Artifact removal in the contour areas of SAXS-CT images by Tikhonov-L1 minimization

Small-angle X-ray scattering (SAXS) coupled with computed tomography (CT), denoted SAXS-CT, enables the spatial distribution of the characteristic parameters of nanoscale structures inside samples to be visualized. In this work, a new scheme with Tikhonov regularization was developed to remove the effects of artifacts caused by streak scattering originating from contour regions of the sample.


Introduction
Small-angle X-ray scattering (SAXS) has been widely used to characterize nanoscale structures within soft materials (Roe, 2000;Narayanan, 2009;Sakamoto & Hashimoto, 1995;Perret & Ruland, 1970;Takenaka, 2013). Recently, SAXS was combined with computed tomography (CT) to develop a powerful technique, known as the SAXS-CT method, for visualizing the spatial distribution of nanoscale structures inside samples (Feldkamp et al., 2009;Schaff et al., 2015;Skjønsfjell et al., 2016;Georgiadis et al., 2015;Hé monnot & Kö ster, 2017;Hu et al., 2017;Conceiçã o et al., 2020). In SAXS-CT, we reconstruct the image of the sample from the SAXS intensity, while the image obtained from conventional CT is reconstructed from the transmittance of X-rays within the sample. Thus, the characteristic parameters obtained from the scattered intensity can be used as a contrast factor to form CT images. For example, when we construct a CT image from the intensity of the peak position characterizing the long spacing between the lamellar structures of crystalline polymers, we can obtain the spatial distribution of the lamellar structures Stribeck et al., 2006Stribeck et al., , 2008. Moreover, if we use the orientation factor obtained from 2D SAXS patterns, we can visualize the spatial distribution of nanostructural orientations.
In the SAXS-CT method, the basic experimental geometry is the same as that of conventional SAXS. The sample is irradiated by the narrow incident beam (x direction). SAXS-CT also needs a 'scan' along the axis perpendicular to the incident beam (y direction), achieved by moving the sample or the incident beam. The scan is repeated while the sample is rotated around the axis perpendicular to both the x and the y directions. The rotation angle () corresponds to the 'projection angle' in conventional CT geometry. Thus, we obtain the 2D SAXS patterns at y and .
In this experimental geometry, we often face the serious problem that the reflection of incident X-rays interferes with the 2D SAXS patterns near the sample edge, which can result in anomalous scattering (artifacts) and seriously damage the reconstructed CT image. Voids within samples also cause strong scattering (Nozue et al., 2007;Yang et al., 1997;Etrillard et al., 2005;Grubb & Murthy, 2010;Tomisawa et al., 2019) which interferes with the accuracy of the reconstructed CT image. We can avoid the appearance of artifacts in CT images by analyzing the intensities at q positions outside these streaks or by changing the measurement conditions, such as the camera length. However, these approaches can be applied in only a limited number of cases.
Therefore, we attempted to remove streak-derived intensities from the sinogram ( À y) by implementing Tikhonov-L1 optimization. We treated the removal procedure of the streak-derived noise as a constrained convex optimization problem, where we imposed Tikhonov-type regularization on the sinogram to exploit its underlying smoothness and used L1 norm regularization to characterize the sparsity of the streakderived noise. For a sample, we employed a crystalline polymer exhibiting an isotropic peak in the SAXS scattering pattern originating from lamellar structures. We found almost identical SAXS patterns at any and y value except at the edge of the sample. When the incident beam irradiated the edge region of the sample, strong streak scattering was observed in the 2D SAXS pattern. By using this framework, we succeeded in obtaining a sinogram with the noise eliminated. However, we were able to apply this framework only to the data in the y direction at specific positions containing noise while preserving the y direction data at other positions. By reconstructing a CT image from this sinogram, we assessed the possibility of evaluation in the contour areas.

Sample
We used high-density polyethylene (HDPE, Tosoh Corporation), a typical crystalline polymer, as the sample in this study. In the SAXS region, we can observe the long spacing in lamellar structures (Schultz et al., 1978;Strobl & Schneider, 1980;Bartczak et al., 1992;Albrecht & Strobl, 1995;Hughes et al., 1997;Tashiro et al., 1998;Kishimoto et al., 2020). Isotropic lamellar structures can be obtained by isothermal crystallization after the onset of quenching from the melt state to the crystallization temperature; thus, we can observe the isotropic scattering pattern of the sample at each irradiation position. Details of the polymer properties and measurement samples are given in the supporting information. The measurement sample had a cuboid shape, 0.86 Â 0.98 Â 22.5 mm (x Â y Â z) in size.

SAXS measurements
SAXS measurements were performed at the second experimental hutch of beamline BL03XU at SPring-8, Frontier Soft-Material Beamline (FSBL), which is dedicated to SAXS experiments, using an intense beam (10 13 photons s À1 ) with very low divergence [12.3 mrad (horizontal) Â 1.1 mrad (vertical)]. The X-ray wavelength and the sample-todetector distance were 0.1 nm and 4438 mm, respectively (Masunaga et al., 2011). The beam size at the sample position was estimated using the method of scanning a blade. Fig. 1 shows the direct beam intensities when the blade is scanned horizontally at y = 2.0 mm. We fitted the beam profile with a Gaussian function, resulting in a full width at half-maximum (FWHM) of 75 mm. Furthermore, the beam diameter derived from the positions at which the intensity decayed from the peak intensity to 1/exp(2) was 128 mm. In the same manner, the beam diameter in the vertical direction was found to be 114 mm (see Fig. S1 of the supporting information). The scattering images were detected by a PILATUS 1M (Dectris Ltd.) with an exposure time of 0.5 s.
To reconstruct the images in the lateral directions using the CT method for the HDPE sample, we scanned a distance spanning 1.8 mm in steps of 30 mm in the direction perpendicular to the axis of rotation (y axis). The scanning step was approximately 1/4 of the incident beam width (the beam size in the horizontal direction). In the rotation scan , images were acquired in 3.0 steps for 0.0 < 180.0 .

Tikhonov-L1 minimization
This section is devoted to introducing our streak-removal framework based on Tikhonov-L1 minimization. Let v be a measured sinogram with noise. Then, our framework to eliminate noise with Tikhonov-L1 minimization is formulated as the following constrained optimization problem: Find u Ã ¼ argmin u jjDðuÞjj 2 þjjuÀvjj 1 subject to ðuÞ ¼ ðvÞ; where u* is a sinogram with noise eliminated and u is the transient candidate of u*. The first term jjD(u)jj 2 is the Tikhonov regularization term for the image, where D(Á) is an operator computing the 2D local differences of the input. jÁj 2 denotes the squared norm (the sum of the squared values in the array), which plays a role in exploiting the inherent smoothness of the sinogram for estimation. The second term jju À vjj 1 is the L1 data fidelity with respect to the measured sinogram v, where jjÁjj 1 denotes the L1 norm (the sum of the absolute values). The parameter balances these two terms. We characterized the noise by using the L1 norm, known as an effective sparsity-inducing criterion, since the noise (expressed as u À v in the optimization problem) is expected to be sparsely distributed on the measured sinogram.
The hard constraint (u) = (v) allowed us to maintain the measured values in v that reside in noise-free areas, where the operator selects all the entries in those areas. If no information was known about the noise-free areas in advance, this constraint was simply removed.
In general, total variation (TV) type regularizations are better than the Tikhonov regularization for noise removal and compressed sensing of images with a piece-wise smooth structure (Chambolle, 2004;Bredies et al., 2010). Our formulation is somewhat unusual in that it imposes hard constraints on the region specified by , such that the value of the measurement v must be maintained. As a result, the optimization can only change the signal values in a small number of local regions, and since the local regions of the sinogram have a very smooth structure, the Tikhonov regularization, which is more strongly smoothing than TV-type regularization, is more appropriate.
Owing to the above mathematical characterizations, noise can be effectively removed while maintaining the detailed structure of the sinogram. To solve our optimization problem, we also developed an efficient algorithm based on a state-ofthe-art optimization technique called the primal-dual splitting method (PDS; Condat, 2013).
We should note that the number of iterations required for convergence is generally larger in PDS than in the well known proximal algorithm of the alternating direction method of multipliers (ADMM; Boyd et al., 2011). However, in ADMM, at each iteration, it is necessary to solve a quadratic minimization involving a matrix consisting of a difference operator D and a region selection operator . As a result, it is necessary to solve a system of linear equations for each iteration, which incurs a considerable computational cost. On the other hand, PDS does not require such a step, and so PDS is less computationally expensive and easier to implement. For more information on proximal algorithms see Parikh & Boyd (2014) and Combettes & Pesquet (2011).
The programming language used was MATLAB. The optimization scheme iterated 2500 times, and the time to convergence was less than 1.0 s. The MATLAB code for the main part of the algorithm is shown in the supporting information. Fig. 2(a) shows a 2D SAXS image acquired around the center part of the sample at = 0 . We observed a peak in the scattering pattern reflecting the periodicity of the lamellar structures. The peak intensity was isotropic, indicating that the orientation of the lamellar structures was isotropic. 1D profiles at various y values are plotted as a function of the y axis wavenumber q y in Fig. 2(e). We observed a broad peak at q y = 0.219 nm À1 [as indicated by A in Fig. 2( f)], which corresponds to the long spacing between lamellar structures. An isotropic pattern was observed when the incident X-rays were irradiated inside the sample. On the other hand, the scattering patterns at the edges were affected by the reflection of the incident beam. Figs. 2(b)-2(d) show representative 2D SAXS images observed when the incident X-rays irradiated the sample edges. Fig. 2(b) reveals strong streaks in the horizontal (y axis) direction from the beam center position; the streak is particularly strong at q y > 0 nm À1 , indicating that reflection from one edge of the sample was observed without   attenuation in this direction. Note that the peak intensities from 270 to 90 were higher than those from 90 to 270 . We observed these asymmetric intensities when the edge of the sample was irradiated. This asymmetry was due to the effects of air scattering before the sample. When irradiating the right edge of the sample, air scattering in the range 90-270 is attenuated by the sample. On the other hand, the air scattering at 270-90 does not pass through the sample. As a result, the left and right halves of the image might show different intensities. Fig. 2(b) shows that the diffraction peak appeared at around q = 0.138 nm À1 . The reflected beam from the edge of the sample is intense. We attributed this diffraction to the reflected light irradiating the Kapton (the window material of the vacuum path). In Fig. 2(c), a strong streak was observed at q y < 0 nm À1 at the sample edge on the other side. We also observed streaks in the horizontal direction in the 2D SAXS image at = 90 [ Fig. 2(d)]. As shown in Fig. 2(e), at y = 0.45 mm and = 0 [corresponding to Fig. 2(b)], the streak intensity overwhelmed the peak intensity of lamellar structures in all q y regions. Consequently, we were not able to identify the scattering peak [as indicated by B in Fig. 2(e)]. At y = 1.41 mm and = 0 [corresponding to Fig. 2(c)], a high streak intensity was observed at q y < 0.195 nm À1 , but it did not affect the peak profile. For q y > $ 0.195 nm À1 , the intensity was almost identical to that obtained from Fig. 2(a). The scattering profile at y = 0.45 mm and = 90 in Fig. 2(e) was affected by the streak intensity, although the peak was observed in the profile. These results indicate that the intensity at the peak position q y = 0.219 nm À1 was affected by the streak intensity. The effect of the streak intensity became increasingly significant with decreasing q y at the sample edges. The disturbance caused by the streak scattering can be discerned at position C.

Results and discussion
Note that the streak scattering from the edges in this case did not affect the peak intensity parallel to the axis of rotation or q z direction, as indicated by point A in Figs. 2(a)-2(d). The scattered intensities along q z are plotted in Fig. 2( f ). We could not detect any effects from the streak scattering at any value of y, indicating that the sinogram and the reconstructed image were not affected by the streak-scattering disturbance. Thus, we first reconstructed a CT image from the intensity at point A to obtain a sinogram free from streak-scattering noise. Fig. 3(a) shows the sinogram obtained from the intensity at point A in the parameter space and y. The sinogram does not contain any abrupt intensity spikes. The intensity profiles for = 0 in Fig. 3(a) are plotted as a function of y (as indicated by the dotted line S A ) in Fig. 3(b). An inclination can be observed at both ends of the profile. This inclination originated from the change in the irradiation area of the incident beam at the edges of the samples, causing the width of the inclination y to correspond to the beam diameter. However, the width of the inclination at the edges of the sample (at = 0 ) was estimated at 90 < y < 150 mm, which is consistent with the horizontal beam diameter [as indicated by RS A in Fig. 3(b)]. The contour areas corresponding to the inclination can be observed in the CT image reconstructed from the sinogram, as shown in Fig. 3(c). Fig. 3(d) shows the crosssectional intensity profile for x = 0.84 mm as a function of y [as indicated by the dotted line C A in Fig. 3(c)]. The inclination of the contour area was again evaluated at 90 < y < 150 mm [as indicated by RC A in Fig. 3(d)], which is consistent with the values estimated in the sinogram. Thus, when streak scattering does not affect the reconstruction, inclination of the beam width can be observed at the edge of the sample in the CT image. Next, we will discuss how streak scattering affects CT images. We obtained sinograms from the scattering intensities at various q y positions. Fig. 4 shows the sinograms of the scattered intensity at a given q y = 0.219 nm À1 corresponding to the peak position in the parameter space of and y. We observed spots at the y positions along the sample edges at approximately = 0, 90 and 180 , as indicated by S B 1 À S B 6 in Fig. 4(a). The intensity profiles  along the dotted line S B at = 0 in Fig. 4(a) are plotted as a function of y in Fig. 5(a). A distinct peak in the profile was found at y = 0.45 mm [as indicated by PS B 1 in Fig. 5(a)]. The peak width was evaluated to be 120 < y < 180 mm, consistent with the horizontal beam diameter. This agreement indicates that streak scattering appears once the incident beam irradiates the edge of the sample at y = 0.45 mm. On the other hand, we were not able to observe a distinct peak at another edge of the sample, y = 1.38 mm [as indicated by PS B 2 in Fig. 5(a)]. However, the width of the inclination was in the range 60 < y < 120 mm, which is approximately 47-94% smaller than the horizontal beam diameter. This decrease in the width originated from the fact that streak scattering compensates for the gradual decrease in the intensity at the inclination area. Although the streak scattering at the edge of y = 1.38 mm did not appear as strong, the profile was modified by streak scattering.
The intensity profile along the dotted line S B at = 90 in Fig. 4(a) is shown in Fig. 5 Fig. 5(b)], and the peak widths were estimated to be 120 < y < 180 mm and 90 < y < 150 mm, respectively. The horizontal beam diameters were found to be within these ranges.

indicated by PS B 3 and PS B 4 in
The CT image reconstructed from the original sinogram of Fig. 4(a) is shown in Fig. 6(a). Artifacts are apparent in the x direction at the IC B region in Fig. 6(a) and are attributed to the intensities in parts S B 1 and S B 5 in Fig. 4(a). Additionally, we observed partial artifacts in regions IIC B and IIIC B in the CT image due to the intensities in the S B 3 and S B 4 parts of Fig. 4(a). In contrast, there were no artifacts clearly detected in region IVC B in the CT image.
We applied our framework to the sinogram in Fig. 4(a) and successfully extracted the abrupt increase within the sinogram as noise, as shown in Fig. 4(b). Then, we subtracted the noise from the sinogram in Fig. 4(a) and obtained the sinogram of the signal components [ Fig. 4(c)]. In this case, we implemented Tikhonov regularization while specifying only the profiles in the y direction at the positions = 0-9 , = 81-96 and = 174-177 . In contrast, the original data in the y direction at the other positions were preserved. The intensity profiles for = 0 in Figs. 4 Fig. 5(a). In the profile of the noise component, the peak was identified at y = 0.45 mm [as indicated by PS B 1 in Fig. 5(a)]. Additionally, we confirmed the peak on the opposite side at approximately y = 1.41 mm (PS B 2), although it was difficult to determine the peak in the original profile. The profile from the signal component is characterized by smooth intensity decays in these regions. However, owing to the smooth intensity decay in the tail areas, the inclination widths in both regions were approximately 60 mm larger than those obtained from the original sinogram. In addition to the rapid increase in peak intensity values, the true signal data in this region also changed significantly; as a consequence, smoothing resulted in a broader intensity decay in the tail. Because of the absence of the removed noise for 0.57 y 1.29 mm, the intensities were the same as the original intensities. As shown in Fig. 5(b), we could also remove the peaks at the edges or y = 0.45 mm and y = 1.32 mm for = 90 [as indicated by PS B 3 and PS B 4 in Fig. 5(b)]. Fig. 6(b) shows the CT image reconstructed from the signalcomponent sinogram in Fig. 4(c). Comparison with the original CT image reconstructed from the original sinogram shows that the artifacts in regions IC B , IIC B and IIIC B are missing from the improved CT image. Fig. 6(c) shows the cross-sectional intensity profiles for x = 0.84 mm in Figs. 6(a) and 6(b) as a function of y [as indicated by the dotted lines C B in Fig. 6(a) and C B in Fig. 6(b)]. In Fig. 6(d), we show the cross-sectional intensity profiles for y = 0.84 mm in Figs. 6(a) and 6(b) as a function of x [as indicated by the dotted lines C B in Figs. 6(a) and C B in Fig. 6(b)]. The removal of artifacts resulted in improved profiles at approximately y = 0.39 mm [as indicated by PC B 1 in Fig. 6(c)] and approximately x = 0.39 mm and x = 1.26 mm [as indicated by PC B 2 and PC B 3 in Fig. 6(d)]. Additionally, the profile at the sample edge position y = 1.35 mm was improved [as indicated by PC B 4 in Fig. 6(c)].

(b) and 4(c) [as indicated by the dotted lines S B in Figs. 4(b) and 4(c)] are plotted in
Figs. 4-6 shows an attempt to remove the noise for a signal-to-noise intensity ratio of about 200%. We examined the upper limit of the signalto-noise ratio of the framework using these parameter values. As a result, we were able to remove noise with an intensity ratio of up to 2000%, as shown in Figs. 7-9. We have shown the results of applying our framework to the sinogram obtained from the scattering intensities in the lower q y region [as indicated by C in Figs. 2(a)-2(d)]. As shown in the 1D profiles, the effect of streak scattering became more evident with decreasing q y . As shown in Fig. 2(e), the differences between the profile at y = 0.93 mm and = 0 (black solid line), and that at y = 0.45 mm and = 0 (red solid line) increased with decreasing q y . Thus, the sinogram obtained from the intensity at q y = 0.170 nm À1 in Fig. 7(a) exhibited more pronounced spots than that at q y = 0.219 nm À1 in Fig. 7(a) [as indicated by S C 1-S C 6 in Fig. 7(a) Fig. 4(a). (b) Improved CT image reconstructed from the sinogram of the signal components in Fig. 4(c). (c) Cross-sectional intensity profiles at x = 0.84 mm along C B in (a) and C B in (b). (d) Cross-sectional intensity profiles at y = 0.84 mm along C B in (a) and C B in (b). profile for = 0 (S C ) is plotted as a function of y in Fig. 8(a). We observed peaks at both edges of the sample at y = 0.45 mm and y = 1.41 mm [as indicated by PS C 1 and PS C 2 in Fig. 8(a)]. The widths of both peaks were estimated to be 120 < y < 180 mm, consistent with the horizontal beam diameter. We then applied Tikhonov regularization to the sinogram to remove the noise under the same angular range conditions () specified in Fig. 4(a). We were able to extract the noise components successfully, as shown in Fig. 7(b), and an improved sinogram was obtained by subtracting the noise component from the original image, as shown in Fig. 7(c). The intensity profiles demonstrate that the noise components were only the peak profiles from the edge areas [as indicated by PS C 1 and PS C 2 in Fig. 8(a) and PS C 3 and PS C 4 in Fig. 8(b)]. On the other hand, the intensity profiles from the signal component in these areas became smoother due to the removal of noise. Fig. 9(a) shows the CT image reconstructed from the original sinogram. Streak scattering induced artifacts not only in the contour areas [as indicated by IC C , IIC C , IIIC C and IVC C in Fig. 9(a)] but also outside the sample. Since the relative spot intensities at the six positions in the sinogram increased, the artifacts in the x and y directions in the original CT image became more pronounced. Furthermore, when the spot intensities in the sinogram increased in the directions, artifacts were also observed for the corresponding     directions. These artifacts overlapped, resulting in a broader width in the x and y directions. The cross-sectional intensity profile at x = 0.84 mm [as indicated by the dotted lines C C in Fig. 9(a) and C C in Fig. 9(b)] is plotted as a function of y in Fig. 9(c), and the cross-sectional intensity profile at y = 0.84 mm is plotted as a function of x in Fig. 9(d) [as indicated by the dotted lines C C in Fig. 9(a) and C C in Fig. 9(b)]. Strong artifacts are visible as broad peaks at approximately y = 0.39 mm and y = 1.35 mm [as indicated by PC C 1 and PC C 4 in Fig. 9(c)] and at approximately x = 0.39 mm and x = 1.26 mm [as indicated by PC C 2 and PC C 3 in Fig. 9(d)]. In both profiles, the peak profiles prevented us from identifying the edges of the sample. Moreover, an oscillation behavior was observed around the peaks [as indicated by RC C 1 and RC C 3 in Fig. 9(c) and RC C 2 and RC C 4 in Fig. 9(d)]. In ordinary CT reconstruction calculations, the sinogram is subject to filtering and then backprojection. Since the filtering process is mathematically identical to differentiation, impact-type noise such as streaks can cause unexpectedly large errors. Furthermore, due to the resolution limit of numerical differentiation, damping waves propagate around the impacts, as seen in regions RC C 1 and RC C 3 in Fig. 9(c) and RC C 2 and RC C 4 in Fig. 9(d). These factors generated false signals in the projection direction, yielding the streak lines in the rectangular dotted boxes in the reconstructed images. Thus, we were not able to evaluate a large area in the reconstructed CT image from the sinogram affected by strong streak scattering. Fig. 9(b) shows the reconstructed CT image from the sinogram of the signal component. As a result of removing the artifacts, we were able to observe the contour areas [as indicated by VC C , VIC C , VIIC C and VIIIC C in Fig. 9(b)]. As shown in Figs. 9(c) and 9(d), the cross-sectional intensity profiles became smooth after applying our framework. The profiles also reveal improved intensities in the background region. Moreover, the intensity values decreased more effectively in the interior regions, which allowed us to obtain information on the spatial distribution of the structures therein [as indicated by RC C 3 and RC C 4 in Figs. 9(c) and 9(d)]. Although only the ranges 0.66 < y < 1.20 mm and 0.54 < x < 1.08 mm inside the sample could be evaluated in the original CT image, we could evaluate the ranges 0.42 < y < 1.35 mm and 0.39 < x < 1.26 mm in the improved CT image. Furthermore, estimating the inclination width of the sample edge at position PC C 1 was difficult in the original CT image because of the large propagation effect of the attenuated wave described above, but in the improved CT image, the width at the same edge could be estimated as 150 < y < 210 mm [ Fig. 9(c)]. This width was approximately 60 mm larger than the value estimated at the same edge of the sample in the CT image in Fig. 3(d). The reason for this increased inclination width was its increase along the edge at = 0 in the sinogram after the removal of noise.
These results show that our framework is applicable even for the removal of high noise intensities. We expect that this framework will also be useful in removing the high-intensity components that partially occurred inside the sample. Finally, we compare the scattering intensity profile obtained from the improved CT image with the original. We also improved the CT images at each position from q y = 0.12 nm À1 to q y = 0.49 nm À1 in addition to the B and C positions. The averaged intensity along the x direction at the edge position y = 0.45 mm in these images is plotted against each q y as shown in Fig. 2(e) (red dashed line). On the lower q y side, this is the upper limit of the signal-to-noise ratio of this framework based on the set parameter values. On the other hand, at the higher q y side, the framework is applied up to the q y region where streaks affect the signal intensities. As a result, we plotted the intensity profile in the limited q y region. In contrast to the case for the original profile with y = 0.45 mm and = 0 , we could identify the peak of the lamellar structure at q y = 0.219 nm À1 , suggesting that the method can remove the effect of streak scattering from the measured scattering function. Our (a) Original CT images reconstructed from the original sinogram in Fig. 7(a). (b) Improved CT images reconstructed from the sinogram of the signal components in Fig. 7(b). (c) Cross-sectional intensity profiles at x = 0.84 mm along C C in (a) and C C in (b). (d) Cross-sectional intensity profiles at y = 0.84 mm along C C in (a) and C C in (b). method can effectively remove noise without losing any information in the sinogram, provided that the dimension of the measurements is less than half of the dimension v, due to the powerful smoothing capability of the Tikhonov regularization. We suggest that this framework could be used in applications other than streaks coming from the sample edge, such as those originating from voids in the interior.

Conclusions
We have developed a framework with Tikhonov regularization to remove the effects of artifacts originating from reflections that occur at the edges or the voids of a sample during SAXS-CT. We applied the framework to the reconstruction of a CT image for the spatial distribution of the lamellar structure of an HDPE sample. The SAXS data used for the reconstruction of the CT image were affected by the streak scattering originating from the reflections at the edges of the sample. We were able to remove the effect of streak scattering on the reconstruction of the CT image by employing the proposed framework and obtained an improved CT image, whereas disturbances were found in the CT image obtained without the framework. This technique is useful for removing spot-like noise not only for SAXS-CT but also for conventional X-ray CT.