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Exp Neurobiol 2011; 20(2): 110-115
Published online June 30, 2011
© The Korean Society for Brain and Neural Sciences
Sang Jin Yoo1, Jongmin Kim2, Chang-Soo Lee2 and Yoonkey Nam1*
1Department of Bio and Brain Engineering, KAIST, Daejeon 305-701, 2Department of Chemical Engineering, Chungnam National University, Daejeon 305-764, Korea
Correspondence to: *To whom correspondence should be addressed.
TEL: 82-42-350-4362, FAX: 82-42-350-4310
Conventional method of cell culture studies has been performed on two-dimensional substrates. Recently, three-dimensional (3D) cell culture platforms have been a subject of interest as cells in 3D has significant differences in cell differentiation and behavior. Here we report a novel approach of 3D cell culture using a nylon micro mesh (NMM) as a cell culture scaffold. NMM is commonly used in cell culture laboratory, which eliminates the requirement of special technicality for biological laboratories. Furthermore, it is made of a micro-meter thick nylon fibers, which was adequate to engineer in cellular scales. We demonstrate the feasibility of the NMM as a 3D scaffold using E18 rat hippocampal neurons. NMM could be coated with cell adhesive coatings (polylysine or polyelectrolyte) and neurons showed good viability. Cells were also encapsulated in an agarose hydrogel and cultured in 3D using NMM. In addition, the 3D pattern of NMM could be used as a guidance cue for neurite outgrowth. The flexible and elastic properties of NMMs made it easier to handle the scaffold and also readily applicable for large-scale tissue engineering applications.
Keywords: 3D culture, scaffold, micro mesh, neuronal culture, 3D cell patterning
Conventional method of cell culture studies has been performed on 2-dimensional (2D) surfaces such as glass, well plate and Petri dishes. Theses 2D cell culture platforms are widely used because of the easy of handling, its convenience and bio-compatibility. Although the understanding of basic biology has been improved with these advantages of 2D systems, many scientists give careful attention to 3-dimensional (3D) cell culture system due to the limitation of 2D environment (Lund et al., 2009).
Two-dimensional substrates have a limitation in the replication of 3D cellular environments and the absence of 3D factors in cellular developments could limit the biological outcome in the culture (Zhang, 2004). Moreover, cells cultured on the 2D substrate have to adapt to rigid and flat surfaces while natural
There have been active pursuits in developing new biomaterials for 3D cell culture scaffolds (Shin and Mikos, 2003). For example, polymer based biomaterials (Cheung et al., 2007), protein based biomaterials (Stegemann et al., 2007) and nanofiber (Yoshimoto et al., 2003) have been utilized as a 3D cell culture scaffold. And with these biomaterials, there have been many applications of 3D cell culture scaffolds (Dutta and Dutta, 2009). For example, there were clinical trials that artificial tissues which were made by 3D scaffolds used for regenerative medicine (Karageorgiou and Kaplan, 2005) and
Here we propose a nylon micro-mesh (NMM) as a new 3D cell culture scaffold based on its mechanical flexibility, biocompatibility, and practicality. And we show that NMM is suitable for 3D cell culture scaffold and has some potential for 3D tissue engineering applications.
Three kinds of Nylon micro meshs (NMMs) which had 20, 10, 8 µm pore size were purchased from Spectrum Laboratories (Spectrum, CA, USA). And NMMs with 40 µm pores were taken from a cell strainer (BD Falcon, NJ, USA).
NMMs were sonicated with acetone, isopropylalcohol (IPA) and DI water for 5min per each and dried by air stream. NMMs were coated with Poly-D-Lysine (PDL, Sigma, MO, USA) by soaking the NMMs in PDL solution (0.1 mg/ml in borate buffer, pH 8.5) at 37℃. After 6 hour, PDL solution was aspirated and NMMs were immersed in 70% ethanol for sterilization. After the sterilization, NMMs were rinsed with DI water. The NMMs were finally dried in clean-bench or incubator.
Polyelectrolyte multilayer (PEL) were coated using layer-by-layer method. The cleaned NMMs were immerged in the solution of Poly allylamine hydrochloride (PAH, 20 mM, pH 9.0, Sigma, MO, USA) for 1 min, followed by five times washing with DI water. The PAH coated NMMs were immerged in the solution of Poly sodium 4-stlrensulfonate (PSS, 60 mM, pH 9.0, Sigma, MO, USA) for 1 min, followed by five times washing with DI water. The process of PEL coating were repeated ten times and finished with the PAH coating. NMMs were sterilized by UV for 5 min and dried in clean-bench or incubator.
Agarose gel (gelling range: 36~39℃, Amresco Inc., Ohio, USA) was dissolved in 100℃ DI water and 0.7% (w/v) agarose hydrogel was formed. After cooling the agarose gel to 36℃, cell suspension was mixed with the agarose and plated on PDL coated NMMs.
Hippocampus tissues were dissected from E18 Sprague/Dawley rat embryo. The tissues were washed three times with Hank's Balanced Salt Solution (HBSS) and mechanically dissociated using 1 ml pipette tips. Cell suspensions were centrifuged for 3 min at 1,000 rpm and the cell pellets were suspended again in plating medium which was composed of serum free Neurobasal/B27 (Invitrogen, CA), 12.5 µM L glutamate (sigma, MO), 2 mM L glutamine (Gibco) and 1% penicillin streptomysin (invtrogen, CA). Finally, the cell suspend plated onto the coated NMMs at the density of 200 to 300 cells/mm2. Cultures were maintained in an incubator (5% CO2, 37℃). After three days from cell plating, half of the medium was replaced with fresh culture medium without L glutamine every 3 days.
Neurons were stained by Live-Dead viability/cytotoxicity kit (Invitrogen, CA, USA). 10 µl of ethidium homodimer and 2.5 µl calcein acetocymethyl ester were mixed in 5 ml of phosphate buffered saline (PBS). 200 µl of the dye solution was added in 1 ml sample and covered with aluminum foil to protect the dye from photobleaching. After the incubation (5% CO2, 37℃) of the sample for 20 min, the solution in the sample was removed and NMMs washed with PBS.
Appropriate mechanical properties of 3D scaffold are important in 3D tissue engineering (Lee et al., 2008). First, flexibility is required to maintain the shape of scaffold and handling. Second, micro and nano-scale structural architecture is desirable to mimic
Fig. 1A shows the compliance of the NMM to the mechanical bending. It was also easy to handle by hand for forceps. Fig. 1 also shows the ordered structures of NMM in micrometer scales. The thickness of the individual nylon fiber was 30 or 35 µm and the thickness of NMM was 75 µm, 45 µm, 55 µm, 60 µm, respectively (Fig. 1B~E). NMMs have many regular pores with the pore diameters of 8 µm, 10 µm, 20 µm, and 40 µm (Fig. 1F~I). These properties made NMMs suitable for 3D cell culture scaffolds.
Biocompatibility of materials is a crucial parameter, since it can be decisive criteria as a culture scaffold. Most of the reported scaffolds were composed of ECM molecules (Badylak, 2002), or had bioactive molecules to modulate cellular activities (Zhu, 2010), or they had controllability in chemicals (Yildirim et al., 2010).
Fig. 2 shows the surface modification of NMMs using positively charged polymers. We coated NMMs with either poly-D-lysine (PDL) or polyelectrolyte multilayer (PEL). PDL is one of the most common polymer used as a cell adhesive coating material. PEL was used to modify the NMM surface with much denser positive charge layers through layer-by-layer coating technique, which turned out to be more efficient in terms of reproducibility and reliability.
In order to investigate the effect of chemical controllability and viability of cells on the NMM, we prepared different pore size of NMMs coated by PDL and PEL and cell plate. Fig. 3 shows excellent cell viability at 9 DIV. Neurons tend to grow on and in-between the micro-fibers and pores were be filled with neuronal growth.
Entrapment of cells in three dimensional space has a special meaning that it provide distinct differences in cell morphogenesis, behavior, gene expression, differentiation from 2D environment (Holmes et al., 2000; Zaman et al., 2006). In other word, the recovered 3D environment cause different viability and functionality of cell.
Many of the studies used natural hydrogels or synthetic gel such as alginate (Pangas et al., 2003), collagen (Batorsky et al., 2005) and poly ethylene glycol (PEG) (Elisseeff et al., 1999) to entrap cells. We used agarose hydrogel which is a common material in biological laboratories for the cell entrapment (Fig. 2). Fig. 4 shows the neuronal growth in agarose hydrogels. Neurons were well dispersed in the gel, and neurites were formed and extended (Fig. 4B, E). They tend to get clustered in the gel after forming thick fiber bundles. As the gel was not functionalized to be cell adhesive, the clustering process was likely to occur in the matured neuronal cultures. However, neurons were still viable and maintained in 3D NMM scaffolds.
As NMMs had ordered structures in micrometer scales (Fig. 1), each nylon fiber can provide the topographical guidance cues to the growing neurites. Fig. 5A shows an example of the guided neurite outgrowth along the 3D mesh fibers. The fiber thickness was comparable to the size of soma and neurites followed the edge of the fibers. This is also shown in scanning electron micrograph in Fig. 5B. Fig. 5C shows more 'patterned' neurites on the mesh. Although the fiber itself was too thick to control thinner neurites, its edges clearly had an effect on neurite guidance.
In summary, we proposed NMMs as a simple but effective 3D cell culture scaffold. Unlike other 3D scaffold materials that requires expensive or special technicality, NMMs are an inexpensive material that is common biological laboratories. NMM had excellent mechanical and structural properties to support neuronal cell growth and gel based cell cultures. It was also chemically modifiable to convert the nylon surface into cell adhesive surfaces. Moreover, the micro-scale structural regularity could be potentially be applicable to 3D tissue engineering applications.