Attention! Your ePaper is waiting for publication!
By publishing your document, the content will be optimally indexed by Google via AI and sorted into the right category for over 500 million ePaper readers on YUMPU.
This will ensure high visibility and many readers!
Your ePaper is now published and live on YUMPU!
You can find your publication here:
Share your interactive ePaper on all platforms and on your website with our embed function
ARUP; ISBN: 978-0-9562121-5-3 - CMBBE 2012 - Cardiff University
ARUP; ISBN: 978-0-9562121-5-3 - CMBBE 2012 - Cardiff University
ARUP; ISBN: 978-0-9562121-5-3 - CMBBE 2012 - Cardiff University
You also want an ePaper? Increase the reach of your titles
YUMPU automatically turns print PDFs into web optimized ePapers that Google loves.
line under translation. Information Processing Letters, 1991, Vol. 38, 12-127.
line under translation. Information Processing Letters, 1991, Vol. 38, 12-127.
2-D MESHLESS ALGORITHM FOR MODELLING OF SOFT TISSUE UNDERGOING FRAGMENTATION AND LARGE DEFORMATION: VERIFICATION AND PERFORMANCE EVALUATION Xia Jin 1 , Guiyong Zhang 1 , Grand. R. Joldes 1 , King. H. Yang 2 , Xin Jin 2 , Pierre-Y. Rohan 3 , Karol Miller 1 , Adam Wittek 1 1. ABSTRACT In injury biomechanics and surgery simulation, modelling of soft tissues/soft organs is generally performed using (non-linear) finite element procedures. However, the accuracy of finite element method deteriorates when the mesh undergoes fragmentation and distortion due to damage/cutting and large deformations caused by injury and surgical intervention. Therefore, in this study, we developed a meshless algorithm with visibility criterion for fragmentation modeling. The algorithm provides robust solution for predicting soft tissue responses for large strains and discontinuities due to fragmentation. Verification against the well-established non-linear finite element procedures available in ABAQUS confirms the accuracy of our meshless algorithm with visibility criterion for fragmentation modelling. Evaluation of the algorithm performance through modelling of the pia-arachnoid tissue samples subjected to rupture-causing elongation indicates that the overall deformation within the sample predicted by the algorithm qualitatively agrees with that observed in the previously published experimental results. 2. INTRODUCTION The ability to model fragmentation of soft tissues due to rupture/cutting is of immense importance for impact and injury biomechanics as well as for biomechanics for medicine. Potential applications include computer evaluation of car crash safety performance through modelling of traumatic injury to car occupants and pedestrians as well as simulators for surgical training and surgery planning. So far, in both impact/injury biomechanics and surgery simulation, non-linear finite element procedures have been a method of choice [1-6]. However, the finite element method becomes unstable and its accuracy deteriorates when the finite element computational grid (i.e. finite element mesh) undergoes fragmentation and distortion due to rupture/damage of the analysed continuum [7]. 1 Intelligent Systems for Medicine Laboratory, School of Mechanical and Chemical Engineering, The <strong>University</strong> of Western Australia, 35 Stirling Highway, Crawley-Perth 6009, Western Australia, Australia 2 Bioengineering Center, Wayne State <strong>University</strong>, 818 W. Hancock, Detroit, MI 48201, USA 3 Ecoles des Mines de Saint-Etienne, France (study conducted during internship at Intelligent Systems for Medicine Laboratory, The <strong>University</strong> of Western Australia)
- 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 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 and 512:
Indenter Stroke [mm] Muscle Force [
- Page 513 and 514:
Objectives Long bone failure charac
- 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
Inappropriate
Loading...
Inappropriate
You have already flagged this document.
Thank you, for helping us keep this platform clean.
The editors will have a look at it as soon as possible.
Mail this publication
Loading...
Embed
Loading...
Delete template?
Are you sure you want to delete your template?
DOWNLOAD ePAPER
This ePaper is currently not available for download.
You can find similar magazines on this topic below under ‘Recommendations’.