Muge Karaman1,2, Shunan Che3, Rahul Mehta1,2, Guangyu Dan1,2, Zheng Zhong1,2, Han Ouyang3, X. Joe Zhou1,4, and Xinming Zhao3
1Center for Magnetic Resonance Research, University of Illinois at Chicago, Chicago, IL, United States, 2Department of Bioengineering, University of Illinois at Chicago, Chicago, IL, United States, 3Department of Radiology, Cancer Hospital, Chinese Academy of Medical Sciences, Beijing, China, 4Departments of Radiology and Neurosurgery, University of Illinois at Chicago, Chicago, IL, United States
Synopsis
An early imaging assessment of breast
cancer’s response to neoadjuvant chemotherapy (NAC) is critical for timely planning
of treatment strategies. In this study, we develop a machine-learning-based
approach to investigate whether the combined features obtained from the intravoxel
incoherent motion and continuous-time random-walk diffusion models provide an
early prediction of pathologic response in patients receiving NAC. Our results
have shown that a gradient boosting classifier trained with the early-treatment
parametric changes within tumor can predict
the response with an accuracy that is 96% of the accuracy achieved by using the
post-treatment parametric changes.
Introduction:
Neoadjuvant chemotherapy (NAC) can improve surgical management
in both locally advanced inoperable and operable breast cancer1. For
patients with insufficient response, however, receiving weeks of ineffective chemotherapy
increases the toxic side effects; and more importantly delays alternative
treatment. Therefore, an early imaging assessment of response to NAC is
critical for managing breast cancer patients. Despite its success in predicting
breast cancer response as early as after the first NAC cycle2-4,
apparent diffusion coefficient (ADC) from diffusion-weighted MRI (DWI) has not
been established as an imaging marker for breast cancer response to NAC5.
While ADC has been shown to be associated with tissue cellularity, tumor tissue
alterations during NAC often involve other changes, such as vascularity and
structural heterogeneity. These various tumor tissue changes can be studied by
utilizing a specific portion of the b-value “spectrum”6. For
example, intravoxel incoherent motion (IVIM) model7 with low-b-values
(~0-200; 800 s/mm2) can characterize micro-vascularity. High-b-value
(~3500 s/mm2) non-Gaussian models, such as continuous-time random
walk (CTRW) model8-10, can be used to probe tissue structural
heterogeneity. In this study, we investigate the predictive power of
multi-modal DWI, consisting of IVIM and CTRW models, for the pathologic
response to NAC of breast cancer by utilizing a full b-value spectrum
together with a machine-learning-based classification technique. Methods:
Patients: 26 histologically confirmed breast cancer patients with
scheduled NAC were recruited to the study. Patients with
Miller-Payne grade 4 or 5 were categorized as having a pathologic response (pR,
n=10), and with grades 1-3 as not
having a pR (npR, n=16).
Image Acquisition: All patients were scanned on a 3T scanner (GE
Healthcare, MR750) at three time points: before (pre-Tx), after the second
course of (mid-Tx), and after (post-Tx) chemotherapy. The DWI was performed
with 12 b-values (0 to 3000s/mm2),
TR/TE=3500/80ms, slice thickness=5.5mm, FOV=34cm×34cm, and matrix=256×256.
DWI Analysis: The co-registered multi-b-value diffusion-weighted images11-13 at each time
point were first analyzed with a CTRW model8,
$$S/S_0=E_α (-(bD_m )^β), (1)$$
by using all the 12 b-values.
In Eq. (1), Dm is an
anomalous diffusion coefficient, α
and β are temporal and spatial
diffusion heterogeneity parameters, respectively, and Eα is a Mittag-Leffler function. The diffusion-weighted
images were also analyzed with an IVIM model7,
$$S/S_0 =fe^ \left(-b(D_{diff}+D_{perf} )\right) +(1-f)e^ \left(-bD_{diff} \right) , (2)$$
in the low b-value
range (50-800 s/mm2). In Eq. (2), f is the perfusion fraction,
Ddiff is diffusion coefficient, and Dperf is the pseudo-diffusion coefficient.
Pre-Processing: The tumor regions of interest (ROIs) were drawn on the
pre-treatment images by a radiologist; and propagated to the parameter maps
computed from the co-registered diffusion-weighted images. This was followed by
obtaining relative difference maps at mid-Tx or post-Tx by Δmid/post P=(Pmid/post-Ppre)/Ppre for each DWI parameter, P. The
ROIs were then randomly cropped, flipped, and
rotated to prevent overfitting and increase the effective size of the dataset.
Feature Extraction and
Selection: Nine histogram features were
generated from each
ROIs: kurtosis, skewness, variance, mean,
median, interquartile range, 10% quantile, first, and third quartiles, resulting
in 54 features. A recursive feature selection was performed by using a Boruta
algorithm with a modified two-stage multiple testing methodology
process using Benjamin Hochberg FDR and Bonferroni correction.
Machine-learning-based
Classification: The predictive
performance of the mid-Tx features from multi-modal DWI was evaluated by
training a machine-learning classifier using the postsurgical histopathology as
a gold standard. The same procedure was repeated by using the post-Tx features.
Gradient boosting (GB), adaBoost (AB), naïve Bayes (NB), random forest (RF),
decision tree (DT), and Gaussian process (GP) algorithms were employed for
comparison by splitting the training and test sets to a ratio of 80/20. After
performing a preliminary comparison between the classifiers, the best performer
classifier was fine-tuned using grid search with a stratified cross-validation
of 10 repeated 5-folds. The workflow of the data analysis is shown in Figure 1. Results:
Figs.2a-2c show Dm, α, β, Ddiff, Dperf, and f
maps of a representative
patient from the pR group at pre-Tx, mid-Tx, and post-Tx while the results from
a representative patient in the npR group are shown in Fig.3. The
parameters, Dm, α,
Ddiff, and f
exhibited greater changes in the pR patient than the npR patient starting from
the mid-Tx. The features extracted from the CTRW and IVIM parameters
collectively contributed to the “top performing features” to predict treatment
response using mid-Tx (Fig.4a) or post-Tx changes (Fig.4b). The GB classifier provided
the best prediction performance with a mean area-under-the-curve of 0.939 and 0.969,
accuracy of 0.903 and 0.935, and F1 score of 0.878 and 0.916 for both the
mid-Tx (Fig.5a,5c) and post-Tx changes (Fig.5b,5d), respectively. Discussion and Conclusion:
We
have demonstrated the prognostic value of multi-modal DWI in early prediction
of tumor response to treatment in breast cancer. This study suggests that a
machine-learning-based approach, using multiple features from a combination of
DWI models, can comprehensively probe various tumor tissue changes during NAC. Our results showed that the parametric
changes at mid-Tx can predict breast
cancer’s response to NAC with an accuracy that is 96% of the accuracy achieved
by using post-Tx changes. This encouraging predictive power demonstrates the potential
of multi-modal DWI for monitoring NAC for
improved breast cancer management.Acknowledgements
No acknowledgement found.References
[1] Charfare H, Limongelli S, Purushotham AD.
Neoadjuvant chemotherapy in breast cancer. Br J Surg. 2005; 92(1):14-23.
[2] Pickles MD, Gibbs P, Lowry M, et al. Diffusion changes
precede size reduction in neoadjuvant treatment of breast cancer. Magn Reson
Imaging. 2006;24(7):843-847.
[3] Partridge SC, Nissan N, Rahbar H, et al.
Diffusion-weighted breast MRI: Clinical applications and emerging techniques. J
Magn Reson Imaging. 2017;45(2):337-355.
[4] Li X, Abramson RG, Arlinghaus LR, et al.
Multiparametric magnetic resonance imaging for predicting pathological response
after the first cycle of neoadjuvant chemotherapy in breast cancer. Invest
Radiol. 2015;50(4):195-204.
[5] Nilsen L,
Fangberget A, Geier O, et al. Diffusion-weighted magnetic resonance imaging for
pretreatment prediction and monitoring of treatment response of patients with
locally advanced breast cancer undergoing neoadjuvant chemotherapy. Acta Oncol.
2010;49(3):354-360.
[6] Tang L, Zhou XJ. Diffusion MRI of cancer: From low
to high b-values. J Magn Reson Imaging. 2019;49(1):23-40.
[7] Le Bihan D, Breton E, Lallemand D, et al. MR
imaging of intravoxel incoherent motions: application to diffusion and
perfusion in neurologic disorders. Radiology. 1986;161(2):401-407.
[8] Karaman MM,
Sui Y, Wang H, et al. Differentiating low- and high-grade pediatric brain
tumors using a continuous-time random-walk diffusion model at high b-values.
Magn Reson Med. 2016;76(4):1149-1157.
[9] Zhang J, Weaver TE, Zhong Z, et al. White matter
structural differences in OSA patients experiencing residual daytime sleepiness
with high CPAP use: a non-Gaussian diffusion MRI study. Sleep Med.
2019;53:51-59.
[10] Zhong Z, Merkitch D, Karaman M, et al.
High-Spatial-Resolution Diffusion MRI in Parkinson Disease: Lateral Asymmetry
of the Substantia Nigra. Radiology. 2019;291(1):149-157.
[11] Thirion JP. Image
matching as a diffusion process: an analogy with maxwell's demons. Med Image
Anal. 1998; 2(3):243-260.
[12] Kroon DJ and Slump CH. MRI modality
transformation in demon registration. IEEE International Symposium on
Biomedical Imaging: From Nano to Macro, 2009; 1-2:963-966.
[13] Dan G, Karaman M, Che S, et al.
Co-registration of breast diffusion MR images across multiple time points in a
longitudinal study to evaluate the response to neoadjuvant chemotherapy. In:
International Society for Magnetic Resonance in Medicine 27th Scientific
Meeting, 0280; 2019.