 Research Article
 Open access
 Published:
Statistical Permutationbased Artery Mapping (SPAM): a novel approach to evaluate imaging signals in the vessel wall
BMC Medical Imaging volumeÂ 17, ArticleÂ number:Â 36 (2017)
Abstract
Background
Cardiovascular diseases are the leading cause of death worldwide. A prominent cause of cardiovascular events is atherosclerosis, a chronic inflammation of the arterial wall that leads to the formation of so called atherosclerotic plaques. There is a strong clinical need to develop new, noninvasive vascular imaging techniques in order to identify highrisk plaques, which might escape detection using conventional methods based on the assessment of the luminal narrowing. In this context, molecular imaging strategies based on fluorescent tracers and fluorescence reflectance imaging (FRI) seem well suited to assess molecular and cellular activity. However, such an analysis demands a precise and standardized analysis method, which is orientated on reproducible anatomical landmarks, ensuring to compare equivalent regions across different subjects.
Methods
We propose a novel method, Statistical Permutationbased Artery Mapping (SPAM). Our approach is especially useful for the understanding of complex and heterogeneous regional processes during the course of atherosclerosis. Our method involves three steps, which are (I) standardisation with an additional intensity normalization, (II) permutation testing, and (III) clusterenhancement. Although permutation testing and cluster enhancement are already wellestablished in functional magnetic resonance imaging, to the best of our knowledge these strategies have so far not been applied in cardiovascular molecular imaging.
Results
We tested our method using FRI images of murine aortic vessels in order to find recurring patterns in atherosclerotic plaques across multiple subjects. We demonstrate that our pixelwise and clusterenhanced testing approach is feasible and useful to analyse tracer distributions in FRI data sets of aortic vessels.
Conclusions
We expect our method to be a useful tool within the field of molecular imaging of atherosclerotic plaques since clusterenhanced permutation testing is a powerful approach for finding significant differences of tracer distributions in inflamed atherosclerotic vessels.
Background
Cardiovascular diseases are the leading cause of death worldwide [1] and most prominently originate from atherosclerosis, a chronic inflammation of the arterial vessel wall [2]. The complex pathophysiology of atherosclerosis includes the accumulation of lipids, inflammatory cells and fibrous tissue in the arterial wall, leading to its thickening. This results in the formation of so called atherosclerotic plaques, which may be asymptomatic, or, if plaques compromise the vessel lumen, leads to a hypoperfusion (ischemia) of organs downstream of the respective artery. Lifethreatening clinical complications of atherosclerosis mainly occur when the atherosclerotic plaque becomes unstable (vulnerable) and ruptures, which immediately triggers clot formation resulting in the thrombotic occlusion of the affected artery. As a consequence of this event, the blood flow to an organ is suddenly terminated, resulting in organ hypoxia and loss of tissues as occurs in the major clinical scenarios myocardial infarction, stroke and peripheral vascular disease. Numerous inflammatory processes and other mechanisms that contribute to plaque vulnerability have been described [3]. There is a clinical need to develop new, noninvasive vascular imaging techniques in order to identify highrisk plaques, which might escape detection using conventional methods based on the assessment of the luminal narrowing of an artery secondary to a plaque in the arterial wall. Such an early and noninvasive diagnosis could have a major impact on individual treatment decisions as well as efficiency and hence the overall survival of the population at risk.
In this respect, molecular imaging strategies based on fluorescent or radioactive tracers combined with the respective imaging modalities such as fluorescence reflectance imaging (FRI), positron emission tomography (PET), and single photon emission tomography (SPECT) seem well suited to assess molecular and cellular activity. Various approaches of this kind targeting vascular inflammation have been described (reviewed in [4]). However, analysing tracer distribution in the arterial wall of a given vessel or the entire vascular tree in wholebody images remains a huge challenge. This is due to (a) the complex and variable anatomy of arteries across model systems, but also patients, (b) the thin vascular wall (partial volume), and (c) the spillin of signals into the vascular wall from either the blood or tissues/organs surrounding the vessel, and various other factors. To address these issues, a precise and standardized analysis method is required which orientates itself on anatomical landmarks, ensuring to compare equivalent regions across different subjects [5].
Image standardization approaches are a common method for comparing functional images across different subjects, like in functional magnetic resonance imaging (fMRI) or PET data [6, 7]. This is due to the fact that Statistical Parametric Mapping (SPM) image analysis is widely used in neuroimaging research [6, 8]. Since Holmes et al. [9] discovered the advances of permutationbased statistical testing, there have been many achievements in nonparametric based image testing [10, 11]. Generally, permutationbased image testing performs better than parametric approaches [12], which explains the preference for permutation testing in neuroimaging and for electroencephalography (EEG) data. Additionally, such methods can be combined with clusterenhancement of pixels [13, 14]. However, to the best of our best knowledge, so far these strategies have not been applied to cardiovascular molecular imaging. We therefore propose a novel method, Statistical Permutationbased Artery Mapping (SPAM). Our approach is especially useful in understanding the complex and heterogeneous regional processes in the course of atherosclerosis.
We chose 2D fluorescence reflectance imaging (FRI) data sets of tracer distribution in murine aortic vessels as an example for the application of permutation testing in combination with a clusterenhancement approach to standardized images. We demonstrate that our pixelwise and clusterenhanced testing approach is feasible and useful for analysing MMP tracer distributions in FRI data sets of 13 aortic vessels.
Methods
Our novel SPAM method involves three steps, namely standardisation, permutation, and clusterenhancement, for the analysis of atherosclerotic plaque formation and tracer distribution in FRI images of murine aortic vessels. The overall workflow of the proposed method is depicted in Fig. 1. An anatomical overview of the analysed vessel region is presented in Fig. 2. First, we define regions of interest (ROIs) within the vessels for the subsequent analysis. Each region is transformed into a standardized map, i.e. the region of the vessel is unwarped (i.e. straightened) and its length and width rescaled to predefined values. Furthermore, the fluorescence intensity of these maps is normalized to improve comparability between different subjects. To compare two different groups of subjects, we then apply permutation testing in combination with a clusterenhancement method. In the subsequent sections, we will describe each of the steps in detail. All images depict fluorescence intensity maps, which were visualized by application of a false colour palette.
ROI definition
To acquire comparable ROIs across all subjects, we propose a semiautomatic approach. Although there are automated segmentation approaches for vessel structures (such as described in [15] and [16]), we propose a method relying on userdefined boundary points. This allows our method to be applied on a wide variety of different image modalities where multiple sets of parameters or even entirely different automated segmentation approaches would be necessary otherwise.
At first, several boundary points are marked manually along each of the two outer boundaries of the vessel to be analysed. Those points are then used to retrieve the vessel boundaries by performing a natural cubic spline curve interpolation [17]. An example of this process is depicted in Fig. 2 d. Each of the two outer aortic curves is evaluated at multiple positions, which results in a list of points along the curve constituting a piecewise linear approximation of the curve, i.e. a polygonal chain. To obtain a sufficient number of points regarding the resolution of the image, we experimentally chose a step size of 0.1 along the spline. The step size is defined in terms of the spline curve length according to the centripetal scheme proposed by Lee [17] and corresponds to approximately 1.88 steps per pixel or a step size of 18 Î¼m. This results in nearly a thousand points per curve and ensures a complete overlap of the vessel area later on (see results section and Fig. 3 a).
In the next step, we compute orthogonal line segments from one vessel boundary curve to the other which are later used for unwarping the vessel. For each point along a polygonal chain A we compute its nearest neighbour on polygonal chain B and vice versa, resulting in a set of orthogonal line segments for each of the boundary chains. An example showing the resulting orthogonals for both aortic boundary curves is depicted in Fig. 2 a. Combining these two sets of line segments results in instances of crossing orthogonals (see Fig. 2 b). We then aim to find a subset of the line segments in the union of the two sets which best represents the area within the vessel so that in the unwarping process no information is lost, i.e. to prevent holes which might originate when choosing the line segments of the shorter boundary curve (see Fig. 2 a). This is achieved by choosing the line segments resulting from the locally longer curve (i.e., the curve at the outside of a bend) and switch at inflection points of the vessel if necessary. At such points (or straight vessel segments) two points are assigned to each other from both sides, i.e. they are mutually nearest neighbours. Figure 2 b depicts the line segments between those points using the red colour. The result of combining the sets of line segments using the aforementioned approach is a set of orthogonal line segments, which represents the entire area of the vessel (see Fig. 2 b). The line segments are used to generate a medial axis (centre line) of the vessel which is defined by a polygonal chain consisting of the centre point of each line segment, providing length information of the vessel or its anatomical sub parts.
Based on the set of orthogonal line segments, it is possible to choose orthogonals which define the boundaries of anatomical regions of interest. The first and last selected line segments thereby define the closure of the region, providing a mask for the ROI. To improve the comparability of the anatomical landmarks and reduce the difficulty of manually selecting corresponding sections in images of multiple subjects, we limit the selection to the noncrossing orthogonal line segments from the previous step. Figure 2 d shows an example of selected ROI sections using the dotted lines orthogonal to the vessel.
For analysing aortic vessels, the anatomical ROIs are defined as the vessel segments between the major branching points, as these may affect shear stress and are robust to identify across subjects. The major branching points are the aortic artery and the brachiocephalic artery, the left common carotid artery, and finally the left subclavian artery. Thereby homologues regions are formed that are suitable for comparison. Making use of the automatic generated centre line, it would even be possible to split up the sections into inner and outer curvature ROIs, taking into account the different flow patterns.
Unwarping, standardization and normalisation
Using the orthogonal line segments and anatomical section definition outlined above, it is now possible to compute an intensity map along the vessel. This produces an unwarped version of the aortic vessel, which we refer to as map throughout the remainder of this article. To compute the map, we first create a temporary image by recording the image intensities along each of the orthogonal line segments computed in the previous step into a separate row of a new image. To account for the varying distance of the line segments along the vessel, we perform an additional correction step where the image is stretched according to the physical length of the vesselâ€™s medial axis by resampling the rows using bicubic interpolation, resulting in the actual map. An example is depicted in Fig. 2 e.
To compare maps across subjects, each map must be standardized to a uniform length and width. Using the information of anatomical sections, the mapâ€™s sections are stretched to predefined lengths, again using bicubic interpolation. For our example data, we specified 5 sections (A _{1} to A _{5}) which were standardized to the lengths L _{1}=L _{2}=L _{3}=L _{4}=50 pixels and L _{5}=200 pixels to alleviate the problem of underrepresenting certain regions. Otherwise the aortic arch region would be relatively reduced in size due to strong bending. Moreover, each profile is scaled to a predefined width to compensate for lumen narrowing. For the whole map, a uniform width W=40 pixels was chosen. Those parameters can be adjusted by the user according to the specific application. To overcome spatial inaccuracies and signal noise, a Gaussian smoothing operation is applied to the maps. For the initial Gaussian smoothing, the parameter Ïƒ=3 was used. When computing the mean difference maps, for lower values of Ïƒ, noise and artifacts are visible in the images, while larger values lead to overly smoothed, i.e. blurry, images. An exemplary visualization of this parameterâ€™s influence is shown in figure Fig. 3 b.
These standardized maps can be compared to each other, providing high anatomical accuracy. Furthermore, each map is normalized to the subjectâ€™s mean background signal intensity, e.g. the uninflamed left common carotid artery (see Fig. 2 c) to allow a comparison of the intensity maps. An example of the standardized and normalized map is depicted in Fig. 2 f).
Now that comparable maps have been computed, the following section will focus on the methodology of comparing those maps in a reliable way to identify statistically significant differences between groups of subjects.
Permutation testing
A simple form of evaluating maps is to calculate an average map over a group of subjects. To compare two groups, a mean difference map, i.e. the difference image of the two average maps, can be computed. However, this method provides no statistical significance, as this information cannot be derived directly from the difference image. To overcome this problem, groups of standardised maps can be compared by means of pixelwise permutation testing or clusterwise permutation testing. This technique is already wellestablished in quantitative analysis of fMRI, e.g. [9, 10, 12]. The main idea of permutation testing is to build up an H0 distribution by randomly exchanging group labels of the measurements between the two test groups [10]. If the biggest difference between two groups is observed in the original assignment, this difference is likely not due to random variation [9]. Using the H0 distribution, one can check this assumption using a test statistic [18].
Permutation tests share the benefit that only few assumptions have to be met in order to be applicable [10]. However, one key assumption is that subjects are interchangeable between the two subject groups [10]. Unfortunately, there are circumstances when this assumption is not correct, such as in paired comparisons (e.g. comparing two tracers in the same individuals such that there is a pair of images for the same subject, each image in one of the two groups). Therefore, we apply two different permutation approaches, one for unpaired and one for paired comparisons.
Unpaired permutation
For permutation testing of two unpaired groups, the mean difference map is calculated for each of the groups. As mentioned previously, the goal is to eliminate insignificant differences, i.e. arbitrary differences that are also present when randomly exchanging the assignment of subjects to group A and B. This is done by sequentially computing permutations of the group labels which are assigned to the images (see Fig. 4 a) and calculating the mean difference map of the groups resulting from each permutation. For n subjects in total and k<n subjects in one of the groups, we obtain \(\binom {n}{k}\) combinations in total [10]. Unfortunately, for large numbers of subjects, testing of all combinations is not feasible due to the large number of combinations [18]. For instance, even a moderate number of n=30 subjects with a group size of k=15 leads to over 155Â·10^{6} combinations in total. In such cases, it is possible to choose a random subset of permutations, which is sometimes referred to as MonteCarlo permutation testing [10]. In general, selecting 1000 permutations is sufficient to obtain effective approximate permutation tests [10]. In our implementation, we restrict the maximum number of permutations to 5000 for instances where more combinations are possible.
The aforementioned mean difference maps lack the information on signal scatter. A high local difference suggesting a disparity might be misleading due to high signal scatter. Therefore, for each pixel, the standard deviation (SD) of its intensity is calculated over the mean difference maps of all permutations and used to normalize this pixel in each of the difference maps, i.e. the pixelâ€™s intensity is divided by its SD [18]. The resulting maps are referred to as normalized difference maps for the remainder of this section. The maximum pixel value is calculated for each individual normalized difference map to derive a distribution of maximum values over the permutations. Thereby, permutation testing produces its own H0 test distribution. Since the distribution consists of the maximum difference values (regardless of the pixel location containing the maximum at a given permutation) it is taken account of the multiple comparisons problem. Using the acquired maximum difference distribution, the desired percentile (e.g. 5%, see Fig. 4 c) can be used to identify a threshold t which is then used for thresholding the normalized difference map computed using the original labelling of the images, i.e. the actual groups.
As the (normalized) difference maps contain signed values, we perform the same test using the minimum pixel value (i.e. maximum negative pixel value) on the normalized difference maps computed from the permutations, which allows us to identify significantly smaller pixels across groups analogue to its maximum counterpart. Some exemplary results of the whole procedure are included in the results section.
Paired permutation
A slightly different approach is used when group A and B are paired. In this situation, we apply the method proposed by Simpson et al. [19]. Only corresponding group members, i.e. images of the same subject, are exchanged between groups (see Fig. 4 b). If the true assignment of group A and B is significantly different for any pixel, swapping images of one subject results with high likelihood in a less extreme maximum or minimum difference value. The maximal amount of permutations is given by \(2^{\frac {n}{2}}\). After building the test distribution, subsequent calculations are performed analogously to the paired permutation test. It should be noted that a comparison of two tracers is made possible using this method because of the aforementioned normalisation of each image to a predefined background region. Therefore, background normalized tracer images are compared to each other.
Clusterbased enhancement
A limitation of the described permutation test is that it explicitly ignores cooperative effects between pixels. If a given pixel has a high value and its surrounding neighbours also show a comparable signal, it is more likely to be significant than if it is surrounded by pixels with low signal. As pixels should not be regarded as independent observations, it seems more suitable to perform a clusterbased statistic rather than a pixelwise one. A cluster in this regard is a group of adjacent pixels with similar intensities.
The ThresholdFree Cluster Enhancement (TFCE) approach proposed by Smith and Nichols [13] aims at solving the aforementioned problem by enhancing the image through means of adding local support by its neighbourhood to a pixel. Intuitively, the method interprets the twodimensional image as a threedimensional topological surface given by the pixel intensities and enhances local maxima of pixels in local clusters by incorporating the extent of the connected region below them (see Fig. 5 a). The clusterenhanced value of a pixel p in the normalized difference map is computed by evaluating the following equation:
where h _{0} is the lowest intensity in the image, h _{ p } is the original intensity of p in the normalized difference map, e(h) is the extent of the connected region under p at height h, and E as well as H are the additional parameters of the model. It should be noted that only locally connected regions directly under the pixel p at height h contribute to the enhancement so that unconnected local maxima are ignored (see Fig. 5 a). The TFCEenhanced map is thus not only dependent on the original signal intensity, but on the amount of surrounding pixels that show a similar signal intensity. Therefore, TFCE supports pixels bundled to clusters to be more likely significant (see Fig. 5 b). For the parameters E and H, the standard values 0.5 and 2 have been used as defined by Smith and Nichols [13]. It should be noted that the TFCE method retains local maxima of the input image (although transforming their height) and that an isocontour in the original image necessarily corresponds to an isocontour in the TFCEenhanced image, i.e. while TFCE is a nonlinear transformation, it retains important basic features of the data [13]. In our implementation, a finite approach is used by thresholding the mean difference map at 500 levels between the imageâ€™s minimum and maximum. At each step, the size of a cluster containing the considered pixel is determined and multiplied with the current thresholding height h _{ t }.
We apply the clusterenhancement in the permutation tests described above to each of the normalized difference maps, i.e. to the normalized difference map of each individual permutation (as well as the original labelling of the images). The aforementioned maximum and minimum distributions are thus already computed from the TFCEenhanced values.
Animal details and data acquisition
For our exemplary study, 13 ApoE deficient mice (Charles River Laboratories International, Inc., Wilmington, MA, USA) were fed a Western type diet (Altromin GmbH, Lage, Germany; 21% fat, 19.5% casein, 0.25% cholesterol) either for 12 (n = 6) or 17 (n = 7) weeks. At diet end, mice were injected intravenously with 2 nmol of the MMP photoprobe Cy5.5AF443 [20]. Three hours past tracer administration, animals were euthanized (anaesthetized by 2% Isoflurane, 0.5l O_{2}/min), perfused using a sodium chloride solution and dissected for the aortic artery explantation. To acquire the ex vivo fluorescence images, we employed an IVIS Spectrum Imaging System and the Living Image Software 4.0 (Caliper Life Sciences, Hopkinton, MA, USA).
Results
One of the crucial steps of our proposed method is the calculation of a medial axis for unwarping the vessels to ultimatively obtain comparable regions of interest between different subjects. To validate the accuracy of our medial axis, we analyzed its position with respect to the two vessel boundary curves. For each pixel of the detected medial axis, we determined the pixels with the smallest distance on each of the two vessel boundaries. If the difference of those two distances is close to zero, the medial axis pixel is in the middle of the two boundaries, which is the optimal position. We evaluated 13 FRI data sets (see below) and obtained a mean difference of 0.3451 pixels with a standard deviation of 0.8636 pixels. Since both of those values are below one pixel, we can conclude that the medial axis is generally in a good position.
In addition to validating the medial axis in terms of its distance to the boundary curves, we performed an evaluation of the step size parameter for the boundary points of the spline curves with respect to the coverage of the vessel area by the orthogonals. The covered vessel area for different step sizes can be found in Fig. 3 a. The chosen step size of 0.1 leads to a complete coverage of the underlying vessel area and is therefore an optimal choice for unwarping the vessel, as the image information is completely retained. Increasing the step size decreases the covered vessel area considerably so that lower values would result in information loss in the unwarped maps.
To evaluate our method as a whole, we used two groups of ApoE deficient mice (n=13 in total), which were fed with a high cholesterol diet for 12 or 17 weeks. Both the genotype and diet have been shown to promote the development of atherosclerosis [21]. The MMP binding Cy5.5AF443 photoprobe was administered intravenously 3 h before image acquisition [20]. At the end of the diet animals were sacrificed, aortic vessels were dissected and ex vivo FRI images acquired. Aortic arteries were cut at the root proximally and at the diaphragm hiatus distally. Figure 6 a shows the average maps computed from the two groups as well as the mean difference map derived from those average images [22]. Figure 6 b shows the resulting normalized difference map after permutation testing as well as the thresholded difference map where the threshold t has been derived from the maximum and minimum distributions using the significance level Î±=0.05. Figure 6 c shows the same results with the addition of the TFCE. Note that the cluster of pixels significantly differing between group A and group B is difficult to identify in the normalized difference map of the first example, but clearly visible when applying the clusterenhancement.
The greatest difference of Cy5.5AF443 signal between the two diet groups (12 vs. 17 weeks) is located in the middle of the descending aortic artery. There is a significant hotspot of MMP activity adjacent to the inner curvature due to higher intensities of the 17 weekâ€™s average map (p<0.05). Additionally, the 17week group shows more Cy5.5AF443 signal compared to the 12week group in the outer curvature of the aortic arch, but this difference is not significant (p>0.05).
Discussion
In the current study we present a novel method, which we call SPAM, for analysing inflamed atherosclerotic aortic vessels in order to find significant patterns of tracer distribution in FRI images. In this respect, targeting MMPs by tracers seems a promising approach for imaging atherosclerotic plaque [23â€“26]. However, to evaluate the chosen Cy5.5Af443 MMP tracer or any other tracer targeting atherosclerosis for identifying dangerous plaques, it is mandatory to use precise and standardized image analysis methods. Our method enables the definition of vascular ROIs in a highly reproducible and accurate manner using vessel branching points as landmarks. This allows us to compare results across subjects to study the development of atherosclerotic plaque and potential tracer uptake per vascular segment.
Alternatives to ROIbased image quantification have been published, like the combination of whole image sets to form standardized maps [5, 6]. To display and analyse vessel images in such a standardized manner, unwarping is a common procedure [27â€“29]. While we also apply unwarping, we use vascular branching points in our method to transform the image into a standardized map. This overcomes the topographical image variety consisting of positional and morphological contribution [7].
We demonstrated the vessel standardization using 13 FRI images of murine aortic vessels in total. Our strategy of average map generation and display provides a clear overview of the relevant image features. There are several other approaches to mask, refine and display vessel segmentation volumes [30â€“33]. However, these lack the possibility to test maps against each other.
The use of permutation testing provides a strong control over alpha errors in imaging settings [12]. There are other approaches to find significant changes between groups of maps, like Gaussian Random Field. However, these could lead to too liberal results due to violation of the Gaussian Random Field assumptions [11, 12]. Adjusting the Î±value for every pixel using Bonferroni correction, on the other hand, may lead to a too conservative result [34]. Thus, the nonparametric permutation seems to be best suited.
Wholemap testing is especially useful as there is often no regional distribution hypothesis for atherosclerotic plaque. This could lead to excessive ROI definitions with an alpha error accumulation. In contrast, our approach enables the user to find significant patterns of plaque, which would not be visible without it. This is demonstrated by our data, indicating that the 17week group bears more Cy5.5AF443 signal activity in the descending part of the aorta than the 12week group, which sets our approach apart from the general expectation that the aortic arch is a universal predisposed site of atherosclerotic plaque formation [35]. However, further studies are necessary to validate the correlation of FRI signal intensity with atherosclerosis.
The TFCEenhanced map enables the viewer to find the hotspot more easily prior to the thresholding operation. Furthermore, the distal significant cluster is bigger compared to the nonTFCE result. This distal cluster is located at the prolongation of the inner curvature which is a well described predilection side for atherosclerosis [35].
We expect that our method will provide a useful tool for the field of molecular imaging of atherosclerosis. Although vessel sites prone to atherosclerotic plaque formation have been described, very little is known about the underlying biophysical parameters. This results in a lack of a priori knowledge that would be needed to define meaningful ROIs for specific vessel parts. Our standardization and testing method does not need this a priori information and is therefore able to study atherosclerotic vessels in an unbiased manner. Moreover, it helps to gain a deeper understanding of the underlying biophysical parameters and thereby leads to valuable a priori knowledge for future molecular imaging approaches.
The presented method is equally applicable to image information obtained in vivo. However, FRI images are not easily acquired in vivo due to limitations of tissue preparation and light scattering caused by adjacent anatomical structures. Yet we do believe that suitable in vivo data could become available soon, e.g. through highly refined intravital multiphoton microscopy approaches. To fine tune and validate our methodology, ex vivo data seems to be the most robust and appropriate choice.
In future work, we will extend our method to the analysis of threedimensional datasets (e.g. acquired by PET). For doing so, the specification of orthogonal slices through the aortic vessel must be modified to take care of threedimensional spillin artefacts. The remaining parts of SPAM can easily be adjusted to volume analysis [32, 36]. Furthermore, we want to include more automated segmentation methods in the ROI definition step of our workflow for specific image modalities.
Conclusion
We propose a novel method for analysing molecular images with regard to atherosclerosis plaque formation which is based on a semiautomatic standardisation approach in combination with permutation testing and a cluster enhancement method. Although permutation tests are already wellestablished in other areas, to the best of our knowledge such methods have not been applied to molecular image analysis so far. We tested our method using FRI images of murine aortic vessels in order to find recurring patterns of atherosclerotic plaque across multiple subjects. In addition, we have shown that clusterenhanced permutation testing is a powerful approach for finding significant differences of tracer distributions in atherosclerotic inflamed vessels.
Abbreviations
 AA:

Aortic arch
 APO E:

Apolipoprotein E
 BA:

Brachycephalic artery
 CCA:

Common carotid artery
 DA:

Descending aorta
 EEG:

Electroencephalography
 fMRI:

Functional magnetic resonance imaging
 FRI:

Fluorescence reflectance imaging
 MMP:

Matrix metalloproteinase
 PET:

Positron emission tomography
 ROI:

Region of interest
 SA:

Subclavian artery
 SPAM:

Statistical permutation based artery mapping
 SPECT:

Single photon emission computed tomography
 SPM:

Statistical parametric mapping
 TFCE:

Thresholdfree cluster enhancement
References
Go AS, Mozaffarian D, Roger VL, Benjamin EJ, Berry JD, Blaha MJ, Dai S, Ford ES, Fox CS, Franco S, Fullerton HJ, Gillespie C, Hailpern SM, Heit JA, Howard VJ, Huffman MD, Judd SE, Kissela BM, Kittner SJ, Lackland DT, Lichtman JH, Lisabeth LD, Mackey RH, Magid DJ, Marcus GM, Marelli A, Matchar DB, McGuire DK, Mohler ER, Moy CS, Mussolino ME, Neumar RW, Nichol G, Pandey DK, Paynter NP, Reeves MJ, Sorlie PD, Stein J, Towfighi A, Turan TN, Virani SS, Wong ND, Woo D, Turner MB, on behalf of the American Heart Association Statistics Committee and Stroke Statistics Subcommittee. Executive Summary: Heart Disease and Stroke Statisticsâ€“2014 Update: A Report From the American Heart Association. Circulation. 2014; 129(3):399â€“410.
Ross R. Atherosclerosis â€” An Inflammatory Disease. N Engl J Med. 1999; 340(2):115â€“26.
Toutouzas K, Benetos G, Karanasos A, Chatzizisis YS, Giannopoulos AA, Tousoulis D. Vulnerable plaque imaging: updates on new pathobiological mechanisms. Eur Heart J. 2015; 36(45):3147â€“54.
Vrachimis A, Honold L, Faust A, Hermann S, SchÃ¤fers M. New Molecular Probes of Vascular Inflammation. Q J Nucl Med Mol Imaging. 2016; 60(3):194â€“204.
Friston KJ, Ashburner J, Frith CD, Poline JB, Heather JD, Frackowiak RSJ. Spatial registration and normalization of images. Hum Brain Mapp. 1995; 3(3):165â€“89.
Friston KJ, Frith CD, Liddle PF, Frackowiak RS. Comparing functional (PET) images: the assessment of significant change. J Cereb Blood Flow Metab. 1991; 11(4):690â€“9.
Friston KJ, Frith CD, Liddle PF, Frackowiak RSJ. Plastic Transformation of PET Images. J Comput Assist Tomogr. 1991; 15(4):634â€“9.
Worsley KJ, Evans AC, Marrett S, Neelin P. A ThreeDimensional Statistical Analysis for CBF Activation Studies in Human Brain. J Cereb Blood Flow Metab. 1992; 12(6):900â€“18.
Holmes A, Blair RC, Watson JD, Ford I. Nonparametric analysis of statistic images from functional mapping experiments. J Cereb Blood Flow Metab. 1996; 16(1):7â€“22.
Nichols TE, Holmes AP. Nonparametric permutation tests for functional neuroimaging: a primer with examples. Hum Brain Mapp. 2002; 15(1):1â€“25.
Nichols TE. Multiple testing corrections, nonparametric methods, and random field theory. NeuroImage. 2012; 62(2):811â€“5.
Hayasaka S, Nichols TE. Validating cluster size inference: random field and permutation methods. NeuroImage. 2003; 20(4):2343â€“356.
Smith SM, Nichols TE. Thresholdfree cluster enhancement: Addressing problems of smoothing, threshold dependence and localisation in cluster inference. NeuroImage. 2009; 44(1):83â€“98.
Pernet CR, Latinus M, Nichols TE, Rousselet GA. Clusterbased computational methods for mass univariate analyses of eventrelated brain potentials/fields: A simulation study. J Neurosci Methods. 2015; 250:85â€“93.
Cohen LD, Kimmel R. Global minimum for active contour models: A minimal path approach. Int J Comput Vis. 1997; 24(1):57â€“78.
Chen Y, Zhang Y, Yang J, Cao Q, Yang G, Chen J, Shu H, Luo L, Coatrieux J, Feng Q. Curvelike structure extraction using minimal path propagation with backtracking. IEEE Trans Image Process. 2016; 25(2):988â€“1003.
Lee ETY. Choosing nodes in parametric curve interpolation. Comput Aided Des. 1989; 21(6):363â€“70.
Chen C, Witte M, Heemsbergen W, Herk M. Multiple comparisons permutation test for image based data mining in radiotherapy. Radiat Oncol. 2013; 8(1):293â€“11.
Simpson SL, Lyday RG, Hayasaka S, Marsh AP, Laurienti PJ. A permutation testing framework to compare groups of brain networks. Front Comput Neurosci. 2013; 7:171.
Faust A, Waschkau B, Waldeck J, HÃ¶ltke C, Breyholz HJ, Wagner S, Kopka K, Heindel W, SchÃ¤fers M, Bremer C. Synthesis and Evaluation of a Novel Fluorescent Photoprobe for Imaging Matrix Metalloproteinases. Bioconjugate Chem. 2008; 19(5):1001â€“8.
Meir KS, Leitersdorf E. Atherosclerosis in the apolipoproteinEdeficient mouse: a decade of progress,. Arterioscler Thromb Vasc Biol. 2004; 24(6):1006â€“14.
Borland D, Taylor MR. Rainbow color map (still) considered harmful. IEEE Comput Graphics Appl. 2007; 27(2):14â€“17.
Hermann S, Starsichova A, Waschkau B, Kuhlmann M, Wenning C, Schober O, SchÃ¤fers M. NonFDG imaging of atherosclerosis: will imaging of MMPs assess plaque vulnerability?. J Nucl Cardiol. 2012; 19(3):609â€“17.
Sasaki T, Nakamura K, Sasada K, Okada S, Cheng XW, Suzuki T, Murohara T, Sato K, Kuzuya M. Matrix metalloproteinase2 deficiency impairs aortic atherosclerotic calcification in ApoEdeficient mice. Atherosclerosis. 2013; 227(1):43â€“50.
Newby AC. Dual Role of Matrix Metalloproteinases (Matrixins) in Intimal Thickening and Atherosclerotic Plaque Rupture. Physiol Rev. 2005; 85(1):1â€“31.
Galis ZS, Khatri JJ. Matrix metalloproteinases in vascular remodeling and atherogenesis: the good, the bad, and the ugly. Circ Res. 2002; 90(3):251â€“262.
Zhu L, Haker S, Tannenbaum A. Flattening maps for the visualization of multibranched vessels. IEEE Trans Med Imaging. 2005; 24(2):191â€“8.
Kanitsar A, Wegenkittl R, Fleischmann D, Groller ME. Advanced Curved Planar Reformation: Flattening of Vascular Structures. In: Proceedings of the 14th IEEE Visualization 2003 (VISâ€™03). Washington, DC: IEEE Computer Society: 2003. p. 7. doi:10.1109/VISUAL.2003.1250353. http://dx.doi.org/10.1109/VISUAL.2003.1250353
Ropinski T, Hermann S, Reich R, SchÃ¤fers M, Hinrichs K. Multimodal vessel visualization of mouse aorta PET/CT scans. IEEE Trans Vis Comput Graph. 2009; 15(6):1515â€“22.
Schumann C, Oeltze S, Bade R, Preim B, Peitgen HO. Modelfree Surface Visualization of Vascular Trees. In: Proceedings of the 9th Joint Eurographics/IEEE VGTC Conference on Visualization. AirelaVille, Switzerland: Eurographics Association: 2007. p. 283â€“290. doi:10.2312/VisSym/EuroVis07/283290. http://dx.doi.org/10.2312/VisSym/EuroVis07/283290
Straka M, Cervenansky M, La Cruz A, Kochl A, Sramek M, Groller E, Fleischmann D. The VesselGlyph: Focus & Context Visualization in CTAngiography. In: Proceedings of the Conference on Visualization â€™04. Washington, DC: IEEE Computer Society: 2004. p. 385â€“392. doi:10.1109/VISUAL.2004.104. http://dx.doi.org/10.1109/VISUAL.2004.104
Diepenbrock S, Hermann S, SchÃ¤fers M, Kuhlmann M, Hinrichs K. Comparative Visualization of Tracer Uptake in In Vivo Small Animal PET/CT Imaging of the Carotid Arteries. Comput Graph Forum. 2013; 32(3pt2):241â€“50.
Joshi A, Qian X, Dione D, Bulsara K. Effective visualization of complex vascular structures using a nonparametric vessel detection method. IEEE Trans Vis Comput Graph. 2008; 14(6):1603â€“10.
Friston KJ, Holmes A, Poline JB, Price CJ, Frith CD. Detecting activations in PET and fMRI: levels of inference and power. NeuroImage. 1996; 4(3 Pt 1):223â€“235.
VanderLaan PA, Reardon CA, Getz GS. Site specificity of atherosclerosis: siteselective responses to atherosclerotic modulators. Arterioscl Thromb Vasc Biol. 2004; 24(1):12â€“22.
Soret M, Bacharach SL, Buvat I. Partialvolume effect in PET tumor imaging. J Nuclear Med. 2007; 48(6):932â€“45.
Acknowledgements
The authors would like to thank Stefanie Bouma and Sarah Eligehausen for their excellent support.
Funding
This work was partially supported by the Deutsche Forschungsgemeinschaft, CRC 656 "Molecular Cardiovascular Imaging", WestfÃ¤lische WilhelmsUniversitÃ¤t MÃ¼nster, MÃ¼nster, Germany, projects C06 and C10. Publication fees were covered by the Open Access Publication Fund of the University of MÃ¼nster.
Availability of data and materials
If there are any questions concerning the source code or the raw data, please do not hesitate to contact Robert Seifert (robert.seifert@unimuenster.de).
Authorsâ€™ contributions
RS collected mouse data, implemented the method using Matlab, conducted the exemplary study, and drafted the manuscript. RS and AS revisited the code. RS, AS, FK, SH, XJ and MS designed and organized this report, and participated in writing the manuscript. All authors read and approved the final manuscript.
Competing interests
The authors declare that they have no competing interests.
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Not applicable.
Ethics approval and consent to participate
All murine experiments were approved by the State Review Board of NordrheinWestfalen (Germany) in accordance with the German law for animal welfare.
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Seifert, R., Scherzinger, A., Kiefer, F. et al. Statistical Permutationbased Artery Mapping (SPAM): a novel approach to evaluate imaging signals in the vessel wall. BMC Med Imaging 17, 36 (2017). https://doi.org/10.1186/s1288001702077
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DOI: https://doi.org/10.1186/s1288001702077