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Regulation of Epithelial-to-Mesenchymal Transition Using Biomimetic Fibrous Scaffolds Anitha Ravikrishnan, Tugba Ozdemir, Mohamed A Bah, Karen A Baskerville, S. Ismat Shah, Ayyappan K Rajasekaran, and Xinqiao Jia ACS Appl. Mater. Interfaces, Just Accepted Manuscript • DOI: 10.1021/acsami.6b05646 • Publication Date (Web): 20 Jun 2016 Downloaded from http://pubs.acs.org on June 22, 2016

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ACS Applied Materials & Interfaces

Regulation of Epithelial-to-Mesenchymal Transition Using Biomimetic Fibrous Scaffolds

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Anitha Ravikrishnan,1$ Tugba Ozdemir,1$ Mohamed Bah,1 Karen A. Baskerville,2 S. Ismat

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Shah,1,3 Ayyappan K. Rajasekaran,1,4,5 and Xinqiao Jia1,4,6*

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USA

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Department of Materials Science and Engineering, University of Delaware, Newark, DE 19716,

Department of Biology, Lincoln University, Lincoln University, PA 19352, USA Department of Physics and Astronomy, University of Delaware, Newark, DE 19716, USA Department of Biological Sciences, University of Delaware, Newark, DE, 19716, USA Therapy Architects, LLC, Helen F Graham Cancer Center, Newark, DE, 19718, USA Department of Biomedical Engineering, University of Delaware, Newark, DE 19716, USA

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These two authors contributed equally to this work.

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*To whom correspondence should be addressed: Xinqiao Jia, 201 DuPont Hall, Department of

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Materials Science and Engineering, University of Delaware, Newark, DE, 19716, USA. Phone:

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302-831-6553, Fax: 302-831-4545, E-mail: [email protected].

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Keywords: Fibrous Scaffolds; MDCK Cells; Fiber Diameter; Hepatocyte Growth Factor;

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Epithelial-to-Mesenchymal Transition; Phenotype.

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ACS Paragon Plus Environment


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Abstract.

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Epithelial-to-mesenchymal transition (EMT) is a well-studied biological process that takes

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place during embryogenesis, carcinogenesis and tissue fibrosis. During EMT, the polarized

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epithelial cells with a cuboidal architecture adopt an elongated fibroblast-like morphology. This

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process is accompanied by the expression of many EMT-specific molecular markers. While the

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molecular mechanism leading to EMT has been well established, the effects of matrix

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topography and microstructure have not been clearly elucidated. Synthetic scaffolds mimicking

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the mesh-like structure of the basement membrane with an average fiber diameter of 0.5 µm

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and 5 µm were produced via electrospinning of poly(-caprolactone) (PCL) and were used to

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test the significance of fiber diameter on EMT. Cell-adhesive peptide motifs were conjugated to

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the fiber surface to facilitate cell attachment. Madin-Darby Canine Kidney (MDCK) cells grown

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on these substrates showed distinct phenotypes. On 0.5 µm substrates, cells grew as compact

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colonies with an epithelial phenotype. On 5 µm scaffolds, cells were more individually dispersed

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and appeared more fibroblastic. Upon addition of hepatocyte growth factor (HGF), an EMT

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inducer, cells grown on the 0.5 µm scaffold underwent pronounced scattering, as evidenced by

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the alteration of cell morphology, localization of focal adhesion complex, weakening of cell-cell

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adhesion, and upregulation of mesenchymal markers. By contrast, HGF did not induce a

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pronounced scattering of MDCK cells cultured on the 5.0 µm scaffold. Collectively, our results

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show that the alteration of the fiber diameter of proteins found in the basement membrane may

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create enough disturbances in epithelial organization and scattering that might have important

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implications in disease progression.

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1. Introduction

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Epithelial to mesenchymal transition (EMT) is a complex biological process that takes

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place during tissue development and disease progression. During development, successive

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EMT events generate embryonic organs and tissues. In healthy adult epithelial tissues,

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polarized epithelial cells bonded to the basement membrane are held together through

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adherens junction complexes, consisting of F-actin, catenins and E-cadherin.1-3 Under

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pathological conditions, in response to EMT-inducing signals, the epithelial cells weaken their

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cell-cell adhesions and lose the apico-basal polarity as the EMT inducers suppress the genes

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encoding proteins involved in both adherens junctions and cell polarity.2,

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During EMT, cells

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also undergo cytoskeletal reorganization,5-6 adopt a more elongated cell morphology and

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become progressively more migratory and invasive.7-8 In chronic fibrosis, the transformed cells

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undergo abnormal remodeling of their extracellular matrix (ECM) and produce excessive

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proteins and proteoglycans,9 resulting in the thickening and scarring of the tissue. At the onset

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of carcinoma invasion, epithelial cells are released from the cell clusters into neighboring tissues

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with varying tissue structures, mechanical properties and dimensionality, spreading cancer to a

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distal organ.

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The basement membrane/extracellular matrix (ECM) composed mainly of fibrillar proteins,

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such as collagen and fibronectin, and amorphous fillers, such as glycosaminoglycans, provides

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structural support and contextual information to the resident cells, serving as a key regulator of

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cell functions. During EMT, the ECM undergoes drastic compositional, structural and

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mechanical changes to accommodate aberrant tissue growth.10-12 The ECM reorganization

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is associated with the alteration in the density and orientation of fibrillar proteins.16 The increase

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or decrease in fiber crosslinking not only affects the matrix stiffness but also alters the ligand

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density, thereby influencing cell migration.

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remodeled by the stromal cells to generate invasive pathways for cancer cell migration.18 By

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During cancer metastasis, the interstitial matrix is

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13-15



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contrast, increased deposition of fibrillar proteins prevents the normal wound healing process

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and results in tissue fibrosis 19-20.

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Paracrine effectors are potent inducers of EMT. Particularly, hepatocyte growth factor

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(HGF), a fibroblast-derived protein known as the scatter factor, affects the intercellular

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connections and mobility of normal epithelial cells, and thus might be involved in embryogenesis

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or wound healing. 21 Madin-Darby canine kidney (MDCK) epithelial cells grown in collagen gels

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in the presence of exogenous HGF form branching tubules, whereas cells grown in control gels

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without HGF or in fibroblast conditioned media with HGF antibody only develop into spherical

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cysts. 22 It is known that HGF binds a tyrosine kinase receptor c-Met proto-oncogene with high 23

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affinity to induce epithelial morphogenesis.

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dependent not only on the target cell type but also the environmental context and culture

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conditions. Although a large body of literature 24-26 reports the HGF-induced scattering or

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tubulogenesis by culturing MDCK cells on planar substrates or in collagen gels or Matrigel, the

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roles of the ECM topography on the initial clustering and HGF-induced scattering have not been

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elucidated.

Of note, the morphogenetic effects of HGF are

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To gain a fundamental understanding on how physical features of the ECM define cellular

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behaviors and alter cell phenotypes, a straightforward and reliable method for producing

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biomimetic fibrous scaffolds with controlled diameter and surface chemistry is needed.

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Electrospinning is a powerful technique for the fabrication of synthetic scaffolds that closely

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mimic the structure, morphology and mechanical properties of the natural ECM. 27-29 These

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micro/nano fibrous scaffolds, with the interconnected porous network and high surface to

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volume ratio, provide a favorable environment for cell attachment, migration and proliferation.30-

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32

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caprolactone) (PCL) 33 has been electrospun into fibrous scaffolds for various tissue engineering

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applications.34-36 Various surface modification methods have been applied to the PCL fibers to

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improve the hydrophilicity and to promote cell-scaffold interactions without compromising the

Owing to its biocompatibility, high molecular weight and semi-crystalline nature, poly(-

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bulk properties.

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scaffolds with varying fiber diameters to support the attachment, growth and differentiation of

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MDCK cells. Because integrin signaling is important in EMT, the amino acid sequence

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corresponding to integrin binding receptors at focal adhesion complexes

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the PCL scaffold. We further evaluated how the fiber diameter affects the HGF-induced cell

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scattering on the scaffold. Our results highlight the importance of the biophysical attributes of

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the cellular microenvironment on the fundamental aspects of EMT in tissue morphogenesis and

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wound healing.

In the current investigation, we assessed the ability of electrospun PCL

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was conjugated to

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2. Materials and Methods

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2.1. Chemicals and reagents.

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Poly(-caprolactone) (PCL, ~80 kDa), hexamethylenediamine (HMD) and ethylene-

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diaminetetraacetic acid (EDTA.4Na) were purchased from Sigma-Aldrich (St. Louis, MO).

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Organic solvents, including chloroform, N, N-dimethyl formamide (DMF), methylene chloride,

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dichloromethane

(DCM)

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sulfosuccinimidyl

4-(N-maleimidomethyl)

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obtained from Thermo-Fisher (Rockford, IL) and were used without further purification.

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Deionized water (DI H2O) was sourced from a NANOpure Diamond water purification system

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(Thermo Scientific, Barnstead, NH). Phosphate buffered saline (PBS) was purchased from

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Gibco (Life Technologies Carlsbad, CA). Monoclonal anti-vinculin antibody was purchased from

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Sigma-Aldrich (St. Louis, MO), monoclonal mouse anti-vimentin antibody was purchased from

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GenWay Biotech, Inc., (San Diego, CA) and purified mouse anti-E-cadherin antibody was

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purchased from BD Biosciences (San Diego, CA). Alexa 488, Alexa 647 and Alexa 488-

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conjugated goat anti-mouse or rabbit IgG, as well as Alexa 568-conjugated Phalloidin, were

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purchased from Molecular Probes (Eugene, OR). Recombinant human hepatocyte growth factor

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isopropanol,

as

well

as

difunctional

cyclohexane-1-carboxylate

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the


crosslinker,

(sulfo-SMCC),

were


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(HGF), DAPI, Syto 13 and propidium iodide (PI) were obtained from Invitrogen (Grand Island,

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NY). CellTrackerTM red was purchased from Life Technologies (Carlsbad, CA).

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2.2. Scaffold fabrication and modification

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2.2.1. Scaffold fabrication. Fibrous PCL scaffolds with varying fiber diameter were

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fabricated using different solvents and electrospinning parameters. To produce a nonwoven mat

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of uniform submicron fibers, PCL was dissolved in DCM/DMF (7:3, v/v) at a concentration of 12

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wt%. The solution was transferred to a 3 mL syringe capped with a 21G blunt ended needle

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(Becton Dickinson, Franklin Lakes, NJ). The syringe was suspended horizontally adjacent to a

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grounded aluminum collector plate at a fixed distance of 21 cm and a power supply was wired to

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the metal needle with an alligator clip to establish a constant electric potential of 12 kV. The

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PCL solution was spun at a flow rate of 1 mL/h using an automatic syringe pump (New Era

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Pump Systems, Farmingdale, NY). To produce micron-sized fibers, a 15 wt% PCL/chloroform

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solution was spun from a 16G needle at a flow rate of 1.5 mL/h with a needle-to-collector

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distance of 16 cm. The collected fiber mats, with an average thickness of 130 µm, were dried

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overnight under vacuum.

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2.2.2. Surface functionalization. A cell-adhesive peptide with a sequence of

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CGGWGRGDSPG (RGD-SH) was prepared on a PS3 peptide synthesizer (Protein

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Technologies Tucson, AZ) using the Rink Amide resin (EMD Millipore, Billerica, MA) following

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standard Fmoc solid phase peptide synthesis protocols, with the N-terminus was acetylated and

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the C-terminus amidated.

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with a Phenomenex® C18 preparative column and lyophilized to obtain dry powder. The HPLC

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traces of the purified peptide are shown in Fig. S1. The molecular weight of the purified peptide

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was analyzed by electrospray ionization mass spectrometry (ESI-MS, Fig. S2) (Thermo LCQ

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The crude peptide was purified using the Waters HPLC equipped

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LC-MS system with ion trap mass analyzer, San Jose, CA). ESI-MS m/z ([M+H]⁺): 1089.0

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(calculated), 1089.7 (found).

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PCL scaffolds were cut into circular disks of 10 mm diameter using an Acuderm punch

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(Fort Lauderdale, FL). Individual disks were immersed in an ethanol/water mixture (1/1, v/v)

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under gentle shaking for 2 h to remove any residual contaminants. Scaffolds were then allowed

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to react with hexamethylenediamine (HMD) in 2-propanol (10 wt%) at ambient temperature for

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24 h,

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scaffolds were then washed with PBS (0.1 M) containing 0.15 M NaCl at pH 7.2 three times (5

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min each). Next, the scaffolds were incubated with a sulfo-SMCC solution (4 mg/mL in PBS, pH

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7.4) at room temperature for 1 h. The sulfo-SMCC-treated scaffolds were washed three times

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with a PBS buffer containing 0.1 M EDTA at pH 7.0. Finally, the scaffold was incubated with

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RGD-SH at 0.2 mg/mL in PBS at 4 C overnight to immobilize the cell adhesive peptide.46

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Scaffolds were washed thoroughly with PBS to remove excess unbound peptides and dried

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under vacuum.

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and unreacted HMD was removed by a thorough wash with DI H2O. The HMD-treated

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2.3. Scaffold characterization

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2.3.1. Scanning electron microscopy (SEM). Scaffold morphology was characterized

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using a Hitachi S4700 Scanning Electron Microscope. Samples were mounted on aluminum

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stubs using carbon tape and were sputter coated with platinum using Leica EM ACE600. The

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average diameter and pore size of the fibrous scaffolds were analyzed using DiameterJ,

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ImageJ 48 software, respectively.

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and

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2.3.2. Contact angle analysis. For contact angle analysis, spun-cast films were used in

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place of the fibrous mats to eliminate topography related complications in data analysis and to

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unambiguously confirm the changes of surface chemistry. Specifically, PCL was spun cast from

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a 5 wt% chloroform solution onto a silicon wafer with a 300 nm-thick oxide layer, freshly clean

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using a Piranha solution. The as-spun films were annealed at 60 C for 1 h. The silicon wafer

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supported PCL film (3.6 µm thick, as determined by profilometry) was subjected to the same

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surface modifications described above for PCL fibers. Water contact angle was measured at

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room temperature using the sessile drop method on a Ramé-Hart contact angle Goniometer

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(Succasunna, NJ). A distilled water droplet was placed on five different regions of the test

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substrates and the measured angles were averaged.

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2.3.3. X-ray photoelectron spectroscopy (XPS). X-ray photoelectron spectroscopic

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(XPS) spectra of the spun-cast films, before and after various steps of surface modification,

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were recorded using Surface Science Instruments Model 301 ESCA with monochromatic Al

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Kα and Mg Kα X-rays dual source, with a resolution of 0.4 eV. The C 1s standard at 284.6 eV

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was used for the correction of the obtained spectra, in order to account for peak shifting due to

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charging. Data reported represents the chemical composition of the surface of the polymer film

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at a sampling depth of 3 to 10 nm, depending on the intensity of the emitted electron. The x-ray

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source is located perpendicular to the analyzer, while the sample is located 50 from the

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analyzer.

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2.3.4. Fourier transform infrared spectroscopy (FT-IR). A Fourier Transform Infrared

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Spectrometer (Nexus 670 FT-IR, Thermo Nicolet, Waltham, MA) was used to confirm the

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aminolysis on the surface of PCL films. Spun-cast films, before and after surface modification,

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were analyzed. The absorption spectra at the mid-infrared region (500 to 4000 wavenumbers)

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were recorded.

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2.3.5. Confocal microscopy. The as-spun fibers and the peptide modified fibers were

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imaged using an LSM880 Multiphoton Confocal Microscope (Zeiss). For confocal imaging of

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the as-spun scaffolds, the collected fibers were immersed in a PBS solution of CellTrackerTM

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Red (1:1000) for 30 min. Separately, a multi-photon confocal microscope, operated at 30% laser

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power, was used to confirm the peptide conjugation on PCL scaffolds based on tryptophan

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fluorescence. Briefly, virgin PCL scaffolds, RGD-conjugated PCL scaffolds and RGD-coated

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clean glass slides were imaged separately in order to get sample specific fluorescence emission

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spectra. All samples were excited at 280 nm with an argon laser source and the unfiltered

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emission spectra were collected. The fluorescence signal associated with tryptophan residue on

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RGD-modified PCL scaffolds was obtained by subtracting the background fluorescence from

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PCL.

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2.4. Cell culture

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Madin-Darby canine kidney (MDCK) NBL2 cells (ATCC, Manassas, VA) were cultured in

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Eagle's minimum essential medium (EMEM) (ATCC, Manassas, VA) supplemented with 10%

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fetal bovine serum (FBS) and 100 IU/mL penicillin/streptomycin in a humidified 37 C incubator

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maintained at 5% CO2 and 95% air. Cell culture media was changed every other day, and cells

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were routinely passaged using 0.25% (w/v) trypsin containing 0.02% EDTA. Prior to cell culture,

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the fibrous scaffolds were gently agitated in 70% ethanol overnight. After washing with fresh,

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serum free media, the scaffolds were exposed to germicidal UV light for 15 min, followed by a 3-

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h equilibration in cell culture media. MDCK cells were plated on the scaffold at a seeding density

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of 10,000 cells/scaffold and were incubated in media containing 0.5 % FBS for 2 h.

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Subsequently, the low serum media was replaced by EMEM containing 10% FBS. After 36-h

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incubation, the media was supplemented with HGF (50 ng/mL) and cells were cultured for an

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additional 12 h before individual constructs were collected and processed for immunostaining

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and confocal imaging. 9



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2.5. Biological characterization of cell-laden scaffolds

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2.5.1. Live/dead staining. MDCK cells were cultured on scaffolds of different fiber

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diameters in the presence or absence of HGF, as described above. After a total of 48 h of

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culture, the constructs were rinsed with PBS and incubated with a mixture of Syto13 (1:1000)

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and propidium iodide (1:2000) in PBS for 15 min to stain live and dead cells, respectively. After

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an additional PBS wash to remove the unbound staining reagents, the constructs were imaged

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using a Zeiss LSM 710 confocal microscope. Five different confocal images were taken per

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sample and the number of clustered cells is defined as a group of more than five cells in close

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proximity.49

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2.5.2. Immunofluorescence. MDCK cells were fixed using an ice-cold cytoskeleton

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stabilization buffer for 1 min, incubated in freshly prepared with 4% paraformaldehyde/PBS

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solution for 15 min, washed three times with PBS and finally incubated overnight in a

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permeabilization buffer (2% BSA, 0.1% Triton X-100). Focal adhesions and cell-cell contacts

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were detected via immunostaining for vinculin, vimentin and E-cadherin, respectively. To this

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end, constructs were first incubated with primary antibodies (prepared in permeabilization

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buffer), monoclonal mouse anti-vinculin, monoclonal mouse anti-vimentin and purified mouse

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anti-E-cadherin, respectively for 90 min. After a 3-min wash with PBS, samples were incubated

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with the secondary antibodies (1:200, in 2% BSA), Alexa 488, Alexa 647 and Alexa 488-

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conjugated goat anti-mouse IgG (1:100 in 2% BSA) for 45 min, respectively. After washing with

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copious PBS to remove unbound antibodies, the constructs were incubated with DAPI (1:5000)

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and Alexa-conjugated phalloidin (1: 1000) for 5 and 30 min, respectively to counter stain cell

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nuclei and F-actin. The stained constructs were placed in Nunc chambers (Thermo Scientific,

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Rockford, IL) for imaging using a Zeiss LSM880 Multiphoton Confocal Microscope.

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2.6. Statistical analysis

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All the quantitative data obtained were analyzed using one-way analysis of variance

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(ANOVA) to compare the means of different data sets within each experiment from at least

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three repeats. Errors were expressed as the standard error of the mean. A value of p

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