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

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TOWARDS A WAVELET BASED MEDICAL IMAGE ENHANCEMENT PROCEDURE 1. ABSTRACT M. Pinheiro 1 , F. Martins 2 and J.L. Alves 3 In this work we present a comparative study between three of the most relevant Wavelet-based image enhancement algorithms in the literature and apply them in the denoising of phantom head Modified Shepp-Logan medical images. The results obtained corroborate the conclusions drawn in [12], however is does not seem to be the best approach for Wavelet-based image denoising. 2.INTRODUCTION Wavelet analysis provides a time or space-scale representation of signals that has found in the last few decades a wide range of applications in areas such as physics, signal and image processing, applied mathematics, among others. The basic idea of the Wavelet Transform is to locally decompose the signal in contributions belonging to different scales [1]. This representation unfolds the time-space and frequency and enables the spatial localization of relevant short lasting signal events. In order to accomplish that, two parameters are needed, one to handle the frequency or scale a and other to manipulate the time or space b. Given the values of parameters a and b there can be defined a set of analysing wavelets by applying a series of dilations and translations to a single base wavelet (or mother wavelet
spatial length of a time limited waveform that enables not only a local analysis but also a multi-scale analysis of the signal [3]. The computation of the CWT across all scales and positions is computationally unfeasible, thus for practical purposes, a discretized version of the CWT is calculated over discrete values of a and b [3]. The most common choice for the scaling and translation parameters are
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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
Page 179 and 180: and angular rates were registered b
Page 181 and 182: former, there were assumed the foll
Page 183 and 184: delivered dynamic support, which pr
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 192 and 193: at which microdamage originates. Fo
Page 194 and 195: 4. RESULTS The load response varied
Page 196 and 197: current study to explore the effect
Page 198 and 199: implant correctly from the finite e
Page 200 and 201: (a) (b) (c) (d) (e) Figure 3. The s
Page 202 and 203: (a) (b) Figure 6. The meshed model
Page 204 and 205: (a) (b) Figure 9. Cumulative probab
Page 206 and 207: NUMERICAL EVALUATION AND MEDICAL CO
Page 208 and 209: compared by overlaying the real dat
Page 210 and 211: four sample patient data, outcomes
Page 212 and 213: A POROELASTIC APPROACH FOR AN OPEN
Page 214 and 215: where indexes U, P refer to the unk
Page 216 and 217: RESULTS As a preliminary test, a 0.
Page 218 and 219: BIOMECHANICAL BEHAVIOR OF CANCELLOU
Page 220 and 221: cement acts perfectly, therefore it
Page 222 and 223: cancellous bone of natural joints a
Page 224 and 225: COMPUTATIONAL MODELING OF TANGLED A
Page 226 and 227: The centers of the simulated cells
Page 228 and 229: untangled, the local fiber displace
Page 232 and 233: however at each decomposition scale
Page 234 and 235: the MATLAB software (for the Modifi
Page 236 and 237: A FLUID STRUCTURE INTERACTION MODEL
Page 238 and 239: hyperelastic based on available exp
Page 240 and 241: t [ms] 30 70 160 220 270 Pressure [
Page 242 and 243: 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
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Figure 1: A three-step process simu
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The validation process employed on
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FLUID-STRUCTURE INTERACTION ANALYSI
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The coupled SQA model and the conve
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Point P7, located at the toe of the
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THE INFLUENCE OF UNCERTAIN ANATOMIC
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Figure 3 exemplifies for intradisca
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8. CONCLUSIONS Unsurprisingly, the
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COMPARISON OF DIFFERENT LOADING CON
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Figure 1 Finite element model of th
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6 CONCLUSION It is a feasible way t
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FROM CELL CONTRACTILITY TO CURVATUR
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4. MODEL When cells adhere on a sub
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organisation. Understanding the pri
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PREOPERATIVE PLANNING SUPPORT SYSTE
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[9]. Stenosis of 25, 45, 65 and 85
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Fig. 1:Dependent and independent va
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1. ABSTRACT Local strain measuremen
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around 100µm (halfway through the
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sampling points at different cross
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CLASSIFICATION OF PHYSICAL ACTIVITY
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induces a vertical alignment of the
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accelerations combination). However
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line under translation. Information
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In this study, we apply a meshless
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used the PAC constitutive constants
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1006031) is gratefully acknowledged
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improvements were seen in both grou
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Pre-augmentation Position 1, V=3mL
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5. ACKNOWLEDGEMENTS Funding for thi
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the hemodynamics in cerebral aneury
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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
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6. REFERENCES 1. Ganz, R., Parvizi,
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NUMERICAL IDENTIFICATION OF THE PER
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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
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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
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and estimate in vivo tissue strains
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tendon has a larger moment arm abou
Page 555 and 556:
Song, H. M., Smith, R. L., Longaker
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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
Page 567 and 568:
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
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Figure 3. Relative length change in
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5. Erdemir A, Sibole S. Open Knee:
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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
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catheterization mean measurements (
Page 607 and 608:
the different virtual surgical desi
Page 609 and 610:
1. ABSTRACT DIGITAL ULTRASOUND DESP
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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
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But, the soft repulsive force can n
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Ratio of adhered PLT a simplificati
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DEGRADATION OF MAGNESIUM ALLOY STEN
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study and the parameter setting can
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Fig. 5. Damage evolution of the thr
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NUMERICAL SIMULATIONS OF FATIGUE FO
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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
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complexity of the vertebrae and sku
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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
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impedances were maintained within p
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6. Pennati G., Corsini C., Cosentin
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analyse the effect that different a
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attached cases this value was highe
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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
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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
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present work is to show the ability
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[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
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3.4 Modeling of the facet joints Th
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The column diagramm of Fig.8 shows
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tool to evaluate the drug distribut
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Figure 3: The mean value of the dos
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INFLUENCE OF KYPHOSIS ON SPINAL LOA
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(a) (b) (c) Fig. 1. The three repre
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etween T6 and T9 with a higher degr
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A COMPARISON BETWEEN STANDARD AND D
Page 689 and 690:
the SB with a 2.5 mm balloon; ii) o
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A TAWSS [Pa] B OSI [Pa] C 0 0.25 0.
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ABSTRACT CONSTITUTIVE MODELLING OF
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20% compression strains were impose
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4. DISCUSSION The limited number of
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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
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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
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A SENSITIVITY ANALYSIS OF ADAPTIVE
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elationships can be found that rela
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Fig. 2: Percentage of bone volume w
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APPLICATION OF REACTION-DIFFUSION W
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AIRFLOW VENTILATION THROUGH HUMAN M
Page 721 and 722:
solve all the governing equations.
Page 723 and 724:
Fig. 4 Streamlines through the osti
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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
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vivo menisco-tibial kinematics duri
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Loading the fully extended knee wit
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is also subject to variation due to
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environment in comparison to fixed
Page 743 and 744:
4. RESULTS AND DISCUSSION Convergen
Page 745 and 746:
Because of the orthotropic assumpti
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3D RECONSTRUCTION OF STENTED PORCIN
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Fluid model. The final configuratio
Page 751 and 752:
Table 1: Computed slice measurement
Page 753 and 754:
ANALYSIS OF THE EFFECT OF CONSIDERI
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For all these models, C1 = µ/2, µ
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the difference in percentage betwee
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A COMPUTATIONAL METHOD TO ESTIMATE
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C10, C01 and d were taken from [10]
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4. RESULTS Fig. 2 shows the results
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COMPUTATIONAL AND EXPERIMENTAL MODE
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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
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Optimal acceleration adjustment to
Page 779 and 780:
, , , ,
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The vertical force bump observed du
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NEURAL NETWORK-BASED PREDICTION OF
Page 785 and 786:
3. MATERIAL AND METHODS 3.1 Experim
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from subjects S1, S2, S3, S5, and S
Page 789 and 790:
APPLICATION OF A MODIFIED ELASTIC F
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h and h being the thickness of the
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0.3 were used for the flat surface
Page 795 and 796:
simulations of the mechanical respo
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50000 images have been acquired. Th
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Fig.1 Modules of the proposed capsu
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5. CONCLUSION This paper describes
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dependent on the implementation of
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joint computer model was driven wit
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otation. The AP laxity test showed
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A COMPUTATIONAL MODEL OF THE GROWTH
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where n p is the number of prolifer
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Hypertrophic columnar cartilage 0.2
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SIMULATION OF DAILY LIVING MOVEMENT
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otations were kept at zero, since t
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cavity (van der Helm, 1994). Howeve
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Solving Overconstrained Kinematic i
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3.3. Muscles Muscles are modelled a
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5. DISCUSSION A musculoskeletal num
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EFFECT OF OSCILATORY FLOW ON MORPHO
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dimensionless frequency . With the
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Wntsignaling, J Clin Invest., 2006,
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Maximization (EM) algorithm witch e
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4. RESULTS: n 1 2 x f ( x ; )
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5. CONCLUSION In this work, a semi-
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allow cell construct image inspecti
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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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