Skip to main content

Thank you for visiting nature.com. You are using a browser version with limited support for CSS. To obtain the best experience, we recommend you use a more up to date browser (or turn off compatibility mode in Internet Explorer). In the meantime, to ensure continued support, we are displaying the site without styles and JavaScript.

Design of Acquisition Schemes and Setup Geometry for Anisotropic X-ray Dark-Field Tomography (AXDT)

Abstract

Anisotropic X-ray Dark-field Tomography (AXDT) is a new imaging technique for reconstructing the three-dimensional scattering profile within a sample using the dark-field signal measured in an X-ray grating interferometry setup. As in any tomographic measurement, the acquisition geometry plays a key role in the accurate reconstruction of the scattering information. More- over, the anisotropic nature of the dark-field signal poses additional challenges for designing the acquisition protocols. In this work, we present an efficient approach to measure scattering orientations spread over the unit sphere and prove its efficacy using the knowledge from conventional tomography. In addition, we conclude (using analytical and experimental results) that placing the gratings such that the grating bars make an angle of 45 degrees with respect to the vertical direction is the optimal setup configuration for AXDT.

Introduction

X-ray imaging using a grating interferometer has gained much attention in recent years1,2,3. By analyzing the interference pattern created by a phase grating at specific downstream positions, we obtain three signals namely attenuation, phase contrast and dark-field. While the attenuation and phase-contrast signals originate from the attenuation and phase shift of the incident X-ray beam caused by the sample, the dark-field signal originates from the small-angle scattering caused by micron and sub-micron sized structures4,5,6,7,8. The dark-field signal is anisotropic9,10,11 which means that the measured signal depends on the relative orientation of the sample with respect to the propagation direction of X-rays and the orientation of the grating bars.

The anisotropic property of the dark-field signal can be utilized to obtain two-dimensional orientation of microstructures in the imaging plane by rotating the sample around the beam propagation direction in a technique known as X-ray Vector Radiography (XVR)12, 13. A single-shot variant of XVR was recently presented by Kagias et al.14 where a specialized grating was used to obtain the two-dimensional orientations without any sample rotation. Since XVR can only resolve orientations in a plane orthogonal to the direction of beam propagation, it is best suited for investigating relatively flat samples. Revol et al.15 presented a method to calculate the strength of scattering along certain a priori known orientations in different layers of a multi-layered composite material. Bayer et al.9 presented a three-dimensional extension of XVR, however, they were able to reconstruct only the projection of orientations onto a plane.

Malecki et al.16 presented the first fully three-dimensional directional dark-field imaging method and termed it “X-ray Tensor Tomography” (XTT). XTT, as the name suggests, approximates the scattering profile in every volume element by a symmetric rank-2 tensor. Vogel et al.17 presented several algorithmic improvements for the fast and efficient reconstruction of these tensors in three dimensions. The tensor approximation, however, is insufficient for recovering multiple scattering orientations in a single volume element which is especially relevant since the structures probed with this technique are typically smaller than the spatial resolution. To overcome this limitation, Wieczorek et al.18 presented a technique termed “Anisotropic X-ray Dark-field Tomography” (AXDT) which reconstructs the scattering profile as a spherical function represented using spherical harmonics. This method not only provides a more accurate and robust representation of the three-dimensional scattering profile but also allows for the extraction of multiple scattering orientations in a single volume element. Directional dark-field imaging in two and three dimensions, such as XVR or XTT, has been found useful for resolving orientations in composite materials made of carbon and glass fibers as well as in biological specimens such as bones and teeth19,20,21.

In order to reconstruct the three-dimensional scattering function accurately, the recorded anisotropic scattering information must be well distributed over all possible scattering orientations $$q\in {{\mathbb{S}}}^{2}$$ (we denote the border of the unit sphere in three dimensions as $${{\mathbb{S}}}^{2}=\{u\in {{\mathbb{R}}}^{3};|u|=1\}$$). Malecki et al.16 presented a first idea of such a scheme utilizing the three rotation axes provided by an Eulerian cradle shown in Fig. 1. Sharma et al.22 presented a detailed analysis of similar schemes and introduced an analytical measure known as the “Coverage Metric” suitable for the relative comparison of XTT/AXDT acquisition schemes. These schemes were motivated mainly by convenience and speed of acquisition and even though they probe many scattering orientations as shown in our previous work22, all of these orientations are measured insufficiently.

In this work, we present an approach to acquire three-dimensional anisotropic dark-field data such that specific orientations on the unit sphere are probed completely. However, due to the physical limitations of the setup discussed in the next section, most of the orientations can only be probed up to a certain extent. We analyze the resulting acquisition schemes for different setup configurations and show that certain grating orientations are advantageous compared to others for measuring the most information within the physical limitations of the setup. In addition, we visualize the null space23, 24 of the proposed schemes to illustrate the correlation between the reconstruction and acquisition methods for AXDT. Finally, we corroborate the theoretical findings with experimental results for an industrially relevant fiber composite sample.

Methods

This section is divided into three sub-sections. In the first sub-section, we present our novel concept of acquisition schemes and explain how to obtain such schemes mathematically. In the second sub-section, we present a short summary of Anisotropic X-ray Dark-field Tomography. Finally, we present a method for estimating one component of the null space of an AXDT acquisition scheme.

Design of Acquisition Schemes

In conventional tomography, we acquire line integrals through a three-dimensional object onto a 2D detector and use analytic or iterative methods to reconstruct the 3D volume from several 2D images acquired at different poses of the sample. The pre-requisite for recovering the 3D spatial information from 2D projections is that the total measured signal in any projection is constant, that is, the measured quantity (such as X-ray attenuation coefficient) is invariant under rotation. This is, however, not true for the dark-field signal. Due to its anisotropic nature, the dark-field signal varies as the object is rotated around an axis. However, it is possible to define an axis of rotation such that a certain component of the scattering function (q) is invariant under rotation of the object around this particular axis25. We use this concept to design an acquisition trajectory that comprises of several poses for which a unique component of the dark-field signal remains invariant, thus allowing for a full tomographic reconstruction of this particular component. In the following, we explain how such an acquisition trajectory can be designed for any scattering orientation $$q\in {{\mathbb{S}}}^{2}$$.

We define the sensitivity vector $$s(x)\in {{\mathbb{S}}}^{2}$$ and the tomographic vector $$t(x)\in {{\mathbb{S}}}^{2}$$ for every acquisition pose x = (ψ, θ, ϕ), where the Euler angles ψ (rotation around y), θ (rotation around z′) and ϕ (rotation around y′) are shown in Fig. 1. We have:

$$\begin{array}{rcl}s(x) & = & R(x)\cdot S,\\ t(x) & = & R(x)\cdot T,\end{array}$$
(1)

where $$R(x)\in {{\mathbb{S}}}^{3\times 3}$$ is the Euler rotation matrix for the pose x, $$S\in {{\mathbb{S}}}^{2}$$ is the setup sensitivity, $$T\in {{\mathbb{S}}}^{2}$$ is the direction of beam propagation ([0, 0, 1]T in the setup shown in Fig. 1) and · denotes standard matrix-vector multiplication. S is the direction in which the phase shift is measured by the grating interferometer setup; it is orthogonal to the grating bars in the plane of the gratings ([0, 1, 0]T in the setup shown in Fig. 1). Evidently, the sensitivity vector denotes the scattering orientation that is probed at the acquisition pose x while the tomographic vector represents the direction along which the signal is integrated.

Let us define an acquisition scheme as:

$$A(\psi ,\theta ,N):=\{x=(\psi ,\theta ,\varphi );\varphi \in \{{0}^{\circ },\frac{{180}^{\circ }}{N},\ldots ,{180}^{\circ }-\frac{{180}^{\circ }}{N}\};N\in {\mathbb{N}}\}\mathrm{.}$$
(2)

A conventional X-ray CT acquisition scheme in this notation can be expressed as A(0, 0, N). The points ±t(x) for xA(0, 0, 11) are shown as blue dots in Fig. 2(a). Such a circular measurement trajectory with sufficiently large value of N is desired for analytic reconstruction in X-ray CT. However, the sensitivity vector has no significance in X-ray CT since the measured quantity is invariant under rotation. In the case of dark-field signal, we also compute ±s(x) for xA(0, 0, 11) assuming horizontally (S = [0, 1, 0]T), vertically (S = [1, 0, 0]T) and diagonally (S = [0.7071, −0.7071, 0]T) oriented gratings which are shown as red points in Fig. 2(a–c).

Using the concept of rotational invariance, we postulate that a scattering orientation $$q\in {{\mathbb{S}}}^{2}$$ can be recovered for a three-dimensional volume by measuring it from N poses x i , i = 1, 2, …, N, such that s(x i ) = q and the vectors t(x i ) consist of N points equally spaced on a circular trajectory. It can be seen that this condition is satisfied for q = [0, 1, 0]T in Fig. 2(a). On the other hand, each of the 11 points of scheme A(0, 0, 11) measure a separate sensitivity vector when gratings are placed vertically (Fig. 2(b)) or diagonally (Fig. 2(c)). However, we can obtain the same blue and red points as Fig. 2(a) for vertical and diagonal gratings with the schemes A(0, 90, 11) and A(0, 45, 11), respectively. More generally, we can obtain an acquisition scheme Y(q, S, N) := {y i (q, S) := (ψ, θ, ϕ), i = 1, …, N} that fully measures the orientation q for the setup sensitivity S. In other words, s(y i (q, S)) = q for all i. To obtain a scheme Y(q, S, N), we transform x i A(0, 0, N) to y i (q, S). Note from Fig. 2(a) that A(0, 0, N) = Y([0, 1, 0]T, [0, 1, 0]T, N). The method to calculate Y(q, S, N) from A(0, 0, N) is given in Algorithm 1.

Figure 2(d) shows an orientation vector ± q in red and the vectors ± t(y) in blue for all yY(q, [0.7071, −0.7071, 0]T, 10). Using the procedure described above, we can design an acquisition scheme Z(S, N) that measures L scattering orientations fully and comprises of L*N poses for the given setup sensitivity S:

$$Z(S,N)=\{Y({q}_{l},S,N);l=1,\ldots ,L\}.$$
(3)

Algorithm 1: Calculate Y(q, S, N) from A(0, 0, N)

For every xA(0, 0, N)

1. 1.

Calculate Euler rotation matrix R(x).

2. 2.

Calculate R intermediate (x, q) such that R intermediate (x, q) · [0, 1, 0]T = q:

$${R}_{intermediate}(x,q)=R(x)\cdot M([0,1,0{]}^{T},q),$$
(4)

where $$M({v}_{1},{v}_{2})\in {{\mathbb{R}}}^{3\times 3}$$ is a matrix such that v 2 = M(v 1, v 2) · v 1 for all $${v}_{1},{v}_{2}\in {{\mathbb{S}}}^{2}$$.

3. 3.

Estimate the orientation $$u(x,q,S)\in {{\mathbb{S}}}^{2}$$ measured by the rotation matrix R intermediate (x, q) given the setup sensitivity S:

$$u(x,q,S)={R}_{intermediate}(x,q)\cdot S\mathrm{.}$$
(5)
4. 4.

Rotate u(x, q, S) to q:

$${R}_{final}(x,q,S)={R}_{intermediate}(x,q)\cdot M(u(x,q,S),q\mathrm{).}$$
(6)
5. 5.

Compute the pose y(q, S) = (ψ, θ, ϕ) from the matrix R final (x, q, S) such that the absolute value of ψ in y(q, S) is minimized.

Anisotropic X-ray Dark-Field Tomography

The goal of tomographic reconstruction of the anisotropic dark-field signal is to reconstruct the scattering information at each location within the measured object. In order to do so, we use the recently introduced AXDT method18. Here the scattering profile in each location of the object is modeled as a spherical function such that the process of reconstruction aims at recovering this field of spherical functions $$\eta :{{\mathbb{S}}}^{2}\times {{\mathbb{R}}}^{3}\to {\mathbb{R}}$$. In order to model the sensitivity vector s(x) and tomographic vector t(x) for every pose x, a weighting function $$h:{{\mathbb{S}}}^{2}\times {{\mathbb{S}}}^{2}\times {{\mathbb{S}}}^{2}\to {\mathbb{R}}$$ is used. Further, both the field of scattering functions as well as this weighting function are expressed in terms of real-valued spherical harmonics with their coefficients denoted as $${\eta }_{k}^{m}$$ and $${h}_{k}^{m}$$ respectively, where k specifies the degree and m the order of the spherical harmonics. With this notation and a truncation degree K, the dark-field measurement at the acquisition pose x can be approximately modelled by:

$$d(x)\approx \exp (-\frac{1}{4\pi }\sum _{k=0}^{K}\sum _{m=-k}^{k}{h}_{k}^{m}(s(x),t(x)){\int }_{T(x)}{n}_{k}^{m}(r)dr)\mathrm{.}$$
(7)

By using one of the standard discretization methods for line integrals of p = (−ln(d(x))) over the rays T(x) yielding a system matrix P and by forming weighting matrices $${W}_{k}^{m}$$ according to $${h}_{k}^{m}(s(x),t(x))$$, the reconstruction of the spherical harmonics coefficients of the field of scattering profiles reduces to solving the following linear equation system:

$$p=\sum _{k=0}^{K}\sum _{m=-k}^{m=k}{W}_{k}^{m}P{\eta }_{k}^{m}=\mathop{\underbrace{(\begin{array}{ccccc}{W}_{0}^{0}P & \cdots & {W}_{K}^{-K}P & \cdots & {W}_{K}^{K}P\end{array})}}\limits_{\,=A\,}(\begin{array}{c}{\eta }_{0}^{0}\\ \vdots \\ {\eta }_{K}^{-K}\\ \vdots \\ {\eta }_{K}^{K}\end{array}),$$
(8)

where we call A as the full system matrix. We solve this system using the conjugate gradient method with K = 4. Spherical harmonics of degree 4 are sufficient to describe the spherical function completely with the weighting function that is used.

Null space estimation

One way to analyze the acquisition schemes and their effect on the reconstruction is to analyze the nature of the full system matrix A. An important aspect of a linear operator, such as A in the AXDT model described above, is the null space (or kernel) of A. It is defined as ker(A) := {v|Av = 0} and is of special interest as for w ker(A) and any v ker(A), the measurement does not change under addition i.e.,

$$Aw=A(w+v\mathrm{).}$$
(9)

The kernel provides a tool to analyze the matrix A and gives information about the uncertainty of a computed reconstruction. While it is well known that incomplete data leads to a larger nullspace, it is of special interest how elements of this space look like as they provide a relative insight of which regions are likely to be affected more/less.

Standard methods such as singular value decomposition (SVD) are typically used for computing the null space of such matrices. However, these methods rely on the full representation of the matrix. It should be noted that the system matrix P of the standard tomographic problem is typically too large to store in the memory of currently available computing devices. The full system matrix A for AXDT is larger by an additional factor of 2K − 1 due to the weighting function. Therefore, we reconstruct one vector spanning a subspace of the nullspace of A by iteratively solving Av = 0 for v. Different vectors v ker(A) can be computed by starting from different initial guesses for v. We compute one component of the null space by starting with an initial guess of v such that:

$$v=\{{\eta }_{k}^{m};{\eta }_{k}^{m}=0\,{\rm{for}}\,k\ne 0,{\eta }_{k}^{m}=(\begin{array}{c}0.01\\ \vdots \\ 0.01\end{array})\,{\rm{for}}\,k=0\},$$
(10)

for all voxels. Since spherical harmonics are equivalent to a fourier series in terms of angular frequency, this initial guess is equivalent to starting with a uniform spherical function which is a good initial guess for clearly visualizing the effect of AXDT acquisition schemes. For computing the null space, we set the reconstruction volume size to 50 × 50 × 50, the detector size to 100 × 100 to limit computation times and use a parallel geometry assumption in order to eliminate errors at the edges due to forward and back-projection.

Results

In this section, we present an analysis of the acquisition schemes designed in the previous section with respect to the setup geometry and its limitations. In addition, we use null space analysis to demonstrate the correlation of these schemes with the AXDT reconstruction. In the end, we corroborate the results presented in this section with experimental observations for an industrially relevant sample consisting of micrometer sized structures.

Acquisition Schemes and Setup Geometry

In the previous section, we presented a method to design an acquisition scheme Z(S, N) that fully measures several sensitivity orientations on the unit sphere. The first step for designing such a scheme is to choose a set of orientations that we wish to measure. In order to reconstruct the spherical function using AXDT, it is required to choose orientations that are uniformly distributed on the unit sphere. One example of such sets of orientations are the t-designs presented by Hardin and Sloane26. We use these designs as they are a good choice for selecting uniformly distributed points on the sphere. However, any uniform distribution of points on the sphere can be used. We begin with a symmetric t-design consisting of 56 directions spread over the unit sphere as shown in Fig. 3(a). Since the AXDT model is symmetric around the origin, we use only 28 directions of this t-design spread over one half of the unit sphere.

Next, we generate an acquisition scheme:

$$Z({[0.7071,-0.7071,0]}^{T},100)=\{Y({q}_{i},{[0.7071,-0.7071,0]}^{T},100),\,i=1,\ldots ,28\},$$
(11)

consisting of 2800 poses. The vectors ± t(x) for all xZ([0.7071, −0.7071, 0]T, 100) are shown in Fig. 3(b). This acquisition scheme fully measures the 56 points shown in Fig. 3(a). However, it can be seen in Fig. 1 that the Eulerian cradle intercepts the beam for high values of ψ, hence, the setup is limited to −40 ≤ ψ ≤ 40. Therefore, all of the 2800 poses for the scheme Z(S, 100) cannot be measured. Figure 3(c) shows the points of Fig. 3(b) that can be measured with the condition |ψ| ≤ 40°.

The ratio of the points that can be measured (Fig. 3(c)) to the total number of desired points (Fig. 3(b)) is a function of the maximum reachable value of ψ and the setup sensitivity. Therefore, to study this effect, we calculate Z(S, N) for 91 values of S such that:

$$\langle S,[1,0,0]\rangle =\,\cos (\alpha );\alpha \in [{0}^{\circ },{1}^{\circ },{2}^{\circ },\ldots ,{90}^{\circ }],$$
(12)

where $$\langle \cdot ,\cdot \rangle$$ denotes the inner product. Figure 4(a) shows a 2D plot of the relative fraction of measurable poses (out of 2800) for the acquisition scheme Z(S, 100) for different values of reachable ψ [0°, 1°, 2°, …, 90°]. A line of this 2D plot for the maximum reachable ψ limit of 40° is shown in Fig. 4(b) (red curve). The point of maximum of this line plot corresponds to Z([0.7071, −0.7071, 0]T, 100), that is, when the grating bars are placed diagonally. In addition, similar line plots for acquisition schemes Z(S, N), N = 60, 20 are shown. We observe that the line plots for lower values of N have step-like artifacts arising from round-off errors which can be circumvented by using large number of sampling orientations. As it is difficult to actually align gratings at precise angles in most of the currently available setups, we only study the three extreme points marked in Fig. 4(b). We define the notation Z D (N), Z H (N) and Z V (N) to denote acquisition schemes with diagonal, horizontal and vertical arrangement of grating bars respectively. Figure 3(c–e) shows the vectors ± t(x) for the measurable poses of acquisition schemes Z D (100), Z H (100), and Z V (100), respectively, assuming that poses with |ψ| > 40° cannot be measured. It is evident from these results that the maximum amount of poses can be probed by placing the gratings such that the grating lines are aligned diagonally. From now on, we will assume that all acquisition schemes Z(S, N) are truncated at |ψ| = 40°, since this is the practical limit of our setup.

Correlation of the Design of Acquisition Schemes with AXDT Reconstruction

We presented a method to design acquisition schemes by extending the concept of circular acquisition trajectories normally used in conventional CT to the special case of XTT/AXDT. In this section, we visualize the null space of the new schemes to demonstrate the correlation between the acquisition schemes and the AXDT reconstruction.

It was outlined above that the acquisition trajectories are truncated due to the physical limitations of the setup. This means that we cannot measure the full tomographic trajectory Y(q i , S, N) for all the orientations q i , i = 1, …, 28. The missing angles lead to circular trajectories with missing wedges similar to the ones in limited angle tomography. In standard tomography, the null space is easily understood in terms of the Fourier Slice theorem. However, the Fourier Slice theorem does not carry over to our system due to its sensitivity specificity. Hence, it is not possible to assume that similar limited angle artifacts can also be seen for the case of AXDT. Moreover, all of the poses for Z(S, N) are used for the reconstruction of the spherical harmonic coefficients in AXDT reconstruction, and there is no direct reconstruction of individual components corresponding to each of the truncated trajectory. However, we postulate that our acquisition schemes correlate well to the reconstruction process of AXDT and, hence, some effect of the limited angle trajectories should be visible in the corresponding spherical function.

To check this hypothesis, we estimate the null space for the proposed schemes as explained previously. Next, we probe the reconstructed null space (in terms of spherical coefficients) at the specific points q i , i = 1, …, 28, in order to evaluate the effect of the missing wedges for these individual scattering orientations. Figure 5 shows the null space components for the scheme Z D (100) (similar figures for Z V (100) and Z H (100) are provided in the Supplementary Material). The magenta points show the tomographic trajectory for all components q i as projected onto the x − z plane. Analogously, the images show the null space averaged over all x − z planes for the corresponding component after the first iteration. The null space artifacts caused by the ψ truncation can be seen explicitly in the individual components reconstructed with AXDT.

Comparison to Schemes Presented by Malecki et al

In this section, we compare the schemes in Fig. 3(c–e) to the ones previously used by our group16,17,18, 21. Such a scheme can be written as:

$$\begin{array}{rcl}W(N) & = & \{w=(\psi ,\theta ,\varphi );\,\psi \in \{{0}^{\circ },{20}^{\circ },{40}^{\circ }\},\theta \in \{{0}^{\circ },{30}^{\circ },{60}^{\circ },{90}^{\circ }\},\\ \quad \,\,\,\,\varphi & \in & \{{0}^{\circ },\frac{{360}^{\circ }}{N},\ldots ,{360}^{\circ }-\frac{{360}^{\circ }}{N}\}\}.\end{array}$$
(13)

The trajectory ± t(w) for all wW(100) is shown in Fig. 3(f). Here we assume vertical grating alignment which is the most commonly used configuration.

In order to compare the proposed schemes for different grating orientations and W(N), we use the Coverage Metric (CM) proposed in our previous work22. This is a metric which determines the degree up to which an acquisition scheme measures all orientations on the unit sphere or, in other words, CM(X) provides a measure of the efficiency of any acquisition scheme X. The usability of CM as a valid metric for XTT acquisition schemes was established in ref. 22. It can be directly applied to AXDT as well, since the two methods only differ in the reconstruction method and the acquisition protocol is identical. Figure 6(a) shows the coverage metric for Z D (N), Z H (N), Z V (N), and W(N) for different values of N.

Experimental Results

In this section, we present experimental results to support the observations made in the previous sections. We measured a circular thermoplastic short fibre moulding part, composed of fibres that are 7 μm thick and 200 μm long, at a resolution of approximately 80 μm. We employed 7 phase steps with 1 sec. exposure per step using a setup7 comprising of an X-ray WorX micro-focus X-ray tube (operated at voltage 60 kVp and power 25 W) and a Varian PaxScan 2520DX detector (pixel size 127 μm). The three gratings with periods of 10 μm, 5 μm and 10 μm, respectively, were arranged in the first fractional Talbot configuration at a design energy of 45 keV. Since we obtain both the dark-field and attenuation signal in a grating interferometer, we can also reconstruct the attenuation volume. One slice of the attenuation data is shown in Fig. 7(a). Obviously, the imaging resolution is not sufficient to resolve the fibres with a diameter of 7 μm. However, we can resolve the porosity as seen in the bottom of Fig. 7(a).

Next, we perform AXDT reconstruction. A slice of $${\eta }_{0}^{0}$$, which is the isotropic component of the dark-field signal, is shown Fig. 7(b). Figure 7(c) shows the main orientation in every third voxel as extracted from the spherical function. The vectors have been masked with the attenuation signal to avoid the undesired effect of edge-scattering at the pores27, 28. The red box in Fig. 7(c) shows a feature in this sample which cannot be seen in either of 7(a) or 7(b). This is a weld-line and is only revealed by extracting the orientations of the fibres in the region using AXDT. Very high resolution micro CT may be required to directly resolve this structure but then a sample of this dimension (28 × 23 × 21 mm3) cannot be measured at once and one would have to resort to multiple tomographies or even to destroying the sample.

In order to evaluate the effect of the grating orientation on the reconstruction result, we show the region marked in Fig. 7(c) for different acquisition schemes in Fig. 8. The columns in Fig. 8 correspond to three different values of N = {100, 20, 10} for a specific scheme, while the rows show four different schemes for the same value of N. Next, we define an Experimental Metric, EM(X), for an acquisition schemes X as:

$$EM(X)=\frac{1}{I}\sum _{i=1}^{I}|\langle {U}_{i}(X),{U}_{i}({Z}_{D}(100))\rangle |$$
(14)

where $$\langle \cdot ,\cdot \rangle$$ is the standard scalar product, U i (Z D (100)) and U i (X) denote the structure orientation for the voxel index i = 1, …, I in the region-of-interest (red rectangle in Fig. 8) calculated using the acquisition scheme Z D (100) and an arbitrary scheme X, respectively. The value of the Experimental Metric for different schemes is shown in Fig. 6(b).

Discussion

We present a new technique to design acquisition schemes for directional dark-field tomographic imaging. We use the concept of rotational invariance to design tomographic trajectories that fully measure a unique component of the three dimensional scattering function. However, we show that all of the desired poses cannot be measured in a regular setup. In fact, this is a problem for most of the setup configurations, since it is always difficult to measure along the axis of the sample mount with X-rays. Therefore, we show the fraction of poses that can be measured for different setup configurations in Fig. 4(a,b). We observe that while it is possible to measure all the information with any grating orientation in an ideal setup, the grating orientation starts to play a major role when the setup limitation, that is the availability of the angle ψ only up to a certain value, is enforced. It can be seen that we can optimize the amount of measurable poses by placing the gratings diagonally.

Next, we study the effect of the aforementioned setup limitation by visualizing the null space of the AXDT operator. It can be seen in Fig. 5 that the ψ limitation leads to missing wedges (magenta points) in the tomographic trajectories for most of the orientations. We note that the effect of these missing wedges can be directly seen in the null space of the corresponding component. This is an interesting finding because of the fact that even though the AXDT operator uses all of the poses at the same time to reconstruct the spherical function, we are still able to see the effect of the limited angle trajectories at the corresponding sensitivity points on the reconstructed field. More importantly, the null space visualization is proof that the initial concept of calculating tomographic trajectories which provide invariant dark-field signal for certain pre-defined orientation vectors works exactly as we expect it to. Please note that the fact that we only get one component of ker(A) is not a limitation for our work since we compute this component in the exact same way for all the orientations.

We use the Coverage Metric (CM)22 to compare the new schemes Z D (N), Z H (N), Z V (N) among themselves and to the schemes that have been used by our group in previous works W(N). It can be seen in Fig. 6(a) that the value of CM decreases with the value of N for all four schemes and that the new schemes outperform the previously used scheme W(N). Moreover, Z D (N) has the highest value of CM amongst the new schemes. This implies that diagonal grating alignment is the most efficient of the proposed schemes (as also seen in Fig. 4), followed by horizontal alignment, and vertical grating alignment is the least favorable.

Finally, we show an example of the application of AXDT to an industrially relevant composite material. We show in Fig. 7(c) that AXDT is able to resolve orientations of fibres with sizes that are much below the resolution of the imaging system. Moreover, the fibre orientations calculated using AXDT reveal a particular feature (weld-line) in the sample which cannot be seen in conventional attenuation or even the isotropic component of the dark-field signal. We compare, qualitatively in Fig. 8 and quantitatively in Fig. 6(b), the new schemes Z(S, N) for three different grating orientations and the old schemes W(N). We can see in Fig. 8 that although the weld-line is clearly visible in all the schemes with N = 100 (first row), the scheme Z D (100) provides the most comprehensible distinction of the weld-line. More importantly, the quality of this result is maintained for Z D (20) and Z H (20), while significant deterioration can be seen for Z V (20) and W(20). The vectors reconstructed with the schemes W(N) (last column in Fig. 8) seem to be oriented in certain preferred directions and the variations are lost. This is due to the fact that the schemes W(N) provide an uneven sampling of the unit sphere22 and the reconstruction is biased towards a partial reconstruction of the most commonly sampled scattering orientations.

In Fig. 6(b), we compare the performance of the schemes with respect to the scheme Z D (100), which is assumed as the reference dataset. Here, we can see that the vectors in the region-of-interest deviate most from the reference for the schemes W(N). Also, we observe that the trend of the graph for the four schemes matches the corresponding trend observed in Fig. 6(a). This observation supports our claim that the new type of acquisition schemes provide better results than the old ones. Moreover, we can also conclude that diagonal grating orientation is the most favorable followed by horizontal and vertical alignment of gratings for the new schemes. It should also be noted that Z D (20) corresponds to a measurement time of only ~2 hours and is still of comparable quality to Z D (100) which requires ~10 hours of measurement. This reduction in acquisition time is a substantial improvement compared to the long measuring times of ~10 hours required for the schemes used previously16, 17, 22.

Conclusion

In this work, we present a more efficient method to design acquisition schemes for tomographic imaging of the directional dark-field signal and present results of diagonal grating orientation being the most optimal setup configuration for these schemes. Finally, we also show that the new schemes with diagonal grating alignment allow us to obtain good image quality with only ~2 hours of measurement time instead of the ~10 hours of measurements that was used previously.

References

1. Momose, A. et al. Demonstration of x-ray talbot interferometry. Japanese Journal of Applied Physics 42, L866 (2003).

2. Pfeiffer, F., Weitkamp, T., Bunk, O. & David, C. Phase retrieval and differential phase-contrast imaging with low-brilliance X-ray sources. Nature Physics 2, 258–261 (2006).

3. Pfeiffer, F. et al. Hard-X-ray dark-field imaging using a grating interferometer. Nature materials 7, 134–137 (2008).

4. Cong, W., Pfeiffer, F., Bech, M. & Wang, G. X-ray dark-field imaging modeling. J. Opt. Soc. Am. A 29, 908–912 (2012).

5. Pelzer, G. et al. Energy weighted x-ray dark-field imaging. Opt. Express 22, 24507–24515 (2014).

6. Wang, Z. et al. Non-invasive classification of microcalcifications with phase-contrast X-ray mammography. Nature communications 5, 3797 (2014).

7. Prade, F., Yaroshenko, A., Herzen, J. & Pfeiffer, F. Short-range order in mesoscale systems probed by x-ray grating interferometry. EPL (Europhysics Letters) 112, 68002 (2015).

8. Strobl, M. General solution for quantitative dark-field contrast imaging with grating interferometers. Scientific Reports 4, 7243 (2014).

9. Bayer, F. L. et al. Reconstruction of scalar and vectorial components in x-ray dark-field tomography. Proceedings of the National Academy of Sciences 111, 12699–12704 (2014).

10. Bayer, F. et al. Projection angle dependence in grating-based x-ray dark-field imaging of ordered structures. Opt. Express 21, 19922–19933 (2013).

11. Yashiro, W. et al. Distribution of unresolvable anisotropic microstructures revealed in visibility-contrast images using x-ray talbot interferometry. Phys. Rev. B 84, 094106 (2011).

12. Schaff, F. et al. Correlation of X-ray vector radiography to bone micro-architecture. Scientific reports 4, 3695 (2014).

13. Jensen, T. H. et al. Directional x-ray dark-field imaging. Physics in Medicine and Biology 55, 3317 (2010).

14. Kagias, M., Wang, Z., Villanueva-Perez, P., Jefimovs, K. & Stampanoni, M. 2d-omnidirectional hard-x-ray scattering sensitivity in a single shot. Physical Review Letters 116, 093902 (2016).

15. Revol, V., Kottler, C., Kaufmann, R., Neels, A. & Dommann, A. Orientation-selective x-ray dark field imaging of ordered systems. Journal of Applied Physics 112, 114903 (2012).

16. Malecki, A. et al. X-ray tensor tomography. EPL (Europhysics Letters) 105, 38002 (2014).

17. Vogel, J. et al. Constrained X-ray tensor tomography reconstruction. Opt. Express 23, 15134–15151 (2015).

18. Wieczorek, M., Schaff, F., Pfeiffer, F. & Lasser, T. Anisotropic X-Ray Dark-Field Tomography: A Continuous Model and its Discretization. Physical Review Letters 117, 158101 (2016).

19. Prade, F. et al. Nondestructive characterization of fiber orientation in short fiber reinforced polymer composites with X-ray vectorradiography. NDT & E International 86, 65–72 (2016).

20. Malecki, A. et al. Correlation of X-Ray Dark-Field Radiography to Mechanical Sample Properties. Microscopy and Microanalysis 20, 1528–1533 (2014).

21. Jud, C. et al. Dentinal tubules revealed with x-ray tensor tomography. Dental Materials 32, 1189–1195 (2016).

22. Sharma, Y. et al. Six dimensional x-ray tensor tomography with a compact laboratory setup. Applied Physics Letters 109, 134102 (2016).

23. Zeng, G. L. & Gullberg, G. T. Null-space function estimation for the interior problem. Phys. Med. Biol. Phys. Med. Biol 57, 1873–1887 (2012).

24. Wilson, D. et al. Decomposition of images and objects into measurement and null components. J. Nucl. Med 29, 1704–1709 (1988).

25. Feldkamp, J. M. et al. Recent developments in tomographic small-angle X-ray scattering. Phys. Status Solidi A 206, 1723–1726 (2009).

26. Hardin, R. H. & Sloane, N. J. A. Mclaren’s improved snub cube and other new spherical designs in three dimensions. Discrete & Computational Geometry 15, 429–441 (1996).

27. Yashiro, W. & Momose, A. Effects of unresolvable edges in grating-based x-ray differential phase imaging. Opt. Express 23, 9233–9251 (2015).

28. Wolf, J. et al. Lens-term- and edge-effect in X-ray grating interferometry. Biomedical Optics Express 6, 4812–4824 (2015).

Download references

Acknowledgements

This work was funded by the European Commission under grant agreement number 605162 (BERTI) and the DFG Cluster of Excellence, Munich-Centre for Advanced Photonics (MAP). The authors thank O. Focke (Faserinstitut Bremen), S. Zabler (Fraunhofer EZRT) and M. Willner (MITOS GmbH) for providing and discussing the sample used in this study. Additional support was provided by the German Research Foundation (DFG) and the Technische Universität München within the funding programme Open Access Publishing, DFG Gottfried Wilhelm Leibniz program, the TUM Institute for Advanced Study and the Karlsruhe Nano Micro Facility (KNMF, www.kit.edu/knmf).

Author information

Authors

Contributions

Y.S., F.S., F.P. and T.L. conceived the experiment. F.S. and Y.S. implemented the methods and performed the experiments. M.W. helped with AXDT reconstruction and null space estimation. Y.S. performed the data analysis with significant inputs from T.L. and M.W. Y.S. prepared the manuscript with contributions from all authors.

Corresponding author

Correspondence to Y. Sharma.

Ethics declarations

Competing Interests

The authors declare that they have no competing interests.

Additional information

Publisher's note: Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Rights and permissions

Open Access This article is licensed under a Creative Commons Attribution 4.0 International License, which permits use, sharing, adaptation, distribution and reproduction in any medium or format, as long as you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The images or other third party material in this article are included in the article’s Creative Commons license, unless indicated otherwise in a credit line to the material. If material is not included in the article’s Creative Commons license and your intended use is not permitted by statutory regulation or exceeds the permitted use, you will need to obtain permission directly from the copyright holder. To view a copy of this license, visit http://creativecommons.org/licenses/by/4.0/.

Reprints and Permissions

About this article

Cite this article

Sharma, Y., Schaff, F., Wieczorek, M. et al. Design of Acquisition Schemes and Setup Geometry for Anisotropic X-ray Dark-Field Tomography (AXDT). Sci Rep 7, 3195 (2017). https://doi.org/10.1038/s41598-017-03329-0

Download citation

• Received:

• Accepted:

• Published:

• DOI: https://doi.org/10.1038/s41598-017-03329-0

Further reading

• Fast acquisition protocol for X-ray scattering tensor tomography

• Jisoo Kim
• Matias Kagias
• Marco Stampanoni

Scientific Reports (2021)

• X-ray dark-field tomography reveals tooth cracks

• Christoph Jud
• Yash Sharma
• Daniela Pfeiffer

Scientific Reports (2021)

• A 3-D Projection Model for X-ray Dark-field Imaging

• Lina Felsner
• Shiyang Hu
• Christian Riess

Scientific Reports (2019)

• Tilted grating phase-contrast computed tomography using statistical iterative reconstruction

• Lorenz Birnbacher
• Manuel Viermetz
• Franz Pfeiffer

Scientific Reports (2018)

• Brain Connectivity Exposed by Anisotropic X-ray Dark-field Tomography

• Matthias Wieczorek
• Florian Schaff
• Tobias Lasser

Scientific Reports (2018)

Comments

By submitting a comment you agree to abide by our Terms and Community Guidelines. If you find something abusive or that does not comply with our terms or guidelines please flag it as inappropriate.

Search

Quick links

Sign up for the Nature Briefing newsletter — what matters in science, free to your inbox daily.

Get the most important science stories of the day, free in your inbox. Sign up for Nature Briefing