Abstract
Background
Experimental, fully three-dimensional mechanical characterization of opaque materials with arbitrary geometries undergoing finite deformations is generally challenging.
Objective
We present a promising experimental method and processing pipeline for acquiring and processing full-field displacements and using them toward inverse characterization using the Virtual Fields Method (VFM), a combination we term MR-u.
Methods
Silicone of varying crosslinker concentrations and geometries is used as the sample platform. Samples are stretched cyclically to finite deformations inside a 7T MRI machine. Synchronously, a custom MRI pulse sequence encodes the local displacement in the phase of the MR image. Numerical differentiation of phase maps yields strains.
Results
We present a custom image processing scheme for this numerical differentiation of MRI phase-fields akin to convolution kernels, as well as considerations for gradient set calibration for data fidelity.
Conclusions
The VFM is used to successfully determine hyperelastic material properties, and we establish best practice regarding virtual field selection via equalization.
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References
Pierron F, Grédiac M (2012) The virtual fields method, 1st edn. Springer, New York
Pierron F, Grédiac M (2000) Identification of the through-thickness moduli of thick composites from whole-field measurements using the Iosipescu fixture: theory and simulations. Compos Appl Sci Manuf 31(4):309–318
Avril S, Pierron F (2007) General framework for the identification of constitutive parameters from full-field measurements in linear elasticity. Int J Solids Struct 44(14-15):4978–5002
Grédiac M, Pierron F, Surrel Y (1999) Novel procedure for complete in-plane composite characterization using a single T-shaped specimen. Exp Mech 39(2):142–149
Pierron F, Vert G, Burguete R, Avril S, Rotinat R, Wisnom MR (2007) Identification of the orthotropic elastic stiffnesses of composites with the virtual fields method: sensitivity study and experimental validation. Strain 43(3):250–259
Xavier J, Avril S, Pierron F, Morais J (2007) Novel experimental approach for longitudinal-radial stiffness characterisation of clear wood by a single test. Holzforschung 61(5):573–581
Grédiac M, Pierron F (2006) Applying the virtual fields method to the identification of elasto-plastic constitutive parameters. Int J Plast 22(4):602–627
Chalal H, Avril S, Pierron F, Meraghni F (2006) Experimental identification of a nonlinear model for composites using the grid technique coupled to the virtual fields method. Compos Part A Appl Sci Manuf 37 (2):315–325
Pannier Y, Avril S, Rotinat R, Pierron F (2006) Identification of elasto-plastic constitutive parameters from statically undetermined tests using the virtual fields method. Exp Mech 46(6):735–755
Promma N, Raka B, Grédiac M, Toussaint E, Le Cam J-B, Balandraud X, Hild F (2009) Application of the virtual fields method to mechanical characterization of elastomeric materials. Int J Solids Struct 46(3–4):698–715
Avril S, Badel P, Duprey A (2010) Anisotropic and hyperelastic identification of in vitro human arteries from full-field optical measurements. J Biomech 43(1):2978–2985
Romo A, Badel P, Duprey A, Favre J-P, Avril S (2014) In vitro analysis of localized aneurysm rupture. J Biomech 47(3):607– 616
Bersi MR, Bellini C, Di Achille P, Humphrey JD, Genovese K, Avril S (2016) Novel methodology for characterizing regional variations in the material properties of murine aortas. J Biomech Eng 138(7)
Avril S, Evans S (2017) Material parameter identification and inverse problems in soft tissue biomechanics, 1st edn. Springer, New York
Hild F, Roux S (2006) Digital image correlation: from displacement measurement to identification of elastic properties – a review. Strain 42(2):69–80
Ri S, Fujigaki M, Morimoto Y (2010) Sampling moiré method for accurate small deformation distribution measurement. Exp Mech 50(4):501–508
Pierron F, Zhu H, Siviour C (2014) Beyond Hopkinson’s bar. Philos Trans Royal Soc A 372(2023):20130195
Fletcher L, van Blitterswyk J, Pierron F (2019) A novel image-based inertial impact test (IBII) for the transverse properties of composites at high strain rates. J Dyn Behav Mater 5(1):65–92
Mallett KF, Arruda EM (2017) Digital image correlation-aided mechanical characterization of the anteromedial and posterolateral bundles of the anterior cruciate ligament. Acta Biomater 56: 44–57
Luetkemeyer CM, Cai L, Neu CP, Arruda EM (2018) Full-volume displacement mapping of anterior cruciate ligament bundles with dualMRI. Extreme Mech Lett 19:7–14
Stout DA, Bar-Kochba E, Estrada JB, Toyjanova J, Kesari H, Reichner JS, Franck C (2016) Mean deformation metrics for quantifying 3D cell–matrix interactions without requiring information about matrix material properties. Proc Natl Acad Sci USA 113(11):2898–2903
Fu J, Pierron F, Ruiz PD (2013) Elastic stiffness characterization using three-dimensional full-field deformation obtained with optical coherence tomography and digital volume correlation. J Biomed Opt 8(12):121512
Gillard F, Boardman R, Mavrogordato M, Hollis D, Sinclair I, Pierron F, Browne M (2014) The application of digital volume correlation (DVC) to study the microstructural behaviour of trabecular bone during compression. J Mech Behav Biomed Mater 29:480–499
Bay BK, Smith TS, Fyhrie DP, Saad M (1999) Digital volume correlation: three-dimensional strain mapping using X-ray tomography. Exp Mech 39(3):217–226
Midgett DE, Pease ME, Jefferys JL, Patel M, Franck C, Quigley HA, Nguyen TD (2017) The pressure-induced deformation response of the human lamina cribrosa: analysis of regional variations. Acta Biomater 53(15):123–139
Stejskal EO, Tanner JE (1965) Spin diffusion measurements: spin echoes in the presence of a time-dependent field gradient. J Chem Phys 42:288–292
Aletras AH, Ding S, Balaban RS, Wen H (1999) Dense: displacement encoding with stimulated echoes in cardiac functional MRI. J Magn Reson 137:242–247
Neu CP, Walton JH (2008) Displacement encoding for the measurement of cartilage deformation. Magn Reson Med 59(1):149–55
Butz KD, Chan DD, Nauman EA, Neu CP (2011) Stress distributions and material properties determined in articular cartilage from MRI-based finite strains. J Biomech 44(15):2667–72
Pierce DM, Ricken T, Neu CP (2018) Image-driven constitutive modeling for FE-based simulation of soft tissue biomechanics. Book Chapter, numerical methods and advanced simulation in biomechanics and biological processes. Academic Press , London
Osman NF, Kerwin WS, McVeigh ER, Prince JL (1999) Cardiac motion tracking using CINE harmonic phase (HARP) magnetic resonance imaging. Magn Reson Med 42(6):1048–60
Sampath S, Osman NF, Prince JL (2009) A combined harmonic phase and strain-encoded pulse sequence for measuring three-dimensional strain. Magn Reson Imaging 27(1):55–61
Sabet AA, Christoforou E, Zatlin B, Genin GM, Bayly PV (2008) Deformation of the human brain induced by mild angular head acceleration. J Biomech 41(2):307–315
Bayly PV, Clayton EH, Genin GM (2012) Quantitative imaging methods for the development and validation of brain biomechanics models. Annu Rev Biomed Eng 14:369–396
Scheven UM, Estrada JB, Luetkemeyer CM, Arruda EM (2020) Robust high resolution strain imaging by alternating pulsed field gradient stimulated echo imaging (APGSTEi) at 7 Tesla. J Magn Reson 310:106620
Mariappan YK, Glaser KJ, Ehman RL (2010) Magnetic resonance elastography: a review. Clin Anat 23(5):497–511
Arruda EM, Boyce MC (1993) A three-dimensional constitutive model for the large stretch behavior of rubber elastic materials. J Mech Phys Solids 41(2):389–412
Connesson N, Clayton EH, Bayly PV, Pierron F (2015) Extension of the optimized virtual fields method to estimate viscoelastic material parameters from 3D dynamic displacement fields. Strain 51(2):110–134
Marek A, Davis FM, Rossi M, Pierron F (2019) Extension of the sensitivity-based virtual fields to large deformation anisotropic plasticity. Int J Mater Form 12(3):457–476
Cotts RM, Hoch MJR, Sun T, Markert JT (1989) Pulsed field gradient stimulated echo methods for improved NMR diffusion measurements in heterogeneous systems. J Magn Res 83:252–266
Abdul-Rahman HS, Gdeisat MA, Burton DR, Lalor MJ, Lilley F, Moore CJ (2007) Fast and robust three-dimensional best path phase unwrapping algorithm. Appl Opt 46:6623–6635
Jenkinson M (2003) Fast, automated, N-dimensional phase-unwrapping algorithm. Magn Reson Med 49 (1):193–197
International Digital Image Correlation Society, Jones EMC, Iadicola MA (eds.) (2018) A good practices guide for digital image correlation. https://doi.org/10.32720/idics/gpg.ed1
Markl M, Bammer R, Alley MT, Elkins CJ, Draney MT, Barnett A, Moseley ME, Glover GH, Pelc NJ (2003) Generalized reconstruction of phase contrast MRI: analysis and correction of the effect of gradient field distortions. Mag Reson Med 50:791–801
Nelder JA, Mead R (1965) A simplex method for function minimization. Comput J 7:308–313
Bower AF (2009) Applied mechanics of solids, 1st edn. CRC Press, Boca Raton
Wang Z, Huan X, Garikipati K (2019) Variational system identification of the partial differential equations governing the physics of pattern-formation: inference under varying fidelity and noise. Comput Methods Appl Mech Engrg 356: 44–74
Huan X, Marzouk YM (2013) Simulation-based optimal Bayesian experimental design for nonlinear systems. J Comput Phys 232(1):288–317
Acknowledgements
The authors would like to acknowledge Profs. Xun Huan, Alan Wineman, and Krishna Garikipati, Dr. Jin Yang, and Ryan Rosario for helpful discussions in the development of the study and manuscript. This work was supported by the National Science Foundation grant number CMMI 1537711 and its Graduate Fellowship Research Program.
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Appendices
Appendix A: Divolution
We illustrate our complex division-based numerical gradient approximation technique by the following example. Suppose first that we have an unwrapped scalar phase field θ = angle(Z) which is proportional to a single component of our induced displacement field uk. We can smooth or numerically differentiate θ by convolution, or passing filter kernels w and d, respectively, over it as illustrated in Fig. 5. The phase function θ is defined at every pixel index i and j for the 2D example, which is henceforth denoted as θ(i,j). By passing a symmetric smoothing filter w in the j direction over θ(i,j), we produce a smoothed function
while by passing an antisymmetric edge filter d (with a middle component of zero) in the j direction, we determine the average central phase difference
where 2H + 1 is the length of the respective filter, and w and d follow normalizations of
If instead, the phases are wrapped on (−π/2,π/2), simple convolution operators will produce unwanted phase gradients or smoothing operations at the ±π/2 jumps. We can avoid smoothing wrap jumps by using the complex data Z directly. Notably, the values of Z are independent of the wrapping of θ, making Z itself a usable quantity to minimize unwrapping artifacts. Distinguishing the wrapped phase field \(\widetilde {\theta } = \text {wrap}(\theta )\) from its unwrapped counterpart θ, the complex magnetic resonance output field Z at a pixel (i,j) is represented in polar form as
where r(i,j) represents the magnitude of the image signal. With equation (16), complex division can be used to produce the result of equation (14) in a similar way to a convolution filter - pixels on either side of the filter can be divided by one another, or divolved, to subtract phases. The divolution process is illustrated in Fig. 5(d), and the phase gradient can be expressed as
Appendix B: Gradient Coil Calibration
Correcting for the non-linearity in the imaging gradient set requires a set of two experiments: (a) a rigid translation of a large block of material to determine the higher order deviations from a linear gradient and (b) a spatial grid of material to determine both local and global dilation along the longitudinal direction, essentially the integration constant from the former. In general, we can describe the unwrapped phase field θ(X) for a sample in an ideal gradient coil, as in equation (7), as
where X is a position in our sample’s reference configuration, u(X) is the displacement in the sample, and Λ is the encoding length chosen by the user corresponding to how many phase wraps occur per 2π in the respective direction. However, as real gradient coils are designed to be very close to linear in the central region, the non-linearity at the periphery must be considered for calculating displacements and strains to a high degree of accuracy. We can describe the non-ideal gradient \(\boldsymbol {G}^{\prime }\) with higher-order terms as G(1 + α(X)). Given the relation between our encoding length Λ and the applied magnetic field gradient,
we can write the phase in a non-ideal gradient coil as
where α is the higher order gradient coil correction function which is purely a vector function of the MR coordinate system χ (with all χi parallel to Xi). For cases of rigid translation of amplitude w, we can then rearrange for α(X),
where θ0 is the value at the gradient coil center θ(χ = 0), and C is a constant taking into account the possibility of an offset error at the center.
For calibration of our setup, we ran two rigid translation experiments of 5mm and 7.5mm, respectively. As described in Section “Loading and Imaging Procedure”, phase maps were put through the processing procedure shown in Fig. 5. Importantly, phase maps were first unwrapped using the procedure described in [41], which prioritizes unwrapping of pixels based on the flatness of the second central difference. Surface fits for the components αi(χ) (i.e. using θi(χ)) were then performed to values on symmetric planes in the gradient coil (χ1-χ2, χ1-χ3). Furthermore, due to symmetry in gradient set design and winding, α1 is comprised of even terms, while α2 and α3 are comprised of odd terms in χ. The expressions αi were found to be well-described by the analytical forms:
where ni, Ci, ai, bi, ci, di, and ei are all fitting constants.
To correct displacement gradient tensor data in practice, we can take analytical derivatives of the gradient coil correction function α and apply them to components,
where \(F^{\prime }_{ij}\) is the correction of the deformation gradient tensor with components Fij, and \(\frac {\partial {\alpha _{i}}}{\partial {\chi _{j}}}(\boldsymbol {X})\equiv \alpha _{i,j}(\boldsymbol {X})\), for completeness, are,
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Estrada, J., Luetkemeyer, C., Scheven, U. et al. MR-u: Material Characterization Using 3D Displacement-Encoded Magnetic Resonance and the Virtual Fields Method. Exp Mech 60, 907–924 (2020). https://doi.org/10.1007/s11340-020-00595-4
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DOI: https://doi.org/10.1007/s11340-020-00595-4