 Research Article
 Open Access
 Published:
Noise and Speckle Reduction in Doppler Blood Flow Spectrograms Using an Adaptive PulseCoupled Neural Network
EURASIP Journal on Advances in Signal Processing volume 2010, Article number: 918015 (2010)
Abstract
A novel method, called adaptive pulse coupled neural network (ADPCNN) using a twostage denoising strategy, is proposed to reduce noise and speckle in the spectrograms of Doppler blood flow signals. ADPCNN contains an adaptive thresholding PCNN and a threshold decaying PCNN. Firstly, PCNN pulses based on the adaptive threshold filter a part of background noise in the spectrogram while isolating the remained noise and speckles. Subsequently, the speckles and noise of the denoised spectrogram are detected by the pulses generated through the threshold decaying PCNN and then are iteratively removed by the intensity variation to speckle or noise neurons. The relative root mean square (RRMS) error of the maximum frequency extracted from the ADPCNN spectrogram of the simulated Doppler blood flow signals is decreased 25.2% on average compared to that extracted from the MPWD (matching pursuit with Wigner Distribution) spectrogram, and the RRMS error of the ADPCNN spectrogram is decreased 10.8% on average compared to MPWD spectrogram. Experimental results of synthetic and clinical signals show that the proposed method is better than the MPWD in improving the accuracy of the spectrograms and their maximum frequency curves.
1. Introduction
The Doppler ultrasound blood flow signal has been extensively used in clinic to diagnose arterial and venous diseases due to its advantage of being noninvasive [1]. The diagnostic indices which are necessary for a clinical judgment are all extracted from the maximum frequency waveform of the Doppler spectrogram, calculated by using shorttime Fourier transform (STFT), and are very useful in diagnosing arterial stenosis or other vascular disease by evaluating the vascular resistance [2]. However, two types of noise are present in the Doppler spectrogram. Firstly, there is background noise, arising from additional frequency components, added to the Doppler ultrasound signals. Additionally, the characteristic granular pattern, known as Doppler speckles, of spectrogram is obtained from Fourier transformbased analyzers when the Doppler signal scattered from cells moving within the same velocity resolution cell interferes with each others [3]. Noise and speckle, which are considered as undesirable properties, directly impact on the subjective study of the maximum frequency waveform extracted from the spectrogram, deteriorate the quality and the perceivable resolution of the indices and the features based on the estimated spectrograms and thus lead to inaccuracy in diagnoses of the artery diseases. Therefore, it is preliminary and essential to remove noise and speckles in the spectrogram of the Doppler ultrasound signal.
Discrete wavelet frames (DWFs), which is superior to methods based on standard discrete wavelet transform (DWT), were used to denoise the Doppler ultrasound signal [4]. Here discrete wavelet frame analysis was first applied to obtain the wavelet coefficients of the Doppler signal at multiple scales. Then, these coefficients were processed by a soft thresholdingbased denoising algorithm to remove noise in the signal. In order to improve the adaptability of the threshold, a thresholdbased wavelet packet denoising method was employed [5]. This approach, which can adaptively select the threshold, preserved useful high frequency components and offered higher signaltonoise ratio (SNR) compared with straightforward waveletbased denoising methods. The matching pursuit (MP) method was also used for improving the SNR of Doppler blood flow signals [6]. Using MP, the denoised Doppler signal was reconstructed by iteratively selecting the components approximate to the signal by a given directory while removing the incoherent residue, which was determined as noise, through a decay parameterbased algorithm. The performance of the MP method was better than those of the DWT and WPs (Wavelet Packets) methods for Doppler ultrasound signal denoising [6]. These denoising methods are effective in removing background noise in the Doppler spectrogram. However, they cannot suppress Doppler speckles in the STFT spectrograms due to the fact that background noise is usually random Gaussian distribution while speckle may be modeled by Rayleigh or distribution [7, 8].
To alleviate the negative effect of the speckle, two types of specklereduction approaches, ensemble averaging and filtering [9], have been developed. Ensemble averaging approach is usually achieved by averaging a series of regular spectrograms produced by a flow phantom. However, physiological changes such as heart rate variation make the synchronization of the required waveforms difficult. Moreover, these uncorrelated images may be sampled at different times, from different views, or with different frequencies for the same target. Therefore, ensemble averaging is complex in clinical implementation. The filtering approaches, which treat the Doppler spectrogram as a grayscale image, offer an alternative for clinical applications, and many adaptive filters have been developed. Filtering approaches eliminate the speckle at each pixel based on the local statistics estimated from the Doppler spectrogram. However, the spatial spectral content of sharp intensity variations, such as edges contained in images, extends to infinity and overlaps with noise. Therefore, filters suppress noise while blurring important informationbearing features and fine image details. Meanwhile these speckle reduction methods become ineffective in filtering Doppler background noise and cause loss of the timefrequency resolution in the STFT spectrograms.
In order to effectively suppress Doppler noise and speckle in the STFT spectrograms, a method, called matching pursuit with Wigner distribution (MPWD), was proposed and has obtained good performance in noise and speckle suppression [10]. Using MPWD, a segmented Doppler ultrasound signal was first decomposed by MP greedy iterations for denoising purpose, and then the Wigner distribution was calculated and averaged during each small interval to reconstruct the spectrogram of the denoised signal for Doppler speckle reduction. Since the time interval is small, the Doppler speckle can be effectively smoothed. Meanwhile, this method may not cause the loss of timefrequency resolution in spectrograms as the interval is small enough, and it also does not require invariant heart rate to produce the very regular spectrograms. However, since MP is a greedy iteration and the Wigner distribution is calculated and averaged based on each small time interval, the MPWD is implemented at a high expense of computing complexity. Moreover, since the decomposition continues until the decay parameter is less than a predefined small value and the averaging interval is empirically selected, the MPWD method cannot completely remove all the background noise, and the adaptability of the method is relatively low.
To compensate for the drawback of the previous techniques, a method, called adaptive Pulse Coupled Neural Network (ADPCNN), is proposed for noise and speckle reduction in the spectrograms of Doppler blood flow signals, while improving the accuracy of the spectrograms and their maximum frequency curves. PCNN biologically inspired from the visual cortex of mammals was first introduced by Eckhorn in [11] and has been widely used for image denoising [12–17]. The pulse capture characteristics of PCNN determine that the neurons that spatially connected and intensity correlated are tend to pulse together, while Doppler noise or speckle, which is independent and uncorrelated to the signal component, can not capture neighboring neurons or can not be captured by neighboring neurons. Thus each contiguous set of synchronously pulsing neurons indicates a coherent structure of the spectrogram, corresponding to the signal component, and the residue, defined as Doppler noise or speckle, can be identified. However, when conventional PCNN is applied for noise and speckle reduction, present theories cannot explain the relationship between the parameters of PCNN mathematical model and the processing effect. Satisfactory results usually require timeconsuming selection of experimental parameters. Meanwhile, in a properly selected parametric model, the number of iteration that determines the denoising effect is evaluated by visual judgment, which decreases the efficiency of PCNN. Various improved PCNN models have developed for noise filtering, such as weightedlinking PCNNs [12], which contains four PCNN models to filter Gaussian and impulse noise in images, and a twostep PCNN impulse noise filter [13], which first determines the noisy pixels and then modifies the intensities of noisy pixels in the image. In addition PCNN was combined with other new techniques such as fuzzy, rough set theory and morphology to depress noises [14–17] meanwhile adaptively determining the PCNN parameters. However the computational complexity is therefore increased. These PCNN denoising approaches are proved to be effective in removing isolated noise while the performance of filtering Gaussian noise is degraded since all pixels in an image are contaminated by Gaussian noise. Therefore, conventional PCNN or existing PCNNs cannot be directly applied to suppress noise and speckles in Doppler spectrogram.
In order to improve the adaptability of parameter selection, decrease the computation redundancy of conventional PCNN algorithm, and to be effective in suppressing noise and speckles in Doppler spectrogram, an adaptive PCNN, which contains an adaptive thresholding PCNN and a threshold decaying PCNN is proposed. The proposed PCNN is greatly simplified compared to conventional PCNN and employs an adaptive threshold, which is defined as the basic intensity of the signal component based on the histogram of the spectrogram. The proposed PCNN is a twodimensional structure with the same size of the Doppler spectrogram, and each neuron is corresponding to a pixel in the spectrogram. The PCNN pulses based on the adaptive threshold decompose the spectrogram into two parts of neurons, coherent structure which is spatially connected and intensity correlated and incoherent component, indicating the signal and noise or speckle in the spectrogram, respectively. After removing a part of noise from the coherent signal, the rule, the Gaussian distribution of the background noise and the Rayleigh or distribution of speckle is broken, and the remained noise or speckle is greatly isolated. Subsequently, the firing matrix of the denoised spectrogram, specifying what time a neuron first fires, is calculated by using the threshold decaying PCNN through iterations, and then the target neuron is detected as a speckle or noise if it fires but more than 50% of the neurons in the linking window do not fire [13], indicating that the intensity of the target neuron is sharply variant compared to other neurons in the linking window. Finally, spectrograms are improved by iteratively suppressing the speckles or noise through a median filter [13], while the signal neurons are kept unmodified. Experiment results show that the proposed method can effectively conserve fine detail information, such as edges while removing speckles and noise. Furthermore, the iteration continues until the firing matrix of the threshold decaying PCNN is unchanged any further. Therefore, the iteration time can be adaptively determined.
The distinctive elements of the proposed method are as follows. () a twostep PCNN model is proposed for noise and speckle suppression in Doppler spectrogram. Firstly an adaptive threshold, taking advantages of the pulse capture characteristics of PCNN and the histogram statistics of the spectrogram, is employed to filter noise from the signal component in the spectrogram. () After a part of background noise is removed by the adaptive threshold PCNN, the remained noise and speckle are greatly isolated and the rule, that background noise is usually Gaussian distribution and speckle is molded by Rayleigh or distribution, is broken. Therefore the isolated noise and speckle can be effectively suppressed by the proposed threshold decaying PCNN, which first detects noise and speckles and then iteratively suppresses the noise and speckles with a median filter. () It is the first attempt to reduce noise and speckles for Doppler ultrasound spectrogram by using PCNN algorithm. The indices, the relative rootmeansquare (RRMS) errors of the spectrograms, and their maximum frequency curves between the estimated ones and their corresponding theoretical ones are used to evaluate the performance of the proposed method. Furthermore, effective noise and speckle suppression methods, MP and MPWD [10], are compared with the proposed method.
The remainder of this paper is organized as follows. Section 2 briefly describes the mathematical background of the MPWD and the proposed ADPCNN noise and speckle reduction methods. Section 3 presents the simulation of the Doppler blood flow signals and experiments on simulated Doppler signals and clinical cases based on two different methods, ADPCNN and MPWD [10]. Section 4 exhibits experimental results and discussions. Finally, some conclusions are drawn in Section 5.
2. Methods
2.1. MPWD Noise and Speckle Reduction Algorithm
The principle of matching pursuit is to decompose a signal into the linear superposition of the basis function () that belongs to a redundant dictionary . After greedy search a is gained, which best matches the signal structures, and the signal can be decomposed into
where is a signal residuum after approximating in the direction of . Obviously, is orthogonal to , so
To minimize , we must choose such that is maximized, which is the first step of the approximation procedure. It is repeated iteratively into the residual signal obtained. If the decomposition is performed times, is decomposed into a sum of atoms and of the thorder residue :
In the present study, the discrete implementation of a matching pursuit for a Gabor dictionary is employed [18]. It is supposed that the signal is real and have samples. At any scale , the window function is defined as
where the constant normalizes the discrete norm of to 1. For any integer and , we denote , then the real discrete atoms of matching pursuit implementation with Gabor dictionary are given by
with is such that .
MP is an iterative algorithm. When the MP is applied for denosing purpose, the atoms which are best coherent to the dictionary are isolated as the signal, and the residue is defined as noise at each iteration. The decomposition, which is determined by a decay parameter [18], is stopped after extracting the first coherent structures of the signal. The first coherent structures are determined using a decay parameter, denoted by
where is the residual energy level at the M th iteration. The decomposition is continued until the decay parameter does not reduce any further. At this stage, the selected components represent the coherent structures, and the residue represents the incoherent structures in the signal with respect to the dictionary.
After extracting the first M coherent structures, a timefrequency energy distribution that is free of crossterms is derived by adding the Wigner distribution of selected atoms
where is the Wigner distribution of the selected atom :
In the processing, the Doppler signal is divided into successive small segments, each one has a time interval . The Wigner distribution in a time interval, estimated from the denoised signal by (7)(8), is averaged during this time duration for Doppler speckle reduction in the spectrum. Since the time interval is small, the Doppler speckle, which arises from the interference with each other of cells moving within the same velocity resolution cell, could be smoothed. Meanwhile, this method may not cause the loss of timefrequency resolution in spectrograms as the is small enough, and it also does not require the invariant heart rate to produce the very regular spectrograms, one of the limitations of the ensemble average speckle suppression method. However, since MP is a greedy iteration and the Winger distribution is calculated and averaged based on each small time interval , the MPWD is implemented at a high expense of computing complexity. Moreover, since the decomposition continues until the decay parameter is no more than a predefined small value and the averaging interval is empirically selected, the MPWD method cannot completely remove all the background noise.
2.2. Adaptive PCNN Noise and Speckle Reduction Algorithm
The adaptive PCNN network model of neuron is shown in Figure 1(a), where is the feeding, is the linking, is the dynamic threshold, is the internal activity, and and are the pulse output of the adaptive threshold PCNN and the threshold decaying PCNN, respectively.
The feeding field corresponds to the input impulse signal :
The linking field accepts input from an eightneuron linking window, shown in Figure 1(b):
where , which means each neuron is connected in a neighboring field and the neighboring field does not include the neuron itself. Therefore the center element of is equal to 0, but not 1. The linking inputs are biased and then multiplied with the feeding input to form the internal activity :
The pulse generator of the neuron consists of a stepfunction generator and a threshold signal generator. At each firing step, the neuron output is set to 1 when the internal activity is greater than the threshold ; otherwise the output is set to 0:
The threshold of PCNN for removing background noise in the Doppler spectrogram is adaptively defined as the basic intensity of the signal estimated from the histogram of the spectrogram. Suppose the PCNN contains neurons distributed on intensity levels , which is normalized into , the intensity histogram of Doppler spectrogram is expressed as
where indicates the number of the neuron with intensity and . A Doppler spectrogram contains three elements, which are background, signal, and noise or speckle. Therefore, the three extreme values shown in the intensity histogram of the spectrogram correspond to the basic intensities of these three elements. Consequently, the two extreme values whose intensities are less than 1 in the histogram represent the basic intensity of noise and signal components, respectively,
where , and are the two extreme values on the histogram of the Doppler spectrogram, and and are the intensities corresponding to the two extremes, respectively. The intensity of the signal is lower than that of the noise in the Doppler spectrogram. Therefore, the adaptive threshold for denoising the spectrogram is defined as
After filtering a part of background noise from the spectrum, a threshold decaying PCNN is employed to detect and suppress the remained noise and speckles, where the threshold is defined as
where is the decaying parameter. The firing matrix of the threshold decaying PCNN denotes what time each neuron first fires and is calculated through times of iteration:
The iteration is continued until the firing matrix does not change any further to adaptively determine the iteration time .
During the firing procedure, the intensity value of each pixel and the status of its neighbors (active or inactive) determine what time a neuron fires. Neurons in the same region or with an approximate value tend to fire at the same time. When there are pixels whose intensity values are approximate in their linking region, the pulse output of one of them will fire the others in the linking region, and then produce a firing matrix. Obviously, the firing matrix of PCNN includes the information of the image intensity distribution and the geometry of the original image, which makes noise and speckle detection possible.
When using ADPCNN for noise and speckle reduction in Doppler spectrogram, in the first step, since the threshold is defined as the basic intensity of the signal, the firing matrix of the adaptive threshold PCNN separates noise, independent and uncorrelated to the signal components, from the signal neurons, which are spatially connected and intensity correlated and then remove the detected noise. Subsequently, the firing matrix of the threshold decaying, indicating what time a neuron first fires, is calculated. If the target neuron fires but more than 50% the neurons in the filtering window do not fire, it denotes that the target neuron has sharp intensity fluctuation and can not capture most of the other neurons in the filtering window; therefore, it is detected as noise or speckle. Finally, the noise and speckle pixels are modified to be the median intensity values in the filtering window and are removed. Since the threshold decaying PCNN detects noise and speckle first and performs intensity variation to the noise and speckle only, the fine image details, such as edges, can be well preserved.
3. Experiments
In the experimental study, simulated and clinical Doppler ultrasound signals are used as test sources. The two algorithms, ADPCNN and MPWD [10], are used to reduce noise and speckle for the simulated Doppler ultrasound signals with a 1024point duration. The performance of noise and speckle reduction in Doppler spectrogram based on the ADPCNN is compared with that based on the MPWD method.
3.1. Simulation Study
A signal model proposed by Mo and Cobbold [19] is used to simulate the onedirectional Doppler signal of the carotid artery, by which the performance of the ADPCNN is evaluated. The maximum frequency waveform used in the simulation is shown in Figure 2, and the details of this simulation model can be found in the work by Mo and cobbold [19]. The sampling frequency is 20 kHz, above the Nyquist rate; the cardiac cycle period is 1000 ms. Thirty realizations of the Doppler signal of the carotid artery are simulated on cardiac cycle basis by changing the random seed used in the model. The prespecified SNRs (SNR = 0 dB, SNR = 5 dB, and SNR = 10 dB) are obtained by adding white Gaussian noise to the simulated Doppler signals.
For the STFT spectrogram, a 10 ms window is normally used in practice because the signal is assumed to be stationary over this segment. The Gaussian window, which produces best compromise between the time and frequency resolution [20], is chosen in the present study for the STFT analysis. The signal is divided into 100 intervals, each of which has a 10 ms time duration, and their frequency spectra are calculated respectively,
where is the window, and are the discrete time and frequency, respectively, and is the window length.
A 200point fast Fourier transform (FFT) is computed for each windowed signal segment. Within onesecond cardiac period, 100 spectra are computed. This signal is divided into 100 intervals, each of which has a 10 ms time duration for the MPWD method, in which the Doppler signals are decomposed and denoised according to the decay parameter algorithm [10]. The STFT spectrograms of the original simulated Doppler signals and the MPbased denoised signals, and the MPWD spectrograms calculated by adding and averaging the Wigner distribution of selected atoms, are estimated for comparison. For the proposed ADPCNN noise and speckle reduction algorithm, Figure 3 shows the coarse structure of such a proposed method, and the detailed algorithm is described below, which can be directly implemented by MATLAB or C language.

(1)
The pixel intensity of the original Doppler spectrogram is normalized to and input to . Initialize , , , , , as a weightmatrix of linking field, and as a temporal matrix. Calculate by (13)–(16).

(2)
Calculate linking field by (10).

(3)
, , and .

(4)
If go to (5); else, go back to (3).

(5)
.

(6)
Set , , , , , , and iteration time .

(7)
, .

(8)
, , , and .

(9)
In a filtering window, if the target neuron fires but more than 50% the neurons do not fire, then the target neuron is identified as a speckle or noise [13]. Modify the intensity of the target neuron to be the median intensities of the neurons in the filtering window. Otherwise, keep the target neuron unchanged.

(10)
If stop, and output the spectrum after noise and speckle reduction; else, go to (7).
The maximum frequency waveforms are extracted from the spectrograms. The indices, the RRMS errors of the spectrograms, and their maximum frequency curves between the estimated ones and their corresponding theoretical ones are used to evaluate the performance of the proposed method for noise and speckle suppression in the spectrograms:
where and are the simulated original signal and the signal after noise and speckle suppression of the length , respectively. The RRMS errors of the spectrogram and their maximum frequency waveform from 30 simulated signals are calculated before and after noise and speckle suppression and are used to compare the performance improvements of the ADPCNN algorithm to that by MPWD.
3.2. Clinical Study
To obtain the clinical Doppler ultrasound signal, a pulsed Doppler unit of HP SONOS 5500 ultrasound imaging system is used in pulse mode, and the applied frequency of the ultrasound is set to 2.7 MHz. The clinical Doppler signals are recorded from a child's aorta by placing sample volume near the center of the aortic arch. The audio Doppler signals are sampled by using an analogtodigital Sound Blaster Card in a personal computer, and the sampling rate is set to 22.05 kHz. The objective effect and subjective indices of the spectrogram and their maximum frequency waveform are used to compare the performance of the ADPCNN and the MPWD noise and speckle suppression algorithms.
4. Results and Discussions
Figure 4 presents the STFT, MP, MPWD, and ADPCNN spectrograms and their maximum frequency waveforms, which are superimposed on the spectrograms with the solid curves, of a simulated original, MPbased and PCNNbased noise and speckle reduced Doppler signals with different noise levels (SNR = 0 dB, 5 dB, and 10 dB), respectively. In Figures 4(f), 4(k), and 4(p), it can be observed that the STFT spectrograms estimated from the signals with different noise levels (SNR = 0 dB, 5 dB, and 10 dB) include a mass of disturbance distributed in whole frequency band. The maximum frequency waveforms extracted from these estimated spectrograms include considerable distortion and illegibility, which implies the difficulty in finding correct indices used for quantification of vascular diseases' severity from the spectrograms. However, compared with the theoretical spectrogram shown in Figure 4(a), the disturbance components in both the MP spectrograms (shown in Figures 4(g), 4(l), and 4(q)) and the MPWD spectrograms (shown in Figures 4(h), 4(m), and 4(r)) have been significantly suppressed because these spectrograms are estimated from the denoised signals by using the MPbased denoising method. But obvious Doppler speckles can be found in the all STFT spectrograms estimated from the signals without added noise (shown in Figure 4(b)), signals added different noise levels (shown in Figures 4(f), 4(k), and 4(p)), and MPbased denoised signals (shown in Figures 4(g), 4(l), and 4(q)). This means that the MPbased denoising algorithm, which can effectively reduce the random noise in Doppler signals, can not suppress the Doppler speckle in the STFT spectrograms. From Figures 4(c), 4(h), 4(m), and 4(r), it can be found that the Doppler speckles in the MPWD spectrograms have been obviously suppressed. However, the MPWD spectrograms inevitably include background noise and discontinuity. Meanwhile, the computing complexity of MPWD is high since MP is a greedy algorithm, and Wigner distribution is calculated and averaged based on each small time interval. The background noise in the PCNNdenoised spectrogram (shown in Figures 4(d), 4(i), 4(n), and 4(s)) has been partly removed, and the remained noise has been greatly isolated so that it can be effectively reduced by using the threshold decaying PCNN. From Figures 4(e), 4(j), 4(o), and 4(t), it is obvious that the Doppler random noise and speckles can be effectively removed by using ADPCNN. The spectrograms and their maximum frequency waveforms obtained by using the ADPCNN are much closer to the theoretical one than those by using the MPWD.
Table 1 lists the mean and standard deviation of the RRMS errors of the maximum frequency waveforms extracted from the spectrograms of the 30 independent realizations of Doppler signals with SNR = 0 dB, 5 dB, 10 dB and based on the MP, the MPWD, and the PCNNbased methods, respectively. From Table 1 it can be concluded that the RRMS errors of the maximum frequency waveforms extracted from the PCNN spectrograms have decreased much more than those before noise and speckle reduction. For example, the RRMS errors of the maximum frequency waveforms of the original STFT are 2.92 and 3.84 times higher than those denoised by using MPWD and ADPCNN on Doppler signals with SNR = 10 dB, respectively. While the MPWD has presented the RRMS errors of the maximum frequency waveforms , , and results on Doppler signals with SNR = 0 dB, 5 dB, 10 dB, and , respectively, the ADPCNN has presented the RRMS errors 9.68%, 38.10%, 31.58%, and 21.43% decrease compared to MPWD spectra. Table 2 lists the mean and standard deviation of the RRMS errors of the spectrograms of the 30 independent realizations of Doppler signals with SNR = 0 dB, 5 dB, 10 dB, and based on the STFT, the MPWD, and the PCNN methods, respectively. Table 2 indicates that the Doppler noise and speckles in the STFT spectrograms have been greatly suppressed by using MPWD and ADPCNN. For example, the RRMS errors of the spectrogram of the original STFT are 1.65 and 1.83 times higher than those denoised by using MPWD and ADPCNN on Doppler signals with SNR = 10 dB, respectively. While the MPWD has presented the RRMS errors of the spectrogram , , and results on Doppler signals with SNR = 0 dB, 5 dB, 10 dB, and respectively, the ADPCNN has presented RRMS errors 9.52%, 9.52%, 10.0%, and 10.0% decrease compared to MPWD spectra. It is found that in all cases, the RRMS errors of the maximum frequency waveforms and the spectrograms based on the ADPCNN method are smaller than those based on the STFT and MPWD, which means that the ADPCNN spectrograms are much closer to the theoretical ones and contain least extra frequency components and least distortion in the estimated maximum waveforms.
When the MPWD and the ADPCNN algorithms are applied to process the clinical Doppler ultrasound signals, all of the cases show that the ADPCNN achieves better performance for suppressing noise and speckles in the spectrograms and smoothing the maximum frequency waveforms. As an illustration, the spectrogram and its maximum frequency waveform of a segment of Doppler ultrasound signal recorded from a child's aortic arch based on the MP, the MPWD, and the ADPCNN algorithms are shown in Figure 5. From Figure 5(b), we can observe that the MPdenoised spectrogram has fewer additional noise and distortion than the original STFT spectrogram shown in Figure 5(a). The superimposed maximum frequency waveform also confirms that MP achieves a good denoising performance. However, Doppler speckles in the MP spectrogram are obvious. As observed in Figure 5(c), the random noise and Doppler speckles have been suppressed in the spectrogram by using the MPWD method. However, the MPWD spectrogram inevitably includes background noise. From Figure 5(d), it is obvious that the Doppler random noise and speckles are effectively suppressed; meanwhile the superimposed maximum frequency waveform indicates that the ADPCNN obtains a better noise and speckle reduction performance than MPWD.
5. Conclusions
A novel method, ADPCNN has been proposed to enhance Doppler blood flow spectrograms. First, the Doppler spectrograms are denoised by using the adaptive threshold PCNN, which removes background noise from the coherent component with spatiality vicinity and intensity correlation in the Doppler spectrogram and isolates the remained noise. Then, the firing matrix of the denoised spectrogram, calculated by the threshold decaying PCNN is employed to detect speckles. Finally the improved spectrogram is reconstructed by modifying the speckles to be the median intensity in the filtering window. Results from the experiments on simulation and clinical signals show that the proposed method performs effectively in noise and speckle suppression, improves the accuracy of spectrograms and their maximum frequency curves, and achieves better performance than MPWD algorithm. The RRMS errors of the ADPCNN spectrograms and the extracted maximum frequency of simulated Doppler blood flow signals are decreased by 10.8% and 25.2% on average when compared to MPWD spectrograms on Doppler signals with various SNRs, respectively.
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Acknowledgments
This paper was supported by Grant (60861001) from the National Natural Science Foundation of China, Grant (2009CD016) from the Yunnan Natural Science Foundation, Grant (2008YB009) from the Science and Engineering Fund of Yunnan University, and Grant (21132014) from the Young and Middleaged Backbone Teacher's Supporting Programs of Yunnan University.
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Li, H., Zhang, Y. & Xu, D. Noise and Speckle Reduction in Doppler Blood Flow Spectrograms Using an Adaptive PulseCoupled Neural Network. EURASIP J. Adv. Signal Process. 2010, 918015 (2010). https://doi.org/10.1155/2010/918015
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Keywords
 Doppler Signal
 Wigner Distribution
 Matching Pursuit
 Relative Root Mean Square Error
 Pulse Couple Neural Network