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Creating Individual-specific Biomechanical Models of the Breast for Medical Image Analysis

Rationale and Objectives

Anatomically realistic biomechanical models of the breast potentially provide a reliable way of mapping tissue locations across medical images, such as mammograms, magnetic resonance imaging (MRI), and ultrasound. This work presents a new modeling framework that enables us to create biomechanical models of the breast that are customized to the individual. We demonstrate the framework’s capabilities by creating models of the left breasts of two volunteers and tracking their deformations across MRIs.

Materials and Methods

We generate customized finite element models by automatically fitting geometrical models to segmented data from breast MRIs, and characterizing the in vivo mechanical properties (assuming homogeneity) of the breast tissues. For each volunteer, we identified the unloaded configuration by acquiring MRIs of the breast under neutral buoyancy (immersed in water). Such imaging is clearly not practical in the clinical setting; however, these previously unavailable data provide us with important data with which to validate models of breast biomechanics. Internal tissue features were identified in the neutral buoyancy images and tracked to the prone gravity-loaded state using the modeling framework.

Results

The models predicted deformations with root-mean-square errors of 4.2 and 3.6 mm in predicting the skin surface of the gravity-loaded state for each volunteer. Internal tissue features were tracked with a mean error of 3.7 and 4.7 mm for each volunteer.

Conclusions

The models capture breast shape and internal deformations across the images with clinically acceptable accuracy. Further refinement of the framework and incorporation of more anatomic detail will make these models useful for breast cancer diagnosis.

Breast cancer diagnosis involves the careful examination and analysis of clinical images across multiple views and imaging modalities including x-ray mammography, magnetic resonance imaging (MRI), and ultrasound. In analyzing these images, the clinician must interpret the image patterns (noting that each modality measures a different quantity, mammograms measuring x-ray radiation) and track suspicious lesions across these views to determine their state. Apart from the complexity of inferring and mapping across different image patterns, the analysis is further complicated by the fact that the breast is a soft biologic tissue. Its shape changes significantly during any imaging procedure because of mechanical loads such as gravity or compression. Consequently, internal tissue configurations are substantially different across the images that are obtained for diagnosis.

To alleviate these difficulties, significant efforts have been made in the field of image registration ( ). Traditionally, registration algorithms have used image intensity–based statistics, such as mutual information, to determine the optimal transformation for aligning the images ( ). However, the transformations are free form and therefore do not necessarily give physically plausible alignments. To this end, there is increasing interest in the development of biomechanical models of the breast that simulate the deformations and constrain the transformations to be physically admissible ( ).

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Materials and methods

Volunteers and MRI Acquisition

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Modeling Large Deformations: Finite Elasticity Theory

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Kinematics

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Equilibrium Equations

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Imaging the Breast in the Neutral Buoyancy Configuration

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Figure 1, Effect of immersing the breast in water. Top , magnetic resonance (MR) image slice of the breast of Volunteer 2 immersed in a bag of water (bright region). Bottom , The MR image slice taken in the prone, gravity-loaded state. Distance between extreme points in the breast is shown in the two images to give an initial estimate of the effect of gravity on breast shape.

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Creating Individual-specific Breast Models

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Figure 2, Process of creating an individual-specific breast model. (a) Segmentation of tissue boundaries from a magnetic resonance (MR) image. Light spots represent the skin surface, and dark spots represent the muscle surface. (b) Dataset of skin (light spots) , and muscle (dark spots) after segmenting an entire MR image set. (c) Generic finite element breast geometry and breast skin and muscle datasets. (d) Finite element model fitted to skin and muscle surface data. (e) Fitted model without surface rendering to show the volumes of the fitted elements.

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Figure 3, Finite element model (surfaces) fitted to the skin surface data sets (spots) of five subjects lying prone in a magnetic resonance imaging scanner. The fitted model of Cambridge subject 1 is shown in Figure 2 .

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Loading and Boundary Conditions

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Characterizing Individual-specific In Vivo Mechanical Properties

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Results

Volunteer 1

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Figure 4, Convergence of root-mean-square (RMS) error in Euclidean displacements of selected material points inside the fitted model of the breast of Volunteer 1 with increasing mesh resolution.

Figure 5, Refined model (a and b) and (c) a magnetic resonance (MR) image slice embedded in the refined model of the breast of Volunteer 1 in neutral buoyancy. The MR image shows the left breast in neutral buoyancy, where the white block represents the water bath.

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Figure 6, Tracking surface and internal tissues from the neutral buoyancy reference configuration to the prone gravity-loaded deformed state of the breast of Volunteer 1. (a) Neutral buoyancy magnetic resonance (MR) image with tissue features encircled by spots and numbered sequentially. (b) Fitted finite element model of the neutral buoyancy state superimposed on the neutral buoyancy MR image and embedded with the same tissue features. (c) Predicted finite element model of the prone gravity-loaded configuration superimposed on prone gravity-loaded breast MR image. Spots show predicted locations of the four tracked tissue features and the labeled regions indicate actual locations of the features. (d) Prone gravity-loaded breast MR image superimposed with the predicted locations of tracked tissue features in (encircled by spots ) together with actual locations identified and labeled in white . See Table 1 for quantitative comparisons of tissue feature localization.

Table 1

Euclidean Distances between Centroids of Actual and Predicted Locations of the Four Tissue Regions Tracked from the Neutral Buoyancy State to the Gravity-loaded Prone Configuration in Volunteer 1

Tissue Region 1 2 3 4 Displacement (mm) 5.1 20.5 19.0 21.7 Euclidean distance (mm) 1.6 4.8 4.5 4.0

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Volunteer 2

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Figure 7, Refined model ( a and b ) and (c) a magnetic resonance (MR) image slice embedded in the refined model of the breast of Volunteer 2 in neutral buoyancy. The MR image shows the left breast in neutral buoyancy, where the white block represents the water bath.

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Table 2

Euclidean Distances between Centroids of Actual and Predicted Locations of the Four Tissue Regions Tracked from the Neutral Buoyancy State to the Gravity-loaded Prone Configuration in Volunteer 2

Tissue Region 1 2 3 4 Displacement (mm) 16.9 16.6 17.0 18.0 Euclidean distance (mm) 4.9 5.0 4.0 4.8

Figure 8, Tracking surface and internal tissues from the neutral buoyancy reference configuration to the prone gravity-loaded deformed state of the breast of Volunteer 2. (a) Neutral buoyancy magnetic resonance (MR) image with tissue features encircled by spots and numbered sequentially. (b) Fitted finite element model of the unloaded state superimposed on the neutral buoyancy MR image and embedded with the same tissue features. (c) Predicted finite element model of the prone gravity-loaded configuration superimposed on prone gravity-loaded breast MR image. Spots show predicted locations of the four tracked tissue features and the labeled regions on the MR image indicate actual locations of the features. (d) Prone gravity-loaded breast MR image superimposed with the predicted locations of tracked tissue features (encircled by spots ) together with actual locations identified and labeled in white . See Table 2 for quantitative comparisons of tissue feature localization.

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Discussion

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