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ORIGINAL PAPER
Improvement of biomaterials used in tissue engineeringby an ageing treatment
Cristian A. Acevedo • Paulo Dıaz-Calderon •
Javier Enrione • Marıa J. Caneo • Camila F. Palacios •
Caroline Weinstein-Oppenheimer • Donald I. Brown
Received: 17 May 2014 / Accepted: 26 October 2014
� Springer-Verlag Berlin Heidelberg 2014
Abstract Biomaterials based on crosslinked sponges of
biopolymers have been extensively used as scaffolds to
culture mammal cells. It is well known that single bio-
polymers show significant change over time due to a phe-
nomenon called physical ageing. In this research, it was
verified that scaffolds used for skin tissue engineering (based
on gelatin, chitosan and hyaluronic acid) express an ageing-
like phenomenon. Treatments based on ageing of scaffolds
improve the behavior of skin-cells for tissue engineering
purposes. Physical ageing of dry scaffolds was studied by
differential scanning calorimetry and was modeled with
ageing kinetic equations. In addition, the physical properties
of wet scaffolds also changed with the ageing treatments.
Scaffolds were aged up to 3 weeks, and then skin-cells
(fibroblasts) were seeded on them. Results indicated that
adhesion, migration, viability, proliferation and spreading of
the skin-cells were affected by the scaffold ageing. The best
performance was obtained with a 2-week aged scaffold
(under cell culture conditions). The cell viability inside the
scaffold was increased from 60 % (scaffold without ageing
treatment) to 80 %. It is concluded that biopolymeric scaf-
folds can be modified by means of an ageing treatment,
which changes the behavior of the cells seeded on them. The
ageing treatment under cell culture conditions might become
a bioprocess to improve the scaffolds used for tissue engi-
neering and regenerative medicine.
Keywords Physical ageing � Scaffolds � Tissue
engineering
Introduction
The preparation of tissue engineering systems is not an
easy process. First, it is necessary to have an adequate
material called scaffold, which carries the mammal cells
into a bioreactor and allows the tridimensional culture
expansion. The system formed by cells attached on a
scaffold is a complex biosystem where many bioprocesses
occur to transform the tridimensional culture in a tissue
engineering device. The selection of an adequate scaffold
and its treatment are critical steps in the design of tissue
engineering systems to support the cellular component.
Scaffolds based on crosslinked sponges of gelatin (Ge) and
chitosan (Ch) are extensively used for tissue engineering
applications. Ge/Ch-scaffolds have been used as biomaterials
to regenerate skin [1], bones [2] and cartilages [3]. The fact
that Ge/Ch-scaffolds are successful for tissue engineering
C. A. Acevedo (&)
Centro de Biotecnologıa, Universidad Tecnica Federico Santa
Marıa, Avenida Espana 1680, Valparaıso, Chile
e-mail: [email protected]
P. Dıaz-Calderon � J. Enrione
Biopolymer Research and Engineering Lab, Escuela de
Nutricion y Dietetica, Facultad de Medicina, Universidad de los
Andes, Monsenor Alvaro del Portillo 12455, Las Condes,
Santiago, Chile
M. J. Caneo � C. F. Palacios � D. I. Brown
Laboratorio de Biologıa de la Reproduccion y del Desarrollo,
Instituto de Biologıa, Facultad de Ciencias, Universidad de
Valparaıso, Avenida Gran Bretana 1111, Valparaıso, Chile
M. J. Caneo � C. F. Palacios
Escuela de Tecnologıa Medica, Facultad de Medicina,
Universidad de Valparaıso, Alcalde Sergio Prieto Nieto 452,
Vina del Mar, Chile
C. Weinstein-Oppenheimer
Escuela de Quımica y Farmacia, Facultad de Farmacia,
Universidad de Valparaıso, Avenida Gran Bretana 1093,
Valparaıso, Chile
123
Bioprocess Biosyst Eng
DOI 10.1007/s00449-014-1319-x
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applications can be explained by two reasons: (a) gelatin
contains an Arg-Gly-Asp (RGD)-like sequence which pro-
motes cell adhesion and migration [4]; and (b) gelatin is
blended with chitosan to improve its physical properties
because Ge/Ch-copolymers form polyelectrolyte complexes
[5]. Moreover, modifications of Ge/Ch-sponges with hyalu-
ronic acid (Ha) produce Ge/Ch/Ha-scaffolds that mimic the
extracellular matrix allowing the growth of skin-cells [6].
It has been described that ageing of biomaterials is a
problem in the pharmaceutical industry, because it can limit
the shelf-life of pharmaceutical devices [7]. Polymers and
biopolymers show significant change over time due to the
non equilibrium condition of the amorphous fraction. Phe-
nomena associated to physical ageing have been studied
extensively in synthetic polymers, some pharmaceutical
polymers [7] and a few scaffolds [8]. Physical ageing is of
significant importance at both the scientific and technolog-
ical levels, because it leads to changes to the properties of
the material, these include hardening, densification,
increased brittleness and decreased permeability [9, 10]. In
pharmaceutical polymers, this phenomenon strongly influ-
ences the drug diffusion and consequently alters biological
phenomena [7]. Information about shelf-life or ageing of
biopolymer scaffolds is scarce in the scientific literature.
It has been described that single biopolymer systems based
on gelatin or chitosan express physical ageing [9, 11]. Nev-
ertheless, the Ge/Ch/Ha-sponges are complex systems, which
are not easy to characterize. Most critically, the Ge/Ch/Ha-
scaffolds are sponges covalently crosslinked, of which there is
little information describing the physicochemical properties
and how that affects the cell behavior [12, 13].
It is well known that cells have the ability to interact
with extracellular matrix. Specifically skin-cells sense
change of collagen-fibrils [14], and probably may sense
changes of collagen-derived protein as gelatin. If the
scaffolds components change with ageing, it is likely that
this can affect the behavior of the cells seeded on them.
Since gelatin and chitosan express physical ageing, we
hypothesized that Ge/Ch/Ha-scaffolds also express struc-
tural changes caused by ageing, and the cells cultured on
them would be able to sense these changes.
In this work, we verified that Ge/Ch/Ha-scaffolds express
an ageing-like phenomenon and that this modified the skin-
cells behavior. This finding opens an alternative to investi-
gate novel strategies to improve tissue engineering matrixes.
Materials and methods
Preparation of Ge/Ch/Ha-scaffolds
Gelatin (from bovine, bloom value 200, grade Ph Eur BP
NF) was purchased from Merck (Germany), chitosan (from
crab shells, 88 % deacetylated, 120 kDa, food grade) was
purchased from Quitoquimica (Chile) and hyaluronic acid
(medical grade, 980 kDa) was purchased from Lifecore
(USA). EDC (1-ethyl-(3,3-dimethyl-aminopropyl)-carbo-
diimide), MES (2-morpholine-ethane sulfonic acid) and
NHS (N-hydroxysuccinimide) were purchased from
Sigma–Aldrich (USA). The scaffolds were prepared using
the method described by Liu et al. [6] with minimum
modifications as described below.
A solution of Ge/Ch/Ha was prepared mixing gelatin
(1.0 %) with chitosan (2 % in 1 % acetic acid) and hyal-
uronic acid (0.01 %) at 50 �C in proportions of 7:2:1
(Ge:Ch:Ha). The solution was poured into a Petri dish
adjusting the volume to obtain a height of 3 mm. The Ge/
Ch/Ha solution was cooled at 4 �C, frozen at -80 �C,
immersed in liquid nitrogen and lyophilized using a freeze
dry system (Labconco, USA). Then, the dry Ge/Ch/Ha-
sponge was crosslinked by the use of a solution composed
by EDC (30 mM), MES (50 mM) and NHS (8 mM), using
ethanol 90 % as solvent. The resultant crosslinked matrix
was then washed with ethanol, frozen and lyophilized. The
Ge/Ch/Ha-scaffolds were stored with silica gel until
experimentation.
Skin-cells
The skin-cells were obtained from rat dermis (strain cpr
100). Rats were anesthetized with ketamine/xylazine (5 and
2 mg per 100 g of body weight, respectively), shaved and
disinfected with a povidone-iodine solution. A biopsy of
1 cm2 was taken from the dorsal area of the animal.
The biopsy was washed with saline phosphate-buffered
(PBS) containing penicillin (100 U/mL) and streptomycin
(100 lg/mL), cut in 1-mm pieces and incubated for 3 h at
37 �C in collagenase solution (2 mg/mL). The epidermis
layer and visible fat were discarded. Then, the cells were
recovered by centrifugation and cultured in DMEM (Gib-
co-Invitrogen, USA) with 10 % fetal bovine serum (FBS)
in 25 cm2 T-flasks under standard cell culture condition
(37 �C and 5 % CO2).
Histochemistry and immunohistochemistry
The scaffolds were fixed in Bouin’s solution for 24 h,
dehydrated and embedded in Paraplast-Plus (Sigma, USA).
Then, the scaffolds were cut completely using a microtome
(Leica, Germany). Five micrometer-thick serial sections
were obtained and mounted on silane-coated microscope
slides, deparaffinized and rehydrated.
The cell distribution and morphology were analyzed
using a trichrome stain (Hematoxylin/Erythrosine B–
Orange G/Methyl blue) [5, 13]. The first section of each
series (15 sections) was stained and analyzed.
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Selected sections of each series were immunostained
with anti-TGF-b antibody (1:100 dilution, rabbit poly-
clonal, ab66043; Abcam, UK). After use of primary anti-
body, sections were incubated with biotinylated anti-rabbit
IgG (1:500 dilution) and processed using a commercial
peroxidase-ABC kit (Vector, USA), stained with DAB as
chromogen and counterstained using Harris Hematoxylin.
Viable biomass measurement
Resazurin assay was used to measure viable biomass [15].
Viable biomass inside and outside the scaffold was mea-
sured to estimate adhesion and migration of cells seeded
onto the scaffold, respectively.
The cells or scaffolds with cells were incubated in
24-wells culture plate with 200 ll of fresh culture medium
and 200 ll of resazurin solution (50 lM; Sigma–Aldrich,
USA) for 4 h at 37 �C. The viable biomass was estimated
by resorufin production, which was measured by fluores-
cence (excitation at 544 nm and emission at 590 nm) with
a plate reader (Appliskan Thermo Scientific, USA). For
each experiment, a calibration of a known viable cell
number was made (cells were counted in a Neubauer
chamber with the viability dye trypan blue).
Differential scanning calorimetry (DSC)
Thermal properties were analyzed using a differential
scanning calorimeter (DSC, Mettler Toledo, Switzerland).
Prior to the analysis, all samples were equilibrated (con-
stant weight) in a chamber with 75 % relative humidity
(using NaCl saturated solution). Then, a sample of 15 mg
was hermetically sealed in an aluminum pan of 100 lL.
The thermal scanning conditions were: scan 1) heating
from -20 �C to 130 �C at 10 �C/min, holding at 130 �C
for 1 min; and scan 2) cooling from 130 �C to -20 �C,
holding at -20 �C for 5 min and reheating to 130 �C at
10 �C/min. The DSC was previously calibrated using
indium as a standard (melting at 156.6 ± 0.3 �C and
enthalpy of 28.45 ± 0.6 J/g) and an empty pan was used as
reference.
Physical properties
Bulk-density was estimated as the ratio between the dry
mass and the total volume occupied by the scaffold. The
volume as a whole was measured with a micrometer
(Mitutoyo, Japan) recording the width, length and thickness
of the scaffolds in at least five different positions.
Porosity of the scaffold was measured using gas pic-
nometry (pycnometer MVP 1305, Micrometrics, USA)
using helium as carrying gas.
Prior to bulk-density and porosity measurements the wet
scaffolds were lyophilized as described before.
Mathematical modeling
To model changes associated with ageing (U) as a function
of time (t), the Kohlrausch–William–Watts (KWW) equa-
tion was applied to experimental data [16]:
U ¼ exp � t
T
� �B� �
where T is the characteristic time of ageing and B is a
dimensionless coefficient (measure of non-exponentiality).
The changes of enthalpy relaxation (DH) associated to
physical ageing and other properties were represented by
their dimensionless functions:
U ¼ X � X1ð ÞX0 � X1ð Þ
where X is the property measured, X0 is the initial value
and X? is the value at equilibrium.
Experimental values were fitted to the KWW equation
using a non-linear least square method (Newton’s method)
with the tool Solver for Microsoft Excel. The quality of the
fitting was estimated using the correlation coefficient
(r) between experimental and calculated value.
Statistical methods
Basic statistical analyses to compare among different kind
of samples (e.g. scaffolds treated with different ageing
time) were made using analysis of variance (ANOVA,
p \ 0.05). In addition, comparisons between groups of
samples were made using the Tukey test.
Results and discussion
Biological ageing of the tissue engineering system
Ageing of biological systems based on cell cultured into
scaffolds could be beneficial for tissue engineering pur-
poses. In our model of skin-cells culture on Ge/Ch/Ha-
scaffold, short-time ageing produces beneficial effects,
including cellular migration, development of cell clusters
(colonies) and release of growth factors [13].
In Fig. 1 the behavior of skin-cells seeded into scaffolds
at 1 week and after 2 weeks can be seen. Figure 1a shows
that the cell distribution inside the scaffold changes with
short time of ageing, improving cell homogeneity after
2 weeks. Figure 1b shows single cells typically observed at
1 week, but Fig. 1c shows that with time cells form clus-
ters and they express TGF-b.
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These results show that a whole biological system
changes significantly over time, and these changes are
beneficial in terms of tissue engineering. If the scaffold is
considered totally inert, the mentioned changes could be
associated only with cell processes. But, our hypothesis is
that the scaffolds express ageing changes affecting the cell
behavior. To verify this hypothesis, the expression of
putative phenomena associated with physical ageing was
studied in Ge/Ch/Ha-scaffolds.
Physical ageing of dry scaffold
An initial experiment based on DSC was made to verify
expression of phenomena associated whit ageing in dry Ge/
Ch/Ha-scaffolds (Fig. 2a). The first DSC-scan shows two
thermal transitions: (a) a glass transition temperature (Tg)
with an inflection point close to 37.4 �C (onset 31.9 �C,
endpoint 39.8 �C and heat capacity variation of 148.0 J/
kg �C); and (b) an endotherm with onset at 72.4 �C (peak
85.9 �C, endpoint 99.2 �C and enthalpy of 10.6 J/g). The
endotherm observed in the first scan indicates the presence
of an ordered-like fraction in the scaffold, which could be
associated with the melting of gelatin [5, 12, 13]. The
second DSC-scan showed a completely amorphous struc-
ture indicating the irreversibility of the endothermic tran-
sitions previously discussed.
A spontaneous endothermic event on the thermogram
was observed when the amorphous material in glassy state
was stored (see Fig. 2a). The latter strongly indicated that
the scaffold structure changes with ageing time. In poly-
mers and biopolymers (e.g. gelatin) this phenomenon
associated with physical ageing is often called enthalpy
relaxation or structural relaxation [9, 10].
Figure 2b shows the change in excess of enthalpy of
aged scaffolds. Experimental data of Fig. 2b fitted well to
KWW equation, classically used to model the physical
ageing kinetics [16]. The KWW equation has been used to
model the enthalpy relaxation process of biopolymers as
carbohydrates [17] and proteins [10]. This equation is a
stretched exponential function, where the parameter
B (0 B B B 1) is a measure of its non-exponentiality. If the
parameter B is close to 1, it corresponds to a single
relaxation time with exponential behavior. The estimated
value of B was lower than 1 (B = 0.58), indicating a
Fig. 1 Behavior of skin-cells seeded into scaffolds. a Cell counting
and distribution after 1 and 2 weeks of seeded. b Single cells at
1 week (stained with the thrichrome stain, bar 50 lm). c Cell cluster
after 2 weeks showing positive immunostaining for TFG-b (counter-
stained with hematoxylin, bar 50 lm)
Fig. 2 Thermophysical behavior of dry scaffold. a Thermograms of
scaffolds in semicrystalline state (original material) and amorphous
state aged 24 h at 20 �C. b Enthalpy relaxation (DH) kinetics of
amorphous material and its fitting using KWW equation. Coefficients
fitted were, DH? = 2.64 [J/g], T = 9.69 [h] and B = 0.58
(dimensionless)
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distribution of relaxation time rather than a single relaxa-
tion time. In complex biopolymers systems such as gela-
tinized starches the B values reported are between 0.2 and
0.4 [17]. In addition, the fitting of KWW equation pro-
duced an excess in enthalpy at equilibrium (DH?) of 2.64
[J/g], which is a value similar to values reported for pure
gelatin (2.4 [J/g]) [10].
As far as we know this phenomenon has not been
described in complex systems such as copolymers cova-
lently crosslinked with EDC (like our system). So our
results suggest the occurrence of this relaxation-like phe-
nomenon, which could have an important effect in the
scaffold properties.
Ageing of wet scaffold
Results described before shows that scaffolds can change in
glassy state. However, when the scaffold is used for tissue
engineering applications, it is immersed in a bioreactor
with culture medium at physiological temperature (37 �C)
taken a rubbery state (eliminating in theory all thermal
history of the material). To study if the wet scaffold
(rubbery state) under cell culture conditions is affected by
ageing, we kept the scaffold immersed in medium (DMEM
with 10 % FBS) at 37 �C for 15 days (360 h).
The results shown in Fig. 3 described that porosity and
bulk-density change over time. Porosity decreased linearly
in the time studied (p \ 0.05; ANOVA), but bulk-density
kinetic had a behavior similar to KWW equation. In terms
of tissue engineering, this phenomenon could be affecting
the cell behavior, because it has been reported that porosity
reduction in Ge/Ch/Ha-scaffolds improves the cell growth
and expression of growth factors [12].
Figure 4a shows that the glass transition changes over
ageing time. This kinetic can be modeled by the KWW
equation which describes the ageing phenomenon. Addi-
tionally, the Tg was increased and the heat capacity vari-
ation decreased (Fig. 4b). Yoshioka et al. [8] obtained
changes of Tg in PLGA-scaffolds aged in PBS at 37 �C.
These authors reported decreasing of Tg (second scan) by
the degradation of the polymer and reduction of the
molecular weight. Nevertheless, we obtained an increase of
the Tg (first scan) in contrast to the decrease of heat
Fig. 3 Physical behavior of wet scaffold. Prior to measure porosity
and bulk-density, the wet scaffolds were lyophilized. a Porosity
kinetic. b Bulk-density (q) kinetic and its fitting using KWW
equation. Coefficients fitted were, q? = 50.23 [kg/m3], T = 349.84
[h] and B = 0.56 (dimensionless)
Fig. 4 Glass transition kinetic. Wet scaffolds were sampled and
lyophilized, and then equilibrated at 75 % relative humidity. a Glass
transition temperature (Tg) and its fitting using KWW equation.
Coefficients fitted were, Tg? = 88.98 [�C], T = 341.54 [h] and
B = 0.69 (dimensionless). b Glass transition temperature (Tg) and
heat capacity variation (DCp) relationship in a semi-log plot
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capacity, suggesting an increase of the crystalline fraction.
The latter has been informed in PLLA-scaffolds aged in
alkaline medium at 37 �C [18], where the rise of Tg was
associated to increase of crystallinity.
Our results show that physical and thermophysical
properties of the scaffold change with ageing. It is well
known that changes in extracellular matrix affect the cell
behavior. In our previous work [13], it was reported that
different gelatin content modify the Tg and porosity of Ge/
Ch/Ha-scaffolds, and that these modifications improved the
cell growth. Then a question arises, if a treatment based on
ageing of the scaffold could also modify the behavior of
cells seeded on them.
Effect of ageing treatment on cell affinity
A key issue in tissue engineering is the interaction between
the biomaterial or scaffold and the living cells. Cell
attachment and migration in the scaffold are relevant for
building an implant system, which mimic a tissue and
therefore is useful for tissue engineering applications [19].
To estimate the affinity between cells and the aged scaf-
folds, cell adhesion and migration outside the scaffold were
studied.
A set of aged scaffolds with different ageing time was
prepared. For that, the scaffolds (without cells) were kept
in cell culture medium (DMEM with 10 % FBS) at 37 �C
for 1, 2 and 3 weeks. Then, skin-cells were seeded on the
aged scaffolds to study their affinity.
Figure 5a shows the cell adhesion. Scaffold not aged has
a cell adhesion close to 39 %. Similar values have been
reported for this kind of scaffolds [6, 13]. However, when
the scaffold is aged, the adhesion decreases to reach a value
close to 25 %. It is very likely that the ageing affects some
structuring properties of the scaffolds, and which might
influence the behavior of the cells in contact with them.
Figure 5b shows that ageing affects the migration out-
side the scaffold (p \ 0.05; ANOVA). The scaffold not
aged has low migration rate in comparison with scaffold
aged for 2 and 3 weeks (p \ 0.05; Tukey test). In terms of
tissue engineering this effect could be beneficial, because
in early stage it is necessary to have cells growing within
the scaffold. But in a long term, when the scaffold is
implanted on patients, it is necessary that the cells can
migrate outside the scaffold for tissue healing or repair.
These results suggest that the scaffold is a non-inert
matrix and that ageing phenomenon affects the cell
behavior.
Effect of ageing treatment on physiological cell
behavior
The physiological behavior (viability and proliferation) of
cells cultured onto scaffolds with different ageing time (1,
2 and 3 weeks) was analyzed using histological techniques.
Cells were seeded on aged scaffolds and after 1 week of
culture they were fixed to prepare the histological analysis.
Figure 6 shows cells observed (single cells, clusters of
cells, pyknotic cells and mitotic figures).
Figure 7 shows physiological rates (viability and mitotic
rate) in three zones of the scaffolds. Viability of cells
cultured onto aged scaffold is higher than non-aged scaf-
folds (Fig. 7a). All zones of aged scaffolds had at least
80 % of viability. However, in the middle and bottom
zones of the not aged scaffolds displayed viabilities close
to 60 %. This is an important finding since cell viability
within the whole thickness of the scaffold has been
described as a relevant success factor for medical devices
in tissue engineering [19, 20].
Figure 7b shows the mitotic rate, indicating that the
scaffold aged for 2 weeks is the most proliferative
Fig. 5 Affinity between cells and aged scaffolds. Cells were seeded
on scaffolds with different ageing levels. Scaffolds with cells
(2 9 104 cells/cm2) were incubated in a 24-wells culture plate.
a Cell adhesion. Adhesion is the rate between the number of cells
initially seeded onto the scaffold and viable cells attached after 24 h.
b Cell migration. Migration rate is a relative value of viable biomass
outside the scaffold (onto plastic well bottom) at 48 h, and it was
arbitrary considered a value of 100 % for not aged scaffolds. Asterisk
symbols (* and **) show not significant differences (p [ 0.05; Tukey
test)
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promoting matrix. The mitotic rate in the intermediate zone
of scaffolds aged for 2 weeks was 0.53 %. This value is
slightly lower than mitotic rates reported to fetal monolayer
cultures. For instance, a mitotic rate of mouse fetal skin
fibroblasts was reported as close to 1.3 % [21]. Prolifera-
tion within the scaffold is another success factor for tissue
engineering devices [19], indicating that the ageing bio-
process is improving the scaffold performance probably
influencing cell signaling through chemical and physical
stimuli.
These results suggest that the biological properties of the
scaffold could be improved using the ageing phenomena as
a bioprocess.
Effect of ageing treatment on cell distribution
The importance of cell spreading within a scaffold has been
recognized in the tissue engineering field for optimizing the
scaffold properties [19]. Figure 8 shows the cell distribu-
tion inside the scaffolds. Figure 8a indicates strongly that
the higher biomass is obtained with a scaffold aged for
2 weeks. In addition, the scaffold with 2 weeks of ageing
has a homogeneous distribution of cells inside the scaffold,
which again shows that the 2 weeks ageing bioprocess
improved the native scaffold.
Figure 8b shows the distribution of aggregated cells in
different zones of the scaffold. We observed that the
scaffold aged for 2 weeks has the higher presence of cell
cluster and the best distribution of them. Cell aggregation
is a very important factor in tissue engineering because it
allows cell–cell interaction and it is a qualitative evidence
of cell growth. It has been reported that cell clusters of
skin-cells immobilized in fibrin-scaffolds appear after the
third day of seeded [22]. This could be inducing a micro-
environment favorable for the synthesis of growth factors,
such as TGF-b [23], which are recognized as relevant
determinants of tissue regeneration. Our results show that
the cell clusters inside the aged scaffolds expressed TGF-b(Fig. 6e), but single cells into non-aged scaffold did not
express TGF-b (Fig. 6f). This is a significant finding since
TGF-b family members have been reported to improve
tissue healing [24] and to participate in wound healing
Fig. 6 Photomicrographs of
histological sections from
scaffolds seeded with cells.
Sections stained with the
thrichrome stain. a Single cells
(bar 50 lm). b Cluster of cells
(bar 50 lm). c Pyknotic cells
(bar 25 lm). d Polar view of a
cell in metaphase (bar 25 lm).
e Cell clusters into aged
scaffolds with positive
immunostaining for TGF-b(counterstained with
hematoxylin) (bar 50 lm).
f Cell into non-aged scaffold
with negative immunostaining
for TGF-b (bar 25 lm)
Bioprocess Biosyst Eng
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through the stimulation of macrophage recruitment, re-
epithelization and wound contracture [25].
These results strongly suggest that the behavior of cells is
modified by the ageing of the scaffold. There could be an
optimal degree of ageing to cultivate cells for tissue engi-
neering. In our model, we obtained the best condition with
2 weeks of ageing, originating an improved construct, as
compared with the starting material. This exhibits the main
features for tissue formation on an artificial substrate such as
attachment, cell viability, proliferation and migration.
Conclusions
Polymeric scaffolds based on crosslinked Ge/Ch/Ha-
sponges express a phenomenon related with enthalpy
relaxation. Additionally, the physical properties of wet
scaffolds change with time. Treatments based on ageing
allow the design of modified scaffolds.
The cell behavior is affected by the ageing time of the
scaffold. Biological responses of the cell culture as cell
adhesion, viability and proliferation changed with the
ageing of the scaffold. In our experimental model, the best
condition was obtained with a 2 weeks aged scaffold under
cell culture conditions.
Finally, we concluded that the scaffold is not an inert
matrix, and its ageing affects the behavior of cells seeded
on them. The scaffolds used for tissue engineering could be
improved using an ageing treatment under cell culture
conditions. Overall, the bioprocess described herein can be
proposed to build wound and tissue healing medical
devices.
Acknowledgments The authors wish to thank CONICYT from
Chile by FONDECYT Grant 1120166.
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