Experimental validation of a quasirealtime human respiration detection method via UWB radar
Shiyou Wu^{1} , Zhenghuan Xia^{2} , Kai Tan^{3} , Jie Chen^{4} , Shengwei Meng^{5} , Guangyou Fang^{6} , Hejun Yin^{7}
^{1, 3, 4, 6}Key Laboratory of Electromagnetic Radiation and Sensing Technology Institute of Electronics, Chinese Academy of Sciences, Beijing, China
^{2}State Key Laboratory of SpaceGround Integrated Information Technology, Beijing, China
^{2}Space Star Technology Co., Ltd., Beijing, China
^{3}University of Chinese Academy of Sciences, Beijing, China
^{5}Harbin Institute of Technology, Beijing, China
^{7}Chinese Academy of Sciences, Beijing, China
^{1}Corresponding author
Journal of Vibroengineering, Vol. 17, Issue 5, 2015, p. 26692680.
Received 8 June 2015; received in revised form 25 July 2015; accepted 2 August 2015; published 15 August 2015
JVE Conferences
In this paper, we propose a quasirealtime human respiration detection method via UWB radar system in throughwall or similar condition. With respect to the previous proposed automatic detection method, the new proposed method assures competitive performance in the human respiration motion detection and effective noise/clutter rejection, which have been proved by experimental results in actual scenario. This new method has also been implemented in a UWB throughwall lifedetection radar prototype, and its time consuming is about 2 s, which can satisfy the practical requirement of quasirealtime for throughwall sequential vital sign detection. Therefore, it can be an alternative for throughobstacles static human detection in antiterrorism or rescue scenarios.
Keywords: quasirealtime, human respiration detection, UWB radar.
1. Introduction
The ultrawideband (UWB) radar system for throughwall detecting human subjects has always been an important technique to prevent the crimes and terror due to its high range resolution, strong penetrating power, and good resolving ability. In recent years, the vital sign electromagnetic detection using UWB radar is becoming an advanced noncontact detection technique which extracts information from observations on human subject. Regarding to vital sign detection, many research groups have been proposing many novel detection algorithms using different radar systems like Doppler radar [1], Continuous Wave radar [2, 3] and UWB pulse radar [47]. Changzhi Li et al. employed the relaxation (RELAX) algorithm to process baseband signals for Doppler radar noncontact vital sign detection [1]. Marcello Ascione et al. properly exploited a CW signal source working at 10 GHz and took advantage of the phase modulation due to the chest movement to detect the respiratory activities from the measured signal [2]. Lanbo Liu et al. studied the human vital sign detection with the SFCW radar technique with physical experiments under laboratory conditions [3]. Amer. Nezirovi´c et al. proposed a developed respiration motion detection (RMD) algorithm that could separate the nonstationary clutter from the respiratory response using a UWB pseudorandomnoise radar [4]. Based on a UWB pulse radar, Lanbo Liu applied the HilbertHuang Transform (HHT) for the nonlinear and nonstationary signal processing to identify and differentiate a variety of respiratory statuses [5]. Zhu Zhang et al. mainly focused on the estimation of the surrounding structure between the human target and the radar [6]. Zhao Li et al. found the respirationlike clutter reflected from the wall or rubble due to the jitter or drift of the radar, and they proposed an adaptive clutter cancellation [7]. Meanwhile, many respiration detection methods in the medical area are also attractive and worth mentioning for throughwall applications [8, 9].
In this paper, we apply a UWB pulse radar system in throughobstacles human respiration detection and present the experimental validation of the new proposed quasirealtime detection method that aims at improving the performance of respiration detection. Compared to the previous proposed method [10], nonstationary clutter will be suppressed effectively in the new method. Meanwhile, the time consuming is about 2 s so that the quasirealtime throughwall human respiration detection is possible. This feature might also be suitable for throughobstacles static human detection in antiterrorism.
The rest of this paper is organized as follows. In section 2, the overall radar system is described both in measurement device and detection procedure aspects, while the experimental results are reported in section 3. Finally, section 4 concludes this paper.
2. UWB throughwall lifedetection radar system
2.1. UWB time domain respiratory signal model
Referring to [11, 12], for impulse UWB radar system, the received signal $S\left(t\right)$ with the respiration motion of one human subject can be expressed as:
where “$\mathrm{*}$” represents convolution. $u\left(t\right)$ is the transmitted signal, $t$ represents fasttime, slowtime is discrete with $nT$, on which the reflected signal is received, $N$ is slowtime sampling points, $n=\text{0,}\text{}\text{1,}\text{\u2026}\text{,}\text{}N1$ and $T$ is the effective pulse repetition time (PRT). ${h}_{r}\left(t\right)$ is the respiratory response of the human subject, and ${h}_{p}\left(t\right)$ is the joint impulse response of transmitting antenna, receiving antenna, and $P1$ static objects. ${\tau}_{r}$ and ${\tau}_{p}$ are the propagation timedelay of the human subject and the $p$th object, respectively. $\gamma \left(t\right)$ is the nonstationary inference, and $\omega \left(t\right)$ is the additive white Gaussian noise.
In order to avoid frequency aliasing and range ambiguities, $T$ should be set to satisfy Nyquist sampling theorem and guarantee that all the reflected signals of objects are received in one PRT [10]. The discrete signal of all the reflected signals can be expressed as 2D (fasttime and slowtime) $M$×$N$ matrix $S\left(m,n\right)$:
where $M$ is fasttime sampling points, $m=\text{0,}\text{}\text{1,}\text{\u2026}\text{,}\text{}M1$, and $N$ is slowtime sampling points, $n=\text{0,}\text{}\text{1,}\text{\u2026}\text{,}\text{}N1$. Every term in Eq. (2) corresponds to that in Eq. (1).
2.2. Quasirealtime detection procedure
Here, we propose an improved version of the previous method [10], referred to as the quasirealtime human respiration detection (QHRD) method in the following. The proposed QHRD method consists of three main steps: ${A}^{\text{'}}$) PreProcessing, ${B}^{\text{'}}$) FFT in Slowtime Convolution Dimension and ${C}^{\text{'}}$) Spectrum Weighted Accumulation (SWA) method, as illustrated in Fig. 1(a). In the previous method, there are also three main steps: $A$) PreProcessing, $B$) FFT in Slowtime Dimension and $C$) Constant False Alarm Rate Clustering (CFARClustering) method, as shown in Fig. 1(b). Obviously, the step ${A}^{\text{'}}$ is developed from the step $A$. The adaptive background subtraction (ABS) method in [13] is used to remove the static clutter. The linear trend suppression (LTS) method in [4] is adopted to suppress the nonstatic clutter and linear trend in slowtime dimension caused by the data acquisition accompanying with the instability of radar timebase. The advance normalization (AN) method in [14] is used for the enhancement of the weak human respiratory signal. A moving average filter is also applied both along the fasttime and slowtime dimensions to eliminate and suppress the highfrequency clutter interferences [7].
As shown in Fig. 1(a), the 2D $M$×$N$ matrix $S\left(m,n\right)$ in Eq. (2) is taken as the input of the step ${A}^{\text{'}}$, the corresponding output matrix is named as $\stackrel{~}{S}\left(m,n\right)$. The aim of all the above methods performed in the step ${A}^{\text{'}}$ is to further improve the signal to noise/clutter ratio (SNCR) of $\stackrel{~}{S}\left(m,n\right)$. In the following, the step ${B}^{\text{'}}$ and step ${C}^{\text{'}}$ in the QHRD method different from the previous method will be given out.
Fig. 1. a) The flowchart of the QHRD method, b) the flowchart of the previous method
a)
b)
2.2.1. FFT in slowtime convolution dimension
Generally, there is a strong correlation among the values of the deterministic signal in different time instant. Otherwise, the correlation of the interference noise is always weak because of the high randomness. Based on this characteristic, the deterministic signal can be extracted from the interference noise. For the $\mathrm{m}\mathrm{t}\mathrm{h}$ slowtime signal ${x}_{m}\left(\tau \right)$ in $\stackrel{~}{S}\left(m,n\right)$ added with zero mean random noise, the contribution from the noise can be very small in the autocorrelation function ${R}_{{x}_{m}}\left(\tau \right)$, which mainly consists of the characteristics of the deterministic signal like DC, the amplitude and frequency of the periodic components and so on. For the nonperiodic noise, the autocorrelation function is prone to zero:
where ${0\le \tau}_{1}\text{,}$${\tau}_{2}\le N1$ and $\tau ={\tau}_{1}{\tau}_{2}\text{.}$ The periodic component and its harmonic components of the slowtime signal ${x}_{m}\left(\tau \right)$ are still preserved and expressed as ${R}_{{x}_{m}}\left(\tau \right)$. ${R}_{{x}_{m}}\left(\tau \right)$ can be discretized and taken as the $m$th row vector of the 2D (fasttime and slowtime convolution) $M$×$\left(2N1\right)$ matrix ${R}_{x}\left(m,n\right)$, where $M$ is fasttime sampling points and $m=\text{0,}\text{}\text{1,}\text{\u2026}\text{,}\text{}M1$, $2N1$ is convolution length and $n=\text{0,}\text{}\text{1,}\text{\u2026}\text{,}\text{}2N2$. To extract the respiratory frequency, the FFT is performed for ${R}_{x}\left(m,n\right)$ in slowtime convolution dimension, and its resultant matrix is the output rangefrequency matrix ${\stackrel{~}{R}}_{x}\left(m,n\right)$ of the step ${B}^{\text{'}}$ shown in Fig. 1(a). According to the fact that the respiratory frequency is confined in a narrow frequency range, one selected frequency window ranging from 0.05 to 1 Hz is added to eliminate high frequencies, high harmonics, and very low frequencies in ${\stackrel{~}{R}}_{x}\left(m,n\right)$.
2.2.2. Spectrum weighted accumulation (SWA) method
According to the implementation steps mentioned in Fig. 1(b), the CFARClustering method is performed to extract respiratory frequency. The CFAR method based on the characteristic of vital sign in the FFT resultant matrix is used to detect vital sign in low SNCR conditions automatically. The decision whether the vital sign exists or not and the estimation of the detailed vital information are implemented in the clustering decision method. However, the CFAR moving energy window calculation in the CFAR method and the vital sign points of interest (VSPOI) identification in the clustering decision method are always time consuming. Furthermore, the detection probability of the vital sign is highly depended on the selected local signal to background energy ratio ${T}_{r}$, which is empirically determined to be greater than one requiring that the energy of the vital sign is stronger than that of background.
Here, a new spectrum weighted accumulation (SWA) method is proposed for the vital sign extraction without any thresholds, the empirical adjustment of which might decrease the practicability of any detection method in actual scenarios. Define the nonweighted spectrum accumulation signal $\stackrel{~}{v}\left(n\right)$, which can be expressed as:
where $n=\text{0,1,}\text{\u2026}\text{,}\text{}2N2$ and ${\stackrel{~}{r}}_{m}\left(n\right)$ is the $m$th FFT result in rangefrequency matrix ${\stackrel{~}{R}}_{x}\left(m,n\right)$, which can be used to extract the periodic component. Although the spectral amplitude of the periodic component of respiration motion is always small in ${\stackrel{~}{r}}_{m}\left(n\right)$, it can be strengthened in the spectrum accumulation signal $\stackrel{~}{v}\left(n\right)$ to improve the SNCR. Whether the vital sign exists in the range ${[m}_{1}\text{,}\text{}{m}_{2}]$ or not is hard to decide, so the values of ${m}_{1}$ and ${m}_{2}$ are generally selected as $0$ and $M1$ respectively. As the spectral amplitude of nearzero frequency component can also be strengthened in $\stackrel{~}{v}\left(n\right)$, the weighted spectrum accumulation signal ${\stackrel{~}{v}}_{w}\left(n\right)$ is present to further remove the interference from the nearzero frequency components:
The weighted factor $w\left(n\right)$ is defined as:
where $n=\text{0,1,}\text{\u2026}\text{,}\text{}2N2$, ${F}_{s}=N/{T}_{M}$ is the slowtime scanning rate and ${T}_{M}$ is the total measured time, $N$ is slowtime sampling points. Here, the weighted factor $w\left(n\right)$ is selected as the respiratory frequency window. Based on the weighted spectrum accumulation signal ${\stackrel{~}{v}}_{w}\left(n\right)$, it is easy to extract the respiratory frequency by finding the peak value.
Assuming the respiratory frequency of a human being is invariant during the short measured time ${T}_{M}$, there is a onetoone relationship between the maximums of the ${\stackrel{~}{v}}_{w}\left(n\right)$ and the human being in a limited respiratory frequency window, which is set from 0.05 to 1 Hz according to the prior range of respiratory frequency. The index ${i}_{r}$ corresponding to the peak value of the ${\stackrel{~}{v}}_{w}\left(n\right)$ equals to the index in the weighted factor $w\left(n\right)$, so the respiratory frequency ${f}_{r}$ of the human being is:
When the possible respiratory frequency ${f}_{r}$ is extracted from the ${\stackrel{~}{v}}_{w}\left(n\right)$ and $w\left(n\right)$, the corresponding range profile $y\left(m\right)$ of the vital sign in ${\stackrel{~}{R}}_{x}\left(m,n\right)$ can be obtained:
where $M$ is fasttime sampling points and $m=\text{0,1,}\text{\u2026}\text{,}M1$. Similar to the respiratory frequency ${f}_{r}$, the index ${j}_{r}$ corresponding to the peak value of the $y\left(m\right)$ indicates the range location ${L}_{r}$ of the vital sign:
where ${L}_{\mathrm{m}\mathrm{a}\mathrm{x}}$ and ${L}_{\mathrm{m}\mathrm{i}\mathrm{n}}$ are the maximum and minimum distance to be detected respectively. Generally, ${L}_{\mathrm{m}\mathrm{i}\mathrm{n}}$ and ${L}_{\mathrm{m}\mathrm{a}\mathrm{x}}$ can be set to $0$ and ${(M1)c\delta}_{t}/2$. Here, ${\delta}_{t}$ is the fasttime sampling interval and $c$ is the propagation speed of the electromagnetic wave.
2.3. Update echo for sequential detection
The proposed QHRD method implemented in Matlab takes about 2s to obtain the results of the vital sign. Therefore, it can improve the performance of quasirealtime throughwall radars employed in emergency or law enforcement operations. According to the flowchart in Fig. 1(a), the 2D $M$×$N$ raw echo matrix $S\left(m,n\right)$ in the detection procedure is updated by a new 1D $M$×$1$ raw echo $s\left(m\right)$. This procedure has been adopted in our Throughwall LifeDetection Radar prototype (see Fig. 2), and offered the sequential range location and respiratory frequency of a human being.
2.4. Measurement device
As shown in Fig. 2, the radar prototype employed in human respiration detection was designed by the research group of Key Laboratory of Electromagnetic Radiation and Sensing Technology, Institute of Electronics, Chinese Academy of Sciences. This radar prototype packages two UWB antennas in a 45 cm×22 cm×45 cm box and is operated by a wireless personal digital assistant. One antenna is used for the transmitter, and the other is for the receiver. The key parameters of the radar prototype are shown in Table 1.
Table 1. Parameters of the radar prototype
Parameters

Value

Operating mode

Impulse

Centre frequency

400 MHz

Amplitude of transmitted signal

50 V

Pulse repeated frequency (PRF)

600 KHz

Average number (${N}_{A}$)

128

Sampling time window

81 ns

Sampling points ($M$)

2048 or 4096

Antenna gain

57 dBi

Input bandwidth of ADC

2.3 GHz

ADC sampling rate

500 MHz

Data bits

12 bits

Dynamic range of receiver

72 dB

3. Experiment and result analysis
The measurement setups for human respiration detection in throughwall or similar condition are shown in Fig. 2. Two experiments were conducted in the throughwall condition, and the third experiment was carried out in artificialruins condition. The latter two experiments were designed for the sequential detection. In the first experiment, the echoes were acquired with a male volunteer performing as the test human subject standing at several meters behind a concrete wall, which is shown in Fig. 2(a). The test human subject was straightly facing to the wall. The thickness and the measured average dielectric constant of the concrete wall were 24 cm and 4.93, respectively. In the second experiment, as shown in Fig. 2(b), the test human subject seated statically 2.5 m from the wall. To simulate the actual rescue scenario after earthquake, in the third experiment as shown in Fig. 2(c), the test human subject was lying about 30cm under a broken concrete building structure with the thickness of about 1m.
Fig. 2. The measurement setup
a) The test human subject stood behind a concrete wall
b) The test human subject seated statically behind the wall
c) The test human subject lied under a broken concrete building structure
3.1. Performance of the detection procedure
To compare the performances of the two methods shown in Fig. 1, the corresponding results are illustrated and analyzed in the following.
The quasiperiodic slowtime signals representing the respiration of the test human subject are depicted by the red dotted frame in the resultant matrix processed by the step $A$ (see Fig. 3(a)). However, the quasiperiodic respiratory signals cannot be seen clearly. This drawback directly decreases the detection probability of the subsequent step $B$ and step $C$ in the Fig. 1(b). Similarly, the resultant matrix after performing the step ${A}^{\text{'}}$ in Fig. 1(a) is shown in Fig. 3(b).
Fig. 3. a) Resultant matrix corresponding to the step $A$, b) resultant matrix corresponding to the step ${A}^{\text{'}}$, c) rangefrequency matrix obtained from the step $B$, d) rangefrequency matrix obtained from the step ${B}^{\text{'}}$
a)
b)
c)
d)
Fig. 4. Resultant matrices in the specific scenario where a moving person appeared in the front of the test human subject
a) Resultant matrix corresponding to the step $A$
b) Resultant matrix corresponding to the step ${A}^{\mathrm{\text{'}}}$
It is obviously noted that the quasiperiodic respiratory signals from the test human subject (depicted by the red dotted frame) can be distinguished easily. Subsequently, as the output of step $B$ and step ${B}^{\text{'}}$ in Fig. 1, the rangefrequency matrices are present in Fig. 3(c) and Fig. 3(d) respectively. Although the vital sign of the test human subject in the rangefrequency matrix (marked by a red ellipse in Fig. 3(c)) is visible, the range location and respiratory frequency of the vital sign can be hardly extracted due to the low SNCR condition caused by the nonstationary clutter interferences (marked by white dotted frame in Fig. 3(c)). Considering no other moving targets appear in the detection scenario, the nonstationary clutter is mainly brought from the instability of the radar system, but this might not be the only reason. As shown in Fig. 3(d), the nonstationary clutter interferences have been removed dramatically in the resultant matrix obtained from the step ${B}^{\text{'}}$ in Fig. 1(a). Obviously, the background around the vital sign is cleaner than that in Fig. 3(c), which makes the extraction of the vital sign easier.
Fig. 5. a) Rangefrequency matrix obtained from the step $B$, b) rangefrequency matrix obtained from the step ${B}^{\text{'}}$, c) Respiratory spectrum signals of rangefrequency matrix b) and its normalized spectrum weighted accumulation signal
a)
b)
c)
Considering the specific scenario where one moving person appeared in the front of the test human subject, the nonstationary clutter interference is strong as shown in Fig. 4(a) and the quasiperiodic respiratory signals are covered when the moving person is nearby. After performing the step ${A}^{\text{'}}$ in Fig. 1(a), the quasiperiodic respiratory signals are strengthened in Fig. 4(b). However, the nonstationary clutter interference caused by the moving person cannot be eliminated. The two rangefrequency matrices obtained from the step $B$ and step ${B}^{\text{'}}$ are shown in Fig. 5(a) and Fig. 5(b), respectively. It is noted that the step ${A}^{\text{'}}$ and the step ${B}^{\text{'}}$ of the QHRD method play an important role in eliminating the strong interference from the moving person. Compared to Fig. 5(a), the cleaner background in Fig. 5(b) is remarkable, and the vital sign of the test human subject marked by the red ellipse can be found obviously. In Fig. 5(c), the top plot shows the FFT results of the slowtime signals in Fig. 5(b) for all fasttime sampling points and the respiratory frequency of the test human subject is uncertain. The bottom plot of Fig. 5(c) gives out the normalized weighted spectrum accumulation signal defined as Eq. (5), and the desired respiratory frequency can be obtained clearly and its value is 0.34 Hz.
As mentioned above, the proposed QHRD method improves the previous method in reducing the nonstationary clutter interference, cleaning the background and distinguishing the vital sign in rangefrequency matrix effectively.
3.2. Sequential detection
According to Section IIC, the sequential results consisting of the detection range location and respiratory frequency of the test human subject are shown in Fig. 6 and Fig. 7, corresponding to measurement setups in Fig. 2(b) and Fig. 2(c) respectively. In Fig. 2(b), the acquired total trace number of the raw echoes is 1700 during the measured time of about 97 seconds. Similarly, the total trace number is 930 and the measured time is about 53 seconds in Fig. 2(c). Before the first implementation of the proposed QHRD method, the measured time needed for the collection of the raw echo matrix $S\left(m,n\right)$ is about 29 s, which is determined by the scanning rate of the radar prototype. Therefore, the first timeconsuming of the proposed QHRD method is about 31 seconds, then it might keep a constant value (about 2 seconds).
In Fig. 6, during the measured time ranging from about 29 seconds to 97 seconds, the status (range location and respiratory frequency) of the test human subject is detected in quasirealtime, the mean values of which are 2.58 m and 0.32 Hz respectively. Thus, it can be seen that the proposed QHRD method can give out the accordant status of the test human subject sequentially and make the quasirealtime monitoring of a static human being possible in throughwall condition.
Fig. 6. The sequential results consisting of the range location a) and respiratory frequency b) of the test human subject in Fig. 2(b) during the measured time ranging from about 29 s to 97 s
a)
b)
Further, the promising results of the proposed QHRD method in the artificial earthquake rescue scenario (see Fig. 2(c)) are shown in Fig. 7. The rangefrequency matrix obtained from the step ${B}^{\text{'}}$ at the measured time of 29 s is shown in Fig. 7(a). It is easy to extract the vital sign of the test human subject based on the clean background. The sequential status of the vital sign of the test human subject is updated every 2 seconds from the measured time of 29 seconds to 53 seconds, which are shown in Fig. 7(b) and Fig. 7(c). Likewise, the mean values of the detected status are 1.37 m and 0.44 Hz respectively, which are accordant with the practical status of the test human subject. Therefore, the application of the proposed QHRD method in earthquake rescue is feasible.
Fig. 7. a) The Rangefrequency matrix obtained from the step ${B}^{\mathrm{\text{'}}}$ at the measured time of 29 s. The sequential results consisting of the range location b) and respiratory frequency b) of the test human subject in Fig. 2(c) during the measured time ranging from about 29 s to 53 s
a)
b)
c)
4. Conclusion
We have proposed a QHRD method for sequential human respiration detection in throughwall or similar condition and provided experimental validations of its capability. The results show that the step ${A}^{\text{'}}$ and ${B}^{\text{'}}$ provide excellent suppression of static/nonstatic clutter and higher SNCR both in the weighted spectrum accumulation signal and rangefrequency matrix. The “cleaner” rangefrequency matrix makes the extraction of the vital sign easier. The timeconsuming is about 2 s so that the quasirealtime sequential human respiration detection is possible and suitable for throughobstacles static human detection in antiterrorism or rescue scenarios.
Acknowledgements
Funding for this work was provided by the National High Technology Research and Development Program of China (863 Program) under Grant No. 2012AA061403 and the National Science and Technology Pillar Program during the Twelfth Fiveyear Plan Period under Grant No. 2014BAK12B00.
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