2012 Proceedings - International Tissue Elasticity Conference
2012 Proceedings - International Tissue Elasticity Conference
2012 Proceedings - International Tissue Elasticity Conference
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045 STRAIN ESTIMATION FOR QUASI–STATIC ELASTOGRAPHY THROUGH ANALYTICAL PHASE<br />
TRACKING.<br />
Lili Yuan 1 , Peder C. Pedersen 1 .<br />
1 Worcester Polytechnic Institute, 100 Institute Road, Worcester, MA, USA.<br />
Background: Quasi–static elastography with an externally applied force often involves strain of several<br />
percent. In such cases, cross–correlation (CC) based methods are computationally demanding and prone to<br />
ambiguity, while speckle tracking has resolution limitations and may have decorrelation–induced errors.<br />
Aims: To develop a robust and efficient method for extracting axial displacement (DPM) and strain in<br />
response to the applied forcing function in freehand quasi–static elastography. The method is based on<br />
tracking the analytical phase through a slow time sequence of radio frequency (RF) signals.<br />
Methods: For 1D axial DPM estimation, a sequence of RF signals as a function of slow time (applied<br />
external force function) is recorded. Via the Hilbert transform, amplitude and wrapped phase of the<br />
analytical signal are obtained along fast time. The (fast time wrapped) phase values for all RF signals are<br />
stored in a phase matrix, where rows and columns represent slow and fast time, respectively. Let the<br />
analytical signal phase at a specified time, t0, be φ0. Our method is an efficient way of tracking φ0 across the<br />
phase matrix, while recording the time shift in the fast time location of φ0, proportional to DPM of scatterers<br />
initially at t0. This method is distinctly different from other reported phase–based methods with limited<br />
resolution due to windowing, such as extracting DPM from the complex CC at zero lag [1], or at zero phase<br />
[2] and weighted phase separation [3]. In our current implementation, only phase values near 0 radians are<br />
retained, as illustrated by the phase bands in Figure 1a, which can have bifurcation or other anomalies<br />
when the corresponding amplitude is low. Therefore, an amplitude threshold is applied to the phase matrix,<br />
giving the result in Figure 1b. Finally, discontinuous phase bands are removed, with only connected phase<br />
bands retained, as seen in Figure 1c. Connected component labeling is then used to recognize zero phase<br />
trajectories, and slow time shifts are computed by subtracting row index at pre–compression. The axial<br />
strain is estimated by applying 2D linear least square fitting to DPM maps.The method was first tested with<br />
a simulated tissue–mimicking 30mm×15mm phantom with a 5mm diameter circular inclusion at its<br />
center whose stiffness was 5 and 10 times that of the surrounding tissue. Using finite element analysis<br />
(FEA) method (Comsol), axial compressions of 0.8%, 5% and 10% were applied to the phantom, and the<br />
ultrasound RF signals of the compressed medium were simulated with Field II. The DPM and strain were<br />
computed with the phase tracking method and compared to the results from FEA and standard CC. The<br />
method was then tested experimentally on a tofu phantom, using an Ultrasonix RP 4MHz transducer at a<br />
high frame rate. A time sequence of 2D RF lines for several cycles of the manual forcing function was<br />
acquired and the corresponding DPM along slow time were determined and compared with CC result.<br />
Figure 1: (a) Phase matrix showing wrapped (a) (b) (c)<br />
phase values near 0 radians<br />
(limited in +/-0.2π);<br />
(b) Phase matrix with normalized<br />
amplitude threshold applied;<br />
(c) Phase matrix with amplitude<br />
threshold applied and discontinuous<br />
phase curves removed.<br />
Results: The DPM and strain from Comsol and Field II simulations and experiments confirm the validity<br />
of the phase tracking method. For DPM magnitudes on the order of 0.5 to 1 mm, the error at peak<br />
compression is typically 5%. In comparison to a standard implementation of the conventional CC method,<br />
our analytical–phase method was at least 10 times faster, with a resolution, accuracy, SNRe, and CNRe<br />
comparable to or better than what we obtained with the CC method.<br />
Conclusions: The phase tracking method has been implemented with a fast time sampling rate of 30 times<br />
the center frequency and the slow time sampling rate chosen so that the maximum DPM of scatterers<br />
between consecutive RF lines is λ/10 or less. The method minimizes performance degradation through<br />
region of low RF signal amplitude, generally caused by destructive interference, by tracking only wrapped<br />
fast time phase, which is not affected by phase anomalies common to unwrapped phase.<br />
Acknowledgements: Funding by the Telemedicine and Advanced Technology Research Center is greatly appreciated.<br />
References:<br />
[1] O'Donnell M et al.: IEEE UFFC, 41(3), pp. 314–325, 1994.<br />
[2] Pesavento A et al.: IEEE UFFC, 46(5), pp. 1057–1067, 1999.<br />
[3] Lindop JE et al.: IEEE UFFC, 55(1), pp. 94–111, 2008.<br />
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