JPS647784B2 - - Google Patents
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- Publication number
- JPS647784B2 JPS647784B2 JP56008111A JP811181A JPS647784B2 JP S647784 B2 JPS647784 B2 JP S647784B2 JP 56008111 A JP56008111 A JP 56008111A JP 811181 A JP811181 A JP 811181A JP S647784 B2 JPS647784 B2 JP S647784B2
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- Prior art keywords
- airway
- sound waves
- subject
- intensity
- sound wave
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- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は呼吸器系の気道抵抗、特に上気道の気
道抵抗を簡単に評価・測定するための装置に関ん
する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a device for easily evaluating and measuring airway resistance in the respiratory system, particularly in the upper respiratory tract.
気道抵抗を測定することは、閉塞性疾患や喘息
等の呼吸器系の診断と治療に極めて重要であり、
その内の測定方法でオシレーシヨン法が一般的で
ある。
Measuring airway resistance is extremely important for the diagnosis and treatment of respiratory diseases such as obstructive diseases and asthma.
Among these measurement methods, the oscillation method is common.
このオシレーシヨン法は、スピーカーにより10
Hzの正弦波圧を気道に与えて圧検出装置によつて
通気管内の流速および口腔内圧を測定して気道抵
抗を得るようにしている。 This oscillation method uses 10
A sinusoidal pressure of Hz is applied to the airway, and a pressure detection device measures the flow velocity in the ventilation pipe and the intraoral pressure to obtain the airway resistance.
このオシレーシヨン法では、上気道と下気道を
含む全気道抵抗を測定するために閉塞性疾患や喘
息等の原因が気道のどの個所にあるかを明らかに
することはできず、診断および治療上必ずしも十
分な測定方法であるとはいえない。
Since this oscillation method measures the total airway resistance including the upper and lower airways, it is not possible to determine where in the airway the cause of obstructive disease or asthma is located, and it is not always necessary for diagnosis and treatment. It cannot be said that this is a sufficient measurement method.
そこで、上気道部分の気道抵抗のみ測定するた
めの被検者の呼吸による流速および上気道をはさ
む上下部における気道内の圧力差を検出してこれ
ら流速および圧力差から、上気道の抵抗値を算出
するものが開発されている。しかしこの測定方法
では、上気道下部の気道内圧力を検出するために
被検者の頚部から声帯の下側気管内に細い管を刺
し込む必要があり、臨床上一般に受け入れられる
ものではない。 Therefore, in order to measure only the airway resistance in the upper airway, we detect the flow velocity caused by the subject's breathing and the pressure difference in the upper and lower airways that sandwich the upper airway, and from these flow velocity and pressure difference, we calculate the resistance value of the upper airway. A method has been developed to calculate this. However, this measurement method requires a thin tube to be inserted from the subject's neck into the trachea below the vocal cords in order to detect the airway pressure in the lower part of the upper respiratory tract, and is not generally accepted clinically.
本発明は、通気管を介して被検者の気道内に低
周波数の音波を負荷するための音波発生装置と、
この音波発生装置により負荷された音波の強さを
被検者の気道に沿つた外皮上で検出するための振
動検出装置とを有し、さらに必要に応じてこの振
動検出装置からの信号の内上記低周波音波を主と
して検出するためのフイルターを設けたことを特
徴とする。
The present invention provides a sound wave generator for applying low-frequency sound waves into the respiratory tract of a subject through a ventilation pipe;
It has a vibration detection device for detecting the intensity of the sound waves applied by this sound wave generator on the outer skin along the respiratory tract of the subject, and further includes a vibration detection device for detecting the intensity of the sound waves applied by this sound wave generator on the outer skin along the airway of the subject, and further includes a The present invention is characterized in that a filter is provided for mainly detecting the low frequency sound waves.
以上の本発明によると、被検者の気道に低周波
数の音波を与えると共に、気道に沿つた所望位置
の被検者の外皮上に取り付けた振動検出装置によ
つて、この音波の強さを測定し、この音波の強さ
の変化状態からその間の気道抵抗の変化を評価お
よび測定するものである。
According to the present invention, a low-frequency sound wave is applied to the airway of a subject, and the intensity of the sound wave is detected by a vibration detection device attached to the outer skin of the subject at a desired position along the airway. This method evaluates and measures the change in airway resistance from the state of change in the intensity of this sound wave.
以下に本発明の一実施例を図面を用いて説明す
る。
An embodiment of the present invention will be described below with reference to the drawings.
第１図はブロツクダイアグラムであり、図にお
いて、１は通気管で一端は被検者が口にくわえる
か鼻に接続して気道２に接続するようになつてい
る。また通気管１の他端は厚板などで形成した密
閉状の筐体３と、この筐体３の内部に向けて取り
付けたスピーカー４とこのスピーカー４を作動す
るためのアンプ５とからなる音波発生装置６に通
じており例えば、400Hz、600Hz、900Hzなどの適
宜低周波数の音波を被検者の気道２内に向けて発
するようになつている。 FIG. 1 is a block diagram, and in the figure, 1 is a ventilation tube, one end of which is connected to the airway 2 by being held in the mouth or nose by the subject. The other end of the ventilation pipe 1 is made up of a sealed casing 3 made of a thick plate or the like, a speaker 4 attached toward the inside of the casing 3, and an amplifier 5 for operating the speaker 4. It communicates with a generator 6 and emits sound waves at appropriate low frequencies, such as 400 Hz, 600 Hz, and 900 Hz, toward the airway 2 of the subject.
７はバイヤスフローのための排気管で通気管１
内に呼び出された被検者の呼気を吸引ポンプ８に
よつて除去して通気管１内の換気を行う。９は、
筐体３に設けたバイヤスフローのための空気取入
れ口である。 7 is an exhaust pipe for bias flow and ventilation pipe 1
The ventilation tube 1 is ventilated by removing the patient's exhaled breath drawn into the ventilation tube 1 by a suction pump 8. 9 is
This is an air intake for bias flow provided in the housing 3.
１０は、マイクロフオン若しくは加速度計型ピ
ツクアツプ等の振動検出器で被検者の気道に沿つ
た適宜位置の外皮に取り付けるようになつており
図では胸骨上辺の外皮に取り付けてある。１１は
振動検出器１０からの信号のうち主として前記音
波発生装置６によつて発せられた低周波数の音波
を取り出すための例えばf0＝600Hz、48dB／oct
のバンドパスフイルターで、１２は検出した低周
波音波の強さを記録し或いはデジタル表示するた
めのデイスプレー機構である。 Reference numeral 10 denotes a vibration detector such as a microphone or an accelerometer type pickup, which is attached to the outer skin at an appropriate position along the airway of the subject, and is attached to the outer skin above the sternum in the figure. Reference numeral 11 is for extracting low-frequency sound waves mainly emitted by the sound wave generator 6 from among the signals from the vibration detector 10, for example, f 0 =600Hz, 48dB/oct.
12 is a display mechanism for recording or digitally displaying the intensity of the detected low frequency sound waves.
本実施例は以上のように構成されており、口呼
吸をさせた被検者の気道に適宜周波数の音波を加
えるのであるが、この音波の強さは気道の抵抗に
応じて次第に減少していくため、被検者の気道に
沿つた適宜位置例えば第１図に示す胸骨上辺の外
皮に取付けた振動検出器１０によつて与えられた
音波の強さを測定することによつて、口から振動
検出器１０の取付け位置に至る間の気道抵抗を上
記音波の減少度合いから評価・測定するものであ
る。 The present embodiment is configured as described above, and a sound wave of an appropriate frequency is applied to the airway of a subject who is breathing through the mouth, but the intensity of this sound wave gradually decreases depending on the resistance of the airway. For example, by measuring the intensity of the sound waves applied by a vibration detector 10 attached to the outer skin of the upper part of the sternum as shown in FIG. The airway resistance while reaching the mounting position of the vibration detector 10 is evaluated and measured from the degree of reduction of the sound waves.
ここで、音波の強さの減少の度合いと、気道抵
抗との関係を明らかにする実験を行つたので以下
に説明する。 Here, we conducted an experiment to clarify the relationship between the degree of reduction in the intensity of sound waves and airway resistance, which will be explained below.
第２図は、実験に用いた装置のブロツクダイヤ
グラムであり、本発明による音波の強さを測定す
るための第１図に示した機構の他に通気管１内の
流速を測定するための流速検出装置１３とバンド
パスフイルター１３′、および口腔内圧を測定す
るための圧検出装置１４とバンドパスフイルター
１４′および気道内に向けて、10Hzの正弦波圧を
与えるためのスピーカー１５が設けてあり、実施
例と同様に、スピーカー４により気道に音波を与
えて気道に沿つた外皮上で、音波の強さを測定す
ると同時に10Hzの正弦波圧を加えてこの正弦波圧
によつてもたらされる流速および口腔内圧を検出
して気道抵抗を測定するいわゆる従来公知のオシ
レーシヨン法による測定が出来るようになつてい
る。 FIG. 2 is a block diagram of the apparatus used in the experiment, in which, in addition to the mechanism shown in FIG. A detection device 13, a bandpass filter 13', a pressure detection device 14 and a bandpass filter 14' for measuring intraoral pressure, and a speaker 15 for applying a 10Hz sine wave pressure to the airway are provided. , as in the example, a sound wave is applied to the airway by the speaker 4 and the intensity of the sound wave is measured on the outer skin along the airway, and at the same time, a 10 Hz sine wave pressure is applied and the flow velocity caused by this sine wave pressure is measured. It has also become possible to measure airway resistance by the so-called conventionally known oscillation method, which measures airway resistance by detecting intraoral pressure.
この装置を用いて発明者は以下の実験を行つ
た。被検者の鼻をノーズクリツプで閉塞させ、通
気管１の先端をくわえさせて、被検者に通気管１
を通じて呼吸させた。本発明に用いる振動検出器
１０を、被検者の胸骨上辺の外皮に粘着テープで
取付けるとともにスピーカー４により600Hzの低
周波数音波を気道に与えて、この音波の強さを、
デイスプレー１２で得るようにした。なお、同時
に、スピーカー１５により、10Hzの正弦波圧を気
道に与えて流速測定装置１３とバンドパスフイル
ター１３′および圧検出装置１４とバンドパスフ
イルター１４′によつて、それぞれ、前記10Hzの
正弦波圧による通気管１内の流速および口腔内圧
を測定し気道抵抗を得るようにした。 Using this device, the inventor conducted the following experiments. Obstruct the subject's nose with a nose clip, have the subject hold the tip of the vent tube 1 in their mouth, and have the subject insert the vent tube 1 into their mouth.
Breathed through. The vibration detector 10 used in the present invention is attached to the outer skin of the subject's upper sternum with adhesive tape, and a low frequency sound wave of 600 Hz is applied to the respiratory tract by the speaker 4, and the intensity of the sound wave is
I made it possible to obtain it with display 12. At the same time, a 10 Hz sine wave pressure is applied to the airway by the speaker 15, and the 10 Hz sine wave is applied to the airway by the flow velocity measuring device 13 and the band pass filter 13', and the pressure detecting device 14 and the band pass filter 14', respectively. The airway resistance was determined by measuring the flow velocity in the ventilation tube 1 and the intraoral pressure.
測定は、被検者に平常呼吸の呼気終了時、即ち
機能的残気量の状態で呼吸を停止させることによ
り下水道の動きを停止させ、更にこの状態で声帯
を平常の開放状態から閉塞状態に閉じさせること
によつて上気道の気道抵抗のみを増加させて、そ
の過程を測定した。 The measurement is performed by having the subject stop breathing at the end of exhalation during normal breathing, that is, in a state of functional residual capacity, to stop the movement of the sewer, and in this state, the vocal cords are changed from the normal open state to the occluded state. By closing the airway, only the airway resistance of the upper airway was increased, and the process was measured.
第３図Ａは、上気過程において、流速検出装置
１３、バンドパスフイルター１３′で検出した10
Hzの正弦波圧による口腔内流速の変化を示し、１
６は声帯を平常に開放している時点を、また１７
は声帯を閉塞した時点をそれぞれ示している。 Figure 3A shows the 10 detected by the flow rate detector 13 and bandpass filter 13' in the upper air process.
It shows the change in intraoral flow velocity due to Hz sinusoidal pressure, 1
6 indicates the point when the vocal cords are opened normally, and 17
indicates the time point at which the vocal cords were occluded.
また、第３図Ｂは、振動検出器１０およびf0＝
600Hz、48dB／octのバンドパスフイルター１１
によつて検出した600Hzの音波の強さの変化を示
す包絡線、１８は声帯を平常に開放している時点
を、また１９は声帯を閉塞した時点をそれぞれ示
している。第３図ＡおよびＢから明らかなよう
に、両者に極めて相関性が認められ、また、声帯
の開閉即ち、気道抵抗の増加に伴い、口腔内流速
および音波の強さがいずれも順次低下して行き声
帯が完全に閉塞した時点ではいずれも殆どゼロに
なつた。 Further, FIG. 3B shows the vibration detector 10 and f 0 =
600Hz, 48dB/oct bandpass filter 11
Envelopes showing changes in the intensity of the 600 Hz sound waves detected by the method, 18 shows the time when the vocal cords are normally open, and 19 shows the time when the vocal cords are closed. As is clear from Figures 3A and B, there is a strong correlation between the two, and as the vocal cords open and close, that is, the airway resistance increases, both the intraoral flow velocity and the sound wave intensity gradually decrease. When the leading vocal cords were completely occluded, both levels became almost zero.
また、第４図Ａは、声帯を平常の開放状態から
閉塞状態に閉じていく間にオシレーシヨン法によ
つて測定した気道抵抗の増加量即ち、上気道の抵
抗の増加量を示し、第４図Ｂは声帯が平常に開放
されている時点において、検出した音波の強さに
対し、声帯を閉塞して行く経過において検出した
音波の強さを％で表示したもので、上気道の抵抗
を次第に増加させた時の声帯を平常に開放した状
態に対する音波の強さの度合いを示すが、これら
第４図ＡおよびＢから、気道抵抗の増加と、検出
した音波の強さの度合いとの間には、極めて相関
性があることが分かつた。即ち、音波の強さの度
合いをＹ％とし、オシレーシヨン法で得た抵抗値
の増加量をＸcmH2O／／secとすると、ＹとＸ
とは次式(1)に従つて反比例することがわかつた。 In addition, Fig. 4A shows the amount of increase in airway resistance, that is, the amount of increase in upper airway resistance, measured by the oscillation method while the vocal cords are closed from the normal open state to the closed state. B shows the strength of the sound waves detected as the vocal cords are closed, expressed as a percentage of the strength of the sound waves detected when the vocal cords are normally open, and gradually increases the resistance of the upper airway. Figure 4 A and B show that there is a difference between the increase in airway resistance and the intensity of the detected sound waves. were found to be highly correlated. In other words, if the intensity of the sound wave is Y% and the amount of increase in resistance value obtained by the oscillation method is XcmH 2 O//sec, then Y and X
was found to be inversely proportional to the following equation (1).
Ｙ＝−7.35X＋98.9 (1)
また第５図は、スピーカー４により気道に与え
る音波の周波数を、100Hzから1000Hzまで、100Hz
ごとに変えて測定した時の声帯を閉塞した状態で
検出した音波の強さに対する声帯を平常に開放し
た状態で検出した音波の強さの比率を示すグラフ
で、600Hzおよび700Hzにおいて値が大きくこの付
近の周波数の音波が気道抵抗の増加に対する音波
の減少の度合いを顕著にとらえることが出来るこ
とが分かつた。 Y = −7.35
This is a graph showing the ratio of the strength of the sound waves detected with the vocal cords normally open to the strength of the sound waves detected with the vocal cords closed, when measured at different times. It was found that the degree of decrease in sound waves in response to increases in airway resistance can be clearly detected using sound waves at nearby frequencies.
以上述べた如く、気道に音波を与えたときの気
道に沿つた所望位置での音波の強さを測定するこ
とによつて口から振動検出位置に至る気道内の抵
抗を評価することが出来る。 As described above, by measuring the intensity of the sound wave at a desired position along the airway when a sound wave is applied to the airway, it is possible to evaluate the resistance within the airway from the mouth to the vibration detection position.
また、あらかじめ一定の周波数の音波の検出位
置に対して、気道抵抗の変化量と、音波の強さの
変化の度合との間の式(1)に相当する関係式を求め
ておけば本発明の方法によつて求めた音波の強さ
の変化の度合から気道抵抗の変化量を容易に求め
ることができるので、例えば気道に刺激を加え
て、その刺激に対する気道抵抗の変化を見る気道
過敏性テストにおいて、上気道のみの抵抗の変化
量を簡単にとらえることができ、診断および治療
に極めて有効である。 In addition, if a relational expression corresponding to equation (1) between the amount of change in airway resistance and the degree of change in the intensity of the sound wave is determined in advance for the detection position of a sound wave of a certain frequency, the present invention can be applied. The amount of change in airway resistance can be easily determined from the degree of change in the strength of the sound waves determined by the method described above. The test can easily measure the amount of change in resistance only in the upper respiratory tract, making it extremely effective for diagnosis and treatment.
以上本発明について説明したが、本発明は上記
実施例に限定するものではなく、低周波音波とし
ては、測定個所および、目的等に応じて適切な周
波数の音波を使用してもよい。また、振動検出器
は胸骨上辺の外皮以外の位置に取り付けてもよ
く、複数個所に取付けてもよい。 Although the present invention has been described above, the present invention is not limited to the above embodiments, and as the low-frequency sound waves, sound waves with appropriate frequencies may be used depending on the measurement location and purpose. Further, the vibration detector may be attached to a position other than the outer skin on the upper side of the sternum, or may be attached to multiple locations.
また、気道に音波を与えるに際しては必ずしも
口を介して行う必要はなく、鼻孔を介して行つて
もよい。 Further, when applying sound waves to the respiratory tract, it is not necessarily necessary to apply the sound waves through the mouth, but it may be applied through the nostrils.
以上説明した本発明によると、通気管を介して
被検者の気道内に低周波数の音波を負荷するため
の音波発生装置と、この音波発生装置により負荷
された音波の強さを被検者の気道に沿つた外皮上
で検出するための振動検出装置とを設けたことに
より、振動検出装置の検出する音波の変化状態か
ら上気道や下気道の個別の個所の気道抵抗の変化
量をとらえることができ、診断および治療に極め
て有効となる。
According to the present invention described above, there is provided a sound wave generator for applying low-frequency sound waves into the respiratory tract of a subject through a ventilation pipe, and the intensity of the sound waves applied by the sound wave generator is transmitted to the subject. By installing a vibration detection device to detect on the outer skin along the airway of the patient, the amount of change in airway resistance at individual points in the upper and lower airways can be determined from the change state of the sound waves detected by the vibration detection device. This makes it extremely effective for diagnosis and treatment.
第１図は本発明の一実施例を示すブロツクダイ
ヤグラム、第２図は他の実施例のブロツクダイヤ
グラム、第３図Ａは流速検出装置で検出した10Hz
の正弦波圧によつてもたらされる口腔内流速変化
を示すグラフ、第３図Ｂは振動検出器によつて検
出した音波の強さの変化を示す包絡線によるグラ
フ、第４図Ａはオシレーシヨン法で測定した上気
道の抵抗の増加量を示すグラフ、第４図Ｂは声帯
が開いている状態の音波の強さに対する声帯を閉
じて行く過程における音波の強さを％で表示した
グラフ、第５図は声帯を閉じた状態で検出した音
波の強さに対する声帯を開いた状態で検出した音
波の強さの比率を示したグラフである。
１……通気管、２……気道、６……音波発生装
置、１０……振動検出器、１１……バンドパスフ
イルター。
Figure 1 is a block diagram showing one embodiment of the present invention, Figure 2 is a block diagram of another embodiment, and Figure 3A is a flow rate of 10 Hz detected by a flow rate detector.
Figure 3B is a graph showing the change in the intensity of the sound wave detected by the vibration detector, and Figure 4A is a graph showing the change in the intraoral flow velocity caused by the sinusoidal pressure of the oscillation method. Figure 4B is a graph showing the increase in resistance of the upper airway measured in Figure 4. FIG. 5 is a graph showing the ratio of the intensity of the sound wave detected with the vocal cords open to the intensity of the sound wave detected with the vocal cords closed. 1... Ventilation pipe, 2... Airway, 6... Sound wave generator, 10... Vibration detector, 11... Band pass filter.
Claims (1)
音波を負荷するための音波発生装置と、この音波
発生装置により負荷された音波の強さを被検者の
気道に沿つた外皮上で検出するための振動検出装
置とを有し、さらに上記低周波数の音波を主とし
て検出するためのフイルターを設け、気道抵抗の
変化に伴う気道に沿つた位置における上記低周波
数音波の強さの変化を検出して気道抵抗を評価・
測定するための装置。1 A sound wave generator for applying low-frequency sound waves into the airway of the subject through a ventilation tube, and a sound wave generator that transmits the intensity of the sound waves applied to the subject's airway onto the outer skin along the airway of the subject. and a filter for mainly detecting the low frequency sound waves, the change in the intensity of the low frequency sound waves at a position along the airway due to changes in airway resistance. Detect and evaluate airway resistance
Equipment for measuring.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56008111A JPS57122846A (en) | 1981-01-23 | 1981-01-23 | Method and apparatus for estimating and measuring trachea resistance |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP56008111A JPS57122846A (en) | 1981-01-23 | 1981-01-23 | Method and apparatus for estimating and measuring trachea resistance |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS57122846A JPS57122846A (en) | 1982-07-30 |
| JPS647784B2 true JPS647784B2 (en) | 1989-02-10 |
Family
ID=11684177
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP56008111A Granted JPS57122846A (en) | 1981-01-23 | 1981-01-23 | Method and apparatus for estimating and measuring trachea resistance |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS57122846A (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU2005237191A1 (en) * | 2004-05-04 | 2005-11-10 | Dalhousie University | Method of assessment of airway variability in airway hyperresponsiveness |
| WO2006130922A1 (en) * | 2005-06-10 | 2006-12-14 | Telethon Institute For Child Health Research | A method of measuring an acoustic impedance of a respiratory system and diagnosing a respiratory disease or disorder or monitoring treatment of same |
| WO2020093176A1 (en) * | 2018-11-09 | 2020-05-14 | Thorasys Thoracic Medical Systems Inc. | Modular oscillometry device with dynamic calibration |
-
1981
- 1981-01-23 JP JP56008111A patent/JPS57122846A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS57122846A (en) | 1982-07-30 |
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