Tissue Engineering slides

According to Professor Robert Langer:
Tissue Engineering is the field which applies principles of Biology and Engineering
to the development of functional substitutes for damaged tissues(Langer et al. 1993).
Video explaining what tissue engineering is:
https://www.youtube.com/watch?v=7Q3S6q97FiU

https://en.wikipedia.org/wiki/Tissue_engineeri
Process of Tissue Engineering:
1. Initially, cells are being isolated from the patient.
2. Secondly, those cells are cultivated until a “cell bank” is created.
3. Then, different biomaterials are utilized in order to fabricate scaffolds.
4. The next step is to seed the scaffold with cells.
5. The seeded scaffolds can also be bathed with growth factors, as well as they can
be mechanically altered (compressive load, hydrostatic pressure) in order to
stimulate cellular growth and proliferation (bioactive environment).
6. Finally, the engineered scaffolds along with the cells are placed in a bioreactor,
a device which mimics the conditions inside the body (Lanza et al. 2007).
Video showing a heart valve scaffold
inside a muscle ‘like’ bioreactor:
https://www.youtube.com/watch?v=EF
m9qbhsL_A

1. Stem Cells
What are Stem Cells?
Stem cells are cells that (1) can self-renew and (2) have the potential to
differentiate along one or two lineages. The types of progeny a stem cell can
produce determine how it is named (Bernhard Palsson, 2004):
1. Totipotent  Can produce all cell types
2. Pluripotent  Can produce most cell types
3. Unipotent  Can produce one cell type
An illustrating video
explaining what stem cells
are:
https://www.youtube.com/w
atch?v=evH0I7Coc54

1. Stem Cells
What do stem cells look like?
They are small spherical cells that are about 6 to 8 μm in diameter and have
no particular morphological features. They appear to divide rarely and may
commit to growth and differentiation in a stochastic manner, with a first order
rate constant that is about one per six weeks (Tissue Engineering, 2004).
Which tissues have stem cells?
Tissues have their own characteristic replacement times. The more rapidly
proliferating tissues, such as bone marrow, small intestinal epithelium , muscle
and skin, all appear to have stem cell systems( G. Bain, 1995, D.R Campion,
1987, J. Jankowski, 1992). The same seems to be true for organs with slow
turnover times, such as the liver, brain and even the β-islets in the pancreas (K.
Aterman, 1992, S. Sigal, 1992, T. Zigova, 1998).
Stem cells build tissue
Stem-cell commitment along differentiated lineages underlies organ function,
repair and formation. The cellular-fate processes of cell proliferation, cell
death, cell motion and cell differentiation together determine the fate of the
committed cell. Stem cells are the starting material for many key processes in
tissue engineering and must be considered as an important source of
regenerative potential (Bernhard Palsson, 2004).

1.1 Embryonic Stem Cells
 Embryonic stem cells (ESC) are derived from human preimplantation embryos
formed during infertility treatment of couples for in vitro fertilization
(Principles of Tissue Engineering, 2007).
 The embryonic stem cells can self-renew, apparently without limit in culture
and are pluripotent- that is, they can give rise to any cell type in the body (Amit
et al., 2000; Evans and Kaufmann, 1981; G.R Martin, 1981).
This microscope image (400x magnification) shows an oval cluster of
roughly 1,000 human embryonic stem cells growing together as a colony.
www.stemcellresearch.umich.edu
Illustrating video
explaining what an ESC is:
https://www.youtube.com/
watch?v=uC0fLXdu56g

1.1 Embryonic Stem Cells
 A central issue that must be addressed for tissue-engineered products derived
from ES cells is immune rejection based on mismatches at genetic
histocompatibility loci (Lysaght, 2003).
 Therapeutic cloning offers a potential means to generate cells with the exact
genetic constitution of each individual patient so that immune rejection of grafts
should not occur.
 The clinical application of ES cells for tissue engineering will depend on the
development of robust methods to isolate and grow them under conditions
consistent with good manufacturing practice and regulatory review for safety
(Amit et al. , 2003).
 Perhaps the greater challenge remains in directing the differentiation of human
ES cells to a given desired lineage with high efficiency.

1.2 Adult Stem Cells
 Adult stem cells are undifferentiated cell, found among differentiated cells in a
tissue or organ. It can renew itself and can differentiate to yield some or all of
the major specialized cell types of the tissue or organ.
 The primary roles of adult stem cells in a living organism are to maintain and
repair the tissue in which they are found.
Adult Neural Stem Cells. Source: Cell Life Medical
Illustrating video
explaining what an adult
stem cell is:
https://www.youtube.co
m/watch?v=kgHAUmV45
Gc

1.3 Induced Pluripotent Stem Cells
 Induced Pluripotent Stem Cells are adult cells that have been genetically
reprogrammed to an embryonic stem cell–like state by being forced to express
genes and factors important for maintaining the defining properties of
embryonic stem cells (Lanza et al., 2007).
 Although these cells meet the defining criteria for pluripotent stem cells, it is
not known if iPSCs and embryonic stem cells differ in clinically significant
ways. Mouse iPSCs were first reported in 2006, and human iPSCs were first
reported in late 2007 (Lanza et al., 2007).
 Although additional research is needed, iPSCs are already useful tools for drug
development and modeling of diseases. The iPSC strategy creates pluripotent
stem cells that, together with studies of other types of pluripotent stem cells,
will help researchers learn how to reprogram cells to repair damaged tissues in
the human body (Lanza et al., 2007).

1.4 Differences between Embryonic and Adult Stem
Cells
 One major difference between adult and embryonic stem cells is their different
abilities in the number and type of differentiated cell types they can become.
Embryonic stem cells can become all cell types of the body because they are
pluripotent. Adult stem cells are thought to be limited to differentiating into
different cell types of their tissue of origin (Lanza et al., 2007).
 Embryonic stem cells can be grown relatively easily in culture. Adult stem cells
are rare in mature tissues, so isolating these cells from an adult tissue is
challenging, and methods to expand their numbers in cell culture have not yet
been worked out. This is an important distinction, as large numbers of cells are
needed for stem cell replacement therapies (Lanza et al., 2007).

1.5 Cell Differentiation
 Cellular differentiation: is the process where a cell changes from one cell type to
another. Most commonly this is a less specialized type becoming a more specialized
type, such as during cell growth. Differentiation occurs numerous times during the
development of a multicellular organism as it changes from a simple zygote to a
complex system of tissues and cell types.
Source: Choi et al.
,2009

1.6 Cell Sources
 Autologous: Come from the person that needs the new cells.
 Allogeneic: Come from a body from the same species.
 Xenogenic: Come from a different species then the organism they’re going into.
Source: Slideplayer

2. Scaffolds
 Scaffolds are 3-dimensional materials constructed in order to provide
structure to a developing tissue and to allow cells to adhere, proliferate,
differentiate and most importantly, secrete extracellular matrix (ECM)
(Leong MF. et al., 2009).
 Many different materials have been investigated in order to construct scaffolds
such as polymers (PLA, PGA, PCL, PEG), bioactive ceramics (HA, TCP) as
well as natural polymers (Collagen, GAGs, Chitosan).
Source:Smith, B. D, 2015.
Example of a fixed-shape
bone scaffold.

2.1 Scaffold construction requirements
In order to engineer a successful scaffold, a plethora of requirements should be
met, such as:
1. Architecture: Scaffolds should provide void volume for vascularization,
new tissue formation and remodeling so as to facilitate host tissue
integration upon implantation. The biomaterials should be processed to
give a porous enough structure for efficient nutrient and metabolite
transport without significantly compromising the mechanical stability of
the scaffold. Moreover, the biomaterials should also be degradable upon
implantation at a rate matching that of the new matrix production by the
developing tissue( Berger J, et al., 2004).
2. Cyto- and tissue compatibility: Scaffolds should provide support for
either extraneously applied or endogenous cells to attach, grow and
differentiate during both in vitro culture and in vivo implantation. The
biomaterials used to fabricate the scaffolds need to be compatible with
the cellular components of the engineered tissues and endogenous cells in
host tissue ( Berger J, et al., 2004).

2.1 Scaffold construction requirements
3. Bioactivity: Scaffolds may interact with the cellular components of the
engineered tissues actively to facilitate and regulate their activities. The
biomaterials may include biological cues such as cell-adhesive ligands to
enhance attachment or physical cues such as topography to influence cell
morphology and alignment. The scaffold may also serve as a delivery
vehicle or reservoir for exogenous growth-stimulating signals such as
growth factors to speed up regeneration (Discher DE, et al., 2005).
4. Mechanical property: Scaffolds provide mechanical and shape stability
to the tissue defect. The intrinsic mechanical properties of the
biomaterials used for scaffolding or their post-processing properties
should match that of the host tissue. Exerting traction forces on a
substrate, many mature cell types, such as epithelial cells, fibroblasts,
muscle cells, and neurons, sense the stiffness of the substrate and show
dissimilar morphology and adhesive characteristics (Engler AJ, et al.,
2006).

2.2 Scaffolds synthesis
A number of different methods has been introduced for preparing porous
structures to be employed as tissue engineering scaffolds. Each of these
techniques presents its own advantages, but none are free of drawbacks.
1. Nanofiber self-assembly: Molecular self-assembly is one of the few
methods for creating biomaterials with properties similar in scale and
chemistry to that of the natural in vivo extracellular matrix (ECM), a
crucial step toward tissue engineering of complex tissues. Moreover,
these hydrogel scaffolds have shown superiority in in vivo toxicology
and biocompatibility compared to traditional macro scaffolds and animal-
derived materials (Cassidy JW, 2014).
2. Textile technologies: These techniques include all the approaches that
have been successfully employed for the preparation of non-woven
meshes of different polymers. In particular, non-woven polyglycolide
structures have been tested for tissue engineering applications: such
fibrous structures have been found useful to grow different types of cells.
The principal drawbacks are related to the difficulties in obtaining high
porosity and regular pore size(Ekevall E, 2004).

3. Freeze- drying: First, a synthetic polymer is dissolved into a suitable solvent
(e.g. polylactic acid in dichloromethane) then water is added to the polymeric
solution and the two liquids are mixed in order to obtain an emulsion. Before
the two phases can separate, the emulsion is cast into a mold and quickly
frozen by means of immersion into liquid nitrogen. The frozen emulsion is
subsequently freeze-dried to remove the dispersed water and the solvent, thus
leaving a solidified, porous polymeric structure (Haugh MG, 2010).
4. Electrospinning: A highly versatile technique that can be used to produce
continuous fibers from submicrometer to nanometer diameters. In a typical
electrospinning set-up, a solution is fed through a spinneret and a high
voltage is applied to the tip. The buildup of electrostatic repulsion within the
charged solution, causes it to eject a thin fibrous stream. A mounted collector
plate or rod with an opposite or grounded charge draws in the continuous
fibers, which arrive to form a highly porous network. The primary
advantages of this technique are its simplicity and ease of variation. At a
laboratory level, a typical electrospinning set-up only requires a high voltage
power supply (up to 30 kV), a syringe, a flat tip needle and a conducting
collector. For these reasons, electrospinning has become a common method
of scaffold manufacture in many labs. By modifying variables such as the
distance to collector, magnitude of applied voltage, or solution flow rate
researchers can dramatically change the overall scaffold architecture
(Lannutti J, et al., 2007).

Source: Alaribe et al, 2016

3. Bioreactors
 A tissue engineering bioreactor can be defined as a device that uses
mechanical means to influence biological processes (Darling and Athanasiou,
2003).
 Bioreactors can be used to aid in the in-vitro development of new tissue by
providing biochemical and physical regulatory signals to cells and encouraging
them to undergo differentiation and/or to produce ECM prior to in-vivo
implantation (Darling and Athanasiou, 2003).
Source: Awad Lab, University of Rochester
Video showing a bioreactor for
muscle fibers:
https://www.youtube.com/watch?v=X
mDeaP6n9vA

3.1 Introduction to Bioreactors
 Cells do respond to mechanical stimulation and bioreactors can be used to apply
such mechanical stimulation to cells. Such stimuli encourage cells to produce
extracellular matrix (ECM) in a shorter time period and in a more
homogeneous manner than would be the case with static culture.
 According to Carver, PGA scaffolds seeded with equine articular chondrocytes
expressed significantly improved ECM protein levels when cultured under
hydrostatic pressure in comparison with the same scaffolds cultured in static
medium.
 Another important application of bioreactors is in cellular differentiation.
Mechanical stimulation can be used to encourage stem cells down a particular
path and hence provide the cell phenotype required.

 As well as providing mechanical stimulation, bioreactors can also be used to
improve cellular spatial distribution.
 A heterogeneous cell distribution is a major obstacle to developing any 3-D
tissue or organ in-vitro. Defects requiring tissue engineering solutions are
typically many millimeters in size (Goldstein, et al., 2001).
 Scaffolds in such a size range are easily fabricated, however, problems arise
when culturing cells on these scaffolds. Static culture conditions result in
scaffolds with few cells in the centre of the construct (Cartmell, et al., 2003).
 It has been shown that despite homogeneous cell seeding, after long periods in
culture, more cells are found on the periphery of constructs (Cartmell, et al.,
2003), leading to peripheral encapsulation which hinders nutrients and waste
exchange from the centre, resulting in core degradation of TE constructs.
 Thus, bioreactors can be used in TE applications to overcome problems
associated with traditional static culture conditions.

 According to Vunjak-Novakovic, bioreactors are designed to
perform at least one of the following five functions:
1. Provide a spatially uniform cell distribution
2. Maintain the desired concentration of gases and nutrients in culture
medium
3. Facilitate mass transport to the tissue
4. Expose the construct to physical stimuli
5. Provide information about the formation of 3-D tissue

3.2 Bioreactor Design Requirements
 The design of a bioreactor should be as simple as possible e.g. avoiding the
introduction of machined recesses which could become breeding grounds for
micro-organisms.
 Simplicity in design should also mean that the bioreactor is quick to assemble
and disassemble. Apart from being more efficient, this ensures that cell-seeded
constructs inserted into the bioreactor are out of the incubator for the maximum
amount of time possible.
 The material selection is very important as it is vital to ensure that the materials
used to create the bioreactor do not elicit any adverse reaction from the cultured
tissue.
 Any material which is in contact with media must be biocompatible or bioinert.
This eliminates the use of the most metals except for stainless steel and
titanium.

3.2 Bioreactor Design Requirements
 Materials must be usable at 37ο C in a humid atmosphere. They must be able to
be sterilized if they are to be re-used.
 Materials with different properties are needed for various components in the
bioreactor. For example, transparent materials can be of benefit in allowing the
construct to be monitored in the bioreactor during culture while flexible tubing
can help with assembly of the bioreactor.
 If various parameters such as pH, nutrient concentration or oxygen levels are to
be monitored, these sensors should be incorporated into the design.
 The forces needed for cellular stimulation are very small so it is important to
ensure that the pump motor has the capability to apply small forces accurately.

3.3 Types of Bioreactors
 Numerous types of bioreactors are used in various tissue
engineering applications such as:
1. Spinner Flask Bioreactor
2. Rotating Wall Bioreactor
3. Compression Bioreactor
4. Strain Bioreactor
5. Hydrostatic Pressure Bioreactors
6. Flow Perfusion Bioreactor

3.3.1 Spinner Flask Bioreactor
 A spinner flask bioreactor induces mixing of oxygen and nutrients throughout
the medium and reduces the concentration boundary layer at the construct
surface (Goldstein. et al., 2001).
 Scaffolds are suspended at the end of needles in a flask of culture media. A
magnetic stirrer mixes the media and the scaffolds are fixed in place with
respect to the moving fluid (Goldstein. et al., 2001).
 Typically, spinner flasks are around 120mL in volume and run at 50-80rpm and
50% of the medium used in them is changed every two days (Vunjak-
Novakovic, 2000).

3.3.1 Spinner Flask Bioreactor
Video showing spinner flask
bioreactors inside an incubator:
https://www.youtube.com/watch?
v=IwKDynxNAKE
Source: Max Planck Institute,
Monitoring, Design and Optimization of
Bioprocesses
Source: Partak, et al., Intech

3.3.2 Rotating Wall Bioreactor
 The rotating wall bioreactor was developed by NASA (Schwarz et al., 1992).
 Scaffolds are free to move in media in a vessel. A rotating wall vessel bioreactor
consists of a cylindrical chamber in which the outer wall, inner wall, or both are
capable of rotating at a constant angular speed. The vessel wall is then rotated
at a speed such that a balance is reached between the downward gravitational
force and the upward hydrodynamic drag force acting on each scaffold (Freed
et al., 1997).
 The wall of the vessel rotates, providing an upward hydrodynamic drag force
that balances with the downward gravitational force, resulting in the scaffold
remaining suspended in the media (Freed et al., 1997).
 Media can be exchanged by stopping the rotation temporarily or by adding a
fluid pump whereby media is constantly pumped through the vessel (Freed et
al., 1997).
 Gas exchange occurs through a gas exchange membrane and the bioreactor is
rotated at speeds of 15-30 rpm (Freed et al., 1997).

3.3.2 Rotating Wall Bioreactor
Video showing a rotating wall
bioreactor:
https://www.youtube.com/watch?v=pn
_pqMa23Nw
Source: Haj et al., 2015
Source: Bartis et al., 2011

3.3.3 Compression Bioreactors
 This class of bioreactors is generally used in cartilage engineering and can be
designed so that both static and dynamic loading can be applied (Darling and
Athanasiou, 2003).
 In general, compression bioreactors consist of a motor, a system providing
linear motion and a controlling mechanism used to provide displacements of
different magnitudes and frequencies. A signal generator can be used to control
the system including load cells while transformers can be used to measure the
load response and imposed displacement (Huang, et al., 2004).
 The load can be transferred to the cell-seeded constructs via flat platents which
distribute the load evenly (Thorpe, et al., 2008).

3.3.3 Compression Bioreactors
Source: Bartis et al., 2011
Source: McHenry, 2005
Video showing a compression
bioreactor:
https://www.youtube.com/watch?v=O3
6YYp0ZIoU

3.3.4 Strain Bioreactors
 Strain bioreactors have been used in an attempt to engineer a number of
different types of tissues including tendon, ligament, bone, cartilage and
cardiovascular tissue.
 Some designs are very similar to compression bioreactors, only differing in the
way the force is transferred to the construct. Instead of flat platens as in a
compression bioreactor, a way of clamping the scaffold into the device is
needed so that a tensile force can be applied.
 Tensile strain has been used to differentiate MSC along the chondrogenic
lineage. A multistation bioreactor was used in which cell-seeded collagen
glycosaminoglycans scaffolds were clamped and loaded in uniaxial tension
( McMahon, et al., 2008).

3.3.4 Strain Bioreactors
Source: Goodhart et al., 2014
Source: Breen, 2006
Uniaxial Strain Bioreactor for
Engineered Ligaments :
https://www.youtube.com/watc
h?v=FXCqcyNK0nM

3.3.5 Hydrostatic Pressure Bioreactors
 In cartilage tissue engineering, HP bioreactors can be used to apply mechanical
stimulus to cell-seeded constructs. Scaffolds are usually cultured statically and
then moved to a hydrostatic chamber for a specified time for loading.
 HP bioreactors consist of a chamber which can withstand the pressure applied
and a means of applying that pressure (Darling and Athanasiou, 2003).
 For example, a media-filled pressure chamber can be pressurised using a piston
controlled by an actuator (Darling and Athanasiou, 2003). For sterility, the
piston can apply pressure via an impermeable membrane so that the piston itself
does not come in contact with the culture media.
 Variations on this design include a water-filled pressure chamber which
pressurises a media media-filled chamber via an impermeable film and is
controlled using a variable backpressure valve and an actuator (Watanabe, et al.,
2005).

3.3.5 Hydrostatic Pressure Bioreactors
Source: Eric Lima, Cooper
Union Engineering Faculty
Video Showing a HP bioreactor:
https://www.youtube.com/watch?
v=7sOKS2YQDq4
Source: Darling and
Athanasiou, 2004

3.3.6 Flow Perfusion Bioreactors
 Culture using flow perfusion bioreactors has been shown to provide more
homogeneous cell distribution throughout scaffold.
 In comparisons between flow perfusion, spinner flask and rotating wall
bioreactors, flow perfusion bioreactors have proved to be he best for fluid
transport.
 Flow perfusion bioreactors generally consist of a pump and a scaffold chamber
joined together by tubing. A fluid pump is used to force media flow through the
cell-seeded scaffold. The scaffold is placed in a chamber that is designed to direct
flow through the interior of the scaffold. The scaffold is kept in position across the
flow path of the device and media is perfused through the scaffold, thus enhancing
fluid transport.
 Media can easily be replaced in the media reservoir

Source: Jaasma, et al., 2008
3.3.6 Flow Perfusion Bioreactors
Source:
https://www.hindawi.com/
journals/bmri/2009/873816
/fig1/
A 3-D Perfusion Bioreactor:
https://www.youtube.com/watch?v=X
LC49jyj5EE

4. Bioactive Environment
 A Bioactive environment in tissue engineering can be created with the
utilization of:
1. Growth Factors
2. Hormones
3. Cytokines
Source: Lee, et al., 2010

4.1 Growth Factors
 Growth factors are protein molecules made by the body. They function to
regulate cell devision and cell survival. GF can also be produced via genetic
engineering in the lab and used in biological therapy.
 GF bind to receptors on the cell surface, with the result of activating cellular
proliferation and/or differentiation. GFs are quite versatile, stimulating cellular
devision in numerous different cell types.
 GFs secrete diffusible factors that are identified in the conditioned medium of
cell cultures. Examples for GFs are: EGF, FGF, NGF, PDGF, IGF , BMP,
HGF, GDF and many others.

4.1 Growth Factors
 Hematopoietic growth factors are hormone-like substances that stimulate bone
marrow to produce blood cells. Shortages of blood cells cause most of the
symptoms in people with MDS, the use of growth factors is very appealing.
 Erythropoietin is a growth factor which promotes red blood cells production.
Interleukin-11 stimulates platelet production after chemotherapy.
 The sequence of amino acids permits GFs to be placed into families, suggesting
that they evolved from a single ancestral protein. The insulin family comprises
of somatemedins A and C, insulin, insulin like GF (IGF) and multiplication-
stimulating factor (MSF). A 2nd family consists of sarcoma growth factor
(SGF), transforming growth factors (TGFs) and epidermal growth factors
(EGF).

4.1 Growth Factors
Video illustrating the role of GFs
https://www.youtube.com/watch?v=I3T7Tg_Y90ISource: Slideshare.net

4.2 Hormones
 Hormones are chemical messengers that carry and travel signals in the blood
stream from 1 cell or glands to other tissues and organs so as to maintain
chemical levels in the bloodstream that achieve homeostasis. All cellular
organisms produce hormones.
 Hormones also regulate the function of their target cells which express a
receptor for the hormone. The action of hormones is determined by numerous
factors such as its pattern of secretion and the response of the receiving tissue.
 Though few hormones circulate dissolved in the blood-stream, most are carried
in the blood, bound to plasma proteins.
 An example of antagonistic pairs of hormones is the Insulin, which causes the
level of glucose to drop when it has risen and Glucagon causes blood sugar to
rise when it has fallen.

4.2 Hormones
 There are two major classes of hormones.
 1. Proteins, peptides and modified amino acids
 2. Steroids
 In general, steroids are sex hormones related to sexual maturation and fertility.
Steroids are made from cholesterol by placenta by our adrenal gland or gonads.
 Peptides regulate functions such as sleep and sugar concentration. They are
made from long strings of amino acids, so sometimes they are referred to as
“protein” hormones. Growth hormones for example, help us burn fat and build
up muscles.
 Hormones work slowly, over time and affect many different processes in the
body such as Growth and development, metabolism, Sexual function and
Reproduction mood.

4.2 Hormones
.
Mechanisms of Hormones:
https://www.youtube.com/watch?v=TgNwxF3a
QpE
Source:
http://www.argosymedical.co
m/Cellular/

4.3 Cytokines
 Cytokines are small secreted proteins released by cells have a specific effect on
the interactions and communications between cells (Zhang, et al., 2009).
 Cytokine is a general name; other names include lymphokine (cytokines made
by lymphocytes), monokine (cytokines made by monocytes), chemokine
(cytokines with chemotactic activities), and interleukin (cytokines made by one
leukocyte and acting on other leukocytes (Zhang, et al., 2009).
 Cytokines are made by many cell populations, but the predominant producers
are helper T cells (Th) and macrophages. Cytokines may be produced in and by
peripheral nerve tissue during physiological and pathological processes by
resident and recruited macrophages, mast cells and endothelial cells (Zhang, et
al., 2009).
.

4.3 Cytokines
 Proinflammatory cytokines are produced predominantly by activated
macrophages and are involved in the up-regulation of inflammatory reactions.
There is abundant evidence that certain pro-inflammatory cytokines such as IL-
1β, IL-6, and TNF-α are involved in the process of pathological pain (Xie, et
al.,2006).
 IL-1β is released primarily by monocytes and macrophages as well as by
nonimmune cells, such as fibroblasts and endothelial cells, during cell injury,
infection, invasion, and inflammation (De Leo, et al., 1996).
 IL-6 has been shown to play a central role in the neuronal reaction to nerve
injury. Suppression of IL-6R by in vivo application of anti-IL-6R antibodies led
to reduced regenerative effects. IL-6 is also involved in microglial and
astrocytic activation as well as in regulation of neuronal neuropeptides
expression (De Leo, et al., 1996).
.

4.3 Cytokines
 The anti-inflammatory cytokines are a series of immunoregulatory molecules
that control the pro-inflammatory cytokine response. Cytokines act in concert
with specific cytokine inhibitors and soluble cytokine receptors to regulate the
human immune response (Schafers, et al., 2003).
 Their physiologic role in inflammation and pathologic role in systemic
inflammatory states are increasingly recognized. Major anti-inflammatory
cytokines include interleukin (IL)-1 receptor antagonist, IL-4, IL-10, IL-11, and
IL-13 (Schafers, et al., 2003).
 Leukemia inhibitory factor, interferon-alpha, IL-6, and transforming growth
factor (TGF)-β are categorized as either anti-inflammatory or pro-inflammatory
cytokines, under various circumstances. Specific cytokine receptors for IL-1,
TNF-α, and IL-18 also function as inhibitors for pro-inflammatory cytokines
(Schafers, et al., 2003).
.

4.3 Cytokines
.
Source: https://neobiolab.com
Video showing a Macrophage Cytokine Release:
https://www.youtube.com/watch?v=KiLJl3Nwm
pU

.
5. Applications in Tissue engineering
1. Breast reconstruction
2. Cardiovascular system
1. Cardiac-tissue engineering
2. Blood vessels
3. Heart valves
3. Muscoskeletal system
1. Bone Regeneration
2. Bone and Cartilage Reconstruction
4. Nervous system
5. Skin
.

5.1 Breast Reconstruction
Introduction
 Reconstructive surgery after mastectomy or lumpectomy due to breast cancer
may benefit greatly from tissue engineering for the creation of new soft-tissue
replacements.
 Various cell types can be used for breast reconstruction, including
preadipocytes, fibroblasts, smooth muscle cells, muscle myocytes and
chondrocytes (Langer, et al., 2006).
 To introduce a cell-polymeric construct into the body, proper selection of the
polymeric materials should provide 3-D support for engineered new tissue
(Langer, et al., 2006).
 Two strategies for introducing cell-polymer constructs in the body exist:
 Surgical implanting
 Deliver of a specific hydrogel material via injection.
 $8.1 billion is spent each year in the United States for breast cancer treatment
(ACS,2006).
 According to ACS, each year, 182,000 new cases of breast cancer are detected
that can potentially require breast reconstruction (ACS,2006).

Introduction
 Tissue engineering is potentially a potent approach to treating the loss of tissues or
organs and it could find wide utility in breast-tissues reconstruction (Langer and
Vacanti, 1993; Mooney and Mikos,1999).
 Engineered breast reconstruction can be approached through one of two basic
pathways:
1. In-situ adipogenesis
2. De-novo adipogenesis
 The first technique employs the transplantation of a supportive matrix to encourage
the development of adipose tissue in-situ. The matrix is supplemented with specific
growth factors that attract native cells, such as fibroblasts and preadipocytes, to
migrate into the matrix (Patel and Patrick, 2004).
 In the second approach, tissue-specific cells are isolated from a small tissue biopsy
and expanded in-vitro. The cells are subsequently placed onto polymeric scaffolds
that act as synthetic ECM. These scaffolds deliver the cells to the desired site in the
body, define a space for tissue formation, and potentially control the structure and
the function of the engineered tissue (Kim and Mooney, 1998; Mooney, et al.,
1996).

Cell types for soft-tissue engineering
 A major cell type comprising normal breast tissue, and likely the engineered
replacement, is the adipocyte. Adipocytes are terminally differentiated and will
not divide further in in-vivo or under cell culture conditions. If these cells were
to be used, they would have to be harvested from fat in an equivalent volume
required for the construct (Hang –FU et al., 1995; Kononas, et al., 1993).
 Alternatively, preadipocytes could be used for engineering soft tissue
(Coleman, et al., 2000) because these cells potentially can be expanded in
culture. Preadipocytes are similar to fibroblasts in structure and possess the
ability to expand in culture. These cells can be successfully harvested and
isolated from tissues such as omentum and subcutaneous tissues (Fraser, et al.,
2006).
 Since breast tissue is more than fat alone in most cases, additional cell types
must be considered to contribute to the shape and the tactile, elastic and tensile
characteristics of a breast reconstructed via tissue-engineering methods.
Possible other cell types include fibroblasts, smooth muscle cells, skeletal
muscle and elastic cartilage.

Materials
 Several key characteristics make a biomaterial suitable for tissue engineering.
 First, favorable biomaterials must be biodegradable and resorb over time. The
shape and texture of the material must resemble that of natural tissue.
 Cellular adherence is another important aspect of any potential material. The
biomaterial must interact favorably with its cellular components without
negatively impacting them( the material can not be tumorigenic).
 A porous surface is another key feature that potentially allows for cellular
ingrowth into the material, be it native or implanted cells. In addition, a porous
surface allows for the diffusion of nutrients and the establishment of a vascular
network into the biomaterial construct (Beahm, et al., 2003).

Materials
 There are two general strategies for introducing the cell-polymer constructs
back into the body in order to engineer tissues (Langer., et al., 2006).
 The constructs can be implanted using an open surgical procedure (implantable
materials) or by utilizing syringes (injectable materials) (Langer., et al., 2006).
 The implantable forms of materials are typically foams, sponges, films and
other solid devices (Langer., et al., 2006).
 The typical injectable forms of materials include hydrogels and microbeads
(Langer., et al., 2006).
 Natural polymers such as alginate, chitosan, hyaluronic acid and collagen
are good examples of injectable materials (Langer., et al., 2006).

5.2.1 Cardiac-Tissue Engineering
Introduction
 Heart disease remains the leading cause of death in developed countries.
 Along with stroke, they are the principal components of cardiovascular disease
accounting for nearly 40% of all deaths (Gillum, 1994)
 Tissue engineering offers a potential to grow in-vitro functional equivalents of
native myocardium for use in tissue repair and to investigate new ways to treat
or prevent the disease.
Source: Tian et al., 2015

Problem Definition-The myocardium
 The myocardium is a highly differentiated tissue, 1.3-1.6 cm thick in humans,
composed of cardiac myocytes and fibroblasts with a dense supporting
vasculature and collagen-based extracellular matrix (ECM).
 Cardiac myocytes form a 3-D syncytium that enables propagation of electrical
signals across specialized intracellular junctions to produce coordinated
mechanical contractions that pump blood forward ( Severs, 2000).
 Only 20-40% of the cells in the heart are cardiac myocytes, but they occupy 80-
90% of the heart volume. The average cell density in the native rat myocardium
in on the order of 5*10^8 cells/cm^3 (Severs, 2010).
Myocardium - Definition, Function & Anatomy - Human
Anatomy: https://www.youtube.com/watch?v=0bQCPdj_a0o

Problem Definition-Requirements for a functional cardiac
patch
 In order to provide a functional cardiac patch, tissue engineering approaches
must accurately mimic the structure of native myocardium over several
different length scales.
 At the centimeter scale, TE should yield a mechanically stable construct of
clinically relevant thickness, comparable to the thickness of the human
myocardium (~1.5cm) (Yamanda et al., 1985).

Problem Definition-Clinically Relevant Cell Sources
 The major limitation in the progress of cardiac-tissue engineering toward
clinical applications, via either the cardiac patch or drug testing, is the lack of
an appropriate human cell source (Soonpaa and Field, 1998).
 Adult cardiac myocytes are terminally differentiated and have no ability to
proliferate, thus, they cannot be utilized as a source of autologous cells for
tissue engineering( Soonpaa and Field, 1998).
 Cardiac myocytes can be obtained in potentially unlimited quantities and at
high purity from embryonic stem cells (Klug et al., 1996). However, nuclear
transfer is required to make them autologous, and the presence of
undifferentiated cells may lead to teratomas upon implantation (Laflamme and
Murry, 2005).

Cell-Sheet Tissue Engineering
 Shimizu et al. (2002) created sheets of neonatal rat cardiomyocytes by plating
isolated cells onto a temperature sensitive ply(N-isopropylacrylamide) surface.
 The change in temperature from 37ο C to 32ο C causes the cell monolayer to
detach . The initial surface area decreases during the detachment approximately
fivefold, and the thickness of the cell sheet increases from approximately 20μm
to approximately 45μm.
 When the cell sheets were layered over each other, the electrical
communication was established, as evidenced by electrical signals measured
by electrodes and spontaneous beating was observed macroscopically.
 When implanted subcutaneously in nude rats, cell sheets survived for up to 12
weeks and vascularized.

Cell-Sheet Tissue Engineering
Source: Shimuzi et al., 2008

Biomimetic approach to Cardiac-Tissue Engineering
 The biomimetic approach involves an integrated use of cells, biomaterial
scaffolds, and bioreactors to engineer compact, millimeters thick,
synchronously contracting cardiac-tissue constructs.
 The system design is based on providing:
1. Convective-diffusive oxygen transport (critical for cell survival and function)
2. Excitation-contraction coupling (critical for cell differentiation and assembly).
 To mimic the capillary network, culture medium is perfused through a
channeled scaffold seeded with cells at a physiologic density
 To mimic the oxygen supply from hemoglobin, the culture medium is
supplemented with an oxygen carrier.
 To promote cell differentiation and functional assembly, cultured constructs are
subjected to electrical signals designed to mimic those in native heart and to
induce synchronous construct contractions (Radisic, et al., 2004b).

5.2.2 Blood Vessels
Introduction
 Principles of tissue engineering are now being applied in the induction and
development of microvascular networks as well as capacitance conduits,
including the in-vitro and in-vivo biologic modification of synthetic vascular
grafts and the generation of tissue-engineered blood vessels in bioreactors and
in-vivo.
 Alexis Carrel, the father of vascular surgery, was the first to describe the utility
and shortfalls of autogenous and synthetic grafts. The main limitation discussed
was the lack of durability for small-diameter synthetic grafts.
 Unfortunately, cardiovascular has become more prevalent in the last 100 years,
now being the leading cause of death in the world.
 Although autogenous veins or arteries provide the best patency rates for
cardiovascular bypass, many patients do not have suitable autogenous vessels
available for use.

5.2.2 Blood Vessels
Physicochemical modification on current grafts to improve
durability
 The long-term patency of vascular grafts depends on the intrinsic properties of
the graft itself and the hemodynamic environment in which the graft is placed
as well as patient variables (e.g., diabetes and renal failure) and may or may not
be improved by prior or concomitant interventions such as proximal or distal
angioplasty.
 On the grounds that tissue incorporation is important for graft function, grafts
that have this ability are now desirable for medium and small caliber vessel
replacement.
 Polyethylene terephthalate (Dacron) and expanded polytetrafluoroethylene
(ePTFE) are the predominant materials currently used in prosthetic vascular
grafts, but both Dacron and ePTFE react with blood components and perigraft
tissues in concomitantly beneficial and detrimental fashions.

5.2.2 Blood Vessels
Physicochemical modification on current grafts to improve
durability
 All grafts, regardless of their composition and structure, evoke complex but
predictable host responses that begin immediately upon restoration of perfusion,
and this improved understanding of cellular and molecular components of
biomaterial/tissue interactions has led to more intelligent designs of grafts.
 These approaches include protein adsorptive grafts (growth factors,
anticoagulants, antibiotics, etc.) as well as improved graft skeletal construction
via synthetic polymers or biologically derived structural proteins that can be
bonded to various bioactive cytokines and growth factors to induce a favorable
host response (Langer et al., 2006).
Vascular graft for the regeneration of blood vessels:
https://www.youtube.com/watch?v=9bokuAtBJgg

5.2.2 Blood Vessels
Tissue-engineered vascular grafts
 The potential of benefits of tissue engineered vascular grafts (TEVGs) include
the creation of a responsive and self-renewing tissue graft with functional
intimal, medial, and adventitial layers (including both cellular and ECM
components) that can be remodeled by the body according to its needs.
Source: Seifu et al., 2016

5.2.2 Blood Vessels
In-vitro Tissue-Engineered Vascular Grafts
 Weinberg and Bell (1986) were the first to develop a TEVG in vitro.
 Using collagen and cultured bovine vascular cells, they demonstrated the
feasibility of creating a TEVG, but their graft had prohibitively low burst
pressures, requiring external Dacron for support.
 In the following decade L’Heureux et al., (1998) constructed a human blood
vessel with an acceptable burst strength and a thromboresistant endothelium in
vitro using cultured umbilical cord-derived human cells.
 However, due to the immunogenic effects of the heterogeneic ECs in vivo, their
graft, devoid of ECs had only 50% patency rate at 8 weeks in a canine model.
 Since neonatal cells have a greater rejuvenative capacity, the foregoing TEVG
was not considered applicable to the aged population that would benefit from a
TEVG.

5.2.2 Blood Vessels
In-vitro Tissue-Engineered Vascular Grafts
Source: Liu, et al., 2015

5.2.3 Heart Valves
Introduction
 Heart valve disease is a considerable medical problem around the world.
 The American Heart Association has estimated that 87,000 heart valve
replacements procedures were performed in the US in 2000, and nearly 275,000
procedures are performed annually.
 The treatment for end-stage heart valve disease is valve replacement; however,
the best current replacement heart valves suffer from significant shortcomings.
 Promising alternatives to current replacement heart valves are being developed
in the field of tissue engineering.
 This multidisciplinary effort comprises the areas of tissue biomechanics,
immunology, injury response, cellular and tissue development, chemical,
physical and pharmacological manipulation of both cells and biomaterials.

5.2.3 Heart Valves
Application of tissue engineering toward the construction of a
replacement heart valve
 The ideal heart valve replacement would be readily available and perfectly
biocompatible, have the potential for growth and be durable (Mayer, 2001).
 The manufacture of an autologous, tissue engineered heart valve could
potentially be a considerable improvement over the best current technology.
 It would be capable of utilizing the natural mechanisms for repair, remodeling
and regeneration and thereby by highly durable.
 In addition, it would possess the potential for growth. Since the cells could be
harvested from the patient in need of a valve, immune-mediated rejection would
be eliminated. In short, tissue engineered heart valve could be the ideal
replacement heart valve (Shalak and Fox, 1988).

5.2.3 Heart Valves
Tissue Engineering Theory Applied to Heart Valves
 The semilunar heart valve is not completely avascular and nutrients and oxygen
are supplied via two complementary pathways. The thickest section of the valve
is vascularized for transport of oxygen and nutrients (Weing et al.,2001).
 An advantage of tissue engineering a semilunar heart valve is its composition of
easily cultured cells. This is a critical characteristic because it allows for the in
vitro isolation and in vitro expansion of autologous cells.
 Another critical feature enabling the development of a tissue-engineered heart
valve is the fact that valve function can be readily studied using well-
established techniques, such as Doppler ultrasonography and arteriography
(Mayer, 2001)

5.2.3 Heart Valves
Biomaterials and Scaffolds
 Tissue engineering scaffolds must be biocompatible, biodegradable with safe
by-products and highly porous yet sufficiently mechanically stable to
appropriate function ( Rabkin-Aikawa, et al., 2005).
 The scaffold must possess properties that promote cell attachment and
recapitulate complex tissues.
 Scaffolds can be made from either synthetic or natural materials. Natural
biomaterials are usually composed of ECM components:
1. Collagen
2. Fibrin
3. Elastin
4. Glycosaminoglycans
5. Decellularized heart valve

5.2.3 Heart Valves
Biomaterials and Scaffolds
 The most common synthetic polymers in tissue engineering include the poly
α-hydroxyesters poly(glycolic acid) (PGA), poly(L-lactic acid) (PLLA) and
copolymers poly(Lactic-co-glycolic acid) ( PLGA), poly(anhydrides) and
poly(peptides).
 Another popular polymer is PHA, or polyhyroxyalkanoate (Rabkin-Aikawa
et al., 2005). PHA is a thermoplastic that is biocompatible, resorbable and
flexible and that causes minimal inflammatory response (Williams et al.,
1999).

5.2.3 Heart Valves
Source: Butcher et al., 2012Creating Valve Tissue Using 3-D Bioprinting

5.2.3 Heart Valves
Neotissue Development in the Tissue-engineered Heart Valve
 Upon the formation of the cell-scaffold construct, neotissue begins its
development. The process, however, is poorly understood and is controlled by
many factors (Shalak and Fox, 1988).
 The environment of the growing construct will influence the ECM and
histological structure formed.
 Scientists have approached this phenomenon from two perspectives.
 The first is a “blackbox” approach, where the scaffold is used as a cell delivery
device and implanted in vivo shortly after cell attachment has taken place
(Langer and Vacanti., 1993).
 In a second approach, an instrument called bioreactor is used.

5.2.3 Heart Valves
Neotissue Development in the Tissue-engineered Heart Valve
 One type of bioreactor used in tissue engineering a heart valve is the pulse
duplicator. This pulsatile bioreactor supplies physiological flow and pressure to
the developing tissue-engineered heart valve and promotes both the modulation
of cellular function and the development of mechanical strength (Nicklason., et
al., 1999).
 Neotissue made in this way possesses superior mechanical properties over
unstrained controls and results in heart valve cusps that are considerably less
stiff than static controls (Gloeckner et al., 1999).

5.2.3 Heart Valves
Conclusion
 Successful development of a tissue-engineered replacement heart valve may
hold the key to better treatment of end-stage valve disease.
 Although significant progress has been achieved since its inception in the early
90s, the field is young and many key issues need to be resolved.
 As for yet, we are still limited by our knowledge of cell biology and ECM
production and maintenance of a normal valve.
 The identification of an ideal cell source and optimal matrix persists as the point
of focus in tissue-engineering strategy.
 It is possible that a more complete understanding of embryonic and fetal heart
valve development may provide insight that eventually enables tissue engineers
to build consistently clinically acceptable replacement heart valves ex vivo
(Flanagan and Pandit, 2003).

5.3.1 Bone Regeneration
Introduction
 Research in bone regeneration truly took off in the 1960s when Burnwell at al.,
confirmed bone marrow’s osteogenicity and Urist discovered bone morphogens.
 Scientific advances in bone-tissue engineering was thus achieved through both
in-depth understanding of bone cell biology and commercial-scale generation of
bone specific growth factors.
Source: Jiao Li, et al., 2014

Cell-Based Therapy
 The clinical use of cell-based therapies to aid in bone regeneration utilized the
use of bone marrow injections as a source of stem cells into nonunions
(Phemister, 1947).
 In the 1960s, Burwell (1964) further defined the bone regeneration potential of
the iliac crest autograft as a function of the crest’s marrow content. Since that
time, while plain bone marrow injections are still in some cases the therapeutic
option du jour, scientific developments provided health care professionals
with(Langer et al., 2006):
1. Optimized matrices to attach and maintain bone marrow cells
2. Point-of-care bone marrow cell concentration methods
3. Allogeneic, culture-expanded stem cell concentrates

Cell-Based Therapy-Use of Bone Marrow as a Source of Stem
Cells
 Of all human tissues, bone marrow was found to be particularly advantageous
from a cell-sourcing perspective, for it can be obtained from the iliac crest using
a noninvasive procedure with a simple needle aspiration (Langer, et al., 2006).
 More importantly, it is self-renewing and was found to regenerate its own
nucleated cellular content within 90 days (Stroncek, et al., 1991).

5.3.1 Bone and Cartilage Reconstruction
Introduction
 Tissue engineering offers a better approach than conventional surgery for bone
and cartilage repair by reducing donor site morbidity (Langer et al., 2006).
 To achieve this goal, animal study of repairing clinically relevant tissue defects,
especially in large animals, has become a crucial step.
 One of the disadvantages of traditional surgical repair procedure is the need to
harvest autologous tissues from a donor site of the human body for the repair of
a defect on another site, thus leaving a secondary tissue defect (Langer et al.,
2006).
 Tissue engineering offers an approach for tissue repair and regeneration without
the necessity of donor site morbidity (Langer et al., 2006).

Bone Reconstruction
 As early as 1993 Vacanti et al. applied tissue engineering techniques to the
construction of bone grafts in the subcutaneous tissue of nude mice using
periosteum derived osteoblasts and degradable polymer scaffold, which clearly
proved the concept that the tissue engineering approach can regenerate bone
tissue in-vivo.
 Kaplan’s group used silk as a scaffold material for bone engineering (Meinel et
al., 2005).
 In their study, hMSC were isolated and seeded on a porous silk fibroin scaffold,
in-vitro engineered for 5 weeks in a bioreactor and then transplanted to repair
the calvarial bone defects created in nude mice with a diameter of 4 mm.
 Their results showed that hMSC could undergo osteogenic differentiation on
this novel scaffold and that in-vitro engineered bone could achieve better
reparative results than the cell-scaffold complex without in-vitro engineering.

Cartilage Reconstruction
 In 1997, Cao et al. reported that cartilage with a complicated 3D structure, such
as the human ear shape, could be engineered using nude mice as an animal
model, which reveals the great potential for the clinical application of
engineered cartilage (Cao et al., 1997).
Video showing the mice with
the “extra ear” :
https://www.youtube.com/w
atch?v=PEc7QXAjsL4
Source: Cao et al., 1997

Cartilage Reconstruction
 With regard to clinically relevant models, for cartilage engineering and repair,
articular cartilage repair is the most commonly involved subject.
 Liu et al. had as a center the repair of the osteochondral defect in large mammals
using autologous chondrocyte-engineered cartilage (Liu et al., 2002).
 In a porcine mode, autologous articular cartilage was harvested from the knee joint
on one side. On the other side, an 8-mm full-thickness articular cartilage defect deep
to the underlying cancellous bone was created.
 The cell-scaffold construct containing PGA, polyethylene-polypropylene hydrogel,
and chondrocytes was then transplanted to repair the defects in the experimental
group.
 Grossly, cartilage tissues were formed in the defects of the experimental group as
early as 4 weeks after transplantation.
 At 24 weeks postrepair, gross examination revealed a complete repair of the defects
by engineering cartilage, shown by a smooth articular surface indistinguishable
from nearby normal cartilage (Liu et al., 2002).

5.4 Brain Implants
Introduction
 Tissue engineered brain implants have the potential to enable future treatments
of many neurological disorders for which no disease-modifying treatments are
available (Langer, et al., 2006).
 A major obstacle to developing cellular implants for a large number of patients
has been the inability to grow cells with the appropriate therapeutic potential in
large numbers (Langer, et al., 2006).
 The discovery of expandable stem cells from both embryonic and adult sources
has therefore created exciting sources of cell lines potentially applicable to a
large number of patients (Langer, et al., 2006).

5.4 Brain Implants
Introduction
 Experimental data strongly support the use of brain implants and tissue-
engineering concepts in the treatment of brain disorders and promise new
disease-modifying medical products for patients (Langer, et al., 2006).
 Various cellular implants have already been applied in the clinic in proof-of-
concept studies in Parkinson’s disease (PD) (Lindvall and Bjorklund, 2004)
Huntington’s disease (HD) (Blensch and Tuszynski, 2004), epilepsy (Lindvall
and Bjorklund, 2000) and stroke (Savitz, et al., 2004).
 However, a cellular implant has yet to reach the market as a therapeutic product
(Langer et al., 2006).

5.4 Brain Implants
Introduction
Source: St. Jude Medical
Video showing how a pulse generator functions:
https://www.youtube.com/watch?v=wOauyLO_Qr4

5.4 Brain Implants
Combined Replacement and Regeneration Implants
 From a tissue engineering point of view, the future goal is to make replacement
organs for the body that can take over function of a failed organ or structure in
an anatomically and physiologically correct manner (Langer et al., 2006).
 Even though it would be difficult if not impossible to make entirely new brains,
it would become possible not only to replace cells but also to make new axonal
pathways and restore correct connections (Langer et al., 2006).
 A large challenge for TE approaches in the treatment of neurological disorders
is the regeneration of axonal pathways. Axons between the cell bodies and their
targets often extend for several centimeters in the brain and close to one meter
between the brain and the lumbar spinal cord neurons in an adult (Langer et al.,
2006).
 Fortunately, science has made progress in this area. Several molecules are now
known to promote and to guide axonal outgrowth (Langer et al., 2006).

5.4 Brain Implants
Combined Replacement and Regeneration Implants
 Such a molecule is the glial cell line-derived neurotrophic factor (GDNF) which
has been shown to be a strong promoter of axonal outgrowth of dopaminergic
neurons (Zhou and Azmitia, 1988).
 In addition, certain ECM proteins, such as laminin, can guide axonal outgrowth
(Zhou and Azmitia, 1988).
 From a tissue engineering point of view, the combination of replacement cells
with regeneration channels or scaffolding capable of releasing survival and
neurite promoting factors and coated with molecules that facilitate axonal
outgrowth may thus become a future reality (Langer et al., 2006).

5.5 Skin-Wound Repair
Introduction
 The skin is the largest organ in the body, and its primary function is to serve as
a protective barrier against the environment (Langer et al., 2006).
 Other important functions of the skin include fluid homeostasis,
thermoregulation, immune surveillance, sensory detection and self-healing.
Loss of integrity of large potions of the skin due to injury or illness may result
in significant disability or even death (Langer et al., 2006).
 It is estimated that in 1992, there were 35.2 million cases of significant skin loss
(Wound Care, 1993) that required major therapeutic intervention.
 Of these, 7 million wounds became chronic.

Introduction
 The most common single cause of significant skin loss is thermal injury, which
accounts for an estimated 1 million emergency room visits per year (American
Burn Association, 2005).
 Other causes of skin loss include trauma and chronic ulcerations secondary to
diabetes mellitus, pressure and venous stasis (Langer et al., 2006).
 In 2003, a survey estimated the U.S market for advanced wound care products,
including biological and synthetic dressings, to be greater than 1.7 billion
dollars.

Tissue Engineered Therapy: Established practice
 Initial attempts to speed up wound repair and improve the quality of healing in
chronic or burn wounds involved the use of synthetic, composite synthetic or
biological dressings (Broomberg et al., 1965; Purna and Babu, 2000).
 Although effective, these dressings did not offer any permanent treatment, since
eventually an autograft had to be implanted to achieve complete healing, which
is often undesirable due to donor site morbidity.
 The advent of TE constructs has, however, revolutionized the wound-healing
practice (Rosso et al., 2005; Simpson, 2006). These constructs could be
classified into two main categories: cellular and acellular (Langer et al., 2006).
 Regardless of whether they are cellular or acellular, the basic block of theses
constructs is composed of a biomimetic and a scaffolding material.

Tissue Engineered Therapy: Established practice
 While the biomimetic functions to stimulate cells to perform their physiological
functions, the scaffold typically provides a mechanical support for the cells to
spread on and to proliferate within, to produce new tissue (Langer et al., 2006).
 However, scaffolds prepared from naturally occurring biopolymers may provide
additional biological stimuli to support cell and tissue function (Lutolf and
Hubbell, 2005).
 After implantation, these constructs promote faster healing, resulting in the
development of a new tissue that bears a close structural and functional
resemblance to the uninjured, host tissue

Tissue Engineered Therapy: New Approaches
 A general perception of novel engineering approaches emerges from
suggestions such as development of easy-to-handle, user-friendly, cost
effective, acellular that are based on nonanimal products.
 Since tissue cells are the primary source of various ECM molecules that
facilitate and synchronize tissue repair, any acellular product must, therefore, be
conductive to recruiting the host tissue cells rapidly and inductive to stimulating
the invading cells to proliferate, synthesize new ECM, and, if required,
differentiate (Langer et al., 2006).
 Hyaluronan is a nonsulfated GAG present in most human tissues. During
wound repair, it serves multiple important functions, ranging from regulating
inflammation to promoting fibroblast migration and proliferation (Chen and
Abatangelo, 1999).

 Similar to synthetic polymers, hyaluronan can be chemically modified to obtain
a variety of stable derivatives (Prestwich, et al., 1998).
 Therefore, by offering the advantages of both natural and synthetic materials,
hyaluronan promises to be a suitable scaffolding material for acellular matrices.
 Indeed, chemically modified hyaluronan scaffolds have been successfully used
for various tissue-engineering applications, including wound healing
(Campoccia et al., 1998; Kirker et al., 2002).
Source: Kirker et al., 2002

Source: Yannas MIT
Engineering a second skin:
https://www.youtube.com/watch?v=AkpT5BihMio

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