constitutive modeling of an electrospun tubular scaffold
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ArticleTitle Constitutive modeling of an electrospun tubular scaffold used for vascular tissue engineering
Article Sub-Title
Article CopyRight Springer-Verlag Berlin Heidelberg
(This will be the copyright line in the final PDF)
Journal Name Biomechanics and Modeling in Mechanobiology
Corresponding Author Family Name Hu
Particle
Given Name Jin-Jia
Suffix
Division Department of Biomedical Engineering
Organization National Cheng Kung University
Address #1 University Rd., Tainan, 701, Taiwan
Division Medical Device Innovation Center
Organization National Cheng Kung University
Address Tainan, Taiwan
Email [email protected]
Schedule
Received 6 October 2014
Revised
Accepted 16 December 2014
Abstract In this study, we sought to model the mechanical behavior of an electrospun tubular scaffold previously
reported for vascular tissue engineering with hyperelastic constitutive equations. Specifically, the scaffolds
were made by wrapping electrospun polycaprolactone membranes that contain aligned fibers around a
mandrel in such a way that they have microstructure similar to the native arterial media. The biaxial stress-
stretch data of the scaffolds made of moderately or highly aligned fibers with three different off-axis fiber
angles (30 , 45 , and 60 ) were fit by a phenomenological Fung model and a series of structurally
motivated models considering fiber directions and fiber angle distributions. In particular, two forms of
fiber strain energy in the structurally motivated model for a linear and a nonlinear fiber stressstrain
relation, respectively, were tested. An isotropic neo-Hookean strain energy function was also added to the
structurally motivated models to examine its contribution. The two forms of fiber strain energy did not
result in significantly different goodness of fit for most groups of the scaffolds. The absence of the neo-
Hookean term in the structurally motivated model led to obvious nonlinear stress-stretch fits at a greater
axial stretch, especially when fitting data from the scaffolds with a small . Of the models considered, the
Fung model had the overall best fitting results; its applications are limited because of its phenomenological
nature. Although a structurally motivated model using the nonlinear fiber stressstrain relation with theneo-Hookean term provided fits comparably as good as the Fung model, the values of its model parameters
exhibited large within-group variations. Prescribing the dispersion of fiber orientation in the structurally
motivated model, however, reduced the variations without compromising the fits and was thus considered
to be the best structurally motivated model for the scaffolds. It appeared that the structurally motivated
models could be further improved for fitting the mechanical behavior of the electrospun scaffold; fiber
interactions are suggested to be considered in future models.
Keywords (separated by '-') Constitutive modeling - Hyperelasticity - Electrospun scaffolds - Fung model - Structurally motivated
models - Mechanical properties
Footnote Information Electronic supplementary material The online version of this article (doi:10.1007/s10237-014-0644-y)
contains supplementary material, which is available to authorized users.
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Biomech Model Mechanobiol
DOI 10.1007/s10237-014-0644-y
O R I G I N A L PA P E R
Constitutive modeling of an electrospun tubular scaffoldused for vascular tissue engineering
Jin-Jia Hu
Received: 6 October 2014 / Accepted: 16 December 2014
Springer-Verlag Berlin Heidelberg 2014
Abstract In this study, we sought to model the mechan-1
ical behavior of an electrospun tubular scaffold previously2
reported for vascular tissue engineering with hyperelastic3
constitutive equations. Specifically, the scaffolds were made4
by wrapping electrospun polycaprolactone membranes that5
contain aligned fibers around a mandrel in such a way that6
they have microstructure similar to the native arterial media.7
The biaxial stress-stretch data of the scaffolds made of mod-8
erately or highly aligned fibers with three different off-axis9
fiber angles (30, 45, and 60) were fit by a phenom-10
enological Fung model and a series of structurally motivated11
models considering fiber directions and fiber angle distri-12
butions. In particular, two forms of fiber strain energy in13
the structurally motivated model for a linear and a nonlin-14
ear fiber stressstrain relation, respectively, were tested. An15
isotropic neo-Hookean strain energy function was also added16
to the structurally motivated models to examine its contri-17
bution. The two forms of fiber strain energy did not result18
in significantly different goodness of fit for most groups of19
the scaffolds. The absence of the neo-Hookean term in the20
structurally motivated model led to obvious nonlinear stress-21
stretch fits at a greater axial stretch, especially when fitting22
data from the scaffolds with a small . Of the models con-23
sidered, the Fung model had the overall best fitting results;24
Electronic supplementary material The online version of this
article (doi:10.1007/s10237-014-0644-y) contains supplementary
material, which is available to authorized users.
J.-J. Hu (B)
Department of Biomedical Engineering, National Cheng Kung
University, #1 University Rd., Tainan 701, Taiwan
e-mail: [email protected]
J.-J. Hu
Medical Device Innovation Center, National Cheng Kung University,
Tainan, Taiwan
its applications are limited because of its phenomenological 25
nature. Although a structurally motivated model using the 26
nonlinear fiber stressstrain relation with the neo-Hookean 27
term provided fits comparably as good as the Fung model, the 28
values of its model parameters exhibited large within-group 29
variations. Prescribing the dispersion of fiber orientation in 30
the structurally motivated model, however, reduced the varia- 31
tions without compromising the fits and was thus considered 32
to be the best structurally motivated model for the scaffolds. 33
It appeared that the structurally motivated models could be 34
further improved for fitting the mechanical behavior of the 35
electrospun scaffold; fiber interactions are suggested to be 36
considered in future models. 37
Keywords Constitutive modeling Hyperelasticity 38
Electrospun scaffolds Fung model Structurally motivated 39
models Mechanical properties 40
1 Introduction 41
Scaffolds, cells and stimulating signals, generally referred 42
to as the tissue engineering triad, are the key components 43
for making a functional tissue-engineered construct. Specif- 44
ically, the three-dimensional, porous scaffolds not only pro- 45
vide a surface for cells to adhere and grow, but also serve 46
as a template to guide matrix formation. Manipulation of 47
the microstructure of the scaffolds thus has potential to con- 48
trol the microstructure of resulting tissues and hence their 49
mechanical properties. The latter are particularly important 50
for the functionality of load-bearing tissues. 51
Among the numerous polymer processing techniques, 52
electrospinning has been widely used to fabricate scaffolds. 53
Electrospun scaffolds are attractive because of their high 54
porosity, large surface area-to-volume ratio, and nano-scale 55
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fibrous structure, similar to the features of native extracel-56
lular matrix. In general, only a simple, inexpensive setup is57
required for electrospinning (Ramakrishna 2005). Although58
the orientations of electrospun fibers are typically random,59
aligned electrospun fibers can be achieved with special60
collecting mechanisms (Teo and Ramakrishna 2006). The61
aligned electrospun fibers are capable of providing contact62
guidance to cultured cells(Bashur et al. 2006;Wang et al.63
2011; Yang et al. 2005) and can be used to control the64
microstructure of engineered tissues.65
Very few tubular scaffolds that have helically oriented66
fibers were found in the literature although the helical orga-67
nization is often observed in native arteries (Rhodin 1977)68
and appears to reflect on their complex mechanical behav-69
iors. We recently made such a tubular scaffold by wrapping70
electrospun membranes that contain aligned fibers around a71
mandrel(Hu et al. 2012). In this study, we sought to model72
the biaxial stress-stretch data of the tubular scaffold made73
of moderately or highly aligned fibers with different off-axis74
fiber angles using hyperelastic constitutive equations. There75
have been only a few attempts to establish constitutive rela-76
tions of electrospun scaffolds(Courtney et al. 2006;De Vita77
etal. 2006; Nerurkar et al.2007,2008). Forthe interest of bet-78
ter scaffold design, there is a need to model their mechanical79
behavior with constitutive equations. A proper constitutive80
equation with predictive capability can serve as a guideline81
for making scaffolds that have desired mechanicalproperties.82
We first evaluated a two-dimensional (2-D) phenomeno-83
logical Fung model. As the fibrous structure of the tubular84
scaffold suggests that their mechanical behavior canbe quan-85
tified by structural approaches previously applied for soft tis-86
sues (Billiar and Sacks 2000;Dahl et al. 2008;Lanir 1979,87
1983), a series of structurally motivated models considering88
fiber directions and fiber angle distributions were used to fit89
the data. In particular, two forms of fiber strain energy in the90
structurally motivated model for a linear and a nonlinear fiber91
stressstrain relation, respectively, were tested. An isotropic92
neo-Hookean strain energy function was added to the struc-93
turally motivated models to examine its contribution. Finally,94
the influence of prescribing the dispersion of fiber orientation95
on the modeling was examined.96
2 Methods97
2.1 Electrospun tubular scaffolds98
The details of construction and characterization of the tubu-99
lar scaffold are described inHu et al.(2012). Briefly, scaf-100
fold membranes consisting of moderately aligned fibers and101
highly aligned fibers, denoted as membrane MA and mem-102
brane HA, respectively, were prepared by collecting electro-103
spun fibers on a grounded rotating drum at linear tangential104
A
B
Fig. 1 Schematic diagram showing how a tubular scaffold with an off-axis fiber angle was constructed
velocity of 5.3 and 8 m/s, respectively. Rectangular pieces of 105
membrane MA(or HA) were cut in such a way that the angle 106
between the predominant fiber direction and the long axis 107
(i.e.,) is 30, 45, or 60. Two pieces with the same fiber 108
angle were stacked so that thefiber array of each piecealigned 109
symmetrically along the long axis of the rectangle, forming 110
an axisymmetric membrane. The axisymmetric membrane 111
was then wrapped around a mandrel, resulting in a tubular 112
scaffold with an off-axis fiber angle(either 30, 45 or60; 113
see Fig.1). In total, six groups of five tubular scaffolds each, 114
denoted as Tube MA-30 (membrane-), Tube MA-45, Tube 115
MA-60, Tube HA-30, Tube HA-45, and Tube HA-60, were 116
constructed and mechanically characterized (Hu et al. 2012). 117
The pressure-diameter and the pressure-axial load data pre- 118
viously reported were used along with the unloaded dimen- 119
sions of the scaffold to calculate the mean circumferential 120
and axial Cauchy stresses andzz , respectively, as, 121
=Pa
h, zz =
F+ a2 P
h(2a + h)(1) 122
where P is the applied transmural pressure, F is the axial 123
load imposed by extending the scaffold (Hu et al. 2012), 124
a and h are the deformed inner radius and wall thickness, 125
respectively. Note that the scaffolds were treated as a thin- 126
walled tube and thus rr andzz rr. 127
2.2 Hyperelastic constitutive modeling 128
The biaxial mechanical properties of the tubular scaffolds 129
were quantified by hyperelastic constitutive models. Consis- 130
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Correspondingly, for the c_LFM,207
= c2
1
1
42z
208
+ 2
2
2
R( )
k2f 1
sin2
d (12)209
zz = c2z
1 1
4z2
210
+ 2z
2
2
R( )
k2f 1
cos2
d, (13)211
and for the c_NLFM,212
= c2
1
1
42z
+ 2
2
2
R( )
k1
2f 1
213
exp
k2
2f 1
2sin2
d (14)214
zz = c2z
1 1
4z2
+ 2z
2
2
R( )
k12f 1
215
exp
k2
2f 1
2cos2
d. (15)216
Finally, the influence of prescribing the value ofdin the217
c_NLFM on the goodness of fit was examined. For the Tube218
MAand the Tube HA, d= 0.3 and d= 0.1 were prescribed,219
respectively.220
The best-fit values of the parameters of each model for221
each scaffold were determined using nonlinear regression of222
its biaxial data. This was accomplished by using a modi-223
fied fminsearch function (Matlab) to minimize the objective224
function:225
e =
Ni=1
Theory Exp
mean
Exp
2
i
+
Theoryz Expz
mean
Expz
2
i
(16)226
whereNis the number of data points, and superscripts The-227
ory and Exp denote theoretically calculated and experimen-228
tally determined values, respectively. The goodness of fit is229
presented as the coefficient of determination, r
2
.230
Given the deformation and the values of the model para-231
meters of each model for each scaffold, the stored strain232
energy in the scaffold can be determined. The value of stored233
strain energy at = 1.04 & z = 1.00, which can be234
used as a circumferential stiffness index, was calculated.235
The higher the stored strain energy, the stiffer the scaffolds236
in the circumferential direction. Also, the stiffness in the237
stretching directions, defined as K (=SE
) = 2 W
E2and238
Kzz zz (=SzzEzz
) = 2 W
E2zz, whereSandSzz are components of239
the second PiolaKirchhoff stress tensor in directionsand 240
z, respectively, was determined and the ratio of the two
i.e., 241
max
Kzzz zK
, KKzzz z
was calculated at = z = 1.02 as 242
an anisotropy index. The definition of stiffness was selected 243
for the simplicity of derivation; note that the second Piola 244
Kirchhoff stress and the Green strain are work conjugate. 245
The biaxial stretches, at which the stored strain energy and 246the stiffness ratio were calculated, were chosen simply to be 247
within the range of stretching in the mechanical testing as a 248
constitutive model is considered valid only for the conditions 249
under which it is derived. For the Fung model, in particu- 250
lar, another anisotropy index defined as min
c1+c3c2+c3
, c2+c3
c1+c3
251
(Bellini et al. 2011) was also calculated. 252
2.3 Statistical analysis 253
Because all of the constitutive models were used to fit the 254
data of each scaffold, one-way repeated-measures ANOVA 255
with HolmSidak post hoc testing was used for comparing 256
the goodness of fit among models. Results are reported as 257
mean standard deviation. 258
3 Results 259
Figure2 illustrates representative biaxial stress-stretch data 260
from each group of the scaffolds and the corresponding fits of 261
theFung model.The Fung model fitsthe biaxial stress-stretch 262
data well for all groups of the scaffolds. The best-fit values of 263
the parameters of the Fung model and the associated good- 264
ness of fit for each group of the scaffolds are listed in Table 1; 265
details for each scaffold can be found in Supplemental 266
Table 1. 267
Figure 3 shows the same representative biaxial stress- 268
stretch data from each group and the corresponding fits of 269
the LFM, the NLFM, and the c_LFM. Note that the scales 270
in the plots were changed to better illustrate the differences 271
between models. The fitting curves for the 3-parameter LFM 272
and the 4-parameter NLFM were close to each other. Of par- 273
ticular interest, the LFM and the NLFM led to obvious non- 274
linear stress-stretch fits, especially for the Tube MA-30 and 275
the Tube HA-30 that were subjected to axial stretching. The 276
nonlinear fits were not observed for the c_LFM, however. 277
The best-fit values of the parameters of the LFM, the NLFM, 278
and the c_LFM and the associated goodness of fit for each 279
group of the scaffolds are listed in Table 2; details for each 280
scaffold can be found in Supplemental Tables 24. The esti- 281
mated value ofkin the LFMincreased asincreased for both 282
theTubeMA andthe Tube HA.Similarly, the estimated value 283
ofk1in the NLFM increased with increasing . In particular, 284
the value ofk in the LFM or the value ofk1 in the NLFM 285
estimated by fitting data from the Tube MA was greater than 286
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Constitutive modeling of an electrospun tubular scaffold
0.96 0.98 1.00 1.02 1.04 1.06
Circ.
Ca
uchyStress(kPa)
0
200
400
600
800 Fung modelExp
0.96 0.98 1.00 1.02 1.04 1.06
AxialC
auchyStress(kPa)
0
200
400
600
800
1000
1200
1400
Fung model
Exp
0.96 0.98 1.00 1.02 1.04 1.06
Circ.
Cau
chyStress(kPa)
0
200
400
600
800 Fung modelExp
0.96 0.98 1.00 1.02 1.04 1.06
AxialCa
uchyStress(kPa)
0
200
400
600
800
1000
1200
1400
Fung model
Exp
0.96 0.98 1.00 1.02 1.04 1.06
Circ.
CauchyStress(kPa)
0
200
400
600
800 Fung modelExp
0.96 0.98 1.00 1.02 1.04 1.06
AxialCauchyStress(kPa)
0
200
400
600
800
1000
1200
1400
Fung model
Exp
A
Tube
MA-30
Tube
MA-45
Tube
MA-60
B
C
Circ. Stretch
AxialCauchy
Stress(kPa)
0
200
400
600
800
1000
1200
1400
Fung model
Exp
Circ. Stretch
Circ.
Cauchy
Stress(kPa)
0
200
400
600
800 Fung modelExp
0.96 0.98 1.00 1.02 1.04 1.060.96 0.98 1.00 1.02 1.04 1.06
D
Tube
HA-30
Fig. 2 Fits of the Fung model (circle) in the circumferential (left panels) and the axial (right panels) directions to representative experimental
stress-stretch data (plus symbol) from each group of the scaffolds
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Circ.
Ca
uchyStress(kPa)
0
200
400
600
800 Fung modelExp
AxialC
auchyStress(kPa)
0
200
400
600
800
1000
1200
1400
Fung model
Exp
Circ. Stretch
Circ.
Cauc
hyStress(kPa)
0
200
400
600
800 Fung modelExp
Circ. Stretch
0.96 0.98 1.00 1.02 1.04 1.06 0.96 0.98 1.00 1.02 1.04 1.06
0.96 0.98 1.00 1.02 1.04 1.06 0.96 0.98 1.00 1.02 1.04 1.06
AxialCauc
hyStress(kPa)
0
200
400
600
800
1000
1200
1400
Fung model
Exp
E
F
Tube
HA-45
Tube
HA-60
Fig. 2 continued
Table 1 Best-fit values of the parameters of the Fung model and the goodness of fit for each group of the scaffolds
Specimen type Model parameters Goodness of fit
c0 (Pa) c1 c2 c3 r2
Tube MA-30 362,700 196,314 81.06 56.48 64.20 39.67 27.39 15.43 0.992 0.006
Tube MA-45 778,616 904,116 78.74 79.89 144.64 121.98 42.31 41.34 0.975 0.009
Tube MA-60 1,493,720 1,581,935 17.65 15.52 81.20 78.01 12.51 12.64 0.942 0.026
Tube HA-30 167,551 65,250 105.03 44.22 58.96 23.00 44.97 14.80 0.987 0.007
Tube HA-45 57,250 54,848 281.34 140.24 500.34 256.10 243.29 114.50 0.977 0.011
Tube HA-60 264,352 480,152 143.93 116.44 883.30 671.74 177.31 143.94 0.948 0.030
Data are presented as mean standard deviation
the value of the corresponding k or k1 estimated by fitting287
data from the Tube HA given the same. The estimated val-288ues ofk2 (i.e., nonlinearity) in the NLFM was found to be289
in the order: Tube MA-30 = Tube MA-45> Tube MA-60290
and Tube HA-45> Tube HA-30> Tube HA-60. For both291
the LFM and the NLFM, the estimated values ofwere con-292
sistently greater than the experimentally prescribed angles.293
The inclusion of the neo-Hookean term in the LFM altered294
the estimated values of damong groups dramatically and295
affected the estimated values of k as well. Also, the neo-296
Hookean term improved the fits of c_LFM for the scaf-297
folds with = 45 and 60, and no significant differ- 298
ence was found though. In general, the within-group vari- 299ations in the model parameters of the three constitutive 300
models for the Tube HA were less than those for the 301
Tube MA. 302
Figure 4 shows the same representative biaxial stress- 303
stretch data from each group and the corresponding fits of 304
the c_NLFM and the c_NLFM withdprescribed. The fits of 305
the c_NLFM and the c_NLFM withdprescribed were better 306
than those of the previous three structurally motivated mod- 307
els. The best-fit values of the parameters of the c_NLFM and 308
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Constitutive modeling of an electrospun tubular scaffold
A
Tube
MA-30
Tube
MA-45
Tube
MA-60
B
C
0.98 1.00 1.02 1.04
Circ.C
auchyStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
0.98 1.00 1.02 1.04
AxialC
auchyStress(kPa)
0
200
400
600
800
1000
1200
1400
LFM
NLFMc_LFMExp
0.99 1.00 1.01 1.02
Circ.
Ca
uchyStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
0.99 1.00 1.01 1.02
AxialCau
chyStress(kPa)
0
200
400
600
800
1000
1200
1400
LFM
NLFMc_LFMExp
0.990 0.995 1.000 1.005 1.010
Circ.
CauchyStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
0.990 0.995 1.000 1.005 1.010
AxialCauchyStress(kPa)
0
200
400
600
800
1000
LFM
NLFMc_LFMExp
D
Tube
HA-30
Circ. Stretch
0.98 1.00 1.02 1.04 1.06
Circ.
Cauch
yStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
Circ. Stretch
0.98 1.00 1.02 1.04 1.06
AxialCauchyStress(kPa)
0
200
400
600
800
1000
1200
1400
LFM
NLFMc_LFMExp
Fig. 3 Fits of the LFM (inverted triangle), the NLFM (triangle), and the c_LFM (diamond) in the circumferential (left panels) and the axial (right
panels) directions to representative experimental stress-stretch data (plus symbol) from each group of the scaffolds
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J.-J. Hu
E
F
Tube
HA-45
Tube
HA-60
0.99 1.00 1.01 1.02 1.03
Circ.C
auchyStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
0.99 1.00 1.01 1.02 1.03
AxialC
auchyStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
Circ. Stretch
0.990 0.995 1.000 1.005 1.010
AxialCau
chyStress(kPa)
0
100
200
300
400
500 LFMNLFMc_LFMExp
Circ. Stretch
0.990 0.995 1.000 1.005 1.010
Circ.
Cau
chyStress(kPa)
0
200
400
600
800 LFMNLFMc_LFMExp
Fig. 3 continued
the c_NLFM withdprescribed and the associated goodness309
of fit for each group of the scaffolds are also listed in Table 2;310
details for each scaffold can be found in Supplemental Table311
56. Similar to the finding of the c_LFM, the inclusion of the312
neo-Hookean term in the NLFM altered the estimated values313
ofd among groups and affected the estimated values ofk1314
andk2 as well. In particular, there were large within-group315
variations in the model parameters of the c_NLFM. Note316
that the within-group variations in the model parameters of317
the c_LFM were relatively small. Interestingly, prescribing318
the value ofd reduced the within-group variations aforemen-319
tioned for c_NLFM and still resulted in fits comparable to320
those of the c_NLFM (i.e., no significant difference in fits321
between the c_NLFM and the c_NLFM with dprescribed)322
for all groups of the scaffolds. Furthermore, the c_NLFM323
withdprescribed involves only four parameters. Prescribing324
the value ofdslightly reduced the goodness of fit for scaf-325
folds with = 45 and60, thedifference was notsignificant326
though.327
Figure 5 compares the fits of the six constitutive mod-328
els for each group of the scaffolds via one-way repeated-329
measures ANOVA. For fitting the data of the Tube MA,330
there was no significant difference among the structurally331
motivated models. Nevertheless, the Fung model was signif-332
icantly different from the LFM, the NLFM, and the c_LFM. 333
On the other hand, for fitting the data of the Tube HA, the 334
5-parameter c_NLFM had the best fits among the struc- 335
turally motivated models, particularly for the Tube HA- 336
30; it was the only structurally motivated model that had 337
fits as good as the Fung model for all of the scaffolds 338
tested. Note, particularly, that the Tube HA-30 was the only 339
group for which the NLFM provided better fits than the 340
LFM. For both the Tube MA and the Tube HA, the smaller 341
the , the better the fitting for all the constitutive models 342
considered. 343
Based on the constitutive models, the stored strain energy 344
for each group of the scaffolds was calculated at = 345
1.04 &z = 1.00 and the results are listed in Table3;details 346
for each scaffold can be found in Supplemental Table 7. For 347
all the constitutive models, the stored strain energy of the 348
Tube MA-30 was significantly greater than that of the Tube 349
HA-30. That is, the Tube MA-30was circumferentially stiffer 350
than the Tube HA-30. There was no significant difference in 351
the value of stored strain energy between the Tube MA and 352
the Tube HA with = 45 and 60, however. Note that the 353
c_NLFM generated greater within-group variations for the 354
scaffolds with = 45 and 60 probably due to the extreme 355
estimated values ofk2 in these groups of the scaffolds. 356
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J.-J. Hu
A
Tube
MA-30
Tube
MA-45
Tube
MA-60
B
C
Circ.CauchyStress(kPa)
0
200
400
600
800 c_NLFM
c_NLFM; given dExp
AxialCauchyStress(kPa)
0
200
400
600
800
1000
1200
1400
c_NLFM
c_NLFM; given dExp
AxialCauchyStress(kPa)
0
200
400
600
800
1000
1200
1400
c_NLFM
c_NLFM; given dExp
Circ.
CauchyStress(kPa)
0
200
400
600
800 c_NLFM
c_NLFM; given dExp
Circ.
Cau
chyStress(kPa)
0
200
400
600
800 c_NLFMc_NLFM; given dExp
AxialCauc
hyStress(kPa)
0
200
400
600
800
1000
c_NLFM
c_NLFM; given dExp
D
Tube
HA-30
Circ. Stretch
Circ.
Cauch
yStress(kPa)
0
200
400
600
800 c_NLFMc_NLFM; given dExp
Circ. Stretch
AxialCauchy
Stress(kPa)
0
200
400
600
800
1000
1200
1400
c_NLFM
c_NLFM; given dExp
0.98 1.00 1.02 1.04 0.98 1.00 1.02 1.04
0.99 1.00 1.01 1.020.99 1.00 1.01 1.02
0.990 0.995 1.000 1.005 1.010 0.990 0.995 1.000 1.005 1.010
0.98 1.00 1.02 1.04 1.06 0.98 1.00 1.02 1.04 1.06
Fig. 4 Fits of the c_NLFM (inverted triangle) and the c_NLFM with dprescribed (diamond) in the circumferential (left panels) and the axial
(right panels) directions to representative experimental stress-stretch data (plus symbol) from each group of the scaffolds
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Constitutive modeling of an electrospun tubular scaffold
E
F
Tube
HA-45
Tube
HA-60
Circ.C
auchyStress(kPa)
0
200
400
600
800 c_NLFM
c_NLFM; given dExp
AxialC
auchyStress(kPa)
0
200
400
600
800 c_NLFMc_NLFM; given dExp
Circ. Stretch
Circ.
Cauc
hyStress(kPa)
0
200
400
600
800 c_NLFM
c_NLFM; given dExp
Circ. Stretch
0.99 1.00 1.01 1.02 1.03 0.99 1.00 1.01 1.02 1.03
0.990 0.995 1.000 1.005 1.010 0.990 0.995 1.000 1.005 1.010
AxialCauch
yStress(kPa)
0
100
200
300
400
500 c_NLFMc_NLFM; given dExp
Fig. 4 continued
The results of anisotropy analysis for each group of the357
scaffolds are summarized in Table4;details for each scaf-358
fold can be found in Supplemental Table 8. Interestingly,359
the stiffness ratios for all groups of the scaffolds calculated360
at = z = 1.02 were greater than one and their Fung361
model anisotropy index deviated from one; the scaffolds362
with = 30 were stiffer in the axial direction whereas363
the scaffolds with = 45 and 60 were stiffer in the cir-364
cumferential direction regardless of the fiber alignment in365
the scaffolds. In particular, although both the Tube MA-45366
and the Tube HA-45 are structurally isotropic along the two367
stretching directions when unloaded, their stiffness ratios at368
= z = 1.02 were also greater than one (1.42.3) and369
theirFung modelanisotropy index consistently deviatedfrom370
one (0.7). Note, also, that the extent of anisotropy for the371
scaffolds with = 60 was significantly greater than that372
for the scaffolds with = 30 despite their similar structural373
anisotropy. The mechanical anisotropy of each group of the374
scaffolds appeared not correlated well with their structural375
anisotropy. On the other hand, if comparisons were made376
between the Tube MA and the Tube HA that have the same377
, the extent of anisotropy of the Tube HA was greater than378
that of the Tube MA for = 30 and 60 but the differ-379
ence between the Tube MA-45 and the Tube HA-45 was not 380
significant. 381
4 Discussion 382
Although the Fung model provided the overall best fit to the 383
experimental data, it is phenomenological in nature; its para- 384
meters have little physical meaning and its applications are 385
limited. Structurally motivated models, on the other hand, 386
have physically significant parameters and can potentially 387
offer better predictive capability. That is, given experimen- 388
tally prescribedstructural parameters, a successful struc- 389
turally motivated model can accurately predict the mechani- 390
cal response of a scaffold with previously determined mate- 391
rial parameters. Structurally motivated models can thus be 392
used as a guideline to design a scaffold that has mechan- 393
ical properties closer to the tissue to be replaced. More- 394
over, a structurally motivated model is preferred than a phe- 395
nomenological model in the development of a growth and 396
remodeling model that can describe the maturation process 397
of a tissue-engineered construct(Humphrey and Rajagopal 398
2002); the growth and remodeling model can potentially 399
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Constitutive modeling of an electrospun tubular scaffold
Table 3 Stored strain energy calculated based on the best-fit values of the parameters of each model for each group of scaffolds
Specimen type Stored strain energy @= 1.04 &z = 1.00 (J/m3)
Fung LFM NLFM c_LFM c_NLFM c_NLFM; givend
Tube MA-30 15,108 742 15,723 680 15,577 890 15,876 592 15,732 809 15,372 1,396
Tube MA-45 28,146 4,656 26,111 3,337 26,884 3,133 25,622 2,976 37,602 16,484 31,566 3,949
Tube MA-60 47,972 6,793 45,998 4,916 47,430 6,002 45,521 4,798 272,489 333,617 47,695 4,942
Tube HA-30 7,602 411 8,703 208 7,562 472 8,793 256 8,069 371 7,973 317
Tube HA-45 24,308 3,190 20,051 1,498 25,347 3,121 19,635 1659 28,376 5,000 23,908 1,202
Tube HA-60 96,459 53,879 41,724 7,905 44,933 6,551 40,634 6,805 464,929 788,243 46,661 5,672
Data are presented as mean standard deviation
Table 4 Ratio of stiffness in thestretchingdirectionsand theFung model anisotropy indexa calculated based on thebest-fit values of theparameters
of each model for each group of scaffolds
Specimen type Stiffness ratio @= 1.02 &z = 1.02 Anisotropy
Fung
Fung LFM NLFM c_LFM c_NLFM c_NLFM; givend
Tube MA-30 1.26 0.27 1.35 0.31 1.25 0.26 1.21 0.16 1.20 0.16 1.20 0.16 0.87 0.11Tube MA-45 1.99 0.54 1.83 0.48 1.92 0.41 1.63 0.32 2.34 0.78 1.93 0.36 0.64 0.11
Tube MA-60 4.50 1.21 4.34 0.73 4.54 1.08 2.75 0.47 9.92 9.21 3.92 1.19 0.35 0.07
Tube HA-30 1.82 0.22 1.73 0.20 1.82 0.22 1.53 0.16 1.55 0.16 1.56 0.16 0.70 0.06
Tube HA-45 1.93 0.35 1.79 0.29 2.34 0.40 1.44 0.15 2.25 0.35 2.07 0.29 0.70 0.08
Tube HA-60 8.19 2.67 6.05 1.35 6.59 1.10 3.74 0.75 9.51 5.67 5.50 1.18 0.31 0.06
a For the Fung model only. Data are presented as mean standard deviation
For Tube MA-30 and Tube HA-30, Kzzz z
K > K
Kzzz zand c1+c3
c2+c3> c2
+c3c1+c3
whereas for Tube MA-45, 60 and Tube HA-45, 60, Kzzz zK
< K Kzzz z
andc1+c3c2+c3
< c2+c3
c1+c3
The estimated values of the fiber modulus-related para-422
meter,kin the LFM ork1in the NLFM, were expected to be423
the same for either the Tube MA or the Tube HA; the Tube424
MA and the Tube HA were made, respectively, of scaffold425
membranes with distinct fiber angle distributions. Both kand426
k1 were found to increase with increasing of the scaffolds,427
however. The dependence of estimated fiber modulus on the428
in both the LFM and the NLFM indicated that there exists429
some factor whose influence is dependent on the and was430
not accounted for in the two models. One reasonable factor is431
the resistance due to fiber interactions.Croisier et al.(2012)432
observed three orders of magnitude difference in the moduli433
of fiber scaffolds versus single fibers and attributed the dif-434
ference to the lacunar and random structure of the scaffolds.435
The fiber modulus estimated from the fit for the Tube MA436
was also found to be greater than that for the Tube HA for437
the same . This may be well attributed to the higher den-438
sity of fiber interconnections in the Tube MA; the Tube MA,439
compared to the Tube HA, might be subjected to a greater440
resistance due to fiber interactions when inflated.Courtney441
et al.(2006) related fiber alignment in an electrospun mem-442
brane, which was manipulated by controlling the rotation443
speed of a grounded mandrel, to the mechanical behavior444
of the membrane based on a similar structurally motivated445
model. In contrast to our finding, they found that the esti- 446
mated fiber stiffness is greater if the fiber alignment is better. 447
The contradictory findings may be due to different geometry 448
of specimens, different protocols of mechanical testing, and 449
different scaffolding materials. Note that a positive correla- 450
tion between the crystallinity of the polymers in the fibers, 451
which was shown to affect their tensile properties (Lim et al. 452
2008), and the mandrel velocity was also reported in their 453
study. In addition tokor k1, that the value of estimated by 454
both the LFM and the NLFM was in general greater than the 455
experimentally prescribed also suggested that some fac- 456
tor other than those considered in the two models was active 457
in increasing circumferential stiffness during inflation of the 458
scaffolds. 459
In this study, electrospun fibers were collected on a 460
rapidly rotating, grounded drum. As crimped fibers were not 461
observed in the electrospun membranes that were used to 462
fabricate the scaffolds, we did not consider those forms of 463
fiber strain energy function that account for fiber undula- 464
tion (Hill et al. 2012) or fiber curvature (Pai et al. 2011). 465
Nevertheless, we tested a strain energy function that consid- 466
ers nonlinear fiber stressstrain relation. Although the fits 467
of the 3-parameter LFM were comparable to those of the 468
4-parameter NLFM for most groups of the scaffolds, the 469
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J.-J. Hu
performance of the NLFM in fitting data from the Tube470
HA-30 was significantly better than the LFM. The improve-471
ment of fitting due to the introduction of fiber nonlinearity472
may be attributed to gradually increasing fiber interactions473
upon inflation since these aligned polycaprolactone fibers474
likely exhibit linear stress-stretch behavior. Note that the475
fiber nonlinearity-related parameter, k2, in the NLFM was476
also found to be dependent on the of the scaffold; the esti-477
mated nonlinearity increased from = 30 to 45 and then478
decreased from = 45 to 60. The contribution of fiber479
interactions might be increasing upon inflation for the scaf-480
folds with a small but remain steady during inflation for481
the scaffolds with a large .482
Although all of the scaffolds exhibited fair linear stress-483
stretch behavior (only representative data are shown), non-484
linear stress-stretch fits by the LFM and the NLFM were485
observed, which were particularly obvious when the scaffold486
is subjected to axial stretching (e.g.,z = 1.04). This is inter-487
esting but not surprising as in both the LFM and the NLFM,488
fiber interactions were not explicitly considered. In the two489
models, circumferentially oriented fibers in the scaffold can490
freely become crimped when the scaffold is solely axially491
stretched (without inflation) assuming the incompressibility492
of the scaffold. Note that the crimped fibers( f < 1)have493
no mechanical contribution in the two models. The gradually494
straightening of the crimped fibers upon inflation can thus495
lead to the nonlinear fits of the two models. The nonlinear496
fits could also be attributed to the affine motion of fibers or497
fiber re-orientation upon inflation in structurally motivated498
models. The contribution may not be as significant due to499
the small deformation and the axial constraint; nonlinear fits500
were not observed when the inflated scaffold was not axi-501
ally stretched (i.e., z = 1.00). The inclusion of the neo-502
Hookean term in the LFM and the NLFM, however, allevi-503
ated the nonlinearity. The neo-Hookean term was introduced504
in structurally motivated models as a strain energy function505
associated with isotropic deformation of amorphous elastic506
constituents(Holzapfel et al. 2000;Humphrey 1999b). The507
neo-Hookean term is arguably phenomenological (Hollan-508
der et al.2011), and specific quantitative information about509
the term is hardly obtained (from histological and structural510
analyses). Nevertheless, the inclusion of the neo-Hookean511
term did improve the fits of the c_LFM and the c_NLFM512
when compared to the LFM and the NLFM, respectively. We513
suggested that the neo-Hookean term may, in part, account514
for the resistance due to fiber interactions. Note that the tubu-515
larscaffolds that were constitutivelymodeled in this study are516
made of electrospun fibers and contain no isotropic matrix.517
In our preliminary tests, a LFM with a fiber angle dis-518
tribution function that includes explicitly the portion of519
isotropically oriented fibers (i.e., R( ) = x + (1 x)520
d
1 +
d
21, where x is the mass fraction of521
isotropically oriented fibers) wastested. The estimatedvalues 522
ofxfor both the Tube MA and the Tube HA, in most cases, 523
were found to be negligible, which was consistent with the 524
finding ofCourtney et al. (2006). For most of the scaffolds, 525
the fits of this 4-parameter LFM were very similar to those of 526
the 3-parameter LFM; the nonlinear stress-stretch fits were 527
also observed. That is, the additionalparameter,x, inthefiber 528
angle distribution function wasnot effective in improving the 529
fitting. Note that all fibers including those isotropically ori- 530
ented fibers were assumed to share the same fiber modulus in 531
the 4-parameter LFM, and therefore, the neo-Hookean term, 532
which is independent on the fiber modulus, may not be fully 533
compensated by the mass fraction of isotropically oriented 534
fibers or by a different fiber angle distribution function. 535
The potential role of fiber interactions in the mechani- 536
cal behavior of electrospun scaffolds was identified in this 537
study. Although some model parameters, e.g., c, k (or k1), 538
and k2, in the structurally motivated models could some- 539
how account for the resistance of fiber interactions, an 540
isolated strain energy function specific for fiber interac- 541
tions is certainly more desirable. Palmer (2008) proposed 542
a cross-link torsional strain energy to account for the stiff- 543
ness of fiber junction, which was then used to model 544
the mechanical properties of electrospun nonwoven fiber 545
meshes (Pai et al. 2011). The inclusion of torsional strain 546
energy function, however, did not perform as good as the 547
inclusion of the neo-Hookean term in our preliminary tests 548
(data not shown). On the other hand, multi-scale network 549
model that incorporates all the structural information of the 550
specimen was developed to describe the mechanical behavior 551
of electrospun scaffolds (Argento et al. 2012). The network 552
model may be more helpful in accounting for the fiber inter- 553
actions than structural continuum models. Their accuracy, 554
however, depends on how detailed and accurate the micro- 555
mechanics of the network was captured. 556
Both the Fung model and the structurally motivated mod- 557
els fit the mechanical behavior of the scaffolds with a small 558
betterthan thescaffolds with a large.Thismaybeduetoless 559
deformation of the latter during inflation, and the influence of 560
inherent experimental errors became more dominated. Fur- 561
thermore, upon inflation, the two symmetric arrays of fibers 562
in the latter might become closer to each other (i.e., merging 563
into one group) and the structurally motivated models could 564
fail; indeed, the estimated model parameters of the struc- 565
turally motivated models for the Tube MA-60 and the Tube 566
HA-60 became not as unique as those for the Tube MA-30 567
and the Tube HA-30. This certainly constitutes a limitation 568
of the structurally motivated models. 569
The model parameters of an ideal structure-based con- 570
stitutive relation must be independent; that is, the mechani- 571
cal contribution of one model parameter cannot be compen- 572
sated by the other. The estimated value of a model parame- 573
ter can thus represent the physical significance of the para- 574
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