Open Access

Synthetic nanowire/nanotube-based solid substrates for controlled cell growth

  • Ku Youn Baik1,
  • Sung Young Park2,
  • Seon Namgung3,
  • Daesan Kim4,
  • Dong-guk Cho5,
  • Minju Lee5 and
  • Seunghun Hong4, 5Email author
Nano Convergence20141:28

DOI: 10.1186/s40580-014-0028-0

Received: 27 August 2014

Accepted: 15 September 2014

Published: 4 November 2014


The behaviour of cells can be controlled by various microenvironments such as nanostructured cell-culture substrates with controlled nanotopography and chemical properties. One of promising substrates for controlled cell growth is a solid substrate comprised of synthetic one-dimensional nanostructures such as polymer nanofibers, carbon-based nanotubes/nanofibers, and inorganic nanowires. Such nanotube/nanowire structures have a similar dimension as extracellular matrix fibers, and their nanotopography and chemical properties can be easily controlled, which expands their possible applications in controlling the growth and differentiation of cells. This paper provides a concise review on the recent applications of solid substrates based on synthetic nanowires/nanotubes for controlled cell growth and differentiation.


Nanowire Nanotube Cell adhesion Cell growth Cell proliferation Cell differentiation

1 Introduction

Cell behaviors, such as adhesion, proliferation and differentiation, are affected by various microenvironmental factors. Such microenvironments consist of extracellular matrices (ECM) with soluble components such as growth factors and cytokines. In order to create artificial microenvironments, biologically-derived materials have been intensively explored, since they have the advantages of being biocompatible and of having similar mechanical properties as native tissues [1]–[4].

Recent advances in nanotechnology present new possibilities and strategies in cell therapy and tissue engineering. Synthetic bio-inspired materials have been developed to create new controllable microenvironments rather than just to mimic in-vivo environments [5],[6]. Among the synthetic nanomaterials, nanowires and nanotubes have a similar dimension with natural ECM components such as collagen and elastic fibers. The diameter of these nanostructures can be precisely controlled, and they can be aligned, patterned or constructed 3-dimensionally [7]. These properties facilitate mimicking microenvironments of various tissues. For example, the parallel-alignment of nanowires mimics that of ECMs in tendon and muscle, and concentric whorls in bone and mesh-like lattices of skin.

The well-investigated nanowires/nanotubes can be categorized into three gropus: 1) polymer nanofibers, 2) carbon based nanotubes/nanofibers, and 3) inorganic nanowires/nanotubes (Figure 1). These nanowire/nanotube structures have many interesting physical and chemical properties which can be easily modulated (Table 1). Polymer nanofibers are biodegradable, which makes them ideal for tissue regeneration and drug delivery [8]. Carbon-based nanostructures can be easily functionalized by chemical or physical methods to control the degree of cell adsorption [9]. Inorganic nanowires can be utilized as devices for measuring cell adhesion force [10], dynamic drug delivery system [11] and electrical cell sensors [12] due to prominent electrical and mechanical properties.
Figure 1

Schematic diagram showing the controlled cell growth on nanowire/nanotube based-substrates. Cells grown on (A) bundles, (B) laterally-aligned patterns, and (C) vertically-aligned structures of nanowires/nanotubes.

Table 1

Overview of properties of synthetic nanowires/nanotubes





Biomedical applications

Polymer nanofibers

Poly (e-caprolactone) (PCL)

0.01 ~ 100 μm


Controlled cell growth (adhesion, migration, proliferation, differentiation) [14]–[22]

Polyaniline (PANi)

Structure (aligned, random)

Poly (L-lactic acid) (PLLA)

Surface functionalization

Polyethersulfone (PES)


Poly (D,L-lactide-co-glycolide) (PLGA)



Carbon-based nanostructures

Signle wall carbon nanotube (swCNT) multi wall carbon nanotube (mwCNT)

1 ~ 2/2 ~ 100 nm


Controlled cell growth (adhesion, migration, proliferation, differentiation) [26]–[36]

Structure (aligned, random, vertical)

Surface functionalization

Carbon nanofiber (CNF)

3.5 ~ 500 nm

Controlled cell growth (adhesion, migration, proliferation, differentiation) [39]–[41]

Inorganic nanowires/nanotubes

TiO2 nanotube

10 ~ 100 nm


Controlled cell growth (adhesion, proliferation, differentiation) [46]–[48]

Orthopaedic implant [46]–[48]

ZnO nanowire

10 ~ 300 nm


Controlled cell growth (adhesion, proliferation, differentiation) [55]–[57]

Structure (aligned, random, vertical)

GaP Nanowire

20 ~ 100 nm


Controlled cell growth (adhesion, proliferation) [59]

Mechanosensing [58]

Ni nanowire

10 ~ 200 nm


Controlled cell growth (adhesion, separation, positioning) [60],[61]

Structure (aligned, random)

Magnetic property

Au nanowire

3 ~ 100 nm


Controlled cell growth (adhesion, differentiation) [63]

Surface functionalization

Si nanowire

3 ~ 500 nm


Mechanosensing [10]

Electrical sensor [12],[43],[44]

Structure (aligned, random, vertical)

Intracellular delivery [42]

Surface functionalization

In this review, we discuss the cell engineering with solid substrates based on synthetic nanowires/nanotubes, especially polymer nanofibers, carbon based nanostructures and inorganic nanowires. The cellular adhesion, proliferation and differentiation on these substrates and various other applications will be discussed.

2 Review

2.1 Polymer nanofiber-based substrates

A polymer nanofiber is a one-dimensional nanostructure which is comprised of synthetic small molecules typically connected by covalent chemical bonds. The most important and distinguished property of polymer nanofibers compared to other synthetic nanowires is biodegradability. Taking an advantage of this property, polymer nanofibers can be utilized as an implantable substrate for various applications such as tissue regeneration, local treatment of disease, and drug delivery. Furthermore, polymer nanofibers can be functionalized with various biomaterials such as ECM molecules, ECM analogs and growth factors to enhance cellular functionality, and, thus, it has a great potential in biological and biomedical applications.

2.1.1 Effect on cell adhesion

To mimic natural microenvironments for the cell control, various artificial and nanometer-scale structures with different nanotopography have been developed by many groups. For example, fibrous nanostructures can structurally and functionally mimic ECM in biological systems, and they can regulate cell responses. Several groups showed that the proliferation, migration, alignment and gene expression of cells were affected by the alignment and the dimension of nanofibers in contact with cells (Figure 2 (A-H)).
Figure 2

Polymer nanofibers for controlled cell growth. Scanning electron microscopy (SEM) images of (A) aligned PLLA nanofibers and (B) randomly-distributed PLLA nanofibers (reproduced from ref. 14 with permission, © Elsevier). SEM images of PANi-gelatin blend nanofibers with its averaged diameters of (C) 803 nm and (D) 61 nm. (reproduced from ref. 16 with permission, © Elsevier). Immunofluorescence images of neurofilaments (green) in NSCs (E) on aligned PLLA nanofibers and (F) on randomly-distributed PLLA nanofibers (reproduced from ref. 14 with permission, © Elsevier). Immunofluorescence images of actin filaments (red) and nuceli (blue) in myoblasts on the nanofibers with its averaged diameters of (G) 803 nm and (H) 61 nm (reproduced from ref. 16 with permission, © Elsevier).

Patel et al. investigated the combined effects of aligned polymer nanofibers and bioactive factors on cells [13]. Polymer nanofibers were functionalized with laminin and basic fibroblast growth factor (bFGF) to imitate native ECM fibrils. In this research, aligned polymer nanofibers induced longer neurite outgrowth and faster skin cell migration compared with randomly-oriented polymer nanofibers. The cells were elongated, and they migrated along the direction of polymer nanofibers. In addition, growth factors attached to aligned nanofibers were found to be more effective than those in solution on neurite outgrowth.

Yang et al. also examined the effect of nanofiber alignment on the neurite outgrowth of neural stem cells (NSCs) [14]. The aligned nanofibers supported the NSC culture, and they improved the neurite outgrowth (Figure 2 (E, F)). They also found that microscale polymer fibers have no significant effect on the neurite length. Baker et al. showed that the mechanical properties such as stiffness and elastic modulus of polymer nanofibers based cell-laden constructs depend on the alignment of polymers but not on cell type [15]. Meniscal fibrochondrocytes (MFCs) and mesenchymal stem cells (MSCs) were tested on poly (ε-caprolactone) (PCL) polymer nanofibers. The tensile properties of aligned polymer nanofiber based cell-laden constructs were higher than those of randomly distributed one, whereas both cell-laden constructs were comparable in amount of total DNA and produced ECMs.

The diameter of polymer nanofibers is also an important factor affecting cell adhesion. Li et al.[16] used polyaniline (PANi) and gelatin mixed polymer with different volume ratio. They found that the diameter of PANi-gelatine polymer nanofibers decreased from 803 ± 121 nm to 61 ± 13 nm with the decrease of the volume ratio of gelatin (Figure 2 (C, D)). The H9c2 rat cardiac myoblasts cultured on randomly distributed polymer fibers showed no significant difference in proliferation, but their morphology varied with the diameter of polymer nanofibers. Cells on thicker nanofibers showed a large number of pseudo-filopodia attachment to nanofibers (Figure 2 (G)), while cells on thinner nanofibers spread randomly just as those on glass surface (Figure 2 (H)).

2.1.2 Effect on cell differentiation

Cell differentiation is the process in which a progenitor cell or a stem cell becomes a more specified cell such as a bone cell, a neural cell, a liver cell, etc. There are soluble (e.g. growth factors, cytokines) and insoluble (e.g. ECM matrix, physical environments) factors which can affect the cell differentiation. Polymer nanofibers have shown the capability of supporting various stem cell differentiations, and they can even enhance the differentiation of the stem cells compared with a conventional scaffold.

Li et al. investigated the in vitro chondrogenic differentiation of MSCs on a PCL nanofiber-based scaffold in the presence of the transforming growth factor, TGF-ß1 [17]. Cell proliferation on polymer nanofibers was similar to that in a cell pellet culture which is a widely used cell culture system. However, the contents of sulfated glycosaminoglycan (sGAG) as a chondrogenic differentiation marker on polymer nanofibers was higher than that in a cell pellet culture. It indicates that the PCL nanofiber substrate supports a chondrogenic differentiation. MSCs were differentiated into osteoblasts on PCL nanofiber based scaffold in osteogenic differentiation medium as shown by Yoshimoto et al.[18] Cells migrated inside the polymer nanofiber-based scaffolds and produced an ECM of collagen after 1 week. MSCs on PCL nanofibers were also induced to differentiate along adipogenic, chondrogenic and osteogenic lineages in specific differentiation media [19]. Not only PCL but also poly (D,L-lactide-co-glycolide) (PLGA) and poly (L-lactic acid) (PLLA) support cell differentiation. Xin et al. reported hMSC on PLGA retained their phenotype and differentiated into chondrogenic and osteogenic cells in differentiation media [20].

Smith et al. examined the effect of nanofibrous scaffolds on osteogenic differentiation [21]. They prepared polymer nanofiber-based substrates in 2-D and 3-D formation. The nanofibrous structures in 2-D and 3-D enhanced the osteogenic differentiation of human embryonic stem cell (hESC)-derived osteogenic progenitor cells compared to the scaffolds without nanofibers.

The diameter of polymer nanofibers affects not only cell adhesion but also cell differentiation. Polyethersulfone (PES) nanofiber meshes with different diameter regulate proliferation and differentiation of rat neural stem cells (rNSCs) [22]. They used laminin-coated PES with diameters of 238 ± 45 nm, 749 ± 153 nm and 1452 ± 312 nm. As the diameter of polymer nanofibers decreases, cells were spread more on the nanofibers. rNSCs on 238 nm nanofiber mesh were spread on the nanofiber matrix, and they were assumed cell morphology of glial lineage. On the contrary, rNSCs on 749 nm nanofiber mesh adhered onto a single fiber, and they were elongated along a fiber axis. Those cells preferentially differentiated into neuronal lineage. However, both of cells on polymer nanofiber-based substrates showed the higher-level expression of the differentiation markers than those on a flat substrate.

Researchers also investigated the synergistic effect of polymer blends. Ku et al. invesgated the synergic effects of PCL and PANi blended nanofiber alignment on myoblast differentiations [23]. The differentiation of myoblasts on blended nanofibers was affacted by the PANi concentration. Kim et al. used commercial polymers to fabricate suitable biomaterial scaffold for the cell growth [24]. The modified PCL nanofibers incoporated within poly (ethylene oxide) (PEO) showed a good biocompatibility.

These results show that the polymer nanofiber can support multi-lineage differentiation capability of stem cells, and it is a good candidate for a scaffold in tissue regeneration or stem cell theraphy.

2.2 Carbon-based nanotubes/nanofibers

Carbon nanomaterials including carbon nanotubes (CNTs) and carbon nanofibers (CNFs) exhibit excellent mechanical and electrical properties. They have been explored in many biological applications such as bioelectronics, tissue engineering, cellular imaging and therapeutics [9],[25]. The carbon nanomaterials can be advantageous for cell control because they do not emit ions and have a chemically-stable surface.

2.2.1 Carbon nanotubes

A CNT is a rolled-up graphene which is carbon atoms arranged in a planar honeycomb lattice. CNTs can be classified into single-walled CNT (swCNT) and multi-walled CNT (mwCNT) depending on the number of rolled-up graphene layers. Generally, the diameter of swCNT is about 1 ~ 2 nm, and that of mwCNT varies from 2 nm to over 100 nm (Table 1). A CNT is mechanically strong and easy to be functionalized. The electrical and optical properties of CNTs can be used for various applicaions such as ultrasensitive biosensors. We review the recent applications of CNT-based substrates in controlling cell behaviors.

Nanoscale surface roughness of CNT-based substrates can deform cell membrane and hinder the motion of vesicles in cells. Zhang et al. reported that the areal coverage of vesicle motion was reduced in cells grown on a CNT layer, which was observed by total internal reflection fluorescence microscopy (Figure 3 (A)) [26]. Cellot et al. observed the improved postsynaptic current response of the neurons on CNTs [27]. The intimate contact between cell membranes and CNTs provided a close electrical coupling of the neurons and CNTs, which could directly stimulate neural activities (Figure 3 (B)). Furthermore, the spinal cord explants interfaced to CNT scaffolds for long-term period increased the number and length of neuronal fiber outgrowing spinal segments. This study also showed that CNT scaffolds augmented synaptic response in neurons located as far as 5 cell layers from the cell-substrate interactions.
Figure 3

CNT-based substrates for controlling and monitoring cell behaviors. (A) An immunofluorescence image of secretory vesicles inside a cell on a CNT-based substrate with a schematic diagram (reproduced from ref. 26 with permission, © Wiley-VCH). (B) The computed waveforms of the average postsynaptic currents from the neurons on a CNT-based substrate (reproduced from ref. 27 with permission, © Nature Publishing Group). (C) SEM images of a fibroblast (white arrows) cultured on a 3-D CNT structure (reproduced from ref. 32 with permission, © American Chemical Society). (D) SEM images of neurons on positively and negatively charged mwCNTs (reproduced from ref. 33 with permission, © American Chemical Society).

Patterned CNTs on substrates can control the shapes or orientiations of cells. Park et al. succeeded in aligning hMSCs along the patterned CNTs [28]. In this work, CNTs were selectively assembled on the substrate using the pre-patterned hydrophobic SAM molecules. The selective binding of ECM proteins (e.g. fibronectin) onto CNT regions could lead the hMSCs to grow along the CNT pattern. In a similar way, Jang et al. showed highly directional growth of neurites along the line-shape CNT patterns after 14 days of rat hippocampal neuron culture, which was attributed to the higher density adsorption of poly-L-lysine on the CNT patterns [29].

Previously, proteins have been known nonspecifically adsorbed well on sidewall of CNTs. Shim et al. demonstrated that the high affinity of proteins on CNTs could be attributed to the hydrophobic nature of CNTs or the pi-pi bonding between CNTs and proteins [30]. The adsorbed proteins mediated the interaction between cells and CNTs for a improved adhesion.

Aligned CNTs on substrates are useful in accelerating cell migration which is important in regeneration medicine. Galvan-garcia et al. assembled highly oriented mwCNT sheets and yarns, and they observed the directed cell growth along the CNTs [31]. In this work, the migration of fibroblasts on CNT sheets was enhanced, and the cell proliferation speed on the CNT sheets was comparable to that on glass. They also observed the directed neuronal growth along the CNT yarns, closely following the surface topography of the substrate.

A 3-D structure of CNT-film networks was explored for tissue engineering. Correa-Duarte et al. transformed a vertically-aligned structure of mwCNTs to a regular 3-D sieve structure by using chemically induced capillary forces (Figure 3 (C)) [32]. They successfully demonstrated that the controlled growth of a mouse fibroblast cell line (L929) in this 3-D CNT structure.

Surface functionalized CNTs provide great opportunities in controlling cell growth. Hu et al. reported that chemically modified CNTs affected the outgrowth and branching patterns of neurons [33]. The results showed that the positive charges induced more numerous growth cones, longer average neurite length and more neurite branching than the groups with neutral and negative charges (Figure 3 (D)). Zanello et al. cultured osteoblast (ROS 17/2.8) cells on the CNTs with various functional groups [34]. They found the highest cell growth on electrically-neutral swCNTs (as-produced-swCNT and swCNT-PEG). On the other hand, the lowest cell growth was observed on CNTs with charged groups (swCNT-COOH and swCNT-poly (m-aminobenzene sulfonic acid)).

CNTs can be used to transmit electrical stimulation to neural cells. Wang et al. developed a prototype of neural interface using vertically aligned mwCNT pillars [35]. The neurons were grown and differentiated on the hydrophilic functionalized CNT microelectrodes, and they were repeatedly excited with charge-unbalanced stimulation protocols. In this study, the CNT electrodes operated predominantly with capacitive currents without faradic reactions, which were considered ideal for neural stimulations.

CNTs were also explored to control cell differentiation. Tay et al. cultured hMSCs on a thin layer of carboxylic functionalized swCNTs with a vertical height of less than 100 nm [36]. In this report, they showed that the neurogenic genes were increased while osteogenic genes remained at a nominal level. This result suggests that CNT nano-roughness alone was sufficient to modulate the early stage of stem cell lineage commitment without the aid of induction media.

Some researchers performed experimental studies to reveal the mechanisms for the different differentiation behaviors of cells on CNTs. Namgung et al. investigated the enhanced differentiation of hMSCs on the aligned CNT networks [37]. They found that up-regulaed gene expressions of hMSCs related to the mechanotransduction pathways. These results supported that the high cytoskeletal tension of hMSCs could promote the differentiation of cells. Chen et al. suggested that the concentrated human bone marrow mesenchymal stem cells (hBMMSCs) following the carboxylated mwCNTs can up-regulate the secretion of growth factors [38].

2.2.2 Carbon nanofibers

Carbon nanofibers (CNFs) are graphene layers arranged as stacked cones, cups or plates, and their diameter ranges from 3.5 nm to 500 nm (Table 1) [9]. CNFs have been also explored widely in tissue engineering with the combination of polymers.

The topographical effects of CNFs were investigated in cells. McKenzie et al. prepared a CNF and polycarbonate urethane (PCU) composite substrate with different diameters of CNFs ranging from 60 nm to 200 nm [39]. They found that astrocytes preferentially adhered and proliferated on CNFs with the largest diameter. Price et al. demonstrated that this CNF-PCU substrates promoted the adhesion of osteoblasts, but the adhesions of smooth muscle cells, fibroblasts, and chondrocytes were not influenced [40].

Khang et al. examined osteoblast adhesion on microscale CNF patterns (30-μm-width line) on polymer substrates [41]. The patterns of CNFs on PCU substrate were prepared using an imprinting method. Osteoblasts selectively adhered and aligned on CNF patterns on PCU. The greater attractive forces between fibronectin and CNF (compared with PCU) measured by an atomic force microscope gave a plausible explanation for the selective cell adhesion.

2.3 Inorganic nanowires/nanotubes

Inorganic nanowires/nanotubes have been commonly exploited as effective tools for controlling cell behaviors by delivering biomolecules into the cells [42] and sensing intra/extracellular signals [43],[44]. In addition, inorganic nanowires/nanotubes based substrates are utilized as platforms to investigate the effect of nanoscale substrate topography and size-dependent cellular responses [45]–[47]. Furthermore, inorganic nanowires/nanotubes have been also utilized for various other cellular applications such as controlling cell position, measuring cellular forces or sensing cellular activities. Inorganic nanowires/nanotubes could be synthesized with a variety of materials including titanium oxide (TiO2), zinc oxide (ZnO), silicon (Si), etc. The synthesis methods include CVD [48],[49], anodization [50], electrochemical deposition [51] and solvothermal growth [52]. Inorganic nanowires/nanotubes are rather easy to adjust their nanoscale surface topology and chemical properties for the control of cell behaviors.

2.3.1 Titanium oxide nanotubes

The interaction between cells and titanium oxide substrates has been extensively investigated for clinical implant applications. Recent studies showed that the nanoscale modulation of TiO2 surface topography enhanced the efficiency in implantation. In this study, vertically-grown TiO2 nanotubes have been used as an effective scaffold to provide various nanoscale geometries, because the diameter of TiO2 nanotubes is easily controlled in the synthesis process.

Park et al. demonstrated responses of rat MSCs on vertically-oriented and highly-ordered TiO2 nanotubes. TiO2 nanotubes were fabricated on titanium surface by the anodization process, and the diameter of TiO2 nanotubes were varied from 15 nm to 100 nm by controlling the applied voltage (Figure 4 (A)). They showed significantly-enhanced cellular activities such as adhesion, proliferation and differentiation on 15 nm TiO2 nanotubes compared to 70 nm-100 nm TiO2 nanotubes, which was attributed to the accelerated formation of integrin clustering and focal contact [45]. In other work, the similar results of the enhanced cellular activities on 15 nm TiO2 nanotubes were shown with hematopoietic stem cells (HSCs) (Figure 4 (B) and (C)) [46].
Figure 4

TiO 2 nanotubes for controlled cell growth. (A) SEM images of vertically-aligned TiO2 nanotubes with diameters of 15 nm and 100 nm. Scale bars are 200 nm. (B) Immunofluorescence images of αVβ3-integrins (red) and nuclei (blue) in HSCs cultured on TiO2 nanotubes. Scale bars are 200 μm. (C) SEM images of filopodia formation in HSCs on TiO2 nanotubes. Scale bars are 3 μm (reproduced from ref. 46 with permission, © Willey-VCH).

They continued experiments with various types of cells to address the dominant factors determining cell fates on TiO2 nanotubular enviroment [47]. Three different types of cells (endothelial cell line mlEND, hMSCs and human cord blood endothelial progenitor cells) related to blood vessel formation were studied with respect to the diameter, the crystalline structure and the chemical composition of TiO2 nanotubes. As the diameter of TiO2 nanotubes decreased, the cell adhesion and proliferation were enhanced regardless of the cell type. The crystalline structure and the chemical composition of TiO2 nanotubes did not affect significantly on cell behaviors, which strongly suggests that the nanotopography should be a dominant factor for cell growth.

However, the results from Oh et al. were in conflict with previous experiments [50]. They observed that the differentiation of hMSCs into osteoblast-like cells was enhanced on TiO2 nanotubes with larger diameters (70 nm to 100 nm) rather than smaller diameters (30 nm to 50 nm) in the absence of osteogenic inducing factors. These findings suggest that finely-tuned nanotopography of TiO2 nanotubes could determine the cell fate, even though there are still controversies regarding the optimal diameter of TiO2 nanotubes for the enhanced cell adhesion, proliferation and differentiation.

2.3.2 Zinc oxide nanowires

Zinc oxide nanowires (ZnO NWs) are also attractive nanostructures due to their semiconducting and piezoelectric properties, and they have been utilized for biosensors [53] and other biomedical applications [54]. The cell adhesion and proliferation on ZnO-based nanostructures have been also demonstrated. Lee et al. explored the cell adhesion and growth on vertically-grown ZnO NWs with NIH3T3 fibroblasts, umbilical vein endothelial cells and capillary endothelial cells (Figure 5 (A)) [55]. In this case, the ZnO NWs were hydrothermally grown on the uniformly distributed ZnO nano-seeds. ZnO NWs are approximately 50 nm in diameter and 500 nm in height. The cells on ZnO NWs showed weaker adhesion and lower viability than cells on a flat ZnO substrate. The authors attributed the poor adhesion and proliferation of cells on the vertically grown nanowires to the hindrance in focal adhesion formation. Simply speaking, there was not enough space for the integrin clustering on ZnO NWs, which induced poor cell adhesion and proliferation. Zaveri et al. also reported similar results on ZnO NWs with macrophage cells [56]. In addition, in this work, the cytotoxic effects of solubilized ZnO NWs were additionally revealed.
Figure 5

Various inorganic nanowires for controlling and monitoring cell behaviors. (A) A SEM image of NIH3T3 fibroblasts on ZnO NWs with a poor adhesion compared to the flat ZnO surface (reproduced from ref. 55 with permission, © Elsevier). (B) A SEM image of MC3T3-E1 osteoblasts grown on ZnO nanoflowers with an enhanced adhesion compared to the flat ZnO surface. Lamellipodia and filopodia were indicated with pink and red arrowheads, respectively (reproduced from ref. 57 with permission, © Wiley-VCH). (C) Neurons grown on vertically-grown GaP NWs (reproduced from ref. 59 with permission, © American Chemical Society). (D) The forces of a neural growth cone measured with the four GaP NWs (circles using the same color coding in the inset image). The black curve corresponds to the noise obtained by measuring the deflection of a nanowire that was not in contact with a cell (the white circle in inset image). The inset image shows neural growth cone on vertically-ordered GaP NW arrays. A scale bar is 1 μm (reproduced from ref. 58 with permission, © American Chemical Society). (E) An optical micrograph image of the cells internalized by Ni NWs. Ni NWs transported by an external magnetic field to the gap between the ferromagnetic electrode and the gold electrode (reproduced from ref. 62 with permission, © Springer). (F) Phase contrast images of differentiated stem cells on a flat RGD-treated gold surface (left) and on RGD-treated Au NWs (right). Oil red O staining was used for visualizing adipogenic differentiation (reproduced from ref. 63 with permission, © Royal Society of Chemistry).

On the contrary, it was reported that the enhanced cell adhesion, proliferation and differentiation on ZnO nanoflowers (Figure 5 (B)) [57]. In this work, the ZnO nanoflowers were also grown by the hydrothermal methods on the micro-patterned ZnO surface. The nanoflowers were comprised of ZnO NWs with 200 ~ 300 nm in diameter and 3 ~ 4 μm in length. In this platform, osteoblasts on ZnO nanoflowers showed stronger adhesion, more DNA content and higher ALP activity than those on the flat ZnO surface. Furthermore, ZnO nanoflowers were tightly osseointegrated with the regenerated bones in the calvarial bone defects of Sprague Dawley rats. The results were attributed to the enhanced formation of lamellipodia, filopodia, and F-actin filaments on the surface of ZnO nanoflowers.

2.3.3 Other inorganic nanowires

The control of cell adhesion and viability has been also demonstrated on various other nanowires. The effects depend on the physical and chemical properties of nanowires. Of interest, the unique properties of each nanowire allow additional cellular applications. For example, dissociated sensory neurons cultured on vertically-grown epitaxial gallium phosphide nanowires (GaP NWs) showed a higher viability than planar gallium phosphide substrates (Figure 5 (C)) [58]. Interestingly, in other work, GaP NWs were utilized to measure cellular forces by analyzing the bending of GaP NWs (Figure 5 (D)) [59]. The rigidity, the high aspect ratio, and the nanoascale dimension of GaP NWs allow spatially-resolved and sensitive measurements of cellular forces.

Johansson et al. investigated the effect of nickel nanowires (Ni NWs) on L929 mouse fibroblasts and dissociated dorsal root ganglia (DRG) neurons [60]. They synthesized Ni NWs by the alumina template based electro-deposition method, which were 200 nm in diameter and 40 μm in length. They aligned Ni NWs using their magnetic property, and the cells were grown over the aligned Ni NWs. They showed that the cells displayed the contact guidance along the aligned Ni NWs. In other works, the magnetic properties of Ni NWs were utilized for the cell separation [61] or the cell positioning (Figure 5 (E)) [62].

The adhesion and the differentiation of MSCs on gold nanowires (Au NWs) were also demonstrated by Luo et al.[63]. The well-known chemistry on Au surface allowed functionalization of Au NWs with self-assembled monolayers containing diverse functional groups. In this work, Au NWs were functionalized with a cell adhesive peptide (RGD- ONH2). As a result, MSCs on the functionalized Au NWs showed more fillopodia extensions compared to those on flat gold surfaces functionalized with the same RGD peptides. Moreover, in the process of adipogenic differentiation, the enhanced differentiation was observed on Au NWs (Figure 5 (F)).

Al/Al2O3 core/shell nanowires and patterned Si nanopillars were also studied to control the cellular responses such as cell adhesion, growth and proliferation. Lee et al. patterned periodic structures of Al/Al2O3 core/shell nanowires, and showed that the periodic patterns lead to the alignment of glial cells and dorsal root ganglia axons [64]. Similar to the Al/Al2O3 nanowires experiment, Bucaro et al. showed that Si nanopillars could control the cell polarization and alignment by controlling the radius, height and interpillar spacing of Si nanopillars [65].

3 Conclusions

In summary, we discussed various synthetic nanowires/nanotubes utilized in cell engineering. Since it is easy to control the diameter, mechanical property and surface chemistry of synthetic nanowires/nanotubes, they can be utilized to create active microenvironments to control cell behaviors. Moreover, the nanowire/nanotube-based functional devices can be used as intercellular drug delivery system and ultrasensitive biosensors for real-time detection of cell activities. Although their cytotoxicity is still under debate and requires more systematic studies, synthetic nanowires/nanotubes have great potentials not only in fundamental research but also in clinical applications such as drug screening devices, organ-on-a chips and medical tissue grafts. With the advances in nanomaterials and manipulating technique, the synthetic nanowire/nanotube based system should provide enormous opportunities in biomedical applications.



SH acknowledges the support from the BioNano Health Guard Research Center (H-GUARD_2013M3A6B2078961) and the NRF grant (No. 2013–007874).

Authors’ Affiliations

Department of Electrical and Biological Physics, Kwangwoon University
Center for Functional Connectomics, Korea Institute of Science and Technology
Department of Electrical and Computer Engineering, University of Minnesota
Department of Biophysics and Chemical Biology, Seoul National University
Department of Physics and Astronomy, and Institute of Applied Physics, Seoul National University


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