Abstract
Errors in the data and the forward operator of an inverse problem can be handily modelled using partial order in Banach lattices. We present some existing results of the theory of regularisation in this novel framework, where errors are represented as bounds by means of the appropriate partial order. We apply the theory to diffusion tensor imaging, where correct noise modelling is challenging: it involves the Rician distribution and the nonlinear Stejskal–Tanner equation. Linearisation of the latter in the statistical framework would complicate the noise model even further. We avoid this using the error bounds approach, which preserves simple error structure under monotone transformations.
Introduction
Often in inverse problems, we have only very rough knowledge of noise models, or the exact model is too difficult to realise in a numerical reconstruction method. The data may also contain process artefacts from blackbox devices [44]. Partial order in Banach lattices has therefore recently been investigated in [32–34] as a lessassuming error modelling approach for inverse problems. This framework allows the representation of errors in the data as well as in the forward operator of an inverse problem by means of order intervals (i.e. lower and upper bounds by means of appropriate partial orders). An important advantage of this approach vs. statistical noise modelling is that deterministic error bounds preserve their simple structure under monotone transformations.
We apply partial order in Banach lattices to diffusion tensor imaging (DTI). We will in due course explain the diffusion tensor imaging progress, as well as the theory of inverse problems in Banach lattices, but start by introducing our model
That is, we want to find a field of symmetric 2tensors \(u: {\varOmega }\rightarrow {{\mathrm{Sym}}}^2(\mathbb {R}^3)\) on the domain \({\varOmega }\subset \mathbb {R}^3\), minimising the value of the regulariser R on the feasible set. The tensor field u is our unknown image. It is subject to a positivity constraint, as well as partial order constraints imposed through the operators \([A_j u](x) :=\langle b_j,u(x)b_j\rangle \), and the upper and lower bounds \(g_j^l :=\log ({\hat{s}}_j^l/{\hat{s}}_0^u)\) and \(g_j^u :=\log ({\hat{s}}_j^u/{\hat{s}}_0^l)\). These arise from the linearisation (via the monotone logarithmic transformation) of the StejskalTanner equation
central to the diffusion tensor imaging process.
To shed more light on u and the equation (1), let us briefly outline the diffusion tensor imaging process. As a first step towards DTI, diffusionweighted magnetic resonance imaging (DWI) is performed. This process measures the anisotropic diffusion of water molecules. To capture the diffusion information, the magnetic resonance images have to be measured with diffusionsensitising gradients in multiple directions. These are the different \(b_i\)’s in (1). Eventually, multiple DWI images \(\{s_j\}\) are related through the Stejskal–Tanner equation (1) to the symmetric positivedefinite diffusion tensor field \(u: {\varOmega }\rightarrow {{\mathrm{Sym}}}^2(\mathbb {R}^3)\) [4, 29]. At each point \(x \in {\varOmega }\), the tensor u(x) is the covariance matrix of a normal distribution for the probability of water diffusing in different spatial directions.
The fact that multiple \(b_i\)’s are needed to recover u leads to very long acquisition times, even with ultra fast sequences like echo planar imaging (EPI). Therefore, DTI is inherently a lowresolution and lowSNR method. In theory, the amplitude DWI images exhibit Rician noise [24]. However, as the histogram of an in vivo measurement in Fig. 1 illustrates, this may not be the case for practical datasets from blackbox devices. Moreover, the DWI process is prone to eddycurrent distortions [53], and due to the slowness of it, it is very sensitive to patient motion [1, 27]. We therefore have to use techniques that remove these artefacts in solving for u(x). We also need to ensure the positivity u, as nonpositivedefinite diffusion tensor are nonphysical. One proposed approach for the satisfaction of this constraint is that of logEuclidean metrics [3]. This approach has several theoretically desirable aspects, but some practical shortcomings [57]. Special Perona–Maliktype constructions on Riemannian manifolds can also be used to maintain the structure of the tensor field [14, 54]. Such anisotropic diffusion is, however, severely illposed [60]. Recently manifoldvalued discretedomain total variation models have also been applied to diffusion tensor imaging [6].
Our approach is also in the total variation family, first considered for diffusion tensor imaging in [48]. Namely, we follow up on the work in [55, 57–59] on the application of total generalised variation regularisation [9] to DTI. We should note that in all of these works, the fidelity function was the ROFtype [45] \(L^2\) fidelity. This would only be correct, according to the assumption that noise of MRI measurements is Gaussian, if we had access to the original complex kspace MRI data. The noise of the inverse Fouriertransformed magnitude data \(s_j\), that we have in practice access to, is however Rician under the Gaussian assumption on the original complex data [24]. This is not modelled by the \(L^2\) fidelity.
Numerical implementation of Rician noise modelling has been studied in [22, 40]. As already discussed, in this work, we take the other direction. Instead of modelling the errors in a statistically accurate fashion, not assuming to know an exact noise model, we represent them by means of pointwise bounds. The details of the model are presented in Sect. 3. We study the practical performance in Sect. 5 using the numerical method presented in Sect. 4. First we, however, start with the general error modelling theory in Sect. 2. Readers who are not familiar with notation for Banach lattices or symmetric tensor fields are advised to start with the Appendix 2 where we introduce our mathematical notation and techniques.
Deterministic Error Modelling
Mathematical Basis
We now briefly outline the theoretical framework [32] that is the basis for our approach. Consider a linear operator equation
where U and F are Banach lattices, \(A :U \rightarrow F\) is a regular injective operator. The inaccuracies in the righthand side f and the operator A are represented as bounds by means of appropriate partial orders, i.e.
where the symbol \(\leqslant _F\) stands for the partial order in F and \(\leqslant _{L^\sim (U,F)}\) for the partial order for regular operators induced by partial orders in U and F. Further, we will drop the subscripts at inequality signs where it will not cause confusion.
The exact righthand side f and operator A are not available. Given the approximate data \((f^l,f^u,A^l,A^u)\), we need to find an approximate solution u that converges to the exact solution \({\bar{u}}\) as the inaccuracies in the data diminish. This statement needs to be formalised. We consider monotone convergent sequences of lower and upper bounds
We are looking for an approximate solution \(u_n\) such that \(\Vert u_n{\bar{u}}\Vert _U \rightarrow 0\) as \(n \rightarrow \infty \).
Let us ask the following question. What are the elements \(u \in U\) that could have produced data within the tolerances (4)? Obviously, the exact solution is one of such elements. Let us call the set containing all such elements the feasible set \(U_n \subset U\).
Suppose that we know a priori that the exact solution is positive (by means of the appropriate partial order in U), then it is easy to verify that the following inequalities hold for all \(n \in {\mathbb {N}}\)
This observation motivates our choice of the feasible set:
It is clear that the exact solution \({\bar{u}}\) belongs to the sets \(U_n\) for all \(n \in {\mathbb {N}}\). Our goal is to define a rule that will choose for any n an element \(u_n\) of the set \(U_n\) such that the sequence \(u_n \in U_n\) will strongly converge to the exact solution \({\bar{u}}\). We do so by minimising an appropriate regularisation functional R(u) on \(U_n\):
This method, in fact, is a lattice analogue of the wellknown residual method [23, 52]. The convergence result is as follows [32].
Theorem 1
Suppose that

1.
R(u) is bounded from below on U,

2.
R(u) is lower semicontinuous,

3.
level sets \(\{u :R(u) \leqslant C\}\) (\(C=\mathrm{const}\)) are sequentially compact in U (in the strong topology induced by the norm).
Then the sequence defined in (5) strongly converges to the exact solution \({\bar{u}}\) and \({\mathcal {R}}(u_n) \rightarrow {\mathcal {R}}({\bar{u}})\).
Examples of regularisation functionals that satisfy the conditions of Theorem 1 are as follows. Total Variation in \(L^1({\varOmega })\), where \({\varOmega }\) is a subset of \({\mathbb {R}}^n\), assures strong convergence in \(L^1\), given that the \(L^1\)norm of the solution is bounded. The Sobolev norm \(\Vert u \Vert _{W^{1,q}({\varOmega })}\) yields strong convergence in the spaces \(L^p({\varOmega })\), where \(p \geqslant 1\), \(q > \frac{np}{p+n}\). The latter fact follows from the compact embedding of the corresponding Sobolev \(W^{1,q}({\varOmega })\) space into \(L^p({\varOmega })\) [16].
However, the assumption that the sets \(\{u :R(u) \leqslant C\}\) are strong compacts in U is quite strong. It can be replaced by the assumption of weak compactness, provided that the regularisation functional possesses the socalled Radon–Riesz property.
Definition 1
A functional \(F :U \rightarrow {\mathbb {R}}\) has the Radon–Riesz property (sometimes called the Hproperty), if for any sequence \(u_n \in U\) weak convergence \(u_n \rightharpoonup u_0\) and simultaneous convergence of the values \(F(u_n) \rightarrow F(u_0)\) imply strong convergence \(u_n \rightarrow u_0\).
Theorem 2
Suppose that

1.
R(u) is bounded from below on U,

2.
R(u) is weakly lower semicontinuous,

3.
level sets \(R(u) \leqslant C\) (\(C=\mathrm{const}\)) are weakly sequentially compact in U,

4.
R(u) possesses the Radon–Riesz property.
Then the sequence defined in (5) strongly converges to the exact solution \({\bar{u}}\) and \({\mathcal {R}}(u_n) \rightarrow {\mathcal {R}}({\bar{u}})\).
It is easy to verify that the norm in any Hilbert space possesses the Radon–Riesz property. Moreover, this holds for the norm in any reflexive Banach space [16].
As we explain in the Appendix 2 \(L^p({\varOmega }; {{\mathrm{Sym}}}^{2}(\mathbb {R}^m))\) is not a Banach lattice. Therefore, Theorems 1 and 2 cannot be applied directly. Further theoretical work will be undertaken to extend the framework to the nonlattice case. For the moment, however, we will prove that if there are no errors in the operator A in (2), the requirement that the solution space U is a lattice can be dropped.
Theorem 3
Let U be a Banach space, and F be a Banach lattice. Let the operator A in (2) be a linear, continuous and injective operator. Let \(f^l_n\) and \(f^u_n\) be sequences of lower and upper bounds for the righthand side defined in (4), and suppose that there are no errors in the operator A. Let us redefine the feasible set in the following way
Suppose also that the regulariser R(x) satisfies conditions of either Theorem 1 or Theorem 2. Then the sequence defined in (5) strongly converges to the exact solution \({\bar{u}}\) and \(R(u_n) \rightarrow R({\bar{u}})\).
Proof
Let us define an approximate righthand side and its approximation error in the following way
One can easily verify that the inequality \(\Vert ff_{\delta _n}\Vert \leqslant \delta _n\) holds. Indeed, we have
The first two inequalities are consequences of the conditions (4), the third one holds by the definition of supremum and the equality \(f = f \vee (f)\) that holds for all \(f \in F\), and the last inequality is due to the monotonicity of the norm in a Banach lattice.
Similarly, one can show that for any \(u \in U_n\), we have
Therefore, the inclusion \(U_n \subset \{u :\Vert Auf_{\delta _n}\Vert \leqslant \delta _n\}\) holds.
Now we will proceed with the proof of convergence \(\Vert u_n{\bar{u}}\Vert \rightarrow 0\). Will prove it for the case when the regulariser R(u) satisfies conditions of Theorem 1. Suppose that the sequence \(u_n\) does not converge to the exact solution \({\bar{u}}\), then it contains a subsequence \(u_{n_k}\) such that \(\Vert u_{n_k}  {\bar{u}}\Vert \geqslant \varepsilon \) for any \(k \in {\mathbb {N}}\) and some fixed \(\varepsilon >0\).
Since the inclusion \({\bar{u}} \in U_n\) holds for all \(n \in {\mathbb {N}}\), we have \(R(u_n) \leqslant R({\bar{u}})\) for all \(n \in {\mathbb {N}}\). Since the level set \(\{u :R(u) \leqslant R({\bar{u}})\}\) is a compact set by assumptions of the theorem, the sequence \(u_{n_k}\) contains a strongly convergent subsequence. With no loss of generality, let us assume that \(u_{n_k} \rightarrow u_0\). We will now show that \(u_0 = {\bar{u}}\). Indeed, we have
On the other hand, we have
due to continuity of A and \(\Vert \cdot \Vert \). Therefore, \(A u_0 = A {\bar{u}}\) and \(u_0 = {\bar{u}}\), since A is an injective operator. By contradiction, we get \(\Vert u_n  {\bar{u}}\Vert \rightarrow 0\).
Finally, since the regulariser R(u) is lower semicontinuous, we get that \(\lim \inf R(u_n) = R({\bar{u}})\). However, for any n we have \(R(u_n) \leqslant R({\bar{u}})\), therefore, we get the convergence \(R(u_n) \rightarrow R({\bar{u}})\) as \(n \rightarrow \infty \). \(\square \)
Philosophical Discussion and Statistical Interpretation
In practice, our data are discrete. So let us momentarily switch to measurements \({\hat{f}} = ({\hat{f}}^1, \ldots , {\hat{f}}^n) \in \mathbb {R}^n\) of a true data \(f \in \mathbb {R}^n\). If we actually knew the pointwise noise model of the data, then one way to obtain potentially useful upper and lower bounds for the deterministic model is by means of statistical interval estimates: confidence intervals. Roughly, the idea is to find for each true signal f individual random upper and lower bounds \({\hat{f}}^u\) and \({\hat{f}}^l\) such that
If \({\hat{f}}^u\) and \({\hat{f}}^l\) are computed based on multiple experiments (i.e. multiple noisy samples \({\hat{f}}_1,\dots ,{\hat{f}}_m\), of the true data f), the interval \([{\hat{f}}^{u,i}, {\hat{f}}^{l,i}]\) will converge in probability to the true data \({\hat{f}}^i\), as the number of experiments m increases. Thus we obtain a probabilistic version of the convergences in (4).
Let us try to see, how such intervals might work in practice. For the purpose of the present discussion, assume that the noise is additive and normaldistributed with variance \(\sigma \) and zero mean—an assumption that does not hold in practice, as we have already seen in Fig. 1, but will suffice for the next thought experiments. That is, \({\hat{f}}_j=f+\nu _j\) for the noise \(\nu _j\). Let the sample mean of \(\{{\hat{f}}_j\}_{j=1}^m\) be \({\bar{f}}_m = ({\bar{f}}^1_m, \ldots {\bar{f}}^n_m)\), and pointwise sample variance \(\sigma =(\sigma ^1,\ldots ,\sigma ^n)\). The product of the pointwise confidence intervals \(I_i\) with confidence \(1\theta \) is [15, 49]
where \(k^*_{1t} :={\varPhi }^{1}(t)\) with \({\varPhi }\) the cumulative normal distribution function. For \(\theta =0.05\), i.e. the \(95\,\%\) confidence interval, \({\varPhi }^{1}(0.05/2)=1.96\). Now, the probability that \(I_i\) covers the true \(f^i\) is \(1\theta \), e.g. \(95\,\%\). If we have only a single sample \(m=1\), the intervals stay large, but the joint probability \((1\theta )^n\) goes to zero as n increases. As an example, for a rather typical single \(128 \times 128\) slice of a DTI measurement, the probability that exactly \(\phi =5\,\%\) (to the closest discrete value possible) of the \(1\theta =95\,\%\) confidence intervals do not cover the true parameter would be about \(1.4\,\%\), or
The probability of at least \(\phi =5\,\%\) of the pointwise \(95\,\%\) confidence intervals not covering the true parameter is in this setting approximately \(49\,\%\). This can be verified by summing the above estimates over \(m=\lceil \phi n \rceil ,\ldots ,n\).
In summary, unless \(\theta \) simultaneously goes to 1, the product intervals are very unlikely to cover the true parameter. Based on a single experiment, the deterministic approach as interpreted statistically through confidence intervals is therefore very likely to fail to discover the true solution as the data size n increases unless the pointwise confidence is very low. But, if we let the pointwise confidences be arbitrarily high, such that the intervals are very large, the discovered solution in our applications of interest would be just a constant!
Asymptotically, the situation is more encouraging. Indeed, if we could perform more experiments to compute the confidence intervals, then for any fixed n and \(\theta \), it is easy to see that the solution of the “deterministic” error model is an asymptotically consistent and hence asymptotically unbiased estimator of the true f. That is, the estimates converge in probability to f as the experiment count m increases. Indeed, the error boundsbased estimator \({\tilde{f}}_m\), based on m experiments, by definition satisfies \({\tilde{f}}_m \in \prod _{i=1}^n I_i\). Therefore, we have
Thus \(f \overset{P}{\rightarrow } {\bar{f}}\) in probability. Since by the law of large numbers also \({\bar{f}}_m \overset{P}{\rightarrow } f\), this proves the claim, and to some extent justifies our approach from the statistical viewpoint.
It should be noted that this is roughly the most that has previously been known of the maximum a posteriori estimate (MAP), corresponding to the Tikhonov models
In particular, the MAP is not the Bayes estimator for the typical squared cost functional. This means that it does not minimise \({\tilde{f}} \mapsto \mathbb {E}[\Vert f{\tilde{f}}\Vert ^2]\). The minimiser in this case is the conditional mean (CM) estimate, which is why it has been preferred by Bayesian statisticians despite its increased computational cost. The MAP estimate is merely an asymptotic Bayes estimator for the uniform cost function. In a very recent work [12], it has, however, been proved that the MAP estimate is the Bayes estimator for certain Bregman distances. One possible critique of the result is that these distances are not universal and do depend on the regulariser R, unlike the squared distance for CM. The CM estimate, however, has other problems in the setting of total variation and its discretisation [35, 36].
Application to Diffusion Tensor Imaging
We now build our model for applying the deterministic error modelling theory to diffusion tensor imaging. We start by building our forward model based on the Stejskal–Tanner equation, and then briefly introduce the regularisers we use.
The Forward Model
For \(u: {\varOmega }\rightarrow {{\mathrm{Sym}}}^2(\mathbb {R}^3)\), \({\varOmega }\subset \mathbb {R}^3\), a mapping from \({\varOmega }\) to symmetric secondorder tensors, let us introduce nonlinear operators \(T_j\), defined by
Their role is to model the socalled Stejskal–Tanner equation [4]
Each tensor u(x) models the covariance of a Gaussian probability distribution at x for the diffusion of water molecules. The data \(s_j \in L^2({\varOmega })\), (\(j=1,\ldots ,N\)), are the diffusionweighted MRI images. Each of them is obtained by performing the MRI scan with a different nonzero diffusionsensitising gradient \(b_j\), while \(s_0\) is obtained with a zero gradient. After correcting the original kspace data for coil sensitivities, each \(s_j\) is assumed real. As a consequence, any measurement \({\hat{s}}_j\) of \(s_j\) has—in theory—Rician noise distribution [24].
Our goal is to reconstruct u with simultaneous denoising. Following [31, 55], we consider using a suitable regulariser R the Tikhonov model
The constraint \(u\geqq 0\) is to be understood in the sense that u(x) is positive semidefinite for \(\mathcal {L}^n\)a.e. \(x \in {\varOmega }\) (see Appendix 2 for more details). Due to the Rician noise of \({\hat{s}}_j\), the Gaussian noise model implied by the \(L^2\)norm in (7) is not entirely correct. However, in some cases the \(L^2\) model may be accurate enough, as for suitable parameters the Rician distribution is not too far from a Gaussian distribution. If one were to model the problem correctly, one should either modify the fidelity term to model Rician noise or include the (unit magnitude complex number) coil sensitivities in the model. The Rician noise model is highly nonlinear due to the Bessel functional logarithms involved. Its approximations have been studied in [5, 22, 40] for single MR images and DTI. Coil sensitivities could be included either by knowing them in advance or by simultaneous estimation as in [30]. Either way, significant complexity is introduced into the model, and for the present work, we are content with the simple \(L^2\) model.
We may also consider, as is often the case, and as was done with TGV in [57], the linearised model
where, for each \(x \in {\varOmega }\), f(x) is solved by regression for u(x) from the system of equations (6) with \(s_j(x)={\hat{s}}_j(x)\). Further, as in [58], we may also consider
with
In both of these linearised models, the assumption of Gaussian noise is in principle even more remote from the truth than in the nonlinear model (7). We will employ (8) and (7) as benchmark models.
We want to further simplify the model, and forgo with accurate noise modelling. After all, we often do not know the real noise model for the data available in practice. It can be corrupted by process artefacts from blackbox algorithms in the MRI devices. This problem of blackbox devices has been discussed extensively in [44], in the context of Computed Tomography. Moreover, as we have discussed above, even without such artefacts, the correct model may be difficult to realise numerically. So we might be best off choosing the least assuming model of all—that of error bounds. This is what we propose in the reconstruction model
Here \(g_j^l :=\log ({\hat{s}}_j^l/{\hat{s}}_0^u)\) and \(g_j^u :=\log ({\hat{s}}_j^u/{\hat{s}}_0^l)\), \(g_j^l, g_j^u \in L^2({\varOmega })\), are our upper and lower bounds on \(g_j\) that we derive from the data.
Choice of the Regulariser R
A prototypical regulariser in image processing is the total variation, first studied in this context in [45]. It can be defined for a \(u \in L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) as
Observe that for scalar or vector fields, i.e. the cases \(k=0,1\), we have \({{\mathrm{Sym}}}^0(\mathbb {R}^m)=\mathcal {T}^0(\mathbb {R}^m)=\mathbb {R}\), and \({{\mathrm{Sym}}}^1(\mathbb {R}^m)=\mathcal {T}^1(\mathbb {R}^m)=\mathbb {R}^m\). Therefore, for scalars in particular, this gives the usual isotropic total variation
Total generalised variation was introduced in [9] as a higherorder extension of \({{\mathrm{TV}}}\). Following [11, 57], the secondorder variant may be defined with the differentiation cascade formulation for symmetric tensor fields \(u \in L^1({\varOmega }; {{\mathrm{Sym}}}^{k}(\mathbb {R}^m))\) as the marginal
of
It turns out that the standard BVnorm
and the “BGV norm” [9]
are topologically equivalent norms [10, 11] on the space \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), yielding the same convergence results for TGV regularisation as for TV regularisation. The geometrical regularisation behaviour is, however, different, and TGV tends to avoid the staircasing observed in TV regularisation.
Regarding topologies, we say that a sequence \(\{u^i\}\) in \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) converges weakly* to u, if \(u^i \rightarrow u\) strongly in \(L^1\), and weakly* as Radon measures [2, 51, 57]. The latter means that for all \(\phi \in C_c^\infty ({\varOmega }; {{\mathrm{Sym}}}^{k+1}(\mathbb {R}^m))\) holds \(\int _{\varOmega }\langle {{\mathrm{div}}}\phi (x),u^i(x)\rangle {{\mathrm{d}}}x \rightarrow \int _{\varOmega }\langle {{\mathrm{div}}}\phi (x),u(x)\rangle {{\mathrm{d}}}x\).
Compact Subspaces
Now, for a weak* lower semicontinuous seminorm R on \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), let us set
That is, we identify elements \(u, {\tilde{u}} \in {{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), such that \(R(u  {\tilde{u}})=0\). Now R is a norm on the space \({{\mathrm{BV}}}_{0,R}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\); compare, e.g. [42] for the case of \(R={{\mathrm{TV}}}\).
Suppose
is a norm on \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), equivalent to the standard norm. If also the R SobolevKornPoincaré inequality
holds, we may then bound
Now, using the weak* lower semicontinuity of the BVnorm, and the weak* compactness of the unit ball in \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\)—we refer to [2] for these and other basic properties of BVspaces—we may thus find a representative \({\tilde{u}}\) in the \({{\mathrm{BV}}}_{0,R}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) equivalence class of u, satisfying
Again using the weak* compactness of the unit ball in \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), and the weak* lower semicontinuity of R, it follows that the sets
are weak* compact in \({{\mathrm{BV}}}_{0,R}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), in the topology inherited form \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\). Consequently, they are strongly compact subsets of the space \(L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\). This feature is crucial for the application of the regularisation theory in Banach lattices above.
On a connected domain \({\varOmega }\), in particular
That is, the space consists of zeromean functions. Then \(u \mapsto \Vert Du\Vert _{\mathcal {M}({\varOmega }; \mathbb {R}^m)}\) is a norm on \({{\mathrm{BV}}}_{0,{{\mathrm{TV}}}}({\varOmega })\) [42], and this space is weak* compact. In particular, the sets \({{\mathrm{lev}}}_a {{\mathrm{TV}}}\) are compact in \(L^1({\varOmega })\).
More generally, we know from [8] that on a connected domain \({\varOmega }\), \(\ker {{\mathrm{TV}}}\) consists of \({{\mathrm{Sym}}}^k(\mathbb {R}^m)\)valued polynomials of maximal degree k. By extension, the kernel of \({{\mathrm{TGV}}}^2\) consists of \({{\mathrm{Sym}}}^k(\mathbb {R}^m)\)valued polynomials of maximal degree \(k+1\). In both cases, (13), weak* lower semicontinuity of R and the equivalence of \(\Vert \,\varvec{\cdot }\,\Vert '\) to \(\Vert \,\varvec{\cdot }\,\Vert _{{{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))}\) hold by the results in [8, 11, 51]. Therefore, we have proved the following.
Lemma 1
Let \({\varOmega }\subset \mathbb {R}^m\) and \(k \ge 0\). Then the sets \({{\mathrm{lev}}}_a {{\mathrm{TV}}}\) and \({{\mathrm{lev}}}_a {{\mathrm{TGV}}}^2\) are weak* compact in \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) and strongly compact in \(L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\).
Now, in the above cases, \(\ker R\) is finitedimensional, and we may write
Denoting by
the closed ball of radius r in a normed space X, we obtain by the finitedimensionality of \(\ker R\) the following result.
Proposition 1
Let \({\varOmega }\subset \mathbb {R}^m\) and \(k \ge 0\). Pick \(a>0\). Then the sets
for both regularisers \(R={{\mathrm{TV}}}\) and \(R={{\mathrm{TGV}}}^2\), are weak* compact in \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) and strongly compact in \(L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\).
The next result summarises Theorem 3 and Proposition 1.
Theorem 4
With \(U=L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), let the operator \(A: U \rightarrow F\) be linear, continuous and injective. Let \(f^l_n\) and \(f^u_n\) be sequences of lower and upper bounds for the righthand such that
Supposing that there are no errors in the operator A and the exact solution \({\bar{u}}\) exists, define the feasible set as follows
Decomposing \(u \in U\) as \(u=u_0+u^\perp \) with \(u^\perp \in \ker R\), suppose
for some constant \(a>0\), then for \(R={{\mathrm{TV}}}\) and \(R={{\mathrm{TGV}}}^2\), the sequence
converges strongly in \(L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) to the exact solution \({\bar{u}}\) and \(R(u_n) \rightarrow R({\bar{u}})\).
Proof
With the decomposition \(u_n = u_{0,n} + u_n^\perp \), where \(u_n^\perp \in \ker R\), we have \(u_{0,n} \in {{\mathrm{lev}}}_a R\) for suitably large \(a>0\) through
The assumption (15) bounds \(\Vert u_n^\perp \Vert \le a\). Thus \(u_n \in V\) for V as in Proposition 1. The proposition thus implies the necessary compactness in \(U=L^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\) for the application of Theorem 3.
Remark 1
The condition (15) simply says for \(R={{\mathrm{TV}}}\) that the data have to bound the solution in mean. This is very reasonable to expect for practical data; anything else would be very nondegenerate. For \(R={{\mathrm{TGV}}}^2\) we also need that the data bound the entire affine part of the solution. Again, this is very likely for real data. Indeed, in DTI practice, with at least 6 independent diffusionsensitising gradients, A is an invertible or even overdetermined linear operator. In that typical case, the bounds \(f^l_n\) and \(f^u_n\) will be translated into \(U_n\) being a bounded set.
Solving the Optimisation Problem
The Chambolle–Pock Method
The Chambolle–Pock algorithm is an inertial primaldual backwardbackward splitting method, classified in [18] as the modified primaldual hybrid gradient method (PDHGM). It solves the minimax problem
where \(G: X \rightarrow \overline{\mathbb {R}}\) and \(F^*: Y \rightarrow \overline{\mathbb {R}}\) are convex, proper, lower semicontinuous functionals on (finitedimensional) Hilbert spaces X and Y. The operator \(K:X \rightarrow Y\) is linear, although an extension of the method to nonlinear K has recently been derived [55]. The PDHGM can also be seen as a preconditioned ADMM (alternating directions method of multipliers); we refer to [18, 47, 56] for reviews of optimisation methods popular in image processing. For step sizes \(\tau ,\sigma >0\), and an overrelaxation parameter \(\omega >0\), each iteration of the algorithm consists of the updates
We should remark that the order of the primal (u) and dual (y) updates here is reversed from the original presentation in [13]. The reason is that when reordered, the updates can, as discovered in [26], be easily written in a proximal point form.
The first and last update are the backward (proximal) steps for the primal (x) and dual (y) variables, respectively, keeping the other fixed. However, the dual step includes some “inertia” or overrelaxation, as specified by the parameter \(\omega \). Usually \(\omega =1\), which is required for convergence proofs of the method. If G or \(F^*\) is uniformly convex, by smartly choosing for each iteration the step length parameters \(\tau ,\sigma \), and the inertia \(\omega \), the method can be shown to have convergence rate \(O(1/N^2)\). This is similar to Nesterov’s optimal gradient method [43]. In the general case the rate is O(1 / N). In practice the method produces visually pleasing solutions in rather few iterations, when applied to image processing problems.
In implementation of the method, it is crucial that the resolvents \((I+\tau \partial G)^{1}\) and \((I+\sigma \partial F^*)^{1}\) can be computed quickly. We recall that they may be written as
Usually in applications, these computations turn out to be simple projections or linear operations—or the softthresholding operation for the \(L_1\)norm.
As a further implementation note, since the algorithm (17) is formulated in Hilbert spaces (see however [28]) while our problems are formulated in the Banach space \({{\mathrm{BV}}}({\varOmega }; {{\mathrm{Sym}}}^2(\mathbb {R}^3))\), we have to discretise our problems before application of the algorithm. We do this by simple forwarddifferences discretisation of the operator E with cell width \(h=1\) on a regular rectangular grid corresponding to the image voxels.
Implementation of Deterministic Constraints
We now reformulate the problem (11) of DTI imaging with deterministic error bounds in the form (16). Suppose we have some upper and lower bounds \(s_j^l\leqslant s_j\leqslant s_j^u\) on the DWI signals \(s_j\), (\(j=0,\ldots ,N\)). Then the bounds for \(g_j=\log (s_j/s_0)\) are
because \(g_j\) is monotone in regards to \(s_j\). We are thus trying to solve
where
For the ease of notation, we write
so that the Stejskal–Tanner equation is satisfied when
The problem (19) may be rewritten as
for
with \(\delta (g^l \leqslant y\leqslant g^u)\) denoting the indicator function of the convex set \(\{y :g^l \leqslant y\leqslant g^r\}\). Solving the conjugate
and also writing
for some \(R_0\) and \(K_0\), the problem can further be written in the saddle point form (16) with
To apply algorithm (17), we need to compute the resolvents of \(G_0^*\) and \(R_0^*\). For details regarding \(R_0^*\) for \(R={{\mathrm{TGV}}}_{(\beta ,\alpha )}^2\) and \(R=\alpha {{\mathrm{TV}}}\) in the discretised setting, we refer to [57, 58]; here it suffices to note that for \(R=\alpha {{\mathrm{TV}}}\), we have \(K_0=\alpha E\) and \(R_0^*(\phi )\) is the indicator function of the dual ball \(\{\phi \mid \sup _x \Vert \phi (x)\Vert _F \le 1\}\). Thus the resolvent \((I+\tau \partial R_0^*)^{1}\) becomes a projection to the dual ball. The case of \(R={{\mathrm{TGV}}}_{(\beta ,\alpha )}^2\) is similar. For \(F_0^*\) we have
which resolves pointwise at each \(\xi \in {\varOmega }\) into the expression
for
Finally, we note that the saddle point system (16) has to have a solution for the Chambolle–Pock algorithm to converge. In our setting, in particular, we need to find error bounds \(g^l\) and \(g^u\), for which there exists a solution u to
If one uses at most six independent diffusion directions (\(N=6\)), as we will, then, for any g, there in fact exists a solution to \(g=Au\). The condition (21) becomes \(g^l \leqslant g^u\), immediately guaranteed through the monotonicity of (18), and the trivial conditions \(s_j^l \leqslant s_j^u\).
We are thus ready to apply the algorithm (17) to diffusion tensor imaging with deterministic error bounds. For the realisation of (17) for models (8), (9), and (7), we refer to [55, 57–59].
Experimental Results
We now study the efficiency of the proposed reconstruction model in comparison to the different \(L^2\)squared models, i.e. ones with Gaussian error assumption. This is based on a synthetic data, for which a groundtruth is available, as well as a real in vivo DTI data set. First we, however, have to describe in detail the procedure for obtaining upper and lower bounds for real data, when we do not know the true noise model, and are unable to perform multiple experiments as required by the theory of Sect. 2.2.
Estimating Lower and Upper Bounds from Real Data
As we have already discussed, in practice the noise in the measurement signals \({\hat{s}}_j\) is not Gaussian or Rician; in fact we do not know the true noise distribution and other corruptions. Therefore, we have to estimate the noise distribution from the image background. To do this, we require a known correspondence between the measurement, the noise and the true value. As we have no better assumptions available, the standard one that we use is that of additive noise. Continuing in the statistical setting of Sect. 2.2, we now describe the procedure, working on discrete images expressed as vectors \({\hat{f}}=s_j \in \mathbb {R}^n\) for some fixed \(j \in \{0,1,\dots ,N\}\). We use superscripts to denote the voxel indices, that is \({\hat{f}}=(f^1,\ldots ,f^n)\).
In the ith voxel, the measured value \({\hat{f}}^i\) is the sum of the true value \(f^i\) and additive noise \(\nu ^i\):
All \(\nu ^i\) are assumed independent and identically distributed (i.i.d.), but their distribution is unknown. If we did know the true underlying cumulative distribution function F of the noise, we could choose a confidence parameter \(\theta \in (0,1)\) and use the cumulative distribution function to calculate \(\nu _{\theta /2}, \nu _{1\theta /2}\) such that^{Footnote 1}
Let us instead proceed nonparametrically, and divide the whole image into two groups of voxels: the ones belonging to the background region and the rest. For simplicity, let the indices \(i=1,\ldots ,k\), (\(k < n\)), stand for the background voxels. In this region, we have \(f^i = 0\) and \({\hat{f}}^i = \nu ^i\). Therefore, the background region provides us with a number of independent samples from the unknown distribution of \(\nu \). The Dvoretzky–Kiefer–Wolfowitz inequality [17, 37, 41] states that
for the empirical cumulative distribution function
Therefore, computing \(\nu _{\theta /2}\) and \(\nu _{1\theta /2}\) such that
we also have
We may therefore use the values
as lower and upper bounds for the true values \(f^i\) outside the background region.
The Dvoretzky–Kiefer–Wolfowitz inequality implies that the interval estimates converge to the true intervals, determined by (22), as the number of background pixels k increases with the image size n. This procedure, with large k, will therefore provide an estimate of a singleexperiment (\(m=1\)) confidence interval for \(f^i\). We note that this procedure will, however, not yield the convergence of the interval estimate \([{\hat{f}}^{l,i}, {\hat{f}}^{u,i}]\) to the true data; for that we would need multiple experiments, i.e. multiple sample images (\(m>1\)), not just agglomeration of the background voxels into a single noise distribution estimate. In practice, however, we can only afford a single experiment (\(m=1\)), and cannot go to the limit.
Verification of the Approach with Synthetic Data
To verify the effectiveness of the considered approach and to compare it to the other models, we use synthetic data. For the groundtruth tensor field \(u_{g.t.}\) we take a helix region in a 3D box \(100 \times 100 \times 30\), and choose the tensor in each point inside the helix in such a way that the principal eigenvector coincides with the helix direction (Fig. 2). The helix region is described by the following equations:
The vector direction in every point coincides with helix direction:
We take the parameters \(R=0.3, \phi _{\max }=4\pi , r_{\max }=0.07\) in this numerical experiment.
We apply the forward operators \(T_j(u_{g.t.})\) for each \(j=0, \ldots , 6\) to obtain the data \(s_j(x)\). We then add Rician noise to this data \(\bar{s_j}=s_j+\delta \) with \(\sigma =2\), which corresponds to \(PSNR \approx 27\hbox {dB}\).
We apply several models for solving the inverse problem of reconstructing u: the linear and nonlinear \(L^2\) approaches (8) and (7), and the constrained problem (11). As the regulariser we use \(R={{\mathrm{TGV}}}^2_{(0.9\alpha ,\alpha )}\), where the choice \(\beta =0.9\alpha \) was made somewhat arbitrarily, however yielding good results for all the models. This is slightly lower than the range \([1, 1.5]\alpha \) discovered in comprehensive experiments for other imaging modalities [7, 38].
For the linear and nonlinear \(L^2\) models (8) and (7), respectively, the regularisation parameter \(\alpha \) is chosen either by a version of the discrepancy principle for inconsistent problems [52] or optimally with regard to the \(\Vert \,\varvec{\cdot }\,\Vert _{F,2}\) distance between the solution and the groundtruth. In case of the discrepancy principle, such an \(\alpha \) was chosen that the following equality holds:
We find \(\alpha \) by solving this equation numerically using bisection method. We start by finding such \(\alpha _1,\alpha _2\) that \({\varDelta }\rho (\alpha _1)>0\) and \({\varDelta }\rho (\alpha _2)<0\). We calculate \({\varDelta }\rho (\alpha _3)\) for \(\alpha _3=\frac{\alpha _1+\alpha _2}{2}\) and depending on its sign replace either \(\alpha _1\) or \(\alpha _2\) with \(\alpha _3\). We repeat this procedure until the stopping criteria are reached.
As stopping criteria we use \(f(\alpha )<\epsilon \). We use \(\tau =1.05\), \(\epsilon =0.01\) for linear and \(\tau =1.2\), \(\epsilon =0.0001\) for nonlinear \(L^2\) solution. A value of \(\tau \) yielding a reasonable degree of smoothness has been chosen by trial and error, and is different for the nonlinear model, reflecting a different nonlinear objective in the discrepancy principle. For the constrained problem we calculate \(\theta =90\), 95 and \(99\,\%\) confidence intervals to generate the upper and lower bounds. We, however, digress a little bit from the approach of Sect. 2.2. Minding that we do not know the true underlying distribution, which fails to be Rician as illustrated in Fig. 1, we do not use it to calculate the confidence intervals, but use the estimation procedure described in Sect. 5.1. We stress that we only have a single sample of each signal \(s_j\), so are unable to verify any asymptotic estimation properties.
The numerical results are in Table 1 and Figs. 3, 4, and 5, with the first of the figures showing the colourcoded principal eigenvector of the reconstruction, the second showing the fractional anisotropy and principal eigenvectors and the last one the errors in the latter two, in a colourcoded manner. All plots are masked to represent only the nonzero region. The field of fractional anisotropy is defined for a field u of 2tensors on \({\varOmega }\subset \mathbb {R}^m\) as
with \(\lambda _1,\ldots ,\lambda _m\) denoting the eigenvalues of u(x) at a point \(x \in {\varOmega }\). It measures how far the ellipsoid prescribed by the eigenvalues and eigenvectors is from a sphere, with \(FA _u(x)=1\) corresponding a full sphere, and \(FA _u(x)=0\) corresponding to a degenerate object not having full dimension.
As we can see, the nonlinear approach (7) performs overall the best by a wide margin, in terms of the pointwise Frobenius error, i.e. error in \(\Vert \cdot \Vert _{F,2}\). This is expressed as a PSNR in Table 1. What is, however, interesting, is that the constraintbased approach (11) has a much better reconstruction of the principal eigenvector angle, and a comparable reconstruction of its magnitude. Indeed, the 95 % confidence interval in Figs. 3(g) and 4(g) suggests a nearly perfect reconstruction in terms of smoothness. But, the Frobenius PSNR in Table 1 for this approach is worse than the simple unregularised inversion by regression. The problem is revealed by Fig. 5(f): the large white cloudy areas indicate huge fractional anisotropy errors, while at the same time, the principal eigenvector angle errors expressed in colour are much lower than for other approaches. Good reconstruction of the principal eigenvector is important for the process of tractography, i.e. the reconstruction of neural pathways in a brain. One explanation for our good results is that the regulariser completely governs the solution in areas where the error bounds are inactive due to generally low errors. This results in very smooth reconstructions, which is in the present case desirable as our synthetic tensor field is also smooth within the helix.
Results with In Vivo Brain Imaging Data
We now wish to study the proposed regularisation model on a real in vivo diffusion tensor image. Our data are that of a human brain, with the measurements of a volunteer performed on a clinical 3T system (Siemens Magnetom TIM Trio, Erlangen, Germany), with a 32 channel head coil. A 2D diffusionweighted singleshot EPI sequence with diffusionsensitising gradients applied in 12 independent directions (\(b = 1000\,\hbox {s}/\hbox {mm}^2\)). An additional reference scan without diffusion was used with the parameters: \(\hbox {TR}=7900\hbox {ms}\), \(\hbox {TE}=94\hbox {ms}\), flip angle \(90^\circ \). Each slice of the 3D dataset has plane resolution \(1.95\,\hbox {mm} \times 1.95\,\hbox {mm}\), with a total of \(128 \times 128\) pixels. The total number of slices is 60 with a slice thickness of 2mm. The dataset consists of 4 repeated measurements. The GRAPPA acceleration factor is 2. Prior to the reconstruction of the diffusion tensor, eddycurrent correction was performed with FSL [50]. Written informed consent was obtained from the volunteer before the examination.
For error bounds calculation according to the procedure of Sect. 5.1, to avoid systematic bias near the brain, we only use about 0.6 % of the total volume near the borders, or roughly \(k \approx 6000\) voxels.
To estimate errors for the all the considered reconstruction models, for each gradient direction \(b_i\) we use only one out of the four duplicate measurements. We then calculate the errors using a somewhat less than ideal pseudogroundtruth, which is the linear regression reconstruction from all the available measurements.
The results are in Table 2 and Figs. 6, 7, and 8, again with the first of the figures showing the colourcoded principal eigenvector of the reconstruction, the second showing the fractional anisotropy and principal eigenvectors and the last one the errors in the latter two, in a colourcoded manner. Again, all plots are masked to represent only the nonzero region. In the figures, we concentrate on error bounds based on 95 % confidence intervals, as the results for the 90 and 99 % cases do not differ significantly according to Table 2.
This time, the linear \(L^2\) approach (8) has best overall reconstruction (Frobenius PSNR), while the nonlinear \(L^2\) approach (7) has clearly the best principal eigenvector angle reconstruction besides the regression, which does not seem entirely reliable regarding our regressionbased pseudogroundtruth. The constraintsbased approach (11), with 95 % confidence intervals is, however, not far behind in terms of numbers. More detailed study of the corpus callosum in Fig. 8 (small picture in picture) and Fig. 7, however, indicates a better reconstruction of this important region by the nonlinear approach. The constrained approach has some very short vectors there in the white region. Naturally, however, these results on the in vivo data should be taken with a grain of salt, as we have only a somewhat unreliable pseudogroundtruth available for comparison purposes.
Conclusions from the Numerical Experiments
Our conclusion is that the error boundsbased approach is a feasible alternative to standard modelling with incorrect Gaussian assumptions. It can produce good reconstructions, although the nonlinear \(L^2\) approach of [55] is possibly slightly more reliable. The latter does, however, in principle depend on a good initialisation of the optimisation method, unlike the convex boundsbased approach.
Further theoretical work will be undertaken to extend the partialorderbased approach to modelling errors in linear operators to the nonlattice case of the semidefinite partial order for symmetric matrices, which will allow us to consider problems of diffusion MRI with errors in the forward operator.
It also needs to be investigated whether the error bounds approach needs to be combined with an alternative, novel, regulariser that would ameliorate the fractional anisotropy errors that the approach exhibits. It is important to note, however, that from the practical point of view, of using the reconstruction tensor field for basic tractography methods based solely on principal eigenvectors, these are not that critical. As pointed out by one of the reviewers, the situation could differ with more recent geodesic tractography methods [20, 21, 25] employing the full tensor. We provide basic principal eigenvector tractography results for reference in Fig. 9, without attempting to extensively interpret the results. It suffices to say that the results look comparable. With this in sight, the error bounds approach produces a very good reconstruction of the direction of the principal eigenvectors, although we saw some problems with the magnitude within the corpus callosum.
Notes
Recall that for a random variable X with a cumulative distribution function F, the quantile function \(F^{1}\) returns a number \(x_\theta =F^{1}(\theta )\) such that \(P(X \leqslant x_\theta ) = \theta \).
Recall that an indexed subset \(\{ x_\tau :\tau \in \{\tau \} \}\) of an ordered vector space X is called directed upwards if for any pair \(\tau _1,\,\tau _2 \in \{\tau \}\) there exists \(\tau _3 \in \{\tau \}\) such that \(x_{\tau _3} \geqslant x_{\tau _1}\) and \(x_{\tau _3} \geqslant x_{\tau _2}\).
References
Aksoy, M., Forman, C., Straka, M., Skare, S., Holdsworth, S., Hornegger, J., Bammer, R.: Realtime optical motion correction for diffusion tensor imaging. Magn. Reson. Med. 66(2), 366–378 (2011). doi:10.1002/mrm.22787
Ambrosio, L., Fusco, N., Pallara, D.: Functions of Bounded Variation and Free Discontinuity Problems. Oxford University Press, Oxford (2000)
Arsigny, V., Fillard, P., Pennec, X., Ayache, N.: Logeuclidean metrics for fast and simple calculus on diffusion tensors. Magn. Reson. Med. 56(2), 411–421 (2006)
Basser, P.J., Jones, D.K.: Diffusiontensor MRI: theory, experimental design and data analysis—a technical review. NMR Biomed. 15(7–8), 456–467 (2002). doi:10.1002/nbm.783
Basu, S., Fletcher, T., Whitaker, R.: Rician noise removal in diffusion tensor mri. In: Larsen, R., Nielsen, M., Sporring, J. (eds.) Medical Image Computing and ComputerAssisted Intervention – MICCAI 2006, Lecture Notes in Computer Science, vol. 4190, pp. 117–125. Springer, Berlin (2006). doi:10.1007/11866565_15
Bačák, M., Bergmann, R., Steidl, G., Weinmann, A.: A second order nonsmooth variational model for restoring manifoldvalued images (2015)
Benning, M., Gladden, L., Holland, D., Schönlieb, C.B., Valkonen, T.: Phase reconstruction from velocityencoded MRI measurements—a survey of sparsitypromoting variational approaches. J. Magn. Reson. 238, 26–43 (2014). doi:10.1016/j.jmr.2013.10.003
Bredies, K.: Symmetric tensor fields of bounded deformation. Annali di Matematica Pura ed Applicata 192(5), 815–851 (2013). doi:10.1007/s1023101102484
Bredies, K., Kunisch, K., Pock, T.: Total generalized variation. SIAM J. Imaging Sci. 3, 492–526 (2011). doi:10.1137/090769521
Bredies, K., Kunisch, K., Valkonen, T.: Properties of \(L^1\)\(\text{ TGV }^2\): the onedimensional case. J. Math. Anal. Appl. 398, 438–454 (2013). doi:10.1016/j.jmaa.2012.08.053
Bredies, K., Valkonen, T.: Inverse problems with secondorder total generalized variation constraints. In: Proceedings of the 9th International Conference on Sampling Theory and Applications (SampTA) 2011, Singapore (2011)
Burger, M., Lucka, F.: Maximum a posteriori estimates in linear inverse problems with logconcave priors are proper bayes estimators. Inverse Prob. 30(11), 114,004 (2014)
Chambolle, A., Pock, T.: A firstorder primaldual algorithm for convex problems with applications to imaging. J. Math. Imaging Vis. 40, 120–145 (2011). doi:10.1007/s1085101002511
Chefd’hotel, C., Tschumperlé, D., Deriche, R., Faugeras, O.: Constrained flows of matrixvalued functions: Application to diffusion tensor regularization. In: Heyden, A., Sparr, G., Nielsen, M., Johansen, P. (eds.) Computer Vision–ECCV 2002, Lecture Notes in Computer Science, vol. 2350, pp. 251–265. Springer, Berlin (2002). doi:10.1007/3540479694_17
Cox, D., Hinkley, D.: Theoretical Statistics. Taylor & Francis, London (1979)
Dunford, N., Schwartz, J.T.: Linear Operators, Part I General Theory. Interscience Publishers, Hoboken (1958)
Dvoretzky, A., Kiefer, J., Wolfowitz, J.: Asymptotic minimax character of the sample distribution function and of the classical multinomial estimator. Ann. Math. Stat. 27(3), 642–669 (1956). doi:10.1214/aoms/1177728174
Esser, E., Zhang, X., Chan, T.F.: A general framework for a class of first order primaldual algorithms for convex optimization in imaging science. SIAM J. Imaging Sci. 3(4), 1015–1046 (2010). doi:10.1137/09076934X
Federer, H.: Geometric Measure Theory. Springer, New York (1969)
Fuster, A., Dela Haije, T., TristánVega, A., Plantinga, B., Westin, C.F., Florack, L.: Adjugate diffusion tensors for geodesic tractography in white matter. J. Math. Imaging Vis. 54(1), 1–14 (2016). doi:10.1007/s1085101505868
Fuster, A., TristanVega, A., Haije, T., Westin, C.F., Florack, L.: A novel riemannian metric for geodesic tractography in dti. In: Schultz, T., NedjatiGilani, G., Venkataraman, A., O’Donnell, L., Panagiotaki, E. (eds.) Computational Diffusion MRI and Brain Connectivity, Mathematics and Visualization, pp. 97–104. Springer, New York (2014). doi:10.1007/9783319024752_9
Getreuer, P., Tong, M., Vese, L.A.: A variational model for the restoration of MR images corrupted by blur and Rician noise. In: Advances in Visual Computing, Lecture Notes in Computer Science, vol. 6938, pp. 686–698. Springer, Berlin (2011). doi:10.1007/9783642240287_63
Grasmair, M., Haltmeier, M., Scherzer, O.: The residual method for regularizing illposed problems. Appl. Math. Comp. 218(6), 2693–2710 (2011). doi:10.1016/j.amc.2011.08.009
Gudbjartsson, H., Patz, S.: The Rician distribution of noisy MRI data. Magn. Reson. Med. 34(6), 910–914 (1995)
Hao, X., Whitaker, R., Fletcher, P.: Adaptive riemannian metrics for improved geodesic tracking of white matter. In: Székely, G., Hahn, H.K. (eds.) Information Processing in Medical Imaging, Lecture Notes in Computer Science, vol. 6801, pp. 13–24. Springer, Berlin (2011). doi:10.1007/9783642220920_2
He, B., Yuan, X.: Convergence analysis of primaldual algorithms for a saddlepoint problem: From contraction perspective. SIAM J. Imaging Sci. 5(1), 119–149 (2012). doi:10.1137/100814494
Herbst, M., Maclaren, J., Weigel, M., Korvink, J., Hennig, J., Zaitsev, M.: Prospective motion correction with continuous gradient updates in diffusion weighted imaging. Magn. Reson. Med. (2011). doi:10.1002/mrm.23230
Hohage, T., Homann, C.: A generalization of the ChambollePock algorithm to Banach spaces with applications to inverse problems (2014)
Kingsley, P.: Introduction to diffusion tensor imaging mathematics: Parts IIII. Concepts Magn. Reson. A 28(2), 101–179 (2006). doi:10.1002/cmr.a.20048
Knoll, F., Clason, C., Bredies, K., Uecker, M., Stollberger, R.: Parallel imaging with nonlinear reconstruction using variational penalties. Magn. Reson. Med. 67(1), 34–41 (2012)
Knoll, F., Raya, J.G., Halloran, R.O., Baete, S., Sigmund, E., Bammer, R., Block, T., Otazo, R., Sodickson, D.K.: A modelbased reconstruction for undersampled radial spinecho dti with variational penalties on the diffusion tensor. NMR Biomed. 28(3), 353–366 (2015). doi:10.1002/nbm.3258
Korolev, Y.: Making use of a partial order in solving inverse problems: II. Inverse Prob. 30(8), 085,003 (2014)
Korolev, Y., Yagola, A.: On inverse problems in partially ordered spaces with a priori information. J. Inverse IllPosed Prob. 20(4), 567–573 (2012)
Korolev, Y., Yagola, A.: Making use of a partial order in solving inverse problems. Inverse Prob. 29(9), 095,012 (2013)
Lassas, M., Saksman, E., Siltanen, S.: Discretizationinvariant bayesian inversion and Besov space priors. Inverse Prob. Imaging 3(1), 87–122 (2009). doi:10.3934/ipi.2009.3.87
Lassas, M., Siltanen, S.: Can one use total variation prior for edgepreserving bayesian inversion? Inverse Prob. 20(5), 1537 (2004). doi:10.1088/02665611/20/5/013
Lehmann, E., Romano, J.: Testing Statistical Hypotheses. Springer Texts in Statistics. Springer, New York (2008)
de Los Reyes, J.C., Schönlieb, C.B., Valkonen, T.: Bilevel parameter learning for higherorder total variation regularisation models. arXiv:1508.07243 (2015)
Luxemburg, W., Zaanen, A.: Riesz Spaces. NorthHolland Publishing Company, Amsterdam (1971)
Martín, A., Schiavi, E.: Automatic total generalized variationbased DTI Rician denoising. In: Image Analysis and Recognition, Lecture Notes in Computer Science, vol. 7950, pp. 581–588. Springer, Berlin (2013). doi:10.1007/9783642390944_66
Massart, P.: The tight constant in the DvoretzkyKieferWolfowitz inequality. Ann. Prob. 18(3), 1269–1283 (1990). doi:10.1214/aop/1176990746
Meyer, Y.: Oscillating Patterns in Image Processing and Nonlinear Evolution Equations. American Mathematical Society, Boston (2001)
Nesterov, Y.: A method of solving a convex programming problem with convergence rate \(O(1/k^2)\). Sov. Math. Dokl. 27(2), 372–376 (1983)
Pan, X., Sidky, E.Y., Vannier, M.: Why do commercial ct scanners still employ traditional, filtered backprojection for image reconstruction? Inverse Prob. 25(12), 123,009 (2009). doi:10.1088/02665611/25/12/123009
Rudin, L., Osher, S., Fatemi, E.: Nonlinear total variation based noise removal algorithms. Phys. D 60, 259–268 (1992)
Schaefer, H.: Banach Lattices and Positive Operators. Springer, New York (1974)
Setzer, S.: Operator splittings, bregman methods and frame shrinkage in image processing. Int. J. Comput. Vis. 92(3), 265–280 (2011). doi:10.1007/s1126301003573
Setzer, S., Steidl, G., Popilka, B., Burgeth, B.: Variational methods for denoising matrix fields. In: Weickert, J., Hagen, H. (eds.) Visualization and Processing of Tensor Fields, pp. 341–360. Springer, New York (2009)
Shiryaev, A.N.: Probability. Graduate Texts in Mathematics. Springer, New York (1996)
Smith, S.M., Jenkinson, M., Woolrich, M.W., Beckmann, C.F., Behrens, T.E.J., JohansenBerg, H., Bannister, P.R., Luca, M.D., Drobnjak, I., Flitney, D.E., Niazy, R.K., Saunders, J., Vickers, J., Zhang, Y., Stefano, N.D., Brady, J.M., Matthews, P.M.: Advances in functional and structural MR image analysis and implementation as FSL. Neuroimage 23(Suppl 1), S208–S219 (2004). doi:10.1016/j.neuroimage.2004.07.051
Temam, R.: Mathematical problems in plasticity. GauthierVillars, Paris (1985)
Tikhonov, A.N., Goncharsky, A.V., Stepanov, V.V., Yagola, A.G.: Numerical Methods for the Solution of IllPosed Problems. Kluwer, Dordrecht (1995)
Tournier, J.D., Mori, S., Leemans, A.: Diffusion tensor imaging and beyond. Magn. Reson. Med. 65(6), 1532–1556 (2011). doi:10.1002/mrm.22924
Tschumperlé, D., Deriche, R.: Diffusion tensor regularization with constraints preservation. In: IEEE Conference on Computer Vision and Pattern Recognition (CVPR), pp. 948–953 (2001)
Valkonen, T.: A primaldual hybrid gradient method for nonlinear operators with applications to MRI. Inverse Prob. 30(5), 055,012 (2014). doi:10.1088/02665611/30/5/055012
Valkonen, T.: Big images. In: Emrouznejad, A. (ed.) Big Data Optimization: Recent Developments and Challenges, Studies in Big Data. Springer, New York (2015). Accepted
Valkonen, T., Bredies, K., Knoll, F.: Total generalised variation in diffusion tensor imaging. SIAM J. Imaging Sci. 6(1), 487–525 (2013). doi:10.1137/120867172
Valkonen, T., Knoll, F., Bredies, K.: TGV for diffusion tensors: a comparison of fidelity functions. J. Inverse IllPosed Prob. 21, 355–377 (2013). doi:10.1515/jip20130005. Special issue for IP:M&S 2012, Antalya, Turkey
Valkonen, T., Liebmann, M.: GPUaccelerated regularisation of large diffusion tensor volumes. Computing 95, 771–784 (2013). doi:10.1007/s006070120277x. Special issue for ESCO2012, Pilsen, Czech Republic
Weickert, J.: Anisotropic Diffusion in Image Processing, vol. 1. Teubner, Stuttgart (1998)
Acknowledgments
While at the Center for Mathematical Modelling of the Escuela Politécnica Nacional in Quito, Ecuador, T. Valkonen has been supported by a Prometeo scholarship of the Senescyt (Ecuadorian Ministry of Science, Technology, Education, and Innovation). In Cambridge, T. Valkonen has been supported by the EPSRC Grants No. EP/J009539/1 “Sparse & Higherorder Image Restoration” and No. EP/M00483X/1 “Efficient computational tools for inverse imaging problems”. A. Gorokh and Y. Korolev are grateful to the RFBR (Russian Foundation for Basic Research) for partial financial support (Projects 140131173 and 140191151). The authors would also like to thank Karl Koschutnig for the in vivo dataset, Kristian Bredies for scripts used to generate the tractography images and Florian Knoll for many inspiring discussions.
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Appendices
Appendix 1: A Data Statement for the EPSRC
The MRI scans used for this publication have been used by the courtesy of the producer. Data that are similar for all intents and purposes, are widespread, and can be easily produced by making a measurement of a human subject with an MRI scanner. Our source codes are archived at https://www.repository.cam.ac.uk/handle/1810/253422.
Appendix 2: Notation and Techniques
We recall some basic, not completely standard, mathematical notation and concepts in this appendix. We begin with partially ordered vector spaces, following the book [46]. Then we proceed to tensor calculus and tensor fields of bounded variation and of bounded deformation. These are also covered in more detail for the diffusion tensor imaging application in [57].
Banach Lattices
A linear space X endowed with a partial order relation \(\leqslant \) is called an ordered vector space if the partial order agrees with linear operations in the following way:
An ordered vector space is called a vector lattice if each pair of elements \(x,y \in X\) have a supremum \(x \vee y \in X\) and infimum \(x \wedge y \in X\). Supremum of two elements x, y of a Banach lattice X is the element \(z = x \vee y\) with the following properties: \(z \geqslant x, \,\, z \geqslant y\) and \(\forall {\tilde{z}} \in X\) such that \({\tilde{z}} \geqslant x\) and \({\tilde{z}} \geqslant y\) we have \({\tilde{z}} \geqslant z\).
For any \(x \in X\), the element \(x_+ = x \vee 0\) is called its positive part, the element \(x_ = (x) \vee 0 = (x)_+\) is called its negative part and the element \(x = x_+ + x_\) is its absolute value. The equalities \(x = x_+  x_\) and \(x = x \vee (x)\) hold for any \(x \in X\).
It is obvious that suprema and infima exist for any finite number of elements of a vector lattice. A vector lattice X is said to be order complete if any bounded from above set in X has a supremum.
Let X and Y be ordered vector spaces. A linear operator \(U :X \rightarrow Y\) is called positive, if \(x \geqslant _X 0\) implies \(Ux \geqslant _Y 0\). An operator U is called regular, if it can be written as \(U = U_1  U_2\), where \(U_1\) and \(U_2\) are positive operators.
Denote the linear space of all regular operators \(X \rightarrow Y\) by \(L^\sim (X,Y)\). A partial order can be introduced in \(L^\sim (X,Y)\) in the following way: \(U_1 \geqslant U_2\), if \(U_1  U_2\) is a positive operator. If X and Y are vector lattices and Y is order complete, then \(L^\sim (X,Y)\) is also an order complete vector lattice.
A norm \(\Vert \cdot \Vert \) defined in a vector lattice X is called monotone if \(x \leqslant y\) implies \(\Vert x\Vert \leqslant \Vert y\Vert \). A vector lattice endowed with a monotone norm is called a Banach lattice if it is norm complete. If X and Y are Banach lattices, then all operators in \(L^\sim (X,Y)\) are continuous.
Let us list some examples of Banach lattices. The space of continuous functions \(C({\varOmega })\), where \({\varOmega }\subset {\mathbb {R}}^n\), is a Banach lattice under the natural pointwise ordering: \(f \geqslant _C g\) if and only if \(f(x) \geqslant g(x)\) for all \(x \in {\varOmega }\). The spaces \(L^p({\varOmega })\), \(1 \leqslant p \leqslant \infty \), are also Banach lattices under the following partial ordering: \(f \geqslant _{L^p} g\) if and only if \(f(x) \geqslant g(x)\) almost everywhere in \({\varOmega }\). With this partial order, \(L^p({\varOmega })\), \(1 \leqslant p \leqslant \infty \), are order complete Banach lattices. The Banach lattice of continuous functions \(C({\varOmega })\) is not order complete.
Tensors in the Euclidean Setting
We call a klinear mapping \(A: \mathbb {R}^m \times \cdots \times \mathbb {R}^m \rightarrow \mathbb {R}\) a ktensor, denoted \(A \in \mathcal {T}^k(\mathbb {R}^m)\). This is a simplification from the full differentialgeometric definition, sufficient for our finitedimensional setting. We say that A is symmetric, denoted \(A \in {{\mathrm{Sym}}}^k(\mathbb {R}^m)\), if it satisfies for any permutation \(\pi \) of \(\{1,\ldots ,k\}\) that
With \(e_1,\ldots ,e_m\) the standard basis of \(\mathbb {R}^m\), we define on \(\mathcal {T}^k(\mathbb {R}^m)\) the inner product
and the Frobenius norm
The Frobenius norm is rotationally invariant in a sense crucial for DTI. We refer to [57] for a detailed discussion of this, as well of alternative rotationally invariant norms.
Example 1
(Vectors) Vectors \(A \in \mathbb {R}^m\) are of course symmetric 1tensors, the inner product is the usual inner product in \(\mathbb {R}^m\) and the Frobenius norm is the twonorm, \(\Vert A\Vert _F=\Vert A\Vert _2\).
Example 2
(Matrices) Matrices are 2tensors: \(A(x, y) = \langle A x,y\rangle \), while symmetric matrices \(A=A^T\) are symmetric 2tensors. The inner product is \(\langle A,B\rangle =\sum _{i,j} A_{ij}B_{ij}\) and \(\Vert A\Vert _F\) is the matrix Frobenius norm.
We use the notation \(A \ge 0\) for positivesemidefinite matrices A. One can verify that this relation indeed defines a partial order in the space of symmetric matrices:
With this partial order, the space of all symmetric matrices becomes an ordered vector space, but not a vector lattice. However, it enjoys some properties similar to those of vector lattices: for example, any directed upwards subset^{Footnote 2} has a supremum [39, Ch.8].
Symmetric Tensor Fields of Bounded Deformation
Let \(u: {\varOmega }\rightarrow {{\mathrm{Sym}}}^k(\mathbb {R}^m)\) for a domain \({\varOmega }\subset \mathbb {R}^m\). We set
and
The spaces \(L^p({\varOmega }; {{\mathrm{Sym}}}^{k}(\mathbb {R}^m))\) are defined in the natural way using these norms, and clearly satisfy all the usual properties of \(L^p\) spaces.
In the particular case of matrices (\(k=2\)), partial order can be introduced in the space \(L^p({\varOmega }; {{\mathrm{Sym}}}^{2}(\mathbb {R}^m))\) in the following way:
Recall that the symbol \(\ge \) stands for the positivesemidefinite order (25) in the space of symmetric matrices. Since the positivesemidefinite order is not a lattice, neither is the order (26).
If \(u \in C^1({\varOmega }; {{\mathrm{Sym}}}^k(\mathbb {R}^m))\), \(k\ge 1\), we define by contraction the divergence \({{\mathrm{div}}}u \in C({\varOmega }; {{\mathrm{Sym}}}^{k1}(\mathbb {R}^m)\) as
It is easily verified that \({{\mathrm{div}}}u(x)\) is indeed symmetric. Given a tensor field \(u \in L^1({\varOmega }; \mathcal {T}^{k}(\mathbb {R}^m))\) we then define the symmetrised distributional gradient \(E u \in [C_c^\infty ({\varOmega }; {{\mathrm{Sym}}}^{k+1}(\mathbb {R}^m))]^*\) by
With these notions at hand, we now define the spaces of symmetric tensor fields of bounded deformation as (see also [8, 57])
where
For \(u \in {{\mathrm{BD}}}({\varOmega }; {{\mathrm{Sym}}}^{k}(\mathbb {R}^m))\), the symmetrised gradient Eu is a Radon measure, \(Eu \in \mathcal {M}({\varOmega }; {{\mathrm{Sym}}}^{k+1}(\mathbb {R}^m))\). For the proof of this fact we refer to [19, §4.1.5].
Example 3
The space \({{\mathrm{BD}}}({\varOmega }; {{\mathrm{Sym}}}^{0}(\mathbb {R}^m))\) is the space \({{\mathrm{BV}}}({\varOmega })\) of functions of bounded variation while \({{\mathrm{BD}}}({\varOmega }; {{\mathrm{Sym}}}^{1}(\mathbb {R}^m))\) is the space \({{\mathrm{BD}}}({\varOmega })\) of functions of bounded deformation of [51].
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Gorokh, A., Korolev, Y. & Valkonen, T. Diffusion Tensor Imaging with Deterministic Error Bounds. J Math Imaging Vis 56, 137–157 (2016). https://doi.org/10.1007/s1085101606397
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DOI: https://doi.org/10.1007/s1085101606397
Keywords
 Diffusion tensor imaging
 Noise modelling
 Total generalised variation
 Error bounds
 Deterministic
Mathematics Subject Classification
 92C55
 94A08