Coding ultrasound based multi-depth blood flow measurement

LI Shao-xing, ZHANG Tian-jiong, CHEN Xin, QIN Zheng-di

?

Coding ultrasound based multi-depth blood flow measurement

LI Shao-xing1,2,3, ZHANG Tian-jiong1,2,3, CHEN Xin1,2,3, QIN Zheng-di1,2,3

(1. National-Regional Key Technology Engineering Laboratory for Medical Ultrasound, Shenzhen 518060, Guangdong, China;2. Guangdong Key Laboratory for Biomedical Measurements and Ultrasound Imaging, Shenzhen 518060, Guangdong, China;3. Department of Biomedical Engineering, Health Science Center, Shenzhen University, Shenzhen 518060, Guangdong, China)

Blood flow measurement and imaging are important contents in ultrasound diagnostics, which have been widely used in clinical practice because of their unique advantages. However, conventional Transcranial Doppler (TCD) ultrasound system in domestic markets is mainly an analog circuit system with complicated structure. Such instruments are susceptible to external changes and cannot offer a multi-depth blood flow examination. In this study, a multi-depth digital design of TCD ultrasound system is introduced, which can make up for the disadvantages of the traditional analog systemsThis system can achieve a multi-depth inspection and improve the detection sensitivity of the system, the average transmitted energy and system resolution. Furthermore, the feasibility of the system is proved by the phantom test, pump and clinical experiments. All of the results show that the system can display the blood flow information on the path of the ultrasound wave, detect and identify the vessel position. Meanwhile, it can also greatly improve the measurement sensitivity.

coded excitation; transcranial Doppler; multi-depth examination

0 INTRODUCTION

Transcranial Doppler (TCD) ultrasound system has been used successfully in diagnostics for decades. The advantages of the system, such as real-time detection and noninvasive clinical diagnosis, are appreciated by users. Compared with other imaging models, TCD plays an important role in the diagnosis of cardiovascular disease[1-2]. Currently, the techniques of I/Q demodulator, depth-sampling, and wall signal depressing are realized in analog circuits, so most TCD systems are still analog systems. In addition, digital processing portion has been used for spectrum analysis and result display, however strictly, this is just an analog plus digital system[3]. Due to the instability and inconsistency of the components in analog circuits, signal distortion could happen in the I/Q demodulator channel, which would cause the confusion in the direction of blood flow signal. Furthermore, use of analog demodulation can merely detect blood flow information at less depth points. To carry out multi-depth detection and increase sampling points, the number of devices and the volume of the TCD system will be greatly increased. As a result, using conventional TCD ultrasound system becomes impractical and impossible to achieve multi-depth detection and coded excitation imaging[4].

In this paper, a full digital design of TCD system using coded excitation is introduced. Ultrasonic echo signals input into an analog to-digital (A/D) converter, and store in PC's hard disk. Techniques of digital demodulation, decoding, and spectral estimation processing perform on the computer. Since most of data processing has been categorized by digital micro-processing chip, the system can greatly reduce the size of hardware circuits, system complexity and power consumption. When implemented with digital design this system could easily display the blood flow information on the path of the ultrasound wave. Meantime, the code excitation technology can be entered. In this design, the coded transmitting signal is an over-sampled 7-chip Barker code[5-7] modulated by 4 wavelengths basic pulse sequence. Finally, some experiments are performed to test the system.

1 METHODS

1.1 Data processing

After analog to digital converter, ultrasonic echo data save in a variable as a vector in MATLAB (v. 2009a: MathWorks, Natick, MA, USA). After band-pass filtering, the echo data processing techniques, such as digital I/Q demodulation, decoding and down-sampling, are used to generate a row vector. Then the vector is reshaped as a*dimensional matrix.is the sample data at a certain depth, and M is the number at a specified time. To reduce the Gibbs effect, a window of Hanning in the time domain is used[8].

Whererepresents the data after putting the window function of Hanning on, andrepresents a time domain window function. The data analysis ofbased on Fourier transform and suitable windowing operation in frequency domain is as follows[8]:

whereis the data after Fourier transform, andis a window function in frequency domain. Finally, the blood flow information on the path of the ultrasound wave is obtained from matrix.

1.2 Digital I/Q demodulation

The data processing of digital I/Q demodulation technique plays an important role in TCD system. Generally, when implemented with an analog demodulation method, it will bring a series of inevitable shortcomings appearing in gain balance, quadrature phase balance, DC offset, impedance matching and carrier leakage component drift. However digital I/Q demodulation can solve the problem that analog components encountered. The program of digital I/Q demodulation[9] is shown in Fig.1.

Fig.1 Block diagram of digital I/Q demodulator

To reduce data processing in the TCD system, the sampling frequency of the transmitting signal should be an integer multiple of a carrier frequency, and be in the same clock source. In the experimental system, the transmitting carrier frequency of the probe is 2 MHz, and the sampling frequency for the digital signal is four times. After digital I/Q demodulation, the complex signal also should be filtered to eliminate carrier leakage.

1.3 Coded excitation

Coded excitation can improve the system signal-to-noise ratio to the range of 15- 20 dB[10]without increasing the transmitting pulse peak power and affecting the resolution. In our experiments, the coded transmitting signal is an 7-chip Barker code (={1, 1, 1, -1, -1, 1, -1})[11]. Actually, coded excitation could be viewed as a signal modulation, so the process of coded excitation could be viewed as a secondary modulation. The coded sequence is over-sampled before it is loaded to wide emission threshold. Then, it is demodulated by a 2 MHz carrier signal. The process of an over-sampled 7-chip Barker code demodulated by 4 wavelengths base pulse sequence is shown in Fig.2.

Fig.2 Schematic diagram of coded excitation waveform

2 RESULTS

2.1 Doppler phantom experiment

To verify the effectiveness of the system, a Doppler phantom experimental system is set up. As is shown in Fig.3, a Pulsating pump and a Doppler ultrasound phantom are the main instruments required for the experiment.

Fig.3 Schematic diagram of simulated blood circulation device

In this study, there are two kinds of excitation methods. One is single-pulse excitation, and the other is 7-chip Barker code excitation. Both of the excitation methods have the same excitation pulse width and RF energy. As illustrated in Fig. 3, there are two imitation blood vessels which are located just below the ultrasound transducer about 2.5 cm and 3.5cm. The purpose of the experiment is to achieve a multi-depth inspection, which could verify the effectiveness and practicality of this system, and probe whether code excitation could improve the axial resolution. According to the curves in Fig.4, Pnon-codedis the result from the single-pulse excitation system and Pcodedis the result from of the system using coded excitation.

Fig.4 Results of pulse excitation and coded excitation

It could be easily observed that there is only one blood flow message in the single-pulse excitation system. Actually, blood flow signals aliasing is the direct reason, which results in confusion with imitation blood vessels. However, experimental results show that peak amplitude value is greatly improved by coded excitation, and the two opposing blood flow messages are clearly presented in Fig.4. It could be seen that the forward and reverse blood depth values of the coded system are about 2.541 cm and 3.465 cm, respectively, which are consistent with the real depths of two simulated blood vessels. Compared with single-pulse excitation, it is clear that the coded excitation system could significantly improve the vertical resolution. What’s more, as the transmission power is reduced, the axial resolution as well as the SNR is still better than the normal pulse system.

2.2 Analysis of human experiment and result

When implemented with full digital design of TCD, it could visually observe the blood flow information on the path of the ultrasound wave. Doctors could easily find the location of the blood vessel from the blood flow information. In order to find the differences between the single-pulse excitation and the code excitation, in our experiment, both of the excitation methods are designed to compare the sensitivity and reliability of detection. Fig.5 shows the blood flow information image from right temporal window detection of artery (MCA)[12] of the human body.

As is shown in Fig.5,non-codedis the result of single-pulse excitation, andcodedrepresents the result of coded excitation. The curves clearly show the differ- ence between the results of the two different excitation systems. It is obvious that the peak amplitude of thecoded excitation is higher than that of the single-pulse excitation. Under the same normalization condition, the sensitivity and axis resolution of the codes excitation is higher than those of the single- pulse excitation.

Fig.5 Results of single-pulse excitation and coded excitation through temporal window

3 DISCUSSIONS

In the experiment of the codes excitation system, the coded signal is generated by a 7-chip Barker code modulated by 4 wavelengths of base pulse sequence. According to the study of the coded sequence and the decoding filters, such as matched filter, inverse filter, and spike filter, it is found that the number of base pulse sequences is related to the SNR gain and the peak of sidelobe level after pulse compression. When implemented with a shorter coded sequence, it could get a better SNR gain. However, with the increasing of base sequence, the side lobes and random noise are no longer at a low level.

The base pulse sequence length is related to the SNR gain. It could be found that when the base pulse sequence is extended into a larger sequence, the peak of sidelobe level will be higher after pulse compression, which would result in an increase of accumulated time domain. Therefore, it should take a shorter base pulse sequence to improve performance of pulse compression. Due to limitations of the system bandwidth of the probe and other conditions, it is suitable to use the 4 wavelengths base pulse sequence[13].

In this paper, a full digital design of TCD ultrasound system using coded excitation is presented. Meanwhile, the effectiveness and the applicability of the system in theory and the experiment are verified. For this design, a lot of experiments are performed, such as Doppler phantom experiments, pulsating pump experiments, and clinical trials. To get the blood flow information, a large amount of echo data are collected and analyzed. Finally, the power spectrum of the blood flow information is drawn out by using the modern digital signal processing technology. The idea of coded excitation in the TCD system for the blood velocity detection could easily detect the depth of the blood vessel from the blood flow information and improve the axis resolution. In our future study, many new signal processing techniques will be also conducted with the full digital design.

[1] Aaslid R, Markwalder TM, Nornes H. Noninvasive transcranial Doppler ultrasound recording of flow velocity in basal cerebral arteries[J]. Journal ofNeurosurgery, 1982, 57(6): 769-774.

[2] GAO Shangkai. Medical imaging systems [M]. Beijing: Tsinghua University Press, 2000: 88-14.

[3] Li J, Diao X, Zhan K, Qin Z. A Full Digital Design of TCD ultrasound system using normal pulse and coded excitation[C]. Springer International Publishing, 2015, 47: 136-139.

[4] Misaridis T X, Gammelmark K, J?rgensen C H, Lindberg N,Thomsen A H, Pedersen M H, Jensen J A. Potential of coded excitation in medical ultrasound imaging [J]. Ultrasonics, 2000, 38(1-8): 183-189

[5] Barker R H. Group synchronization of binary digital systems [M]//Jackson W, eds. Communication Theory. London: Butterworths, 1953: 273-287.

[6] Welch L R, Fox M D. Practical spread spectrum pulse compression for ultrasound tissue imaging[J]. IEEE Transactions on Ultrasonics Ferroelectrics and Frequency Control, 1998, 45: 349-355.

[7] Qin Z D, Chen S P, Chen X. Coded transmission for ultrasound Doppler detection using truncated long code, Biomedical Engineering and Informatics (BMEI)[C]// 2010 3rd International Conference on, vol. 1, pp. 159-161, 16-18 Oct. 2010.

[8] WAN Mingxi. Biomedical ultrasonics[M]. Beijing:Science Press, 2010: 339-369.

[9] QI M C, GAO S K. Study on a Digital Doppler Ultrasonic Blood Flow Measurement System[J]. Chinese Journal of Biomedical Engineering, 2012, 31(3):349-353.

[10] O ' Donnell M. Coded excitation system for improving the penetration of real - time phased - array imaging systems[J]. IEEE transactions on ultrasonics , ferroelectrics , and frequency control, 1992, 39 (3): 341-351

[11] Peng Q Y, Gao S K. Coded excitation and its applications in medical ultrasound imaging[J]. Journal of Biomedical Engineering, 2005, 22(1): 175-180.

[12] Moehring M A, Spencer M P. Power. M-mode Doppler (PMD) for observing cerebral blood flow and tracking emboli[J]. Ultrasound in medicine & Biology, 2002, 28(1): 49-57.

[13] Xiang L, Gao S K. Coded excitation in pulsed wave Doppler ultrasound blood flow measurements[J]. Journal of Tsinghua University (Natural Science), 2008, 48(6): 1032-1035.

編碼超聲血流多深度檢測

李紹興1,2,3，張?zhí)炀?,2,3，陳昕1,2,3,覃正笛1,2,3

(1. 醫(yī)學(xué)超聲關(guān)鍵技術(shù)國家地方聯(lián)合工程實(shí)驗(yàn)室，廣東深圳518060； 2. 廣東省生物醫(yī)學(xué)信息檢測與超聲成像重點(diǎn)實(shí)驗(yàn)室，廣東深圳518060； 3. 深圳大學(xué)醫(yī)學(xué)部生物醫(yī)學(xué)工程學(xué)院，廣東深圳518060)

血流信息檢測及其成像因其獨(dú)特的優(yōu)勢，在臨床上得到廣泛應(yīng)用。但常規(guī)經(jīng)顱多普勒超聲系統(tǒng)仍采用模擬和數(shù)字電路結(jié)合的傳統(tǒng)技術(shù)，這類系統(tǒng)容易受到外界干擾且不能進(jìn)行多深度檢測。文章設(shè)計(jì)出一種全數(shù)字多普勒超聲血流檢測系統(tǒng)方案，彌補(bǔ)了傳統(tǒng)模擬系統(tǒng)存在的問題。多普勒仿體和人體實(shí)驗(yàn)結(jié)果表明，該系統(tǒng)能夠進(jìn)行多深度檢測，確定血管的深度；同時(shí)，還提高了檢測靈敏度、超聲穿透力和系統(tǒng)成像分辨率。

編碼激勵(lì)；經(jīng)顱多普勒超聲；多深度檢測

R312

A

1000-3630(2017)-01-0038-04

10.16300/j.cnki.1000-3630.2017.01.008

Jun. 14, 2016; Revised: Aug. 25, 2016

*This paper is published in Chinese language in Technical Acoustics, Dec 2016, Vol.35, No.6, 527-530.