ntroduction to polymeric nanoparticles, PLGA coreshell particles and micelles
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Introduction to polymeric nanoparticles, PLGA coreshell particles and micelles
Nanopolymers
Polymer nanocomposites (PNC) is a polymer or copolymer having dispersed in its
nanoparticles. These may be of different shape (e.g., platelets, fibers,
spheroids), but at least one dimension must be in the range of 1 to 50 nm.
These PNC's belong to the category of multi-phase systems (MPS, viz. blends,
composites, and foams) that consume nearly 95% of plastics production. These
systems require controlled mixing/compounding, stabilization of the achieved
dispersion, orientation of the dispersed phase,
and the compounding strategies for all MPS, including PNC, are similar. Because
of the higher surface area of the nano-particles, the interaction with the
other particles within the mixture is more and this increases the strength,
heat resistance, etc and many factors do change for the mixture.
An example of a
nanopolymer is silicon nanospheres which show quite different characteristics;
their size is 40 – 100 nm and they are much harder than silicon, their
hardness being between that of sapphire and diamond.
Bio-hybrid polymer
nanofibers
Many technical applications of biological objects like
proteins, viruses or bacteria such as chromatography, optical information
technology, sensorics, catalysis and drug delivery require their
immobilization. Carbon nanotubes, gold particles and synthetic polymers are
used for this purpose. This immobilization has been achieved predominantly by
adsorption or by chemical binding and to a lesser extent by incorporating these
objects as guests in host matrices.
Applications
The nanofibres, hollow nanofibres, core-shell nanofibres,
and nanorods or nanotubes produced have a great potential for a broad range of
applications including homogeneous and heterogeneous catalysis, sensorics,
filter applications, and optoelectronics.
Tissue engineering
This is mainly concerned with the replacement of tissues
which have been destroyed by sickness or accidents or other artificial means.
The examples are skin, bone, cartilage, blood vessels and may be even organs.
This technique involves providing a scaffold on which cells are added and the
scaffold should provide favorable conditions for the growth of the same.
Nanofibres have been found to provide very good conditions for the growth of
such cells, one of the reasons being that fibrillar structures can be found on
many tissues which allow the cells to attach strongly to the fibers and grow
along them as shown.
Delivery from
compartmented nanotubes
Nano tubes are also used for carrying drugs in general
therapy and in tumor therapy in particular. The role of them is to protect the
drugs from destruction in blood stream, to control the delivery with a
well-defined release kinetics, and in ideal cases, to provide vector-targeting
properties or release mechanism by external or internal stimuli.
Rod or tube-like, rather than nearly spherical,
nanocarriers may offer additional advantages in terms of drug delivery systems.
Such drug carrier particles possess additional choice of the axial ratio, the
curvature, and the “all-sweeping” hydrodynamic-related rotation, and
they can be modified chemically at the inner surface, the outer surface, and at
the end planes in a very selective way. Nanotubes prepared with a responsive
polymer attached to the tube opening allow the control of access to and release
from the tube. Furthermore, nanotubes can also be prepared showing a gradient
in its chemical composition along the length of the tube.
Compartmented drug release systems were prepared based on
nanotubes or nanofibres. Nanotubes and nanofibres, for instance, which
contained fluorescent albumin with dog-fluorescein isothiocyanate were prepared
as a model drug, as well as super paramagnetic nanoparticles composed of iron oxide
or nickel ferrite. The presence of the magnetic nanoparticles allowed, first of
all, the guiding of the nanotubes to specific locations in the body by external
magnetic fields. Super paramagnetic particles are known to display
strong interactions with external magnetic fields leading to large saturation
magnetizations. In addition, by using periodically varying magnetic fields, the
nanoparticles were heated up to provide, thus, a trigger for drug release. The
presence of the model drug was established by fluorescence spectroscopy and the
same holds for the analysis of the model drug released from the nanotubes.
Immobilization of
proteins
Core shell fibers of nano particles with fluid cores and
solid shells can be used to entrap biological objects such as proteins, viruses
or bacteria in conditions which do not affect their functions. This effect can
be used among others for biosensor applications. For example Green Fluorescent
Protein is immobilized in nanostructured fibres providing large surface areas
and short distances for the analyte to approach the sensor protein.
With respect to using such fibers for sensor
applications, the fluorescence of the core shell fibers was found to decay
rapidly as the fibers were immersed into a solution containing urea: urea
permeates through the wall into the core where it causes denaturation of the
GFP. This simple experiment reveals that core-shell fibers are promising
objects for preparing biosensors based on biological objects.
Polymer nanostructured fibers, core-shell fibers, hollow
fibers, and nanorods and nanotubes provide a platform for a broad range of
applications both in material science as well as in life science. Biological
objects of different complexity and synthetic objects carrying specific
functions can be incorporated into such nanostructured polymer systems while
keeping their specific functions vital. Biosensors, tissue engineering, drug
delivery, or enzymatic catalysis is just a few of the possible examples. The
incorporation of viruses and bacteria all the way up to microorganism should
not really pose a problem and the applications coming from such biohybrid
systems should be tremendous.
PLGA
coreshell particles
PLGA or poly(lactic-co-glycolic
acid) is a copolymer which is used in a host of Food
and Drug Administration
(FDA) approved therapeutic devices, owing to its biodegradability and biocompatibility. PLGA is synthesized by means
of random ring-opening co-polymerization of two different monomers, the cyclic dimers
(1,4-dioxane-2,5-diones) of glycolic acid and lactic acid. Common catalysts used in the
preparation of this polymer include tin(II)
2-ethylhexanoate,
tin(II) alkoxides, or aluminum
isopropoxide.
During polymerization, successive monomeric units (of glycolic or lactic acid)
are linked together in PLGA by ester
linkages, thus yielding a linear, aliphatic polyester as a product.
Depending on the ratio of
lactide to glycolide used for the polymerization, different forms of PLGA can
be obtained: these are usually identified in regard to the monomers' ratio used
(e.g. PLGA 75:25 identifies a copolymer whose composition is 75% lactic acid
and 25% glycolic acid). All PLGAs are amorphous rather than crystalline and show a glass
transition temperature
in the range of 40-60 °C. Unlike the homopolymers of lactic acid (polylactide)
and glycolic acid (polyglycolide) which show poor solubilities, PLGA can
be dissolved by a wide range of common solvents, including chlorinated solvents, tetrahydrofuran, acetone or ethyl acetate.
PLGA degrades by hydrolysis of its ester linkages in the
presence of water. It has been shown that the
time required for degradation of PLGA is related to the monomers' ratio used in
production: the higher the content of glycolide units, the lower the time
required for degradation. An exception to this rule is the copolymer with 50:50
monomers' ratio which exhibits the faster degradation (about two months). In
addition, polymers that are end-capped with esters (as opposed to the free
carboxylic acid) demonstrate longer degradation half-lives.
PLGA has been successful as a
biodegradable polymer because it undergoes hydrolysis in the body to produce
the original monomers, lactic acid and glycolic acid. These two monomers under
normal physiological conditions, are by-products of various metabolic pathways
in the body. Since the body effectively deals with the two monomers, there is
very minimal systemic toxicity associated with using PLGA for drug delivery or
biomaterial applications. Also, the possibility to tailor the polymer
degradation time by altering the ratio of the monomers used during synthesis
has made PLGA a common choice in the production of a variety of biomedical
devices such as: grafts, sutures, implants, prosthetic devices, micro and
nanoparticles. It has also been used successfully in delivery Amoxicillin in
treating listeriosis (treatment of Listeria monocytogenes infection) As an
example, a commercially available drug delivery device using PLGA is Lupron
DepotⓇ for the treatment of advanced
prostate cancer.
A micelle is an
aggregate of surfactant molecules dispersed in a
liquid colloid. A typical micelle in aqueous solution forms an aggregate with the hydrophilic "head" regions in
contact with surrounding solvent, sequestering the hydrophobic single tail regions in the
micelle centre. This phase is caused by the insufficient packing issues of
single tailed lipids in a bilayer. The difficulty filling all
the volume of the interior of a bilayer, while accommodating the area per head
group forced on the molecule by the hydration of the lipid head group leads to
the formation of the micelle. This type of micelle is known as a normal phase
micelle (oil-in-water micelle). Inverse micelles have the headgroups at the
centre with the tails extending out (water-in-oil micelle). Micelles are
approximately spherical in shape. Other phases, including shapes such as
ellipsoids, cylinders, and bilayers are also possible. The shape
and size of a micelle is a function of the molecular geometry of its surfactant
molecules and solution conditions such as surfactant concentration, temperature, pH, and ionic strength. The process of forming
micellae is known as micellization and forms part of the phase
behavior of
many lipids according to their polymorphism. This is usually takes place
in soaps when hydrophylic occupies the water and hydrophobic catch hold of the
dirt in clothes we wash
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