JP2009060989A - Respiration monitoring method and apparatus - Google Patents
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Abstract
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本発明は、超広帯域無線波(UWB波:Ultra Wide Band )を用いて、集中治療室などにおける複数の患者といった被検者の呼吸を同時に、非接触かつ無拘束で監視する呼吸監視方法及びそのための装置に関する。 The present invention relates to a respiratory monitoring method for simultaneously monitoring non-contact and unrestrained breathing of a subject such as a plurality of patients in an intensive care unit using an ultra wide band (UWB wave). Relating to the device.
UWB波たとえばUWB−IR(Ultra Wide Band-Impulse Radio)は、10dB比帯域幅が中心周波数の20%以上又は500MHz以上の広い周波数帯域を使用する処から非常に短いパルス幅となり、パルス分解能が高くマルチパス耐性に優れている。また、広帯域である処から電力スペクトル密度が10nW/MHzときわめて低く、他の通信システムとの共存が可能である。 UWB waves such as UWB-IR (Ultra Wide Band-Impulse Radio) have a very short pulse width and a high pulse resolution because a 10 dB relative bandwidth is 20% or more of the center frequency or a wide frequency band of 500 MHz or more. Excellent multipath resistance. In addition, the power spectral density is as low as 10 nW / MHz because of its wide bandwidth, and it can coexist with other communication systems.
一方、病室や集中治療室における患者の呼吸監視のために、患者の胸部に直接電極を貼付したり口や鼻にサーミスタを取り付けるといった方法が採られている。このような接触式或いは配線が必要なセンサは、患者に不快感を与えたり体位の変動などによるセンサの離脱事故を起こしたりするほか介護/看護の妨げになったりする問題がある。 On the other hand, in order to monitor a patient's breathing in a hospital room or an intensive care unit, a method is adopted in which an electrode is directly attached to the chest of the patient or a thermistor is attached to the mouth or nose. Such a sensor that requires contact or wiring has problems that cause discomfort to the patient, cause a sensor detachment accident due to a change in body posture, and hinder care / nursing.
また、無呼吸症候群などへの社会的関心の高まりから、ベッドのマット下に圧力センサを取り付けて無拘束で呼吸運動を監視する方法(たとえば、特許文献1参照)や、患者の枕元に取り付けた画像取得・処理装置やレーザセンサにより呼吸を監視する方法も提案されている。しかし、特許文献1に開示の方法による場合、体動などによる低周波変動も含まれ微妙な呼吸運動を検出するのは困難であり、また、患者の枕元に画像取得・処理装置やレーザセンサを臨ませる方法は、体動による患者の位置変化に対して自動的に対応できない。
In addition, due to increasing social interest in apnea syndrome and the like, a pressure sensor is attached under the mat of the bed to monitor the breathing movement without restraint (for example, see Patent Document 1) or attached to the patient's bedside. A method of monitoring respiration using an image acquisition / processing device or a laser sensor has also been proposed. However, according to the method disclosed in
さらに、マイクロ波センサを用いてドップラ効果の観測や測距を行い被検者の動きを検出する方法(たとえば、特許文献2乃至特許文献6参照)や、ビーム幅が狭い微弱無線で体動を検出する方法も提案されている(たとえば、特許文献7参照)。しかし、室内のように厳しいマルチパス環境下で、人間の微妙な呼吸を検出することは難しい。また、これら従来の方法は、患者毎にセンサと付属装置が必要である。 Further, a method of detecting the movement of the subject by observing the Doppler effect and ranging using a microwave sensor (for example, see Patent Document 2 to Patent Document 6), or a weak radio with a narrow beam width for body movement. A detection method has also been proposed (see, for example, Patent Document 7). However, it is difficult to detect subtle human breathing in a harsh multipath environment such as indoors. Moreover, these conventional methods require a sensor and an attached device for each patient.
本発明は、室内における複数のたとえば患者といった被検者の呼吸運動を同時に、非接触かつ無拘束で検出し、呼吸数や異常呼吸を、必要に応じて監視モニタに表示しまた、自動警報装置を介して医師や看護師に知らせる方法及びそのための装置を提供することを目的とする。 The present invention simultaneously detects a respiratory motion of a plurality of subjects such as patients in a room at the same time without contact and without restraint, and displays a respiratory rate and abnormal breathing on a monitor monitor as necessary. It is an object of the present invention to provide a method for informing doctors and nurses via the device and a device therefor.
上記課題を解決するための請求項1に記載の発明は、超広帯域無線波(UWB波)を被検者に向けて発信し、反射波の受信信号から前置増幅/検波器によって遅延プロファイルを得、該遅延ファイルをA/D変換した後、信号処理部で反射波毎に信号強度の時間変動として観測し、そのうち変動幅が顕著かつ周期性をもつパスを被検者の呼吸に起因する体動によるものと特定し、被検者の呼吸数又は異常呼吸を検出するようにした呼吸監視方法である。
In order to solve the above-mentioned problem, the invention according to
請求項2に記載の発明は、超広帯域無線波発振器と、超広帯域無線波送受信アンテナと、受信信号を増幅、検波し遅延プロファイルを得る前置増幅/検波器と、遅延プロファイル信号をデジタル化するA/D変換器と、A/D変換された遅延プロファイルから反射波毎に信号強度の時間変動を出力する信号処理部とを有する呼吸監視装置である。 The invention according to claim 2 is an ultra-wideband radio wave oscillator, an ultra-wideband radio wave transmitting / receiving antenna, a preamplifier / detector for amplifying and detecting a received signal to obtain a delay profile, and digitizing the delay profile signal The respiratory monitoring device includes an A / D converter and a signal processing unit that outputs a temporal variation in signal intensity for each reflected wave from the A / D converted delay profile.
本発明によれば、同時に複数の被検者の呼吸運動を非接触かつ無拘束で検出し、呼吸数又は異常呼吸を知ることができる。また、検出結果は遠方の監視モニタへ無線で伝送し、呼吸異常を検出した場合は自動警報装置を作動させ、緊急事態を医師や看護師に迅速に知らせることができる。 According to the present invention, the respiratory motion of a plurality of subjects can be detected simultaneously without contact and without restraint, and the respiratory rate or abnormal breathing can be known. In addition, the detection result is wirelessly transmitted to a distant monitoring monitor, and when an abnormal breathing is detected, an automatic alarm device is activated to promptly notify an emergency situation to a doctor or nurse.
本発明は、超広帯域無線波(UWB波)を用いて室内における複数の被検者の呼吸運動を非接触かつ無拘束で同時に検出する呼吸監視システムである。図1に、本発明の呼吸監視システムの概要を示す。図1に示すように、たとえば室内の天井に配設された発信アンテナ3からUWB波が被検者(患者等)Pに向けて発信され、反射波が受信アンテナ3によって受けられる。 The present invention is a respiratory monitoring system that simultaneously detects a respiratory motion of a plurality of subjects in a room using an ultra-wideband radio wave (UWB wave) without contact and without restraint. FIG. 1 shows an outline of the respiratory monitoring system of the present invention. As shown in FIG. 1, for example, a UWB wave is transmitted toward a subject (patient or the like) P from a transmitting antenna 3 disposed on the ceiling of the room, and a reflected wave is received by the receiving antenna 3.
図2に、本発明の呼吸監視装置の構成を示す。図2に示すように、本発明の呼吸監視装置は、超広帯域無線波発振器2および発受信アンテナ3からなる発信部1、発受信切換器(ハイブリッド)4、ならびに発受信アンテナ3からの受信信号から遅延プロファイルを検出するための前置増幅器/検波器6、A/D変換器7、および信号処理部8からなる受信部5、受信部5で得られた呼吸波形データを遠方の監視モニタへ伝送する転送アンテナ9から構成されている。
FIG. 2 shows the configuration of the respiratory monitoring apparatus of the present invention. As shown in FIG. 2, the respiratory monitoring apparatus of the present invention includes a
発信部1は、インパルス状モノサイクル波、ステップドFM波、またはFM−CW波、またはスペクトル拡散波を発振する超広帯域無線波発振器2と発受信アンテナ3から構成されている。一方、受信部5は、受信アンテナ3、前置増幅器/検波器6、A/D変換器7、およびデジタル信号処理部8から構成されている。
The
UWB波が送信アンテナ3から被検者(患者等)Pに向けて発信され、受信した信号から検波した遅延プロファイルはA/D変換された後、信号処理部8において反射波(遅延時間)毎に信号強度の時間変動として観測され、被検者(患者等)Pの呼吸数または呼吸異常が検出される。 The UWB wave is transmitted from the transmitting antenna 3 toward the subject (patient or the like) P, and the delay profile detected from the received signal is A / D converted and then reflected by the signal processing unit 8 for each reflected wave (delay time). Is observed as a time fluctuation of the signal intensity, and the respiratory rate or respiratory abnormality of the subject (patient or the like) P is detected.
遅延プロファイルは、被検者や障害物からの遅延反射波の合成波である。遅延プロファイルはA/D変換され、帯域幅に応じてマルチパスが時間または距離軸上で分離、識別され、各パスの信号強度が信号処理部8に入力される。図3に、遅延プロファイルの一実施例を示す。この遅延プロファイルの距離分解能は、発信帯域幅に比例する。たとえば5GHzでは距離分解能が6cmの遅延プロファイルが得られ、経路長差が6cm以上の反射波を時間軸上で分離・識別ができる。即ち、アンテナから各被検者までの経路長差が6cm以上離れていれば、同時に複数の被検者の呼吸運動を検出できる。 The delay profile is a composite wave of delayed reflected waves from the subject and the obstacle. The delay profile is A / D converted, multipaths are separated and identified on the time or distance axis according to the bandwidth, and the signal strength of each path is input to the signal processing unit 8. FIG. 3 shows an example of the delay profile. The distance resolution of this delay profile is proportional to the transmission bandwidth. For example, at 5 GHz, a delay profile with a distance resolution of 6 cm can be obtained, and reflected waves with a path length difference of 6 cm or more can be separated and identified on the time axis. That is, if the path length difference from the antenna to each subject is 6 cm or more, the respiratory motion of a plurality of subjects can be detected simultaneously.
次に、A/D変換された遅延プロファイルの各標本値は発信毎に観測され、その時間的変化から周期性を検出する。たとえば、床面や固定物からの反射波は殆ど周期性が見られないが、呼吸活動によって発受信アンテナと被検者からの反射波の発受信アンテナ間の距離が変動するためその信号強度も変化する(シンチレーション)。本発明においては、急な呼吸変動に対応すべく、前記呼吸波形はウェーブレット変換によって波形解析を行う。 Next, each sample value of the A / D converted delay profile is observed for each transmission, and the periodicity is detected from the temporal change. For example, the reflected wave from the floor or a fixed object has almost no periodicity, but the signal strength is also high because the distance between the transmitting and receiving antenna and the transmitting and receiving antenna of the reflected wave from the subject fluctuates due to respiratory activity. Change (scintillation). In the present invention, the respiratory waveform is subjected to waveform analysis by wavelet transform in order to cope with sudden respiratory fluctuations.
上記のように本発明においては、距離情報からではなくて、受信した遅延プロファイル上の、被検者Pの呼吸による微小な動きに伴う受信信号強度変動(シンチレーション)から呼吸数を推定する。従って、遅延プロファイルの各距離に相当する位置の電力の変動を監視することによって、被検者Pの呼吸数や異常呼吸などを検出することができる。 As described above, in the present invention, the respiratory rate is estimated not from the distance information but from the received signal intensity fluctuation (scintillation) accompanying the minute movement caused by the breathing of the subject P on the received delay profile. Therefore, by monitoring fluctuations in power at positions corresponding to the respective distances of the delay profile, the respiratory rate or abnormal breathing of the subject P can be detected.
各遅延反射波(到達時間が異なる反射波)の信号強度は信号処理部8に入力され(ステップドFM波、FM−CW波の超広帯域無線波については、検波後、それぞれ逆FFT(fast Fourier transform)、FFTにより時間領域、周波数領域に変換される)、その時間変動から呼吸運動を推定する。図4に、遅延プロファイルの、各反射波毎の信号強度の(送信波の繰り返し周期Tの)時間変動を示す。図4において、S1は床面からの反射波であるため殆ど周期性が見られず(雑音による変動のみ)、固定反射面からの反射波であることが分かる。S2乃至S6は呼吸運動によって周期的に変動しており、人体からの反射波であると判断され、その信号強度の時間的変化を測定する。 The signal intensity of each delayed reflected wave (reflected wave having a different arrival time) is input to the signal processing unit 8 (for the ultra-wideband radio wave of the stepped FM wave and the FM-CW wave, after detection, an inverse FFT (fast Fourier) is obtained. transform) and FFT (transformed into the time domain and frequency domain), and the respiratory motion is estimated from the time variation. FIG. 4 shows the time variation (in the repetition period T of the transmission wave) of the signal intensity for each reflected wave in the delay profile. In FIG. 4, since S 1 is a reflected wave from the floor surface, almost no periodicity is seen (only fluctuation due to noise), and it can be seen that this is a reflected wave from the fixed reflecting surface. S 2 to S 6 periodically change due to respiratory motion, and are determined to be reflected waves from the human body, and the temporal change in the signal intensity is measured.
本発明においては、従来のマイクロ波センサのようにドップラ効果の観測や測距によって人間の動きを検出するのではなくて、検波した遅延プロファイルの各遅延反射波の信号強度変動(シンチレーション)のみを用いている。従って、信号処理部8やA/D変換器7への負荷は小さく低コストの呼吸監視装置を提供できる。図5に、測定した呼吸波形を示す。図5に示す呼吸波形は、被検者Pが故意に呼吸を止めた区間が表示されている。図5には、従来の物理センサ(ワイヤセンサ)を体に取り付けて測定した実際の呼吸波形も併せて示した。 In the present invention, human motion is not detected by observing the Doppler effect or ranging as in the conventional microwave sensor, but only the signal intensity fluctuation (scintillation) of each delayed reflected wave of the detected delay profile is detected. Used. Therefore, the load on the signal processing unit 8 and the A / D converter 7 is small and a low-cost respiration monitoring device can be provided. FIG. 5 shows the measured respiratory waveform. The respiratory waveform shown in FIG. 5 displays a section where the subject P intentionally stopped breathing. FIG. 5 also shows an actual respiratory waveform measured by attaching a conventional physical sensor (wire sensor) to the body.
信号処理部8では、呼吸波形の急な時間的変化に対応するために、ウェーブレット変換によって、周波数解析を行う。図6−1、図6−2に、ウェーブレット変換によって処理した周波数/呼吸数の時間変化(スカログラム)を示す。図6−1に、連続的な信号強度波形とその周波数/呼吸数の時間変化を、図6−2に、途中で呼吸を止めたときの信号強度波形とその周波数/呼吸数の時間変化を示す。ここで、呼吸を止めたときにも僅かな変動が見られるが、これは呼吸を止めても体が微妙に変動しているためである。 In the signal processing unit 8, frequency analysis is performed by wavelet transform in order to cope with a sudden temporal change in the respiratory waveform. FIGS. 6A and 6B show temporal changes (scalogram) of the frequency / respiration rate processed by the wavelet transform. Fig. 6-1 shows the continuous signal intensity waveform and its frequency / respiration rate over time, and Fig. 6-2 shows the signal intensity waveform and its frequency / respiration rate over time when breathing stops halfway. Show. Here, even when breathing is stopped, a slight change is observed, because the body slightly changes even when breathing is stopped.
本発明によれば、複数の被検者Pの呼吸運動を同時に監視することができる。図7に、同時に測定した二人の被検者Pの呼吸波形を示す。図8に、急な体位変化(仰向けからうつ伏せへ)に伴う信号強度波形を示す。図8から明らかなように、急な体位変化に対しても呼吸運動を正確に測定することができる。
また、必要に応じて複数の被検者Pの呼吸波形データや呼吸数を遠方の監視モニタへ無線で伝送し、呼吸異常の場合には自動警報装置を作動させることもできる。
According to the present invention, the respiratory movements of a plurality of subjects P can be monitored simultaneously. FIG. 7 shows respiratory waveforms of two subjects P measured simultaneously. FIG. 8 shows a signal intensity waveform that accompanies a sudden change in body position (from supine to prone). As is clear from FIG. 8, the respiratory motion can be accurately measured even for a sudden change in body position.
Further, if necessary, the respiratory waveform data and respiratory rates of a plurality of subjects P can be transmitted wirelessly to a distant monitoring monitor, and an automatic alarm device can be activated in the case of respiratory abnormalities.
図1に示す室内の天井付近(高さ:2.8m)の発受信アンテナ(Schwarzbeck:9120D)を設置し、ベクトルネットワークアナライザ(Agilent:8722ET)のタイムドメイン機能を利用して無線伝送路の遅延プロファイルを測定し、その結果をPCに転送し信号処理した。ここで、被検者Pのベッドとして金属フレームの折り畳みベッドを使用した。床面はフローリングである。 The transmitter / receiver antenna (Schwarzbeck: 9120D) near the ceiling (height: 2.8 m) shown in Fig. 1 is installed, and the delay of the radio transmission line is made using the time domain function of the vector network analyzer (Agilent: 8722ET) The profile was measured, and the result was transferred to a PC for signal processing. Here, a folding bed of a metal frame was used as the bed of the subject P. The floor is flooring.
検出に用いるUWBの周波数帯域幅(BW(band width))は7GHz(3GHz〜10GHz)で、レンジサイドローブ抑圧の観点から信号スペクトルに窓関数をかけており(サイドローブ比=−43dB)、その6dBパルス幅Δdは次式で与えられる。 The frequency bandwidth (BW (band width)) of UWB used for detection is 7 GHz (3 GHz to 10 GHz), and a window function is applied to the signal spectrum from the viewpoint of range sidelobe suppression (sidelobe ratio = −43 dB). The 6 dB pulse width Δd is given by the following equation.
ここで、cは光速でありc=3×1010[cm/s]である。従って、BW=7GHzにおける分解能Δdは約8.4cmとなる。 Here, c is the speed of light, and c = 3 × 10 10 [cm / s]. Therefore, the resolution Δd at BW = 7 GHz is about 8.4 cm.
図5に、ベッド上で仰向けになっている被検者Pからの反射波信号強度変動(周期T=0.74msec)と、胸部に帯状のワイヤセンサを巻き付けて測定した被検者Pの呼吸に伴う物理的変動を示す。ここで、被検者Pは一定の時間呼吸を止めている。図5から明らかなように、被検者Pの着衣を透過して11回/分〜16回/分の信号強度変動(呼吸数)が見られる。また、比較的低周波の小さな変動が見られるが、これは体が微妙に動いたためである。 FIG. 5 shows the reflected wave signal intensity fluctuation (period T = 0.74 msec) from the subject P lying on his / her back on the bed and the breathing of the subject P measured by winding a band-shaped wire sensor around the chest. The physical fluctuations associated with are shown. Here, the subject P stops breathing for a certain time. As is clear from FIG. 5, signal intensity fluctuations (respiration rate) of 11 times / minute to 16 times / minute are seen through the clothes of the subject P. In addition, small fluctuations at a relatively low frequency are seen, because the body moved slightly.
1 発信部
2 長広帯域無線波発振器
3 発受信アンテナ
4 発受信切換器(ハイブリッド)
5 受信部
6 前置増幅器/検波器
7 A/D変換器
8 信号処理部
9 転送アンテナ
P 被検者
S1〜S6 受信信号
DESCRIPTION OF
5
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Cited By (6)
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JP2010231663A (en) * | 2009-03-27 | 2010-10-14 | Taisei Denshi Seisakusho:Kk | Human body abnormality discriminating device |
JP2015116473A (en) * | 2013-12-18 | 2015-06-25 | 現代自動車株式会社 | Heartbeat measurement device, heartbeat measurement method, and driver monitoring system |
JP2016106734A (en) * | 2014-12-03 | 2016-06-20 | 富士通株式会社 | Body information acquisition device, body information acquisition method, and program |
KR20180046334A (en) * | 2016-10-27 | 2018-05-08 | 비아이에스웍스 주식회사 | Apparatus and method measuring real respiration signal based on the frequency analysis and time analysis |
JP2018187442A (en) * | 2018-08-03 | 2018-11-29 | 国立研究開発法人産業技術総合研究所 | Biological signal detection device |
JP2019111321A (en) * | 2017-12-01 | 2019-07-11 | オリジン ワイヤレス, インコーポレイテッドOrigin Wireless, Inc. | Method, apparatus, and system for periodic motion detection and monitoring |
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Cited By (8)
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JP2010231663A (en) * | 2009-03-27 | 2010-10-14 | Taisei Denshi Seisakusho:Kk | Human body abnormality discriminating device |
JP2015116473A (en) * | 2013-12-18 | 2015-06-25 | 現代自動車株式会社 | Heartbeat measurement device, heartbeat measurement method, and driver monitoring system |
JP2016106734A (en) * | 2014-12-03 | 2016-06-20 | 富士通株式会社 | Body information acquisition device, body information acquisition method, and program |
KR20180046334A (en) * | 2016-10-27 | 2018-05-08 | 비아이에스웍스 주식회사 | Apparatus and method measuring real respiration signal based on the frequency analysis and time analysis |
KR101995966B1 (en) * | 2016-10-27 | 2019-07-04 | 비아이에스웍스 주식회사 | Apparatus and method measuring real respiration signal based on the frequency analysis and time analysis |
JP2019111321A (en) * | 2017-12-01 | 2019-07-11 | オリジン ワイヤレス, インコーポレイテッドOrigin Wireless, Inc. | Method, apparatus, and system for periodic motion detection and monitoring |
JP7278682B2 (en) | 2017-12-01 | 2023-05-22 | オリジン ワイヤレス, インコーポレイテッド | Systems and methods for periodic motion detection and monitoring |
JP2018187442A (en) * | 2018-08-03 | 2018-11-29 | 国立研究開発法人産業技術総合研究所 | Biological signal detection device |
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