Review
Biological, Chemical, and Electronic
Applications of Nanofibers
Luong T. H. Nguyen,* Shilin Chen, Naveen K. Elumalai,
Molamma P. Prabhakaran, Yun Zong, Chellappan Vijila,
Suleyman I. Allakhverdiev, Seeram Ramakrishna
With their high-surface-to-volume ratio, nanofibers have been postulated to increase
interactions between nanofibrous materials and targeted substrates, which are helpful to
overcome many obstacles and enhance the efficiency in a diverse number of applications.
Over the past decade, many studies have been published on the fabrication of nanofibers and
their applications in various fields. In this review, novel biological, chemical, and electrical
characteristics of nanofibers as well as their recent status and achievements in medicine,
chemistry, and electronics are analyzed. It is found that nanofibers can induce fast regeneration of many tissues/organs in
medical applications and improve the
efficiency of many chemical and
electronics applications.
Luong T. H. Nguyen, Shilin Chen, and Naveen Kumar Elumalai
contributed equally to this work.
ß 2012 WILEY-VCH Verlag GmbH & Co. KGaA, Weinheim
1. Introduction
With the development of nanotechnology during the past
two decades, there have been a significantly increasing
number of studies on nanofibers and their applications. The
International Standards Organization (ISO) considers
nanomaterials to be materials that are typically but not
exclusively below 100 nm in at least one dimension.
However, in informal non-wovens, textile, and other
engineered fibers industries, it has been well accepted
that nanofibers are fibers with diameters smaller than
1000 nm.[1] In 1992, carbon nanofibers were discovered to
grow spontaneously by deposition from carbon vapor.[2]
After that, many other techniques have been developed
to fabricate nanofibers such as electrospinning,[3,4] selfassembly,[5,6] phase separation,[7,8] interfacial polymerization,[9,10] rapidly initiated polymerization,[11,12] templateor pattern-assisted growth,[13,14] vapor-liquid-solid
growth[15,16] and hydrothermal synthesis,[17,18] etc. Due
to the nanosize, nanofibers possess high-surface-to-volume
ratios which help to increase interactions between
the nanofibers and targeted substrates in different fields
compared to other micro- to macro-size materials. Thus,
using nanofibers could be a promising approach for the
advanced developments in science and technology. In this
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1
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L. T. H. Nguyen
NUS Graduate School for Integrative Sciences and Engineering
(NGS), National University of Singapore, 28 Medical Drive,
Singapore 117456, Singapore
E-mail: hienluong@nus.edu.sg
S. Chen, N. K. Elumalai, Prof. S. Ramakrishna
Department of Mechanical Engineering, National University of
Singapore, 9 Engineering Drive 1, Singapore 117576, Singapore
S. Chen, N. K. Elumalai, Dr. Y. Zong, Dr. C. Vijila
Institute of Materials Research and Engineering, ASTAR (Agency
for Science, Technology and Research), 3 Research Link, Singapore
117602, Singapore
Dr. M. P. Prabhakaran
Faculty of Engineering, Center for Nanofibers and
Nanotechnology, Nanoscience, and Nanotechnology Initiative,
National University of Singapore, 2 Engineering Drive 3, Singapore
117576, Singapore
Dr. S. I. Allakhverdiev
Institute of Plant Physiology, Russian Academy of Sciences,
Botanicheskaya Street 35, Moscow 127276, Russia, and Institute of
Basic Biological Problems, Russian Academy of Sciences,
Pushchino, Moscow Region 142290, Russia
Prof. S. Ramakrishna
King Saud University, Riyadh 11451, Kingdom of Saudi Arabia
E-mail: seeram@nus.edu.sg
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review, we aim to dissect novel characteristics of nanofibers
and recent achievements in medicine, chemistry, and
electronics. This will allow researchers on various fields to
have an overview of the advantages of nanofibers and
provide guidance for further developments of nanofibers.
2. Fabrication Methods of Nanofibers
There have been many techniques developed for the
fabrication of nanofibers. Representative scanning electron
microscope (SEM) images of the most popular methods are
shown in Figure 1.
2.1. Electrospinning
Electrospinning is a technique using electrostatic forces
to fabricate nanofibers. When a high voltage is applied to
the droplet of a solution, the molecules of the solution
becomes charged and an electrostatic repulsion occurs,
which counteracts the surface tension of the droplet.
When the high voltage increases to a critical point, a jet of
the solution is erupted from the surface. As the solvent
evaporates, further stretching of the charged jet under the
electrostatic forces will push it into a bending instability
stage. The elongation and thinning of the charged jet due
to this instability lead to the formation of continuous
fibers with diameters in nanoscale. Based on this principle,
different electrospinning setups as well as different
types of collectors have been designed to create various
nanofibrous architectures.[3,4]
Properties such as the surface tension, viscosity, and
density of net charges of the polymer jet highly influenced
the morphology of the fibers. Solution concentration is
considered as a major factor that affects the fiber size,
and fiber diameter increases with increasing solution
concentration.[26] The morphology of fibers has a strong
correlation to solution viscosity as well as the solution
concentration and temperature.[27] Lower diameter fibers
were prepared by electrospinning of poly(lactic acid)
(PLA) with tetraethylbenzylammonium chloride (TEBAC),
whereby TEBAC increased the surface tension and electrical
conductivity of the solution. Electrically induced double
layer in combination with the polyelectrolytic nature of
solution was also anticipated as a method for formation of
high-aspect-ratio polyamide-6 nanofibers with diameters
as small as 9–28 nm.[28] In many cases, randomly oriented
fibers are deposited on a flat collector plate forming a
non-woven mat of fibers. Another approach commonly
applied is using a spinneret containing two needles to
produce composite nanofibers.[29] Moreover, many
different types of molecules can be incorporated into the
fibers and a wide range of polymers are electrospun
in varying fiber diameters ranging from <100 nm to
Dr. Seeram Ramakrishna, FREng, FNAE, FAIMBE,
is a professor of materials engineering at the
National University of Singapore. He pioneered
translucent biomaterials and devices, which are
now marketed globally. He ranges among the
world’s topmost researchers in the field electrospinning. He authored 5 books and over 400
international journal papers, which attracted
approximately 14 000 citations with an H-index
of 55 and G-index of 82. He is placed 27th in the
world in biocompatable materials experts by
Elsevier Science. Thomson Reuters Web of
Knowledge Essential Science Indicators (ESI)
places him among the top 1% of materials scientists worldwide (ESI rank is 30).
Yun Zong received his B. Sc. and M. Sc. degrees in
Chemistry from Wuhan University in China, and
his D. Sc. from the University of Mainz in
Germany. He is currently a Scientist at the Institute of Materials Research and Engineering. His
current research focuses on the development of
new functional colloidal nanoparticles and
nanostructured hybrid materials for various
applications.
Chellappan Vijila received her Ph.D. degree in
physics from Anna University, Chennai, India, in
2001. From 2001 to 2002, she was with Åbo
Akademi University, Turku, Finland, as a postdoctoral research fellow working on excited
state dynamics of organic semiconductors using
transient absorption spectroscopy techniques. In
2003, she joined with the Institute of Materials
Research and Engineering, Agency for Science,
Technology, and Research, Singapore, where she
is currently a scientist carrying out research on
organic optoelectronic devices and optical/electrical properties of organic electronic materials
especially on charge transport properties using
transient photoconductivity techniques.
micrometer levels using electrospinning. Controlled fiber
deposition techniques are also applied for the fabrication
of aligned nanofibers, on a rotation drum or a rotating
rim. Using a collector designed of two conductive strips
separated by a void gap of desired width, uniaxially aligned
nanofibers were produced too. The alignment of the fibers
could induce cell elongation and reorganize the cytoskeletal
structures that regulate the cell adhesion and morphology.
However, electrospinning has limitations of low productivity, as solutions are usually fed at a low rate so as to
produce fibers of low diameter.
Various structural variations of the nanofibers include
careful design of core-shell nanofibers, porous surface
scaffolds or even multilayered fiber structures. Electrospun
nanofibers of these architectures can act as drug delivery
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Figure 1. Representative SEM images of nanofibers fabricated by different techniques: (A) PLLA nanofibers fabricated by electrospinning,
(B) TiO2 hollow fibers fabricated by electrospinning,[19] (C) PLLA nanofibers fabricated by self-assembly,[20] (D) PLLA nanofibers fabricated by
thermally induced liquid-liquid phase separation,[21] (E) Polyaniline nanofibers fabricated by interfacial polymerization,[9] (F) Polyaniline
nanofibers fabricated by rapidly initiated polymerization,[22] (G) ZnO nanofibers fabricated by template assisted growth,[23] (H) ZnO
nanofibers fabricated by vapor-liquid-solid liquid growth[24] and (I) TiO2 nanofibers fabricated by hydrothermal synthesis.[25]
reservoirs for controlled and timely release of drugs,
proteins, antioxidants, and other molecules to the site of
tissue repair. The use of molten polymers to produce
electrospun mats introduced as ‘‘melt electrospinning’’ is
an environmentally benign process since it implies a
solvent free approach.[30] Cellular infiltration within
the electrospun scaffold remains a great challenge and
methods such as cell electrospraying are also concurrently
performed during the fabrication of a vascular conduit.[31]
Benefits of electrospinning technique are plenty, but
challenges of obtaining a three-dimensional (3D) scaffold
by electrospinning still remains a field of exploration.
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Nanofibrous and microfibrous 3D scaffolds of desired
shape and size are more preferred as implantable materials
compared to the electrospun 2D scaffolds. Compared to
electrospinning, the major advantage of self-assembly is
that it can produce fine nanofibers smaller than 10 nm and
these nanofibers could be applied as injectable scaffolds for
tissue regeneration. Pore sizes of 5–200 nm are insufficient
for cell migration and proliferation.[32] In this respective,
both electrospinning and self-assembly have one common
drawback, of incapability to control the pore size and
pore structure of the scaffolds. The challenge to integrate
nanofibers into useful devices requires well-controlled
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orientation, size, and other target characteristics of the
nanofibers. Reproducibility in locating them in specific
positions and orientations still remain to be faced.
2.2. Self Assembly
Self assembly is a bottom-up process in which small
molecules spontaneously assemble into well-ordered
nanofibers. The formation of this structure is induced by
many interactions, including chiral dipole/dipole interactions, p–p stacking, hydrogen bonds, non-specific van der
Waals interactions, hydrophobic forces, electrostatic interactions, and repulsive steric forces.[5] Normally, the basic
molecules to fabricate nanofibers using this technique are
peptide amphiphiles (PA). They consist of a dialkyl chain
moiety (hydrophobic component/tail group) attached to an
N-a-amino group of a peptide chain (hydrophilic component/head group).[6] The peptides can be self-assembled
by many reagents such as acid, divalent ion, and covalent
capture, etc.[5]
Bioactive sequences were introduced within PA with
formation of the triple helix structure by Malkar et al.[33]
and it demonstrated much similarity to the native selfassembled triple helix of the extracellular matrix (ECM).
The self-assembly of PAs into nanofibers was developed
by engineering of the peptide head group of the PA by
controlling the pH of the solution.[34] In such a way,
nanofibers of 5–8 nm in diameter with several mm lengths
were developed by these researchers and it was investigated for mineralization potential, with application as
primary building block for bone regeneration. With
advances in this field, even the osteogenic differentiation
of mesenchymal stem cells (MSCs) was possible in selfassembled PA nanofibers containing RGD peptide
sequences.[35] Other methods for formation of selfassembled PAs include divalent ion induced self-assembly
and drying on surface induced self-assembly.[5] Moreover,
PAs can be self-assembled reversibly into nanofibers
and hence it could be applied for versatile material
fabrications. It produced nanofibers in high yield with
low polydispersity, enabling further exploration of this
method for developing ‘‘smart’’ biomaterial scaffolds for
effective tissue regeneration.
2.3. Phase Separation
Thermally induced phase separation was commonly
employed during the early days to produce porous
polymeric scaffolds. The method was explored further to
produce nanofibrous 3D structures from a variety of
biodegradable polymers by Ma and Zhang.[7] Scaffolds
with porous structure and interconnected spaces are
greatly suitable for implantation, mainly because the
continuous fibrous network provide interconnecting
mechanical support for cell attachment, proliferation,
and migration.[36] There are five basic steps in this
technique: (i) polymer dissolution, (ii) phase separation
and gelation, (iii) solvent extraction from the gel with
water, (iv) freezing, and (v) freeze-drying under vacuum.
The selection of proper solvent is considered as one of
the most critical step of nanofibrous structure formation
during this process. The formation of the nanofibrous
structure is postulated to be caused by spinodal liquidliquid phase separation of the polymer solutions and
consequential crystallization of the polymer rich phase.
The method does not require specialized instruments
and it also allows for batch to batch consistency, while the
architecture and scaffold properties can be controlled
easily by varying the polymer concentration, gelation
temperature/time, solvent, and freezing temperature.[7,8]
Macroporosity was another feature that could be
obtained within these scaffolds by incorporating porogens
such as salt or sugars into the polymer solution during
the phase separation process.[7] Such 3D macroporous
structures are advantageous to the cells to absorb
nutrients, receive signals, and to discard wastes. The
presence of both nano- and macro-structures at
the nanofiber level provide additional benefits to cell
distribution and response.[8]
2.4. Interfacial Polymerization
Interfacial polymerization was developed as a templatefree approach to synthesize large quantities of pure,
uniform polyaniline nanofibers. Typically, an immiscible
system consisting of an organic solution of aniline and an
aqueous solution of ammonium peroxysulfate and acid
are left to stand for some time. Nanofibers are obtained
exclusively because the green polyaniline nanofibers
formed in the early stages of aniline polymerization at
the organic/aqueous interface diffuse into the aqueous
phase, thus preventing secondary overgrowth of polyaniline on the nanofibers that produce agglomerates
normally observed in traditional chemical oxidative polymerization of aniline in homogeneous aqueous systems.
Pure polyaniline nanofibers are present in >95% by
volume fraction of the polymer obtained with yields
ranging from 6 to 10%. The nanofibers formed are typically
twisted and interconnected with diameters ranging from
30 to 50 nm and length 500 nm to several micrometers.
Doped and de-doped polyaniline nanofibers have similar
morphology. Nanofiber diameters are affected by the
choice of acid used, while quality and uniformity of
the nanofibers are controlled by acid concentration; the
higher the acid concentration, the higher the fraction
of nanofibers in the final product. The type of organic
solvent, monomer concentration (0.032–1.6 M) and reaction
temperatures (5–60 8C) used have no effect on the size and
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morphology of polyaniline nanofibers. Polyaniline nanofibers synthesized by interfacial polymerization have
a bimodal Mw distribution and a higher average Mw
compared to bulk polyaniline obtained via traditional
chemical oxidative polymerization.[9,10]
2.5. Rapidly Initiated Polymerization
Rapidly initiated polymerization is an alternative
technique to interfacial polymerization for large-scale,
template-free synthesis of pure, uniform polyaniline
nanofibers. Generally, an initiator solution containing
ammonium peroxydisulfate in HCl is poured into a
monomer solution containing aniline in HCl all at
once. The two solutions are then rapidly and vigorously
mixed together for 15 s and left to stand for 1 d.
Nanofibers are produced in this process because
secondary overgrowth of polyaniline on nanofibers is
prevented by rapid consumption of initiator molecules
during the nanofiber formation phase of aniline polymerization. Polyaniline nanofibers obtained via rapidly
initiated polymerization have comparable morphologies
to those obtained by interfacial polymerization. The type of
acid used influences the size of the polyaniline nanofibers
formed, while polarity of the reaction medium affects
the quality of nanofibers; the more polar the solvent, the
better the quality of nanofibers. Reaction temperature
and reactant concentration have no effect on nanofiber
morphology.[11,12]
2.6. Template- or Pattern-Assisted Growth
This method facilitates the production of controlled
arrangements of nanofibers. Porous template-based
growth of nanofiber arrays can be obtained using wellestablished techniques such as electrochemical deposition
and template filling. Various inorganic materials such as
metal oxides, metals, semiconductors, and organic materials have been synthesized as nanofiber arrays using
this technique.[37] The main drawback of this method can
be listed as degradation of the template under longer
polarizations and non-uniform pore filling for high-aspectratio nanostructures. Nanofibers from materials such as
for NiO,[13] Cu2O,[14] and ZnO[38] are developed using this
method.
This method is basically a solution or colloidal dispersion
process in which the geometric features such as diameter,
density, and length of the 1D nanostructure can be
controlled easily. Mesoporous metal oxides which are
widely used for sensing and energy applications can
be produced with well-defined and ordered porous
structure by means of using surfactant as templates
through sol-gel method. In specific cases, copolymer
micelles is also used as templates to produce such
2.7. Vapor-Liquid-Solid (VLS) Growth
This method is well known for synthesizing defect free
one-dimensional (1D) nanostructures for a wide range
of materials. The parameters of the nanofiber such as
diameter, length, and composition as well as growth
direction can be effectively controlled by understanding the
mechanism of the VLS technique. The formation of metal
nanodroplets from gaseous precursors plays a major role
in the growth of nanofibers using this method. At first
the dispersed metallic nanocrystals on a single crystalline
substrate is melted in a tube furnace. Various process gases
introduced during this process leads to the saturation of
the molten metal nanodroplets which acts as catalysts
resulting in the continuous precipitation of single crystalline nanofibers thereby promoting the unidirectional
growth. Both hybrid and doped nanofibers can be produced
using this method. Growth orientation in particular planes
can be effectively controlled by appropriate substrate
selection and optimizing the corresponding temperature
and pressure during growth.[15,16]
The diameter of the 1D nanostructure produced in this
method is controlled by altering the growth parameters
by tuning the properties of the liquid alloy droplet. The
preparation of the nano-sized droplets on the substrate
plays a major role in 1D nanostructure growth since it
determines the kinetics of supersaturation and nucleation
occurring at the liquid/solid interface resulting in the axial
crystal growth. Metal catalysts activate the sites where
the nanofibers are to be grown and hence it determines
the position of the 1D nanostructures.[41] Pressure of the
source species also forms an integral role in growth rate
which is directly proportional to the whisker diameter
and hence the 1D nanostructures grows faster axially in
whiskers of larger diameter.[41]
2.8. Hydrothermal Synthesis
This method involves the growth of the nanofibers in
a heated liquid solution under pressure of 1 atm in an
autoclave at a temperature of about 100–300 8C. The growth
phase is dominated by the chemical decomposition during
which the thermally degraded reactive ions from the
precursors in the solution contribute to the growth of the
nanofibers. The growth can be facilitated in a particular
orientation by using appropriate catalysts which serves to
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nanostructures.[39,40] In this method, desired pore size,
nanostructure morphology, size distribution, and density
of pores can be obtained by selecting the appropriate
template. The most commonly used template is alumina
membranes which has uniform and parallel pores produced
by anodic oxidation of aluminum sheets. Pore size can be
controlled by chemical dissolution of the anodic oxide.[39]
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lower the surface energy. This method was first employed
for growing single crystals of semiconductors which
was later improvised and modified for developing other
nanostructures.[42,43] Some of the metal oxide nanofibers
grown using this method are In2O3,[44] MnO2,[17] and
Ga2O3.[18] The growth of the nanofibers can be controlled by
manipulating the parameters such as temperature, precursor concentration, and pH, etc. The main disadvantage
of this method is the low levels of crystallinity of the
grown nanofibers.
In hydrothermal synthesis, the properties of the 1D
nanostructures are defined by the process kinetics which
in turn dependent on the parameters such as temperature
and pressure in the system, duration of the synthesis,
and the initial pH of the solution medium. Salts called
mineralizers also play a major role in providing supercritical conditions for hydrothermal synthesis since it
forms the hydrothermal solution which determines the
solubility of the metal oxides to be processed.[45] Porosity
of the synthesized 1D nanostructure can be controlled
by selecting suitable surfactants for the targeted nanomaterial. The morphology of the metal oxide nanostructures is dependent on the surface-active agents
(SAA) which has immense influence on the hydrothermal
growth of oxide compounds.[46]
The advantages and disadvantages of the above fabrication methods are shown in Table 1. Electrospinning, selfassembly, and phase separation are methods usually
employed for medical applications. Meanwhile, chemical
applications normally used electrospinning, interfacial
polymerization, and rapidly initiated polymerization as
methods for the fabrication of nanofibers. Lastly, electrospinning, template- or patterned assisted growth, vaporliquid-solid growth, and hydrothermal synthesis are
generally applied in the nanofibrous fabrication of electronics. As such, it can be seen that electrospinning is the
unique fabrication method which can apply to these three
main applications. It is due to the fact that this method is
flexible in material selection (both organic and inorganic
materials) and diverse in nanofibrous architectures and
nanofibrous diameters.
However, these methods can neither repair nor produce
a long-term recovery effect on major damage in a truly
satisfactory way.[47]
Over the past 30 years, tissue engineering has emerged
as an alternative or complementary approach to tissue
and organ reconstruction. As firstly stated by Langer and
Vacanti,[48] tissue engineering is ‘‘an interdisciplinary field
that applies the principles of engineering and life sciences
toward the development of biological substitutes that
restore, maintain, or improve tissue function or a whole
organ.’’ A distinctive feature of tissue engineering is to
regenerate damaged tissues or organs of the own patient
that remarkably enhance biocompatibility and biofunctionality as well as reduce immune rejection. Due to the
great advantages, tissue engineering is often conceived as
an ultimately ideal medical treatment.[49] The worldwide
market of tissue engineering and regenerative medicine
approached US$ 1.5 billion in 2008, and is projected to grow
at a 16.2% compound annual rate from 2008 through 2013,
approaching US$ 3.2 billion by 2013.[50]
Three basic tools utilized in tissue engineering today
are cells, scaffolds, and growth factors. Although tissueengineered products have been applied to patients, their
clinical applications are still very limited. There are many
challenges to overcome before the translation of scientific
discoveries into treatments for millions of patients: (i) risk
of rejection,[51,52] (ii) vascularization of tissue-engineered
constructs,[47,51,52] (iii) lack of proper mechanical properties,[49] (iv) scaffolds able to degrade in response to
remodeling progress,[51] (v) quality control of materials,[47]
(vi) fundamental understanding of tissue differentiation
mechanisms,[47] (vii) enhancement of production scale,[52]
(viii) storage and preservation of tissue constructs,[51,52] (ix)
translation of successful animal studies to humans.[51] and
(x) lack of verifiable clinical data.[52] Among them, the risk
of rejection of tissue-engineered constructs is a major
challenge today. The inflammatory response can lead into
fibrous capsule development which will inhibit tissue
remodeling by limiting nutrient transport and angiogenesis.[53] The importance of nanofibers to reducing the
inflammatory response and inducing fast regeneration
of native tissues will be demonstrated in the following
sections.
3. Medicine
3.1. Current Challenges in Medical Treatment
3.2. Novel Characteristics of Nanofibers in Medical
Applications
Tissue and organ failure is a major health problem, which
can be caused by injury or other types of damage. In the US,
the treatment of this failure accounts for approximately
one half of the total annual expenditure in health care.
Treatment options include transplantation (human or
xenotransplantation), surgical repair, artificial prostheses,
mechanical devices, and in a few cases, drug therapy.
Collagens are the most abundant protein in the ECM
of many tissues in the body such as the bone, skin, and
nerve, etc. They are present as nanofibrillar proteins with
diameters in the range of 50–500 nm. ECM has several
functions such as providing biomechanical strength to the
tissue, serving as a biological scaffold for cells to adhere/
migrate, serving as an anchor for several proteins, and
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Table 1. Advantages and disadvantages of fabrication methods of nanofibers.
Fabrication
method
Advantages
electrospinning
nanofibers are long and continuous
nanofibrous diameters are quite uniform, wide range
of diameters can be fabricated
Disadvantages
small pore size
difficult to produce uniform fibers
with diameters less than 50nm
flexibility in material selection
various architectures can be created
bulk structure can be formed
self assembly
nanofibers can easily be modified and functionalized
bulk structure difficult to obtain
low mechanical strength
limited material selection
only random and short nanofibers
can be fabricated
phase separation
simple
bulk structure can easily be formed
limited material selection
only random and short nanofibers
can be fabricated
large pore sizes with well-defined structures
interfacial
one-pot reaction with no template or template-removing
polymerization
organic solvents required
process required
ease of scale-up production with high yield of uniform
nanofibers
post-fabrication purification
required
dispersibility of nanofibers in water for environmentally
friendly processing and biological applications
large choice of solvents, acids, reaction temperatures, and
reactant concentrations with control of nanofiber
morphology via choice of acid and acid concentration
rapidly initiated
same as interfacial polymerization
polymerization
post-fabrication purification
required
large choice of acids, reaction temperatures, and reactant
concentrations with control of nanofiber morphology via
choice of acid, reaction temperature, reaction medium, and
rate of mechanical agitation
environmentally friendly synthesis process because no
organic solvents required, aniline monomers in spent
aqueous solutions can be decomposed or recovered/
reclaimed, synthesis of substituted polyaniline nanofibers
possible
template- or
good control of arrangement of nanofibers
pore filling is non-uniform for
pattern-assisted
nano-structures with high aspect
growth
ratio, contamination from the
template, template degradation
during longer polarizations and
poor crystallinity
guided growth of nanofibers
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Table 1. (Continued)
Fabrication
method
vapor-liquid-solid
Advantages
Disadvantages
defect-free 1D structures
growth material needs to form an
growth
eutectic liquid with the catalyst for
efficient growth
high temperatures required for
processing therefore fabrication on
plastic and glass substrates cannot
be performed
hydrothermal
high yield
contamination of the
synthesis
nanostructures
low cost
clustering and agglomeration of
the nanostructures within the
solution during growth
easy fabrication
regulating the phenotype of cells.[54] Among existing
biomaterial structures, nanofibrous scaffolds can create
cellular environments mimicking the nanoscale structure
with complexity of the ECM. As opposed to flat surfaces,
the attachment of various cell types such as the smooth
muscle cells, adipose stem cells, and fibroblasts was at a
rate of 50–150% higher on the nanofibers (in 15 min to 8 h
period).[55–57] It has been hypothesized that, the body can
recognize the biomimetic nanofibrous scaffolds as ‘‘self’’
and therefore, all of the intercellular and intracellular
responses can be mimicked which help to stimulate the
healing and the regeneration of tissues and organs.[58–60]
Smartly designed tissue engineered scaffolds are even
capable of promoting an organized deposition of ECM
products from the resident cells. In a study carried out
by Li et al., chondrocytes seeded on electrospun fibers
of 500–900 nm produced double the amount of glycosoaminoglycan in 28 d compared to the cells on microfiber
(15 mm) culture.[61]
In addition, the topography of nanofibers can lead
into changes in focal contacts through a phenomenon
called contact guidance.[62] At the cell/matrix interface,
the focal adhesions play an important role in linking
the ECM on the outside to the actin cytoskeleton on
the inside. The adhesion of cells to ECM causes clustering
of integrins into focal adhesion complexes, and consequently activates intracellular signaling cascades into
the nucleus and cytoskeleton.[63,64] Thus, the changes
in focal adhesions can cause changes in cytoskeletal
organization and integrin-containing adhesions.[65] These
components are known to drive filopodia (or microspikes)
in response to nanotopography for the specific activation
of cytoskeleton- and focal adhesion-related signaling
pathways.[66] Focal adhesion plaque of hMSCs on nanofibrous scaffolds had a more elongated shape than on
those on smooth surfaces after 4 d of culture.[67] This
elongation is associated with the cytoskeletal strengthening as well as the recruitment of focal adhesion-associated
signaling molecules.[68] The guidance of filopodia by
nanotopography may alter mechanical forces within the
cells which can affect the interphase nucleus organization
and genomic regulation.[69,70]
Moreover, due to their large surface-area-to-volume
ratio, nanofibers provide more binding sites to cell
membrane receptors, promote the adsorption of serum
proteins and change the profile of adsorbed proteins.[62,71]
The adsorption of serum fibronectin and vitronectin,
which are known to mediate cell/matrix interactions, are
improved significantly with nanofibrous structures.[72] As
such, changes in the amount or type of adsorbed serum
proteins may provide cells with a better niche to enhance
cellular functions. Besides, the conformation of cellular
proteins on the nanofibers may expose additional cryptic
binding sites and be more favorable for cell/matrix
interactions.[62,73]
The overall advantage of nanofibers over other micro- or
macro-sized fibers is demonstrated in Figure 2.
3.3. In vivo Response to Nanofibers
To achieve a desired tissue/organ reconstruction, biomaterials should possess following properties: good biocompatibility, proper biodegradation, high-cellular infiltration,
high vascularization, and ability to induce angiogenesis.
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hydrophilic/hydrophobic microdomains on the material
surfaces. The biocompatibility not only depends on the
type of the polymer and functional groups, but also on the
structure of the scaffold surface.
Compared to thin films, nanofibrous meshes minimized
host immune responses with the thickness of fibrous
capsule decreased approximately 6 times.[76] Similarly,
fibrous capsule was significantly reduced on nanofibrous
scaffolds compared to microfibrous ones.[77] Electrospun
polyhydroxyalkanoate (PHA) copolymers showed excellent biocompatibility during the course of the subcutaneous implantation, with no fibrous encapsulation,
mild inflammatory responses, and the presence of
thin connective tissue surrounding the scaffolds.[78]
When modified with heparin, silk fibroin nanofibrous
scaffolds did not induce any neutrophil and lymphocyte
which indicated the minor inflammation as well as
no significant rejection of this type of scaffolds.[79]
Excellent biocompatibility in vivo with minor inflammatory reactions and biodegradation after 3 months of
implantation was demonstrated by bi-layer PLLA/silk
fibroin–gelatin nanofibrous meshes.[80] Multi-layered
poly(e-caprolactone) (PCL)/collagen nanofibrous constructs also showed good integration with surrounding
tissues and neovascularization when implanted into
nude mice.[81]
3.4.1. Cell Migration and Infiltration
Figure 2. The advantage of nanofibers over micro- or macrofibers. Due to high-surface-to-volume ratio, nanofibers provide
more binding sites for cell membrane receptors resulting in
activating more related signaling pathways, and consequently
faster tissue regeneration.
In an in vivo condition, cells in distances of >200 mm from
a blood vessel will suffer from hypoxia and limitation
of other nutrients since this is the maximum diffusion
distance.[74] So, angiogenesis and rapid vascularization of
implants are essential for cell survival.[75]
3.4. Biocompatibility and Biodegradation
A biodegradable scaffold is a material capable of degraded
enzymatic hydrolysis, whereby non-toxic alcohols, acids,
or low-molecular-weight products are easily eliminated
of the body. Meanwhile, a biocompatible scaffold is a
material which elicits little or no immune response in
the body and well-integrated with the targeted tissue/
organ. To reduce the immune response, scaffolds should
have non-thrombogenic blood compatible surfaces, and
should be in harmony with the cells and environment.
The antithrombogenic properties can be induced by
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Infiltration of cells through the polymeric scaffold is
a crucial factor while utilizing nanofibrous scaffolds
for tissue regeneration and nanofibrous structure
could encourage migratory and remodeling behavior in
comparison to smooth surface. Optimally designed
pore size and high porosity of electrospun scaffolds
provide sufficient space for cell migration and it enables
the exchange of nutrients between the scaffold and the
environment.
Periosteal cells were infiltrated when PCL nanofibers
were implanted under rabbit periosteum with the
infiltration extent increased from day 1 to day 7.[82]
A hybrid scaffold of electrospun poly(ether urethane
urea) (PEUU) and an ECM-derived scaffold resulted
in a large cellular infiltrate compared to the PEUU
alone.[83] In rat dermal replacement model, electrospun
poly[(lactic acid)-co-(glycolic acid)] (PLGA) nanofibers
achieved good cellular penetration, with no adverse
inflammatory response and no capsule formation.[84]
However, in a cylindrical shape with a inside diameter
of 2 mm and a wall thickness of 200–250 mm for the
implantation into the interstitial space of the rat
vastus lateralis muscle, only electrospun scaffolds
made from collagen showed good infiltration by interstitial and endothelial cells and the formation of functional blood vessels within 7 d.[85] Meanwhile, implants
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made from gelatin, poly(glycolic acid) (PGA), PLA, and
PLGA were not infiltrated to any great extent and
induced fibrosis. The difference might be derived from
a unique topography formed by collagen nanofibers
which promoted cell migration and capillary formation.
Compared to random nanofibers, aligned nanofibers
were shown to increase cell infiltration, guide matrix
organization, and elicit a thinner fibrous capsule.[76,86,87]
Increasing scaffold porosity also promoted cellular
infiltration and angiogenesis.[88] In general, electrospun
nanofibers have limited cell infiltration because of
their small pore sizes. It could restrict the delivery
of nutrients to the cells and waste disposal, and
constrains vascularization. To overcome this problem,
the electrospinning technique was combined with
photopatterning to create multiscale porous scaffolds.[89]
Another solution was the use of ice crystals as templates
to fabricate cryogenic electrospun scaffolds with large
pore sizes.[90] This technique improved cell infiltration
and vascularization compared to conventional electrospun
scaffolds. In addition, layers of micro- and nanofibers
have been proposed,[91] while methods such as salt
leaching and introduction of sacrificial polymers such as
poly(ethylene oxide) (PEO) were moderately successful
in fabricating stable fibers with larger pore sizes
suitable for cell infiltration.[92] Recruitment of endothelial
progenitor cells, MSCs, and myocytes progentitor cells
was achieved in vivo in a peptide nanofiber-assembled
myocardium and the nanofibrous substrates enhanced
vascularization and tissue regeneration.[93] Electrospun
scaffolds fabricated as 3D structures similar to a
‘‘cotton ball’’ might overcome the current challenges and
have great potential in a range of tissue engineering
applications.
3.4.2. Vascularization and Angiogenesis
Vascularization is the development of proliferating
capillaries, while angiogenesis is the formation of new
vessels. Angiogenesis is one of the major processes
required for functional tissue formation. To induce
angiogenesis, nanofibers have been normally combined
with inducers. In mice, supramolecular nanofibers
formed by self-assembly of a heparin-binding peptide
amphiphile (HBPA) and heparin sulfate-like glycosaminoglycans revealed excellent biocompatibility and
developed a new vascularized tissue which demonstrated an angiogenesis-promoting potential of this
material.[75] When injected into rats, IKVAV (IsoleucineLysine-Valine-Alanine-Valine)-containing peptide nanofibers were able to induce angiogenesis as shown
by forming capillary vessels with complete walls.[94]
Chemokines induced by platelet-derived growth
factor (PDGF) released from nanofibers enhanced the
angiogenesis in vivo.[95]
Subcutaneous injection of hepatocyte growth factor
(HGF) incorporated with self-assembled PA nanofibers to
mouse sub-cutis was carried out by Hosseinkhani et al,
and 3 weeks post-evaluation maintained their biological
activities and showed enhanced vascularization.[96]
However, robust strategies for complete integration and
vascularization of the engineered tissue with the host
tissue are apparently lacking after implantation of the bioengineered grafts. Clinical studies to deliver vasculogenic
growth factors in myocardial and peripheral limb ischemia
are in its preliminary stages.[97]
Taken together, with chemical and physical modifications, nanofibers have shown their good in vivo characteristics in biocompatibility, biodegradation, cell infiltration,
vascularization and angiogenesis. These properties would
help to accelerate their success in targeted functional
applications in medical treatment. The studies of in vivo
response to nanofibers are significantly important and have
to be taken into a serious consideration before the studies of
functional applications (bone, cartilage, skin, nerve, heart,
etc.) are performed, especially when a new material is
introduced. The results of biocompatibility, biodegradation,
cell infiltration, vascularization, and angiogenesis studies
will provide a in-depth profile of responses of in vivo
environments (animals/humans) so that researchers can
modify their scaffolds accordingly. A few important
properties of nanofibers that need to be considered before
performing in vivo studies are biocompatibility, biodegradation, and pore sizes of the scaffolds. The biocompatibility
and biodegradation normally can be determined by
the chemical components of nanofibers. The nanofibers
should possess a suitable biodegradable property for tissue
regeneration, but it also has to maintain an appropriate
mechanical property to serve as a scaffold for cellular
growth and differentiation. The pore size is a key factor of
nanofibrous scaffolds which determines cell migration,
infiltration, and vascularization. To achieve a complete cell
migration, infiltration, and vascularization, the nanofibrous scaffolds should have a pore size of 100–200 mm.
3.5. Animal Studies
Due to the novel characteristics of nanofibers, they have
been studied for diverse applications in medicine. Nanofiber-based scaffolds have demonstrated their substantial
support in the repair of skeletal, integumentary, nervous,
and cardiovascular systems as well as the treatment of
many other diseases in a broad range of animal models
(from small to large animals; Table 2).
3.6. Skeletal System
Among applications of nanofiber-based scaffolds in medicine, their application in skeletal system (bone, cartilage,
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Table 2. Animal studies using nanofibers.
Application
Nanofiber-based scaffolda)
Animal model
bone
mouse
subcutaneous
PLLA/differentiated hAFSC[98] PLLA/n-HA;[99] PEOT/
PBT/calcium phosphate/MSC;[100] PCL/gelatin/n-HA/
differentiated DPSC;[101] and Self-assembling
PA/differentiated DPSC[102]
intraperitoneal
tibia
calvaria
rat
subcutaneous
P-15 peptide/ABM/MSC[103]
PLGA/HAp/BMP-2 plasmid[104,105]
fibrin/n-HA/rhBMP-2;[106] and fibrin/ALP[107]
PCL/HS/differentiated MSC[108] PLLA nanofibers
immobilized with rhBMP-7 containing PLGA
nanospheres;[21] and Self-assembling PA/bFGF
combined with collagen/PGA[109]
abdominal omentum
femur
PCL/differentiated MSC[110]
self-assembling PA with phosphoserine residues;[111]
self-assembling PA/Ti;[112] PCL/Irradiated
RGD-modified alginate/rhBMP-2[113,114]
calvaria
PLLA;[115] PCL nanofibrous mesh/PLGA
membrane;[116] PLLA/DBP;[117] PCL/BG;[118]
PCL/simvastatin;[119] Collagen/nBG/bFGF[120]
rabbit
tibia
calvaria
PLLA[121]
chitosan;[122] silk fibroin;[123] silica gel;[124]
SiO2/CaO gel;[125] and PLGA/TCP[126]
sterna
cartilage
mouse
subcutaneous
PLLA/differentiated MSC[127,128]
p(NiPAAm-co-AAc)/TGF-b3/hMSC;[129]
star-shaped PLLA/chondrocyte;[20] articular cartilage
ECM/differentiated MSC[130]
rabbit
subcutaneous
medial femoral condyle
PLLA/cationized gelatin/chondrocyte[131]
p(NiPAAm-co-AAc)/TGF-b3/differentiated hMSC;[129]
and star-shaped PLLA/chondrocyte[20]
pig
medial femoral condyle
PCL/hMSC[132]
medial femoral condyle
PCL/PCL-TCP/MSC resurfaced with PCL/collagen
and patellar groove
mesh[133]
tendon
mouse
intramuscular
PLLA/TSC[134]
skin
mouse
normal wound
chitosan/PVA;[135] PHBV/ORSC/DSC[136]
diabetic ulcers
sNAG;[137] PCL/curcumin;[138] PCL-PEG/LPEI/
DNA;[139] PCL-PEG/rhEGF
[140]
; and PCL-PEG/bFGF/
[141]
EGF
rat
normal wound
collagen;[142] collagen/chitosan/PEO;[143]
PLGA/collagen;[144] PCL, PVA, PVA/wool, PVA/Ag;[145]
genipin-crosslinked silk fibroin/HBC;[146]
RADA16-I self-assembling peptide;[147] and
PLGA/Collagen/CD29/MSC[148]
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normal wound
MDOC/gentamicin;[149,150] hyaluronic acid[151]
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pig
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Table 2. (Continued)
Application
nerve
Nanofiber-based scaffolda)
Animal model
rat
peripheral (sciatic)
chitosan;[152,153] PLGA;[154] PLGA/PCL;[155]
PAN-MA;[156] PLCL/PPG/sodium acetate;[157]
chitosan/CG6YIGSR peptide;[158]
PCLEEP/hGDNF;[159] PLLA-laminin/PLGA-NGF;[160]
BDTM PuraMatrixTM peptide/Schwann cell;[161]
PLCL/PPG/sodium acetate/differentiated
NCSC[162]
central (spinal cord)
polyamide/D50 peptide;[163] RADA16-4G-BMHP1
self-assembling peptide;[164] self-assembling
PA/NPC or self-assembling PA/Schwann cell;[165]
PCL-PLGA nanofiber/RADA16-I-BMHP1
self-assembling peptide[166]
cardiac
self-assembling PA[167]
hamster
central
mouse
myocardial infarction
HBPA/rhVEGF/rh-bFGF[168]
rat
myocardial infarction
self-assembling PA/S-SDF-1(S4V);[169]
self-assembling porcine myocardial ECM;[170]
RAD16-II self-assembling peptide/selected
MSC;[171] and RADA16 self-assembling
peptide/RGDSP/MCSC[172]
vascular
pig
myocardial infarction
mouse
subcutaneous
rat
abdominal aorta
self-assembling PA/bone marrow MNC[173]
PLLA;[174] self-assembling PA/MSC[175]
hyaluronan;[176] PCL/Paclitaxel;[177] and
PEUU/PMBU;[178] PLGA/Tacrolimus[179]
carotid artery
self-assembling PA/nitric oxide;[180]
PLLA/MSC[181]
ischaemic hind limb
rabbit
epigastric-free flap
PLCL/collagen[182]
aortoiliac bypass
PCL/collagen[183]
dog
carotid artery
stent
rabbit
aneurysms
liver
mouse
intramuscular
spleen
abdominal
HBPA/rhVEGF/rh-bFGF[168]
PLGA/MSC/EC[184]
PU[185]
self-assembling PA/growth factors[186]
self-assembling PA/hepatocyte[187]
PEUU;[188] PEUU/PLGA/tetracycline
rat
hydrochloride;[189] and PCL/Biteral[190]
wall
bladder
mouse
subcutaneous
PLLA/MSC[191]
eye
mouse
ocular Surface
polyamide/LSC/MSC[192]
diabetes
mouse
islet transplatation
self-assembling PA/fibronectin/human islet[193]
hemostasis
rabbit
liver wound healing
self-assembling d-EAK16[194]
tumor
mouse
mammary fat pad
RADA16 self-assembling peptide/breast
cancer cell[195]
glioblastoma xenograft
PLGA/Paclitaxel[196]
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Table 2. (Continued)
Application
Animal model
drug/cell
Nanofiber-based scaffolda)
mouse
endo-tracheal
self-assembling PA/ESC[197]
rat
intra-tracheal
calcium pyrophosphate/Dex-P[198]
delivery
suture
PLLA/chitosan;[199] PLLA/CFX-Na[200]
rat
a)
Cells: AFSC, amniotic fluid-derived stem cell; DPSC, dental pulp stem cell; DSC, dermal sheath cell; EC, endothelial cell; ESC, embryonic
stem cell; LSC, limbal stem cell; MCSC, marrow-derived cardiac stem cell; MNC, mononuclear cell; MSC, mesenchymal stem cells; NCSC,
neural crest stem cell; NPC, neural progenitor cell; ORSC, epithelial outer root sheath cell; TSC, tendon stem cell. Growth factors/chemical
agents: ALP, alkaline phosphatase; bFGF, basic fibroblast growth factor; BMP-2, bone morphogenetic protein-2; rhBMP-2, recombinant
human bone morphogenetic protein-2; rhBMP-7, recombinant human bone morphogenetic protein-7; CFX-Na, cefotaxime sodium; Dex-P,
dexamethasone phosphate; EGF, epidermal growth factor; GDNF, glial cell-derived neurotrophic factor; NGF, nerve growth factor; S-SDF1(S4V), protease-resistant stromal cell derived factor-1; TGF-b3, transforming growth factor-b 3; VEGF, vascular endothelial growth factor.
Materials: 4G, 4-glycine spacer; ABM, anorganic bone material; BMHP1, bone marrow homing motif; D5’ peptide, neurite outgrowthpromoting peptide derived from tenascin-C; DBP, demineralized bone powder; EEP, ethyl ethylene phosphate; HAp, hydroxyapatite; HBC,
hydroxybutyl chitosan; HBPA, heparin-binding peptide amphiphile; HS, glycosaminoglycan heparin sulfate; LPEI, linear poly(ethyleneimine); MDOC, microdispersed oxidized cellulose; nBG, nano-bioactive glass; n-HA, nano-hydroxyapatite; P-15 peptide, cell-binding
domain of type I collagen; PA, peptide-amphiphile; PAN-MA, poly(acrylonitrile-co-methacrylate); PBT, poly(butylene terephthalate); PCL,
poly(e-caprolactone); PEG, poly(ethylene glycol); PEO, poly(ethylene oxide); PEOT, poly(ethylene oxide terephthalate); PEUU, poly(ester
urethane) urea; PGA, poly(glycolic acid); PHBV, poly(3-hydroxybutyrate-co-3-hydroxyvalerate); PLCL, poly[(L-lactide)-co-caprolactone];
PLGA, poly[(lactic acid)-co-(glycolic acid)]; PLLA, poly(L-lactic acid); PMBU, poly[2-methacryloyloxyethylphosphorylcholine-co-(methacryloyloxyethyl butylurethane)]; p(NiPAAm-co-AAc), poly[(N-isopropylacrylamide)-co-(acrylic acid)]; PPG, poly(propylene glycol); PU, polyurethane; PVA, poly(vinyl alcohol); RGD, arginine-glycine-aspartic acid; sNAG, poly(N-acetylglucosamine); TCP, tricalcium phosphate; Ti,
titanium.
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indicated good osteoconductivity in the treatment of
calvarial defects.[118,124]
In addition to using the pure nanofibers, nanofibers
have been usually combined with growth factors or
other osteogenic inducers such as bone morphogenetic
proteins (BMPs),[21,106,113,114] basic fibroblast growth factor
(bFGF),[109,120] alkaline phosphatase (ALP),[107] demineralized bone powder (DBP),[117] hydroxyapatite (HA),[99,104,105]
and tricalcium phosphate (TCP),[126] etc. to further improve
bone regeneration. Nanofibers provided a sustained and
prolonged release of the growth factors for bone defects.
The presence of BMP-2 in nanofiber-based scaffolds
resulted in consistent bony bridging for the repair of
critically sized segmental bone defects.[113] Not only growth
factors, but nanofibers also significantly contributed to
bone formation. Although both scaffolds contain bFGF,
only the scaffold with the presence of nanofibers produced
a homogeneous bone formation.[109] In addition to
growth factors, inorganic substances such as HA and TCP
were demonstrated to be very efficient in promoting or
even inducing bone regeneration when combined with
nanofibers.[99,104,105,126]
When injury or other types of damage occur in the body,
stem cells are hypothesized to migrate to the injured sites
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and tendon) is the most popular. The treatment of bone
defects in mouse, rat, or rabbit models have been
successfully done using pure nanofibers made from
synthetic/natural polymers such as PLLA,[115,121] PCL,[116]
chitosan,[122] and silk fibroin;[123] or inorganic matrices
such as bioactive glass (BG)[118] and silica gel.[124]
Woo et al.[115] showed significant advantages of PLLA
nanofibrous scaffolds over PLLA solid-walled scaffolds
in critical-size calvarial defects. The nanofibrous implants
produced substantially more new bone minerals,
abundant collagen deposition, and strong expressions
of Runx2 and bone sialoprotein (BSP) compared to
the solid-walled implants. Especially, electrospun nanofibrous scaffolds have been beneficial to be employed
as guided bone regeneration (GBR) membranes.[116,121–123]
GBR is a standard procedure which uses membranes
to protect bone defects from the ingrowth of surrounding
tissues, and thus promote bone healing. The nano- to
micro-pore size of nanofibrous membranes was shown
to be efficient in preventing from fibrous connective
tissue invasion, but allowing growth factors, nutrients,
and oxygen to be penetrated into the defects, which
leaded to faster bone regeneration. Not only organic
matrices, nanofibers made from BG or silica gel also
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and combine with local cells in the repair response. Thus,
recently, stem cells have been usually incorporated into
scaffolds to speed up tissue regeneration. The incorporation
of MSCs,[100,103,108,110,127,128] amniotic fluid-derived stem
cells (AFSCs)[98] and dental pulp stem cell (DPSCs),[101,102]
etc. into nanofibous scaffolds helped to accelerate bone
regeneration. The cell/scaffold composite indicated obvious
in vivo hard tissue formation with a surrounded thin
fibrous tissue capsule, and without any sign of tissue
ingrowth.[101,102]
In cartilage tissue engineering, using nanofiber-based
scaffolds also brings significant advantages to the treatment
of cartilage defects. Since cartilage regeneration requires a
high-cell density, nanofibers have been usually combined
with cells (chondrocytes[20,131] or MSCs[129,130,132,133])
transforming growth factor-b3 (TGF-b3).[129] In the treatment of 7 mm full-thickness cartilage defects in a swine
model, the MSC-seeded PCL nanofibers demonstrated a
more complete repair in the defects compared to the
acellular PCL scaffolds.[132] Nanofibrous scaffolds have
been fabricated as electrospun meshes of PLLA[131]
and PCL,[132,133] sponges of cartilage ECM,[130] injectable
scaffolds
of
poly[(N-isopropylacrylamide)-co-(acrylic
acid)] [p(NiPAAm-co-AAc)],[129] and star-shaped PLLA.[20]
The nanofibrous hollow microsphere/chondrocyte construct achieved remarkably better repair of a criticalsize rabbit osteochondral defect model than the chondrocyte alone.[20] As such, using nanofibers as cell carriers
would be a promising approach for clinically cartilage
regeneration.
As such, nanofiber-based scaffolds showed their significant achievements in skeletal tissue engineering in
the presence/absence of cells/growth factors. However, it
is still challenging to develop 3D hierarchical nanofibrous
scaffolds with controlled porosity, pore size, fibrous
dimeter, and mechanical property to further facilitate
the hard tissue regeneration. Electrospun nanofibers are
normally limited in pore size; whereas nanofibers fabricated by self-assembly and phase separation methods
usually encounter low-mechanical property and uncontrollable fibrous diameter, respectively. Scaffolds with high
porosity are necessary for efficient mass transport of
nutrients, oxygen, growth factors, and waste products.
To allow cell ingrowth and facilitate vascularization to
avoid necrosis at the core, appropriate pore sizes (100–
200 mm) must also be required. In addition, in the treatment
of large bone or cartilage defects, it is important to develop
biomimetic scaffolds with the osteoinduction and chondroinduction abilities by themselves, without the need
for soluble inducers (or growth factors). Growth factors are
generally derived from animal sources, expensive and
difficult to control the optimal concentration for an efficient
differentiation without side effects, so the development
of osteoinductive and chonroinductive scaffolds could
be a key issue to facilitate the success of clinical trials in
the future.
3.7. Integumentary System
One of the most successful applications of nanofibers in
medical treatment is skin regeneration. Many types of
nanofibrous polymers (natural/synthetic) such as hyaluronic acid,[151] collagen,[142] collagen/PLGA,[144] chitosan/
poly(vinyl alcohol) (PVA),[135] collagen/chitosan/PEO,[143]
PCL,[145] genipin-crosslinked silk fibroin/hydroxybutyl
chitosan (HBC)[146] and RADA16-I self-assembling peptide,[147] etc. have been shown to facilitate wound
healing in animal models. Compared to an adhesive
bandage, a sterilized solid hyaluronic acid, gauze with
Vaseline, and an antibiotic dressing, nanofibrous hyaluronic acid was the best type of wound dressing in a large
animal–pig model.[151] The nanofibers could absorb the
exudates of wounds to a greater extent, allow greater air
to be permeated, and help with the migration and
proliferation of cells in wounds than solid hyaluronic acid,
which led to faster wound healing. The nanofibrous
composite of type I collagen, chitosan, and PEO was also
demonstrated to be better than gauze and commercial
collagen sponge wound dressing in wound healing
rate.[143] Similarly, at 2 and 3 weeks after implantation,
the healing in the PLGA/collagen nanofiber group was
visibly faster than those of the gauze group and the
commercial dressing group, with well integrated into
surrounding skin (Figure 3).[144]
For the healing of acute wound infections, nanofibers
have been usually loaded with antibiotics such as Ag[145]
and gentamicin,[149,150] etc. Micro-dispersed oxidized
cellulose (MDOC) nanofibers blended with gentamicin
indicated their effectiveness in the treatment of fullthickness pig skin infections.[149,150] In addition, seeding
dermal sheath cells (DSCs)/epithelial outer root sheath cells
(ORSCs),[136] and MSCs[148] on nanofibrous scaffolds prior
to implantation was shown to provide significantly better
wound healing than the matrices alone.
Nanofiber-based scaffolds have not been only able to
treat normal wounds, but also to treat diabetic ulcers
which are common in patients with diabetic mellitus.
They can lead to limb loss if proper treatment is delayed.
Some successful approaches in animal models include
poly(N-acetyl-glucosamine) (sNAG),[137] PCL/curcumin,[138]
PCL-poly(ethylene glycol) (PEG)/linear poly(ethyleneimine)
(LPEI)/DNA,[139] PCL-PEG/epidermal growth factor (EGF),[140]
and PCL-PEG/bFGF/EGF.[141] The EGF nanofibers showed
superior in vivo wound healing compared to the nanofibers
or EGF alone.[140]
Taken together, nanofibrous scaffolds showed obvious
evidences of facilitating skin regeneration in comparison
with non-nanofibrous scaffolds in the pre-clinical studies.
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Figure 3. Appearance of wound healing at 1, 2, and 3 weeks after grafting in rat’s back: (A) gauze group, (B) nanofiber group, and
(C) commercial dressing group. The PLGA/collagen nanofiber showed better skin healing than others at week 2 and week 3 (Reprinted from
ref.,[144] Copyright 2010, with permission from Elsevier).
3.8. Nervous System
Nanofiber-based scaffolds have been applied in the
treatment of peripheral (sciatic) and central nervous
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systems. In the peripheral nerve regeneration, most
of tissue-engineered scaffolds of the last few decades
make use of rigid channel guides which may lead to cell
loss during patient’s movement.[155] But with the
ability to fabricate flexible tubular scaffolds, electrospinning technique provides a promising approach for
treatment of nerve injuries. Using electrospun nanofibers
made from natural and/or synthetic polymers such as
chitosan,[152,153] (PAN-MA),[156] and poly[(L-lactide)-cocaprolactone] (PLCL)/poly(propylene glycol (PPG)/sodium
acetate,[157] etc., an effective bridging of critical-size
peripheral nerve gaps were made possible. Scaffolds
have been usually fabricated as aligned nanofibers
in order to guide and promote the regenerating
nerve.[153,156,157] To further facilitate the nerve regeneration, active domains and growth factors such as
CG6YIGSR peptide,[158] glial cell-derived neurotrophic
factor (GDNF),[159] and laminin/nerve growth factor
(NGF),[160] etc. have been loaded into the nanofibers. The
efficacy of aligned PCL-ethyl ethylene phosphate (EEP)/
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The incorporation of cells into nanofibers also provided a
significant improvement. In spite of those achievements,
there are three major challenges still remained in this field
including improving safety of the incorporated cells,
angiogenesis in replacement tissue, and ease of use for
cell delivery approaches. The maximum thickness of a skin
graft substitute which can easily become vascularized is
about 0.4 mm. Thus, with scaffolds thicker than 0.4 mm,
new blood vessels cannot penetrate quickly enough to feed
the epidermal layer once the scaffolds are grafted to the
wound bed. In addition, nanofibrous scaffolds are expected
for further development to mimic chemical components,
physical structures, and mechanical properties of natural
skin ECM, which are important to an efficient skin
regeneration.
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GDNF nanofibers was compared with aligned nanofibrous
PCL-EEP tubes without GDNF and solid-walled PCL-EEP
scaffolds (control) for the treatment of rat peripheral nerve
injury.[159] Three months after implantation, all the rats
that received nanofibrous conduits (with and without
GDNF) showed a complete bridging of a 15 mm critical
defect gap. Meanwhile, bridging was only 50% in the
control group. Electrophysiological recovery was seen in
33 and 44% of the rats with the nanofibers alone and the
nanofibers/GDNF respectively, while none was observed in
the control. As such, nanofibers itself can support peripheral
nerve regeneration; however, the synergistic effect of
embedded growth factors significantly facilitated the
recovery. In addition to growth factors, Schwann cells[161]
and neural crest stem cells (NCSCs)[162] have been seeded
onto the nanofibers prior to implantation to improve
axonal regeneration and myelination. Alternatively a
tubular scaffold to reconnect the transacted nerve stumps
stuffed with a variety of materials such as gels or fibers
within the lumen of the tube are also attempted to serve
as a better graft for in vivo implantation and regeneration
of nerve. We developed PLLA conduits in our lab with
aligned PLGA nanoyarn (intra luminal guidance channel)
in the lumen, and incorporated biomolecules such as
laminin and NGF to determine the efficacy of the nerve graft
for in vivo regeneration.[160] Implantations in rat sciatic
nerve defect model showed high-functional recovery using
such grafts, the conduit with aligned nanoyarn performed
better than the autograft in muscle reinnervation and
withdrawal reflex latency tests.
While most of nanofibers used for peripheral nervous
regeneration were fabricated by electrospinning technique,
the nanofibrous scaffolds employed for the treatment of
central nervous system were based on injectable selfassembling peptides.[164–167] Because of the complexity of
this injury, it would need injectable scaffolds to minimize
damages brought to lesion sites. In the treatment of
rat acute spinal cord injury, RADA16-4G-BMHP1 selfassembling peptide nanofibers were demonstrated to
induce matrix remodeling, and provided physical and
trophic supports to nervous tissue ingrowth.[164]
Empty bridging tubular grafts provide limited tissuelevel guidance (axon mis-direction) and nerve conduits
filled with intraluminal guidance channels are the
most attractive option among the various nerve grafts.
However factors such as the conduit collapse, maintenance
of lumen space (patency of conduit), packing density of
the guidance channels need careful consideration with
respect to the dimension of the nanofibers and its
composition. With advances in electrospinning technology,
the development of new nozzle and collector configurations
has led to the design of nanofibers with desired scaffold
geometry, drug release, or surface properties. However
challenges of mimicking every aspect of native nerve,
within a bioengineered nerve graft is still questionable and
the latest research direction is toward the incorporation
of fibers into a hydrogel and the loading of this ‘‘combined
construct’’ into a 3D conduit. Further resolving the
attributes of such scaffolds for clinical applications turns
even more challenging or sometimes compromising.
3.9. Cardiovascular System
Heart failure following myocardial infarction (MI) is the
leading cause of death in the U.S. Since myocardical tissue
lacks the ability to substantially regenerate itself following
MI, tissue-engineered scaffolds are a requisite for myocardial repair. In particular, injectable nanofibrous scaffolds
possess impressive advantages of mimicking the natural
myocardial ECM and minimally invasive delivery. A natural
myocardial ECM was de-cellularlized and self-assembled to
form a nanofibrous structure with the ability to gel in vivo
upon injection into rat myocardium.[170] Eleven days after
the injection, they observed the migration of endothelial
cells and smooth muscle cells toward the myocardial
matrix, with a significant increase in arteriole formation.
In addition to using a natural matrix, synthetic selfassembling peptides were mixed with autologous
stem cells to repair myocardium and improve cardiac
functions in both small (rat) and large (mature mini-pig)
models.[171–173] It has been postulated that the efficacy
of stem cell transplant is related to paracrine factors.
Thus, instead of using stem cells, growth factors such as
vascular endothelial growth factor (VEGF) and bFGF[168]
were incorporated with HBPA to augment cardiac functions
after MI or enhance vasculature following critical ischemia.
Besides, self-assembling peptide nanofibers were employed
to locally deliver stromal cell derived factor-1 (SDF-1),[169]
a well-characterized chemokine, to drive stem cell recruitment into infracted myocardium. This is a potentially
novel approach to cardiac tissue regeneration.
In addition to myocardial regeneration, cardiovascular
diseases require a large number of revascularization
procedures to complete the tissue regeneration process.
Together with using autologous veins or arteries, biostable
synthetic vascular grafts such as expanded polytetrafluoroethylene (e-PTFE) and polyethylene terephthalate
(Dacron) have been utilized to replace blood vessels.
However, they have encountered some specific problems
as small blood-vessel diameters (<6 mm), whereby these
grafts can lead to graft occlusion and thickening of
the arterial wall due to their inadequate mechanical
properties and biocompatibility.[201] Thus, developing
novel small-diameter vascular graft is an imperative need.
Nanofibrous scaffolds of PLLA,[174] hyaluronan,[176] PEUU/
poly(2-methacryloyloxyethyl
phosphorylcholine-comethacryloyloxyethyl butylurethane) (PMBU),[178] PLCL/
collagen[182] and PCL/collagen,[183] etc. showed promising
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3.10. Other Applications
In addition to numerous animal studies on the above
systems, nanofibers have been applied to a diverse range
of other medical treatments. Injectable self-assembling
peptide nanofibers were loaded with growth factors
derived from a conditionally immortalized human
hepatocyte cell line[186] or hepatocytes[187] for the treatment of liver failure. The self-assembling peptide/hepatocyte construct corrected acute liver failure in mice and
prolonged their survival.[187] In a rat model for abdominal
wall replacement, PEUU nanofibers fabricated by a wet
electrospinning technique provided a good healing with
a mimic mechanical behavior as well as a substantial
cellular infiltration.[188] In combination with tetracycline
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hydrochloride, an antibiotic, PEUU/PLGA nanofibers prevented abscess formation in a contaminated rat abdominal
wall model.[189] Together with proper mechanical properties, this scaffold could be valuable to improve abdominal
laparotomy management. Loading with Biteral, a model
antibiotic, into PCL nanofibers also significantly eliminated
post-surgery abdominal adhesions, and improved the
healing of abdominal wall.[190] Besides, the construct of
PLLA nanofibers and MSCs demonstrated its potential in
bladder regeneration for patients with bladder exstrophy or
cancer who need cystoplasty.[191] Moreover, the treatment
of ocular surface injuries was shown to be successful
by using polyamide nanofibers seeded with limbal stem
cells (LSCs) and MSCs.[192] The scaffold/cell construct
significantly inhibited local inflammatory reactions and
facilitated the healing process.
Human islets embedded in fibronectin/self-assembling
peptide nanofibers and transplanted into streptozotocin
(STZ)-induced diabetic severe combined immunodeficiency
(SCID) mice reestablished the cell/matrix interactions and
maintained the islet functions in vivo for the treatment
of type 1 diabetes mellitus.[193] Self-assembling d-EAK16
nanofibers also showed a rapid hemostasis of approximately
20 s in a rabbit liver wound healing model.[194] Furthermore,
self-assembling peptides effectively reduced the malignant
phenotype of the tumor cells in vivo in comparison with
collagen type I and Matrigel.[195] An optimal paclitaxel
pharmacokinetics was obtained when this drug was
incorporated into PLGA nanofibers to treat malignant
glioblastoma in mice.[196] Forty-one days after the treatment,
the drug-loaded scaffold demonstrated significant (approximately 30-folds) tumor inhibition and significantly lowtumor proliferation index. Calcium pyrophosphate nanofibers also exhibited a controlled release of dexamethasone
phosphate (Dex-P) in a pulmonary inflammation model.[198]
For 42 h following a single application, the nanofibers loaded
with Dex-P inhibited eosinophil and total inflammatory
cell increases in bronchoalveolar lavage fluid. In addition to
drug delivery, nanofibers were indicated to be an effective
carrier for cell delivery. Self-assembling peptide nanofibers
possessed sufficient rigidity to remain embryonic stem cells
(ESCs) localized and gradually release them rather than
immediately dissolving in the abdominal cavity.[197] Finally,
braided nanofibers can be also applied as tissue sutures
with/without antibiotics. PLLA/chitosan[199] and PLLA/
cefotaxime sodium (CFX-Na)[200] exhibited comparable
tensile and knot strengths to those of a commercial suture
and had more preferable histological compatibility performance than commercial silk sutures.
3.11. Clinical Trials
To our best knowledge, up to now, there have been few
published reports on clinical trials of nanofibers as listed
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materials for the reconstruction of small blood vessels
in rat and rabbit models. When implanted into rabbits
to replace the inferior superficial epigastric veins, PLCL/
collagen nanofibrous tubes kept the structure integrity,
and showed patency for 7 weeks.[182] The PEUU/PMBU
vascular grafts indicated a thin neo-intimal layer
covered with endothelial cells and good anastomotic
tissue integration.[178] To prevent neointimal hyperplasia,
paclitaxel,[177] tacrolimus,[179] and nitric oxide[180] were
blended with nanofibers. The PCL/Paclitaxel nanofibrous
graft[177] showed good patency, reendothelialization,
and remodeled with the autologous cells. Moreover,
it reduced neointima formation until the end point of
6-month study. MSCs were also seeded on nanofibers prior
to implantation to prevent thrombosis.[175,181,184] The
combination of PLLA nanofibers with MSCs[181] created
a vascular graft with excellent patency and unique
antithrombogenic property for the treatment of smalldiameter arteries.
On the other hand, using polyurethane (PU) nanofibers to
cover stents was shown to be efficient in treating cerebral
aneurysms.[185] One day after implantation in rabbits,
complete occlusion of the aneurysms occurred with
patency of the parent arteries. On day 10, the aneurysm
neck was completely covered with a neointimal layer.
Designing a bioengineered graft capable of working
in synchronization with the nonlinear elastic behavior of
heart upon integration is a great challenge. Inadequate
mechanical properties of the blood vessel implants can cause
problems such as graft occlusion or arterial wall thickening.
Therefore, the most important factor for designing a
biomaterial graft for cardiovascular engineering is the
mechanical property and structural integrity of the biomaterial. Moreover, disappointments of therapeutic angiogenesis in clinical trial necessitate the development of better
multimodal research strategies for controlled delivery of
angiogenic promoters, with ability to propagate electrical
impulses, creating a functional myocardium.
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Table 3. Clinical trials using nanofibers.
Nanofiber-based scaffold
Application
Status
Reference
nitric oxide releasing nanofibrous patch
cutaneous leishmaniasis
completed phase III
[202,203]
nitric oxide releasing nanofibrous patch
diabetic ulcers
on-going phase III
[204]
bioactive borate glass nanofibers
diabetic ulcers
completed phase II
[205]
nanofibrous mesh
anti-adhesion
completed phase II
[206]
in Table 3. It might be due to the fact that nanofibers have
been only studied for applications in tissue engineering/
medical treatment during the past decade. In addition,
many challenges as shown above are needed to be solved
before moving up with clinical trials. For example, immense
challenge remains in finding the accurate path that guide
the axons to their target and in establishing the microenvironment to facilitate neurite outgrowth while utilizing
nerve graft for clinical trials. Most of the trials have focused
on skin regeneration–the simplest application, including
the treatments of cutaneous leishmaniasis[202,203] and
diabetic ulcers.[204,205] Phase III clinical trial of nitric oxide
releasing nanofibrous patch (3.5 mmol NO cm2 d1 for
20 d) for cutaneous leishmaniasis treatment was completed.[203] Previous pre-clinical studies and clinical trials
of this material showed that the multilayer transdermal
nanofibrous patch fabricated by electrospinning provided
a continuous and stable nitric oxide release when
administered topically without adverse events.[202] In the
phase III, 3 months after the treatment starts, although
the cure rate of the nanofibrous patch was only 37.1%
compared to 94.8% of intramuscular meglumine antimoniate (Glucantime, 20 mg kg1 d1 for 20 d), the
patients treated with the nanofibers showed a significantly
lower frequency of adverse events as well as a decreased
variation in serum markers. Phase III clinical trial of this
material for diabetic ulcer treatment is going on.[204]
Bioactive borate glass nanofibers are also under clinical
trials to treat diabetic ulcers.[205] The result of phase II
with twelve patients demonstrated that the material
helped to heal venous stasis wounds in eight of the
patients who had suffered from diabetes and not
responded to other treatments. The nanofibers supported
the migration of epidermal cells and facilitated the
healing process. This study has been expanded and phase
III clinical trial will be performed soon. In addition,
nanofibers have been performed with clinical trials for
anti-adhesion application.[206] The biodegradable nanofibrous membrane helped body tissues be prevented from
sticking together as they heal. Further results will be
obtained from the phase III clinical trial. Although there
are not many clinical trials, with novel results of nanofibers
as shown in pre-clinical trials, we believe that a large
number of human trials on nanofibers with various
applications are coming.
4. Chemistry
Much has been reported in the literature relating to
chemistry done on or with nanofibers. Numerous reviews
have been written on the chemistry of nanofibers
synthesis,[207,208] bulk/surface modifications,[209,210] and
response to environmental stimuli[211] with applications
in various chemical reactions and processes.[212,213]
Chemical reactions on or with nanofibers do not alter
their nature. Indeed, a recent review on chemistry
involving electrospun polymeric nanofibers revealed no
new chemical reaction that generates any novel type
of chemistry that is different from conventional ones in
terms of reaction pathways, tacticities, or ligand spheres
of complexes.[214] Nonetheless, the use of nanofibers
in processes involving chemical reactions does confer
some advantages over conventional systems. This
section attempts to provide an overview on the practical
applications of nanofibers in chemical processing with
respect to the types of chemical processes/reactions
in which nanofibers have been employed and the
benefits and novel chemical functionalities that nanofibers offer over conventional processes. The applications
of nanofibers in chemical processing are shown in
Figure 4.
4.1. Current Challenges in Chemical Processing
While nanofibers are employed differently in various
applications to address unique challenges (details of which
are discussed in each respective section), the underlying
issue common to all is reaction efficiency in terms of
speed and yield. Heterogeneous reactions involving solids,
particularly heterogeneous catalysis, are widely utilized in
many industrial chemical processes. Finely divided solids
in the form of particles, especially nanoparticles, are usually
used in these processes because their small sizes mean highsurface areas, large number of reactive sites, and better
reaction efficiency. However, aggregation and uncontrolled
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crystal growth during particle synthesis reduce their active
surface areas resulting in loss of reaction efficiency.[214] In
addition, particulates pose difficulties in handling, product
purification and catalysis recovery, and are health hazards
due to their powdery nature.[215,216] Packing particulates or
mounting them onto porous substrates with high-surface
areas ease handling, product purification, and catalyst
recovery/reuse but these again lower reaction efficiency
due to loss of reactive surface areas and porosities, chemical
changes in the particles, and large pressure drops and
moving bed phenomena in continuous flow fixed-bed
processes.[215,216] Furthermore, commonly used catalyst
substrates such as activated charcoal have small and
narrow pores which limit reaction efficiency due to lowmass transfer.[217]
4.2. Novel Characteristics of Nanofibers in Chemical
Processing
Nanofibers can be used in chemical reactions to improve
reaction efficiency due to their unique morphology. The
high-aspect ratio and thin diameters of nanofibers mean
high-specific surface areas for chemical reactions compared
to bulk materials and also for catalyst immobilization. This
translates into greater number of reactive sites and hence
faster reactions and higher yield in chemical reactions.
Fang et al.[218] applied Au-nanoparticle-coated polyethyleneimine (PEI)/poly(vinyl alcohol) (PVA) nanofibers as
catalysts in the hydrogenation of 4-nitrophenol to 4-ami-
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4.3. Catalysis
Catalysis plays critical roles in the production of fuel,
energy, chemicals, food, and pharmaceuticals, and in
environmental remediation as well, contributing to
>35% of global GDP.[221] Owing to its economic and
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Figure 4. Nanofibrous applications in chemical processing following surface functionalization.
nophenol. 97% hydrogenation was achieved with nanofibers in 36 min compared to 72% with Au nanoparticlescoated PEI/PVA film due to higher specific surface area
and porosity of the nanofibers. The open porosity of
nanofiber mats also allows more efficient mass transport
at reactions sites on the fibers. Zhou et al. used Pdnanoparticles-coated carbon nanofibers in the catalytic
hydrogenation of 4-carboxybenzaldehyde (4-CBA) to
terephthalic acid (PTA), a raw material used in the
production of poly(ethylene terephthalate) (PET) and an
important industrial polymer.[217] 98.3% conversion was
achieved using the fabricated catalyst compared to
90% with commercial Pd-on-activated-carbon catalyst
despite a lower specific surface area in the fabricated
catalyst (200 m2 g1) compared to the commercial one
(1000 m2 g1). Analysis of surface porosity on both
catalysts revealed that the commercial catalyst had
mostly micropores of less than 2 nm while the fabricated
catalyst had larger open pores 10 nm in size. Hence, the
authors concluded that better catalytic performance of
the Pd-nanoparticle-coated carbon nanofibers was due to
their higher porosity which promoted greater mass transfer
between reactants, products, and catalytic sites on the
nanofibers.
The ability to macroscopically shape nanofibers and
grow/deposit them onto various substrates facilitates their
handling and customization for different applications.
In catalytic processes, nanofibers can be employed to ease
the separation of catalysts from reactants and products for
product purification and catalyst recycling. For instance,
Chen et al.[219] employed carbon nanofibers containing Pd
nanoparticles as catalyst in the liquid-phase Sonogashria
coupling reaction of iodobenzene and phenylacetylene for
10 runs. After each run, the nanofiber catalyst was retrieved
by filtration, washed, and vacuum-dried before being used
again for the next reaction. It was found that the catalyst
showed near 100% retrieval with no change in catalytic
activity after 10 runs. When mounted on an appropriate
support, nanofibers can be used as reaction membranes in
continuous flow processes, which is useful in large-scale
industrial operations. Ag-doped zeolite Y particles coated
onto the surface of Al2O3 nanofibers had been used as an
integrated membrane in the photo-degradation of Methylene Blue in wastewater treatment with 85% permeating
selectively under visible light irradiation and a flux of
200 L m2 h1 without flux deterioration commonly
encountered with non-catalytic membranes.[220]
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industrial importance, there is always on-going research to
develop better catalysts to improve reaction efficiency.
There has been growing interest in using nanofibers as
catalysts or catalyst supports due to their unique morphology, which promises greater reaction efficiency. Table 4
provides a summary of nanofibers that have been applied
in industrially relevant catalytic reactions.
4.4. Heterogeneous Catalysis
The various challenges associated with the use of catalyst
particles in heterogeneous catalysis have been described.
Nanofibers can offer viable solutions to these challenges
because their thin fibers and open, porous morphology
provide large specific surface areas on which to mount
catalyst nanoparticles with minimum compromise their
large reactive surface areas and mass transport, resulting in
improved reaction efficiency, as discussed above. Aggregation and chemical changes to catalyst particles are avoided,
uniform growth of catalyst nanoparticles on the nanofibers
can be achieved and handling and separation of products
and catalysts for product purification and catalyst recovery/reuse become more convenient, as pointed out earlier.
Besides catalyst supports, nanofibers can be made catalytic
as well by fabricating them directly from catalytic
materials, thus eliminating the need for catalyst immobilization and disadvantages associated with nanoparticle
use. For instance, hollow TiO2 nanofibers were shown to
have greater activity in the photo-catalytic degradation
of formaldehyde, decomposing 80% of formaldehyde
compared to 42% for TiO2 nanoparticles and 50% for
mesoporous TiO2 powder.[250]
Nanofiber catalyst supports can be designed to play an
active role in assisting catalytic reactions. Ledoux and coworkers[222–224] fabricated Ir nanoparticles supported on
carbon nanofibers and compared their catalytic performance in the decomposition of hydrazine with commercially available Ir/Al2O3 catalyst for satellite propulsion.
Faster hydrazine decomposition was achieved with the
synthesized nanofibers compared to the commercial
catalyst in terms of similar or greater thrust generated
with less Ir. Good performance of the synthesized
nanofibers was attributed by the authors in part to better
thermal conductivity of the carbon nanofibers which
reduced formation of hot spots in the catalyst compared
to the commercial catalyst, in addition their higher open
porosity and specific surface area. The same research group
also synthesized Ni nanoparticles supported on carbon
nanofibers for the catalytic oxidation of H2S to sulfur, a
process used to remove H2S from waste gases generated by
various industries.[231] Increased resistance toward catalyst
deactivation was observed compared to Ni/SiC catalyst due
to rapid removal of sulfur formed on the catalytic sites
by the condensed water film formed on the hydrophilic
surface of carbon nanofibers, in addition to increased
desulfurization activity.
4.5. Homogeneous Catalysis
Homogeneous catalysis usually involves reactants and
catalyst molecules in liquid medium. Stability and reactivity of catalyst molecules in the reacting medium are of
relevance in homogeneous catalysis; a loss of either one
would result in decreased reaction efficiency. Instability
and inactivity of catalyst molecules could arise due to a
variety of reasons such as temperature variation, pH
variation, solvent effects, or aggregation.[214,266]
Using nanofibers to immobilize molecular catalysts in
homogeneous catalysis offers several advantages over
the use of free molecules. Like heterogeneous catalysis,
nanofibers offer large specific surface areas for catalyst
immobilization, efficient mass transport due to their
open porous morphology, ease of product purification
and catalyst recovery/reuse, and the possibility of continuous flow operations. Xie and Hsieh[259] investigated
the catalytic activity of lipase-carrying polymer nanofibers
in the hydrolysis of olive oil. While catalytic activity
of lipase immobilized on nanofibers decreased 100-fold
compared to free lipase, it was 6 times more than those
immobilized on cast films due to higher specific surface area
and porous morphology of the nanofibers. Immobilization
of catalyst molecules on nanofiber surfaces also enables
a certain degree of restrain on their spatial and conformational arrangements, protecting them to some extent from
inactivation due to aggregation, solvent effects, and
temperature or pH changes with minimum detrimental
effects to their catalytic activity.[214,266] Jia et al.[263]
fabricated a-chymotrypsin-coated PS nanofibers and
found hydrolytic activity of the immobilized enzymes to
be 65% that of free enzymes. However, this was higher
compared to other forms of enzyme immobilization.
Furthermore, enzyme activity of the synthesized nanofibers in non-aqueous medium was three orders of
magnitude higher compared to free enzymes due to
improved enzyme stability against structural denaturation; half-life of enzymes immobilized on PS nanofibers
was 18-fold longer compared to free enzymes.
Many nanofiber-based catalysts have been developed
and investigated for different industrial catalytic reactions.
It can be generally concluded that they exhibit greater
reaction efficiency due to their larger specific surface areas
and open, porous morphologies, without the disadvantages
commonly associated with traditional particulate catalysts. A variety of nanofiber-based catalysts have also been
synthesized for similar chemical reactions or reaction
types; however, comparison as to which is better is difficult
due to dissimilar methods and characterization techniques
employed in different studies. Many studies conducted
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Table 4. Nanofibers for catalysis.
Type of reaction
Nanofiber useda)
Nanofiber fabrication
technique
heterogeneous
catalysis
decomposition
CCVD
Ir NPs on CNFs on graphite felt[222–224]
hydrodechlorination
CCVD
Ni NPs on CNFs on SiO2[225]
hydrogenation
CCVD, electrospinning,
HDP
Au NPs-coated PEI/PVA NFs;[218] PAN-AA NFs containing
Pd NPs;[226] Pd NPs-coated CNFs;[217,227] Pd NPs-coated
CNFs containing Ni-Fe NPs;[228] Ru NPs-coated CNFs[229]
oxidation
CCVD, electropolymerization
Ag-hollandite NFs;[230] NiS2 NPs on CNFs;[231] PANI NFs on
electrospinning,
Pt/C-coated electrodes;[232] Pt NPs or nanofibers-coated TiO2
flame burning,
NFs;[233] Pt NPs-coated CNFs;[234–236] Pt NPs-coated hollow
hydrothermal synthesis,
polyol reduction,
template synthesis
CNFs;[237] Pt NPs-coated SDS-functionalized CNFs;[238]
Pt NPs-coated CNFs containing MWCNTs;[239,240]
CNFs containing PtRu NPs;[239] PtRu NPs-coated CNFs;[241,242]
silicotungstic acid stabilized PtRu NPs-coated CNFs;[243]
PtRu NPs-coated PAMAM-functionalized CNFs;[244]
LaMnO3 NFs[245]
oxidative
CCVD
CNFs on lava rock[247]
dehydrogenation
oxygen reduction
carbon nanofilaments;[246] CNFs on carbon felt;[215,216]
CCVD, electrospinning,
Pt NPs-coated Nb-doped TiO2 NFs;[248] N-doped CNFs[249]
polyol reduction
photocatalysis
proton exchange
membrane fuel cell
electrospinning
hollow TiO2 NFs;[250] TiO2 NFs[251]
CCVD, electrospinning,
sulfonated polyimide NFs in sulfonated polyimide;[252]
polyol reduction
Pt NPs-coated CNFs;[253] Pt NPs-coated CNFs on carbon
fabrics[254]
chemical coupling
electrospinning
CNFs containing Pd NPs;[219] Pt-, Pd-, or Rh-coated TiO2 or
ZrO2 NFs[255]
electrospinning
TiO2 NFs containing Pt NPs[256]
cell lysis
electrospinning
lysozyme-coated PCL/PLGA-b-PEG-NH2 NFs[257]
hydrolysis
electrospinning
PS/PSMA NFs containing a-chymotrypsin;[258]
water gas shift
homogeneous
catalysis
PVA NFs containing lipase[259]
aza-Diels-Alder
CCVD, electrospinning
PS core, PPX, or PPX C-shell, NFs containing Sc(OTf)3[260,261]
oxidation
CCVD, electrospinning
PAMAM-coated on inner surface of PPX nanotubes[260]
Michael addition
electrospinning
PS NFs containing prolinol-oligostyrene[262]
others
electrospinning
a-Chymotrypsin-coated PS NFs;[263] lipase-coated PANCMPC
NFs;[264] lipase-coated PSU/PVP or PSU/PEG NFs[265]
a)
AA, acrylic acid; CNFs, carbon nanofibers; CCVD, catalytic chemical vapor decomposition; HDP, homogeneous deposition precipitation;
MWCNTs, multi-walled carbon nanotubes; NFs, nanofibers; NPs, nanoparticles; PAMAM, polyamidoamine; PAN, polyacrylonitrile;
PANCMPC, poly[acrylonitrile-co-(2-methacryloyloxyethyl phosphorylcholine)]; PANI, polyaniline; PCL, poly(e-caprolactone); PEG, poly(ethylene glycol); PEI, polyethyleneimine; PLGA, poly[(D,L-lactic acid)-co-(glycolic acid)]; PPX, poly( p-xylylene); PS, polystyrene;
PSU, polysulfone; PSMA, poly[styrene-co-(maleic anhydride)]; PVA, poly(vinyl alcohol); PVP, poly(N-vinyl-2-pyrrolidone); SDS, sodium
dodecylsulfate.
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on the catalytic applications of nanofibers were in vitro,
small-scale, and laboratory-based investigations. While
these may be satisfactory for elucidating and understanding catalytic processes and evaluating materials for
further development, the promising catalytic performance
of nanofiber-based catalysts needs to be assessed and
validated with scale-up studies in pilot plants for potential
industrial applications. Besides reaction efficiency, other
relevant performance parameters need to be examined
in evaluating nanofiber-based catalysts for industrial
catalysis. For instance, selectivity of the catalyst for the
desired reaction pathway or product should be assessed.
Chen et al.[230] studied the acetaldehyde and carbon
dioxide selectivities of Ag-hollandite nanofibers in
the catalytic oxidation of ethanol and found that acetaldehyde selectivity was almost 100% below a reaction
temperature of 170 8C but any further increase in reaction
temperature resulted in a drop in selectivity due to the
formation of carbon dioxide. Catalyst leaching and
catalytic yield after repeated runs are also major concerns
in industrial catalysis. Stasiak et al.[261] investigated the
loss of Sc(OTf)3 catalyst from polystyrene core/poly( pchloroxylylene) shell nanofibers and found that most
catalyst loss occurred during the pre-washing process
and initial catalysis run. Despite the low-catalyst loading
after this initial leaching, catalytic activity of the nanofibers
in aza-Diels-Alder reaction remained high. However, yield
was significantly reduced after the 5th catalytic run.
Other factors of interests in the design and characterization
of nanofiber-based catalysts include catalyst poisoning,
deactivation, stability under different reaction conditions,
and ease of catalyst regeneration/reuse.
4.6. Filtration and Separation
Nanofibers have great potential in filtration due to their
unique morphology. Their thin fibers, high-specific surface
areas and narrow but open pore structures allow for
high-filtration efficiency at high flux with low-pressure
drop.[267,268] Filtration performance is dependent on
nanofiber morphology, which can be modified easily by
varying fabrication parameters.[269–271] Nanofibers have
been investigated for use in particulate filtration in
fluids,[272,273] aerosol,[274] and emulsion filtration[275] with
promising results. This review will focus on the chemical
aspects of filtration and separation using nanofibers.
Table 5 provides a summary of nanofibers that have
been investigated for chemical-related applications in
filtration and separation.
Nanofibers made from inert materials are used
solely as particulate filters. However, with chemical
functionalization, nanofiber filter membranes can
detoxify the filtering medium by removing molecular or
ionic contaminants. Dai et al.[299] electrospun polymeric
nanofibers for the removal of model polycyclic aromatic
hydrocarbons anthracene, benz[a]anthracene, and
benzo[a]pyrene from wastewater. Best absorption
capacity of 4112.3 35.5 mg g1 for anthracene on PCL
nanofibers, and 1338.8 16.9 mg g1 for benz[a]anthracene and 712.1 7.8 mg g1 for benzo[a]pyrene on PLCL
nanofibers were obtained. Absorption mechanisms were
found to be mainly hydrophobic interaction, hydrogen
bonding, p–p interactions and pore-filling between hydrocarbon molecules and polymer nanofibers. Chen et al.[305]
surface-coated carbon nanofibers with b-cyclodextrin
(b-CD) and found that they were able to remove 100%
of phenolphthalein from an ethanol/water mixture in
5 min and 132.43 mg g1 of fuchsin acid compared to
34.2 mg g1 in activated carbon.
Incorporating catalysts that break down contaminants
into nanofiber filter membranes can help prevent membrane fouling due to accumulation of contaminant
molecules on the fiber surfaces, a common phenomenon
observed in molecular filter membranes that leads to
decreased filtering efficiency, low flux, and high-pressure
drop.[220] Ceramic or metal nanoparticles are usually
incorporated into nanofiber filter membranes to catalytically degrade molecular contaminants. Demir et al.[280]
synthesized Ag-nanoparticle-coated poly[acrylonitrile-co(glycidyl methacrylate)] (P(AN-GMA)) and poly(glycidyl
methacrylate) (PGMA) nanofibers and found that they
could completely reduce Methylene Blue in 11 min in
the presence of NaBH4. Ceramic nanofibers can also be
employed for the same purpose. Li et al.[285] electrospun
CeO2–ZnO nanofibers and found that they could photocatalytically degrade 98% of Rhodamine B in 3 h. Besides
molecular contaminants, bacteria also cause membrane
fouling. Integrating anti-bacterial materials such as Ag
nanoparticles[306] or chemical biocides[317] into nanofiber
filter membranes can reduce the amount of bacteria in
both filtrate and membrane and help prevent/delay
membrane biofouling.[318]
Nanofibers have also been applied in product purification
as separation and affinity membranes. Peng and
Ichinose[313] fabricated MnOOH nanofibers and used
them to separate various compounds. Selectivity factor of
4.9 was obtained for ethanol/water separation and
26.7 for CO2 separation from air, with 93% rejection for
5 nm Au nanoparticles (NPs) and 94% absorption for
Cytochrome C after 2 min 40 s in separate tests. Yoshimatsu
et al.[319] synthesized PET nanofibers containing propranolol-imprinted nanoparticles. The nanofibers showed high
selectivity toward propranolol (80%) compared to other
structural analogs (<50%) and stability in various solvent
systems.
Different nanofiber-based membranes have been
synthesized for filtration and separation of various substances. Performance in the functionalities of interest have
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Table 5. Nanofibers for filtration and separation.
Function
Nanofiber useda)
Nanofiber fabrication
technique
catalytic degradation
electrospinning
Fe NPs-coated PAA/PVA NFs;[276–278] Fe3O4 NPs in PANCAA
of organic
NFs;[279] Ag NPs-coated P(AN-GMA) and PGMA NFs;[280] SiO2 NFs
compounds
containing Ag NPs;[281] Cu or Fe NPs supported on CNFs[282]
photocatalytic
degradation
of organic
electrospinning,
hydrothermal synthesis,
NFs;[284] Ag NPs-doped zeolite Y particles on Al2O3 NFs;[220]
sol/gel synthesis,
CeO2ZnO NFs;[285] TiO2 NFs;[286] hydrogen TiO2 NFs;[286,287]
template synthesis
compounds
TiO2 NPs-coated PSEI NFs;[283] polymer NFs containing short TiO2
TiO2 NPs-coated TiO2 NFs;[288] anatase-coated TiO2(B) NFs;[289]
TiO2-coated CNFs[290]
ion absorption
hydrocarbon
absorption
CCVD, electrospinning,
Nylon-6 or PCL NFs containing AlOOH NPs;[291] SiO2 and
hydrothermal synthesis,
PVA/SiO2 NFs;[292,293] dithizone NFs;[294] SiO2 NFs;[295,296]
re-precipitation,
Na2Ti3O7 and Na1.5H0.5Ti3O7 NFs;[297] CNFs in
sol/gel synthesis
Ba2þ-alginate-coated vesicles[298]
electrospinning,
PCL, PDLLA, PLACL, PLGA, and MPEG-PLGA NFs;[299]
hydrothermal synthesis
PMMA/PNIPAM NFs;[300] Azido phenyl-carbomylated or
phenyl-carbomylated b-CD/PMMA NFs;[301] PS NFs containing
a-, b-, or g-CD;[302] DNA-CTMA NFs containing Fe3O4 NPs;[303]
CNFs;[304] b-CD-coated CNFs[305]
pathogen removal
electrospinning
Ag NPs-coated PA, PAA, PEI and PSU NFs;[306] chlorinated
m-aramide NFs;[307] Nylon-6,6 NFs containing various
biocides;[308] Ag NPs-containing CA, PAN and PVC NFs[309]
multi-functional
membranes
electrospinning,
hydrothermal synthesis,
solution aging with
poly(MMA-co-NAAP) NFs;[310] chitosan/PEO NFs;[311]
TiO2 NPs-coated polyamide-1,1 NFs;[312] MnOOH NFs;[313]
TiO2 nanofibers[314]
aminoethanol
affinity membrane
rlectrospinning
Cibacron Blue F3GA-coated cellulose NFs;[315] PET NFs
containing propranolol-imprinted NPs[316]
a)
CA, cellulose acetate; CD, cyclodextrin; CNFs, carbon nanofibers; CTMA, cetyltrimethylammonium; MMA, methyl methacrylate; MPEG,
methoxypoly(ethylene glycol); NAAP, : N-allyl-4,5-di[(2-picolyl)amino]-1,8-naphthalimide; NFs, nanofibers; NPs, nanoparticles; PA,
polyamide; PAA, poly(acrylic acid); PAN, polyacrylonitrile; PANCCA, poly[acrylonitrile-co-(acrylic acid)]; P(AN-GMA), poly[acrylonitrile-co-(glycidyl methacrylate)]; PCL, poly(e-caprolactone); PDLLA, poly(D,L-lactide); PEI, polyethyleneimine; PEO, poly(ethylene oxide);
PET, poly(ethylene terephthalate); PGMA, poly(glycidyl methacrylate); PLACL, poly(lactide-co-caprolactone); PLGA, poly[D,L-lactic acid)-co(glycolic acid)]; PMMA, poly(methyl methacrylate); PNIPAM, poly(N-isopropylacrylamide); PS, polystyrene; PSEI, polydimethylsiloxaneblock-polyetherimide; PSU, polysulfone; PVA, poly(vinyl alcohol); PVC, poly(vinyl chloride).
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degradation performance against the original compounds
would need to be assessed and validated. Furthermore,
different functionalities in multi-functional nanofiber
membranes had mostly been evaluated independently. A
better assessment of multi-functionality and potential for
the intended application is to study the performance of
all functionalities simultaneously in field trials or under
realistically simulated experimental conditions. Relevant
factors of interest in the design and evaluation of nanofiber-
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been evaluated and found to be promising or even better
than the membranes currently in use. Fabrication techniques used depends on the architecture of nanofiber design
while characterization techniques employed depends on
the performance of interest in the application that the
nanofibers have been designed for. Many reported studies
used model compounds such as dyes to study the chemical
degradation performance of nanofiber membranes. For
further development in the intended application, chemical
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based membranes include working capacity, selectivity,
leaching, stability under different working conditions,
mechanical integrity, ease of regeneration, working/
storage life, and environmental compatibility.
4.7. Chemical Protection and Decontamination
Chemical protection and decontamination represents a
niche application for nanofibers that combines their
excellent filtration property, high-fluid flux, and large
specific surface area which can support catalysts,
molecules, and chemical reactions. Research in this area
has focused mainly on the application of nanofibers for
the development of permeable wearable protective systems for military use such as gas masks and chemical
protective suits.[320,321] However, such systems also find
useful potential applications in personnel protection in
environmental remediation and chemical processing
industries, and also in the decontamination of the
environment, facilities, and equipment exposed to toxic
chemicals. Table 6 provides a summary of nanofibers that
have been investigated for use in chemical protection and
decontamination.
Degradation of toxic chemicals by nanofiber membranes
have been achieved through various means. Incorporating
metal or metal oxide nanoparticles into nanofiber
membranes to catalytically degrade toxic chemicals is
a common technique.[321] Krogman et al.[323] fabricated
TiO2-nanoparticle-coated nylon-6,6 composite nanofibers
that could photocatalytically degradation 74% of chloroethylethylsulfide (CEES), a stimulant for mustard gas, while
maintaining a water vapor flux of 14.2 kg m2 d1
compared to 12.1 kg m2 d1 in a US army cotton
battle-dress uniform. Catalytic metal oxide nanofibers
Table 6. Nanofibers for chemical protection and decontamination.
Application
Nanofiber useda)
Nanofiber fabrication
technique
photocatalytic degradation of allyl
electrospinning
TiO2 NP-coated PAN, PEO, PMMA, PS and PSEI
NFs[322]
alcohol
photocatalytic degradation of CEES
electrospinning
TiO2 NP-coated nylon-6,6 NFs[323]
photocatalytic degradation of CEPS
electrospinning
TiO2 NP-coated PANI/PEO and PVC NFs[324]
photocatalytic degradation of CEPS
electrospinning
TiO2 Ns-coated PSU NFs[325]
catalytic hydrolysis of DFP
electrospinning
PAAO-coated PAN NFs and PAAO NFs[326]
catalytic hydrolysis of PNPA
electrospinning
PAAO NFs[327]
catalytic hydrolysis of paraoxon
electrospinning
PVC, PVDF, and PSU NFs containing MgO or Al2O3
NPs[328]
catalytic hydrolysis of paraoxon
electrospinning
PVC NFs containing IBA and b-CD[329]
catalytic hydrolysis of CEES,
electrospinning
ZnO/TiO2 NFs[330]
electrospinning
TiO2 NP-coated nylon-6/PEI NFs and nylon-6/PEI
DMMP and paraoxon
catalytic hydrolysis of DMCP and
NFs[331]
paraoxon
catalytic hydrolysis of DFP;
electrospinning
PU NFs containing glucose oxidase, horseradish
peroxidise and copolymers based on DMAA-MA
and 4-PAM[332]
antimicrobial activity against
aqueous E. coli and S. aureus
absorption of topically
electrospinning
PU NFs containing absorbent particles[333]
applied octylmethoxycinnamate
a)
4-PAM, : N-alkyl-4-pyridiniumaldoxime; CD, cyclodextrin; CEES, chloroethylethylsulfide; CEPS, 2-chloroethylphenylsulfide; DFP, diisopropyl fluorophosphates; DMAA-MA, dimethylacrylamide methacrylate; DMCP, dimethyl chlorophosphate; DMMP, dimethylmethyl
phosphonate; IBA, : o-iodosobenzoic acid; NFs, nanofibers; NPs, nanoparticles; PAAO, polyacrylamidoxime; PAN, polyacrylonitrile; PANI,
polyaniline; PEI, polyethyleneimine; PEO, poly(ethylene oxide); PMMA, poly(methyl methacrylate); PNPA, p-nitrophenyl acetate; PS,
polystyrene; PSEI, polydimethylsiloxane-block-polyetherimide; PSU, polysulfone; PU, polyurethane; PVC, poly(vinyl chloride); PVDF,
poly[(vinylidene fluoride)-co-(hexafluoropropylene)].
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which exhibited poor fidelity to the working conditions
of intended use. Potential for practical applications
could be more accurately assessed with field trials or
under realistically simulated experimental conditions.
For instance, Lee et al.[322] evaluated the degradation
and penetration of allyl alcohol in TiO2-coated nanofibers
under continuous flow, which more accurately represents
the working conditions of intended use. Chemical degradation performances of nanofiber-based catalysts were also
frequently evaluated independently against individual
compounds. It would be interesting to know how
degradation performance of these catalysts would fare in
the presence of multiple agents of similar and/or different
chemical types. Such information are of importance
since it is difficult to predict in advance the compounds
that require decontamination or protection against. In
addition, a more comprehensive assessment against
various pertinent factors which could significantly impact
the chemical degradation performance of nanofiber-based
catalysts is required, such as reactant concentration,
environmental contaminants, catalyst poisons, working
conditions, repeated usage, and wear.
4.8. Textiles and Cosmetics
The applications of nanofibers in textiles and cosmetics
are indicated in Table 7. Natural fibers such as cotton
have been used traditionally for clothing because they
impart comfort due to their softness, high absorbency,
and high-fluid flux. However, their uses in non-clothing
applications such as sporting equipment and upholsteries
are restricted due to low strength, low durability, ease of
soiling, and flammability. Synthetic polymer fibers are
strong and dirt-resistant but they lack the flexibility and
comfort of their natural counterparts.[334] Fabricating and
using synthetic polymers nanofibers as textiles/fabrics
could serve to overcome these short-comings. The thin
diameters of nanofibers provide them with flexibility
comparable to that of natural fibers while their open,
porous morphologies ensure high-fluid fluxes. Mechanical
strength of nanofiber mats/films can be reinforced by
depositing/laminating them onto conventional textiles/
fabrics or synthetic polymer substrates.[335]The resulting
composite textiles/fabrics could maintain their desirable
characteristics such as mechanical strength, nanofiber
morphology, fluid flux, and thermal conductivity after
repeated laundering.[336,337]
Incorporating functional materials into nanofiber
textiles/fabrics during synthesis can endow them with
many useful properties such as resistance to liquid
penetration,[365–368] magnetism,[369] and electrical conductivity[370,371] that are difficult to realize with natural
fabrics. This facilitates the development of functional
textiles/fabrics with applications in personnel protec-
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can also be used directly to decompose toxic compounds.[321] Ramaseshan and Ramakrishna[330] fabricated
ZnOTiO2 nanofibers with different Ti and Zn ratios and
found that nanofibers synthesized with 40% Ti had the
best hydrolytic activity, achieving 91% decomposition of
paraoxon, a stimulant for organo-phosphorus compounds,
in 50 min, and 69% decomposition of CEES in 10 min.
While ZnOTiO2 nanofibers are not likely to be use in
protective clothing due to their brittleness, they can be
mounted onto stiff substrates to be used in filter canisters
in facemasks.
Polymeric materials with reactive functional groups that
can degrade toxic compounds have also been fabricated
into nanofiber membranes. Chen et al.[326] functionalized
the surfaces of electrospun polyacrylonitrile (PAN) nanofibers with oxime groups for the hydrolysis of diisopropyl
fluorophosphates (DFP), an organo-phosphorous nerve
agent. It was found that reaction increased by as much
as 80-fold compared to PAN nanofibers. Molecular
catalysts for the decomposition of toxic chemicals can
be synthesized and integrated into nanofiber membranes
as well. Ramaseshan et al.[329] synthesized a detoxification
catalyst b-CD þ o-iodosobenzoic acid (IBA) and incorporated it into poly(vinyl chloride) (PVC) nanofibers. The
resulting PVC/b-CD þ IBA blended nanofibers was found
to be 11.5 times faster in the hydrolysis of paraoxon
compared to activated charcoal and 2–10 times faster
than PVC/b-CD, PVC/IBA, and PVC/IBA/b-CD blended
nanofibers.
For direct exposure of skin to chemical contaminants,
nanofibers can offer decontamination solutions. Vigorous
washing and scrubbing of exposed skin massages it and
increases transport of contaminants into hair follicles. As
hair follicles are long-term reservoirs for topically applied
substances, harmful effects of contaminants may extend
for long periods of time without detection and elimination.
The use of absorbents is a better way to remove topical
contaminants. Lademann et al.[333] developed electrospun
PU nanofiber films containing absorbent particles trapped
within their matrices and found that they were able to
remove more topically applied sunscreen from skin (65%)
compared to washing (40%).
Nanofibers have proven to be suitable carriers for
catalysts in chemical protection and decontamination,
and could even be made from the catalysts themselves.
Chemical degradation performance of these nanofiberbased catalyst systems had mostly been evaluated against
model compounds in place of more dangerous ones. While
this allows for safer research and evaluation of materials
in the laboratory for further development, the chemical
degradation efficacy of these catalysts still requires
validation against the original compounds. Degradation
performances of nanofiber-based catalysts were also
typically evaluated under closed or static conditions,
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Table 7. Nanofibers for textiles and cosmetics.
Application/
Function
Nanofiber useda)
Nanofiber fabrication
technique
textiles
UV protection
electrospinning
PU NFs containing ZnO NPs[338]
anti-bacterial
electrospinning
CA NFs containing C1-BTMP;[339] PU NFs containing
5,10,15,20-tetraphenylporphyrin[340]
self cleaning
electrospinning
CA NFs containing TiO2 NPs;[341] PAN NFs containing
1,4-bis(o-cyanostyryl)benzene or 1-(o-cyanostyryl)-4( p-cyanostyryl)benzene[342]
color change
electrospinning
PEDOT NFs coated with thermochromic inks;[343] polyimide NFs
containing cis-DATPP[344]
energy storage
electrospinning
PVDF-PEG 1000 NFs containing fumed silica[345]
environmental
electrospinning
activated carbon cloths from lyocell-based regenerated cellulose
nanofiber fabrics;[346] carbonized PAN NFs on activated carbon
remediation
microfibers[347]
multi-functional
textiles
electrospinning
extrusion/extraction
PVA-co-PE NFs coated with 2-AQS, 2,6-AQS or 2,7-AQS;[348] PU NFs
containing ZnO NPs;[349] TiO2-coated PAN NFs;[350] Nylon-6 NFs
sol/gel synthesis
containing TiO2 NPs[351]
fragrance
electrospinning
PS NFs containing a-, b- or g-CD and menthol[352]
topical delivery
electrospinning,
cosmetics
extraction
collagen NFs containing Au NPs, L-ascorbic acid, retinoic acid and
b-CD;[353] CA NFs containing retinoic acid and a-tocopherol;
[354]
PAN NFs containing L-ascorbic acid 2-phosphate and a-tocopherol
acetate;[355] Silk NFs containing 2-phospho-L-ascorbic acid;[356]
BC NFs (BiocelluloseTM and NanoMasqueTM);[357–359] self-dissolving
patch;[360,361] chitin nanofibrils[362–364]
a)
2-AQS, anthraquinone-2-sulfonic acid; 2,6-AQS, anthraquinone-2,6-disulfonic acid; 2,7-AQS, anthraquinone-2,7-disulfonic acid;
BC, bacteria cellulose; C1-BTMP, : bis(N-chloro-2,2,6,6-tetramethyl-4-piperidinyl) sebacate; CA, cellulose acetate; CD, cyclodextrin;
NFs, nanofibers; NPs, nanoparticles; PAN, polyacrylonitrile; PCL, poly(e-caprolactone); PEDOT, poly-3,4-ethylenedioxythiophene; PEG,
poly(ethylene glycol); PLGA, poly[(lactic acid)-co-(glycolic acid)]; PS, polystyrene; PU, polyurethane; PVA, poly(vinyl alcohol); PVA-co-PE,
poly[(vinyl alcohol)-co-ethylene]; PVDF, poly(vinylidene fluoride).
tion,[365,366,372] environmental remediation,[346,347] magnetic shielding,[373] anti-counterfeit tagging,[369] and wearable electronics/energy storage.[345,374–376] Chemical functionalities in textiles/fabrics can be enhanced with the
use of nanofibers. For instance, nanofiber textiles/fabrics
containing anti-microbial/anti-fungal agents showed
greater activity and better performance compared to cast
films as their dense, narrow but open pores and highspecific surface areas which could trap bacteria better and
increase their exposure to the anti-microbial/anti-fungal
agents.[339,340] Similarly, depositing a thin layer of polyurethane nanofibers containing UV-blocking ZnO nanoparticles onto textiles/fabrics could impart them with UV
protection factor >40 for both UV-A and UV-B radiation
while maintaining air and water vapor fluxes through the
composite material due to the dense nanofiber mesh and
its porous morphology.[338] Nanofiber fabrics had also been
employed as sensor materials; their high-specific surface
areas ensured excellent sensor/environment interactions
resulting in shorter response/recovery times and higher
sensitivities.[344,372]
The large specific surface area of nanofibers finds
useful application in cosmetics products as well, usually
as masks/patches for topical delivery/application of
cosmetics/therapeutic substances.[377] Nanofiber facial
masks, such as BiocelluloseTM,[358] NanoMasqueTM,[359]
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4.9. Chemical Sensing
Chemical sensors are typically based on property changes
in their sensing materials due to chemical interactions
with analyte molecules. Sensor performance thus depends
very much on the speed and magnitude with which
the material property is modified. Traditional chemical
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sensors use thin films to speed up their interactions with
analyte molecules. However, their performance remains
unsatisfactory due to slow sensor/analyte interactions,
resulting in long response/recovery times, low sensitivities,
and high limits of detection. Recently, nanofibers have been
investigated as sensing materials for chemical sensors.
Their thin fibers, high-specific surface areas and porous
morphology enable swift sensor/analyte interactions that
produce faster response/recovery, higher sensitivities, and
lower limits of detection.[378] Table 8 provides a summary
of the nanofibers that have been investigated for use in
chemical sensing.
Conducting polymers such as poly(3,4-ethylenedioxythiophene) (PEDOT), polypyrrole, and polyaniline are
commonly used in chemical sensors.[378] Interaction
between polymer and analyte molecules changes the
conductivity of the polymer, which is measured and
used to quantify the amount of analyte present. Kaner
and co-workers synthesized a series of polyanilinebased nanofibers and investigated their use as sensing
materials.[385,386] Results showed that nanofibers outperformed thin films in chemical sensing in terms of
response/recovery times, sensitivity, and limit of detection.
For example, polyaniline-nanofiber-based sensors had a
response time of 2 s and >20% resistance change in the
presence of 20 000 ppm methanol compared to 33 s and
<15% resistance change in film-based sensors. HCl sensing
produced similar results. Polyaniline nanofibers-based
sensors had a response time of 2 s compared to 30 s in
film-based sensors in the presence of 100 ppm HCl
(Figure 5).[410] Chemical sensing in polyaniline occurs
through various means including doping, de-doping,
reduction, swelling, and polymer chain conformation
changes. For analytes that do not interact significantly
with polyaniline, the polymer can be doped, coated, or
composited with other materials during nanofiber synthesis to induce resistance change in the presence of the
analyte. The high specific surface area, porosity, and thin
diameter of nanofibers mean faster diffusion of analyte
molecules into the polymer to effect these changes,
leading to better sensor performance. Besides conducting
polymers, other conducting materials such as ceramic
nanofibers and carbon nanofibers have also been used
in chemical sensing. Santangelo et al.[398] fabricated
VOx-coated carbon nanofibers and applied them to the
detection of NO2 in air. Performance of the sensor was found
to be dependent on the crystal structure of VOx. Beside
resistance, other material properties such as current,[381]
fluorescence,[379,380] color,[344] surface acoustic wave
(SAW),[399,400] and reflectance[382] can also be measured
and used for chemical sensing.
When functionalized with biomolecules, nanofibers can
act as effective biosensors. Tang et al.[406] immobilized
glucose oxidase onto TiO2 nanofibers with chitosan and
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and the Self-Dissolving PatchTM [361] are already commercial
available for topical delivery/application of a wide variety
of cosmeceuticals. Formulating cosmeceuticals into nanofibers also helps to improve their stability against
environmental degradation. For instance, it was found
that incorporating menthol into polystyrene nanofibers as
cyclodextrin/menthol complexes could improve its release
and stability up to 350 8C.[352] Integrating Vitamin A and C
into collagen nanofiber facial masks enhanced their
stability against oxidation as these masks need only be
moisten before use. In contrast, commercial cotton facial
masks that are pre-moistened led to oxidation and
degradation of their active ingredients before use. The
high-specific surface area of the collagen nanofiber facial
masks also helped ensure optimum contact between mask
and skin to enhance penetration of active ingredients into
the skin for maximum effect.[353]
Nanofiber-based textiles with different functionalities
have been developed for a variety of applications.
Performance in the functions of interest have been
investigated and found to be satisfactory or even better
than that of traditional bulk textile materials. However,
other material properties of nanofiber-based textiles that
are relevant to their intended applications also need to be
assessed. For instance, while air and moisture permeabilities are routinely evaluated for nanofibers developed for
clothing applications, mechanical integrity, which is
equally important, is not always investigated. Conventional tensile tests that are used to examine material
strength and stiffness are insufficient to characterize
clothing material; tests for other mechanical properties
such as pliability, tear, bending, compression, or peel
strength would be more relevant and useful.[335,337] Other
material properties that are pertinent to clothing, such
as water repellency, thermal conductivity, and touch,
may also need to be assessed.[336] For skin-contacting
applications, cell viability, and biocompatibility should
to be evaluated. Investigations into the performance of
nanofiber-based textiles after prolonged usage, wear, and
under different working conditions are also required. Field
studies could be conducted to evaluate the performance of
the nanofiber-based textiles in order to better understand
the effects of practical use and identify opportunities for
improvements. Where necessary, safety issues relating to
the use of nanomaterials in nanofiber-based textiles, such
as toxicity and leaching, must be addressed.
L. T. H. Nguyen et al.
www.mme-journal.de
Table 8. Nanofibers for chemical sensing.
Chemical sensor
Nanofiber useda)
Nanofiber fabrication
technique
gas sensors
colorimetric/fluorescence
electrospinning
Polyimide NFs containing cis-DATPP[344]
fluorescence
electrospinning
PU NFs containing PAA-PM;[379] PS NFs containing a
fluorescent sensing polymer (porous/solid)[380]
current
electrospinning,
PANI/TiO2 composite NFs[381]
chemical oxidative
polymerization
reflectance
polymerization
resistance
electrospinning,CCVD,
MWCNT-coated nylon-6,6 NFs;[383] MWCNT-coated
rapidly initiated
nylon-6 NFs and nylon-6 NFs containing MWCNTs;[384]
polymerization,interfacial
PANI NFs;[385–388] PANI NFs modified with CuCl2;[386,389]
polymerization,
PANI NFs modified with CuBr2;[390] amine-coated PANI
chemical deposition,
NFs;[22] PDADMAC-coated APTS-BH/PEO/PANI NFs;[391]
vapor deposition,
polymerization,
atomic layer, deposition
SAW
CNFs[382]
rapidly initiated
PANI NFs containing CNTs;[392] PPy NFs;[393,394]
PMMA/BPO core PPy shell NFs;[395] PEDOT:PSS/PVP
NFs;[396] CNFs;[397] VOx-coated CNFs[398]
PANI NFs;[399] PPy NFs[400]
polymerization
ion sensors
electrospinning
PU NFs containing PAA-PM[379]
fluorescence
electrospinning
H-PURET-coated CA NFs[401]
current
rapidly initiated
Au NPs-coated PANI NFs coated with DNA[402]
fluorescence
biosensors
polymerization
electrogenerated
in carbon paste
amperometric
Cholesterol oxidase immobilized on CNF/CdS hollow
sphere composite[403]
chemiluminescence
electro-polymerization,
HRP immobilized on PANI-PVS NFs;[404] HRP immobilized
bacteria, electrospinning,
on Au NPs-coated BC NFs;[405] glucose oxidase immobilized
polyol reduction
on TiO2 NFs with chitosan;[406] CNFs;[407] Glucose oxidase
immobilized on CNFs;[408] Pt NPs-coated CNFs;[409]
streptavidin immobilized on Au NPs-coated CNFs[386]
a)
APTS, 3-aminopropyltriethoxysilane; BC, bacteria cellulose; BH, 1-bromohexane; BPO, benzoyl peroxide; CA, cellulose acetate; CCVD,
catalytic chemical vapor decomposition; CNFs, carbon nanofibers; cis-DATPP, 5,10-bis(4-aminophenyl)-15,20-diphenylporphyrin;
H-PURET, hydrolyzed poly[2-(3-thienyl)ethanolbutoxycarbonylmethylurethane]; HRP, horseradish peroxidase; MWCNTs, multi-walled
carbon nanotubes; NFs, nanofibers; NPs, nanoparticles; PAA-PM, poly(acrylic acid)-poly(pyrene methanol); PANI, polyaniline; PDADMAC,
poly(diallyldimethylammonium chloride); PEDOT, poly(3,4-ethylenedioxythiophene); PEO, poly(ethylene oxide); PMMA, poly(methyl
methacrylate); PPy, polypyrrole; PS, polystyrene; PSS, poly(styrenesulfonate); PU, polyurethane; PVP, poly(N-vinyl-2-pyrrolidone); PVS,
poly(vinyl sulfonate).
used them for H2O2 and glucose sensing. The composite
nanofibers were able to detect H2O2 within 5 s in the
concentration range of 18–72 106 M and glucose within
10 s in the concentration range of 0.01–6.98 103 M.
Although voltammetry is usually employed in biosensing,
other forms of material changes such as current,[402]
fluorescence,[401] and electrogenerated chemiluminescence[403] can also be utilized.
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reduced. The potential of a nanofiber-based chemical
sensor for an intended application is best evaluated
under conditions that most closely resemble its working
environment. Extensive cyclic evaluations are also essential to assess the robustness, stability, and working life of
the sensors.
5. Electronics
5.1. The Need for Nanofibers
A good chemical sensor should have short response and
recovery times, high selectivity and sensitivity, lowdetection limit, large working range, ease of regeneration/recovery, temporal and thermal stability, and robustness. Nanofibers have proven to be better chemical sensors
compared to conventional film- and ceramic-based sensors
in terms of shorter response times, higher sensitivities,
and lower detection limits. Nevertheless, there are still
opportunities for further development. It is observed, for
instance, with the exception of a few cases, that recovery
times of nanofiber-based gas sensors are usually much
longer than their response times. Furthermore, extensive
flushing with air, nitrogen, or sometimes even a neutralizing gas is required to return the response of these sensors to
their original states. No explanation has been given to
account for their long recovery times. However, for practical
applications, recovery times of nanofiber-based gas sensors
needs to be shorten and sensor regeneration made more
convenient. While some nanofiber-based gas sensors
have been developed with selectivity for a particular
analyte through the use of target-specific ligands, others
made from materials such as polyaniline (PANI), multiwalled carbon nanotubes (MWCNT)-nylon 6, polypyrrole
(Ppy), and PEDOT-poly(styrene sulfonate) (PSS)-polyvinylpyridine (PVP) exhibited response to various chemicals.
This highlights the need to understand and evaluate the
response of nanofiber-based gas sensors to the presence
of multiple gases in the sensing environment, which so
far have focused mainly on a single analyte under
controlled conditions. Sensor performance also has to be
assessed under different environmental conditions since
it has been shown to be affected by humidity[388]
and other environmental factors such as temperature.
Concurrently, selectivity to the target analyte needs to
be enhanced and sensitivity to environmental changes
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5.2. Significance of 1D Nanofibers
One of the most significant aspects of nanofibers is
their 1D aspect ratio. Their thin diameters put the radial
dimension of these structures at or below the characteristic
length scale of various interesting and fundamental solid
state phenomena: the exciton Bohr radius, wavelength of
light, phonon mean free path, critical size of magnetic
domains, exciton diffusion length, and others.[422] Figure 6
shows the guided electron transport pathways in nanofibers compared to that in conventional nanoparticles. In
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Figure 5. Response of 0.3 mm nanofiber () and conventional
polyaniline (---) thin films to 100 ppm HCl (Reprinted from
ref.,[410] Copyright 2004, with permission from American
Chemical Society).
Rapid advancement in science and technology in recent
years and the quest for miniaturization of devices and
circuits for better performance and cost benefits have led
to an emerging interest in nanostructured materials.
These nanostructures, which are confined to nanometer
dimensions, exhibit unique and dissimilar properties
compared to their bulk counterparts. The limited motion
of electrons in these confined systems and the quantum
effects produced by nanostructures are the main driving
criteria for extensive research in this field.[411] In this regard,
1D nanostructures, especially nanofibers and nanowires,
have attracted the attention of many researchers of diverse
disciplines due to their novel properties and applications.[412,413] One major area in nanomaterials in which
the potential of one-dimensionality is widely explored is
in the application of inorganic semiconducting metal
oxides.[414,415] The ability to apply the unique properties
of these materials in practical applications demands better
understanding and further development of current technology. The impact of one-dimensionality in physical and
electrical properties have been observed in many nanomaterials including enhanced photon absorption and
emission,[416] improved ballistic transport characteristics[417] and metal to insulator transition in materials.[418]
A large variety of materials have been synthesized in 1D
and incorporated into devices, proving their intriguing
potentials.[418–421] The present review focuses on the
electronic properties of metal oxide nanofibers and
applications of metal oxide nanofibers with few aspects
of nanowires for comparison.
L. T. H. Nguyen et al.
www.mme-journal.de
Figure 6. The guided electron transport pathway in nanofibers compared to that in conventional nanoparticle system.
nanofibers, the mean free path of the electrons is shorter,
giving rise to the intriguing properties for electronic
applications. Low Debye lengths and large surface area
to volume ratios dominate charge transport in these
nanostructures. The expression for Debye length can be
written as:
s
ffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffi
"0 "kB
LD ¼
T
e2 nd
where kB is Boltzmann’s constant, e the dielectric constant,
e0 the permittivity of free space, T the operating
temperature, e the electron charge and nd the carrier
concentration. Surface properties which are altered in this
regard modify the nanofibers’ conductivity, which affects
their charge transport and which in turn, has direct
implication on device performance.[423] Formation of
surface localized acceptor states particularly in metal
oxides results in charge transfer between bulk and surface
in order to establish thermal equilibrium. Thus a nonneutral region within the semiconductor bulk is formed,
resulting in a surface space charge region.[411] In general,
conventional MOS nanoparticles, which are widely used
as gas sensors, exhibit high sensitivity for gas detection
but their sensing properties degrade with the growth of
aggregates among the nanoparticles under repeated
operations at higher working temperatures.[424] Onedimensional nanofibers, with their high-aspect ratios,
large surface areas, and quantum size effects, have become
a favorable candidate for overcoming this issue. This
property is largely applied in gas sensing since the
addition or depletion of majority charge carriers due to
absorption of gas molecules leads to measurable changes
in nanofiber conductivity. The electron density in these
nanostructures depends on the concentration of surface
oxygen vacancies which in turn varies as a function of
oxygen adsorption and desorption.[425] Oxygen vacancies
acts as donor states in metal oxides such as ZnO and
SnO2, attributed to the semiconducting nature of the
material.[426] Modifying the diameter of these nanofibers
to the depletion layer thickness facilitates complete
control of carrier transport. In polycrystalline metal oxide
sensors, the charge carriers need to overcome the energy
barrier formed at the interface of adjacent grains by
thermionic emission to maintain their movement from
one grain to another. Hence, in these 1D nanostructures,
current flows parallel to the surface via carriers which
are thermally activated from surface states. Doping of
nanofibers further enhances their electrical properties.
Materials such as Al, Ga, and In are used as dopants for
ZnO.[427,428] Sb and In are widely used as dopants for
SnO2.[429,430] Dopants in this case help increase the
stability of nanofibers in maintaining their conductivity
by inducing more charge carriers thereby reducing
the Debye length, providing better air stability for the
devices. Doping also facilitates tailoring of the depletion/
space-charge layer by introducing defect states. In this
case, to enhance sensitivity, different promoters such as
Pd, Pt, Ru, Cu, etc. have been used. These promoters aid
in the catalytic activities of the metals during oxidation of
inflammable gases. One of the main factors affecting
carrier transport between nanofiber networks is the
formation of depletion regions at contacts which act as
a hindrance for electron transfer from one nanofiber
to another.[415] Moreover, adsorbents on the surface of
these nanofibers tend to form a positive space charge due
to accumulation of electrons which widen the depletion
layer further.[431] The change in electronic properties is
due to interaction between metal (Ti)–ZnO nanowire of
Schottky barrier at the metal/nanowire interface. This
causes an increase in resistivity due to alterations in
Fermi-level pinning and an increase in barrier heights
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for electron transfer.[432,433] Similarly, the use of nanofibers
allows the formation of a direct conduction path for
photogenerated carriers to the electrode whereas in
conventional nanoparticle structure based solar cells,
conduction is limited by several charge-hopping events
between individual particles. Using nanofibers ensures
that the mobility of the electrons in the solar cells is much
higher than that in nanoparticle-based solar cells with
improvement in device efficiency since recombination
is highly reduced.[434] Moreover, the nano-dimensional
diameters of these nanofibers allows the formation of
depletion regions at the surface leading to interfacial band
bending. This band bending also assists in sweeping
electrons away from the surface of the nanowires thereby
reducing recombination in these devices. Thus, the nano
dimensionality exhibits interesting electronic properties
which are entirely distinct from their bulk counterparts. The
nanofibers also improve the effective electron diffusion
length which aids in efficient collection of electrons thereby
reducing recombination.[434]
5.3. Nanofiber-Based Sensors
Diverse applications of nanofibers in gas sensors are
demonstrated in Table 9. The fundamental concept of gas
sensors is based on changes on the surface of the active
material upon which its electrical or optical properties
depend. The absorbed species trigger these effects causing
a change in the local charge carrier density leading to
variations in conductivity which can be detected.[435] The
active material is chosen in specific interest to the species
to be detected. As discussed earlier, the high-surface area
of 1D nanofibers enable better detection of target species
due to enhanced electronic properties as a benefit of
confined electron transport.[435,436] Electrical responses
were shown to increase with decreasing nanofiber
diameters due to the scaling effect.[437] These nanostructures offer various advantages such as superior stability
due to high crystallinity, very large surface area to volume
ratios, high sensitivity, and selectivity, dimensions comparable to the Debye length and surface space charge
region. These nanofibers can also be extended for mass
production for large-scale fabrication using the simpler
methods as mentioned earlier. Metal oxides are widely used
as active materials in gas detectors due to their potential to
ionosorb oxygen at temperatures above 100 8C.[438] Metal
oxide nanofibers are usually produced by electrospinning
the precursor solution containing metal ions along with
the polymer-solution mixture. The nanofibers are then
calcined at high temperatures to remove the polymer and to
Table 9. Application of electrospun nanofibers in gas sensing.
Principle
Fiber dimension
(nm)
Detected
Detection
limit
Operating
temperature
Reference
TiO2
resistive
120–850
CO, NO2
50 ppb
300–400 8C
[452]
TiO2/ZnO
resistive
250
O2
5.1 103 Torr
300 8C
[453]
TiO2
resistive
200–500
NO2
500 ppb
150–400 8C
[454]
LiCl/TiO2
resistive
150–260
H2O
11%
room temp.
[455]
SnO2
resistive
100
C2H5OH
10 ppb
330 8C
[456]
SnO2
resistive
80–160
toluene
10 ppm
350 8C
[457]
MWCNT/SnO2
resistive
300–800
CO
47 ppm
room temp,
[458]
ZnO/SnO2
resistive
100–200
toluene
10 ppm
200–400 8C
[459]
Fe–SnO2
resistive
60–150
C2H5OH
10 ppm
300 8C
[460]
In2O3
resistive
30
NO2
500 ppb
400 8C
[461]
In2O3
FET
10
NO2
20 ppb
room temp.
[462]
Ag/In2O3
resistive
60–130
HCHO
5 ppm
115 8C
[463]
ZnO
resistive
100–200
H2S
4 ppm
room temp.
[464]
ZnO
FET
40
O2
10 ppm
room temp.
[465]
Pt/In2O3
resistive
60–100
H2S
50 ppm
140–300 8C
[466]
WO3
resistive
20–140
NH3
50 ppm
350 8C
[467]
SrTixFe0.2O3–x
resistive
<100
CH3OH
5 ppm
400 8C
[468]
SnO2
resistive
<200
H2O
1500 ppm
180 8C
[469,470]
SnO2
resistive
<300
H2
10 ppm
200 8C
[471]
SnO2–Ru
resistive
<500
NO2
250 ppm
room temp.
[472]
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enhance the crystallinity of the metal oxide fibers thus
produced. Reports have shown that the absorbed NO2
molecules on the surface increase the resistance of the
metal oxide nanofibers thereby altering its conductivity
due to interactions between the electrons and absorbed
NO2 ions.[439] Moreover, NO2 molecules adsorb onto SnO2
surface oxygen vacancies with certain desorption energies.[440,441] Therefore, metal oxide sensors are generally
operated at temperatures above 150 8C which ensures
fast molecular desorption as well as full recovery of
the initial sensor surface.[442] Nanofibers employed for
detecting target species of gas molecules in field-effect
transistor (FET) type gas sensors are shown in Figure 7.
Metal oxides such as TiO2, WO3, ZnO, SnO2 and MoO3 are
widely used for detecting trace concentrations.[443,444]
Metal oxide nanofibers made of Molybdenum oxide
(MoO3) is used for detecting ammonia.[445] Wang et al.
demonstrated that electrospun WO3 nanofibers exhibited
rapid response and high sensitivity to various concentrations of ammonia due to the high purity of the material,
larger surface-to-volume ratio and increased porosity of
the surface providing better exposure of the gas to the
sensing material.[446] Cobalt-doped ZnO nanofibers were
also employed as photoelectric oxygen sensors due to
their faster response to the variation in surface states w.r.t
oxygen adsorption.[447] TiO2 nanofibers are used for
detecting NO2 and H2.[448] Electrospun TiO2 non-woven
mats were found to exhibit ultra-high sensitivity to NO2
with a detection limit estimated of about 1 ppb (parts
per billion).[448] Electrospun nanofibers can also serve as
effective supporting substrate for other sensing materials
like nanoparticles of noble metals. TiO2 membranes loaded
with Pd nanoparticles resulted in increased sensitivity
and fast response.[449] The response times in this case varies
as a function of nanofiber diameter.[450] Higher specific
surface area of the nanowires/nanofibers combined with
high-porosity results in higher sensor selectivity and it
Figure 7. Application of nanofibers as sensor material for gas
detection in gas sensors.
also enables rapid transport of target molecules.[448]
Craighead et al. fabricated gas sensors based on the
PANI/PEO composite nanofibers by electrospinning which
also exhibited rapid and reversible resistance change on
exposure to ammonia gas. Similarly, carbon nanotubes/
poly(vinylidene fluoride) (PVdF) composite nanofibers
showed 35 times increase in sensing threshold than that
of the film counterpart.[451]
Ultra-sensitive metal oxide gas sensors made from
nanofibers especially by electrospinning has high-aspect
ratio with long nanofiber lengths varying from 10 to several
100 nm. Though these nanofibers can be produced in large
scale with much ease by electrospinning compared to other
1D nanostructure fabrication techniques, reproducibility
and uniformity of nanofiber dimension is yet to be achieved
for sensor applications. A slight variation in the dimension
and porosity of nanofibers could affect the sensitivity of the
gas sensors. Hence in order to overcome this issue focused
research has to be carried out not only in finding new
materials for gas sensors but also in developing optimized
fabrication protocols for even well studied nanofiber
materials to transcend them from lab results to the
industrial applications.
5.4. Nanofibers for Photovoltaics/Solar Cells
This field of research is intensely focused on capturing the
energy that is freely available from sunlight and convert it
into electric power. Photovoltaics follow the principle of
impinging the photons onto the pre-tailored semiconducting junctions favorable for formation of electron-hole pair
upon light absorption. This creates an electric potential
across the interface driving the charges to its appropriate
electrodes. Typical solar cells use junctions between two
inorganic solids (P-N junctions) for energy harvesting. In
the similar fashion, excitonic solar cells such as dyesensitized solar cells (DSSCs); a kind of photochemical cell
uses the liquid solid combination which is well reviewed
elsewhere.[473] The main function of a highly efficient
photoelectrode for DSSCs is to provide expedient
features such as fast electron transporting pathway, slow
interfacial electron recombination network and enhanced
dye absorption by large specific surface area. The anodes
used in the case of DSSC are usually made of sintered films
of nanostructured metal oxides such as TiO2, ZnO, SnO2,
and Nb2O5. The nanoparticle films provide large surface to
interact with the dye or chromophore. The electron-hole
pair disassociates at this interface with electrons injected
into the semiconductor layer. These injected electrons
need to pass through a large number of traps and grain
boundaries present in the nanoparticle film before reaching
the collecting electrode. The holes on the other hand move
toward the Pt electrode which is later reduced by redox
reaction in the electrolyte. The purpose of using NPs is
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mainly for the ease of fabrication and large surface area.
By replacing the NP layer with nanofibers or single
crystalline nanowire, the charge collection efficiency and
electron diffusion co-efficient can be increased to a large
extent owing to minimized losses due to traps and
grain boundaries. One main drawback in this case is the
reduced surface area for dye absorption which subsequently reduces the energy conversion efficiency. ZnO
photoelectrodes made of electrospun nanofibers with
tunable thicknesses is reported. The DSSCs with this
photoelectrode showed power conversion efficiency of
about 3% which is achieved under irradiation of AM 1.5
with power density of 100 mW cm2.[474] ZnO nanofibers
thus obtained after calcination resulted in high crystallinity
with pure wurtzite phase. The improved performance of
these ZnO nanofibers can be attributed to high porosity
enabling efficient permeability of electrolytes and highsurface area enhancing the dye absorption on the photoelectrode surface. In comparison, Law et al. demonstrated
the use of nanowires in DSSC with solution grown ZnO
nanowires giving an efficiency of 1.5% even though
the charge transport properties are highly enhanced. The
cause of low performance is attributed to the decreased
surface area and low-dye loading onto the nanowire
surface.[475] The importance of the surface area in
the nanowire based devices are compared with other
nanostructures such as dendritic wires.[434,476] Highsurface area and close packing of the nanofibers enables
enrichment of the light harvesting and the reduction of
the electron back-reaction on the transparent conducting
oxide surface without significantly sacrificing electron
transport.
The application of nanofibers and its significant performance characteristics in DSSCs is listed in Table 10.
Electrospun TiO2 nanofibers or nanorods are most
widely used as photoelectrode for DSSCs for their highsurface area and high porosity leading to increased
adsorption of dye sensitizers.[477–479] Figure 8 indicates
the improvement of electron diffusion and reduction
of recombination in DSSCs by incorporating electrospun
TiO2 nanowires as photoanodes. Figure 9 shows the
application of metal oxide nanofibers as photoelectrodes
serving as chief electron transport layer in DSSCs. Song
et al. used the porous electrospun TiO2 nanofibers in
the quasi-solid state DSSCs achieving high-photocurrent
generation.[474,480,481] Transient absorption spectroscopy
studies performed at the dye/semiconductor interface
for nanofibers showed improved kinetics of charge
transfer.[482] Kim and co-workers used high-molecularweight poly(vinyl acetate) (PVAc) to induce phase
separation, which resulted in the formation of TiO2
nanorods of size 15–30 nm within sintered nanofibers
Table 10. Application of nanofibers in DSSC and its significance.
Material
Significance
Nanofiber
diameter
[nm]
Efficiency
[%]
Reference
TiO2
100–150
high electron diffusion coefficient
4.2
[434]
TiO2
150–200
high electron diffusion coefficient and low
9.52
[476]
charge recombination
TiO2 nanoparticles/nanofibers
120
nanofibers as a light-harvesting layer,
10.3
[489]
increased IPCE
nanoporous TiO2
200
high porosity, high sensitizer absorption
5.02
[490]
TiO2(solid-state DSSC)
20
enhanced penetration of polymer gel
3.8
[491]
8.8
[492]
electrolyte
TiO2 nanofiber/nanoparticle
200–300
composite
improved light harvesting, lower series
resistance and large shunt resistance
TiO2
150
increased photocurrent
4.14
[493]
TiO2 multi-core
200
high surface area and increased
5.77
[494]
photocurrent
ZnO
500
efficient electron conducting pathway
3.1
[495]
ZnO
200–500
high surface activity, relatively improved
1.34
[496]
Al-doped ZnO
40–150
high surface adhesion and less tensile
0.55
[497]
photocurrent
stress under calcinations
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exhibit better efficiency than TiO2 nanoparticles since the former provides
a better electron transport pathway
reducing the trapping and detrapping
events during the process of charge
collection.[485] SnO2 nanofibers are also
obtained by electrospinning which on
calcination at 500 8C results in polycrystalline nanofibers with high-aspect
ratios. These fibers employed as photoanodes result in increased charge mobility and electron lifetime. But it also had a
drawback of increased recombination
resulting in low-poor conversion efficiency of about 1% due to poor dye
Figure 8. Schematics showing the difference in diffusion process and recombination
process in nanoparticle and nanofiber systems in DSSCs. The bottom and top panel loading as a function of reduced surface
shows the morphologies and energy levels, respectively. Diffusion is improved in
area. Recently it has been demonstrated
nanofibers with enhanced particle size due to reduction of the space charge region
that increasing the Sn concentration in
within the volume of the nanofibers (Reprinted from ref.,[434] Copyright 2009, with
the precursor solution used for electropermission from American Chemical Society).
spinning could result in highly crystalline nanostructures with enhanced
dye loading, high-electron mobility and
increased charge lifetime. These nanostructures also
of diameter 60 nm having higher specific surface
exhibit high-open circuit voltage of about 700 mV and
area of about 123 m2 g1. The resultant dye loading
photovoltaic power conversion efficiency (PCE) of about 3%
(8.59 108 mol mg1) was 2.5 times greater than that
which is higher than any other pure tin oxide photoelecreported for TiO2 nanoparticles (3.44 108 mol mg1).
trodes.[486] Recently SnO2TiO2 core-shell nanofibers are
This innovative combination resulted in efficiencies of 9–
11% similar to the highest efficiencies reported using
also produced by electrospinning to overcome the drawTiO2 nanoparticles.[483] Furthermore, electrospun nanobacks existing in pure SnO2 devices. This core-shell system
fibers also facilitates longer electron lifetimes, and increase
is designed to meet the present state of the art research
effective electron diffusion coefficients (Deff), thereby
requirements for DSSCs by combining the beneficial
resulting in improved carrier collection and device
properties of both the materials by means of a single
performance efficiencies.[484] Recent reports have also
fabrication process. Power conversion efficiency of about
5.1% by employing this is achieved which is five times
shown that photoelectrodes made of TiO2 nanofibers
higher than pure SnO2 nanofiber or nanotube architecture.[487] P-type materials such as CuO nanofibers are also
obtained by electrospinning copper acetate/poly(vinyl
alcohol)/water solution followed by calcination at 500 8C.
These fibers exhibited enhanced crystallinity as a function
of dwelling time under calcination. The dwell time is
found to affect the crystallite size proportionately thereby
altering the bandgap of the material as a result of quantum
confinement. These CuO nanofibers are used as blocking
layer in conjunction with ZnO photoelectrodes which
resulted in 25% increase in the current density as compared
to plain ZnO photoelectrodes.[488]
The application of nanofibers as a replacement for
nanoparticles as photoelectrodes in DSSCs is still an open
debate among the researchers. One of the main reasons is
the scalability issue. Even though electrospinning method
of producing nanofibers is highly scalable and cost effective
compared to other techniques, achieving nanofibers of
uniform diameter (<50 nm) is still a major challenge
Figure 9. Application of nanofibers as photo-electrodes in DSSC.
which is yet to be addressed. Since the nanofiber diameter
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directly plays a major role is determining the specific
surface area which in turn determines the amount of dye
loading onto the photoelectrode. Hence it has a direct
implication on the performance of DSSCs. Even though
many other quasi 1D structures such as nanoflowers,
nanospheres, and so on are reported, there is a trade-off
between low-production rate, surface area, and performance. Moreover vertically aligned nanofibrous photoelectrode with high-specific surface area is not yet achieved in
any of the methods which is really a need of the hour for
improving the efficiency of DSSCs. Future research in the
direction of nanofibers should be able to address these
existing issues by concentrating simultaneously on both
material as well as charge transport perspective in these
devices.
5.5. Energy Storage (Lithium Ion Batteries)
The main factor for future energy needs and application of
alternative energy sources are effective storage media, such
as batteries. Generally, the capacity loss in batteries often
arises from the volume change in charging and discharging
reactions leading to stress-induced material failure. Therefore, nanostructures with high-surface-to-volume ratio,
which additionally contribute to higher conduction values,
are promising anode materials for lithium ion battery. For
the effective incorporation of Li in the electrode material,
reduction and formation of metallic species is highly
required. Therefore, the formed metal reacts with the
reduced Lithium atoms in order to form an alloy which
serves as the storage medium. The process of battery
discharging (Li inserted) and charging (Li released) at room
temperature takes place at anode electrode. Considering the
above mentioned factors electrospun nanofibers serve as
effective electrode materials since these materials possess
shorter charge diffusion path compared to that of the
nanoparticles. Moreover these nanofibers also exhibit faster
intercalation kinetics due to their high-surface area/mass
ratio. Electrospun nanofibers also plays a major role in
reducing the charge transfer resistance between the electrolyte and the active electrode materials since these fibers have
unique property of possessing large number of lithium
insertion sites. Thus the use of nanofibers as electrode
materials in Li-ion batteries has become indispensable.
Some of the applications of nanofibers as anode, cathode,
and separator materials in Li ion batteries are listed in
Table 11. Electronic conductivity of the nanofibers play a
major role in reducing the resistance, thereby, improving
Table 11. Application of nanofibers in batteries and its significance.
Materials
Functionality
Significance
Reference
MnOx/C
anode
high porosity, large surface area, and high conductivity
Fe3O4/C
anode
highly reversible and large volume changed during conversion reaction
[504,505]
[506]
Co/C
anode
Li-ion diffusion distance is reduced
[507]
Sn/C
anode
Sn parking density is higher
[508]
increased surface area and improved interfacial electrode electrolyte
[509]
contact
Si/C
anode
large reversible capacity, cyclic performance is relatively higher and Li
[510]
ion diffusion distance is short
Cu/C
anode
high surface area and increase in reversible capacity
[511]
improved ionic transfer and high electronic conductivity
[512]
Ni/C
anode
high electronic conductivity and higher rate capacity
[513]
porous C
anode
smaller pore size, high surface area, and enhanced stability in cycling
[514]
performance
LiCoO2
cathode
three-dimensional structure, higher rate capacity, and improved
[515]
reversibility
rapid Li ion diffusion
[516]
LiCoO2/MgO
cathode
core/shell structure, high reversibility, and impedance growth is lower
[517]
Al-doped LiNi1/3Co1/3
cathode
superior rate capacity and better cycling performance
[518]
Mn1/3 O2
separator
cycling capability is higher and capacity loss is less
[519]
PVDF-HFP
separator
enhanced electrochemical stability, high-cycling capacity
[520]
SiO2/PAN
separator
stable cycling performance with improved electrolyte uptake
[521]
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Macromol. Mater. Eng. 2012, DOI: 10.1002/mame.201200143
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PVDF
L. T. H. Nguyen et al.
www.mme-journal.de
the Faradaic reaction through enhanced ionic transfer.
The application of electrospun nanofibers as anode
materials in Li batteries exhibits superior electrochemical
properties compared to its nanopowder counterparts. Kim
et al.[483] employed electrospun carbon fibers in lithium
ion batteries achieving a reversible capacity of up to
500 mA h g1. The employment of nanofibers as cathode
and anode materials in Li ion batteries is described in
Figure 10. Chen and co-workers[484] synthesized C/Co
composite nanofibers using electrospinning which when
employed in Li ion batteries showed higher order of capacity
retention and improved electrical conductivity. The electrospun C/Co composite nanofibers thus produced exhibits large
reversible capacity of about 800 mA h g1 and good cycling
performance. Electrospun LiCoO2 nanofibers with diameters about 500 nm exhibited a high-initial charge and
discharge capacity.[498] However, the formation of crystalline Li2CO3 and CoF2 impurities due to the dissolution of
cobalt and lithium cations from LiCoO2 leads to large loss
for the electrode retention capacity. This problem was
solved by fabricating LiCoO2/MgO coaxial nanofibers using
electrospinning. These core/shell fibers exhibited excellent
reversibility and smaller impedance growth.[499] Fu and
co-workers[500] observed that single-walled nanotube
(SWNT)/NiO composite nanofibers synthesized by electrospinning improved the rate capability when compared
with pure NiO nanofibers. It also exhibited better cycling
performance at large charge and discharge current densities
with a noticeable improvement in durability. Fan et al.
prepared Mn3O4 nanofibers by electrospinning. These
nanofibers exhibited excellent electrochemical capacity
which exceeded 450 mA h g1 for at least 50 cycles.[501]
Sun et al.[502] also applied electrospun Mn oxides
nanofibers to Li cells and obtained a high-reversible
discharge capacity of 160 mA h g1. Recently, nitridated
Figure 10. Application of nanofibers as cathode and anode
materials in Li ion batteries.
electrospun TiO2 hollow nanofibers were synthesized by
Hyungkyu et al.[503] These fibers exhibited an excellent
rate performance with discharge capacity of about
85 mA h g1 which was nearly two times higher than
that of pristine TiO2 nanofibers 45 mA h g1. The
significant improvement in the rate capability is due to
the hollow geometry and conducting shell layer of
these nanofibers which provides a shorter Li ion diffusion
length and a high electronic conductivity along the surface.
Thus the nanofibers play a significant role in altering the
electronic properties of these materials resulting in better
performance compared to its nanoparticle counterparts.
High-performance nanofibrous mats employed as
anodes, cathodes, and separators has promising potential
for replacing commercially used nanoparticle based
systems for lithium-ion batteries. Though these nanofibers
exhibit material homogeneity and porosity suitable for
energy storage applications, low-production rate, high cost
of producing ternary metal oxide composites and nanostructure/performance relationship entities of these novel
nanofibers are not well understood. Development of multistacked morphology from nanofibrous mats with highsurface area, porosity, and good surface activity is needed
without leveraging the production rate and homogeneity.
Furthermore recent advances in electrospinning for producing aligned and bridged nanofibers could also provide
simple solution for maintaining fiber integrity and
composition of ceramic nanofiber networks.
6. Conclusion
With advances in the fabrication techniques, many types
of nanofibers with different morphologies and functional
properties can be fabricated to satisfy various requirements
in specific applications. During the past two decades,
studies on nanofibers have shown their significant
advantages in the treatment of tissue/organ failures as
well as chemical and electrical processes. In medicine,
the regeneration of bone, cartilage, skin, heart, and blood
vessels, etc. has been facilitated when they have been
treated with nanofiber-based scaffolds as shown by
successes in small-to-large animal studies and clinical
trials. Besides, nanofibers have provided greater efficiency
in catalytic reactions; higher efficiency and flux in filtration
and separation processes; as well as fast response and
higher sensitivity in chemical sensors compared to other
micro- to macro-size materials. Similarly, higher sensitivity,
improved efficiency and high-rate capability have been
achieved in the applications of nanofibers in sensors, solar
cells, and lithium ion batteries, respectively. However,
further efforts in the modification of nanofibrous structures
and functions should be done to bring them into the
marketplace.
Macromol. Mater. Eng. 2012, DOI: 10.1002/mame.201200143
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7. Future Perspectives
Science and engineering of nano-dimensional structures
are expected to make a significant contribution in
the field of health and biomedical sciences. Further
modifications of nanofibers should be done to closely
mimic the 3D hierarchical structure and mechanical
properties of native ECM of targeted tissues/organs. This
is expected to significantly facilitate the regeneration
of damaged tissues/organs. Besides, detail biological
mechanisms on the interactions between cells and
nanofibrous matrix should be addressed to clearly
understand the influence of nano-dimensional fibers
at cellular level, especially their role in directing
the differentiation of stem cells. Novel engineering of
‘‘smart and designer’’ scaffolds that offer release of biomolecules for effective differentiation of stem cells
could be aimed at therapeutic level favoring patient care.
Another prolific direction would be to study on the
fundamental design of nanofibers that might systematically delivery multiple bioactives and target the
specific compartments of the body, promote tissue
regeneration including blood-brain barrier crossing.
Collective efforts of biologists, engineers, and clinicians
to improve the life quality of patients using stem cell/
biomaterial approach requires thorough investigation
and understanding on the mechanism of stem cell
differentiation on nanofibrous topographies. Moreover,
in vivo assessment of stem cell/biomaterials and their
therapeutic potential need to be more thoroughly
investigated on a long-term basis. This would lay a solid
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foundation to design excellent scaffolds for medical
treatments. Moreover, further large animal studies and
clinical trials of nanofiber-based scaffolds would be
performed to bring these scaffolds into real clinical
treatments of diverse targeted tissues/organs. The
efficacies obtained from these preliminary evaluated
nanofibers together with the development of advanced
technologies will further lead to new therapeutic
methods in the near future. However, the future of
nanotechnology at large depends on the material design
and tools following the detailed evaluation and understanding of the biological processes rather than applying
various materials in vogue.
In chemical processes, current research on the use of
nanofibers has focused largely on developing nanofibers
with single new functionalities. Looking forward, multifunctional nanofiber membranes/films may be preferred
for practical applications due to the unpredictable and
complex nature of their chemical processes. For instance,
multi-functionality is highly desired in protection and
decontamination since it is not possible to predict for
certain which or how many agent users would need
protection against. Multi-functionality could be achieved
by integrating multiple/multi-functional compounds or
functional groups into nanofibers during synthesis.
Amitai et al.[332] reported on the fabrication of multi/
functional composite polymer nanofibers that were able
to detoxify 85% of DFP in 30 min with anti-bacteria
activity against Escherichia. coli and Staphylococcus aureus.
Multi-functional membranes that could remove various
types of pollutants from wastewater had also been
synthesized.[312,314]
In electronics, taking a future perspective, it can be
considered that the advances in the capability to control
the structural/compositional complexity of nanofibers
leads to the development of unique nanosystems including electronic, optoelectronic circuits, systems for harnessing, and storage of energy. The key factor will be in
the exploitation of the science behind the controlling
factors of producing the nanofibers which determines
the functionality of the device. Appropriate selection of
materials combined with the right nanostructure with
precise organization to form a complete device could result
in novel outcomes capable of changing the technologies of
the coming years. For instance, technology which could
produce hydrogen directly from sunlight can be rendered
possible by meticulous engineering of these nanofibers
from both materials as well as from nano-dimensional
point of view.
Received: April 22, 2012; Revised: June 26, 2012; Published online:
DOI: 10.1002/mame.201200143
Macromol. Mater. Eng. 2012, DOI: 10.1002/mame.201200143
ß 2012 WILEY-VCH Verlag GmbH & Co. KGaA, Weinheim
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Amongst the fabrication methods, electrospinning is
the solely method which can fabricate various nanofibers
for all of the three applications, medicine, chemistry, and
electronics. In medicine, electrospinning has been shown to
be the most successfully used method compared to selfassembly and phase separation in in vivo studies. Chemical
applications also achieved significant outcomes by using
nanofibers from electrospinning. In electronics, electrospinning is a very convenient way to precisely control the
hydrolysis rate of ceramic materials, which is crucial
for preparing well-defined ceramic nanostructures. This
technology is to generate new nanostructures by digesting
the as-spun inorganic/polymer nanofibers, followed by a
hydrothermal reaction. This is a novel aspect of electrospun
ceramic nanofibers. And researchers might hopefully
acquire other ceramic nanocrystals with exciting and
well-defined shapes in this way, and bring to this method
some more powerful features. There is no doubt that
electrospinning has become one of the most favored
techniques for fabricating 1D ceramic nanofibers in a
cost-effective and controllable fashion.
L. T. H. Nguyen et al.
www.mme-journal.de
Keywords: applications; chemistry; electronics; fabrication;
medicine; nanofibers
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