## Serviços Personalizados

## Artigo

## Indicadores

- Citado por SciELO
- Acessos

## Links relacionados

- Citado por Google
- Similares em SciELO
- Similares em Google

## Compartilhar

## DYNA

##
*versão impressa* ISSN 0012-7353

### Dyna rev.fac.nac.minas vol.80 no.182 Medellín nov./dez. 2013

**MR-DTI RICIAN DENOISING **

**ELIMINACIÓN DE RUIDO RICIAN EN MR-DTI **

**ADRIAN MARTIN**

*M.Sc. Departamento de Matemática Aplicada, Universidad Rey Juan Carlos, Madrid, España, adrian.martin@urjc.es*

**JUAN F. GARAMENDI**

*Ph.D. INRIA-VisAGeS Research Team, Rennes, France, juan-francisco.garamendi_bragado@inria.fr *

**EMANUELE SCHIAVI**

*Ph.D., Departamento de Matemática Aplicada, Universidad Rey Juan Carlos, Madrid, España, emanuele.schiavi@urjc.es*

**Received for review March 23 ^{th}, 2012, accepted May 15^{th}, 2013, final version July, 21^{th}, 2013**

**ABSTRACT:** In this work we tackle the problem of Magnetic Resonance Images (MRI) *Rician* denoising to enhance Diffusion Tensor Image (DTI) reconstruction. In a variational framework based on the Total Variation operator, the model of the *Rician* noise leads to the resolution of a highly nonlinear equation associated to the energy minimization problem. An iterative algorithm is proposed and validated on synthetic images. Finally the application to real Diffusion Weighted Images (DWI) is considered.

**KEYWORDS:** MRI, DWI, DTI, *Rician* noise, Variational

**RESUMEN:** En este trabajo se trata el problema de eliminación de ruido *Rician* en imagen de Resonancia Magnética para la mejora de la reconstrucción de las imágenes de DifusiónTensorial. El modelado del ruido *Rician* es enfocado desde un marco variacional basado en el operador de Variación Total, convirtiéndolo en un problema de minimización de energía que conduce a la resolución de ecuaciones severamente no lineales. La solución propuesta es un algoritmo iterativo validado con imágenes sintéticas, que finalmente es probado en imágenes ponderadas en difusión reales.

**PALABRAS CLAVE:** Resonancia Magnética, DWI, DTI. ruido *Rician*, variacional

**1. INTRODUCTION **

MRI denoising is a fundamental step in medical image processing that leads to the assumption that MR magnitude images are corrupted by *Rician* noise (which is a signal dependent noise) (see [1] and [2]). The bias with respect to the typical *Gaussian* noise assumption is particularly severe when low Signal-to-Noise Ratio (SNR) images are used. In this paper we present a denoising model for MR *Rician* noise contaminated images, recently presented in [3]. In a variational framework it combines the Total Variation operator with a data fitting term, which was previously suggested in [4] for DWI *Rician* denoising. When the resulting energy functional is considered for minimization, the variational approach leads to the resolution of a nonlinear degenerate elliptic Partial Differential Equation (PDE) which is the associated Euler Lagrange equation for optimization. This has a number of theoretical problems when the Total Variation (TV) operator is considered as a prior, because the associated energy functional is not differentiable at the origin (i.e.) and approximating problems must be considered. We also embed the PDE in the general iterative regularization procedure presented in [5] which allows to recover high contrast images. The model is then validated using synthetic brain images and finally we apply this framework on a set of real DW brain Images.

The denoising step is crucial for a good Diffusion Tensor reconstruction, which allows the study of white matter tissues in the brain. *Rician* denoising is also essential when anatomical MRI studies are done to characterize differences between healthy and diseased subjects [6].

This paper is organized as follows: in sections 2 and 3 we characterize *Rician* noise and the equations which define the denoising process. These equations are then embedded in an iterative regularization procedure and solved numerically, in section 4. In section 5 we use synthetic images for model validation and finally in section 6 we show the results for real images validating the proposed model.

**2. THE RICIAN DISTRIBUTION OF NOISE IN MRI**

In MRI the original complex signal is measured in the frequency domain (called K-space). It is assumed that the noise in each channel (real and imaginary) follows a *Gaussian* distribution with zero mean and identical variance Using the Inverse Fourier Transform the real and imaginary images are obtained from K-space data. Due to the fact that the Fourier Transform is a linear and orthogonal map, it preserves the characteristics of the noise and this noise can be assumed to be uncorrelated in each voxel. Nevertheless the final image typically used for subsequent analysis is the magnitude image, obtained by calculating the modulus from the real and imaginary images voxel by voxel. This nonlinear mapping transforms the *Gaussian* noise distribution into a *Rician* distribution [1]:

where denotes the (ideal) uncorrupted image intensity, the noisy data, is the variance of the original *Gaussian* noise and is the modified zeroth-order Bessel function of the first kind.

In Figure 1 the behavior of the *Rician* probability density function is shown for different values of the SNR (). It can be seen how the distribution is far from being *Gaussian* especially for small SNR values. When the original signal is zero () a special case of the *Rician* distribution (1) has to be considered:

which is called the *Rayleigh* distribution. The mean and the variance of this distribution can be calculated analytically. This allows the parameter in (1) and (2) to be estimated (see [2] for more details).

**3. MODEL EQUATIONS**

Following [3], the problem of *Rician* denoising can be modeled as follows: Given , representing the noisy image, find the denoised image, minimizing the energy:

where is the Total Variation of the function and is the space of functions with bounded variation; furthermore is the standard deviation of the *Rician* noise of the data and is as before, the modified zeroth-order Bessel function of the first kind. The scale parameter tunes the model by weighting the likelihood term derived from the *Rician* p.d.f. (1).

This functional minimization can be accomplished by calculating the Euler-Lagrange equation of functional (2). Due to the fact that the Total Variation is not differentiable at the origin, a regularization of the resulting diffusion term in the form of , and is implemented to avoid degeneration of the equation where. Using this approximation it is possible to give a (weak) meaning to the following formulation: Given find solving:

where is the modified first-order Bessel function of the first kind.

**4. ITERATIVE REGULARIZATION AND NUMERICAL RESOLUTION**

In this work we apply the iterative regularization method for total variation-based denoising, proposed in [3], to the recovering of MRI images corrupted by *Rician* noise. It is well known that this iterative regularization process allows the original contrast present in the image [3,5] to be preserved. The general iterative procedure is as follows: Let be positive real parameters and set .

1) Given and compute as the minimum of the energy:

The procedure stops when the high frequencies introduced are clearly a product of the noise. So at each iteration we have to minimize the energy (5) solving the associated Euler-Lagrange equations; for notational simplicity we introduce the nonlinear function

and the analogous of equation (4) reads:

These are nonlinear elliptic problems that we solve with a gradient descent scheme until the solution stabilizes to a solution of the elliptic problem. Using forward finite difference for the temporal derivative and a semi-implicit iterative scheme we deduce the (explicit) equation:

where the spatial discretization for the TV-term is performed following [7] .

**5. MODEL VALIDATION ON SYNTHETIC BRAIN IMAGES**

In order to assess the performance of the proposed algorithm we tested it with synthetic brain images obtained from the BrainWeb Simulated Brain Database (http://www.bic.mni.mcgill.ca/brainweb) at the Montreal Neurological Institute. The original phantoms were contaminated artificially with *Rician* noise, the known amount and distribution of it providing a gold standard for our study. In this case we used the value and that assures that the result in the first iteration is a low frequency image and subsequent iterations recover details. In Figure 2 we present the sequence of images .

These images show the evolution of the inverse scaling procedure presented in (4), starting with a structural cartoon image and subsequently adding details (and noise) eventually approximating the original noisy data. Two metrics were considered to determine the best iteration in the inverse scaling procedure. The first is the Signal-to-Noise-Ratio (SNR) between the possible solution and the original (clean) image . It is defined as

The second metric is the Bregman Distance [5] between and . It can be seen in Figure 2(g), how the maximum SNR value and the minimum value for the Bregman Distance are obtained at as shown in Figure 2(h).

These results as well as visual inspection confirm that the images: are over-smoothed versions of with few details while the subsequent images, , become noisier. We also notice that, as we stated, the contrast of the image sequence measured as the standard deviation (SD) of the pixel intensity is monotonically increasing, so providing a high contrast image suitable for tissue classification.

**6. DIFFUSION TENSOR IMAGES APPLICATION**

DTI is becoming one of the most popular methods for the analysis of the white matter (WM) structure of the brain, where some alterations can be found in early stages of some degenerative diseases. A complete review of this technique can be found in [8].

This technique measures the Brownian motion (random motion) of the water molecules in the brain. This motion is assumed to be isotropic when it is not restricted by surrounding structures, but the WM regions contain densely packed fiber bundles that cause an anisotropic diffusion of the water molecules along the perpendicular directions to the fiber bundles. At each voxel of a DTI the water diffusion is represented by a symmetric tensor. The information of the preferred directions of the motion and the relevance of these directions is represented by the eigenvectors and the eigenvalues of the tensor. The information contained in a DTI is encoded by different scalar measurements; one of them is the Fractional Anistropy (FA) of the tissue, which is defined as

with being the eigenvalues of the tensor. The FA values vary from 0 (when the motion in the voxel is completely isotropic) to 1 (totally anisotropic). For the reconstruction of the DTI a set of DWI has to be acquired, scanning the tissue in different directions of space. At least six DWI volumes are needed in order to be able to calculate the DTI but in clinical practice more than 15 DWI volumes are usually acquired. More DWI data imply better DTI reconstruction but longer scanning time. As a result of this bias (image quality vs. scanning time) the noise in the images is high. This shows the importance of the denoising step previous to the DTI reconstruction.

For this preliminary study we have used a DW-MR brain volume provided by Fundación CIEN-Fundación Reina Sofía which was acquired with a 3 Tesla General Electric scanner equipped with an 8-channel coil. The DW images have been obtained with a single-shot spin-eco EPI sequence (FOV=24cm, TR=9100, TE=88.9, slice thickness=3mm, spacing=0.3, matrix size=128x128, NEX=2). The DW-MRI data consists of a volume obtained with b=0/mm2 and 15 volumes with b=1000s/mm2 corresponding with the gradient directions specified in [9]. These DW-MR images, which represent diffusion measurements along multiple directions, are denoised with the proposed method previous to the Diffusion Tensorial Image reconstruction, which was done with the 3d Slicer tools (freely available at http://www.slicer.org). These data were acquired from a patient who suffers from a progressive supranuclear palsy (PSP), a degenerative disease which impairs movements and balance, so the scanner time must be as short as possible. In Figure 3 we show a slice of the original DWI data corresponding to the (1, 0, 0) gradient direction where the effect of noise is clearly visible. The complete DW-MRI data volume is denoised using the proposed method where the *Rician* noise magnitude () has been estimated following [2], while the value used has been assessed empirically as well as the selection of the fifth iteration of the Inverse Scaling procedure. A slice from the associated denoised volume is shown in Figure 4. It can be observed that the noise has been removed but the details and the edges have been fully preserved.

The effect of this denoising process over the reconstructed tensor can be observed comparing the Fractional Anisotropy images (Figures 5 and 6), where the structures and details are enhanced when the DWI data have been preprocessed. The denoising step is even more important when directional information (such as the main eigenvector of the tensor) is required (Figures 7 and 8). The noise on the original DWI data causes artificial inhomogeneities in the eigenvectors field. The directional information provided by the eigenvectors field is crucial for subsequent postprocessing such as tractography, an emergent technique in recent neurological studies [10].

**7. CONCLUSIONS**

In this paper we deal with the problem of accurate *Rician* denoising in DT-MRI. The proposed model successfully incorporates a *Rician* likelihood term which is regularized in a variational framework by means of the Total Variation operator. Staircasing artifacts in the solution are avoided through the inverse scaling procedure. The results obtained in real images are promising and open the way to the method's use in clinical practice.

Further work should include advanced numerical techniques to avoid the approximation of the total variation operator.

**8. ACKNOWLEDGEMENTS**

This work was supported by project TEC2012-39095-C03-02 of the Spanish Ministry of Science.

**9. REFERENCES**

**[1]** Gudbjartsson, H. and Patz, S., The rician distribution of noisy MRI data, Magnetic Resonance in Medicine 34 (6), pp. 910-914, 1995. [ Links ]

**[2]** Sijbers, J. et al., Estimation of the noise in magnitude MR images, Magnetic Resonance Imaging 1 (16) pp. 87-90, 1998. [ Links ]

**[3]** Martín, A. et al., Iterated *Rician* Denoising, Proceedings of IPCV'11, Las Vegas, Nevada, USA, pp. 959-963, 2011 [ Links ]

**[4]** Basu, S. et al., *Rician* noise removal in Difusion Tensor MRI, Medical Image Computing and Computer-Assisted Intervention 9 (Pt 1) pp. 117-125, 2006. [ Links ]

**[5]** Osher, S. et al., An iterative regularization method for Total Variation-based image restoration, Multiscale Modeling & Simulation 4 (2) 460-489, 2005. [ Links ]

**[6]** Rueda, A. et al., Saliency-Based Characterization Of Group Differences For Magnetic Resonance Disease Classification. Dyna 178, pp. 21-28, 2013. [ Links ]

**[7]** Nikolova, M., Algorithms for finding global minimizers of image segmentation and denoising models, SIAM Journal of Applied Mathematics 66 (5) pp. 1632-1648, 2006. [ Links ]

**[8]** Le Bihan, D. et al., Diffusion Tensor Imaging: Concepts and Applications, Journal of Magnetic Resonance Imaging 13 pp. 534-546, 2001. [ Links ]

**[9]** Jones, S. et al., Optimal strategies for measuring diffusion in anisotropic systems by magnetic resonance imaging. Magnetic Resonance in Medicine 42 (3), pp. 515-525, 1999. [ Links ]

**[10]** Ciccarelli, O. et al., Diffusion-based tractography in neurological disorders: concepts, applications, and future developments. The Lancet Neurology 7(8), pp. 715-727, 2008. [ Links ]