Real time simulation of nonlinear tissue response in virtual surgery using the point collocation-based method of finite spheres

Lim, Yi–Je; De, Suvranu

doi:10.1016/j.cma.2006.05.015

Cited by 54 publications

(34 citation statements)

References 20 publications

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“…This is particularly true for soft tissues, which exhibit nonlinearity, non-homogeneity, anisotropy, viscoelasticity (ArItan et al, 2008) and tension/compression asymmetry (Takaza et al, 2013). Skeletal muscle tissue accounts for almost half of human body weight (Wang et al, 1997), so the constitutive properties of passive muscle tissue are crucial for many musculoskeletal models in diverse applications from impact biomechanics (Muggenthaler et al, 2008, Ivancic et al, 2007 to rehabilitation engineering (Linder-Ganz et al, 2008, Linder-Ganz et al, 2007, surgical simulation (Lim andDe, 2007, Audette et al, 2004) and soft tissue drug transport (Wu and Edelman, 2008).…”

Section: Introductionmentioning

confidence: 99%

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

Gindre

Takaza

Moerman

et al. 2013

Journal of the Mechanical Behavior of Biomedical Materials

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Passive skeletal muscle derives its structural response from the combination of the titin filaments in the muscle fibres, the collagen fibres in the connective tissue and incompressibility due to the high fluid content. Experiments have shown that skeletal muscle tissue presents a highly asymmetrical three-dimensional behaviour when passively loaded in tension or compression, but structural models predicting this are not available. The objective of this paper is to develop a mathematical model to study the internal mechanisms which resist externally applied deformation in skeletal muscle bulk. One cylindrical muscle fibre surrounded by connective tissue was considered. The collagenous fibres of the endomysium and perimysium were grouped and modelled as tension-only oriented wavy helices wrapped around the muscle fibre. The titin filaments are represented as non-linear tensiononly springs. The model calculates the force developed by the titin molecules and the collagen network when the muscle fibre undergoes an isochoric along-fibre stretch. The model was evaluated using a range of literature based input parameters and compared to the experimental fibre-direction stress-stretch data available. Results show the fibre direction non-linearity and tension/compression asymmetry are partially captured by this structural model. The titin filament load dominates at low tensile stretches, but for higher stretches the collagen network was responsible for most of the stiffness. The oblique and initially wavy collagen fibres account for the non-linear tensile response since, as the collagen fibres are being recruited, they straighten and re-orient. The main contribution of the model is that it shows that the overall compression/tension response is strongly influenced by a pressure term induced by the radial component of collagen fibre stretch acting on the incompressible muscle fibre. Thus for along-fibre tension or compression the model predicts that the collagen network contributes to overall muscle stiffness through two different mechanisms: 1) a longitudinal force directly opposing tension and 2) a pressure force on the muscle fibres resulting in an indirect longitudinal load. Although the model presented considers only a single muscle fibre and evaluation is limited to along-fibre loading, this is the first model to propose these two internal mechanisms for resisting externally applied deformation of skeletal muscle tissue.2

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Section: Introductionmentioning

confidence: 99%

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

Gindre

Takaza

Moerman

et al. 2013

Journal of the Mechanical Behavior of Biomedical Materials

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“…The latter is of interest in the current study since the work presented here is part of a study aiming to use inverse analysis of MRI based indentation experiments for the non-invasive evaluation of detailed constitutive models for skeletal muscle tissue. Non-invasive mechanical property analysis is important for a wide range of applications including impact biomechanics [4], rehabilitation engineering [5], tissue engineering [6], surgical simulation [7] and tumor detection [8]. However the evaluation of detailed constitutive models describing the complex mechanical (anisotropic, non-linear and viscoelastic) properties of soft tissues requires detailed experimental deformation measurements capturing the complex (anisotropic, non-linear and timevarying) nature of the soft tissue deformation.…”

Section: Introductionmentioning

confidence: 99%

Validation of continuously tagged MRI for the measurement of dynamic 3D skeletal muscle tissue deformation

Moerman¹,

Sprengers²,

Simms³

et al. 2012

Medical Physics

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Purpose: Typically SPAtial Modulation of the Magnetization (SPAMM) tagged MRI requires many repeated motion cycles limiting the applicability to highly repeatable tissue motions only. This paper describes the validation of a novel SPAMM tagged MRI and post-processing frame work for the measurement of complex and dynamic 3D soft tissue deformation following just 3 motion cycles. Techniques are applied to indentation induced deformation measurement of the upper arm and a silicone gel phantom.Methods: A SPAMM tagged MRI methodology is presented allowing continuous (3.3-3.6 Hz) sampling of 3D dynamic soft tissue deformation using non-segmented 3D acquisitions. The 3D deformation is reconstructed by the combination of 3 mutually orthogonal tagging directions, thus requiring only 3 repeated motion cycles. In addition a fully automatic post-processing framework is presented employing Gabor scale-space and filter-bank analysis for tag extrema segmentation and triangulated surface fitting aided by Gabor filter bank derived surface normals. Deformation is derived following tracking of tag surface triplet triangle intersections. The dynamic deformation measurements were validated using indentation tests (~20 mm deep at 12 mm/s) on a silicone gel soft tissue phantom containing contrasting markers which provide a reference measure of deformation. In addition, the techniques were evaluated in-vivo for dynamic skeletal muscle tissue deformation measurement during indentation of the biceps region of the upper arm in a volunteer. Results:For the phantom and volunteer tag point location precision were 44 µm and 92 µm respectively resulting in individual displacements precisions of 61 µm and 91 µm respectively. For both the phantom and volunteer data cumulative displacement measurement accuracy could be evaluated and the difference between initial and final locations showed a mean and standard deviation of 0.44 mm and 0.59 mm for the phantom and 0.40 mm and 0.73 mm for the human data. Finally accuracy of (cumulative) displacement was evaluated using marker tracking in the silicone gel phantom. Differences between true and predicted marker locations showed a mean of 0.35 mm and a standard deviation of 0.63 mm. Conclusions:A novel SPAMM tagged MRI and fully automatic post-processing framework for the measurement of complex 3D dynamic soft tissue deformation following just 3 repeated motion cycles was presented. The techniques demonstrate dynamic measurement of complex 3D soft tissue deformation at sub-voxel accuracy and precision and were validated for 3.3-3.6Hz sampling of deformation speeds up to 12 mm/s.

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“…In contrast, suitably validated computational models have the potential to predict all of these parameters and thus hold significant promise in advancing health care (Taylor and Humphrey, 2009). In particular they are a powerful means for understanding the musculoskeletal system (Erdemir et al, 2007, Marjoux et al, 1998 and are therefore used in diverse applications from impact biomechanics (Muggenthaler et al, 2008, Ivancic et al, 2007 to rehabilitation engineering (Linder-Ganz et al, 2008, Linder-Ganz et al, 2007, surgical simulation (Lim andDe, 2007, Audette et al, 2004) and soft tissue drug transport (Wu and Edelman, 2008). There are also important applications in tissue engineering, as the engineered skeletal muscle tissue needs to have mechanical properties that match those of the replaced native tissue (Hinds et al, 2011, Goldstein et al, 2001.…”

Section: Introductionmentioning

confidence: 99%

The anisotropic mechanical behaviour of passive skeletal muscle tissue subjected to large tensile strain

Takaza

Moerman

Gindre

et al. 2013

Journal of the Mechanical Behavior of Biomedical Materials

130

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The anisotropic mechanical behaviour of passive skeletal muscle tissue subjected to large tensile strain, Journal of the Mechanical Behavior of Biomedical Materials, http://dx.doi.org/10. 1016/j.jmbbm.2012.09.001 This is a PDF file of an unedited manuscript that has been accepted for publication. As a service to our customers we are providing this early version of the manuscript. The manuscript will undergo copyediting, typesetting, and review of the resulting galley proof before it is published in its final citable form. Please note that during the production process errors may be discovered which could affect the content, and all legal disclaimers that apply to the journal pertain. AbstractThe passive mechanical properties of muscle tissue are important for many biomechanics applications. However, significant gaps remain in our understanding of the three-dimensional tensile response of passive skeletal muscle tissue to applied loading. In particular, the nature of the anisotropy remains unclear and the response to loading at intermediate fibre directions and the Poisson's ratios in tension have not been reported. Accordingly, tensile tests were performed along and perpendicular to the muscle fibre direction as well as at 30, 45 and 60 degrees to the muscle fibre direction in samples of Longissimus dorsi muscle taken from freshly slaughtered pigs. Strain was measured using an optical non-contact method. The results show the transverse or cross fibre (TT') direction is broadly linear and is the stiffest (77kPa stress at a stretch of 1.1), but that failure occurs at low stretches (approximately λ = 1.15). In contrast the longitudinal or fibre direction (L) is nonlinear and much less stiff (10kPa stress at a stretch of 1.1) but failure occurs at higher stretches (approximately λ = 1.65). An almost sinusoidal variation in stress response was observed at intermediate angles. The following Poisson's ratios were measured: Ѵ LT = Ѵ LT' = 0.47, Ѵ TT' = 0.28 and Ѵ TL = 0.74. These observations have not been previously reported and they contribute significantly to our understanding of the three dimensional deformation response of skeletal muscle tissue.

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Real time simulation of nonlinear tissue response in virtual surgery using the point collocation-based method of finite spheres

Cited by 54 publications

References 20 publications

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

Validation of continuously tagged MRI for the measurement of dynamic 3D skeletal muscle tissue deformation

The anisotropic mechanical behaviour of passive skeletal muscle tissue subjected to large tensile strain

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