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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
- Page 139 and 140: Stress [Pa] 4 3 2 1 0 Mean stress A
- Page 141 and 142: REFERENCES [1] A.M. Bratt-Leal, R.L
- Page 143 and 144: y exposure to interstitial fluid sh
- Page 145 and 146: according to (Eq. 2), nor averaged
- Page 147 and 148: emoved the oscillations partially a
- Page 149 and 150: static load and a dynamic load. A s
- Page 151 and 152: positive effect of the number of ac
- Page 153 and 154: pathways and their interactions tha
- Page 155 and 156: applications, the need for accuracy
- Page 157 and 158: avoid violating the initial geometr
- Page 159 and 160: 6. CONCLUSION The examples of appli
- Page 161 and 162: Fig. 1 Semicircular canal structure
- Page 163 and 164: 4. RESULT Fig. 6 FSI model of semic
- Page 165 and 166: 6. ACKNOWLEDGEMENT This research wa
- Page 167 and 168: ods to the biocompatible plastic po
- Page 169 and 170: Table 1: Analysis conditions Static
- Page 171 and 172: [3] Brantigan, J. W., Steffee, A. D
- Page 173 and 174: femoral head fracture, the femoral
- Page 175 and 176: Fig 3. Schematic drawing of the ste
- Page 177 and 178: 6. CONCLUSION Fig 7. Analysis resul
- Page 179 and 180: and angular rates were registered b
- Page 181 and 182: former, there were assumed the foll
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- Page 185 and 186: insertion of provisional restoratio
- Page 187 and 188: Figure 4: Implant displacements obt
- Page 189: 5. DISCUSSION AND CONCLUSION Initia
- Page 193 and 194: (a) (b) Fig. 1: (a) 2D axisymmetric
- Page 195 and 196: The difference in pile-up between f
- Page 197 and 198: Developing a Realistic 3D Model of
- Page 199 and 200: (a) (b) Figure 1. original femur an
- Page 201 and 202: Figure 5. Histogram indicating the
- Page 203 and 204: 6. THE DETERMINISTIC STRESS ANALYSI
- Page 205 and 206: 8. REFERENCES 1.Heever D.J., Scheff
- Page 207 and 208: found that the age-adjusted annual
- Page 209 and 210: initialization. Using built-in and
- Page 211 and 212: challenge to the way medical doctor
- Page 213 and 214: with a distinctive set of mechanica
- Page 215 and 216: The constitutive parameters were ch
- Page 217 and 218: ACKNOWLEDGEMENTS The first author w
- Page 219 and 220: prostheses. The stress-shielding ef
- Page 221 and 222: of-freedom. The numerical-experimen
- Page 223 and 224: 2009, 33, 6, 1597-601. 6. Arciero,
- Page 225 and 226: was observed several millimeters aw
- Page 227 and 228: • Case 3: Untangled Fibers. Five
- Page 229 and 230: Table 2. Stresses on a portion of t
- Page 231 and 232: spatial length of a time limited wa
- Page 233 and 234: Mihçak et al. in 1999 proposed a d
- Page 235 and 236: present work were compared given th
- Page 237 and 238: ignored the influence of the blood
- Page 239 and 240: since they are much stiffer than th
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heart valve closure fluid dynamics,
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during the root canal preparation.
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4. RESULTS AND DISCUSSION 4.1 Flexi
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for Mtwo is explained by the high d
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it has been shown how the effect of
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For the IVD model, NBS condition ma
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7. REFERENCES 1. Malandrino A., Noa
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primary knee implants with loading
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curve for each sensor which varied
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ange reported by a previous cemente
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implantation [1-4] assume the femur
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4 3 2 1 a b Figure 2: a) Restrained
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6. REFERENCES 1. Tissakht, M., Ahme
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The modeling of soft tissue structu
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The growth laws for a day, adopted
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al., (2008) and thereby adopting th
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3. METHODS When modelling the mecha
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v J 2 é l ˆ1 2 ù å ê b b b 1b
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9. REFERENCES 1. Limbert G. A mesos
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models have been developed. Because
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elements algorithm from Adams solve
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7. Vigouroux, L., Domalain, M. and
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of re-stenosis in either of the ana
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employed. A fully developed pulsati
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Therefore, it is concluded that the
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a pure moment load of 7.5 Nm to sim
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Figure 4: Bootstrapped confidence i
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2004;29(16):1755-1763. 7. Panjabi M
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3. MATERIALS AND METHODS In order t
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Intradiscal pressure of L4-L5 disc
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thoraco-lumbar spine model for pred
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are not only sensitive to the bioch
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growth observed in-vitro. 5. RESULT
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PF running under DFG contract numbe
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pathological swallowing trajectorie
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is generated. The real tracheal sec
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Even if the error between FE and re
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measuring strain at different level
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Figure 2 microscopic image of fasci
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understanding of the mechanical beh
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computed from acceleration frequenc
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to represent a body-segments-coordi
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need for temporal normalisation. In
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2-D MESHLESS ALGORITHM FOR MODELLIN
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3.2 Verification of meshless algori
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a) 5. DISCUSSION In this study, we
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PATIENT-SPECIFIC MODELLING OF VERTE
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cement volume fraction (CVF), the p
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Fig. 2: The relative overall organ
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CHARACTERIZATION OF THE RUPTURE SIT
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3.2 Hemodynamic simulation In order
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In addition to the analyses of aver
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FINITE ELEMENT ANALYSIS OF MICROSCO
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An algorithm was written (Matlab, R
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Figure 4 - Correlation between FE a
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FINITE ELEMENT MODELS OF THE INTERV
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eduction in height of the L1L2 disc
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taken from the image data, a summar
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A FINITE ELEMENT COMPARISON OF LOCK
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cortical thickness only). The value
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Both types of plating produced larg
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1. ABSTRACT PARAMETER IDENTIFICATIO
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flexion range where the other 5 DOF
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(which, in fact, is associated with
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STRESS EVALUATION DURING ANGIOGENES
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size. The model is used for two dim
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vessels from the pre-existing vascu
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It is well established that trabecu
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5. RESULTS The orthotropic elastic
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8. Taheri, N. S.; Blicblau, A. S. &
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surfaces with two crisscross layers
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spinal behavior except the maximal
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8. REFERENCES 1. Frobin W., Brinckm
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problem is time consuming, which li
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Figure 2: Pipeline to create a pred
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6. REFERENCES 1. Belenguer Querol L
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clarify the factors that cause aneu
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dashed line is the pressure distrib
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Model reduction methods in nonlinea
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approximated by the so-called Ritz
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error at a fixed time step by a red
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3. MATERIALS & METHODS FE-models of
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(p=0.175) bone density between the
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GLOBE-FIXATION SYSTEM FOR ANIMAL EY
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Fig. 2 A schematic view that shows
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6. REFERENCES 1. Dada V. K., and Si
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ANALYSIS OF HUMAN SPINAL CURVATURE
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spinal loading [16]. Muscle forces
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Table 4. RMS value based on exercis
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YOUNGER KOREAN MALE AND FEMALE’S
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spinal loads during manual lifting
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symmetrical hand loads. The raw EMG
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COMPUTATIONAL STUDY OF THE EFFECTS
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600 nm 2 /molecule. Furthermore, th
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degraded, cell shape becomes less o
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EVOLUTION OF ADHESION PROPERTIES IN
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3.1.3 Budding and Growth We assume
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g [-] 9 8 7 6 5 4 3 2 1 FLOplus vs.
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Figure 4: Typical representation of
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joint. The purpose of this study is
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expected. In our graph it is possib
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our result (4.58 BW) is in agreemen
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treatment for the end stage disease
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double limb support position of the
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REFERENCES Valkenburg, H. 1980, "Cl
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High tibial osteotomy (HTO) surgery
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Figure3. Mean EKAM during the stanc
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6. REFERENCES 1. www.arc.org.uk/art
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moments of inertia or eigenvalues w
- Page 459 and 460:
Data has been collected from two pl
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of all abilities. Each player has t
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A simple computational framework to
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determined. The higher ratio value
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understand and implement in the sen
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PREDICTION OF INTERNAL SPINE CURVAT
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A Cartesian axis system was defined
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adiological parameters describing d
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cavity functions, nasal cavity wall
- Page 484 and 485:
In the vestibule, the flow velocity
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AN ENHANCED DISCRETE ELEMENT ANALYS
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h a =acetabular cartilage d = joint
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GHz, 3 GB RAM). FE models required
- Page 492 and 493:
3. Anderson, A.E., et al., Validati
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Currently, diagnosis of cam FAI is
- Page 496 and 497:
denoted by H(.). An ensemble compri
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differences of individual cam femur
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Am. 2009 Nov;91 Suppl 6: 42-58. 15.
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the intrinsic problems of this very
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established. An ideal model used fo
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4. CONCLUSION Comparisons with clas
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Within its application in the seat
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The overall dimensions 10 of the mu
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(a) (b) Fig.8: Seat pressure distri
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Estimating Dynamic properties of lo
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Cook’s equation (Eqn 1). In this,
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4.1 Fracture types from experiments
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EXPERIMENTAL DETERMINATION OF DIVER
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Applying Hernandez-Corvo procedure
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5. NUMERICAL MODEL Once the data wa
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DOWNSIZING THE VEPTR DESIGN TO AVOI
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surfaces on the 3D distal extension
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Fig. 7 -Von Mises stress distributi
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INFLUENCE OF BIOMECHANICAL FACTORS
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Three pieces of software are utiliz
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4.2 Partial thrombosis versus Paten
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CHRONOPHOTOGRAPHIC VISUALIZATION FO
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perform better when there is moveme
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For each pixel on screen we first c
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THE EFFECT OF PARTIAL MENISCECTOMY
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3.3 Finite Element Model 3.3.1 Mesh
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Table 3: Medial and lateral peak pr
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NONUNIFORM MOTION IN THE ACHILLES T
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Fig. 2. Significantly greater tissu
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2008, 30, 1677-84. 2. Longo, U. G.,
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AN IN VIVO METHOD TO QUANTIFY BIOME
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Most current image segmentation alg
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y our Human Subjects Committee and
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SPATIAL AND TEMPORAL VARIATION OF V
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Half symmetry along the axial direc
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Post-stenting Post-relaxation Systo
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3D OPTICAL RECONSTRUCTION TECHNIQUE
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Fig 1: Image of experimental system
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DISCUSSION 3D reconstruction of ste
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MODELLING ADULT SUBVENTRICULAR NEUR
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3. MATERIALS AND METHODS Spatially,
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4. RESULTS AND DISCUSSION Solutions
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OPEN KNEE: CAPACITY TO REPRODUCE AN
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4. RESULTS & DISCUSSION As expected
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6. REFERENCES 1. Homyk A, Orsi A, W
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FORCE RATIO IN CHEWING MUSCLES AFTE
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ecause muscles can not produce comp
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7. CONCLUSION This study describes
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The assessment of the intra-articul
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model to create an efficient simula
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5. Brittenden J. and Robinson P., I
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imaging. Basing on the image datase
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The geometry of bioimplant is saved
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The results presented in Tab.1 were
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physiopathology and to create a rep
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patient, flow conditions drive its
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Computational Mechanics 48: 277-291
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2. INTRODUCTION Ultrasound imaging
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pyramid. This pyramid is built by u
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In this paper two multi-scale metho
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continuum approaches; in initial wo
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In order to have a better understan
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In Fig.3, the distribution of the a
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In this study, a biodegradable mate
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ecoiled. Finally, both expanded sam
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5. DISCUSSION AND CONCLUSION The pr
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typically occurs in cases of very l
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4. RESULTS AND DISCUSSION Results i
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6. REFERENCES 1. Krankenberg H, Sch
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INTRODUCTION The cervical spine is
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Active State 1 0.9 0.8 0.7 0.6 0.5
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thoracic spine. Stemper et al. [29]
- Page 640 and 641:
PATIENT-SPECIFIC EVALUATION OF PULM
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3.3 Working hypothesis The blood wa
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QLPA [cc/s] Fig. 4 - Left: Flow cur
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Parametric Study On The Effect Of M
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Figure 1: Views of the Knee model F
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contact area is very different for
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1. ABSTRACT PATIENT-SPECIFIC FE MOD
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which is closed to the value used b
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A FULLY NONLINEAR FINITE ELEMENT MO
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present at this stage as we only wa
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4.2 Force driven problem. The appli
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A finite element analysis of skull
- Page 666 and 667:
Part Material property Face Elastic
- Page 668 and 669:
4.2 Case NG09 The numerical impact
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MBS - Model for the Estimation of F
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0 -15 -10 -5 0 5 10 15 3.3 Modeling
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Torque[Nm] Force [N] Force [N] 1000
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DRUG RELEASE IN CORONARY BIFURCATIO
- Page 678 and 679:
elease and absorption of the hepari
- Page 680 and 681:
6. REFERENCES 1. M.C. Morice, P.W.
- Page 682 and 683:
essential [5]. The following compon
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a moderate kyphotic curvature (50°
- Page 686 and 687:
Acknowledgement: This project was f
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considered. It has been proposed on
- Page 690 and 691:
geometries, such as the intersectio
- Page 692 and 693:
Figure 5. Comparison of the access
- Page 694 and 695:
muscle fascicle forces from EMG, ki
- Page 696 and 697:
Figure 1. Range of parameter CCE fo
- Page 698 and 699:
2. Arjmand, N. and Shirazi-Adl, A.,
- Page 700 and 701:
challenge due to its anisotropic mu
- Page 702 and 703:
z y x z z x (c) y x (d) Figure 1. 3
- Page 704 and 705:
6. REFERENCES 1. R. Eberlein, G. A.
- Page 706 and 707:
same rating in the tests, but they
- Page 708 and 709:
solver the optimization cycle conti
- Page 710 and 711:
of the our design space, the head h
- Page 712 and 713:
The main goal of this study is to c
- Page 714 and 715:
distribution, with an average diffe
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esult. 5. ACKNOWLEDGEMENTS The auth
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Fig. 1 Snapshots of self-assembly p
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sinus might be of great importance
- Page 722 and 723:
The variation of flow rate with tim
- Page 724 and 725:
6. CONCLUSION In CFD simulations, t
- Page 726 and 727:
experimental results. Langevin-dyna
- Page 728 and 729:
addition, Mg 2+ is also a particle
- Page 730 and 731:
3. METHODS The main advantage of th
- Page 732 and 733:
For each design three different out
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QUANTIFICATION OF 3D, IN-VIVO MENIS
- Page 736 and 737:
4. RESULTS All of the MR images of
- Page 738 and 739:
same slice for 2D analysis for repe
- Page 740 and 741:
CONSIDERATION OF MULTIPLE ACTIVITY
- Page 742 and 743:
A complete heterogeneous orthotropi
- Page 744 and 745:
Figure 2 - Predominant material ori
- Page 746 and 747:
13. Ashman R. et al., A continuous
- Page 748 and 749:
studies provide evidence that the e
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and 2b illustrate the WSS magnitude
- Page 752 and 753:
6. CONCLUSION A detailed 3D micro-C
- Page 754 and 755:
estimated the morphological modific
- Page 756 and 757:
thickness [12]. Boundary conditions
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Innovation (references TIN2010-2099
- Page 760 and 761:
ehavior. Other researchers have mea
- Page 762 and 763:
The combination of JC and H allows
- Page 764 and 765:
1. Brock K. K., Hollister S. J., Da
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palliated with a surgical procedure
- Page 768 and 769:
3.3 Computational study The 3D mode
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model versatility. The disagreement
- Page 772 and 773:
fatigue behaviour of Nitinol periph
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and the plaque inner surface, the d
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ox in Fig. 7, are the nearest to th
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The double differentiation with dig
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second derivatives ( ) of . Joint
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motion. It showed new insight of th
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predicting hand postures. In some c
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Fig. 2. Hand characteristic paramet
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5. ACKNOWLEDGMENTS We would like to
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assumes a constant pressure in the
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Serina et al. [8] who presented exp
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opposed to the relative velocity be
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NEW FUNCTIONALITIES FOR ENDOSCOPIC
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3.2 Image Processing A system that
- Page 800 and 801:
As mentioned before, it is importan
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VALIDATION OF SPECIMEN SPECIFIC ROB
- Page 804 and 805:
After testing, the properties of pa
- Page 806 and 807:
Figure 2: Average of predicted laxi
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well suited for analyzing the behav
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modulation models like the proposed
- Page 812 and 813:
4. COMPUTATIONAL IMPLEMENTATION As
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Endocrinology. 2002. 174:R1-R6. 4.
- Page 816 and 817:
The goal of the present numerical s
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The GHRF of the abduction and flexi
- Page 820 and 821:
6. REFERENCES 1. Bedi, A., Dines, J
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3. METHODS 3.1. Bones The shoulder
- Page 824 and 825:
and teres minor rest inactive throu
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3. D. Karlsson and B. Peterson: Tow
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involved taking into account the co
- Page 830 and 831:
4. RESULTS AND DISCUSSION We observ
- Page 832 and 833:
Gaussian Mixture Model (GMM) for ma
- Page 834 and 835:
3.2. EM algorithm: We use EM with M
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Fig2. Dice coef. mdb019, line1: ROI
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A BIOREATOR TO BIOMECHANICAL AND BI
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Finite Element simulation of human
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Figure 2 Fragment of model and used
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Table 2 Thickness and mechanical pr
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C. Pailler-Mattéi H. Zahouani, Ana
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segmentation to FE analysis. This c
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Fig. 3: Neutral implant micromotion
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axis, respectively. The last step w
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organ’s tissue anisotropy, and b)
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4. RESULTS The results of the algor
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ASSESSMENT OF SURGICAL VARIABILITY
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Crest axis - a best fit line to the
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Table 2. Variability of measured su
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1. ABSTRACT Simulation of the bone
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living [13, 14]. Table 1. Load weig
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Nevertheless, it is worth noting th
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ROLE OF ANATOMICAL REPRESENTATION O
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configuration. During random placem
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cell distribution is considered. In
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LIPS CONTRACTION SIMULATION AND FOR
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Fig. 1 - Finite element mesh of the
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5. DISCUSSION Table1 - Maximum forc
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1. ABSTRACT LOADS ON THE LUMBAR SPI
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and extension angles of up to 12.3
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[24] Dreischarf M, Rohlmann A, Berg
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The tensile test of brittle, highly
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stresses were evaluated. The indivi
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7. ACKNOLEDGMENTS This work was sup
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known about the local stresses expe
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was modelled as linear elastic, whe
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model, strain patterns varied acros
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PARAMETRIC ANALYSIS OF AN ENGINEERE
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properties. The whole model was see
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4.3 Osteochondral defect treatment
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CELL SEEDING OPTIMIZATION IN 3D SCA
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The seeding process was simulated u
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5. DISCUSSION The critical issue in
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EFFICIENCY AND COMFORT OF KNEE BRAC
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order to reach the dimensions of a
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noteworthy that the contact pressur
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PREOPERATIVE ANALYSIS OF THE STABIL
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a) Guide design 1 b) Guide design 2
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5 4 3 2 1 Guide1 Figure 2: The resu
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TRABECULAR BONE REMODELING SIMULATI
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4. PARALELLIZATION OF THE MESH GENE
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data necessary to define the overla
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FORWARD DYNAMICS MOVEMENT SIMULATIO
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defined between each meniscus eleme
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The z-axis is aligned with the tibi
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CALCULATION OF THE HEAT POWER REQUI
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The strain dependent permeability,
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Optimizing the heat dissipation of
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TOWARDS DETERMINING MECHANICAL PROP
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experiment are presented here. Prio
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Figure 6. Indentation of sheep brai
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COMPUTATIONAL FLUID DYNAMICS OF COM
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3.3 Surface and solid mesh reconstr
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4.3.2 Wall shear stress Fig. 3 show
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MESHLESS MODELING OF MICROCRACK GRO
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In the Element-Free Galerkin (EFG)
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Hence, the most important role of t
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THREE DIMENSIONAL ELECTROMECHANICAL
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is that complex problems are reduce
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This model was used to indicate mus
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MICROMOTION ANALYSIS OF PRESS FIT R
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Figure 2 - Geometric model used to
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2. Takwale V.J., Trail I.A. and Sta
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operative situation where the impla
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model has shown good agreement with
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4. RESULTS Figure 1 shows the mean
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6. CONCLUSION In this study, fricti
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of 24 shell elements, while the int
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A sensitivity study was carried out
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the coup. The results of the invest
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parameters of impact such as maximu
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Impact duration (Tp) can be obtaine
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oth deformations resulting from the
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3. MATHEMATICAL MODELLING According
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3.2 Coupled elastic-biphasic model
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In Figure 2 (left) the comparison b
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The aim of the present study was tw
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4. RESULTS The axial compressive lo
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STUDY OF CONTACT MECHANISMS IN THE
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object in all cases. Using the regi
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(a) (b) Fig. 4. Maximum von Mises s
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in individuals with patellofemoral
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matrix components. Several studies
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concentration of molecular factors
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[17] Garzón-Alvarado D. A., Garcí
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2. INTRODUCTION Analyzing mechanica
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1 1 2 the volumetric part of the st
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seated in a upright MRI machine and
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SIGNIFICANCE OF FASCIA FOR MECHANIC
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associated with the volumetric chan
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For the numerical simulation of the
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MUSCLE MODEL COMPOSED BY MOTOR UNIT
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each movement speed. The speed was
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develop moments in the joint and th