 |
Family
ID=16759920
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP3221001A Expired - Fee Related JP2938238B2 (en) | 1991-08-05 | 1991-08-05 | Atherosclerosis measuring device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2938238B2 (en) |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7264594B2 (en) | 2004-05-14 | 2007-09-04 | Osachi Co., Ltd. | Cardiovascular dynamics evaluation apparatus |
| WO2010032293A1 (en) | 2008-09-17 | 2010-03-25 | 独立行政法人産業技術総合研究所 | Arterial wall hardness evaluation system |
| JP2012520102A (en) * | 2009-03-13 | 2012-09-06 | キング、ディヴィッド、エイチ． | Estimating hemodynamic data |
| CN106618517A (en) * | 2016-12-06 | 2017-05-10 | 山东大学 | Method for evaluating arterial elastic function through pulse waves on basis of arm position variation |
| CN109464137A (en) * | 2018-11-29 | 2019-03-15 | 东莞市康助医疗科技有限公司 | A kind of buck arterial stiffness evaluation method, system and device |
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Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
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| JP3553919B2 (en) * | 2001-12-12 | 2004-08-11 | コーリンメディカルテクノロジー株式会社 | Lower limb artery stenosis diagnostic device |
| JP5842107B2 (en) | 2011-10-19 | 2016-01-13 | パナソニックＩｐマネジメント株式会社 | Cardiodynamic measurement device |
-
1991
- 1991-08-05 JP JP3221001A patent/JP2938238B2/en not_active Expired - Fee Related
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7264594B2 (en) | 2004-05-14 | 2007-09-04 | Osachi Co., Ltd. | Cardiovascular dynamics evaluation apparatus |
| WO2010032293A1 (en) | 2008-09-17 | 2010-03-25 | 独立行政法人産業技術総合研究所 | Arterial wall hardness evaluation system |
| US9730594B2 (en) | 2008-09-17 | 2017-08-15 | National Institute Of Advance Industrial Science And Technology | Arterial-wall stiffness evaluation system |
| JP2012520102A (en) * | 2009-03-13 | 2012-09-06 | キング、ディヴィッド、エイチ． | Estimating hemodynamic data |
| CN106618517A (en) * | 2016-12-06 | 2017-05-10 | 山东大学 | Method for evaluating arterial elastic function through pulse waves on basis of arm position variation |
| CN106618517B (en) * | 2016-12-06 | 2020-12-08 | 山东大学 | Method for evaluating artery elasticity function based on pulse wave of arm position change |
| CN109464137A (en) * | 2018-11-29 | 2019-03-15 | 东莞市康助医疗科技有限公司 | A kind of buck arterial stiffness evaluation method, system and device |
| JP2021532953A (en) * | 2018-11-29 | 2021-12-02 | 東莞市康助医療科技有限公司 | Arterial stiffness display methods, systems and equipment |
| CN109464137B (en) * | 2018-11-29 | 2021-12-10 | 东莞市康助医疗科技有限公司 | Method, system and device for evaluating hardness of blood pressure reduction type artery |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2938238B2 (en) | 1999-08-23 |
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