JPS58133235A - Electronic hemomanometer - Google Patents
Electronic hemomanometerInfo
- Publication number
- JPS58133235A JPS58133235A JP57015701A JP1570182A JPS58133235A JP S58133235 A JPS58133235 A JP S58133235A JP 57015701 A JP57015701 A JP 57015701A JP 1570182 A JP1570182 A JP 1570182A JP S58133235 A JPS58133235 A JP S58133235A
- Authority
- JP
- Japan
- Prior art keywords
- blood pressure
- sound
- determined
- peak value
- 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】
本発明は、殊に最低血圧を正確且つ迅速に決定し得る電
子血圧計に関する。DETAILED DESCRIPTION OF THE INVENTION The present invention particularly relates to an electronic sphygmomanometer capable of accurately and quickly determining diastolic blood pressure.
一般に血圧を測定する場合、所謂コロトコフ音（以下に
音という）と称される血流が血管内壁に衝突する音を検
出し、このに音発生時の血圧値を最高血圧、Ｋ音消滅時
の血圧値を最低血圧としている。ところか被検者によっ
ては、Ｋ音が一時的に消滅して再発生する現象、すなわ
ち聴診間隙が生ずる場合があり、これが最低血圧を誤ま
って決定させる原因となっている。Generally, when measuring blood pressure, the so-called Korotkoff sound (hereinafter referred to as "sound"), the sound of blood flow colliding with the inner wall of a blood vessel, is detected, and the blood pressure value at the time of the sound is calculated as the systolic blood pressure and the sound when the K sound disappears. The blood pressure value is taken as the diastolic blood pressure. However, depending on the subject, a phenomenon in which the K sound temporarily disappears and then reappears, that is, an auscultation gap may occur, which causes erroneous determination of diastolic blood pressure.
そこで従来、Ｋ音消滅後−疋の時間若しくは一定の血圧
降下を待ち、Ｋ音の再発生があるか否かを確認し、これ
によりノμ°低血圧の決定を行なっている。ところが前
記の聴診間隙は全ての被検者に生ずる現象ではなく、従
って前記の待ち時間を十分長く設定することは、血圧測
定作業の能率を著しく低下させる結果となる。一方待ち
時間を短かく設定すると、Ｋ音の再発生を見逃す虞れが
あり、血圧測定の正確さを確保できない不利がある。Conventionally, therefore, after the disappearance of the K sound, the patient waits for a period of time or until the blood pressure drops to a certain extent, and then it is confirmed whether the K sound reappears or not, thereby determining the degree of hypotension. However, the above-mentioned auscultation gap does not occur in all subjects, and therefore, setting the above-mentioned waiting time to be sufficiently long will result in a significant decrease in the efficiency of blood pressure measurement work. On the other hand, if the waiting time is set short, there is a risk that the reoccurrence of the K sound may be missed, and there is a disadvantage that the accuracy of blood pressure measurement cannot be ensured.
本発明は、上記実情に鑑み、殊に最低血圧を正確且つ迅
速に決定できる電子血圧計を提供することを目的とする
ものであり、以下図面に示す実施例に基つき本発明を具
体的に説明する。In view of the above circumstances, it is an object of the present invention to provide an electronic blood pressure monitor that can specifically and quickly determine diastolic blood pressure. explain.
本発明は、Ｋ音の発生、および消滅が脈波ピーク値の増
減傾向と一定の関連があることに着目したものであり、
本発明の電子血圧計は第１図に示す如く、コロトコフ音
の発生を検出する第１センサ部１と、脈波を検出する第
２センサ部２と、第２センサ部２の出力レベルのピーク
値を検出して該ピーク値の増減傾向を判別する判別手段
３とを具備して成る。The present invention focuses on the fact that the occurrence and disappearance of the K sound have a certain relationship with the increase/decrease tendency of the pulse wave peak value,
As shown in FIG. 1, the electronic blood pressure monitor of the present invention includes a first sensor section 1 for detecting the occurrence of Korotkoff sounds, a second sensor section 2 for detecting pulse waves, and a peak of the output level of the second sensor section 2. It is equipped with a discriminating means 3 for detecting the peak value and discriminating the increasing/decreasing tendency of the peak value.
第１センサ部１は、マイクロホン等より成るに音センサ
１１の出力信号をバンドパスフィルタ１２を通過させ、
これを増幅器１３で増幅して、Ｋ音信号１１を取り出す
ものである。このに音信号１１は比較器４へ入力され、
基準値Ｖｏを越える信号レベルに対し［１−Ｉ Ｊレベ
ルとなるパルス出力１２を得る。The first sensor unit 1 passes the output signal of the sound sensor 11, which is composed of a microphone or the like, through a band-pass filter 12.
This is amplified by an amplifier 13 to extract a K sound signal 11. The sound signal 11 is then input to the comparator 4,
For a signal level exceeding the reference value Vo, a pulse output 12 of [1-I J level is obtained.
第２センサ部２は、圧力センサ、マイクロホン等より成
る脈波センサ２１の出力信号をバンドパスフィルタ２２
を通過させ、これを増幅器２３で増幅して、脈動する脈
波信号Ｊ１を取り出す。この脈波信号ｊ１はアナログ−
デジタル変換器５でサンプリングして、デジタル量のデ
ータ信号ｊ２に変換され、このデータ信号Ｊ２はマイク
ロプロセッサ６のシステムに含まれるメモリヘスドック
される。このデータは後記する如く、マイクロプロセッ
サ６へ読み込まれて、脈波信号Ｊｌのピーク値が順次チ
ェックされると共に、このピーク値が増大若しくは減少
の何れの傾向にあるかが判別される。The second sensor section 2 filters the output signal of the pulse wave sensor 21, which includes a pressure sensor, a microphone, etc., through a bandpass filter 22.
is passed through and amplified by an amplifier 23 to extract a pulsating pulse wave signal J1. This pulse wave signal j1 is an analog
The digital converter 5 samples and converts it into a digital data signal j2, and this data signal J2 is docked into the memory included in the microprocessor 6 system. As will be described later, this data is read into the microprocessor 6, and the peak value of the pulse wave signal Jl is sequentially checked, and it is determined whether the peak value tends to increase or decrease.
第２図はピーク値レベルの変動状況を示すと共に（第２
図（１）に示す）、Ｋ音にかかる＋１ｉｌ記パルス出力
（第２図（２）に示す）との対応関係を示しである。同
図において、脈波ピー り値は増大傾向（図中Ｘで示す
）と減少傾向（図中Ｙで示す）とを繰り返し呈するもの
であり、Ｋ音はこの増大傾向中に発生し、その発生時点
の血圧値を最大血圧Ｐ ｍａ ｘと決定される。またに
音は脈波ピーク値の減少傾向中に消滅し、その消滅時点
の血圧値を最低血圧Ｐｍ１ｎと決定されるが、ピーク値
の上昇傾向中にに音が一時消滅した場合、これを聴診間
隙Ｓと認定する。Figure 2 shows the fluctuation situation of the peak value level (the second
(1)) and the +1il pulse output applied to the K sound (shown in FIG. 2 (2)). In the figure, the pulse wave peak value repeatedly exhibits an increasing tendency (indicated by X in the figure) and a decreasing tendency (indicated by Y in the figure), and the K sound occurs during this increasing trend, and The blood pressure value at the time is determined as the maximum blood pressure Pmax. Additionally, the sound disappears while the pulse wave peak value is decreasing, and the blood pressure value at the time of its disappearance is determined to be the diastolic blood pressure Pm1n. However, if the sound temporarily disappears while the peak value is increasing, this can be checked by auscultation. It is recognized as gap S.
第３図は聴診間隙の判定動作を含む最低血圧を決定する
ための動作フローを示す。FIG. 3 shows an operation flow for determining the diastolic blood pressure, including an operation for determining the auscultation gap.
第３図において、ステップ７１は最高血圧が決定された
か否かを判定するもので、Ｋ音の発生によりステップ７
１の判定はＹＥＳとなり、つぎのステップ７２へ進む。In FIG. 3, step 71 is to determine whether the systolic blood pressure has been determined, and step 71 is determined by the generation of the K sound.
1 becomes YES, and the process proceeds to the next step 72.
またに音が発生していない状態では最高血圧は未だ決定
されておらず、従ってステップ７１の判定がＮｏとなり
、最高血圧決定待となる。Furthermore, in a state where no sound is generated, the systolic blood pressure has not yet been determined, and therefore the determination in step 71 is No, and the process waits for the systolic blood pressure to be determined.
ついでステップ７２において、脈波信号がデジタル量の
データ信号に変換され、更にステップ７３で脈波信号の
ピーク値が順次チェックされる。そしてステップ７３で
ピーク値と判定されたデータはステップ７４において、
マイクロプロセッサ６が内蔵するレジスタＭｎにセット
されると共に、該レジスタＭｎにセット中の前回のデー
タが他のレジスタＭｎ−＋ へ移される。Next, in step 72, the pulse wave signal is converted into a digital data signal, and further, in step 73, the peak values of the pulse wave signal are sequentially checked. Then, the data determined to be the peak value in step 73 is processed in step 74.
It is set in a register Mn built into the microprocessor 6, and the previous data being set in the register Mn is moved to another register Mn-+.
一方に音の発生間隔はタイマ等で常時監視されており、
タイムアツプにより一定時間以上に音の発生が途絶えた
とき、ステップ７５の判定がＹＥＳとなり、つぎのステ
ップ７６においてこのに音の消滅が聴診間隙によるもの
か否かが判定される。すなわちステップ７６は、レジス
タＭｎおよびＭｎ−＋のデータ内容を用いて、脈波ピー
ク値が増大若しくは減少の何れの傾向にあるかを判定す
るものであり、レジスタＭｎのデータ内容がレジスタＭ
ｎ−＋のデータ内容以上のとき増加傾向を判断できるか
ら、前記に音の途絶えは聴診間隙によると判定され、従
って最低血圧の測定動作が継続される。On the other hand, the interval between sounds is constantly monitored by a timer, etc.
When the generation of sound ceases for a certain period of time due to time-up, the determination in step 75 becomes YES, and in the next step 76, it is determined whether or not the disappearance of the sound is due to the auscultation gap. That is, step 76 uses the data contents of registers Mn and Mn-+ to determine whether the pulse wave peak value tends to increase or decrease.
Since an increasing tendency can be determined when the data content is equal to or greater than n-+, it is determined that the above-mentioned cessation of sound is due to the auscultation gap, and therefore the diastolic blood pressure measurement operation is continued.
一方レジスタＭｎの内容がレジスタＭｎ−＋の内容より
小さいとき、ピーク値は減少傾向と判断され、ステップ
７６の判定がＮＯとなってステップ７７へ進む。このス
テップ７７では、レジスタＭｎとレジスタＭｎ−＋との
データ内容の差が一定値α以」−か否かをチェックして
おり、ステップ７７の判定がＹＥＳのとき、前記に音の
消滅時点をもって最低血圧を決定し、一方ステップ７７
の判定がＮｏのとき、Ｋ音の途絶えを聴診間隙によるも
のと認定して、最低血圧の測定動作を継続させる。On the other hand, when the contents of register Mn are smaller than the contents of register Mn-+, it is determined that the peak value tends to decrease, and the determination in step 76 becomes NO, and the process proceeds to step 77. In this step 77, it is checked whether the difference in data contents between the register Mn and the register Mn-+ is equal to or less than a certain value α'-, and when the determination in step 77 is YES, the point at which the sound disappears is Determine the diastolic blood pressure while step 77
When the determination is No, the discontinuation of the K sound is recognized as being caused by the auscultation gap, and the diastolic blood pressure measurement operation is continued.
本発明は上記の如く構成したから、Ｋ音の消滅が聴診間
隙によるものか否かを容易に判定でき、従って最低血圧
を誤認することなく正確且つ迅速に決定できる等、発明
目的を達成した優れた効果を奏する。Since the present invention is configured as described above, it is possible to easily determine whether the disappearance of the K sound is due to the auscultation gap, and therefore, the diastolic blood pressure can be accurately and quickly determined without misidentifying it. It has a great effect.
第１図は本発明にかかる電子血圧計の回路構成を示すブ
ロック図、第２図は本発明の原理を示す説明図、第３図
は電子血圧計の動作を示す流れ図である。
■・・・・・・第１センサ部 ２・・・・・・第２セン
サ部３・・・・・・判別手段
特許出願人 立石電機株式会社FIG. 1 is a block diagram showing the circuit configuration of an electronic blood pressure monitor according to the present invention, FIG. 2 is an explanatory diagram showing the principle of the present invention, and FIG. 3 is a flowchart showing the operation of the electronic blood pressure monitor. ■...First sensor part 2...Second sensor part 3...Discrimination means patent applicant Tateishi Electric Co., Ltd.
Claims (1)
検出する第２センサ部と、第２センサ部の出力レベルの
ピーク値を順次検出して該ピーク値の増減傾向を判別す
る判別手段とを具備して成る電子血圧計。A first sensor section that detects the occurrence of Korotkoff sounds, a second sensor section that detects pulse waves, and a determining means that sequentially detects peak values of the output levels of the second sensor sections and determines trends in increases and decreases in the peak values. An electronic blood pressure monitor comprising:
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57015701A JPS58133235A (en) | 1982-02-02 | 1982-02-02 | Electronic hemomanometer |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57015701A JPS58133235A (en) | 1982-02-02 | 1982-02-02 | Electronic hemomanometer |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS58133235A true JPS58133235A (en) | 1983-08-08 |
| JPH0344767B2 JPH0344767B2 (en) | 1991-07-09 |
Family
ID=11896068
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57015701A Granted JPS58133235A (en) | 1982-02-02 | 1982-02-02 | Electronic hemomanometer |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS58133235A (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6060833A (en) * | 1983-09-14 | 1985-04-08 | 松下電工株式会社 | Hemomanometer |
| JPS63246137A (en) * | 1988-01-26 | 1988-10-13 | 松下電工株式会社 | Electronic hemomanometer |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS55134808U (en) * | 1979-03-15 | 1980-09-25 | ||
| JPS573293A (en) * | 1980-06-06 | 1982-01-08 | Nec Corp | Delay circuit |
-
1982
- 1982-02-02 JP JP57015701A patent/JPS58133235A/en active Granted
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS55134808U (en) * | 1979-03-15 | 1980-09-25 | ||
| JPS573293A (en) * | 1980-06-06 | 1982-01-08 | Nec Corp | Delay circuit |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6060833A (en) * | 1983-09-14 | 1985-04-08 | 松下電工株式会社 | Hemomanometer |
| 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 |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0344767B2 (en) | 1991-07-09 |
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