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

Recommendations

Info

(a) (b) Fig.8: Seat pressure distribution beneath one thigh measurement (a) and simulation (b) Comparing the changes between the two states an increased pressure in the frontal part of the thigh can be observed for the simulation as well as for the measurement. Background is the stiffening of the muscle tissue due to muscle contraction. This first step shows that the selected modeling technique and the material properties are adequate for implementation of the muscle activity in the CASIMIR model. 6. CONCLUSION With respect to the simulation results for the isolated muscle and the model of the complete thigh it was shown that the invented modeling approach enables the possibility for implementing the muscle activation in the human body model CASIMIR. The next step will be the qualitative validation procedure with the thigh resp. the complete human body model. Later this process will have to be enhanced to consider internal values as e.g. the stress and strain states to fulfill the requirements for clinical relevance to apply the model for medical investigations. 7. REFERENCES Gravity Muscle contracted 1. Siefert A., et al.: Virtual optimisation of car passenger seats: … International Journal of Industrial Ergonomics, Vol. 38: pp. 410-424, 2008 2. Siefert A., et al.: Detailed 3D muscle approach for computing dynamic loads on the lumbar spine for implant design. World Congress on Biomechanics, Singapore 2010 3. Böl, M. et al.: A new approach for validation of skeletal muscle modelling using MRI data. CMBBE (2011), Vol. 47, pp. 591-601 4. ABAQUS (Software), Version 6.10, Abaqus Inc., Providence, RI, USA, www.abaqus.com 5. Hedenstierna, S., et al.: Evaluation of a combination of continuum and truss finite elements in a model of passive and active muscle tissue, CMBBE (2008), Vol. 11, pp. 627-639 6. Fung, Y.C.: Biomechanics: mechanical properties of living tissues. Springer Publishing, ISBN 0387979476, New York 1993 7. Van Loocke, et al.: A validated model of passive muscle in compression. Journal of Biomechanics (2006), Vol. 39, pp. 2999-3009 8. Blemker S.S., et al.: A 3D model of muscle reveals the causes of non-uniform strains in the biceps brachii. Journal of Biomechanics (2005), Vol. 38, pp. 657-665 9. Siebert, T. et al.: Work partitioning of transversally loaded muscle experimentation and simulation. CMBBE, accepted 10. Siebert, T. et al.: A 3D-geometric model for the deformation of a transversally loaded muscle. Journal of Theoretical Biology (2012), Vol. 298,pp. 116-121
Objectives Long bone failure characteristics under impact bending: an in-depth study Mike WJ Arun, A Chawla, S Mukherjee, Debasis Sahoo, Sourabh Barouah The objective of the current work is to exper- imentally study the tolerance of long bones bending under impact and to understand the mechanism which causes their failure. Materials & Methods Twelve isolated human humerus were tested in three point bending mode in the anterior to posterior direction. Bone specimens were “potted” with fixtures using a quick setting bone cement (Poly Methyl Methacrylate, PM- MA). Figure 1 Drop tower setup An instrumented drop tower was used to impact the bone. The drop tower consists of a car- riage of mass 31 kg that can fall freely through guided slots. The height of the drop can be ad- justed to vary impact velocity. Results Figure 2 shows the force vs time plot for the experiments. All plots are plotted till the fracture initiation as observed in high-speed videos. Indian Institute of Technology, Delhi, India 1.5 m drop 1.0 m drop 0.5 m drop Average Figure 2 Force-Time plots The average load taken by the bones for both 1.5 m and 1.0 m drop was around 2.7 kN, while for 0.5 m drop it was 1.9 kN . Thus there was a 30% increase in maximum load at higher drop heights (i.e. higher strain rates), which is a well-documented behavior of bones. In 1.0 m drop tests, the force vs time plots had two peaks before failure. This phenomenon was due to the inertial effect. For 1.0 m drop, the average time to fracture was 0.57 ms and for 1.5 m drop, it was 0.3 ms. The slope of the force history during the first peak was observed to be the highest (20.1 kN/ms) in the 1.5 m drop case while the 0.5 m drop tests recorded the lowest (10.4 kN/ms). This shows an increase in bone stiffness with increase in impact velocity and signifies the strain rate dependen- cy of bones. It was observed that the average time for fracture propagation across the tensile side of bending was 0.1 ms, while across the compressive side was 0.8 ms. This is due to the asymmetric strength of bone in tension and compression. Eleven fractures were oblique and one fracture was transverse in na- ture. Eight of the oblique fractures were of the pattern as shown in Figure 3.a, where there was a crack diversion in the compression side of impact. These fractures are observed only in 1.5 m and 1.0 m drop experiments. The other three were of the pattern as shown in Figure 3.b, where there was no crack diversion in the compression side of impact. This pattern is observed only in 0.5 m drop tests. The transverse fracture is shown in Figure 3.c. b. Oblique fracture with no crack diversion Figure 3 Observed fracture types a. Oblique fracture with crack diversion c. Transverse fracture The fracture event captured by high speed camera is shown in Figure 4. a. at time=0.26ms b. at time=0.37ms c. at time=1.1ms Figure 4 Fracture captured by high speed camera Conclusion A detailed experimental work had been carried out to study the tolerance and the mechanism of fracture in long bones. Interesting observa- tions have been made, which were not previ- ously reported. This information can be used effectively to derive material models that can be used in finite element simulations.
Page 1 and 2:
The Proceedings of the 10 th Intern
Page 3 and 4:
Install Adobe Reader 8 or 9 (http:/
Page 5 and 6:
Content: POSTERS: BRAIN: CELL: EVAL
Page 7 and 8:
Modeling of blood flow through a fl
Page 9 and 10:
The mesh generation of the model wa
Page 11 and 12:
Figure6 . The stroke volume data fo
Page 13 and 14:
Digital Subtraction Phonocardiograp
Page 15 and 16:
mobile cart for easy recording in c
Page 17 and 18:
Figure 7. This image shows PCG samp
Page 19 and 20:
Our approach is an improvement in t
Page 21 and 22:
one cements as well as its behaviou
Page 23 and 24:
Typical dimensions of lumbar verteb
Page 25 and 26:
attributed to the change of stiffne
Page 27 and 28:
lifestyle and obesity. In that cont
Page 29 and 30:
T was the temperature in Kelvin and
Page 31 and 32:
sustained tensile strains stimulate
Page 33 and 34:
An approach aiming at determining a
Page 35 and 36:
failure load. 2.4 Simulation of reh
Page 37 and 38:
REFERENCES 1. Vunjak-Novakovic G, A
Page 39 and 40:
3. FIF-BAL BIOREACTOR The FIF devic
Page 41 and 42:
value of p nearest to dqc=0 we cont
Page 43 and 44:
(Wanless, 1999). This low value cou
Page 45 and 46:
3. MATERIALS AND METHODS A CAD mode
Page 47 and 48:
did not allow gap closure. Maximum
Page 49 and 50:
hand, if the IFM is too large, remo
Page 51 and 52:
2. INTRODUCTION Intervertebral disc
Page 53 and 54:
Figure 3. T1 signal enhancement in
Page 55 and 56:
1. ABSTRACT TIP CELLS AT THE TOP: M
Page 57 and 58:
Fig. 1. Schematic overview of the m
Page 59 and 60:
Fig. 3. Image of the amount of VEGF
Page 61 and 62:
THE COMPUTATIONAL MODEL OF DENTAL I
Page 63 and 64:
processing application STL Model Cr
Page 65 and 66:
For the implant/bone interaction as
Page 67 and 68:
ABSTRACT THE IMPACT OF SELECTION BI
Page 69 and 70:
Figure 1: flow chart showing the op
Page 71 and 72:
Figure 2: Time course of cytosolic
Page 73 and 74:
CONSTITUTIVE MODELLING OF THE ANNUL
Page 75 and 76:
it is well known the non-linear nat
Page 77 and 78:
Therefore, we have decided to carry
Page 79 and 80:
EXTRACTION OF PHALANGEAL JOINT PARA
Page 81 and 82:
column vectors of P. Denoting the v
Page 83 and 84:
End i joint angles and length offse
Page 85 and 86:
Validation of Strain Mapping for th
Page 87 and 88:
allows the calculation of strain ma
Page 89 and 90:
RMS error was 0.054 and the strains
Page 91 and 92:
AN APPROACH FOR THE REDUCTION OF TH
Page 93 and 94:
The relation between the time-deriv
Page 95 and 96:
Error in position [mm] Error in pos
Page 97 and 98:
ANALYSIS OF THE INTRAINDIVIDUAL DIF
Page 99 and 100:
Fig.1: Frontal view on all subchond
Page 101 and 102:
[6] M. Bozkurt, B. B. Kentel, G. Ya
Page 103 and 104:
on the actual necessary time needed
Page 105 and 106:
Illustration 2: The initially spher
Page 107 and 108:
cell if it is hardly able to deform
Page 109 and 110:
fit with a reference anatomy in min
Page 111 and 112:
show that patellar mal-positioning
Page 113 and 114:
Experimental and numerical analysis
Page 115 and 116:
stenosis in both simulations and ex
Page 117 and 118:
stented case, corresponding to the
Page 119 and 120:
EVALUATION OF DIFFERENT LOADING CON
Page 121 and 122:
were modeled with identical geometr
Page 123 and 124:
each simulation and the position of
Page 125 and 126:
FINITE ELEMENT MODEL ANALYSIS OF HU
Page 127 and 128:
Figure 1: Maximal principal strains
Page 129 and 130:
Method for classification of porcin
Page 131 and 132:
3.3 Identification of Paths Accordi
Page 133 and 134:
Table. 1. Descriptive Patterns used
Page 135 and 136:
CHARACTERIZING THE MECHANICAL MICRO
Page 137 and 138:
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
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 230 and 231:
TOWARDS A WAVELET BASED MEDICAL IMA
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
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 300 and 301:
6 CONCLUSION It is a feasible way t
Page 302 and 303:
FROM CELL CONTRACTILITY TO CURVATUR
Page 304 and 305:
4. MODEL When cells adhere on a sub
Page 306 and 307:
organisation. Understanding the pri
Page 308 and 309:
PREOPERATIVE PLANNING SUPPORT SYSTE
Page 310 and 311:
[9]. Stenosis of 25, 45, 65 and 85
Page 312 and 313:
Fig. 1:Dependent and independent va
Page 314 and 315:
1. ABSTRACT Local strain measuremen
Page 316 and 317:
around 100µm (halfway through the
Page 318 and 319:
sampling points at different cross
Page 320 and 321:
CLASSIFICATION OF PHYSICAL ACTIVITY
Page 322 and 323:
induces a vertical alignment of the
Page 324 and 325:
accelerations combination). However
Page 326 and 327:
line under translation. Information
Page 328 and 329:
In this study, we apply a meshless
Page 330 and 331:
used the PAC constitutive constants
Page 332 and 333:
1006031) is gratefully acknowledged
Page 334 and 335:
improvements were seen in both grou
Page 336 and 337:
Pre-augmentation Position 1, V=3mL
Page 338 and 339:
5. ACKNOWLEDGEMENTS Funding for thi
Page 340 and 341:
the hemodynamics in cerebral aneury
Page 342 and 343:
4. RESULTS AND DISCUSSION In order
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
Page 350 and 351:
analysis of the tissue mechanics. B
Page 352 and 353:
3. METHODS 3.1 Specimen Preparation
Page 354 and 355:
of five points across the mid mid-c
Page 356 and 357:
equired to replicate the deformatio
Page 358 and 359:
pre-load within the plate (compress
Page 360 and 361:
4. RESULTS The load-deformation beh
Page 362 and 363:
fracture fixation. Medical Engineer
Page 364 and 365:
model. It approximates knee kinemat
Page 366 and 367:
computational cost remains moderate
Page 368 and 369:
Concerning the optimization procedu
Page 370 and 371:
aesthetic recovery. However, in som
Page 372 and 373:
atio experimented by both wounds is
Page 374 and 375:
VARIATION OF MICRO-ARCHITECTURE AND
Page 376 and 377:
osteoporotic (OP). The sample volum
Page 378 and 379:
Figure 4: Mean error in orthotropy
Page 380 and 381:
INVESTIGATION OF CORTICAL SHELL STR
Page 382 and 383:
When creating the degenerated FE mo
Page 384 and 385:
Figure 4. Degeneration sensitivity
Page 386 and 387:
METHODS TO ACCELERATE FINITE ELEMEN
Page 388 and 389:
the “joint” constraints configu
Page 390 and 391:
Figure 4: Absolute prediction error
Page 392 and 393:
EFFECT OF POST TREATMENT FOR MULTIP
Page 394 and 395:
Fig.2 Inlet velocity profile indica
Page 396 and 397:
4.3 WSS results Figure 8 shows the
Page 398 and 399:
approximated by the so-called Ritz
Page 400 and 401:
Figure 2: Viscohyperelastic cube: (
Page 402 and 403:
There is no optimal density-elastic
Page 404 and 405:
Fig. 2 Cut view of FE-model. Shown
Page 406 and 407:
5. Weis JA, Miga MI, Granero-Moltó
Page 408 and 409:
3. SYSTEM DESIGN Sheep eyes, as the
Page 410 and 411:
which provides natural tactile feed
Page 412 and 413:
113:341-342 20. Henderson B. A., Gr
Page 414 and 415:
health area. According to estimates
Page 416 and 417:
Table 1. RMS Value based on subject
Page 418 and 419:
6. REFERENCES 1. http://www.disable
Page 420 and 421:
ehavior [5]. From the viewpoint of
Page 422 and 423:
Fig. 1 Average Male and Female's L4
Page 424 and 425:
4. Deyo, R.A., and Weinstein, J. N.
Page 426 and 427:
geometry of the cell and ECM degrad
Page 428 and 429:
Shown in Fig. 2(b) is a plot of the
Page 430 and 431:
6. REFERENCES 1. Dubin-Thaler B.J.,
Page 432 and 433:
We implemented our individual-based
Page 434 and 435:
3.3.1 Centers of mass Table 1: Base
Page 436 and 437:
average coordination num ber averag
Page 438 and 439:
BIOMECHANICAL ANALYSIS OF THE MUSCU
Page 440 and 441:
of the ligament strain; a linear re
Page 442 and 443:
lengthening, respectively, if compa
Page 444 and 445:
THE EFFECT OF HIGH TIBIAL OSTEOTOMY
Page 446 and 447:
The 3D LiveWire tool was used as an
Page 448 and 449:
Table II: Peak medial and lateral f
Page 450 and 451:
INVESTIGATING CHANGES IN JOINT LOAD
Page 452 and 453:
4. RESULTS Table 1 shows the mean m
Page 454 and 455:
Fig.5 displays the OKS and KOS pre
Page 456 and 457:
Dynamic Touch of Effective Golf Swi
Page 458 and 459:
properties of a golf club and hand
Page 460 and 461:
perturbation in e3 whereas player B
Page 462 and 463: 1. Kim, W., Response to letter to t
Page 464 and 465: configuration.[4] have explained ho
Page 466 and 467: compartments as well as a single mu
Page 468 and 469: 5. Shabana, A.A., Dynamics of multi
Page 470 and 471: Five healthy volunteers (age: 38.3
Page 472 and 473: internal lumbar spinal shape was de
Page 480 and 481: Airflow Simulation of Nasal Cavity
Page 482: temperature [5], and Wbl is the wat
Page 485 and 486: Figure 8. Figure 8(a) illustrates t
Page 487 and 488: Finite element models of the hip ca
Page 489 and 490: 3.2 Finite Element Analysis Followi
Page 491 and 492: 5. DISCUSSION Previous DEA implemen
Page 493 and 494: STATISTICAL SHAPE MODELING OF CAM-T
Page 495 and 496: Thirty-three control femurs (25 mal
Page 497 and 498: asymptomatic subjects 7,9 . The Hot
Page 499 and 500: 6. REFERENCES 1. Ganz, R., Parvizi,
Page 501 and 502: NUMERICAL IDENTIFICATION OF THE PER
Page 503 and 504: 2. METHOD AND NUMERICAL MODEL. 2.1
Page 505 and 506: 1 u dV V u. (Eq. 2) V The permeab
Page 507 and 508: 1. ABSTRACT PASSIVE AND ACTIVE MUSC
Page 509 and 510: presented in figure 2 the simulatio
Page 511: Indenter Stroke [mm] Muscle Force [
Page 515 and 516: the specimens in three point bendin
Page 517 and 518: developing a subject-specific finit
Page 519 and 520: Models used in the past, mostly bas
Page 521 and 522: In this work it is presented the de
Page 523 and 524: Average Table 1.- Walk average test
Page 525 and 526: angles for the step of 2.28° and 8
Page 527 and 528: insufficiency syndrome (TIS), defin
Page 529 and 530: a) b) c) Fig. 5 - Contact interface
Page 531 and 532: EOS. Among these options, VEPTR has
Page 533 and 534: dissection occurs when blood intrud
Page 535 and 536: mean value of 0.0310 m s -1 . The o
Page 537 and 538: progression. It can in turn contrib
Page 539 and 540: dependent data. They conclude that
Page 541 and 542: found that it is extremely difficul
Page 543 and 544: endering loop is started and the ra
Page 545 and 546: 3.1 Imaging protocol of the knee A
Page 547 and 548: 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
Page 559 and 560: 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
Page 575 and 576:
migrate in a unique fashion to the
Page 577 and 578:
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
Page 585 and 586:
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
Page 597 and 598:
1. ABSTRACT COMPUTER AIDED TUMOR RE
Page 599 and 600:
B. Cutting planes The surgeon defin
Page 601 and 602:
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
Page 653:
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
Page 707 and 708:
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
Page 733 and 734:
ENUM (MPa) 100 90 80 70 60 50 40 30
Page 735 and 736:
vivo menisco-tibial kinematics duri
Page 737 and 738:
Loading the fully extended knee wit
Page 739 and 740:
is also subject to variation due to
Page 741 and 742:
environment in comparison to fixed
Page 743 and 744:
4. RESULTS AND DISCUSSION Convergen
Page 745 and 746:
Because of the orthotropic assumpti
Page 747 and 748:
3D RECONSTRUCTION OF STENTED PORCIN
Page 749 and 750:
Fluid model. The final configuratio
Page 751 and 752:
Table 1: Computed slice measurement
Page 753 and 754:
ANALYSIS OF THE EFFECT OF CONSIDERI
Page 755 and 756:
For all these models, C1 = µ/2, µ
Page 757 and 758:
the difference in percentage betwee
Page 759 and 760:
A COMPUTATIONAL METHOD TO ESTIMATE
Page 761 and 762:
C10, C01 and d were taken from [10]
Page 763 and 764:
4. RESULTS Fig. 2 shows the results
Page 765 and 766:
COMPUTATIONAL AND EXPERIMENTAL MODE
Page 767 and 768:
data using commercial software (Mim
Page 769 and 770:
vitro (40 vs 34%), at the expense o
Page 771 and 772:
FINITE ELEMENT ANALYSES OF IN VIVO
Page 773 and 774:
The non-linear behaviour of the art
Page 775 and 776:
Figure 6. Constant-life diagram for
Page 777 and 778:
Optimal acceleration adjustment to
Page 779 and 780:
, , , ,
Page 781 and 782:
The vertical force bump observed du
Page 783 and 784:
NEURAL NETWORK-BASED PREDICTION OF
Page 785 and 786:
3. MATERIAL AND METHODS 3.1 Experim
Page 787 and 788:
from subjects S1, S2, S3, S5, and S
Page 789 and 790:
APPLICATION OF A MODIFIED ELASTIC F
Page 791 and 792:
h and h being the thickness of the
Page 793 and 794:
0.3 were used for the flat surface
Page 795 and 796:
simulations of the mechanical respo
Page 797 and 798:
50000 images have been acquired. Th
Page 799 and 800:
Fig.1 Modules of the proposed capsu
Page 801 and 802:
5. CONCLUSION This paper describes
Page 803 and 804:
dependent on the implementation of
Page 805 and 806:
joint computer model was driven wit
Page 807 and 808:
otation. The AP laxity test showed
Page 809 and 810:
A COMPUTATIONAL MODEL OF THE GROWTH
Page 811 and 812:
where n p is the number of prolifer
Page 813 and 814:
Hypertrophic columnar cartilage 0.2
Page 815 and 816:
SIMULATION OF DAILY LIVING MOVEMENT
Page 817 and 818:
otations were kept at zero, since t
Page 819 and 820:
cavity (van der Helm, 1994). Howeve
Page 821 and 822:
Solving Overconstrained Kinematic i
Page 823 and 824:
3.3. Muscles Muscles are modelled a
Page 825 and 826:
5. DISCUSSION A musculoskeletal num
Page 827 and 828:
EFFECT OF OSCILATORY FLOW ON MORPHO
Page 829 and 830:
dimensionless frequency . With the
Page 831 and 832:
Wntsignaling, J Clin Invest., 2006,
Page 833 and 834:
Maximization (EM) algorithm witch e
Page 835 and 836:
4. RESULTS: n 1 2 x f ( x ; )
Page 837 and 838:
5. CONCLUSION In this work, a semi-
Page 839 and 840:
allow cell construct image inspecti
Page 841 and 842:
formula can be written as a linear
Page 843 and 844:
( ) (4) Poisson‟s ratio was assum
Page 845 and 846:
a) b) c) d) Figure 7 Validation: a)
Page 847 and 848:
DEVELOPMENT OF A NEW COMPUTATIONAL
Page 849 and 850:
The ScanIP wizard creates the new i
Page 851 and 852:
Fig. 5: Computer experiments: poste
Page 853 and 854:
A BIOMECHANICAL CONCEPT FOR CONSTRU
Page 855 and 856:
Figure 3. Construction of the radia
Page 857 and 858:
6. REFERENCES 1. Lees, S., A study
Page 859 and 860:
from cadaver surgeries were recreat
Page 861 and 862:
mean resection parameters and the p
Page 863 and 864:
5. DISCUSSION This study proposes a
Page 865 and 866:
simulations are evaluated by quanti
Page 867 and 868:
improvement of the shoulder prosthe
Page 869 and 870:
13. Coley B., Jolles B. M., Farron
Page 871 and 872:
simulations. Implicit in this setup
Page 873 and 874:
assigned zero fluid pressure bounda
Page 875 and 876:
the efficacy of predicting cellular
Page 877 and 878:
Another important function of the l
Page 879 and 880:
The insert (Fig. 3) is the part aga
Page 881 and 882:
changes due to the testing conditio
Page 883 and 884:
3. IN VIVO MEASURED LOAD COMPONENTS
Page 885 and 886:
anthropometric data - a data set fo
Page 887 and 888:
COMPUTATIONAL MODELING OF HIGHLY PO
Page 889 and 890:
objects smaller than one tenth of a
Page 891 and 892:
as 221.5 MPa. This value is more th
Page 893 and 894:
Macrostress and Macrostrain Finite
Page 895 and 896:
3.2. Extraction of individual artic
Page 897 and 898:
Unique strain patterns were observe
Page 899 and 900:
poroviscoelastic simulation of the
Page 901 and 902:
anchorage of the cartilage into a p
Page 903 and 904:
load of 0.5 N) resulted in a 55 kPa
Page 905 and 906:
properties as well as protect the h
Page 907 and 908:
Dynamic cell seeding combines two c
Page 909 and 910:
order (PB). The particles adhered (
Page 911 and 912:
2. D. Wendt, A. Marsano, M. Jakob,
Page 913 and 914:
2. Only a few high-level clinical s
Page 915 and 916:
A quasi-static analysis was perform
Page 917 and 918:
e increased by using stiffer or tig
Page 919 and 920:
Despite the importance of taking th
Page 921 and 922:
Table 2: Score chart presented to t
Page 923 and 924:
We conclude that the model develope
Page 925 and 926:
presented system - parallelization
Page 927 and 928:
image is projected to the subsequen
Page 929 and 930:
6. CONCLUSIONS The presented in the
Page 931 and 932:
first simulation uses data provided
Page 933 and 934:
Table 1: Models used in this study.
Page 935 and 936:
direction at knee extension, placin
Page 937 and 938:
3. METHODS 3.1. Model of heat trans
Page 939 and 940:
condition before and after heating.
Page 941 and 942:
during daily activities reported in
Page 943 and 944:
samples of brain tissue were extrac
Page 945 and 946:
5. DETERMINING MECHANICAL PROPERTIE
Page 947 and 948:
2001, Vol. 38 (4), 335-345. 8. Vela
Page 949 and 950:
chamber [4]. After obtaining the va
Page 951 and 952:
4. RESULTS 4.2 Surface and solid me
Page 953:
7. ACKNOWLEDGMENTS Financial fundin
Page 956 and 957:
affect crack penetration into osteo
Page 958 and 959:
Therefore, in order to examine the
Page 960 and 961:
3. Mischinski, S., Ural, A., 2011,
Page 962 and 963:
esearchers. The power of a finite-e
Page 964 and 965:
figure 2, we can determine the node
Page 966 and 967:
architecture, Muscle & Nerve, 2004,
Page 968 and 969:
ensure good short-term and long-ter
Page 970 and 971:
Table I - Micromotion results at th
Page 972 and 973:
COMBINED BONE-IMPLANT FIXATION: A P
Page 974 and 975:
FRICTIONAL PROPERTIES OF OSTEOARTHR
Page 976 and 977:
With the following boundary conditi
Page 978 and 979:
pressures higher than normal contac
Page 980 and 981:
1. ABSTRACT DYNAMIC PRESSURE RESPON
Page 982 and 983:
quasi-static solution, and both pos
Page 984 and 985:
(excluding the cadaveric validation
Page 987 and 988:
AN ANALYTICAL MODEL TO INVESTIGATE
Page 989 and 990:
K sh = 2. 3E sh 2 ( ) 2 1 2 1−ν
Page 991 and 992:
Fig. 7 modeling the oblique impact
Page 993 and 994:
A NON-LINEAR BIPHASIC MODEL FOR THE
Page 995 and 996:
system, it is convenient to write t
Page 997 and 998:
only with very small damping parame
Page 999 and 1000:
A PARAMETERIZED FE MODEL FOR SIMULA
Page 1001 and 1002:
the study of Polikeit et al. [10].
Page 1003 and 1004:
There are obvious limitations to ou
Page 1005 and 1006:
Abnormal stresses are often cited a
Page 1007 and 1008:
4. RESULTS The methods used to meas
Page 1009 and 1010:
that muscle imbalance associated wi
Page 1011 and 1012:
BIOCHEMICAL MODEL TO PREDICT THE ON
Page 1013 and 1014:
3.1 Model description The regulator
Page 1015 and 1016:
[3] Shier D., 2001, Hole’s Human
Page 1017 and 1018:
Biomechanics of Human Gluteal Tissu
Page 1019 and 1020:
information. Based on the indentati
Page 1021 and 1022:
t 1 ⎧⎪ ⎫ 2 2 ⎪ ττττ ( t
Page 1023 and 1024:
REFERENCES 1. Gefen A., Gefen N., L
Page 1025 and 1026:
analysis of the large-scale human m
Page 1027 and 1028:
λ σ = σ (8) act isom f f 0 ⋅
Page 1029 and 1030:
In the absence of membranes, the mu
Page 1031 and 1032:
predicted. This is possible for mod
Page 1033 and 1034:
-7.2 mN. The average value of the m
Page 1035:
efore the joint moment reaches zero
show all

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

Create successful ePaper yourself

Delete template?

Save as template?