2. We are going to talk about...
• Why three-dimensional cell cultures?
• What is the technology used for?
• Factors affecting SC differentiation in 3D cultures
• How can it help us—microbial biotechnologists?
• Summary
3. We are going to talk about...
• Why three-dimensional cell cultures?
• What is the technology used for?
• Factors affecting SC differentiation in 3D cultures
• How can it help us—microbial biotechnologists?
• Summary
4. Why three-dimensional cell cultures?
• Growing cells on flat surfaces is artificial and unnatural.
• Naturally ECM plays an important role in regulating cellular behaviors by influencing
cells with: biochemical signals and topographical cues.
• In 3-D cultures, we can control scaffold morphology, architecture and components
(haman).
• Therefore cells behave and respond more like they would in vivo to stimuli.
Blagovic, Katarina, et al. "Engineering cell–cell signaling." Current opinion in biotechnology 24.5 (2013): 940-947.
5. Why three-dimensional cell cultures?
Lee, Jungwoo, Meghan J. Cuddihy, and Nicholas A. Kotov. "Three-dimensional cell culture matrices: state of the art." Tissue
Engineering Part B: Reviews 14.1 (2008): 61-86.
6. Why three-dimensional cell cultures?
• 2D culture substrates not only fall short of reproducing the complex and dynamic
environments of the body, but also are likely to misrepresent findings to some
degree by forcing cells to adjust to an artificial flat, rigid surface 1.
• These matrices, or scaffolds, are porous substrates that can support cell growth,
organization, and differentiation on or within their structure. Architectural and
material diversity is much greater on 3D matrices than on 2D substrates 1.
• Other than physical properties, chemical/ biochemical modification with specific
biological motives to facilitate cell adhesion, cell-mediated proteolytic degradation
and growth factor binding and release 2 .
[1] Lee, Jungwoo, Meghan J. Cuddihy, and Nicholas A. Kotov. "Three-dimensional cell culture matrices: state of the art."
Tissue Engineering Part B: Reviews 14.1 (2008): 61-86.
[2] Lienemann, Philipp S., et al. "A Versatile Approach to Engineering Biomolecule‐Presenting Cellular Microenvironments."
Advanced healthcare materials 2.2 (2013): 292-296.
7. We are going to talk about...
• Why three-dimensional cell cultures?
• What is the technology used for?
• Factors affecting SC differentiation in 3D cultures
• How can it help us—microbial biotechnologists?
• Summary
8. What is the technology used for?
Clinical
application
in vitro studies
Regenerative
medicine
Drug
Discovery
process
Analysis of cell
biology at the
molecular level
Lee, Jungwoo, Meghan J. Cuddihy, and Nicholas A. Kotov. "Three-dimensional cell culture matrices: state of the art."
Tissue Engineering Part B: Reviews 14.1 (2008): 61-86.
9. 3D culture engineering to regenerate tissues
Adopted from: Tandon, Nina, et al. "Bioreactor engineering of stem cell environments."Biotechnology advances 31.7 (2013):
1020-1031.
10. 3D culture engineering to regenerate tissues
• In order to induce cell growth in the third dimension and to support tissue
development, it is critical to provide mass transport to and from all cells using
dynamic culture systems such as bioreactors.
• In bioreactors, stirring, perfusion, and dynamic loading have been applied to
provide convective transport and allow tissue development on a millimeter to
centimeter scale
Tandon, Nina, et al. "Bioreactor engineering of stem cell environments."Biotechnology advances 31.7 (2013): 1020-1031.
Figure adopted from: http://www.tissuegrowth.com/prod_systems.cfm
11. We are going to talk about...
• Why three-dimensional cell cultures?
• What is the technology used for?
• Factors affecting SC differentiation in 3D cultures
• How can it help us—microbial biotechnologists?
• Summary
12. 1. Matrix elasticity/stiffness
CASE STUDY A:
• Cells experience a wide
range of matrix
mechanics, from soft (e.g.
brain 0.1 kPa) to stiffer
(e.g. precalcified bone 80
kPa) tissues, which direct
many aspects of cellular
function. az guvendiren
• Hydrogel mechanics can
be easily controlled by
increasing crosslinking
density.
Engler, Adam J., et al. "Matrix elasticity directs stem cell lineage specification." Cell 126.4 (2006): 677-689.
13. Cigognini, Daniela, et al. "Engineering in vitro microenvironments for cell based therapies and drug discovery." Drug
discovery today 18.21 (2013): 1099-1108.
1. Matrix elasticity/stiffness
14. 2. Mechanical properties
Cigognini, Daniela, et al. "Engineering in vitro microenvironments for cell based therapies and drug discovery." Drug
discovery today 18.21 (2013): 1099-1108.
15. 3. Matrix topology
Lee, Jungwoo, Meghan J. Cuddihy, and Nicholas A. Kotov. "Three-dimensional cell culture matrices: state of the art."
Tissue Engineering Part B: Reviews 14.1 (2008): 61-86.
16. CASE STUDY B:
• Neural stem cells (NSCs) are capable of self-renewal and differentiation into three
principle central nervous system cell types under specific local microenvironments.
3. Matrix topology
Chi-F
Chi-MC
Chi-PS
Wang, Gan, et al. "The effect of topology of chitosan biomaterials on the differentiation and proliferation of neural
stem cells." Acta biomaterialia 6.9 (2010): 3630-3639.
17. Wang, Gan, et al. "The effect of topology of chitosan biomaterials on the differentiation and proliferation of neural
stem cells." Acta biomaterialia 6.9 (2010): 3630-3639.
18. 3. Matrix topology
Cigognini, Daniela, et al. "Engineering in vitro microenvironments for cell based therapies and drug discovery." Drug
discovery today 18.21 (2013): 1099-1108.
19. 4. soluble signaling molecules
• Natural ECM hosts soluble signaling molecules, including growth factors (GFs).
• They play significant roles in tissue development by triggering a wide range of
cellular responses.
• Therefore, it is important to introduce well-controlled GF presentation into
hydrogels to instruct encapsulated stem cell behavior.
• Direct encapsulation is the traditional method of GF presentation in hydrogels.
• Limitations in this approach (e.g. lack of control over delivery profiles) led to the
development of micro/ nano delivery vehicles within hydrogels for GF delivery.
Guvendiren, Murat, and Jason A. Burdick. "Engineering synthetic hydrogel microenvironments to instruct stem
cells." Current opinion in biotechnology24.5 (2013): 841-846.
20. CASE STUDY C:
• Amsden and colleagues reported rapid induction and enhancement of
chondrogenesis of encapsulated adipose-derived stem cells (ASCs) in chitosan-based
hydrogels with coencapsulation of microspheres containing either BMP-6 or TGF-b3 .
4. soluble signaling molecules
Guvendiren, Murat, and Jason A. Burdick. "Engineering synthetic hydrogel microenvironments to instruct stem
cells." Current opinion in biotechnology24.5 (2013): 841-846.
21. 4. soluble signaling molecules
Cigognini, Daniela, et al. "Engineering in vitro microenvironments for cell based therapies and drug discovery." Drug
discovery today 18.21 (2013): 1099-1108.
22. Analytical/Mathematical modeling of 3D cultures
bioreactor
Supporting
3D scaffold
cells
The choice of cells
concerns mainly their
capability to proliferate
and the preservation of
biological activity
The scaffold is not only a
physical support for the
cells, but it also affects cell
metabolism, differentiation,
and morphogenesis
its function is to provide
suitable nutrients and
oxygen flow to the cells in
the scaffold to ensure their
growth and to remove
catabolic products
23. Analytical/Mathematical modeling of 3D cultures
• Mathematical models are very useful in order to better understand the complex
chemical, mechanical, and biological factors involved in engineered tissue cultures.
• Since many studies have highlighted, especially for osteoblasts, the sensitivity of cell
growth to mechanical stress, several studies have been made of fluid dynamics
inside the bioreactor.
• Botchwey calculated the shear stress inside the construct, describing the velocity
with Darcy’s law for porous media.
• Critical for fluid dynamic studies is the identification of scaffold geometry. For this
purpose, optical methods have been used. Raimondi captured a light microscopy
image of a cross section of the construct’s histological sample to generate a
computation fluid dynamics (CFD) model and, then, computed the shear stress
inside a perfused scaffold.
Coletti, Francesco, Sandro Macchietto, and Nicola Elvassore. "Mathematical modeling of three-dimensional cell cultures
in perfusion bioreactors." Industrial & engineering chemistry research 45.24 (2006): 8158-8169.
24. Analytical/Mathematical modeling of 3D cultures
• Cell growth and mass transport are the two major phenomena that affect
bioreactor performance.
• For this reason, efforts have been made to describe cell growth and the supply of
metabolites to the growing cells.
• Nehring proposed a reaction/diffusion model in a spherical chondrocytes pellet.
• Malda developed a mathematical model for oxygen gradient calculations in a three
dimensional polymeric scaffold and compared simulated with experimental data
given by a glass microelectrode.
• Using the method of volume averaging, Pathi developed a dynamical mathematical
model for the growth of haematopoietic cells in a perfusion bioreactor in which the
scaffold is placed between two perfusion chambers where the medium flows.
•
Coletti, Francesco, Sandro Macchietto, and Nicola Elvassore. "Mathematical modeling of three-dimensional cell cultures
in perfusion bioreactors." Industrial & engineering chemistry research 45.24 (2006): 8158-8169.
25. Analytical/Mathematical modeling of 3D cultures
• Various types of bioreactors have been used to culture cells for tissue
regeneration or repair.
• Recent studies show the importance of perfusion (the forcing of medium
flow through the scaffold) in growing a uniform and high-density tissue.
•
Intlet
Outlet
Scaffold
Coletti, Francesco, Sandro Macchietto, and Nicola Elvassore. "Mathematical modeling of three-dimensional cell cultures
in perfusion bioreactors." Industrial & engineering chemistry research 45.24 (2006): 8158-8169.
26. Analytical/Mathematical modeling of 3D cultures
•
Coletti, Francesco, Sandro Macchietto, and Nicola Elvassore. "Mathematical modeling of three-dimensional cell cultures
in perfusion bioreactors." Industrial & engineering chemistry research 45.24 (2006): 8158-8169.
27. Analytical/Mathematical modeling of 3D cultures
Coletti, Francesco, Sandro Macchietto, and Nicola Elvassore. "Mathematical modeling of three-dimensional cell cultures
in perfusion bioreactors." Industrial & engineering chemistry research 45.24 (2006): 8158-8169.
28. We are going to talk about...
• Why three-dimensional cell cultures?
• What is the technology used for?
• Factors affecting SC differentiation in 3D cultures
• How can we—microbial biotechnologists— involve?
• Summary
29. How can we involve?
• Problem: scaffolds can be colonized by bacteria, and the ensuing
infection can have catastrophic consequences.
• Solution case study: “Development of bioactive glass based
scaffolds for controlled antibiotic release in bone tissue engineering
via biodegradable polymer layered coating”.
• Our involvement: Antibiotics can affect ell adhesions and
differentiation....*.
Antimicrobial scaffolds for tissue engineering
[*] Xing, Zhi-Cai, et al. "In vitro assessment of antibacterial activity and cytocompatibility of quercetin-containing PLGA
nanofibrous scaffolds for tissue engineering." Journal of Nanomaterials 2012 (2012): 1.
30. How can we involve?
• Appropriate topology for neuroblastoma differentiation generated by
using a nanocellulose extracellularly excreted by Gluconacetobacter
xylinus.
• Case study: “3D Culturing and differentiation of SH-SY5Y
neuroblastoma cells on bacterial nanocellulose scaffolds”.
• Our involvement: Other potential bacterial products to be used in
3D matrice with optimized geometry for a specific application....
Bacterial nanofibers
31. How can we involve?
• Problem: Immobilization of microbial cells in membranes and
bioreactors provides enhanced catalytic activity and stability,
protecting microorganisms from mechanical degradation and
deactivation and allowing for an overall intensification of biochemical
reactions **.
• Pattern and rate of proliferation and function can be depended on
the matrix properties which should be studied.
Scaffolds with Immobilized Bacteria for 3D
Cultures!
[**] Gutiérrez, María C., et al. "Hydrogel scaffolds with immobilized bacteria for 3D cultures." Chemistry of
materials 19.8 (2007): 1968-1973.
32. We are going to talk about...
• Why three-dimensional cell cultures?
• What is the technology used for?
• Factors affecting SC differentiation in 3D cultures
• How can we—microbial biotechnologists— involve?
• Summary
33. Summary
• 2D cell cultures differ greatly from natural state of cells
in vitro studies are not much reliable.
• 3D culture preparation for any application must be
comprehensively optimized it is complex
• No general mathematical analysis exists.
• Researches are still being conducted in tuning the
cultures.
PICTURE SOURCES FROM LEFT TO RIGHT:
http://www.microtissues.com/three_dimensional_3d_cell_culture_versus_two_dimensional_2d_cell_culture.htm
http://www.medgadget.com/2011/05/new_scaffold_for_controlled_threedimensional_cell_culture.html
http://nextbigfuture.com/2011/03/nanomembrane-tubes-support-controlled.html
http://www.kit.edu/kit/english/pi_2010_790.php
The ECM is variable in different tissues ECM is tissue-specific.
since it does not bear a resemblance to the in vivo architectures where cells flourish at their best.
3-dimensional (3-D) cell culture scaffolds are a better representation of the natural environment experienced by cells in the living organism. Reflecting natural conditions allows for intercellular interactions with more realistic biochemical and physiological responses.
The ECM is variable in different tissues ECM is tissue-specific.
In the body, nearly all
tissue cells reside in an extracellular matrix (ECM) consisting
of a complex 3D fibrous meshwork with a wide distribution
of fibers and gaps that provide complex biochemical
and physical signals.1 az lee2008
internal and external : such as changes in temperature, pH, nutrient absorption, transport, and differentiation.
2-dimensional (2D) surfaces such as micro-well
plates, tissue culture flasks, and Petri dishes because of the
ease, convenience, and high cell viability of 2D culture. az lee 2008
Significant attention has been given to engineering the soluble microenvironment and adhesive scaffolds that emulate the extracellular matrix (ECM). az blagovic2013
from lee 2008
Comparison of natural cell and tissue morphology cultured on 2D and 3D substrates. Natural tissues and cells have distinct 3D organized morphological features: histological images of (A) bone and (D) liver,2 and (G) scanning electron microscope image of the thymus.21 When tissue cells are cultured on 2D substrate, they show a similar morphological pattern (stretched). Optical microscope images of (B) osteoblasts, (E) hepatocytes, and (H) co-culture of lymphocytes and stromal cells.21 Cellular morphology becomes closer to that of natural tissue when cultured on 3D matrices; different appearance of (C) osteoblasts,22 (F) hepatocytes,23 and (I) mononuclear cells in a 3D matrix.
For example, osteoblasts are located on the surface of bone in
a sheet-like arrangement of cuboidal cells, hepatocytes are
closely packed together in the liver in hexagonal-shaped
lobules, and lymphocytes are individually suspended in circulating
blood or lymphatic vessels (Fig. 1).
Applications of 3D matrices can be divided into clinical
and in vitro 3D modeling approaches. Clinical applications
mainly consist of tissue engineering or regenerative medicine,
which target the creation of a functional implants using
artificial 3D matrices.16,17 Scaffolds are designed to be implanted
in a patient as a temporary template to restore or
maintain original tissue function. Accordingly, scaffolds
should not only have proper architecture for supporting cell
growth, but should also match the shape of the defect site.
Materials should be biodegradable and metabolized in the
body without causing serious systemic or immunogenic. lee 2008
use as an in vitro 3D model system. Here, the
aim is to facilitate systematic analysis of cell biology at the
molecular level that will significantly improve the understanding
of tissue physiology and pathophysiology.19,20 For
experiments within this application, the 3D matrix should be
designed to mimic the 3D organization and the differentiated
function of tissues in the body. Three-dimensional matrix
accessibility through optical or other imaging tools and
processability to precisely control matrix properties are important
in this experimental context.
tandon 2013
In the 1990s, it was proposed that 3D human tissue substitutes
could be engineered in vitro by the cultivation of cells on scaffolding
materials, which act as temporary biodegradable templates for tissue
development, in bioreactor systems providing environmental control
and biochemical and biophysical signaling
tandon 2013
In static cultures, mass transport is based on diffusion, and generally limits tissue development to thicknesses less than 0.2 mm due to drops in oxygen tension and increased concentrations of toxic metabolites
In the 1990s, it was proposed that 3D human tissue substitutes
could be engineered in vitro by the cultivation of cells on scaffolding
materials, which act as temporary biodegradable templates for tissue
development, in bioreactor systems providing environmental control
and biochemical and biophysical signaling
ax : http://www.tissuegrowth.com/prod_systems.cfm site ro bara anave bioreac ha bekhun
az stiff
betartib az chap neurogenic/myogenic/osteogenic
Mesenchymal stem cells (MSCs) become adipocyte-like, neuron-like, myocyte-like and osteoblast-like when cultured on substrates having elasticity typical of fat, brain, muscle and cross-linked collagen of osteoid, respectively. az cigognini2013
In the field of drug discovery there is increasing evidence that changes in matrix stiffness influence cancer cell behaviour and sensitivity to therapeutic drugs. Cancer progression in soft tissues is typically associated with an increase in ECM rigidity [86,87]. haman
Examples of how mechanical forces have been applied in cell culture studies and tissue engineering strategies to affect stem cell fate, extracellular matrix (ECM) synthesis, and cell phenotype and proliferation. Abbreviations: MSCs, mesenchymal stem cells. ac cigognini
Overview of polymer processing techniques for obtaining porous scaffolds. Macro-scale structure of (A) an electrospun fibrous
mesh sheet and (B) a poly(lactic-co-glycolic acid) scaffold.160 Micro-scale fibrous structures: (C),161 (D),162 (E),152 and micro-scale
sponge-like structures: (F),163 (G),163 (H).147 Nano-scale (I) alginate-based nanofibers164 and (J) surface topology after sodium hydroxide
treatment.165 Modification of polymer processing techniques: (K) compartmented scaffold structures,155 (L) nano-fibrous scaffolds,48 and
(M) inverted colloidal crystal scaffolds. az lee2008
wang2010
Chitosan films (Chi-F), chitosan porous scaffolds (Chi-PS) and chitosan multimicrotubule conduits (Chi-MC) were used to investigate their effects on the differentiation and proliferation of NSCs isolated from the cortices of fetal rats.
Fig. 1. SEM characterization of three different topological chitosan biomaterials. (a) Chi-F; (b) Chi-PS; (c) cross-section of Chi-MC; (d) longitudinal section of Chi-MC. Scale
bar: 100 lm.
These observations indicate that chitosan topology can play an important role in regulating differentiation and proliferation of NSCs and raise the possibility of the utilization of chitosan in various structural biomaterials in neural tissue engineering.
Immunofluorescence analysis of NSCs cultured on three different topological chitosan biomaterials in the presence of 10% FBS for 5 days. (a and b) Cells cultured on
Chi-F; (c) cells on Chi-PS; (d) cells on Chi-MC. The differentiated cells were verified using anti-b-tubulin III antibody (red) and anti-GFAP antibody (green), with the nuclei
counterstained with DAPI. Scale bars: (a) 100 lm; (b–d) 20 lm.
The ratio of b-tubulin III-positive cells. Error bars represent means ± SD
(n = 3). **P < 0.01.
SEM images of NSCs cultured on three different topological chitosan biomaterials in the presence of 10% FBS for 5 days. (a and b) Cells cultured on Chi-F; (c and d) cells
on Chi-PS; (e and f) cells on Chi-MC. Scale bars: (a, b and d–f) 10 lm; (c) 100 lm. Arrows indicate the cells.
NSCs cultured on
Chi-F in the presence of 10% FBS preferentially differentiated into
astrocytes and showed the highest proliferation in serum-free
medium in the presence of 20 ng ml1 bFGF. Chi-MC significantly
promoted neuronal differentiation and acceptable proliferation.
However, Chi-PS did not perform well in either regulation of NSC
differentiation
The differentiation and proliferation properties of NSCs
cultured on Chi-MC might be exploited in the treatment of spinal
cord injuries. The utilization of different topological chitosan biomaterials
to control NSCs behavior could result in the design of
more efficient biomaterials for neural tissue engineering.
Examples of how topographical cues influence cell behaviour in vitro. Abbreviation: MSCs, mesenchymal stem cells. from cigognini2013
az lee2008
az guvendiren
az guvendiren
In contrast to physical encapsulation techniques, covalent tethering of GFs to the hydrogel provides long-term control over GF availability; however, this approach may affect the activity of GFs due to possible changes in protein conformations or hindrance of active binding sites An alternative approach is to harness endogenous GF activity by mimicking noncovalent interactions of proteoglycans (PGs) and glycosaminoglycans (GAGs) with GFs [53], such as with the covalent or noncovalent incorporation of chondrotin sulfate or heparin sulfates into hydrogels to sequester GFs [54,55]. For instance, the stimulation and sequestering of BMP2 within heparin-functionalized PEG hydrogels promoted hMSC osteogenesis [56]. In some occasions, heparin binding GFs can exhibit direct reversible binding to the hydrogels, such as in alginate hydrogels, enabling sustained and localized release [15,57]. These approaches represent another step toward controlling stem cell signaling with synthetic hydrogels.
The effect of the localized release
of BMP-6 and TGF-β3 from P(TMC-CL)2-PEG microspheres on the chondrogenic differentiation of the
encapsulated ASCs in the RGD-grafted gels was assessed over 28 days. Based on gene and protein expression
data, the ASCs were directed towards the chondrogenic lineage more rapidly when induced with BMP-6 and
TGF-β3 delivered from the embedded microspheres, as compared to growth factor supplementation in the
culture medium. Overall, injectable, in situ gelling N-methacrylate glycol chitosan grafted with a cell adhesive
peptide shows great potential for the minimally invasive delivery of ASCs. Further, the localized, controlled
co-delivery of BMP-6 and TGF-β3 using microspheres may be a promising alternative to enhance the
chondrogenic differentiation of human ASCs.
In addition, the biological half-life of most growth factors is
short (in the range of minutes), emphasizing the importance of controlled, continuous release within a
protective delivery vehicle
az suarto2012 disscusiion ash ham bekhun
az cigognini
Routinely, cells are cultured under hyperoxic conditions (21% O2), although physiological conditions in several adult and developing tissues are hypoxic. Considerable effort is ongoing to adjust oxygen levels of cultured cells with the desired tissue engineering application. Examples of how hypoxia influences stem cell fate and matrix production are shown. Abbreviations: ECM, extracellular matrix; MSCs, mesenchymal stem cells; NSCs, neural stem cells; ESCs, embryonic stem cells.
Indeed, in vitro and in vivo data convincingly demonstrate that molecular oxygen levels regulate cell behaviour and play a significant part in developmental pro-cesses, such as angiogenesis, haematopoiesis and morphogenesis [91]. Therefore, a considerable research effort has been directed towards optimisation of oxygen supplementation for in vitro engi-neering (Fig. 3) of various tissues [92], including cartilage [93,94], tendon [95], bone [96,97], intervertebral disc [98], nucleus pulpo-sus [99] and heart [100,101].
Recent studies also demonstrate that oxygen tension is of paramount importance in maintaining stem cell niche and stem cell commitment towards a specific lineage [109]. In MSC cultures it has been shown that low oxygen tension (5% O2) retains their undifferentiated and multipotent status [110,111]. Moreover, dif-ferent oxygen concentrations have been employed to stabilise a chondrogenic phenotype or to promote hypertrophy of cartilagi-nous grafts, suggesting a possible application for cartilage repair therapies or endochondral bone repair strategies, respectively [112]. Human ESCs maintain pluripotency at oxygen tensions between 3% and 5%, whereas they spontaneously differentiate when cultured at 21% O2 [113]. This is not surprising considering the relatively oxygen-poor environment in which the mammalian embryo develops.
Both experiments and
quantitative mathematical models are needed to better understand the physical, mechanical, and biochemical
phenomena and for the rational design of suitable reactor geometries and operating protocols for the production
of functional engineered artificial grafts. az ie051144v
Multifactorial and interdisciplinary approaches are likely to make an impact in the years to come and lead to clinically relevant in vitro tissue equivalents, providing suitable analysis systems are developed. cigognini
az ie051144v
The tissue
reconstruction is based on three fundamental components:
az ie051144v
az ie051144v
az ie051144v
Schematic representation of a typical perfusion bioreactor: the
medium flows directly through the pores of the scaffold (shaded area)
transporting oxygen and other substrates to the cells seeded on the pores
surface and removing catabolic products.
az ie051144v
Reference geometry and system coordinates for a total perfusion
bioreactor. H and R are the scaffold height and radius; L1 and L2 are,
respectively, the lengths of inlet and outlet sections. The three domains for
the model in section 3, ¿1, ¿2, and ¿3, are indicated.
2.1. Geometry. Figure 3 shows the cross section of a
cylindrical bioreactor and gives the reference coordinates and
dimensions used in the mathematical representation. The
medium fluid is fed from the bottom of the bioreactor by a
volumetric peristaltic pump, flows through an empty inlet
section, then perfuses the scaffold, and exits from the top
through another empty exit section. Since the flow regime inside
the empty sections of the bioreactor is different from that inside
the scaffold porous medium, the reactor is divided into three
distinct subdomains, as indicated in Figure 3:
¥ ¿1 is an empty inlet section of height L1.
¥ ¿2 is a scaffold section of height H.
¥ ¿3 is an empty outlet section of height L2.
All sections have radius R. The medium flow is assumed to
be laminar at the entrance of the inlet section ¿1 (this
assumption is justified later in the paper). The scaffold is
characterized in terms of the usual properties of a porous
medium (porosity, tortuosity, void fraction, and permeability).
The scaffold void is saturated by the fluid medium that is
assumed to be monophase. In this work, we consider in
particular a scaffold made of collagen sponges.
The mass transport within EBs has been measured
experimentally128 and modeled mathematically165 as a
function of the EB size (radius), ECM composition,
cell packing density and molecular uptake rate. az kinney 2014
az ie051144v
Interacting phenomena in a perfusion bioreactor. In this network
diagram, each arrow corresponds to a mathematical equation or equation
set: line A to eqs 2, 3, 18, and 19; line B to eqs 1 and 14; line C to eq 25;
line D to eq 27; line E to eq 29; line F to eq 30; line G to eq 31; line H to
eq 32; line I to eq 26; line J to eq 27.
Living cells are complex systems, and a complete model
should include their metabolism, growth, and death mechanisms
in addition to other age-dependent aspects.
In addition, hydrochloride tetracycline loaded in either alginate or gelatin coatings was released rapidly at the initial stage (∼1 h), while the released rate subsequently decreased and was sustained for 14 days in phosphate buffered saline. Therefore, these layered polymer coated scaffolds exhibit attractivecharacteristics in terms of improved mechanical properties and controlled drug release, simultaneously with the added advantage that the drug release rate is decoupled from the intrinsic scaffold Bioglass degradation mechanism. The layered polymer coated scaffolds are of interest for drug-delivery enhanced bone regeneration applications. case study
Two types of bacteria strains, Staphylococcus aureus (SA) and Klebsiella pneumoniae (KP), were used to evaluate the antibacterial properties of the scaff. our involve az In vitro assessment of antibacterial activity and cytocompatibility of quercetin-containing PLGA nanofibrous scaffolds for tissue engineering
BNC is extracellularly excreted by Gluconacetobacter xylinus (G. xylinus) in the shape of long non-aggregated nanofibrils. The cellulose network created by G. xylinus has good mechanical properties, 99% water content, and the ability to be shaped into 3D structures by culturing in different molds.Read More: http://informahealthcare.com/doi/abs/10.3109/21691401.2013.821410
This 3D model based on BNC scaffolds could possibly be used for developing in vitro disease models, when combined with human induced pluripotent stem (iPS) cells (derived from diseased patients) for detailed investigations of neurodegenerative disease mechanisms and in the search for new therapeutics.Read More: http://informahealthcare.com/doi/abs/10.3109/21691401.2013.821410