ARUP; ISBN: 978-0-9562121-5-3 - CMBBE 2012 - Cardiff University

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6 CONCLUSION It is a feasible way to apply muscle forces calculated with the IS model to a FE model. Even though loading with muscle forces is intrinsically more realistic and allows for complex motions with different conditions of the human, loading with a follower load and an additional pure moment is a feasible means to simulate simplified postures. 7 ACKNOWLEDGMENTS This study was supported by the China Scholarship Council. 8 REFERENCE [1] Solomonow M, Zhou BH, Harris M, Lu Y, Baratta RV. The ligamento-muscular stabilizing system of the spine. Spine (Phila Pa 1976). 1998;23:2552-62. [2] Goel VK, Kong W, Han JS, Weinstein JN, Gilbertson LG. A combined finite element and optimization investigation of lumbar spine mechanics with and without muscles. Spine (Phila Pa 1976). 1993;18:1531-41. [3] Arjmand N, Gagnon D, Plamondon A, Shirazi-Adl A, Lariviere C. Comparison of trunk muscle forces and spinal loads estimated by two biomechanical models. Clin Biomech (Bristol, Avon). 2009;24:533-41. [4] Zander T, Rohlmann A, Calisse J, Bergmann G. Estimation of muscle forces in the lumbar spine during upper-body inclination. Clin Biomech (Bristol, Avon). 2001;16 Suppl 1:S73-80. [5] Rohlmann A, Bauer L, Zander T, Bergmann G, Wilke HJ. Determination of trunk muscle forces for flexion and extension by using a validated finite element model of the lumbar spine and measured in vivo data. J Biomech. 2006;39:981-9. [6] Kim K, Lee SK, Kim YH. The biomechanical effects of variation in the maximum forces exerted by trunk muscles on the joint forces and moments in the lumbar spine: a finite element analysis. Proc Inst Mech Eng H. 2010;224:1165-74. [7] 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 (Phila Pa 1976). 1999;24:1003-9. [8] Shirazi-Adl A, Parnianpour M. Load-bearing and stress analysis of the human spine under a novel wrapping compression loading. Clin Biomech (Bristol, Avon). 2000;15:718-25. [9] Rohlmann A, Zander T, Rao M, Bergmann G. Applying a follower load delivers realistic results for simulating standing. J Biomech. 2009;42:1520-6. [10] Rohlmann A, Zander T, Rao M, Bergmann G. Realistic loading conditions for upper body bending. J Biomech. 2009;42:884-90. [11] de Zee M, Hansen L, Wong C, Rasmussen J, Simonsen EB. A generic detailed rigid-body lumbar spine model. J Biomech. 2007;40:1219-27. [12] Nolte LP, Panjiabi MM, Oxland TR. Biomechanical properties of lumbar spinal ligaments. Clinical Implant Materials,Advancesin Biomaterials Elsevier, Heidelberg. 1990;9:663-8. [13] Han KS, Zander T, Taylor WR, Rohlmann A. An enhanced and validated generic 5
thoraco-lumbar spine model for prediction of muscle forces. (in press) [14] Sham ML, Zander T, Rohlmann A, Bergmann G. Effects of the rib cage on thoracic spine flexibility. Biomed Tech (Berl). 2005;50:361-5. [15] Zander T, Rohlmann A, Bergmann G. Influence of different artificial disc kinematics on spine biomechanics. Clin Biomech (Bristol, Avon). 2009;24:135-42. [16] Zhu R, Cheng L, Yu Y, Zander T, Chen B, Rohlmann A. Comparison of four reconstruction methods after total sacrectomy: a finite element study. (submitted). [17] Standring S, Ellis H, Healy JC, Johnson D, Williams A. 39th edition of Gray's Anatomy. 2008. [18] Wilke H, Neef P, Hinz B, Seidel H, Claes L. Intradiscal pressure together with anthropometric data--a data set for the validation of models. Clin Biomech (Bristol, Avon). 2001;16 Suppl 1:S111-26. 6
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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
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parameters necessaries to use this
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F1 and Mtwo were directly related t
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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 294 and 295: 8. CONCLUSIONS Unsurprisingly, the
Page 296 and 297: COMPARISON OF DIFFERENT LOADING CON
Page 298 and 299: Figure 1 Finite element model of th
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
Page 344 and 345: processing methods need to be devel
Page 346 and 347: 3. METHODS 3.1 Experimental Method
Page 348 and 349: 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,
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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
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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
Page 549 and 550:
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
Page 561 and 562:
could quantify the initial structur
Page 563 and 564:
expansion of a stent, a metallic sc
Page 565 and 566:
immediately after stent expansion a
Page 567 and 568:
6. ACKNOWLEDGMENT This research is
Page 569 and 570:
Deformation of the arterial surface
Page 571 and 572:
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
Page 579 and 580:
Furthermore, the values are spread
Page 581 and 582:
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
Page 589 and 590:
during mouth closing and chewing. O
Page 591 and 592:
BIOMECHANICAL MODELING OF THE HUMAN
Page 593 and 594:
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
Page 603 and 604:
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
Page 627 and 628:
NUMERICAL SIMULATIONS OF FATIGUE FO
Page 629 and 630:
Figure 1. Scheme of the two approac
Page 631 and 632:
Figure 3. On the left, alternating
Page 633 and 634:
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
Page 639 and 640:
9. Ito S, Ivancic PC, Panjabi MM, C
Page 641 and 642:
[Ntsinjana et al., 2011], commonly
Page 643 and 644:
impedances were maintained within p
Page 645 and 646:
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
Page 657 and 658:
iomechanical response of the leg to
Page 659 and 660:
algorithm has to be integrated into
Page 661 and 662:
to a modification in the tooth disp
Page 663 and 664:
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
Page 669 and 670:
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
Page 685 and 686:
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
Page 701 and 702:
1 - Compute the centre of the botto
Page 703 and 704:
(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
Page 709 and 710:
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
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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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