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8. CONCLUSIONS Unsurprisingly, the disc and the facet joints have the greatest impact on the model response and need to be modeled as accurately as possible. An insufficiently modeled disc can therefore severely harm the predictive power of a spine model. Concerning the question about the meaningfulness of deterministic models, we can conclude that a model with a deterministic set of parameters is just that: A model of one specific spine. If calibrated and validated carefully, such models might be able to represent either a patient-specific or an “average spine”—at least, if one had enough measured data to validate against. Nevertheless, averages are purely statistical constructs, non-existent in reality. FE models will find differences between any slight modification of the model (well, up to machine precision). But does the difference matter? Likewise, an implant might perform better than implant in the model by some arbitrary factor. But is this factor—this effect—really relevant in relation to the wide scatter in the biomechanics of true human spines? Indeed, even for patient-specific models, were inter-individual variability can be neglected for obvious reasons, model parameters are still afflicted with some amount of measuring error and hence uncertainty, which must not be ignored, if a model's prediction shall meet certain reliability constraints. ACKNOWLEDGEMENTS This work was supported by the German Research Foundation (DFG Wi-1352/12-1), Bonn, Germany. 9. REFERENCES 1. Schmidt H, Heuer F, Drumm J, et al. Application of a calibration method provides more realistic results for a finite element model of a lumbar spinal segment. Clinical Biomechanics. 2007;22(4):377–384. 2. Schmidt H, Heuer F, Simon U, et al. Application of a new calibration method for a three-dimensional finite element model of a human lumbar annulus fibrosus. Clinical Biomechanics. 2006;21(4):337–344. 3. Wilke H-J, Wenger K, Claes L. Testing criteria for spinal implants: recommendations for the standardization of in vitro stability testing of spinal implants. European Spine Journal. 1998;7(2):148–154. 4. Patwardhan AG, Havey RM, Meade KP, Lee B, Dunlap B. A follower load increases the load-carrying capacity of the lumbar spine in compression. Spine. 1999;24(10):1003–1009. 5. Shirazi-Adl A, Parnianpour M. Load-bearing and stress analysis of the human spine under a novel wrapping compression loading. Clinical Biomechanics. 2000;15(10):718–725. 6. Masharawi Y, Rothschild B, Dar G, et al. Facet orientation in the thoracolumbar spine: three-dimensional anatomic and biomechanical analysis. Spine.
2004;29(16):1755–1763. 7. Panjabi MM, Goel V, Oxland T, et al. Human lumbar vertebrae. Quantitative threedimensional anatomy. Spine. 1992;17(3):299–306. 8. Panjabi MM, Oxland T, Takata K, et al. Articular facets of the human spine. Quantitative three-dimensional anatomy. Spine. 1993;18(10):1298–1310. 9. McKay MD, Beckman RJ, Conover WJ. A Comparison of Three Methods for Selecting Values of Input Variables in the Analysis of Output from a Computer Code. Technometrics. 1979;21(2):239–245. 10. Helton JC, Davis FJ. Latin hypercube sampling and the propagation of uncertainty in analyses of complex systems. Reliability Engineering & System Safety. 2003;81(1):23–69. 11. Davison AC, Hinkley DV. Bootstrap Methods and their Application. Cambridge: Cambridge <strong>University</strong> Press; 1997. 12. Zuber V, Strimmer K. High-Dimensional Regression and Variable Selection Using CAR Scores. Statistical Applications in Genetics and Molecular Biology. 2011;10(1):34. 13. Grömping U. Relative Importance for Linear Regression in R: The Package relaimpo. Journal of Statistical Software. 2006;17(1):1–27. 14. Grömping U. Estimators of Relative Importance in Linear Regression Based on Variance Decomposition. The American Statistician. 2007;61(2):139–147.
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The Proceedings of the 10 th Intern
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Install Adobe Reader 8 or 9 (http:/
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Content: POSTERS: BRAIN: CELL: EVAL
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Modeling of blood flow through a fl
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The mesh generation of the model wa
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Figure6 . The stroke volume data fo
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Digital Subtraction Phonocardiograp
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mobile cart for easy recording in c
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Figure 7. This image shows PCG samp
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Our approach is an improvement in t
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one cements as well as its behaviou
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Typical dimensions of lumbar verteb
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attributed to the change of stiffne
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lifestyle and obesity. In that cont
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T was the temperature in Kelvin and
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sustained tensile strains stimulate
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An approach aiming at determining a
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failure load. 2.4 Simulation of reh
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REFERENCES 1. Vunjak-Novakovic G, A
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3. FIF-BAL BIOREACTOR The FIF devic
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value of p nearest to dqc=0 we cont
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(Wanless, 1999). This low value cou
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3. MATERIALS AND METHODS A CAD mode
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did not allow gap closure. Maximum
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hand, if the IFM is too large, remo
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2. INTRODUCTION Intervertebral disc
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Figure 3. T1 signal enhancement in
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1. ABSTRACT TIP CELLS AT THE TOP: M
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Fig. 1. Schematic overview of the m
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Fig. 3. Image of the amount of VEGF
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THE COMPUTATIONAL MODEL OF DENTAL I
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processing application STL Model Cr
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For the implant/bone interaction as
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ABSTRACT THE IMPACT OF SELECTION BI
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Figure 1: flow chart showing the op
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Figure 2: Time course of cytosolic
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CONSTITUTIVE MODELLING OF THE ANNUL
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it is well known the non-linear nat
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Therefore, we have decided to carry
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EXTRACTION OF PHALANGEAL JOINT PARA
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column vectors of P. Denoting the v
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End i joint angles and length offse
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Validation of Strain Mapping for th
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allows the calculation of strain ma
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RMS error was 0.054 and the strains
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AN APPROACH FOR THE REDUCTION OF TH
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The relation between the time-deriv
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Error in position [mm] Error in pos
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ANALYSIS OF THE INTRAINDIVIDUAL DIF
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Fig.1: Frontal view on all subchond
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[6] M. Bozkurt, B. B. Kentel, G. Ya
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on the actual necessary time needed
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Illustration 2: The initially spher
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cell if it is hardly able to deform
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fit with a reference anatomy in min
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show that patellar mal-positioning
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Experimental and numerical analysis
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stenosis in both simulations and ex
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stented case, corresponding to the
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EVALUATION OF DIFFERENT LOADING CON
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were modeled with identical geometr
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each simulation and the position of
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FINITE ELEMENT MODEL ANALYSIS OF HU
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Figure 1: Maximal principal strains
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Method for classification of porcin
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3.3 Identification of Paths Accordi
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Table. 1. Descriptive Patterns used
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CHARACTERIZING THE MECHANICAL MICRO
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3.1.3 Cell proliferation It is assu
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Stress [Pa] 4 3 2 1 0 Mean stress A
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REFERENCES [1] A.M. Bratt-Leal, R.L
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y exposure to interstitial fluid sh
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according to (Eq. 2), nor averaged
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emoved the oscillations partially a
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static load and a dynamic load. A s
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positive effect of the number of ac
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pathways and their interactions tha
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applications, the need for accuracy
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avoid violating the initial geometr
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6. CONCLUSION The examples of appli
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Fig. 1 Semicircular canal structure
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4. RESULT Fig. 6 FSI model of semic
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6. ACKNOWLEDGEMENT This research wa
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ods to the biocompatible plastic po
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Table 1: Analysis conditions Static
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[3] Brantigan, J. W., Steffee, A. D
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femoral head fracture, the femoral
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Fig 3. Schematic drawing of the ste
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6. CONCLUSION Fig 7. Analysis resul
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and angular rates were registered b
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former, there were assumed the foll
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delivered dynamic support, which pr
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insertion of provisional restoratio
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Figure 4: Implant displacements obt
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5. DISCUSSION AND CONCLUSION Initia
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at which microdamage originates. Fo
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4. RESULTS The load response varied
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current study to explore the effect
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implant correctly from the finite e
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(a) (b) (c) (d) (e) Figure 3. The s
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(a) (b) Figure 6. The meshed model
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(a) (b) Figure 9. Cumulative probab
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NUMERICAL EVALUATION AND MEDICAL CO
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compared by overlaying the real dat
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four sample patient data, outcomes
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A POROELASTIC APPROACH FOR AN OPEN
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where indexes U, P refer to the unk
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RESULTS As a preliminary test, a 0.
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BIOMECHANICAL BEHAVIOR OF CANCELLOU
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cement acts perfectly, therefore it
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cancellous bone of natural joints a
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COMPUTATIONAL MODELING OF TANGLED A
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The centers of the simulated cells
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untangled, the local fiber displace
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TOWARDS A WAVELET BASED MEDICAL IMA
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however at each decomposition scale
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the MATLAB software (for the Modifi
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A FLUID STRUCTURE INTERACTION MODEL
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hyperelastic based on available exp
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t [ms] 30 70 160 220 270 Pressure [
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MECHANICAL BAHAVIOR OF DIFFERENT NI
Page 244 and 245: parameters necessaries to use this
Page 246 and 247: F1 and Mtwo were directly related t
Page 248 and 249: MECHANICAL EFFECT ON METABOLIC TRAN
Page 250 and 251: an initial nil lactate concentratio
Page 252 and 253: present study, such values were phe
Page 254 and 255: EVALUATION OF FEMORAL COMPONENT MIC
Page 256 and 257: TS implants employed a “hybrid”
Page 258 and 259: 5. DISCUSSION i ii Figure 2: Compar
Page 260 and 261: THE MECHANICAL ENVIRONMENT IN THE D
Page 262 and 263: instead the femur was supported by
Page 264 and 265: It must be noted however, that in t
Page 266 and 267: 1. ABSTRACT MODELING OF ARTICULAR C
Page 268 and 269: exp 1 1 2 1 where and are i
Page 270 and 271: Implant Fig.2. Axisymmetric represe
Page 272 and 273: A MULTI-SCALE ANISOTROPIC CONSTITUT
Page 274 and 275: 3.2 Decoupled invariant formulation
Page 276 and 277: Fig. 1. Experimental data from unia
Page 278 and 279: VALIDATION AND CALIBRATION PROCESSE
Page 280 and 281: Figure 1: A three-step process simu
Page 282 and 283: The validation process employed on
Page 284 and 285: FLUID-STRUCTURE INTERACTION ANALYSI
Page 286 and 287: The coupled SQA model and the conve
Page 288 and 289: Point P7, located at the toe of the
Page 290 and 291: THE INFLUENCE OF UNCERTAIN ANATOMIC
Page 292 and 293: Figure 3 exemplifies for intradisca
Page 296 and 297: COMPARISON OF DIFFERENT LOADING CON
Page 298 and 299: Figure 1 Finite element model of th
Page 300 and 301: 6 CONCLUSION It is a feasible way t
Page 302 and 303: FROM CELL CONTRACTILITY TO CURVATUR
Page 304 and 305: 4. MODEL When cells adhere on a sub
Page 306 and 307: organisation. Understanding the pri
Page 308 and 309: PREOPERATIVE PLANNING SUPPORT SYSTE
Page 310 and 311: [9]. Stenosis of 25, 45, 65 and 85
Page 312 and 313: Fig. 1:Dependent and independent va
Page 314 and 315: 1. ABSTRACT Local strain measuremen
Page 316 and 317: around 100µm (halfway through the
Page 318 and 319: sampling points at different cross
Page 320 and 321: CLASSIFICATION OF PHYSICAL ACTIVITY
Page 322 and 323: induces a vertical alignment of the
Page 324 and 325: accelerations combination). However
Page 326 and 327: line under translation. Information
Page 328 and 329: In this study, we apply a meshless
Page 330 and 331: used the PAC constitutive constants
Page 332 and 333: 1006031) is gratefully acknowledged
Page 334 and 335: improvements were seen in both grou
Page 336 and 337: Pre-augmentation Position 1, V=3mL
Page 338 and 339: 5. ACKNOWLEDGEMENTS Funding for thi
Page 340 and 341: the hemodynamics in cerebral aneury
Page 342 and 343: 4. RESULTS AND DISCUSSION In order
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processing methods need to be devel
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3. METHODS 3.1 Experimental Method
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Figure 2 - Micrographs for tensile
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analysis of the tissue mechanics. B
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3. METHODS 3.1 Specimen Preparation
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of five points across the mid mid-c
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equired to replicate the deformatio
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pre-load within the plate (compress
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4. RESULTS The load-deformation beh
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fracture fixation. Medical Engineer
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model. It approximates knee kinemat
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computational cost remains moderate
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Concerning the optimization procedu
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aesthetic recovery. However, in som
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atio experimented by both wounds is
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VARIATION OF MICRO-ARCHITECTURE AND
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osteoporotic (OP). The sample volum
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Figure 4: Mean error in orthotropy
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INVESTIGATION OF CORTICAL SHELL STR
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When creating the degenerated FE mo
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Figure 4. Degeneration sensitivity
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METHODS TO ACCELERATE FINITE ELEMEN
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the “joint” constraints configu
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Figure 4: Absolute prediction error
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EFFECT OF POST TREATMENT FOR MULTIP
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Fig.2 Inlet velocity profile indica
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4.3 WSS results Figure 8 shows the
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approximated by the so-called Ritz
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Figure 2: Viscohyperelastic cube: (
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There is no optimal density-elastic
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Fig. 2 Cut view of FE-model. Shown
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5. Weis JA, Miga MI, Granero-Moltó
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3. SYSTEM DESIGN Sheep eyes, as the
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which provides natural tactile feed
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113:341-342 20. Henderson B. A., Gr
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health area. According to estimates
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Table 1. RMS Value based on subject
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6. REFERENCES 1. http://www.disable
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ehavior [5]. From the viewpoint of
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Fig. 1 Average Male and Female's L4
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4. Deyo, R.A., and Weinstein, J. N.
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geometry of the cell and ECM degrad
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Shown in Fig. 2(b) is a plot of the
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6. REFERENCES 1. Dubin-Thaler B.J.,
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We implemented our individual-based
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3.3.1 Centers of mass Table 1: Base
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average coordination num ber averag
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BIOMECHANICAL ANALYSIS OF THE MUSCU
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of the ligament strain; a linear re
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lengthening, respectively, if compa
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THE EFFECT OF HIGH TIBIAL OSTEOTOMY
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The 3D LiveWire tool was used as an
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Table II: Peak medial and lateral f
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INVESTIGATING CHANGES IN JOINT LOAD
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4. RESULTS Table 1 shows the mean m
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Fig.5 displays the OKS and KOS pre
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Dynamic Touch of Effective Golf Swi
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properties of a golf club and hand
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perturbation in e3 whereas player B
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1. Kim, W., Response to letter to t
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configuration.[4] have explained ho
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compartments as well as a single mu
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5. Shabana, A.A., Dynamics of multi
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Five healthy volunteers (age: 38.3
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internal lumbar spinal shape was de
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Airflow Simulation of Nasal Cavity
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temperature [5], and Wbl is the wat
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Figure 8. Figure 8(a) illustrates t
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Finite element models of the hip ca
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3.2 Finite Element Analysis Followi
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5. DISCUSSION Previous DEA implemen
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STATISTICAL SHAPE MODELING OF CAM-T
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Thirty-three control femurs (25 mal
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asymptomatic subjects 7,9 . The Hot
Page 499 and 500:
6. REFERENCES 1. Ganz, R., Parvizi,
Page 501 and 502:
NUMERICAL IDENTIFICATION OF THE PER
Page 503 and 504:
2. METHOD AND NUMERICAL MODEL. 2.1
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1 u dV V u. (Eq. 2) V The permeab
Page 507 and 508:
1. ABSTRACT PASSIVE AND ACTIVE MUSC
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presented in figure 2 the simulatio
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Indenter Stroke [mm] Muscle Force [
Page 513 and 514:
Objectives Long bone failure charac
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the specimens in three point bendin
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developing a subject-specific finit
Page 519 and 520:
Models used in the past, mostly bas
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In this work it is presented the de
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Average Table 1.- Walk average test
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angles for the step of 2.28° and 8
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insufficiency syndrome (TIS), defin
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a) b) c) Fig. 5 - Contact interface
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EOS. Among these options, VEPTR has
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dissection occurs when blood intrud
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mean value of 0.0310 m s -1 . The o
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progression. It can in turn contrib
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dependent data. They conclude that
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found that it is extremely difficul
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endering loop is started and the ra
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3.1 Imaging protocol of the knee A
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Fig. 3: Pressure distribution in th
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7. REFERENCES 1. Masouros, S.D., Bu
Page 551 and 552:
and estimate in vivo tissue strains
Page 553 and 554:
tendon has a larger moment arm abou
Page 555 and 556:
Song, H. M., Smith, R. L., Longaker
Page 557 and 558:
Fig. 1. Single line transducer resu
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Let P INT be the data set of the lo
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could quantify the initial structur
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expansion of a stent, a metallic sc
Page 565 and 566:
immediately after stent expansion a
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6. ACKNOWLEDGMENT This research is
Page 569 and 570:
Deformation of the arterial surface
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separate study to be described in a
Page 573 and 574:
3. Timmins, L.H., Miller M.W. Clubb
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migrate in a unique fashion to the
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Fig. 1: Domain and schematic repres
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Furthermore, the values are spread
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this study, our goal is to establis
Page 583 and 584:
Figure 3. Relative length change in
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5. Erdemir A, Sibole S. Open Knee:
Page 587 and 588:
lateralis (inferior and superior) f
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during mouth closing and chewing. O
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BIOMECHANICAL MODELING OF THE HUMAN
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appropriates mechanical properties
Page 595 and 596:
Fig. 4: Correlation of the location
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1. ABSTRACT COMPUTER AIDED TUMOR RE
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B. Cutting planes The surgeon defin
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4.RESULTS To test the developed sys
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FROM PATIENT-SPECIFIC DATA TO MULTI
Page 605 and 606:
catheterization mean measurements (
Page 607 and 608:
the different virtual surgical desi
Page 609 and 610:
1. ABSTRACT DIGITAL ULTRASOUND DESP
Page 611 and 612:
2.2 Filtering Based Wavelet 2.2.1 C
Page 613 and 614:
Table 1: quantitative criteria used
Page 615 and 616:
Mural Thrombosis in a Two-Level Com
Page 617 and 618:
But, the soft repulsive force can n
Page 619 and 620:
Ratio of adhered PLT a simplificati
Page 621 and 622:
DEGRADATION OF MAGNESIUM ALLOY STEN
Page 623 and 624:
study and the parameter setting can
Page 625 and 626:
Fig. 5. Damage evolution of the thr
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NUMERICAL SIMULATIONS OF FATIGUE FO
Page 629 and 630:
Figure 1. Scheme of the two approac
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Figure 3. On the left, alternating
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INVESTIGATION OF HEAD-NECK KINEMATI
Page 635 and 636:
complexity of the vertebrae and sku
Page 637 and 638:
nearly no tension occurred for the
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9. Ito S, Ivancic PC, Panjabi MM, C
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[Ntsinjana et al., 2011], commonly
Page 643 and 644:
impedances were maintained within p
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6. Pennati G., Corsini C., Cosentin
Page 647 and 648:
analyse the effect that different a
Page 649 and 650:
attached cases this value was highe
Page 651 and 652:
References 1. Nordin M and Frankel
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therapy to achieve the desired medi
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iomechanical response of the leg to
Page 659 and 660:
algorithm has to be integrated into
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to a modification in the tooth disp
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5. CONCLUSIONS 5.1 Geometry and per
Page 665 and 666:
present work is to show the ability
Page 667 and 668:
[6,7]. In order to reproduce numeri
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5. DISCUSSION, CONCLUSIONS AND PERS
Page 671 and 672:
3.1 Generation of the vertebral sur
Page 673 and 674:
3.4 Modeling of the facet joints Th
Page 675 and 676:
The column diagramm of Fig.8 shows
Page 677 and 678:
tool to evaluate the drug distribut
Page 679 and 680:
Figure 3: The mean value of the dos
Page 681 and 682:
INFLUENCE OF KYPHOSIS ON SPINAL LOA
Page 683 and 684:
(a) (b) (c) Fig. 1. The three repre
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etween T6 and T9 with a higher degr
Page 687 and 688:
A COMPARISON BETWEEN STANDARD AND D
Page 689 and 690:
the SB with a 2.5 mm balloon; ii) o
Page 691 and 692:
A TAWSS [Pa] B OSI [Pa] C 0 0.25 0.
Page 693 and 694:
ABSTRACT CONSTITUTIVE MODELLING OF
Page 695 and 696:
20% compression strains were impose
Page 697 and 698:
4. DISCUSSION The limited number of
Page 699 and 700:
AN ALGORITHM FOR MODELING THE FIBRE
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1 - Compute the centre of the botto
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(a) (b) Figure 2. Load-displacement
Page 705 and 706:
A bio-mechanics based methodology t
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to a particular body part based on
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Injury Cost (USD) Million 0.7 0.6 0
Page 711 and 712:
A SENSITIVITY ANALYSIS OF ADAPTIVE
Page 713 and 714:
elationships can be found that rela
Page 715 and 716:
Fig. 2: Percentage of bone volume w
Page 717 and 718:
APPLICATION OF REACTION-DIFFUSION W
Page 719 and 720:
AIRFLOW VENTILATION THROUGH HUMAN M
Page 721 and 722:
solve all the governing equations.
Page 723 and 724:
Fig. 4 Streamlines through the osti
Page 725 and 726:
MOLECULAR DYNAMICS SIMULATIONS FOR
Page 727 and 728:
COARSE-GRAINED MOLECULAR DYNAMICS S
Page 729 and 730:
DESIGN AND STRUCTURAL EVALUATION OF
Page 731 and 732:
Figure 2 shows the optimal unit-cel
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ENUM (MPa) 100 90 80 70 60 50 40 30
Page 735 and 736:
vivo menisco-tibial kinematics duri
Page 737 and 738:
Loading the fully extended knee wit
Page 739 and 740:
is also subject to variation due to
Page 741 and 742:
environment in comparison to fixed
Page 743 and 744:
4. RESULTS AND DISCUSSION Convergen
Page 745 and 746:
Because of the orthotropic assumpti
Page 747 and 748:
3D RECONSTRUCTION OF STENTED PORCIN
Page 749 and 750:
Fluid model. The final configuratio
Page 751 and 752:
Table 1: Computed slice measurement
Page 753 and 754:
ANALYSIS OF THE EFFECT OF CONSIDERI
Page 755 and 756:
For all these models, C1 = µ/2, µ
Page 757 and 758:
the difference in percentage betwee
Page 759 and 760:
A COMPUTATIONAL METHOD TO ESTIMATE
Page 761 and 762:
C10, C01 and d were taken from [10]
Page 763 and 764:
4. RESULTS Fig. 2 shows the results
Page 765 and 766:
COMPUTATIONAL AND EXPERIMENTAL MODE
Page 767 and 768:
data using commercial software (Mim
Page 769 and 770:
vitro (40 vs 34%), at the expense o
Page 771 and 772:
FINITE ELEMENT ANALYSES OF IN VIVO
Page 773 and 774:
The non-linear behaviour of the art
Page 775 and 776:
Figure 6. Constant-life diagram for
Page 777 and 778:
Optimal acceleration adjustment to
Page 779 and 780:
, , , ,
Page 781 and 782:
The vertical force bump observed du
Page 783 and 784:
NEURAL NETWORK-BASED PREDICTION OF
Page 785 and 786:
3. MATERIAL AND METHODS 3.1 Experim
Page 787 and 788:
from subjects S1, S2, S3, S5, and S
Page 789 and 790:
APPLICATION OF A MODIFIED ELASTIC F
Page 791 and 792:
h and h being the thickness of the
Page 793 and 794:
0.3 were used for the flat surface
Page 795 and 796:
simulations of the mechanical respo
Page 797 and 798:
50000 images have been acquired. Th
Page 799 and 800:
Fig.1 Modules of the proposed capsu
Page 801 and 802:
5. CONCLUSION This paper describes
Page 803 and 804:
dependent on the implementation of
Page 805 and 806:
joint computer model was driven wit
Page 807 and 808:
otation. The AP laxity test showed
Page 809 and 810:
A COMPUTATIONAL MODEL OF THE GROWTH
Page 811 and 812:
where n p is the number of prolifer
Page 813 and 814:
Hypertrophic columnar cartilage 0.2
Page 815 and 816:
SIMULATION OF DAILY LIVING MOVEMENT
Page 817 and 818:
otations were kept at zero, since t
Page 819 and 820:
cavity (van der Helm, 1994). Howeve
Page 821 and 822:
Solving Overconstrained Kinematic i
Page 823 and 824:
3.3. Muscles Muscles are modelled a
Page 825 and 826:
5. DISCUSSION A musculoskeletal num
Page 827 and 828:
EFFECT OF OSCILATORY FLOW ON MORPHO
Page 829 and 830:
dimensionless frequency . With the
Page 831 and 832:
Wntsignaling, J Clin Invest., 2006,
Page 833 and 834:
Maximization (EM) algorithm witch e
Page 835 and 836:
4. RESULTS: n 1 2 x f ( x ; )
Page 837 and 838:
5. CONCLUSION In this work, a semi-
Page 839 and 840:
allow cell construct image inspecti
Page 841 and 842:
formula can be written as a linear
Page 843 and 844:
( ) (4) Poisson‟s ratio was assum
Page 845 and 846:
a) b) c) d) Figure 7 Validation: a)
Page 847 and 848:
DEVELOPMENT OF A NEW COMPUTATIONAL
Page 849 and 850:
The ScanIP wizard creates the new i
Page 851 and 852:
Fig. 5: Computer experiments: poste
Page 853 and 854:
A BIOMECHANICAL CONCEPT FOR CONSTRU
Page 855 and 856:
Figure 3. Construction of the radia
Page 857 and 858:
6. REFERENCES 1. Lees, S., A study
Page 859 and 860:
from cadaver surgeries were recreat
Page 861 and 862:
mean resection parameters and the p
Page 863 and 864:
5. DISCUSSION This study proposes a
Page 865 and 866:
simulations are evaluated by quanti
Page 867 and 868:
improvement of the shoulder prosthe
Page 869 and 870:
13. Coley B., Jolles B. M., Farron
Page 871 and 872:
simulations. Implicit in this setup
Page 873 and 874:
assigned zero fluid pressure bounda
Page 875 and 876:
the efficacy of predicting cellular
Page 877 and 878:
Another important function of the l
Page 879 and 880:
The insert (Fig. 3) is the part aga
Page 881 and 882:
changes due to the testing conditio
Page 883 and 884:
3. IN VIVO MEASURED LOAD COMPONENTS
Page 885 and 886:
anthropometric data - a data set fo
Page 887 and 888:
COMPUTATIONAL MODELING OF HIGHLY PO
Page 889 and 890:
objects smaller than one tenth of a
Page 891 and 892:
as 221.5 MPa. This value is more th
Page 893 and 894:
Macrostress and Macrostrain Finite
Page 895 and 896:
3.2. Extraction of individual artic
Page 897 and 898:
Unique strain patterns were observe
Page 899 and 900:
poroviscoelastic simulation of the
Page 901 and 902:
anchorage of the cartilage into a p
Page 903 and 904:
load of 0.5 N) resulted in a 55 kPa
Page 905 and 906:
properties as well as protect the h
Page 907 and 908:
Dynamic cell seeding combines two c
Page 909 and 910:
order (PB). The particles adhered (
Page 911 and 912:
2. D. Wendt, A. Marsano, M. Jakob,
Page 913 and 914:
2. Only a few high-level clinical s
Page 915 and 916:
A quasi-static analysis was perform
Page 917 and 918:
e increased by using stiffer or tig
Page 919 and 920:
Despite the importance of taking th
Page 921 and 922:
Table 2: Score chart presented to t
Page 923 and 924:
We conclude that the model develope
Page 925 and 926:
presented system - parallelization
Page 927 and 928:
image is projected to the subsequen
Page 929 and 930:
6. CONCLUSIONS The presented in the
Page 931 and 932:
first simulation uses data provided
Page 933 and 934:
Table 1: Models used in this study.
Page 935 and 936:
direction at knee extension, placin
Page 937 and 938:
3. METHODS 3.1. Model of heat trans
Page 939 and 940:
condition before and after heating.
Page 941 and 942:
during daily activities reported in
Page 943 and 944:
samples of brain tissue were extrac
Page 945 and 946:
5. DETERMINING MECHANICAL PROPERTIE
Page 947 and 948:
2001, Vol. 38 (4), 335-345. 8. Vela
Page 949 and 950:
chamber [4]. After obtaining the va
Page 951 and 952:
4. RESULTS 4.2 Surface and solid me
Page 953:
7. ACKNOWLEDGMENTS Financial fundin
Page 956 and 957:
affect crack penetration into osteo
Page 958 and 959:
Therefore, in order to examine the
Page 960 and 961:
3. Mischinski, S., Ural, A., 2011,
Page 962 and 963:
esearchers. The power of a finite-e
Page 964 and 965:
figure 2, we can determine the node
Page 966 and 967:
architecture, Muscle & Nerve, 2004,
Page 968 and 969:
ensure good short-term and long-ter
Page 970 and 971:
Table I - Micromotion results at th
Page 972 and 973:
COMBINED BONE-IMPLANT FIXATION: A P
Page 974 and 975:
FRICTIONAL PROPERTIES OF OSTEOARTHR
Page 976 and 977:
With the following boundary conditi
Page 978 and 979:
pressures higher than normal contac
Page 980 and 981:
1. ABSTRACT DYNAMIC PRESSURE RESPON
Page 982 and 983:
quasi-static solution, and both pos
Page 984 and 985:
(excluding the cadaveric validation
Page 987 and 988:
AN ANALYTICAL MODEL TO INVESTIGATE
Page 989 and 990:
K sh = 2. 3E sh 2 ( ) 2 1 2 1−ν
Page 991 and 992:
Fig. 7 modeling the oblique impact
Page 993 and 994:
A NON-LINEAR BIPHASIC MODEL FOR THE
Page 995 and 996:
system, it is convenient to write t
Page 997 and 998:
only with very small damping parame
Page 999 and 1000:
A PARAMETERIZED FE MODEL FOR SIMULA
Page 1001 and 1002:
the study of Polikeit et al. [10].
Page 1003 and 1004:
There are obvious limitations to ou
Page 1005 and 1006:
Abnormal stresses are often cited a
Page 1007 and 1008:
4. RESULTS The methods used to meas
Page 1009 and 1010:
that muscle imbalance associated wi
Page 1011 and 1012:
BIOCHEMICAL MODEL TO PREDICT THE ON
Page 1013 and 1014:
3.1 Model description The regulator
Page 1015 and 1016:
[3] Shier D., 2001, Hole’s Human
Page 1017 and 1018:
Biomechanics of Human Gluteal Tissu
Page 1019 and 1020:
information. Based on the indentati
Page 1021 and 1022:
t 1 ⎧⎪ ⎫ 2 2 ⎪ ττττ ( t
Page 1023 and 1024:
REFERENCES 1. Gefen A., Gefen N., L
Page 1025 and 1026:
analysis of the large-scale human m
Page 1027 and 1028:
λ σ = σ (8) act isom f f 0 ⋅
Page 1029 and 1030:
In the absence of membranes, the mu
Page 1031 and 1032:
predicted. This is possible for mod
Page 1033 and 1034:
-7.2 mN. The average value of the m
Page 1035:
efore the joint moment reaches zero
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ARUP; ISBN: 978-0-9562121-5-3 - CMBBE 2012 - Cardiff University

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