- Research article
- Open Access
Probabilistic independent component analysis of dynamic susceptibility contrast perfusion MRI in metastatic brain tumors
Cancer Imagingvolume 19, Article number: 14 (2019)
To identify clinically relevant magnetic resonance imaging (MRI) features of different types of metastatic brain lesions, including standard anatomical, diffusion weighted imaging (DWI) and dynamic susceptibility contrast (DSC) perfusion MRI.
MRI imaging was retrospectively assessed on one hundred and fourteen (N = 114) brain metastases including breast (n = 27), non-small cell lung cancer (NSCLC, n = 43) and ‘other’ primary tumors (n = 44). Based on 114 patient’s MRI scans, a total of 346 individual contrast enhancing tumors were manually segmented. In addition to tumor volume, apparent diffusion coefficients (ADC) and relative cerebral blood volume (rCBV) measurements, an independent component analysis (ICA) was performed with raw DSC data in order to assess arterio-venous components and the volume of overlap (AVOL) relative to tumor volume, as well as time to peak (TTP) of T2* signal from each component.
Results suggests non-breast or non-NSCLC (‘other’) tumors had higher volume compare to breast and NSCLC patients (p = 0.0056 and p = 0.0003, respectively). No differences in median ADC or rCBV were observed across tumor types; however, breast and NSCLC tumors had a significantly higher “arterial” proportion of the tumor volume as indicated by ICA (p = 0.0062 and p = 0.0018, respectively), while a higher “venous” proportion were prominent in breast tumors compared with NSCLC (p = 0.0027) and ‘other’ lesions (p = 0.0011). The AVOL component was positively related to rCBV in all groups, but no correlation was found for arterial and venous components with respect to rCBV values. Median time to peak of arterial and venous components were 8.4 s and 12.6 s, respectively (p < 0.0001). No difference was found in arterial or venous TTP across groups.
Advanced ICA-derived component analysis demonstrates perfusion differences between metastatic brain tumor types that were not observable with classical ADC and rCBV measurements. These results highlight the complex relationship between brain tumor vasculature characteristics and the site of primary tumor diagnosis.
Brain metastases are the most common type of intracranial neoplasm [1, 2]. The majority of brain metastases originate from primary cancers in the lung (40–50%), breast (15–25%) or melanoma (5–20%) [3, 4]. The brain metastatic cascade is schematized by tumor cell dissociation from the host organ, intravasation into the vasculature, migration along the vessels and adhesion to the capillary bed, and lastly extravasation into the brain tissue through blood brain barrier (BBB) . Recent studies speculate that tumor can grow at a clinically detectable stage with vessel co-option , a non-angiogenic mechanism . Such processes have been reported in non-small cell lung tumors (NSCLC)  and melanoma . Interestingly, Valiente et al., recently demonstrated that metastatic tumors can survive and grow while adhering to capillaries , causing resistance to anti-angiogenic treatments . Evidence also suggests significant differences in vascular density between breast and melanoma brain metastases that may be influenced by genetic factors, including the expression of CD105, a transforming growth factor (TGF)-beta receptor endoglin .
In clinical practice, patients were often screened with brain lesion and some potential unknown primary tumor located in the body. A robust and highly specific diagnosis is very important, however, conventional imaging approaches encounter limited specificity to differentiate and predict primary lesions. MRI has been long time used to assess tumor localization and burden. Moreover, specific functional features could be extracted by using DWI and DSC-MRI . The DWI derived measurement of ADC has been shown to correlate with tissue cellularity in brain lesions  as well as in metastatic brain lesions . From DSC-MRI, rCBV can be estimated and used as a marker for hypervascularization, as studies have suggested rCBV may reflect vascular morphometry . Additionally, arterial, venous and overlap (AVOL) components present within tumor volume could be extracted from ICA, based on DSC signal . As another surrogate assessment of vascularization reflecting differences in the dispersion or tortuosity of the vessels, TTP may be extracted from normalized R2* signal for both arterial and venous ICA components.
In this study, we investigated the potential differences in tumor burden, water diffusivity and perfusion features and that between different subtypes of secondary brain lesions. We additionally hypothesized possible differences between metastatic lesions, especially in the proportion of each vascular component (arterial, venous or overlap), present within contrast enhancing region.
Inclusion criteria were based on the known primary tumor location; specific secondary organ (brain parenchyma) and available brain MRI study including anatomical, diffusion- and perfusion-weighted images acquired prior to radiation treatment. After the discovery and histopathological diagnosis of primary neoplasm (breast, lung, etc), a whole body FDG-PET/CT was performed as part of active clinical surveillance to identify the presence of metastatic disease. If a metabolically active region was detected within the brain, it was assumed to be due to the primary tumor type, and a subsequent high-resolution brain MRI was performed. From August 2014 to December 2016, 114 patients (71 female and 43 male) were selected for the current retrospective study, including various primary tumors: breast (n = 27, female = 100%) lung adenocarcinoma (non-small cell lung cancer (NSCLC), n = 43, female = 51%) and ‘other’ (n = 44, female = 50%). The ‘other’ group, or non-breast and non-NSCLC tumors, consisted of different primary tumors (hepatocellular carcinoma, renal cell carcinoma, clear cell carcinoma-kidney, etc). More details of patient’s primary tumor location are reported for the former group (Additional file 1: Table S1). The median age of patents at time of imaging was breast = 56 years, NSCLC = 65 years and ‘other’ = 62.5 years.
All images were acquired on either 1.5 T or 3 T scanners. T1-weighted images were acquired before and after contrast agent injection (gadopentetate-dimeglumine, Gd-DTPA, Magnevist) with repetition time (TR)/echo time (TE) ranging from 400 to 2100 ms/1.18–1.53 ms; slice thickness = 1–1.5 mm; number of slice = 118–192. DWI were acquired before injection of contrast with TR/TE = 4–13 s/65–124 ms; flip angle = 90 degree; slice thickness = 2-5 mm; matrix size = 128 × 128 and number of slices ranged 24–86. DSC perfusion MR images were acquired during contrast agent bolus with TR/TE = 1.1–2.4 s/17–45 ms; slice thickness = 4-5 mm; inter-slice gap = 4–6.5 mm; matrix size = 128 × 128; flip angle = 350, 600 or 900; number of repetitions = 50–120 times for a total number of slices = 6–48. Gd-DTPA was power-injected through a venous catheter at standardized pre-load of 0.025 mmol/kg followed by a bolus dose of 0.075 mmol/kg.
Contrast-enhanced digital T1 subtraction maps (delta T1 maps) were performed as previously described . First, pre- and post-contrast T1-weighted images were registered and intensity normalized (NIMH MEG Core, Bethesda, MD; kurage.nimh.nih.gov/meglab/Med/3dNormalize) followed by voxel-by-voxel subtraction, resulting in ∆T1 maps highlighting areas of active tumor burden. ADC maps (expressed in μm2/ms) were computed offline using a mono-exponential model  using clinically available b values (either 0 and 1000s/mm2 or 0, 500 and 1000s/mm2).
Two types of analyses were performed with DSC perfusion data: 1) traditional estimation of rCBV and 2) estimation of vascular volume fraction of arterial and venous vasculature identified through ICA, using the MELODIC toolbox (FMRIB library).
For traditional perfusion measures, dynamic time series data were first motion corrected (MCFLIRT, FMRIB library). Next, rCBV maps were calculated using a bi-directional contrast agent leakage correction algorithm to model contrast flux into and out of the vasculature [20, 21]. Lastly, normalized rCBV (expressed in a.u.) was computed by dividing the rCBV map by the average rCBV value in within a 5 mm sphere in contralateral, normal appearing white matter (NAWM).
In order to estimate the volume fraction of “arterial” and “venous” vasculature within the tumor, independent component analyses (ICA) was applied to the dynamic time series data following motion correction . Next, intensity normalization was performed over time frames and a single-session ICA model with 4 components was opted; arterial, venous  and structured noise for last two components (motion-related, physiological artifacts, sawtooth pattern, etc)  with a statistical threshold of p < 0.5 to preserve voxels with temporal patterns significantly different from noise. Results were visually inspected and arterial and venous components were selected according to presence of Circle of Willis (arterial) and major draining sinuses (venous). In questionable datasets the temporal arrival of the contrast bolus was considered, with components having the fastest arrival categorized as “arterial” and those with slower, delayed bolus arrival categorized as “venous”. A single investigator with ~ 5 years of experience initially categorized the components, which was confirmed by a second investigator with > 10 years of experience.
Z-score normalized maps were binarized (only positive voxels) to create an overlap mask that combine both arterial and venous mixed (AVOL map) regions (Fig. 1), similar to those described by LaViolette et al. . Since ICA is highly dependent of bolus temporal evolution, we hypothesized existence of potential differences in TTP between arterial or venous components across the different tumor types. TTP has been calculated from the start of the inflection point of T2* signal. As we extracted TTP from normalized T2* after ICA processing, values are reported for each patient and not individual lesions.
Image registration was performed using FMRIB Software Library (FSL) linear image registration toolbox (FLIRT, http://www.fmrib.ox.ac.uk/fsl/; FSL Version 5.3). Perfusion and diffusion images were registered to high-resolution T1-weighted post-contrast image using a 12-degree of freedom transformation with a mutual-information cost function and a tri-linear interpolation.
Regions of interest
Contrast-enhancing tumors (CET) from ∆T1 maps were segmented using a semi-automatic procedure as previously described  with Analysis of Functional NeuroImages (AFNI) software (NIMH Scientific and Statistical Computing Core; Bethesda, MD, USA). Briefly, a large ROI was drawn over contrast-enhancing regions on the ∆T1 maps in each contiguous slice, covering the entire lesion (including any macroscopic necrosis). Then, an intensity threshold was manually chosen to segment the CET (without necrosis). Each lesion was then labeled and volumes reported in microliters (μl) for each subsequent lesion.
Median with interquartile range was reported for each lesion including tumor volume, ADC, rCBV, arterial, venous and overlap components. The normality of each distribution was evaluated using Shapiro-Wilk test. Pairwise tests of Wilcoxon-Mann-Whitney method were used to assess differences between groups for estimated variables. A p < 0.05 was considered to indicate a statistically significant result. Linear regression between rCBV maps and ICA-derived components were performed. Receiver-operating characteristic (ROC) analyses was performed to test the accuracy of differentiation between tumor types. The accuracy was estimates with area under the curve (AUC) as well as optimal cut-off value. We reported as well specificity and sensitivity of each parameter. All the statistics were performed using JMP Pro13 (SAS®).
A total of 346 lesions were examined with a median frequency of 2 lesions per patient. We analyzed 72 individual lesions from breast metastases (group range 1–3/subject), 159 from NSCLC (group range 1–4/subject) and 115 from ‘other’ group (group range 1–3/subject). Figure 2 shows anatomical (T1w pre- and post-contrast images, T2w-FLAIR and ∆T1 maps), diffusion (ADC) and perfusion-derived (rCBV and AVOL) images for representative patients of each group (Breast (Fig. 2a), NSCLC (Fig. 2b) and ‘other’ (Fig. 2c), respectively). All the patients clearly demonstrated blood brain barrier (BBB) disruption and contrast enhancement in all lesions. Qualitative analyses based on visual inspection revealed surrounding edema seen on T2w-FLAIR images, present on both patients in Fig. 2a and c and appeared in 83.9% of all lesions examined (respectively 85.1% for Breast, 86.0% for NSCLC and 80.9% for ‘other’ group). The ADC maps show higher values within tumor area (CET, red overlay), along with increased rCBV compared to NAWM (Fig. 2a, b and d). Within the CET regions, a variety of volume fractions of arterio-venous components were identified from ICA. Within areas of vasogenic edema characterized by T2 hyperintensity, we observed characteristic increased ADC and hypovascularity (low rCBV), particularly when compared to CET regions. The areas of T2 hyperintensity surrounding regions of contrast enhancement did not show any detectable arterio-venous components from ICA analysis (no AVOL observed).
Quantification of tumor volume, ADC and rCBV metrics within enhancing lesions
Quantitatively, CET volumes in the non-breast, non-NSCLC ‘other’ group (median volume = 627.5 μl) were significantly larger than NSCLC (Fig. 3a; median volume = 236.0 μl, p = 0.0056) and primary breast cancer (median volume = 300.0 μl, p = 0.0003). No significant difference in median CET ADC or median CET rCBV was observed between groups (Fig. 3b and C, respectively). Statistical reports are available under each corresponding graph and numerical values (median and interquartile range) are reported per group and measurement (Table 1).
Differences of AVOL components within enhancing lesions
The proportion of the CET with a statistically significant “arterial” ICA component (red, Fig. 4) was significantly larger in breast metastases (median = 27.33%) and NSCLC metastases (median = 32.57%) compared with the non-breast, non-NSCLC ‘other’ group (median = 15.12%, p = 0.0062 and p = 0.0018, respectively). The proportion of the tumor with a significant “venous” component (blue) for breast brain metastases (median = 54.39%) was significantly larger when compared with NSCLC (median = 24.18%, p = 0.0027) and ‘other’ brain metastases (median = 24.11%, p = 0.0011). No difference was observed between groups for mixed proportion of vascular components (orange). While the breast and NSCLC brain metastases did not differ significantly in terms of the volume fraction of arterial, venous and overlap ICA components, the ‘other’ group contained a significant proportion of tumor with “overlap” components (mixture of arterial and venous components) (median = 48.66%) compared to purely arterial (p < 0.0001) or venous (p = 0.0141) components. Numerical values (median and range) are reported for each ICA component and group (Table 1).
Temporal patterns of DSC-MRI (time to peak) in metastatic brain lesions
Results suggested no difference in TTP within arterial component, with a TTP = 7.74 s for breast (range: 7.21–9.85 s), 8.72 s for NSCLC (range: 7.60–10.50s) and 8.95 s for ‘other’ tumors (range: 6.60–11.71 s). Similarly, no differences in TTP were observed within the venous component across groups, with TTP = 12.60s for breast (range: 11.40–14.01 s), 12.67 s for NSCLC (range: 11.38–14.70s) and 12.65 s for ‘other’ group (range: 10.89–15.23 s).
Prediction of lesion type with ROC curve analysis
We next determined by ROC analyses whether tumor types could be differentiated from each other (Table 2). Between breast and ‘other’ group, the highest accuracy was reached with venous component (AUC = 0.698, cut-off value > 68.69%). The venous component has shown the best discrimination between breast and NSCLC (AUC = 0.687, cut-off value > 46.46%). Between NSCLC and ‘other’, arterial component has shown the highest accuracy (AUC = 0.658, cut-off value < 29.26%). Similarly, arterial component was the most robust parameter to differentiate breast and NSCLC (pooled) vs. ‘other’ (AUC = 0.666, cut-off value > 20.20%).
Correlation between DSC-MRI metrics; rCBV and AVOL maps
Lastly, we explored whether there was an inherent relationship between rCBV and ICA-derived measurements within CET. The percentage of overlap and its relationship with rCBV revealed highest linear correlation for breast: rCBV = 0.019*Arterial+ 1.551 (r = 0.68, p = 0.0002), NSCLC: rCBV = 0.013*Arterial+ 2.710 (r = 0.70, p < 0.0001) and ‘other’ group: rCBV = 0.021*Arterial+ 1.945 (r = 0.58, p < 0.0001) (Fig. 5b). No significant linear correlation was observed when comparing rCBV to arterial (Fig. 5a) or venous components (Fig. 5c). Together, this suggests measures of CET proportions exhibiting pure arterial and venous components with ICA are unique compared with traditional rCBV measures, whereas rCBV is most closely related to regions of the tumor exhibiting a mixture of arterial and venous components.
Although conventional MRI is often used for diagnosis and response assessment of metastatic brain tumors, MRI has traditionally been nonspecific and unable to reliably differentiate different subtypes of secondary metastatic brain lesions. While the identification of specific types of brain metastases via MRI are of limited clinical value given the primary cancer has likely already been diagnosed at the time of brain metastases identification, the specific vascular characteristics in brain metastases unique to particular primary tumor types may be of important biological significance. For example, our study suggests the proportion of CET with “venous-like” perfusion hemodynamics is higher in breast cancer compared with other tumor types, while the proportion of CET with “arterial-like” perfusion hemodynamics are substantially lower in non-breast, non-NSCLC ‘other’ tumor types. Although speculative, these differences may be explained partially by eloquent preclinical studies demonstrating differential metastatic tumor types preferring either vascular cooption or angiogenesis . Specifically, breast and melanoma brain metastases have been shown to exhibit mostly vascular cooption for further continuous tumor growth [25, 26], while lung carcinoma is thought to initiate neovascularization through pro-angiogenic factors . Thus, perfusion signatures that are unique to specific types of primary lesions may reflect different aspects of the tumor microenvironment or biological behavior that could be further explored or therapeutically exploited.
Results from the current study also suggest CET size of individual brain metastases from breast and NSCLC are significantly smaller than those from non-breast, non-NSCLC ‘other’ tumors. This volumes difference may also be explained by the asymptomatic screening of secondary metastatic brain lesions, detected at various stages of tumorogenesis. It is also important to note that we segmented and considered each lesion as single entity, whereas other studies analyzing the product or totality of enhancing lesions on a per patient basis. Thus, our results appear to underestimate tumor volumes reported in the literature (e.g. NSCLC) .
Previous investigations using diffusion and perfusion have primarily focused on glioma grading and differences between metastatic lesions versus primary brain lesions  and very few attempted to study brain metastases from differing primary tumor types [29,30,31]. We found no differences in ADC values between brain metastases from differing primary tumor types. These results were consistent with other studies, where ADC values in the current study did not differ from those previously reported in NSCLC and melanoma  and between lung and breast cancers . Another study has found lower ADC values only in central nervous system lymphomas compared to lung, breast, melanoma, sarcoma, etc. . However no significant differences were found between other tumor types, which suggest that DWI derived ADC maps, are not robust to differentiate metastatic brain lesions. In our clinic, standard perfusion measurements, including normalized rCBV, were not different between metastatic brain tumors from different primary tumor types. Our measurements of rCBV were consistent with previous reports, showing elevated rCBV (> 1.5) within solid part of the tumor in brain metastases . In accord with our study, only moderate differences in rCBV have been reported among secondary brain lesions (e.g. lymphoma, breast and lung cancer metastasized to the brain) [35, 36]. In addition, Huang et al. , reported similar median values of normalized rCBV for the NSCLC metastases, while in breast metastases, they found more elevated rCBV values. However, the former study collects only sub-regional active tumor parts, combining 3-5 mm ROI’s and no leakage correction was performed on DSC signal, which is controversial and may have resulted in erroneous results compared with our approach.
Our findings of ICA are similar to untreated glioblastoma patients for arterial and AVOL components, but the venous component averaged ~ 29% in our study, which was lower than the 38% reported by LaViolette et al. . We also confirmed that ICA-derived regions of overlap were volumetrically bigger (~ 40%) than arterial and venous tumor proportions.
During this current retrospectively study, we were not able to control or homogenize the acquisition parameters, especially slice thickness, between T1-, diffusion-, and perfusion-weighted images. Since we were not able to perfectly control the acquisition parameters, it is conceivable that differences in the timing between contrast administration and acquisition of post-contrast T1-weighted images resulted in under or overestimation of CET tumor size. Additionally, scans were performed at differing magnetic field strengths, which poses another potential limitation. However, subsequent examination indicated that only venous components were found to be significantly smaller at 3 T as compared to 1.5 T scans (18% vs. 33%, p < 0.005, Additional file 2: Figure S1 and Additional file 3: Figure S2), which could have potentially influenced our results. (As indicated in Additional file 3: Figure S2, if 3 T data was excluded we observed a stronger difference between venous components across tumor types). Additionally, compared with the large number of patients with brain metastases diagnosed each year, the size of the current study is relatively small and therefore results should be interpreted with caution until it can be verified in a larger, more comprehensive study.
In conclusion, the current study demonstrated significant differences in vascular characteristics in brain metastases arising from specific types of primary lesions; however, we did not detect differences in conventional diffusion or perfusion characteristics between breast, NSCLC, and ‘other’ primary tumor types. A significant correlation between rCBV and ICA overlap component (volume fraction) was observed, suggesting potential sensitivity of transiting flow and ‘capillary’ fraction, and that, for all tumor types. The present results highlight the biological importance to identify abnormal vascularization (arterial, venous and overlap) in metastatic brain lesions, especially with advanced ICA post-processing approach. Finally, it is important to note that the current investigation was preliminary and genetic subgrouping and immunohistological analyses would have to be the subject of future explorations in addition to multiparametric MRI.
T1-weighted digital subtraction map
Apparent diffusion coefficient
Area under curve
Blood brain barrier
Dynamic susceptibility contrast
Diffusion weighted imaging
Independent component analysis
Magnetic resonance imaging
Normal appearing white matter
Non-small-cell lung cancer
Relative cerebral blood volume
Receiver operating characteristic
Repetition time/time to echo
Time to peak
Gavrilovic IT, Posner JB. Brain metastases: epidemiology and pathophysiology. J Neuro-Oncol. 2005;75:5–14 https://doi.org/10.1007/s11060-004-8093-6.
Maher EA, Mietz J, Arteaga CL, DePinho RA, Mohla S. Brain metastasis: opportunities in basic and translational research. Cancer Res. 2009;69:6015–20 https://doi.org/10.1158/0008-5472.CAN-08-4347.
Nayak L, Lee EQ, Wen PY. Epidemiology of brain metastases. Curr Oncol Rep. 2012;14:48–54 https://doi.org/10.1007/s11912-011-0203-y.
Barnholtz-Sloan JS, Sloan AE, Davis FG, Vigneau FD, Lai P, Sawaya RE. Incidence proportions of brain metastases in patients diagnosed (1973 to 2001) in the metropolitan Detroit cancer surveillance system. J Clin Oncol. 2004;22:2865–72 https://doi.org/10.1200/JCO.2004.12.149.
Eichler AF, Chung E, Kodack DP, Loeffler JS, Fukumura D, Jain RK. The biology of brain metastases-translation to new therapies. Nat Rev Clin Oncol. 2011;8:344–56 https://doi.org/10.1038/nrclinonc.2011.58.
Donnem T, Hu J, Ferguson M, Adighibe O, Snell C, Harris AL, et al. Vessel co-option in primary human tumors and metastases: an obstacle to effective anti-angiogenic treatment? Cancer Med. 2013;2:427–36 https://doi.org/10.1002/cam4.105.
Frentzas S, Simoneau E, Bridgeman VL, Vermeulen PB, Foo S, Kostaras E, et al. Vessel co-option mediates resistance to anti-angiogenic therapy in liver metastases. Nat Med. 2016;22:1294–302 https://doi.org/10.1038/nm.4197.
Pezzella F, Pastorino U, Tagliabue E, Andreola S, Sozzi G, Gasparini G, et al. Non-small-cell lung carcinoma tumor growth without morphological evidence of neo-angiogenesis. Am J Pathol. 1997;151:1417–23.
Leenders WPJ, Küsters B, de Waal RMW. Vessel co-option: how tumors obtain blood supply in the absence of sprouting angiogenesis. Endothelium. 2002;9:83–7.
Valiente M, Obenauf AC, Jin X, Chen Q, Zhang XH-F, Lee DJ, et al. Serpins promote cancer cell survival and vascular co-option in brain metastasis. Cell. 2014;156:1002–16 https://doi.org/10.1016/j.cell.2014.01.040.
Carmeliet P, Jain RK. Molecular mechanisms and clinical applications of angiogenesis. Nature. 2011;473:298–307 https://doi.org/10.1038/nature10144.
Salgado KB, Toscani NV, Silva LLM, Hilbig A, Barbosa-Coutinho LM. Immunoexpression of endoglin in brain metastasis secondary to malignant melanoma: evaluation of angiogenesis and comparison with brain metastasis secondary to breast and lung carcinomas. Clin Exp Metastasis. 2007;24:403–10 https://doi.org/10.1007/s10585-007-9077-7.
Chakhoyan A, Woodworth DC, Harris RJ, Lai A, Nghiemphu PL, Liau LM, et al. Mono-exponential, diffusion kurtosis and stretched exponential diffusion MR imaging response to chemoradiation in newly diagnosed glioblastoma. J Neuro-Oncol. 2018;139:651–9 https://doi.org/10.1007/s11060-018-2910-9.
Chen L, Liu M, Bao J, Xia Y, Zhang J, Zhang L, et al. The correlation between apparent diffusion coefficient and tumor cellularity in patients: A meta-analysis. PLoS One. 2013;8(11):e79008 https://doi.org/10.1371/journal.pone.0079008.
Hayashida Y, Hirai T, Morishita S, Kitajima M, Murakami R, Korogi Y, et al. Diffusion-weighted imaging of metastatic brain tumors: comparison with histologic type and tumor cellularity. Am J Neuroradiol. 2006;27:1419–25.
Aronen HJ, Pardo FS, Kennedy DN, Belliveau JW, Packard SD, Hsu DW, et al. High microvascular blood volume is associated with high glucose uptake and tumor angiogenesis in human gliomas. Clin Cancer Res. 2000;6:2189–200.
LaViolette PS, Cohen AD, Prah MA, Rand SD, Connelly J, Malkin MG, et al. Vascular change measured with independent component analysis of dynamic susceptibility contrast MRI predicts bevacizumab response in high-grade glioma. Neuro-Oncology. 2013;15:442–50 https://doi.org/10.1093/neuonc/nos323.
Ellingson BM, Kim HJ, Woodworth DC, Pope WB, Cloughesy JN, Harris RJ, et al. Recurrent glioblastoma treated with bevacizumab: contrast-enhanced T1-weighted subtraction maps improve tumor delineation and aid prediction of survival in a multicenter clinical trial. Radiology. 2014;271:200–10 https://doi.org/10.1148/radiol.13131305.
Le Bihan D, Breton E, Lallemand D, Grenier P, Cabanis E, Laval-Jeantet M. MR imaging of intravoxel incoherent motions: application to diffusion and perfusion in neurologic disorders. Radiology. 1986;161:401–7 https://doi.org/10.1148/radiology.161.2.3763909.
Leu K, Boxerman JL, Ellingson BM. Effects of MRI protocol parameters, preload injection dose, fractionation strategies, and leakage correction algorithms on the fidelity of dynamic-susceptibility contrast MRI estimates of relative cerebral blood volume in gliomas. Am J Neuroradiol 2016; https://doi.org/10.3174/ajnr. A5027.
Leu K, Boxerman JL, Lai A, Nghiemphu PL, Pope WB, Cloughesy TF, et al. Bidirectional contrast agent leakage correction of dynamic susceptibility contrast (DSC)-MRI improves cerebral blood volume estimation and survival prediction in recurrent glioblastoma treated with bevacizumab. J Magn Reson Imaging. 2016;44:1229–37 https://doi.org/10.1002/jmri.25227.
Kao YH, Guo WY, Wu YT, Liu KC, Chai WY, Lin CY, et al. Hemodynamic segmentation of MR brain perfusion images using independent component analysis, thresholding, and Bayesian estimation. Magn Reson Med. 2003;49:885–94 https://doi.org/10.1002/mrm.10440.
Kelly RE, Alexopoulos GS, Wang Z, Gunning FM, Murphy CF, Morimoto SS, et al. Visual inspection of independent components: defining a procedure for artifact removal from fMRI data. J Neurosci Methods. 2010;189:233–45 https://doi.org/10.1016/j.jneumeth.2010.03.028.
Harris RJ, Yao J, Chakhoyan A, Raymond C, Leu K, Liau LM, et al. Simultaneous pH-sensitive and oxygen-sensitive MRI of human gliomas at 3 T using multi-echo amine proton chemical exchange saturation transfer spin-and-gradient echo echo-planar imaging (CEST-SAGE-EPI). Magn Reson Med. 2018;3:1–17 https://doi.org/10.1002/mrm.27204.
Lorger M, Felding-Habermann B. Capturing changes in the brain microenvironment during initial steps of breast cancer brain metastasis. Am J Pathol. 2010;176:2958–71 https://doi.org/10.2353/AJPATH.2010.090838.
Kienast Y, von Baumgarten L, Fuhrmann M, Klinkert WEF, Goldbrunner R, Herms J, et al. Real-time imaging reveals the single steps of brain metastasis formation. Nat Med. 2010;16:116–22 https://doi.org/10.1038/nm.2072.
Yoo H, Nam BH, Yang HS, Shin SH, Lee JS, Lee SH. Growth rates of metastatic brain tumors in nonsmall cell lung cancer. Cancer. 2008;113:1043–7 https://doi.org/10.1002/cncr.23676.
Svolos P, Kousi E, Kapsalaki E, Theodorou K, Fezoulidis I, Kappas C, et al. The role of diffusion and perfusion weighted imaging in the differential diagnosis of cerebral tumors: a review and future perspectives. Cancer Imaging. 2014;14:1–20 https://doi.org/10.1186/1470-7330-14-20.
Bette S, Wiestler B, Delbridge C, Huber T, Boeckh-Behrens T, Meyer B, et al. Discrimination of different brain metastases and primary CNS lymphomas using morphologic criteria and diffusion tensor imaging. Fortschr Röntgenstr. 2016;188:1134–43 https://doi.org/10.1055/s-0042-115572.
Huang BY, Kwock L, Castillo M, Keith Smith J. Association of choline levels and tumor perfusion in brain metastases assessed with proton MR spectroscopy and dynamic susceptibility contrast-enhanced perfusion weighted MRI. Technol Cancer Res Treat. 2010;9:327–37 https://doi.org/10.1177/153303461000900403.
Mills SJ, Thompson G, Jackson A. Advanced magnetic resonance imaging biomarkers of cerebral metastases. Cancer Imaging. 2012;12:245–52 https://doi.org/10.1102/1470-7330.2012.0012.
Zakaria R, Das K, Radon M, Bhojak M, Rudland PR, Sluming V, et al. Diffusion-weighted MRI characteristics of the cerebral metastasis to brain boundary predicts patient outcomes. BMC Med Imaging. 2014;14:26 https://doi.org/10.1186/1471-2342-14-26.
Svolos P, Tsolaki E, Kapsalaki E, Theodorou K, Fountas K, Fezoulidis I, et al. Investigating brain tumor differentiation with diffusion and perfusion metrics at 3T MRI using pattern recognition techniques. Magn Reson Imaging. 2013;31:1567–77 https://doi.org/10.1016/j.mri.2013.06.010.
Young RJ, Sills AK, Brem S, Knopp EA. Neuroimaging of metastatic brain disease. Neurosurgery. 2005;57:4–23 https://doi.org/10.1227/01.NEU.0000182774.54193.37.
Kremer S, Grand S, Remy C, Pasquier S, Benabid AL, Bracard S, et al. Contribution of dynamic contrast MR imaging to the differentiation between dural metastasis and meningioma. Neuroradiology. 2004;46:642–8 https://doi.org/10.1007/s00234-004-1194-2.
Hakyemez B, Erdogan C, Bolca N, Yildirim N, Gokalp G, Parlak M. Evaluation of different cerebral mass lesions by perfusion-weighted MR imaging. J Magn Reson Imaging. 2006;24:817–24 https://doi.org/10.1002/jmri.20707.
This study was founded by UCLA SPORE in Brain Cancer (NIH/NCI 1P50CA211015-01A1) (Dr. Ellingson).
Availability of data and materials
Datasets analyzed during this study are available from the corresponding author on reasonable request.
Ethics approval and consent to participate
This retrospective study was approved by our institutional review board (IRB) with an informed consent waiver.
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The authors declare that they have no competing interests.
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Table S1. Histopathology of primary lesion for ‘Other’ cohort. Primary lesion site and number of case. (XLSX 8 kb)
Figure S1. Comparison of tumor volume, ADC and rCBV in different magnetic fields. Tumor volume and rCBV were not different in 1.5 T or 3 T and that for all patient groups (blue and red, respectively). ADC value within enhancing lesion was significantly lower at 1.5 T (1.062μm2/ms) compared to 3 T (1.163μm2, p < 0.05) within ‘other’ group. No other valuable difference was found with standard MRI metrics. (TIF 174 kb)
Figure S2. Comparison of arterial, venous or overlap components proportional to enhancing tumor volume at 1.5 T and 3 T. The arterial component was significantly smaller in ‘other’ group when using 1.5 T (7.59%) as compared to 3 T (17.99%, p < 0.05). We found a smaller composition of veins with 3 T (10.74%) compared to 1.5 T (30.94%, p < 0.005). The same pattern was seen in ‘Breast’ group at a higher proportion. We also found a median venous component composition of 72.72% with 1.5 T, while at 3 T, this value was equal to 16.62% (p < 0.0005). (TIF 145 kb)