element simulation
S. Raith1, M.Eder1, F. v Waldenfels1, J. Jalali2, A.Volf1, L. Kovacs1
1Research Group CAPS (Computer Aided Plastic Surgery) - Klinik und Poliklinik für Plastische Chirurgie und Handchirurgie, Klinikum rechts der Isar, Technische Universität München, Ismaninger
Str. 22, D-81675 Munich, Germany
2Institute of Medical Engineering at the Technische Universität München (IMETUM), Boltzmannstr. 11, D-85748 Garching, Germany
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Clinic for Plastic Surgery and Handsurgery
Klinikum rechts der Isar
Technische Universität München
medical staff:
engineering staff:
Who is research group CAPS?
Computer Aided Plastic Surgery
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Klinikum rechts der Isar IMETUM Garching
PD Dr. Laszlo Kovacs
Head of the group Dr. M. Eder
Dr. F.v.Waldenfels A. Volf J. Jalali S. Raith
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Breast cancer is very common: 140.337 surgical interventions
in Germany in 2010
[source: S. B. Deutschland, „Statistisches Bundesamt,“ [Online]. Available:
https://www.destatis.de/DE/ZahlenFakten/GesellschaftStaat/Gesundheit/Krankenhaeuser/Tabellen/DiagnosenWeiblich.html. [4 9 2012].]
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Additionally there are reductions, asymmetry corrections,
reconstructions and augmentations
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There is a need for better planning in breast surgery to
overcome todays ad-hoc heuristic approaches
–
Software tools from engineering science might be used for planning
Simulations of the mechanical behavior of the breast’s soft tissues
is evident
Current Situation and Motivation
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Krouskop, T., Wheeler, T., Kallel, K., Garra, B., Hall, T.,
1998. Elastic moduli of breast and prostate tissues under compression. Ultrason Imaging. 20, 260-274.
Wellman, P., Howe, R., Dalton, E., Kern, K., 1999. Breast tissue stiffness in compression is correlated to histological diagnosis. Harvard Biorobotics Laboratory; Availabe at http://biorobotics.harvard.edu/pubs/1999/mechprops.pdf Accessed March 01, 2012
Azar, F., Metaxas, D., Schnall, M., 2001. A deformable finite element model of the breast for predicting mechanical deformations under external perturbations. Acad Radiol. 8, 965-975.
Samani, A., Bishop, J., Yaffe, M.J., Pelwes, D., 2001. Biomechanical 3D finite element modeling of the Human Breast using MRI data. IEEE Trans Med Imaging. 20, 271-279.
Samani, A., Plewes, D., 2004. A method to measure the hyperelastic parameters of ex vivo breast tissue samples. Phys Med Biol. 49, 4395-4405.
Tanner, C., Schnabel, J.A., Hill, D.L., Hawkes, D.J., Leach, M.O., Hose, D.R., 2006. Factors influencing the accuracy of biomechanical breast models. Med Phys. 33, 1758-1769.
Samani, A., Zubovits, J., Plewes, D., 2007. Elastic moduli of normal and pathological human breast tissues: an inversion-technique-based investigation of 169 samples. Phys. Med Biol. 52, 1565-1576.
Rajagopal, V., Lee, A., Chung, J., Warren, R., Highnam R.,
2008. Creating individual-specific biomechanical models of the breast for medical image analysis. Acad Radiol. 15, 1425–1436.
Del Palomar, A.P., Calvo, B., Herrero, J., López, J., Doblaré, M., 2008. A finite element model to accurately predict real deformations of the breast. Med Eng Phys. 30, 1089-1097.
Lapuebla-Ferri, A., Del Palomar, A.P., Herrero, J., Jiménez-Mocholí, A.J., 2011. A patient-specific FE-based methodology to simulate prosthesis insertion during an augmentation mammoplasty. Med Eng Phys. 33, 1094-1102.
Publications dealing with mechanical behaviour of
female breast soft tissue
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Publication
Krouskop et al. (1998)
Wellman et al. (1999)
Azar et al. (2001)
Samani et al. (2001)
Samani et al. (2004)
Samani et al. (2007)
Tanner et al. (2006)
Del Palomar et al. (2008)
Rajagopal et al. (2008)
Lapuebla-F. et al. (2011)
Theoretical constitutive models
utilized by the different authors
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Constitutive Model
Piecewise linear elastic
Piecewise linear elastic
Exponential Hyperelastic
Polynomial Elastic
Mooney-Rivlin
Linear Elastic
Various Material Models
Neo-Hookean
Neo-Hookean
Neo-Hookean
Different testing methods such as ex vivo material tests (uni- or biaxial tension, shear)
or numerical simulations(FEA)
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Taking advantage of modern imaging technologies
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MRI imaging
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inner anatomy of the test persons’ chests
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possible in prone or supine position
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3-D surface scanning
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possible in standing position
Method for in vivo calculation of the breast’s
material parameters
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Taking advantage of modern imaging technologies
Method for in vivo calculation of the breast’s
material parameters
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3-D surface scan Standing position
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Principle workflow of the
material model validation
Machbarkeitsstudie
D
D
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3-D Laser Scan im Brustbereich
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scanning device:
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stitching and merging of the 3 separate surface scan data
Utilized software tool:
3-D laser scans of the breast region
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3 different compartments are defined:
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thorax wall, pectoral muscle and soft tissue (fat
and glandular)
Segmentation of the relevant anatomical
compartments
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Finite element mesh for simulation
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Finite element mesh for simulation
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System boundaries (green)
-> fixed boundary condition
Thorax treated as rigid
-> fixed boundary condition
Muscle also considered to be rigid -> fixed boundary condition
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Apparent deformation due to gravity loading is non negligible
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-> for physically meaningful calculations a stress free starting configuration
has to be found
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Inverse algorithm for the determination of the
unloaded breast shape
deformed configuration
segmented from MRI data
First estimation of the
unloaded configuration
new forward calculation
of the deformed shape
g
g
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Comparison
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better approximation of the undeformed configuration
reaction forces may be determined form
the comparison to the undeformed configuration
comparison via
prescribed displacements
!F
!D
Prob 04g
forward calculation
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Iterativer Prozess
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variation of material parameters according to Tanner et al. and further
Neo Hookean (Young’s modulus varying, PR=0.49)
Simulation results with different sets of
material properties
* Tanner et al., Factors influencing the accuracy of biomechanical breast models, Am. Assoc. Phys. Med. 33 (2006) 1758-1769
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Registration of surfaces in one common
coordinate system
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Coordinate systems of simulation an scans have to be
registered for the comparison.
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Calculation of 3D deviation (so called Hausdorff distance)
and summed over the surface as one scalar value
3-D surface comparison
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Comparison of different simulation
results with
material parameters too stiff
matching material parameters
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Principle workflow of the
parameter identification loop
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D
Optimization loop
Preprocessing
MR Imaging 3-D surface scan FEA Mesh merged surfaceD
Material parameters 3D compare scalar value of accordance FEA result9. Weimarer Optimierungs- und Stochastiktage
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Results:
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Patient individual optimal material parameters:
Young‘s modulus: 0.000827 MPa
(Factor 1.06 to Tanner et al.)Poisson‘s ratio: 0.5 (perfectly incompressible materail)
Results:
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Results:
clearly defined optimal set of parameters
Material parameters: Poisson‘s ratio always at 0.5 Young‘s Modulus as
a factor to the
parameters of Tanner at al. Output: average deviation in mm
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In vivo approximation of material properties is feasible
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Based on a combination of:
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3-D surface scans of standing position
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MRI in prone lying position
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non-invasive approach for material parameter determination
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Patient individual determination of material parameters is possible
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Acquired material parameters may be used for surgical
planning and operation simulations
Conclusion
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application to training set of test persons to get better
statistical evidence (18 are yet available)
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using more complex material models
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Mooney-Rivlin, Ogden etc…
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with more parameters than E and nu (or G and K, respectively)
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material is yet considered to be homogeneous and isotropic
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glandular tissue is not considered
Outlook
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Determined material parameters may be used in clinical
surgery planning e.g. breast reconstruction
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Thank you for your attention
www.caps.me.tum.de
Contact: Stefan Raith
stefan.raith@caps.me.tum.de