awssigmc {qMRI}

Estimate noise variance for multicoil MR systems

Description

The distribution of image intensity values S_i divided by the noise standard deviation in K-space \sigma in dMRI experiments is assumed to follow a non-central chi-distribution with 2L degrees of freedom and noncentrality parameter \eta, where L refers to the number of receiver coils in the system and \sigma \eta is the signal of interest. This is an idealization in the sense that each coil is assumed to have the same contribution at each location. For realistic modeling L should be a locally smooth function in voxel space that reflects the varying local influence of the receiver coils in the the reconstruction algorithm used.

The functions assume L to be known and estimate either a local (function awslsigmc) or global ( function awssigmc) \sigma employing an assumption of local homogeneity for the noncentrality parameter \eta.

Function afsigmc implements estimates from Aja-Fernandez (2009). Function aflsigmc implements the estimate from Aja-Fernandez (2013).

Usage

awssigmc(y, steps, mask = NULL, ncoils = 1, vext = c(1, 1), lambda = 20, 
         h0 = 2, verbose = FALSE, sequence = FALSE, hadj = 1, q = 0.25, 
         qni = .8, method=c("VAR","MAD"))
awslsigmc(y, steps, mask = NULL, ncoils = 1, vext = c(1, 1), lambda = 5, minni = 2, 
         hsig = 5, sigma = NULL, family = c("NCchi"), verbose = FALSE, 
         trace=FALSE, u=NULL)

Arguments

y

3D array, usually obtained from an object of class dwi as obj@si[,,,i] for some i, i.e. one 3D image from an dMRI experiment. Alternatively a vector of length sum(mask) may be suppied together with a brain mask in mask.

steps

number of steps in adapive weights smoothing, used to reveal the unerlying mean structure.

mask

restrict computations to voxel in mask, if is.null(mask) all voxel are used. In function afsigmc mask should refer to background for method %in% c("modem1chi","bkm2chi","bkm1chi") and to voxel within the head for method=="modevn".

ncoils

number of coils, or equivalently number of effective degrees of freedom of non-central chi distribution divided by 2.

vext

voxel extentions

lambda

scale parameter in adaptive weights smoothing

h0

initial bandwidth

verbose

if verbose==TRUE density plots and quantiles of local estimates of sigma are provided.

trace

if trace==TRUE intermediate results for each step are returned in component tergs for all voxel in mask.

sequence

if sequence=TRUE a vector of estimates for the noise standard deviation sigma for the individual steps is returned instead of the final value only.

hadj

adjustment factor for bandwidth (chosen by bw.nrd) in mode estimation

q

quantile to be used for interquantile-differences.

qni

quantile of distribution of actual sum of weights N_i=\sum_j w_{ij} in adaptive smoothing. Only voxel i with N_i > q_{qni}(N_.) are used for variance estimation. Should be larger than 0.5.

method

in case of function awssigmc the method for variance estimation, either "VAR" (variance) or "MAD" (mean absolute deviation). In function afsigmc see last column in Table 2 in Aja-Fernandez (2009).

minni

Minimum sum of weights for updating values of sigma.

hsig

Bandwidth of the median filter.

sigma

Initial estimate for sigma

family

One of "Gauss" or "NCchi" (default) defining the probability distribution to use.

u

if verbose==TRUE an array of noncentrality paramters for comparisons. Internal use for tests only

Value

a list with components

sigma

either a scalar or a vector of estimated noise standard deviations.

theta

the estimated mean structure

Author(s)

J\"org Polzehl [e-mail]

References

K. Tabelow, H.U. Voss, J. Polzehl, Local estimation of the noise level in MRI using structural adaptation, Medical Image Analysis, 20 (2015), pp. 76–86.

See Also

aws