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EURASIP Journal on Wireless Communications and Networking
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`Through-wall human being detection using UWB impulse radar

EURASIP Journal on Wireless Communications and Networking volume 2018, Article number: 46 (2018) | Download Citation

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Abstract

Ultra-wideband (UWB) impulse radar plays an important role in contactless vital sign (VS) detection. The VS can be extracted remotely by acquiring the oscillations in the human chest. Unfortunately, it is usually challenging to identify VS due to the low signal-to-noise ratio (SNR) only based on the traditional fast Fourier transform (FFT) especially in complicated conditions. To extract VS accurately, this paper presents a new scheme by analyzing the skewness characteristic of the received UWB impulses, which are modulated by life activities. The distance from the human subject to the radar antenna can be calculated by performing the discrete short-time Fourier transform (DSFT) on skewness. The frequency of human respiratory movement can be estimated based on the developed ensemble empirical mode decomposition (EEMD)-based accumulation technique by canceling out the harmonics effectively. The performance of the developed detection method is tested with several experiments carried out in different environments.

Introduction

Recently, contactless vital sign (VS) detection has drawn wide attention and achieved great achievements [1,2,3,4].The electromagnetic detection is regarded as the most promising technique, which can acquire VS in the range-frequency matrix. Ultra-wide band (UWB) impulse radar has been widely applied in indoor target localization, VS detection, and human fall detection by employing the continuous wave [5,6,7,8]. As a better alternative, UWB pulse radar has been widely used in moving target detection [3, 9, 10], through-wall imaging [11, 12] and post-earthquake search and rescue [13,14,15] due to its insightful advantages such as strong permeability and excellent time resolution.

Many techniques have been analyzed for VS detection [16,17,18,19,20,21,22,23,24,25,26,27,28,29,30,31,32,33,34,35,36,37,38,39,40,41,42]. The fast Fourier transform (FFT)-based Hilbert transform is used in analyzing the time-frequency characteristic of the respiratory movements [24, 25]. Considering the additive white Gaussian noise (AWGN), a maximum likelihood period estimator with lower complexity is proposed to acquire the period of human respiratory motions [29]. The singular value decomposition (SVD) algorithm is used to improve signal-to-noise ratio (SNR) by suppressing the non-stationary clutter [30]. The stationary clutter and linear trend are removed by employing the linear trend subtraction (LTS) technique [35]. In [39], the harmonics are suppressed based on the effective complex signal demodulation (CSD) algorithm. The accuracy of human respiratory frequency (RF) is improved by using the arctangent demodulation (AD) method [40]. However, they cannot achieve better performance especially in complicated conditions as they can only deal with some aspects including stationary and non-stationary clutter removal, respiratory characteristic analysis, and frequency estimates. Consequently, extensive research efforts are required to apply UWB pulse radar in VS detection.

This paper presents a new method for VS detection in through-wall and long-range conditions. The distance from human target to the radar antenna is calculated by performing the discrete short-time Fourier transform (DSFT) algorithm on the calculated skewness from the received pulses. A whole new analytical framework is provided for VS detection. The frequency of human respiratory movement can be estimated more accurately by employing the developed ensemble empirical mode decomposition (EEMD)-based accumulation method for the first time, which can better eliminate the harmonics of human respiratory movement. The performance of the developed method is validated with several experiments carried out based on the UWB radar designed by the Key Laboratory of Electromagnetic Radiation and Sensing Technology, Chinese Academy of Sciences.

The remainder of this paper is organized as follows. Section 2 introduces the VS detection model. The developed detection technique is analyzed in Section 3. Section 4 shows the performance of the proposed method in different environments. Section 5 concludes the whole paper.

System model

In VS detection, the distance from human subject to radar antenna can be expressed as [37]:

$$ d(t)={d}_0+r(t)={d}_0+{A}_{\mathrm{r}}\sin \left(2\pi {f}_{\mathrm{r}}t\right)+{A}_{\mathrm{h}}\sin \left(2\pi {f}_{\mathrm{h}}t\right) $$
(1)

where t represents the slow time and d0 represents the distance from the radar antenna to the center of the human chest; the respiratory amplitude is Ar, and the heartbeat amplitude is Ah; the frequencies of the respiratory and heartbeat movements are fr and fh, respectively.

If any other objects in the detection environment are stationary except for the human subject, the impulse responses can be given by:

$$ h\left(\tau, t\right)={a}_v\delta \left(\tau -{\tau}_v(t)\right)+\sum \limits_i{a}_i\delta \left(\tau -{\tau}_i\right) $$
(2)

where τ represents the fast time, \( \sum \limits_i{a}_i\delta \left(\tau -{\tau}_i\right) \) represents the response from the ith stationary object with the amplitude a i and time delay τ i , and a v δ(τ − τ v (t)) represents the response from life activity with the amplitude a v and time delay τ v (t), which is:

$$ {\tau}_v(t)=\frac{2d(t)}{v}={\tau}_0+{\tau}_r\sin \left(2\pi {f}_{\mathrm{r}}t\right)+{\tau}_{\mathrm{h}}\sin \left(2\pi {f}_{\mathrm{h}}t\right) $$
(3)

where v represents the light speed; τ0 = 2d0/v; τr = 2Ar/v; τh = 2Ah/v.

To clearly show the relationship between the fast time and slow time, the sketch map of the received pulses only reflected from the respiratory movements is given in Fig. 1.

Fig. 1
figure1

The sketch map of the received pulse reflected only with human respiratory

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The received pulses can be given by:

$$ R\left(\tau, t\right)=s\left(\tau \right)\times h\left(t,\tau \right)={a}_vs\left(\tau -{\tau}_v(t)\right)+\sum \limits_i{a}_is\left(\tau -{\tau}_i\right) $$
(4)

where s(τ) represents the transmitted pulse.

Equation (4) can be described in the discrete form as:

$$ {\displaystyle \begin{array}{l}R\left(m,n\right)={a}_vs\left(m{\delta}_T-{\tau}_v\left({nT}_s\right)\right)+\sum \limits_i{a}_is\left(m{\delta}_T-{\tau}_i\right)\\ {}\kern5.5em ={a}_vs\left(m{\delta}_R-v{\tau}_v\left({nT}_s\right)\right)+\sum \limits_i{a}_is\left(m{\delta}_R-v{\tau}_i/2\right)\\ {}\kern5.5em =h\left[m,n\right]+c\left[m\right]\kern0.5em \end{array}} $$
(5)

where T s represents the pulse repetition time; t = nT s , n = 0,  . . …,  N − 1; δ T represents the interval of the fast-time samples, m = 0,  . …,  M − 1; δ R  = vδ T /2 represents the interval of the range samples; h[m, n] represents the discrete life signals; and c[m] represents the discrete stationary clutter.

However, various clutters exist in the real environment. Equation (4) may contain not only stationary clutter and life signals but also the Gaussian noise w[m, n], non-stationary clutter q[m, n], linear trend a[m, n], and some unwanted clutters g[m, n].

As a result, (5) can be represented as:

$$ R\left[m,n\right]=h\left[m,n\right]+c\left[m\right]\kern0.5em +a\left[m,n\right]+w\left[m,n\right]+q\left[m,n\right]+g\left[m,n\right]\kern0.5em $$
(6)

In a static environment, the ideal pulses without clutters can be given by:

$$ R\left(\tau, t\right)={a}_vs\left(\tau -{\tau}_v(t)\right) $$
(7)

However, the existing various clutters as shown in (6) make it challenging to estimate the fast-time estimate τ0 and cause large errors in frequency estimates. Figure 2a shows (7), and the received pulses under AWGN are given in Fig. 2b, which indicate it is challenging to extract VS in low SNR.

Fig. 2
figure2

The resulting matrix: a without clutter and b under AWGN

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Detection method

In this section, the presented method for VS detection is analyzed based on the detailed steps as shown in Fig. 3.

Fig. 3
figure3

The flowchart of the proposed detection method

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Clutter suppression

The VS are usually covered by c[m] with strong amplitude, which can be estimated as:

$$ \Im =\frac{1}{M\times N}\sum \limits_{m=1}^M\sum \limits_{n=1}^N\Psi \left[m,n\right] $$
(8)

After removing (8), the resulting matrix ΩM × N can be expressed as:

$$ \Omega =\Psi -\Im $$
(9)

To remove a[m, n], the LTS algorithm is used. The result WM × N is

$$ W={\Omega}^{\mathrm{T}}\hbox{-} X{\left({X}^{\mathrm{T}}X\right)}^{-1}{X}^{\mathrm{T}}{\Omega}^{\mathrm{T}} $$
(10)

where X = [x1,  x2], x1 = [0,  1,  . . …,  N − 1]Τ and \( {x}_2={\left[1,\kern0.5em 1,\kern0.5em ..\dots, 1\right]}_{N\times 1}^{\mathrm{T}} \).

Usually, the maximum SNR cannot be obtained only based on the matched filter, as the reflected pulses are different from the traditional radiated signals. Some other effective methods are required to improve SNR. In this paper, an infinite impulse response band-pass filter is used with the transfer function given by:

$$ {\left|H\left(\omega \right)\right|}^2=\frac{1}{1+{\left(\omega /{\omega}_{\mathrm{c}}\right)}^{2{N}_{\mathrm{f}}}}. $$
(11)

where ωc represents the cut-off frequency and Nf represents the filter order.

The band-pass filter is performed on (10) in the range direction for each slow-time index n; the outputs are:

$$ \Lambda \left[m,n\right]={\chi}_1W\left[m,n\right]+{\chi}_2W\left[m-1,n\right]+\dots +{\chi}_{N_b+1}W\left[m-{N}_b,n\right]-{\kappa}_2W\left[m-1,n\right]-\dots -{\kappa}_{N_a+1}W\left[m-{N}_a,n\right] $$
(12)

where N b  = N a  = 5 and κ i and χ i are the filter coefficients.

Further, to improve SNR, an average extraction filter is applied in (12) in slow-time direction with λ = 7, and the result is given by:

$$ \Phi \left[k,n\right]=\frac{1}{7}\sum \limits_{m=7\lambda}^{8\lambda -1}\Lambda \left[m,n\right] $$
(13)

where k = 1, . …, ⌊M/λ⌋. ⌊M/λ⌋ represents the maximum integer less than M/λ.

After removing the various clutters as shown in (6), (7) can be described in the discrete form as:

$$ \Psi \left[m,n\right]={a}_vs\left(m{\delta}_T-{\tau}_v\left({nT}_s\right)\right)={a}_vs\left(m{\delta}_R-v{\tau}_v\left({nT}_s\right)\right)=h\left[m,n\right]\kern0.5em $$
(14)

Range estimate

In this section, a new scheme for range estimate is developed by analyzing the skewness of VS.

The skewness for each range index m in (14) can be given by [43, 44]:

$$ Z(m)=E\left[{\left(\frac{\Psi \left[m,N\right]-\mu }{\sigma}\right)}^3\right] $$
(15)

where Ε[•] represents the expectation and μ and σ are the mean and standard deviation.

In this paper, the skewness spectrum is analyzed to estimate the range between the radar antenna and human subject. To show the skewness of VS, one data acquired from one female subject is applied. The distance from the human subject to the radar antenna is 9 m outdoors, which will be introduced in Section 4.

As shown in Fig. 4a, the skewness in human subject area follows the periodicity approximately as show in Fig. 4b. To estimate the range, the DSFT is performed on (15), which has been widely applied in signal processing [44, 45]. The result is given by:

$$ K\left[o,p\right]=\sum \limits_{m=1}^MZ\left[m,1\right]\Xi \left[o-m\right]{e}^{-j2 p\pi m/P}. $$
(16)

where P denotes the discrete frequency, which follows the uniform distribution. Ξ represents the Hamming window, which can be expressed as:

$$ \Xi (o)=\alpha -\beta \cos \left(\frac{2\pi o}{O}\right),\kern1.5em o=0,1,..\dots O. $$
(17)

where α = 0.54, β = 0.46, and O = 512 is the width of the Hamming window [46].

Fig. 4
figure4

a The calculated skewness values with the data acquired at a distance of 9 m away from the radar antenna. b The local values

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The result KO × P acquired by performing DSFT on (15) with human subject is shown in Fig. 5. When there is no any human subject in the detection environment, the calculated skewness is shown in Fig. 6a, and the corresponding time-frequency matrix is given in Fig. 6b.

Fig. 5
figure5

The resulting matrix with DSFT performed on the skewness values at a distance of 9 m away from the antenna

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Fig. 6
figure6

The calculated results without human target: a the calculated skewness values with normalized amplitude and b the time-frequency characteristic using the DSFT method

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It can be seen that the distance can be estimated as:

$$ \widehat{L}=v\widehat{\tau}\kern0.5em $$
(18)

where \( \widehat{\tau} \) represents the time estimate related to the maximum in (16).

Frequency estimate

The index of the time estimate in (13) can be given by:

$$ \Im =\widehat{\tau}/{\delta}_T $$
(19)

To acquire the frequency of human respiratory, the corresponding signal in slow time is chosen as the effective signal, which can be given by:

$$ \mathrm{O}=\Psi \left[\Im, n\right] $$
(20)

As an adaptive method, EEMD has been widely applied in analyzing non-stationary signals [45, 46], which overcomes the drawback in the traditional empirical mode decomposition [47]. Based on the EEMD technique, the non-stationary signal can be broken down into several intrinsic mode functions (IMFs) and a residual trend by employing the AWGN adaptively. The IMFs and residual trend can be used to reconstruct AWGN, which can improve SNR effectively.

To acquire the IMFs of (20), the steps for the EEMD method can be summarized as:

  1. I)

    Add the AWGN to (20);

  2. II)

    Based on the empirical mode decomposition, (20) can be decomposed into IMFs as:

  1. 1)

    Let v = 0, which is used to indicate the vth IMF;

  2. 2)

    To acquire all these local maximum and minimum values of (20);

  3. 3)

    To get the envelopes including the upper envelope r u (t) and the lower envelope r l (t)of (20) based on the values from 2) by employing the cubic spline function;

  4. 4)

    To generate the average envelope from 3), which can be given by [48]:

$$ m(t)=\frac{r_u(t)+{r}_l(t)}{2} $$
(21)
  1. 5)

    Subtracting (21) from (20), which can be given by:

$$ h(t)={\tilde{\mathrm{O}}}_{1\times \mathrm{N}}-m(t) $$
(22)
  1. 6)

    Go to step (II), (22) is processed until an IMF meets the stoppage criteria;

  2. 7)

    v = v + 1,  IMF v (t) = h(t). The residue trend can be given by [49]:

$$ {q}_v(t)={\tilde{\mathrm{O}}}_{1\times \mathrm{N}}-{\mathrm{IMF}}_v(t) $$
(23)
  1. 8)

    Go to step (II) and (23) is processed. The whole decomposition stops until the amplitude of IMF v (t) is small enough.

Based on the empirical mode decomposition method, (20) can be broken into several IMFs, and the residue signal given by:

$$ {\tilde{\mathrm{O}}}_{1\times \mathrm{N}}=\sum \limits_{v=1}^{M_v}{\mathrm{IMF}}_v(t)+{q}_{M_v}(t) $$
(24)
  1. III)

    For each added AWGN, (20) is processed by employing the steps (I)–(II) repeatedly;

  2. IV)

    The average values of the IMFs are considered as the final result, which are given by:

$$ {\tilde{\mathrm{O}}}_{1\times \mathrm{N}}=\sum \limits_{v=1}^{M_v}{\mathrm{IMF}}_v^{\mathrm{mean}}(t)+{q}_{M_v}^{\mathrm{mean}}(t) $$
(25)

where

$$ {IMF}_v^{\mathrm{mean}}(t)=\frac{1}{N_v}\sum \limits_{v=1}^{N_v}{\mathrm{IMF}}_v(t) $$
(26)
$$ {q}_{M_v}^{\mathrm{mean}}(t)=\frac{1}{N_v}\sum \limits_{v=1}^{N_v}{q}_v(t) $$
(27)

and N v is the times of the added AWGN.

For the EEMD method, two key parameters are required to be determined such as the amplitude and the times of the added AWGN. Usually, the relationship between the amplitude of (20) and the added AWGN can be given by:

$$ {\varepsilon}_n=\frac{\varepsilon }{\sqrt{N_v}} $$
(28)

where ε is the standard deviation of the added AWGN and ε n is the error between (20) and the ideal signal reconstructed based on the chosen IMFs.

Figure 7 shows the time-frequency matrix of (20) and the acquired IMFs based on EEMD, and Fig. 8 shows the corresponding welch power spectral density of the IMFs. As known, the frequency of human respiratory movement is usually within 0.2–0.5 Hz with the amplitude of 0.5–1.5 cm. As a result, the corresponding IMFs with the power being in the range of 0.1–0.8 Hz are chosen to reconstruct the signal, which can be given by:

$$ {\tilde{\mathrm{O}}}_{1\times \mathrm{N}}\kern0.5em =\kern0.5em \sum \limits_{v=4}^5{\mathrm{IMF}}_v^{\mathrm{mean}}(t) $$
(29)
Fig. 7
figure7

The time-frequency characteristic of the calculated IMFs using EEMD: a original signal, b IMF1, c IMF2, d IMF3, e IMF4, f IMF5, g IMF6, h IMF7, i IMF8, j IMF9, and k IMF10

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Fig. 8
figure8

The welch power spectral density of the IMFs: a IMF1, b IMF2, c IMF3, d IMF4, e IMF5, f IMF6, g IMF7, h IMF8, i IMF9, and j IMF10

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A rectangular window χ is performed on the frequency components of (29), which gives

$$ \Omega \left[n\right]=\chi \left[n\right]\left\{\mathrm{DFT}\left\{{\tilde{\mathrm{O}}}_{1\times N}\right\}\right\}\kern2.12em n\in {K}^{\ast };{K}^{\ast }=\left\{{k}^{\ast },{k}^{\ast }+1,\dots, {k}^{\ast }+\kappa -1\right\} $$
(30)

where \( \mathrm{DFT}\left\{{\tilde{\mathrm{O}}}_{1\times N}\right\} \) is the discrete fast Fourier transform (DFT) of (29) and k∗ corresponds to the index of the lowest retained frequency component.

The frequency of human respiratory movement can be acquired as:

$$ {f}_{\mathrm{r}}=w\left({\mu}_{\mathrm{r}}\right)\kern0.5em $$
(31)

where μr corresponds to the index of the maximum value in (30), and w ∈ (0.1,  0.8).

As known, the harmonics are the major factor affecting the frequency estimate. To suppress the harmonics, an accumulation method is proposed [50], which gives:

$$ \delta \left[n\right]=l\left[n\right]+ jl\left[n\right] $$
(32)

where

$$ l\left[n\right]=\left\{\begin{array}{l}2\Omega \left[n\right],\kern4.5em \kappa >0\\ {}\Omega \left[n\right],\kern5.5em \kappa =0\\ {}0,\kern8em \kappa <0\end{array}\right. $$
(33)

Results and performance

Measurement setup

To test the performance of the presented method, several experiments are carried out in different environments. The measurement setup for the experiments is shown in Fig. 9a.

Fig. 9
figure9

Measurement setup for acquiring data. a The sketch map. b Outdoor environment. c Indoor environment

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(I) Several experiments are conducted outdoors at the Institute of Electronic, Chinese Academy of Science, as shown in Fig. 9b. A female volunteer served as the detection subject for data acquisition. The used UWB radar is placed on a table, which is 1.5 m in the air. The wall consists of three materials such as brick wall (.3 m), concrete (.35 m), and plank (.35 m). The volunteer standing behind the wall stayed dormant, relaxed, and breathed normally. She faced the radar straightly. The distance from the detection subject to the radar is 3, 6, 9, and 11 m, respectively.

(II) Several experiments are conducted indoors in the China National Fire Equipment Quality Supervision Center, Shanghai, as shown in Fig. 9c. A male volunteer served as the detection subject for data acquisition. The volunteer standing behind the wall stayed dormant, relaxed, and breathed normally. She faced the radar straightly. The distance from the detection subject to the radar is 4, 7, 10, and 12 m, respectively.

In this section, the methods such as the FFT, constant false alarm ratio (CFAR), and the advanced method (AM) are used to validate the performance of the new method.

UWB radar

The UWB impulse radar used for data acquisition consists of one transmitting antenna and one receiving antenna, which are stored in a 45 cm × 22 cm × 45 cm box and operated by a wireless personal digital assistant. The key parameters for the radar system are given in Table 1. The time window is 124 ns with 4096 samples acquired in the fast time totally. To improve SNR, 128 points are averaged for one measurement. In slow time, it takes 17.6 s to store 512 pulses. The received pulse with the normalized amplitude is shown in Fig. 10.

Table 1 The key parameters for the UWB radar system
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Fig. 10
figure10

The normalized received signal using the UWB radar

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Intuitive detection performance

The results are analyzed in this section based on the steps for clutter suppression using the data sets acquired outdoors. The distance from the detection to the radar antenna is 9 m. The received raw echoes are shown in Fig. 11a. Figure 11b shows the result by removing the stationary clutter, and the result after canceling out the linear trend is shown in Fig. 11c. We can see that the VS is too weak to extract. By employing the band-pass filter, the result is shown in Fig. 11d, and Fig. 11e shows the result after filtering in slow time. All these steps for clutter suppression result in an improvement in VS. By employing the methods for clutter suppression mentioned above, the VS becomes more and more easy to extract compared with the raw echo as shown in Fig. 11a.

Fig. 11
figure11

The resulting matrix at a distance of 9 m. a Received pulses. b Remove static clutter. c LTS. d Filtering in fast-time dimension. e Filtering in slow-time dimension

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Performance outdoors

As usual, VS can be extracted more easily by improving SNR [37]. If only the frequency component containing VS is referred as the effective frequency any other components are considered as AWGN. SNR can be estimated as [37]:

$$ \mathrm{SNR}=20\cdot {\log}_{10}\left(\frac{\sum \limits_{n={\mu}_{\mathrm{r}}-1}^{\mu_{\mathrm{r}}+1}\left|\delta \left[n\right]\right|}{\sum \limits_{n={\gamma}_1}^{\mu_{\mathrm{r}}-2}\left|\delta \left[n\right]\right|+\sum \limits_{n={\mu}_{\mathrm{r}}+2}^{\gamma_2}\left|\delta \left[n\right]\right|}\right) $$
(34)

where μr represents the respiratory rate estimate. γ1 and γ2 are the indexes of χ.

Usually, (34) decreases with increasing the distance from the radar to the detection subject due to the attenuation of electromagnetic wave. Consequently, the capability of improving SNR can be analyzed qualitatively by analyzing the performance of VS detection at different distances.

The skewness values obtained from the data sets outdoors are shown in Fig. 12. The distance from the detection subject to the radar antenna is 3, 6, 9, and 11 m, respectively. Figure 13 shows the range estimates based on the developed detection method. The range estimates are 3.079, 6.113, 9.084, and 11.24 m. The frequency estimates are shown in Fig. 14. The estimates are 0.23, 0.23, 0.29, and 0.33 Hz, respectively.

Fig. 12
figure12

The calculated skewness values with normalized amplitude at the distance of a 3 m, b 6 m, c 9 m, and d 11 m away from the antenna

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Fig. 13
figure13

The range estimations using the new method at the distance of a 3 m, b 6 m, c 9 m, and d 11 m away from the antenna

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Fig. 14
figure14

The RF estimations using the new method at the distance of a 3 m, b 6 m, c 9 m, and d 11 m away from the antenna

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By employing the AM, the detection results including the range and frequency estimates based on the acquired data sets outdoors are shown in Fig. 15. The range estimates are 3.942, 6.86, 3.837, and 18.58 m. The respiratory frequency estimates are 0.08, 0.20, 0.14, and 0.78 Hz, respectively. Compared with the results acquired from the AM method, we can see that the developed method can provide range and frequency estimates more accurately. Further, Table 2 gives the detection performance based on different methods.

Fig. 15
figure15

The range and RF estimations using the advanced method at the distance of a 3 m, b 6 m, c 9 m, and d 11 m away from the antenna

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Table 2 Performance with different methods
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Performance indoors

In this section, the data sets acquired indoors are used to test the performance of the developed detection algorithm. Based on the acquired data sets at different distances, the skewness values are shown in Fig. 16. The distances from the radar antenna to the detection subject are 4, 7, 10, and 12 m, respectively. Figure 17 shows the range estimates based on the developed method. The range estimates are 4.122, 7.078, 10.071, and 12.25 m, respectively. The frequency estimates are shown in Fig. 18; the estimates are 0.24, 0.23, 0.22, and 0.27 Hz, respectively.

Fig. 16
figure16

The calculated skewness values with normalized amplitude at the distance of a 4 m, b 7 m, c 10 m, and d 12 m away from the antenna

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Fig. 17
figure17

The range estimations using the new method at the distance of a 4 m, b 7 m, c 10 m, and d 12 m away from the antenna

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Fig. 18
figure18

The RF estimations using the new method at the distance of a 4 m, b 7 m, c 10 m, and d 12 m away from the antenna

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Table 3 shows the detection results by employing the CFAR and the developed method. We can see that the developed method shows better capability of improving SNR than the CFAR method such as SNR is 5.07 dB using the new method while it is − 5.21 dB for the CFAR method at 7 m.

Table 3 Detection performances compared with the reference CFAR method
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Performance of clutter suppression

In this section, the capability of clutter removal is discussed based on the data set acquired at a distance of 6 m from the antenna outdoors. To remove the harmonics, the accumulation method is used for four times in the paper. In this section, several techniques are used as examples to validate the performance of the new method such as the including FFT, EEMD-based one accumulation (OA) method, EEMD-based two accumulation (TA) method, EEMD-based four accumulation (FA) method, and EEMD-based six accumulation (SA) method.

The detection result is shown in Fig. 19a based on the FFT. It can be seen that various clutters exist in the frequency domain with the same band as human respiratory, which makes it challenging to extract VS. The corresponding results based on the EEMD-based accumulation methods for different times are shown in Fig. 19b–e. We can see that the FA method can better remove clutters and improve SNR compared with other methods. Table 4 shows the SNR values based on different methods. It is clear that SNR cannot be further improved even SA is performed.

Fig. 19
figure19

The ability to remove clutter using a FFT, b EEMD-based one FA method, c EEMD-based two FA method, d EEMD-based four FA method, and e EEMD-based six FA method

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Table 4 Detection performances in improving SNR
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Table 5 shows the frequency estimates based on the reconstructed signal from different IMFs. Results indicate VS primarily concentrates upon IMF6 and IMF5. As a result, the VS can be extracted effectively based on the selected IMFs. All results prove the capability of clutter suppression and improving SNR based on the new method.

Table 5 Human respiratory frequency (Hz) estimates based on different IMFs
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Conclusions

This paper presents a new de-noising method for VS detection. The VS information such as the range and respiratory frequency can be estimated based on the developed algorithm more accurately by employing the UWB pulse radar. Further, the EEMD-based accumulation method is proposed to remove harmonics effectively. By analyzing the skewness of the VS, the range can be estimated via applying the DSFT method. Several experiments are conducted in different conditions to show the excellent performance of the developed algorithm. The detection capability of the proposed method is validated compared with several techniques. Results are presented to show the ability to remove clutter and improve SNR.

Abbreviations

AD:

Arctangent demodulation

AM:

Advanced method

AWGN:

Additive white Gaussian noise

CFAR:

Constant false alarm ratio

CSD:

Complex signal demodulation

DSFT:

Discrete short-time Fourier transform

EEMD:

Ensemble empirical mode decomposition

FA:

Four accumulation

FFT:

Fast Fourier transform

IMFs:

Intrinsic mode functions

LTS:

Linear trend subtraction

OA:

One accumulation

RF:

Respiratory frequency

SA:

Six accumulation

SNR:

Signal-to-noise ratio

SVD:

Singular value decomposition

TA:

Two accumulation

UWB:

Ultra-wideband

VS:

Vital signs

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Acknowledgements

The authors would like to thank the anonymous reviewers for their valuable comments and suggestions to improve the quality of the article.

Funding

This work was funded by the National High Technology Research and Development Program of China (2012AA061403), National Science & Technology Pillar Program during the Twelfth Five-year Plan Period (2014BAK12B00), National Natural Science Foundation of China (61501424, 61701462 and 41527901), Ao Shan Science and Technology Innovation Project of Qingdao National Laboratory for Marine Science and Technology (2017ASKJ01), Qingdao Science and Technology Plan (17-1-1-7-jch), and the Fundamental Research Funds for the Central Universities (201713018).

Author information

Affiliations

  1. Department of Electronic Engineering, Ocean University of China, Laoshan District Song Ling Road 238th, Qing Dao, People’s Republic of China

    • Xiaolin Liang
    • , Tingting Lv
    • , Hao Zhang
    •  & Yong Gao

  2. The Key Laboratory of Electromagnetic Radiation and Sensing Technology, Institute of Electronics, Chinese Academy of Science, Haidian District North 4th Ring West Road 19th, Beijing, People’s Republic of China

    • Guangyou Fang

  3. Department of Electrical Computer Engineering, University of Victoria, 3800 Finnerty Road, Victoria, BC, V8P 5C2, Canada

    • Hao Zhang

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Contributions

XL conceived and performed the experiments, analyzed the data, and wrote the paper; TLv, HZ, YG, and GF helped to review and revise the whole paper. All authors read and approved the final manuscript.

Corresponding author

Correspondence to Tingting Lv.

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Keywords

  • Ultra-wideband (UWB) impulse
  • Vital signs (VS)
  • Discrete short-time Fourier transform (DSFT)
  • Ensemble empirical mode decomposition (EEMD)