**2. Materials and methods**

#### **2.1. Materials**

Polycaprolactone pellets (PCL, average *Mn*45000), 1,6-hexanediamine (98%), glycidyl metha‐ crylate (GMA, >97%), 2-bromoisobutyrl bromide (BIBB, 98%), 2,2'-bipyridine (bpy, 98%), di‐ chloromethane (anhydrous, >99.8%), triethylamine (TEA, 98%), isopropyl alcohol, hexane (anhydrous, >95%), copper (I) bromide (CuBr, 99%), copper (II) bromide (CuBr2, 98%), and gelatin (Porcine skin, Type A) were obtained from Sigma-Aldrich Chemical Co. (St. Louis, MO, USA), and were used without further purification. GMA was passed through a silica gel column to remove the inhibitor, and stored under a nitrogen atmosphere at -4o C. All the other chemical reagents and solvents were used as received. Human Umbilical Vein Endothelial cells (HUVECs, ATCC CRL-1730TM) were purchased from American Type Culture Collection (Manassas, VA, USA). Cell culture medium (MCDB131), heparin and paraformaldehyde (4%, v/v) were obtained from Sigma-Aldrich Chemical Co. Medium supplements, such as Foetal Bovine Serum (FBS), penicillin, amphotericin, bovine brain extract, streptomycin, and Tryp‐ sin-EDTA (0.25%), were purchased from Life Technologies (Carlsbad, CA, USA). LIVE/ DEAD® cell viability assay reagent, AlamarBlueTM reagent, tissue thromboplastin (human brain extract), ellagic acid, and DAF-FM Diacetatewere obtained from Life Technologies. The P-selectin assay reagents were obtained from Serotec Co. (Kidlington, Oxford, UK).

#### **2.2. Aminolysis of PCL film substrates and immobilization of ATRP initiator**

tensively investigated as scaffolds for vascular tissue engineering applications [17-21]. However, the intrinsic hydrophobicity and poor cytocompatibility of PCL substrates lead to poor affinity for cell adhesion, thereby restricting their applications as blood-contacting de‐ vices. Consequently, surface modification of PCL is necessary to improve cell adhesion and proliferation. Functional polymer brushes containing reactive hydroxyl (-OH), carboxyl (- COOH) or amine (-NH2) groups have been successfully grafted onto the PCL surfaces using γ-ray irradiated, ozone or photo-induced polymerization grafting to introduce hydrophilici‐ ty [9,16,22-24]. These flexible reactive groups on the polymer brushes are well-suited to con‐ jugate bioactive macromolecules for improved cytocompatibility. However, γ-ray irradiated, ozone or photo-induced polymerization grafting of polymer brushes has several limitations, including low density of grafting due to steric hindrance, uncontrollable graft yield of polymer brushes, and undesired formation of a covalent bond between reactive groups on the polymer brushes and the surface [25]. Hence, an alternative grafting approach

that allows control over brush density, polydispersity and composition is desired.

was not thoroughly investigated in those studies.

178 Advances in Biomaterials Science and Biomedical Applications

**2. Materials and methods**

**2.1. Materials**

the thrombogenicity of the attached cells was also investigated.

One such alternative is the use of surface-initiated atom transfer radical polymerization (ATRP) approach to covalently graft polymer brushes in a tunable and controllable manner [26]. This approach allows the preparation of well-defined dense polymer brushes contain‐ ing reactive pendant groups (e.g. -OH, -COOH, or epoxide groups), and provides highly re‐ active binding sites for functional biomolecules.[27] As a result, surface-initiated ATRP provides a promising approach to fabricate PCL substrates with well-defined polymer brushes of controlled length and density, as well as tunable grafting density of biomacromo‐ lecules. However, to the best of our knowledge, only few studies have been devoted to mod‐ ifying biodegradable polyester polymers using surface-initiated ATRP to improve their cytocompatibility or blood compatibility [27,28]. Also, the functionality of the attached cells

As such, the aim of the current study is to utilize the surface-initiated ATRP method to tailor PCL substrates with dense functional P(GMA) brushes and high-density immobilized gela‐ tin to improve their properties for cell attachment and proliferation. Each functionalization step was ascertained by XPS, AFM and water contact angle measurements. The cytocompat‐ ibility of the functionalized PCL substrates was evaluated using human umbilical vein en‐ dothelial cells (HUVECs) and the effect of different surface properties on the regulation of

Polycaprolactone pellets (PCL, average *Mn*45000), 1,6-hexanediamine (98%), glycidyl metha‐ crylate (GMA, >97%), 2-bromoisobutyrl bromide (BIBB, 98%), 2,2'-bipyridine (bpy, 98%), di‐ chloromethane (anhydrous, >99.8%), triethylamine (TEA, 98%), isopropyl alcohol, hexane (anhydrous, >95%), copper (I) bromide (CuBr, 99%), copper (II) bromide (CuBr2, 98%), and gelatin (Porcine skin, Type A) were obtained from Sigma-Aldrich Chemical Co. (St. Louis, Polycaprolactone (PCL) films were prepared by solution casting method using previously established methods [29]. Briefly, 5 g of the PCL pellets was dissolved in 40 ml of dichloro‐ methane to form the PCL solution. The polymer solution was then cast onto the glass sub‐ strate with predetermined thickness using the automatic film applicator (PA-2105, BYK). The solvent was removed at room temperature by slow evaporation over a 24 h period, and was further dried in a vacuum oven for another 24 h at 35 o C to obtain the translucent PCL films with a thickness of about 150 μm. The resultant PCL films were cut into round-shaped specimens with a diameter of 2 cm. The activation of PCL substrates was performed by ami‐ nolysis treatment using a procedure previously described [30,31]. Briefly, the PCL films were immersed in a 10% (w/w) 1,6-hexanediamine and isopropanol mixture at 40 o C for a predetermined time. After aminolysis treatment, the resultant PCL-NH2 surfaces were thor‐ oughly rinsed with copious amounts of deionized water and isopropanol, respectively, to remove free 1,6-hexanediamine, and dried in a vacuum oven at 30 o C for 24 h.

The introduction of an alkyl halide ATRP initiator on the PCL-NH2 surface was accomplish‐ ed through the reaction of the amino groups with 2-bromoisobutyrate bromide (BIBB) [32]. The PCL-NH2 films were immersed in 30 ml of anhydrous hexane solution containing 1.0 ml (7.2 mmol) of triethylamine (TEA). After 30 min of degassing with nitrogen, the reaction mixture was cooled in an ice bath, and 0.89 ml (1.65g, 7.2 mmol) of BIBB was added drop‐ wise via a syringe. The reaction was allowed to proceed with gentle stirring at 0 o C for 2 h and then at room temperature for 12 h. The resulting surface (referred to as the PCL-Br sur‐ face) was washed thoroughly with copious amounts of hexane, ethanol, and finally deion‐ ized water, in that order, and was subsequently dried in a vacuum oven under reduced pressure at ambient temperature overnight.

#### **2.3. Surface-initiated ATRP of GMA and immobilization of gelatin**

For the grafting of P(GMA) brushes from the PCL-Br surfaces, surface-initiated ATRP of GMA was performed using a [GMA (3 ml)]:[CuBr]:[CuBr2]:[Bpy] molar feed ratio of 100:1.0:0.2:2.0 in 5 ml of methanol/water mixture (5/1, v/v) at room temperature in a Pyrex® tube. The reaction was allowed to proceed for 0.5 to 3 h to produce the PCL-*g*-P(GMA) sur‐ faces. After the prescribed reaction time, the films were removed and washed sequentially with copious amount of methanol and deionized water, followed by immersing in methanol for about 48 h to ensure the complete removal of the physically-adsorbed reactants or poly‐ mers. For the immobilization of gelatin onto the pendant epoxide groups of the P(GMA) brushes, the PCL-*g*-P(GMA) films were incubated in 10 ml of the phosphate buffered saline (PBS, pH 7.4) containing 3 mg/ml gelatin. The reaction was allowed to proceed at room tem‐ perature for 24 h under continuous stirring to produce the corresponding PCL-*g*-P(GMA)-*c*gelatin surfaces. After the reaction, the gelatin-immobilized PCL films were washed thoroughly with PBS solution and deionized water to remove the physically adsorbed (re‐ versibly-bound) gelatin, prior to being dried in a vacuum oven under reduced pressure overnight.

#### **2.4. Grafting density of the P(GMA) brushes and immobilized gelatin**

The grafting density of the P(GMA) brushes and the amount of immobilized gelatin on the PCL substrates was determined by the grafting yield (GY) using the following equation [27,33]:

$$
\Delta GY = \frac{W\_a - W\_b}{A} \tag{1}
$$

Where Wa and Wb are the weights of the dry film after and before graft polymerization (or immobilization of gelatin) respectively, and A is the film area (about 3.2 cm2 ). For each GY measurement, a minimum of three pieces of PCL films was used and the resulting values were averaged.

#### **2.5. Surface characterization**

The composition of the functionalized PCL films was determined by X-ray photoelectron spectroscopy (XPS). All the XPS spectra were recorded on a Krato AXIS Hsi spectrometer with a monochromatic Al Kα X-ray source (1486.6 eV photons), using procedures similar to those described previously [32]. The N 1s core-level signal can be used as an indicator of the immobilized gelatin. The [N]/[C] ratio, as determined from the sensitivity-factor-corrected N 1s and C 1s core-level XPS spectral area, indicated the relative abundance of the immobi‐ lized gelatin on the PCL substrates. Static water contact angles of the functionalized PCL film surfaces were measured at 25 o C and 60% relative humidity using a sessile drop method with 3 μl water droplets on a FTÅ 200 contact angle goniometer (First Ten Angstroms Inc., Portsmouth, VA, USA). The contact angles reported were the mean values from four sub‐ strates, with the value of each substrate obtained by averaging the contact angles for at least three surface locations. The surface topography of the functionalized PCL substrates was in‐ vestigated by atomic force microscope (AFM). A multimode scanning probe microscope equipped with a NanoscopeIIIa controller (Digital Instrument, Santa Barbara, USA) was used to capture the AFM images in air. 10 μm scans were recorded in tapping mode with a silicon cantilever. The drive amplitude was about 300 mV, and the scan rate was between 0.5 and 1.0 Hz. The arithmetic mean of the surface roughness (Ra) was determined by Nano‐ scope software.

#### **2.6. Cytocompatibility of the functionalized PCL substrates**

Human umbilical vein endothelial cells (HUVECs, ATCC CRL-1730TM) were cultured in gel‐ atin-coated T25 flasks containing MCDB131 cell culture medium supplemented with Foetal Bovine Serum, 0.2% Bovine Brain Extract, 0.25 ug/ml amphotericin, 0.1 mg/ml heparin, 100 U/ml penicillin, and 100 ug/ml streptomycin, in a CO2 environment at 37o C. The MCDB131 medium was changed every other day. Upon 90% culture confluency, cells were harvested by trypsinization using 0.25% Trypsin-EDTA. ECs between 4-6 passages were used for sub‐ sequent experiments.

#### *2.6.1. Cell proliferation*

faces. After the prescribed reaction time, the films were removed and washed sequentially with copious amount of methanol and deionized water, followed by immersing in methanol for about 48 h to ensure the complete removal of the physically-adsorbed reactants or poly‐ mers. For the immobilization of gelatin onto the pendant epoxide groups of the P(GMA) brushes, the PCL-*g*-P(GMA) films were incubated in 10 ml of the phosphate buffered saline (PBS, pH 7.4) containing 3 mg/ml gelatin. The reaction was allowed to proceed at room tem‐ perature for 24 h under continuous stirring to produce the corresponding PCL-*g*-P(GMA)-*c*gelatin surfaces. After the reaction, the gelatin-immobilized PCL films were washed thoroughly with PBS solution and deionized water to remove the physically adsorbed (re‐ versibly-bound) gelatin, prior to being dried in a vacuum oven under reduced pressure

The grafting density of the P(GMA) brushes and the amount of immobilized gelatin on the PCL substrates was determined by the grafting yield (GY) using the following equation

Where Wa and Wb are the weights of the dry film after and before graft polymerization (or

measurement, a minimum of three pieces of PCL films was used and the resulting values

The composition of the functionalized PCL films was determined by X-ray photoelectron spectroscopy (XPS). All the XPS spectra were recorded on a Krato AXIS Hsi spectrometer with a monochromatic Al Kα X-ray source (1486.6 eV photons), using procedures similar to those described previously [32]. The N 1s core-level signal can be used as an indicator of the immobilized gelatin. The [N]/[C] ratio, as determined from the sensitivity-factor-corrected N 1s and C 1s core-level XPS spectral area, indicated the relative abundance of the immobi‐ lized gelatin on the PCL substrates. Static water contact angles of the functionalized PCL

with 3 μl water droplets on a FTÅ 200 contact angle goniometer (First Ten Angstroms Inc., Portsmouth, VA, USA). The contact angles reported were the mean values from four sub‐ strates, with the value of each substrate obtained by averaging the contact angles for at least three surface locations. The surface topography of the functionalized PCL substrates was in‐ vestigated by atomic force microscope (AFM). A multimode scanning probe microscope equipped with a NanoscopeIIIa controller (Digital Instrument, Santa Barbara, USA) was used to capture the AFM images in air. 10 μm scans were recorded in tapping mode with a


C and 60% relative humidity using a sessile drop method

). For each GY

*W W a b GY A*

immobilization of gelatin) respectively, and A is the film area (about 3.2 cm2

**2.4. Grafting density of the P(GMA) brushes and immobilized gelatin**

180 Advances in Biomaterials Science and Biomedical Applications

overnight.

[27,33]:

were averaged.

**2.5. Surface characterization**

film surfaces were measured at 25 o

The pristine and functionalized PCL films were sterilized by immersing into 75% (v/v) etha‐ nol solution for 60 min, and then rinsed thrice with sterile PBS, followed by MCDB131 medi‐ um incubation overnight. Gelatin-coated coverslips (0.1%) were used as positive controls. Cell viability and proliferation was determined using the AlamarBlueTM(AB) assay. 0.5 ml of EC cell suspension (2×104 cells/ml) was seeded into each well of 24-well plate containing the pristine and functionalized PCL films, and incubated in a 5% CO2 environment at 37 o C for 1, 3, 5 and 7 days. The cell culture medium was changed every other day. After the predeter‐ mined incubation period, culture media was removed from the wells, and 0.5 ml of the AB solution (10% AB solution in culture media without FBS) was added to the wells. The plates were incubated in a 5% CO2 atmosphere at 37ºC for 4 h and the fluorescence density was measured using a microplate reader (Model 680, Bio-Rad Laboratories, Inc. Hercules, CA, USA) at an excitation wavelength of 570 nm and an emission wavelength of 580 nm. Cell numbers were calculated using standards derived from seeding known quantities of cells and correlating with fluorescence emission.

#### *2.6.2. Cell imaging*

*In vitro* qualitative analysis of cell coverage and viability was performed using a LIVE/ DEAD® viability/cytotoxicity assay to assess the extent of endothelialization on the function‐ alized PCL surfaces. For this procedure, calcein AM (4 mM in anhydrous dimethyl sulfox‐ ide, DMSO) and EthD-1 (2 mM in DMSO/H2O, 1:4 v:v) were added to PBS (1:1000 ratio) to produce a LIVE/DEAD® staining solution. The cell-seeded PCL samples, obtained after 7 days cell culture, were first washed thrice with PBS to eliminate the nonadherent cells, fol‐ lowed by staining using 0.1 ml of LIVE/DEAD staining solution. After incubation in a 5% CO2 atmosphere at 37o C for 30 min, the samples were visualized by Nikon Image Ti fluores‐ cence microscope (emission at 515 nm and 635 nm (Nikon Instruments, Tokyo, Japan) to ac‐ quire fluorescent images using NIS-Elements Br software.

#### **2.7. Blood compatibility of the bare and endothelialized PCL substrates**

The hemolysis rate, coagulant activity, nitric oxide (NO) production, and platelet activation of the bare and endothelialized PCL films with various surface functionalizations were in‐ vestigated to evaluate their blood compatibility. The endothelialized PCL substrates were obtained by culturing ECs (2×104 cells/ml) for 7 days on surface-functionalized PCL films us‐ ing the procedures described above.

#### *2.7.1. Hemolysis rate test*

The pristine and functionalized PCL samples were immersed in diluted blood solution con‐ taining 2% fresh anticoagulated (ACD) human blood and 98% physiological salt solution and incubated at 37o for 1 h. After centrifugation at 3000 rpm for 5 min, the absorbance of solution was recorded as Dt . Under the same conditions, the solution containing 2% ACD blood and 98% physiological salt solution was used as a negative reference, and the solution containing 2% ACD blood and 98% distilled water was used as a positive reference. These absorbances were recorded as Dnc and Dpc, respectively. The hymolysis rate α of the samples was calculated using the following equation:

$$
\alpha = \frac{D\_t \cdot D\_{nc}}{D\_{pc} \cdot D\_{nc}} \times 100\% \tag{2}
$$

#### *2.7.2. Coagulation assays*

Whole blood of healthy human volunteers was mixed with 3.8% sodium citrate at a volume ratio of 1:9. The blood was centrifuged at 3000 rpm for 15 min at room temperature to obtain platelet-poor plasma (PPP). Aliquots of 500 μl of PPP were added to be in contact with the surfaces of each bare or endothelialized PCL substrate for 10 min at 37o C. The PPP was then collected and added with tissue thromboplastin (human brain extract) for prothrombin time (PT) tests, or added with a partial thromboplastin reagent (ellagic acid) for activated partial thromboplastin time (APTT) test. Subsequently, the fibrin clot formation time was deter‐ mined by an automatic coagulation analyzer (Sysmex CA-7000). PPP that was not exposed to the PCL substrates was used as a blank sample.

#### *2.7.3. Nitric Oxide (NO) secretion by HUVEC*

ECs cultured for 7 days on the functionalized PCL substrates were washed twice with PBS and incubated at 37o C with trypsin-EDTA (0.25%) solution for cell detachment. The resul‐ tant ECs were serum-starved overnight in serum-free medium. After incubation with fresh serum-free medium for 6 h, the medium was removed and DAF-FM diacetate (Molecular Probes, D-23842) was added to the medium to effect a final concentration of 10 μM.The me‐ dium was subsequently incubated at 37 °C for 1 h, followed by detection of fluorescence us‐ ing Glomax 20/20 luminometer equipped with a blue fluorescent module. The end product of DAF-FM diacetate and NO is a benzotriazole derivative with a fluorescence excitation and emission maxima of 495 and 515 nm, respectively. Fluorescence units were normalized to cell numbers.

#### *2.7.4. Platelet activation determination by P-selectinassay*

**2.7. Blood compatibility of the bare and endothelialized PCL substrates**

ing the procedures described above.

182 Advances in Biomaterials Science and Biomedical Applications

*2.7.1. Hemolysis rate test*

solution was recorded as Dt

*2.7.2. Coagulation assays*

and incubated at 37o

was calculated using the following equation:

to the PCL substrates was used as a blank sample.

*2.7.3. Nitric Oxide (NO) secretion by HUVEC*

The hemolysis rate, coagulant activity, nitric oxide (NO) production, and platelet activation of the bare and endothelialized PCL films with various surface functionalizations were in‐ vestigated to evaluate their blood compatibility. The endothelialized PCL substrates were obtained by culturing ECs (2×104 cells/ml) for 7 days on surface-functionalized PCL films us‐

The pristine and functionalized PCL samples were immersed in diluted blood solution con‐ taining 2% fresh anticoagulated (ACD) human blood and 98% physiological salt solution and incubated at 37o for 1 h. After centrifugation at 3000 rpm for 5 min, the absorbance of

blood and 98% physiological salt solution was used as a negative reference, and the solution containing 2% ACD blood and 98% distilled water was used as a positive reference. These absorbances were recorded as Dnc and Dpc, respectively. The hymolysis rate α of the samples

Whole blood of healthy human volunteers was mixed with 3.8% sodium citrate at a volume ratio of 1:9. The blood was centrifuged at 3000 rpm for 15 min at room temperature to obtain platelet-poor plasma (PPP). Aliquots of 500 μl of PPP were added to be in contact with the

collected and added with tissue thromboplastin (human brain extract) for prothrombin time (PT) tests, or added with a partial thromboplastin reagent (ellagic acid) for activated partial thromboplastin time (APTT) test. Subsequently, the fibrin clot formation time was deter‐ mined by an automatic coagulation analyzer (Sysmex CA-7000). PPP that was not exposed

ECs cultured for 7 days on the functionalized PCL substrates were washed twice with PBS

tant ECs were serum-starved overnight in serum-free medium. After incubation with fresh serum-free medium for 6 h, the medium was removed and DAF-FM diacetate (Molecular Probes, D-23842) was added to the medium to effect a final concentration of 10 μM.The me‐ dium was subsequently incubated at 37 °C for 1 h, followed by detection of fluorescence us‐ ing Glomax 20/20 luminometer equipped with a blue fluorescent module. The end product of DAF-FM diacetate and NO is a benzotriazole derivative with a fluorescence excitation

C with trypsin-EDTA (0.25%) solution for cell detachment. The resul‐

*<sup>α</sup>* <sup>=</sup> *Dt* - *Dnc*

surfaces of each bare or endothelialized PCL substrate for 10 min at 37o

. Under the same conditions, the solution containing 2% ACD

*Dpc* - *Dnc* ×100% (2)

C. The PPP was then

Platelet activation by the bare and endothelialized PCL substrates was investigated using the P-selectin (CD62P) assay. Briefly, 100 μl of fresh human platelet rich plasma (PRP) was incubated with the bare or 7-day endothelialized PCL substrates at 37o C for 2 h. At the end of incubation, the films were thoroughly with copious amounts of PBS solution thrice, fol‐ lowed by adding 40 μl of anti-CD62P (1:100, v:v) to each film, and then incubated at 37o C for 1 h. After being washed thrice with PBS solution, the films were each incubated with 40 μl of horseradish peroxidase-conjugated sheep anti-mouse polycolonal antibody at 1:100 (v:v) at 37o C for 1 h. Subsequently, the PCL films were reacted with 150 μl of 3,3',5, 5'-tetrame‐ thylbenzidine (TMB) chromogenic solution for 10 min. The color reaction was terminated by adding of 100 μL of 1 M H2SO4, and the optical densities (OD) were measured at 450 nm using a Varioskan Flash Microplate Reader (Thermo Fisher Scientific, Waltham, MA, USA).

#### *2.7.5. Gene and protein expression of vWF and activity of MMP-2 in ECs cultured on functionalized PCL surfaces*

For the real-time qPCR of von Willebrand factor (vWF) and matrix metalloproteinase-2 (MMP-2), the total RNA was extracted from the ECs after 7 days in culture, reverse-transcri‐ bed into cDNA and analyzed as described above. The expression of vWF and MMP-2 was normalized to the housekeeping ribosomal protein L27 (rpl27). Endothelial cells treated with 10 ng /ml TNF were used as positive controls.

For the immunoblot detection of vWF protein, cells were lyzed in protein lysis buffer (0.1% sodium dodecyl sulfate, 0.5% triton X-100, and 0.5% sodium deoxycholate dissolved in pH 7.4 PBS) and resolved using a denaturing 10% SDS-PAGE. The proteins were then blotted onto a nitrocellulose membrane and after blocking with 5% non-fat milk in tris-buffered sal‐ ine with 0.1% Tween (TBS-T), the membrane stained using a rabbit anti-human vWF anti‐ body at 1:5000 and subsequently with anti-rabbit HRP-conjugated antibody at 1:10,000 in TBS-T. The vWF was then visualized after developing using chemiluminescence on X-ray film. For determination of the MMP-2 activity, proteins were extracted from trypsinized cells using the protein lysis buffer before resolving by electrophoresis through a 10% SDS-PAGE copolymerized with 0.1% gelatin as substrate for enzymatic digestion. The molecular sizes of gelatinolytic activities were determined using protein standards (Fermentas, Prestained PAGE rulers). Upon completion of gel running, the gel was incubated with 100 mL renaturation buffer containing 2.5% triton X-100 for 1 h at room temperature with agitation. The gel was subsequently incubated in 100 ml of development buffer containing 50 mM Tris base, 200 mM NaCl, 5 mM CaCl2, and 0.02% Brij-35 overnight at 37 °C. Developed gel was then stained by the Coomassie Blue and gelatinolytic activities of MMP-2 were determined by the transparent bands appeared at the molecular weight of approximately 68 kDa and 98 kDa, respectively.

#### **2.8. Statistical analysis**

Each experiment was carried out with four replicates (n = 4), and the data are presented as mean ± standard deviation (SD) unless of otherwise stated. Statistical analysis was carried out by means of one-way analysis of variance (ANOVA) with Tukey's post hoc test. The confidence levels of 95% (p<0.05) and 99% (p<0.01) were used and no adjustments were made for multiple comparisons.

#### **3. Results and discussion**

Polycaprolactone (PCL) films with gelatin-coupled poly(glycidyl methacrylate) (P(GMA)) brushes were prepared via the following reaction sequence (Fig. 1): (a) active amine groups were introduced to the PCL film surfaces by the aminolysis reaction, (b) the immobilization of an alkyl bromide ATRP initiator was achieved via TEA-catalyzed condensation reaction between the amine groups on the aminolyzed PCL substrates and 2-bromoisobutyryl bro‐ mide (BIBB), (c) well-defined P(GMA) functional brushes were covalently grafted from the ATRP initiator-immobilized PCL surface via surface-initiated ATRP of GMA, (d) cell-adhe‐ sive gelatin was directly coupled to the pendant active epoxide groups of the grafted P(GMA). Details of each functionalization step are discussed below.

**Figure 1.** Schematic illustration of the process of (a) aminolysis of PCL substrates to introduce the free amino groups (the PCL-NH2 surface), (b) immobilization of a alkyl bromine-containing initiator via condensation reaction to give the PCL-Br surface, (c) surface-initiated atom transfer radical polymerization (ATRP) of GMA from the PCL-Br surface to produce the PCL-*g*-P(GMA) surface, and (d) subsequently covalent conjugation of gelatin to obtain the PCL-*g*-P(GMA) *c*-gelatin surface.

#### **3.1. Aminolysis of PCL substrates and immobilization of ATRP initiator**

**2.8. Statistical analysis**

made for multiple comparisons.

184 Advances in Biomaterials Science and Biomedical Applications

**3. Results and discussion**

*c*-gelatin surface.

Each experiment was carried out with four replicates (n = 4), and the data are presented as mean ± standard deviation (SD) unless of otherwise stated. Statistical analysis was carried out by means of one-way analysis of variance (ANOVA) with Tukey's post hoc test. The confidence levels of 95% (p<0.05) and 99% (p<0.01) were used and no adjustments were

Polycaprolactone (PCL) films with gelatin-coupled poly(glycidyl methacrylate) (P(GMA)) brushes were prepared via the following reaction sequence (Fig. 1): (a) active amine groups were introduced to the PCL film surfaces by the aminolysis reaction, (b) the immobilization of an alkyl bromide ATRP initiator was achieved via TEA-catalyzed condensation reaction between the amine groups on the aminolyzed PCL substrates and 2-bromoisobutyryl bro‐ mide (BIBB), (c) well-defined P(GMA) functional brushes were covalently grafted from the ATRP initiator-immobilized PCL surface via surface-initiated ATRP of GMA, (d) cell-adhe‐ sive gelatin was directly coupled to the pendant active epoxide groups of the grafted

**Figure 1.** Schematic illustration of the process of (a) aminolysis of PCL substrates to introduce the free amino groups (the PCL-NH2 surface), (b) immobilization of a alkyl bromine-containing initiator via condensation reaction to give the PCL-Br surface, (c) surface-initiated atom transfer radical polymerization (ATRP) of GMA from the PCL-Br surface to produce the PCL-*g*-P(GMA) surface, and (d) subsequently covalent conjugation of gelatin to obtain the PCL-*g*-P(GMA)-

P(GMA). Details of each functionalization step are discussed below.

Aminolysis represents an easy-to-perform chemical technique to engraft amino groups along the polyester chains, and hence has been widely used in the surface modification of scaffolds for tissue engineering applications [31,34]. In this study, PCL substrates were acti‐ vated by the aminolysis reaction to introduce active amine groups. The relative amount of amine groups on the aminolyzed PCL (defined as the PCL-NH2) surface was quantitatively determined by XPS measurements. The [N]/[C] ratio, as determined from sensitivity factorcorrected N 1s and C 1s core-level XPS spectral area, increases with the aminolysis time and reaches the maximal value after 1 h, which is estimated to be about 0.043 (Figs. 2). The result is consistent with the data reported previously [35,36]. As a degradation reaction, the ami‐ nolysis reaction is found to proceed preferentially at the amorphous regions of polymer in diamine solution during the initial period [37]. At longer aminolysis time, the decrease in bound amine groups may be caused by chain scission, formation of oligomers and other low mass fragments that are removed from the surface during reaction and the rinsing process [38]. Thus, the optimal aminolysis time for PCL film was found to be 1 h, and this reaction time was chosen for the subsequent surface modification and cell studies.

**Figure 2.** The [N]/[C] ratio of the aminolyzed PCL surface as a function of aminolysis time determined by XPS measure‐ ments. The analysis reaction of PCL films proceeded at 40oC in 10 wt% 1,6-hexanediamine/2-propanol solution. Error bars represent the standard deviation over separate measurement on three PCL films. The optimized aminolysis time was observed at 1 h with the [N]/[C] ratio of 0.043.

The chemical composition of the PCL film surfaces at various stages of surface modification was ascertained by XPS. Figs. 3a-3c show the respective wide scan, C 1s, and N 1s core-level spectra of the pristine PCL and PCL-NH2 surfaces from 1 h of aminolysis. The C 1s core-lev‐ el spectra of the pristine PCL can be curve-fitted into three peak components with binding energies (BEs) at about 284.6, 286.2 and 288.7 eV, attributable to the C-H, C-O, and O=C-O species, respectively (Fig. 3b) [39]. The area ratio of [C-H]:[C-O]:[O=C-O] is around 5.0:1.1:1.0 (Table 1), which is in good agreement with the theoretical value of 5:1:1 for the polycaprolactone structures. The appearance of N 1s signal in the wide scan spectrum (Fig. 3a) and an additional peak component at 285.5 eV, attributable to C-N species, in the curvefitted C 1s core-level spectrum (Fig. 3c) indicate the successful introduction of amine groups onto the PCL substrates after 1 h of aminolysis. The only peak component found at the BE of 399.6 eV in the N 1s core-level spectrum is associated with the free amine group on the PCL-NH2 film surface (Fig. 3c') [38]. The decrease in static water contact angles of the PCL sub‐ strates from 93 ± 2o to 66 ± 3o is consistent with the presence of amine groups on the PCL-NH2 surface (Table 1). The amine groups on the aminolyzed PCL surface can not only improve surface hydrophilicity, but also offer the active sites for further functionalization.

**Figure 3.** Wide scan and C 1s core-level curve-fitted XPS spectra of the (a,b) pristine PCL, (c,d) PCL-NH2 from 1 h of aminolysis, and (e,f) PCL-Br surfaces. Insets of (d') and (f') correspond to the N 1s and Br 3d core-level XPS spectra of the PCL-NH2 and PCL-Br surfaces, respectively.

The immobilization of a uniform monolayer of initiators on the solid surface is indispensible in the surface-initiated ATRP process [40]. An alkyl bromide ATRP initiator was introduced onto the PCL-NH2 surface via TEA-catalyzed condensation reaction to produce the PCL-Br surface. Successful introduction of the alkyl bromide-containing ATRP initiator onto the PCL substrates can be deduced from the appearance of three additional signals with BEs at about 70, 189 and 256 eV, attributable to Br 3d, Br 3p, and Br 3s, respectively, in the wide scan spectrum of the PCL-Br surface (Fig. 3a) [41]. The [Br]/[C] ratio, as determined from the Br 3d and C 1s core-level spectral area ratio, was about 3.17×10-2 (Fig. 3d). The correspond‐ ing Br 3d core-level spectrum of the PCL-Br surface with a Br 3d5/2 BE of 70.4 eV is consistent

with the presence of the alkyl bromide species [41] (Fig. 3d'). The alkyl bromide-immobi‐ lized PCL surface became more hydrophobic, as static water contact angle increased noticea‐ bly to 85 ± 3o (Table 1).

energies (BEs) at about 284.6, 286.2 and 288.7 eV, attributable to the C-H, C-O, and O=C-O species, respectively (Fig. 3b) [39]. The area ratio of [C-H]:[C-O]:[O=C-O] is around 5.0:1.1:1.0 (Table 1), which is in good agreement with the theoretical value of 5:1:1 for the polycaprolactone structures. The appearance of N 1s signal in the wide scan spectrum (Fig. 3a) and an additional peak component at 285.5 eV, attributable to C-N species, in the curvefitted C 1s core-level spectrum (Fig. 3c) indicate the successful introduction of amine groups onto the PCL substrates after 1 h of aminolysis. The only peak component found at the BE of 399.6 eV in the N 1s core-level spectrum is associated with the free amine group on the PCL-NH2 film surface (Fig. 3c') [38]. The decrease in static water contact angles of the PCL sub‐

NH2 surface (Table 1). The amine groups on the aminolyzed PCL surface can not only improve surface hydrophilicity, but also offer the active sites for further functionalization.

**Figure 3.** Wide scan and C 1s core-level curve-fitted XPS spectra of the (a,b) pristine PCL, (c,d) PCL-NH2 from 1 h of aminolysis, and (e,f) PCL-Br surfaces. Insets of (d') and (f') correspond to the N 1s and Br 3d core-level XPS spectra of

The immobilization of a uniform monolayer of initiators on the solid surface is indispensible in the surface-initiated ATRP process [40]. An alkyl bromide ATRP initiator was introduced onto the PCL-NH2 surface via TEA-catalyzed condensation reaction to produce the PCL-Br surface. Successful introduction of the alkyl bromide-containing ATRP initiator onto the PCL substrates can be deduced from the appearance of three additional signals with BEs at about 70, 189 and 256 eV, attributable to Br 3d, Br 3p, and Br 3s, respectively, in the wide scan spectrum of the PCL-Br surface (Fig. 3a) [41]. The [Br]/[C] ratio, as determined from the Br 3d and C 1s core-level spectral area ratio, was about 3.17×10-2 (Fig. 3d). The correspond‐ ing Br 3d core-level spectrum of the PCL-Br surface with a Br 3d5/2 BE of 70.4 eV is consistent

is consistent with the presence of amine groups on the PCL-

strates from 93 ± 2o

to 66 ± 3o

186 Advances in Biomaterials Science and Biomedical Applications

the PCL-NH2 and PCL-Br surfaces, respectively.


a Pristine PCL refers to the cleaned PCL film after rigorous wasing with alcohol/water solution and deionized water, b PCL-NH2 was obtained after 1 h of aminolysis in a 10% (w/w) 1,6-hexanediamine/isopropanol solution at 40 oC, c PCL-Br was obtained after the PCL-NH2 surface reacted with 2-bromoisobutyryl bromide (BIBB) in dried hexane containing 1:1 (molar ratio) BIBB and triehtylamine (TEA), d,e Reaction conditions: [GMA]:[CuBr]:[CuBr2]:[bpy]=100:1:0.2:2 in meth‐ anol-water solution (1:1, v:v) at room temperature for 1 and 3 h to produce the PCL-*g*-P(GMA)1 and PCL-*g*-P(GMA)2 surfaces, respectively, f Reaction conditions: the PCL-*g*-P(GMA)1 and PCL-*g*-P(GMA)2 surfaces incubated in PBS (pH 7.4) solution containing the gelatin at a concentration of 3 mg/mL at room temperature for 24 h, g GY denotes the graft‐ ing yield, and is defined as GY = (Wa - Wb)/A, where Wa and Wb corresponds to the weight of the dry films before and after grafting of polymer brushes, respectively, and A is the film area (about 3.2 cm2

), h SD denotes standard deviation, i Determined from the corresponding sensitivity factor-corrected element core-level spectral area ratios, j Determined from the curve-fitted C 1s core-level spectra. Theoretical values are shown in paren‐ theses. k WCA denotes static water contact angles.

**Table 1.** Grafting yield, surface composition, and water contact angles of the pristine PCL and surface-functionalized PCL surfaces

#### **3.2. Surface-initiated ATRP of GMA and immobilization of gelatin**

P(GMA) is an effective surface linker to immobilize biomolecules, such as proteins, antibod‐ ies or enzymes, for tissue engineering applications [42]. Fig. 4 shows the respective wide scan, C 1s and Br 3d core-level spectra of the PCL-*g*-P(GMA) surface from 1 and 3 h of ATRP reaction. The C 1s core-level spectra of the PCL-*g*-P(GMA) surface can be curve-fitted into three peak components with BEs at 284.6, 286.2 and 288. 7 eV, attributable to C-H, C-O and O=C-O, respectively (Figs. 4b and 4d). For the PCL-*g*-P(GMA)1 surface from 1 h of ATRP, the area ratio of [C-H]:[C-O]:[O=C-O] is about 3.8:2.8:1.0 (Table 1), which is slightly different from the theoretical value of 3:3:1 for the GMA unit structure. The deviation in peak compo‐ nent area ratio of C 1s core-level spectrum of the PCL-g-P(GMA)1 surface suggests that the thickness of the P(GMA) brushes is less than the probing depth of XPS technique (about 8 nm in an organic matrix) [41]. Increasing the reaction time to 3 h leads to a [C-H]:[C-O]: [O=C-O] ratio of about 3.1:3.0:1.0, which is close to the theoretical value of the GMA repeat unit structure (Table 1). This is an indication that the P(GMA) brushes were thicker than the probing depth of XPS technique. It has been reported that the thickness of the P(GMA) brushes grafted on the silicon surface is around 30 nm after 3 h of ATRP of GMA under sim‐ ilar reaction conditions [41]. The presence of P(GMA) brushes leads to decrease in static wa‐ ter contact angles to 62 ± 4o and 61 ± 5o , respectively, for the PCL-*g*-P(GMA)1 and PCL-*g*-P(GMA)2 surfaces, owing to the presence of hydrophilic epoxide groups [43].

**Figure 4.** Wide scan, C 1s, and Br 3d core-level curve-fitted XPS spectra of the (a,b,b') PCL-*g*-P(GMA)1 from 1 h of ATRP reaction and (c,d,d') PCL-*g*-P(GMA)2 from 3 h of ATRP reaction. Successful grafting of P(GMA) polymer brushes can be deduced from the area ratios of [C-H]:[C-O]:[O=C-O] peak components comparable to the theoretical value of 3:3:1 of GMA molecular structure.

The grafting yield (GY) was measured to evaluate the kinetics of polymer chain growth in this study. As shown in Fig. 5, an approximate linear increase in GY of the grafted P(GMA) chains with polymerization time could be observed for the PCL-Br surface. The result sug‐ gests that the chain growth from the PCL-Br surface proceeds in a controlled and well-de‐ fined manner. The GY values of the PCL-*g*-P(GMA)1 and PCL-*g*-P(GMA)2 surfaces are about 6.31 ± 1.32 and 14.76 ± 2.63 μg/cm2 (Table 1), respectively. The persistence of the Br 3d core-level signal (Figs. 4b' and 4d') is consistent with the fact that the living chain end from the ATRP process involves a dormant alkyl halide group, which can be readily reactivated to initiate the block copolymerization [25]. However, the molecular weight and molecular weight distribution of the surface-graft polymers cannot be determined with sufficient accu‐ racy without precise cleavage of the grafted P(GMA) from the film surfaces [27].

the area ratio of [C-H]:[C-O]:[O=C-O] is about 3.8:2.8:1.0 (Table 1), which is slightly different from the theoretical value of 3:3:1 for the GMA unit structure. The deviation in peak compo‐ nent area ratio of C 1s core-level spectrum of the PCL-g-P(GMA)1 surface suggests that the thickness of the P(GMA) brushes is less than the probing depth of XPS technique (about 8 nm in an organic matrix) [41]. Increasing the reaction time to 3 h leads to a [C-H]:[C-O]: [O=C-O] ratio of about 3.1:3.0:1.0, which is close to the theoretical value of the GMA repeat unit structure (Table 1). This is an indication that the P(GMA) brushes were thicker than the probing depth of XPS technique. It has been reported that the thickness of the P(GMA) brushes grafted on the silicon surface is around 30 nm after 3 h of ATRP of GMA under sim‐ ilar reaction conditions [41]. The presence of P(GMA) brushes leads to decrease in static wa‐

**Figure 4.** Wide scan, C 1s, and Br 3d core-level curve-fitted XPS spectra of the (a,b,b') PCL-*g*-P(GMA)1 from 1 h of ATRP reaction and (c,d,d') PCL-*g*-P(GMA)2 from 3 h of ATRP reaction. Successful grafting of P(GMA) polymer brushes can be deduced from the area ratios of [C-H]:[C-O]:[O=C-O] peak components comparable to the theoretical value of 3:3:1 of

The grafting yield (GY) was measured to evaluate the kinetics of polymer chain growth in this study. As shown in Fig. 5, an approximate linear increase in GY of the grafted P(GMA) chains with polymerization time could be observed for the PCL-Br surface. The result sug‐ gests that the chain growth from the PCL-Br surface proceeds in a controlled and well-de‐ fined manner. The GY values of the PCL-*g*-P(GMA)1 and PCL-*g*-P(GMA)2 surfaces are

core-level signal (Figs. 4b' and 4d') is consistent with the fact that the living chain end from

, respectively, for the PCL-*g*-P(GMA)1 and PCL-*g*-

(Table 1), respectively. The persistence of the Br 3d

and 61 ± 5o

P(GMA)2 surfaces, owing to the presence of hydrophilic epoxide groups [43].

ter contact angles to 62 ± 4o

188 Advances in Biomaterials Science and Biomedical Applications

GMA molecular structure.

about 6.31 ± 1.32 and 14.76 ± 2.63 μg/cm2

**Figure 5.** A linear relationship between the grafting yield (GY) of the P(GMA) brushes with the surface-initiated ATRP time. The polymer chain growth was tuneable by varying reaction time.

Nucleophilic reactions involving –NH2 moieties of biomolecules and the pendant epoxide groups have been widely reported [44]. In this work, cell-adhesive gelatin was directly cou‐ pled to the pendant epoxide groups of the PCL-*g*-P(GMA)1 and PCL-*g*-P(GMA)2 surfaces to produce the corresponding PCL-*g*-P(GMA)1-*c*-gelatin and PCL-*g*-P(GMA)2-*c*-gelatin surfa‐ ces, respectively. Fig. 6 shows the respective wide scan, C 1s and N 1s core-level spectra of the gelatin-immobilized PCL surfaces. The corresponding curve-fitted C 1s core-level spec‐ trum was composed of five peak components with BEs at about 284.6, 285.5, 286.2, 288.2 and 289.1 eV, attributable to the C-H, C-N, C-O, O=CNH, and O=C-O species [41], respectively (Figs. 6b and 6d). The C-N peak component is associated with the linkages in gelatin itself, as well as the linkage between P(GMA) and gelatin. The O=CNH peak component is ascri‐ bed to the peptide bonds in gelatin. The above results and the appearance of a strong N 1s signal with BE at 399.6 eV (Figs. 6b' and 6d'), characteristic of amine species, are consistent with the fact that gelatin has been covalently immobilized on the P(GMA) brushes. The sur‐ face wettability of the PCL substrates is significantly improved after the immobilization of gelatin, as water contact angles decrease to 37 ± 2o (for the PCL-*g*-P(GMA)1-*c*-gelatin) and 35 ± 3o (for the PCL-*g*-P(GMA)2-*c*-gelatin) (Table 1). It is reported that gelatin contains large amount of glycine (Gly) and proline (Pro) which are hydrophilic amino acids [45]. The hy‐ droxyl groups (-OH) generated in the ring-opening reaction of epoxide groups by coupling of gelatin could have also contributed to the lower water contact angle of the PCL-*g*-P(GMA)-*c*-gelatin surfaces.

**Figure 6.** Wide scan, C 1s and N 1s core-level curve-fitted XPS spectra of the (a,b,b') PCL-*g*-P(GMA)1-*c*-gelatin and (c,d,d') PCL-*g*-P(GMA)2-*c*-gelatin surfaces. The appearance of two additional peak components of C-N and O=CNH as a result of immobilized gelatin.

#### **3.3. Surface topography**

The changes in topography of the PCL film surfaces after each functionalization step were investigated by AFM. Fig. 7 shows the representative AFM height images of the pristine PCL and functionalized PCL surfaces with scanned areas of 10 μm × 10 μm. The pristine PCL film surface is relatively uniform and smooth with a root-mean-square surface rough‐ ness values (Ra) of about 19 nm (Fig. 7a). After the aminolysis treatment, the Ra value in‐ creases to 31 nm (Fig. 7b). The observation that aminolysis caused a noticeable increase in surface roughness is in agreement with the findings by other groups [30,35]. The existence of shallow pits is probably the result of the penetration of hexanediamine molecules into the PCL films, since it has been previously reported that the aminolysis reaction can take place at a depth of around 50 μm [23,30]. After graft polymerization of GMA, obvious increases in Ra values are observed on the PCL-*g*-P(GMA)1 (56.9 nm, Fig. 7c) and PCL-*g*-P(GMA)2 surfa‐ ces (67.8 nm, Fig. 7e), and characteristic fiber-like features of polymer brushes are also visi‐ ble on the P(GMA)-grafted film surfaces (Figs. 7c and 7e). The subsequent coupling of gelatin to P(GMA) brushes resulted in a further slight increase in surface roughness of PCL substrates, as Ra values increase to 59 nm and 71.5 nm for the PCL-*g*-P(GMA)1-*c*-gelatin and the PCL-*g*-P(GMA)2-*c*-gelatin surfaces, respectively.

of gelatin could have also contributed to the lower water contact angle of the PCL-*g*-

**Figure 6.** Wide scan, C 1s and N 1s core-level curve-fitted XPS spectra of the (a,b,b') PCL-*g*-P(GMA)1-*c*-gelatin and (c,d,d') PCL-*g*-P(GMA)2-*c*-gelatin surfaces. The appearance of two additional peak components of C-N and O=CNH as

The changes in topography of the PCL film surfaces after each functionalization step were investigated by AFM. Fig. 7 shows the representative AFM height images of the pristine PCL and functionalized PCL surfaces with scanned areas of 10 μm × 10 μm. The pristine PCL film surface is relatively uniform and smooth with a root-mean-square surface rough‐ ness values (Ra) of about 19 nm (Fig. 7a). After the aminolysis treatment, the Ra value in‐ creases to 31 nm (Fig. 7b). The observation that aminolysis caused a noticeable increase in surface roughness is in agreement with the findings by other groups [30,35]. The existence of shallow pits is probably the result of the penetration of hexanediamine molecules into the PCL films, since it has been previously reported that the aminolysis reaction can take place at a depth of around 50 μm [23,30]. After graft polymerization of GMA, obvious increases in Ra values are observed on the PCL-*g*-P(GMA)1 (56.9 nm, Fig. 7c) and PCL-*g*-P(GMA)2 surfa‐ ces (67.8 nm, Fig. 7e), and characteristic fiber-like features of polymer brushes are also visi‐ ble on the P(GMA)-grafted film surfaces (Figs. 7c and 7e). The subsequent coupling of gelatin to P(GMA) brushes resulted in a further slight increase in surface roughness of PCL

P(GMA)-*c*-gelatin surfaces.

190 Advances in Biomaterials Science and Biomedical Applications

a result of immobilized gelatin.

**3.3. Surface topography**

**Figure 7.** Representative two-dimensional (2D) AFM images of (a) pristine PCL, (b) PCL-NH2, (c) PCL-*g*-P(GMA)1 from 1 h of ATRP, (d) PCL-*g*-P(GMA)2 from 3 h of ATRP, (e) PCL-*g*-P(GMA)1-*c*-gelatin, and (f) PCL-*g*-P(GMA)2-*c*-gelatin surfa‐ ces. The arithmetical mean roughness (Ra) of different PCL substrates was obtained from a scan size of 10 μm × 10 μm.

#### **3.4. Endothelial cells proliferation and surface endothelialization**

The adhesion and proliferation of endothelial cells (ECs) on the functionalized PCL surfaces was quantitatively determined by the AlamarBlueTM (AB) assay, and the results are shown in Fig. 8. The pristine PCL film surface is the least conducive for supporting cellular growth, since only a marginal increase in cells over 7 days of culture was observed. The cells attach‐ ed to the PCL-NH2 film surfaces showed a slight improvement in proliferation as compared to the pristine PCL surface. This result is consistent with previous findings that the presence of amine groups on the PCL surfaces leads to a positive effect on cell proliferation [23,30], albeit to a limited extent. Despite the improvement in surface hydrophilicity and roughness, the grafting of P(GMA) brushes onto the PCL film surfaces did not lead to an enhancement in EC proliferation behavior, which is probably associated with the cytotoxicity and mutage‐ nicity of epoxides groups to ECs [46]. Besides the fact that polymer surfaces with moderate hydrophilicity of water contact angles in a range of 30-70o and rougher nano-topography are favorable for cell attachment and proliferation [47,48], other factors (e.g. biological cues) may also be required for positive cell interaction with material substrates. This hypothesis was confirmed by the observation that the gelatinized P(GMA)-grafted PCL substrates ex‐ hibited higher affinity and proliferation for ECs as compared to the surfaces that did not contain the bioactive gelatin motifs.

In fact, the proliferation rates of the PCL-*g*-P(GMA)1-*c*-gelatin and PCL-*g*-P(GMA)2-*c*-gelatin surfaces were comparable to that of the gelatin-coated coverslips (positive controls). Cell prolif‐ eration on the gelatin-immobilized PCL surfaces was not only significantly enhanced, but also found to be positively correlated to the amounts of immobilized gelatin. The PCL-*g*-P(GMA)2 *c*-gelatin surface exhibited more pronounced enhancement in cell adhesion and proliferation than that of the PCL-*g*-P(GMA)1-*c*-gelatin surface, as the longer ATRP reaction time allowed for more gelatin to be attached. This result suggests that an increase in surface density of the immo‐ bilized gelatin can lead to an increase in EC proliferation over time. This phenomenon is proba‐ bly associated with the fact that immobilization of gelatin provides many epitopes or ligands for cell adhesion molecules, such as integrins, thus mimicking the natural extracellular environ‐ ment that is favorable for EC adhesion, spreading and proliferation.

**Figure 8.** EC proliferation profile on the gelatin-coated coverslips, pristine PCL and functionalized PCL surfaces after 1, 3, 5 and 7 days of incubation at 37 oC in a 5% CO2 atmosphere as determined by the AlamarBlueTM(AB) assay. Data presented as means ± SD. *\*p<*0.05 and *\*\*p<*0.01 refers to statistically significant difference compared with the pristine PCL surface. The cell proliferation rate of ECs seeded on the gelatin-immobilized surfaces was significantly improved as compared to that the pristine PCL film.

The visualization of EC coverage on the functionalized PCL surfaces enabled a good assess‐ ment of the efficacy of endothelialization over the entire surface. Fig. 9 shows the represen‐ tative fluorescence images of LIVE/DEAD-stained ECs on the pristine PCL and functionalized PCL film surfaces after 7 days of culture. The sparse coverage of ECs on the pristine PCL substrate further confirmed the unfavorable surface properties of pristine PCL for cell adhesion and proliferation (Fig. 9b). Poor endothelialization was also observed on the aminolyzed PCL (Fig. 9c) and P(GMA)-grafted PCL surfaces (Fig. 9d). The dense growth of ECs on the PCL-*g*-P(GMA)1-*c*-gelatin (Fig. 9e) and PCL-*g*-P(GMA)2-*c*-gelatin (Fig. 9f) sur‐ faces indicated significant improvement in EC coverage for the gelatin-immobilized PCL surfaces. The observed denser coverage of ECs on the PCL-*g*-P(GMA)2-*c*-gelatin surfaces compared to the PCL-*g*-P(GMA)1-*c*-gelatin surfaces meant that the efficacy of endotheliali‐ zation is positively correlated to the amount of immobilized gelatin. Taken together, the re‐ sults suggest that the higher the surface concentration of immobilized gelatin, the better the endothelialization efficacy of the material within a given period of time.

of amine groups on the PCL surfaces leads to a positive effect on cell proliferation [23,30], albeit to a limited extent. Despite the improvement in surface hydrophilicity and roughness, the grafting of P(GMA) brushes onto the PCL film surfaces did not lead to an enhancement in EC proliferation behavior, which is probably associated with the cytotoxicity and mutage‐ nicity of epoxides groups to ECs [46]. Besides the fact that polymer surfaces with moderate

favorable for cell attachment and proliferation [47,48], other factors (e.g. biological cues) may also be required for positive cell interaction with material substrates. This hypothesis was confirmed by the observation that the gelatinized P(GMA)-grafted PCL substrates ex‐ hibited higher affinity and proliferation for ECs as compared to the surfaces that did not

In fact, the proliferation rates of the PCL-*g*-P(GMA)1-*c*-gelatin and PCL-*g*-P(GMA)2-*c*-gelatin surfaces were comparable to that of the gelatin-coated coverslips (positive controls). Cell prolif‐ eration on the gelatin-immobilized PCL surfaces was not only significantly enhanced, but also found to be positively correlated to the amounts of immobilized gelatin. The PCL-*g*-P(GMA)2 *c*-gelatin surface exhibited more pronounced enhancement in cell adhesion and proliferation than that of the PCL-*g*-P(GMA)1-*c*-gelatin surface, as the longer ATRP reaction time allowed for more gelatin to be attached. This result suggests that an increase in surface density of the immo‐ bilized gelatin can lead to an increase in EC proliferation over time. This phenomenon is proba‐ bly associated with the fact that immobilization of gelatin provides many epitopes or ligands for cell adhesion molecules, such as integrins, thus mimicking the natural extracellular environ‐

**Figure 8.** EC proliferation profile on the gelatin-coated coverslips, pristine PCL and functionalized PCL surfaces after 1, 3, 5 and 7 days of incubation at 37 oC in a 5% CO2 atmosphere as determined by the AlamarBlueTM(AB) assay. Data presented as means ± SD. *\*p<*0.05 and *\*\*p<*0.01 refers to statistically significant difference compared with the pristine PCL surface. The cell proliferation rate of ECs seeded on the gelatin-immobilized surfaces was significantly improved as

and rougher nano-topography are

hydrophilicity of water contact angles in a range of 30-70o

ment that is favorable for EC adhesion, spreading and proliferation.

contain the bioactive gelatin motifs.

192 Advances in Biomaterials Science and Biomedical Applications

compared to that the pristine PCL film.

**Figure 9.** Fluorescence images of LIVE/DEAD-stained ECs on the (a) gelatin-coated coverslips (positive control), (b) pristine PCL, (c) PCL-NH2, (d) PCL-*g*-P(GMA)2, (e) PCL-*g*-P(GMA)1-*c*-gelatin, and (f) PCL-*g*-P(GMA)2-*c*-gelatin after 7 days of incubation in cell suspension (2×104 cells/ml). Scale bar: 20 μm. Rapid endothelialization was observed for the gelatin-immobilized PCL surfaces.

#### **3.5. Blood compatibility tests**

#### *3.5.1. Hemolysis rate test*

Hemolysis rate is an important factor for characterization of the blood compatibility. The lower the hemolysis rate, the better the blood compatibility. Figure 10 shows the hemolysis rate of the pristine PCL and surface-functionalized PCL samples. It can be seen that the he‐ molysis rate of the functionalized samples has no substantial improvement. The gelatin-im‐ mobilized PCL substrates even show a relatively higher hemolysis rate than those of the pristine PCL and PCL-NH2 surfaces. This result is consistent with the previous findings that gelatin exhibited somewhat hemostatic effect by nature. However, the hemolysis rate of the gelatin-immobilized PCL samples is approximately 3%, far below the accepted threshold value of 5% for biomaterial applications. Thus, the gelatin-immobilized samples can be used as a novel material with good hemocompatibility.

**Figure 10.** Hemolysis rate of the pristine PCL and surface-functionalized PCL samples. Data presented as means ± SD, n=3.

#### *3.5.2. Coagulation activity on the bare and endothelialized PCL substrates*

Blood coagulation, particularly under conditions of relatively low flow, has been recognized to be one of the main problems of vascular occlusion [49]. Activated coagulation factors in‐ fluence the clotting time through extrinsic, intrinsic and common coagulation pathways. Prothrombin time (PT) is used to evaluate deficiencies in the extrinsic factor, and represents the time for blood plasma to clot after the addition of thromboplastin (activator of the extrin‐ sic pathway) [50]. Activated partial thromboplastin time (APTT) is used to evaluate the in‐ trinsic factors, such as VIII, IX, XI and XII, and common coagulation pathway factors V, X and II [50]. Both PT and APTT are commonly used to screen for adverse activation of the coagulation pathways on the vascular grafts and to evaluate their haemocompatibility in vi‐ tro. Thus, the PT and APTT values of the bare and endothelialized PCL substrates with vari‐ ous surface modifications were measured.

**3.5. Blood compatibility tests**

194 Advances in Biomaterials Science and Biomedical Applications

as a novel material with good hemocompatibility.

Hemolysis rate is an important factor for characterization of the blood compatibility. The lower the hemolysis rate, the better the blood compatibility. Figure 10 shows the hemolysis rate of the pristine PCL and surface-functionalized PCL samples. It can be seen that the he‐ molysis rate of the functionalized samples has no substantial improvement. The gelatin-im‐ mobilized PCL substrates even show a relatively higher hemolysis rate than those of the pristine PCL and PCL-NH2 surfaces. This result is consistent with the previous findings that gelatin exhibited somewhat hemostatic effect by nature. However, the hemolysis rate of the gelatin-immobilized PCL samples is approximately 3%, far below the accepted threshold value of 5% for biomaterial applications. Thus, the gelatin-immobilized samples can be used

**Figure 10.** Hemolysis rate of the pristine PCL and surface-functionalized PCL samples. Data presented as means ± SD,

Blood coagulation, particularly under conditions of relatively low flow, has been recognized to be one of the main problems of vascular occlusion [49]. Activated coagulation factors in‐ fluence the clotting time through extrinsic, intrinsic and common coagulation pathways. Prothrombin time (PT) is used to evaluate deficiencies in the extrinsic factor, and represents the time for blood plasma to clot after the addition of thromboplastin (activator of the extrin‐ sic pathway) [50]. Activated partial thromboplastin time (APTT) is used to evaluate the in‐ trinsic factors, such as VIII, IX, XI and XII, and common coagulation pathway factors V, X and II [50]. Both PT and APTT are commonly used to screen for adverse activation of the coagulation pathways on the vascular grafts and to evaluate their haemocompatibility in vi‐

*3.5.2. Coagulation activity on the bare and endothelialized PCL substrates*

*3.5.1. Hemolysis rate test*

n=3.

**Figure 11.** a) PT and (b) APTT results (means ± SD, n=3) for the bare and endothelialized surfaces of pristine PCL and surface-functionalized PCL, The coagulation activity of all surfaces was found to be in the normal range for healthy blood plasma.

The normal ranges of PT and APTT for healthy blood plasma are 12.0-14.5 s and 27.0-35.6 s, respectively [51]. Fig. 11 shows the PT and APTT results for the bare and endothelialized PCL substrates with various surface modifications. For the bare PCL and functionalized PCL surfaces, both PT and APTT are all within the normal ranges of coagulation time. None of the PCL substrates was found to affect the coagulation pathways significantly, and no discernible effect was observed in the presence of gelatin, indicating that surface functionali‐ zation activated neither the intrinsic nor the extrinsic coagulation pathways. This result is consistent with previous findings by other groups that cell-adhesive proteins and peptides do not affect or convert blood coagulation pathways [51,52]. Even after the PCL substrates were coated with a layer of ECs, the PT and APTT readings were still observed to be in the normal range of the clinical reference, and no significant differences in the coagulant activi‐ ties were observed on the endothelialized PCL substrates as compared to the bare PCL sub‐ strates. The results also revealed that the ECs cultured on the pristine PCL and functionalized PCL surfaces remained unactivated and did not exhibit procoagulation phe‐ notypes. Hence, it could be concluded that the presence of the monolayer of ECs had no ef‐ fect on the intrinsic or the extrinsic coagulation pathways.

#### *3.5.3. Nitric Oxide (NO) production*

Nitric oxide (NO) is an important regulator of vascular tone and platelet adhesion and the continuous NO release by ECs prevents thrombogenesis [53]. In this study, the NO secretion of the ECs on the pristine PCL and functionalized PCL surfaces were measured. As shown in Fig. 12, the amount of NO secreted by ECs on the gelatin-immobilized PCL surfaces was significantly higher than those on the pristine PCL, aminolyzed and P(GMA)-grafted PCL surfaces. The amount of NO production of the ECs seeded on the PCL-*g*-P(GMA)2-*c*-gelatin surface was around 2-fold higher than that on the PCL-*g*-P(GMA)1-*c*-gelatin surfaces, indi‐ cating that the improved NO production observed for ECs grown on the gelatin-immobi‐ lized PCL surface may be positively correlated to the amount of covalently immobilized gelatin. The above results suggest that a high density of immobilized gelatin led to the en‐ hancement in NO secretion.

**Figure 12.** The amount of NO production for the ECs seeded on the pristine and functionalized PCL substrates. Data presented as means ± SD, n=3. *\*p<*0.05 and *\*\*p<*0.01 corresponds to statistically significant difference as compared to the pristine PCL.

#### *3.5.4. Platelet activation on the bare and endothelialized PCL substrates*

Apart from coagulation pathways, platelet activation is considered another important crite‐ rion in assessing blood compatibility of the biomaterial surface. The activation of attached platelet results in platelet aggregation and the formation of a thrombus [54]. The subendo‐ thelial collagens (i.e., types I - IV) have been found to interact directly with platelets to trig‐ ger their activation for thrombogenic initiation [55]. As gelatin is a derivative of collagen, one downside of using gelatin-immobilized surfaces could be the detrimental adhesion and activation of platelets, which could initiate clotting. Therefore, the extent of platelet activa‐ tion by the different biomaterial surfaces was studied.

normal range of the clinical reference, and no significant differences in the coagulant activi‐ ties were observed on the endothelialized PCL substrates as compared to the bare PCL sub‐ strates. The results also revealed that the ECs cultured on the pristine PCL and functionalized PCL surfaces remained unactivated and did not exhibit procoagulation phe‐ notypes. Hence, it could be concluded that the presence of the monolayer of ECs had no ef‐

Nitric oxide (NO) is an important regulator of vascular tone and platelet adhesion and the continuous NO release by ECs prevents thrombogenesis [53]. In this study, the NO secretion of the ECs on the pristine PCL and functionalized PCL surfaces were measured. As shown in Fig. 12, the amount of NO secreted by ECs on the gelatin-immobilized PCL surfaces was significantly higher than those on the pristine PCL, aminolyzed and P(GMA)-grafted PCL surfaces. The amount of NO production of the ECs seeded on the PCL-*g*-P(GMA)2-*c*-gelatin surface was around 2-fold higher than that on the PCL-*g*-P(GMA)1-*c*-gelatin surfaces, indi‐ cating that the improved NO production observed for ECs grown on the gelatin-immobi‐ lized PCL surface may be positively correlated to the amount of covalently immobilized gelatin. The above results suggest that a high density of immobilized gelatin led to the en‐

**Figure 12.** The amount of NO production for the ECs seeded on the pristine and functionalized PCL substrates. Data presented as means ± SD, n=3. *\*p<*0.05 and *\*\*p<*0.01 corresponds to statistically significant difference as compared to

Apart from coagulation pathways, platelet activation is considered another important crite‐ rion in assessing blood compatibility of the biomaterial surface. The activation of attached platelet results in platelet aggregation and the formation of a thrombus [54]. The subendo‐

*3.5.4. Platelet activation on the bare and endothelialized PCL substrates*

fect on the intrinsic or the extrinsic coagulation pathways.

*3.5.3. Nitric Oxide (NO) production*

196 Advances in Biomaterials Science and Biomedical Applications

hancement in NO secretion.

the pristine PCL.

**Figure 13.** P-selectin expression for the (a) bare and (b) endothelialized surfaces of the pristine and functionalized PCL substrates. Plasma rich platelet (PRP) was used as positive control. *\*p<*0.05 and *\*\*p<*0.01 corresponds to statistically significant difference compared with the pristine PCL surface.

In this study, platelet activation on the bare and endothelialized PCL substrates was de‐ termined using the P-selectin assay, since P-selectin is one of intracellular granular mole‐ cules released upon platelet activation and stimulation [5], For the bare PCL substrates, the amount of activated platelets on the gelatin-immobilized PCL surfaces was compara‐ ble to those of the pristine PCL surfaces (Fig. 13a). In contrast, platelet activation was found to be significantly higher on the P(GMA)-grafted PCL surfaces, indicative of an in‐ creased risk for thrombogenesis. The results suggest that the immobilization of gelatin on the P(GMA)-grafted PCL surfaces not only rendered them with adhesion-promoting prop‐ erties, but also decreased the risk of inducing the activation of platelets. It has been re‐ ported previously that the biological motifs immobilized on the polymers could not bind effectively with the platelet integrin unless their separation distances was between 1.48-2.2 nm [56], and that polymers with small spacer, such as lauric acid-conjugated GRGDS, ex‐ hibited no increase in activation [57]. Here, the gelatin was directly conjugated onto the grafted P(GMA) brushes (small spacer), and thus the gelatin motif could not gain access to the binding sites of the platelet integrin (such as α2β1). In addition, it is probable that the other surface properties (e.g. enhanced hydrophilicity) were also responsible for re‐ duced platelet activation activity.

In the case of the endothelialized PCL substrates, the amount of activated platelets on the gelatin-immobilized PCL surfaces was significantly reduced with respect to the other endo‐ thelialized PCL substrates (Fig. 13b), indicative of good anti-thrombogenic behavior of the EC confluent layer. This result is consistent with the high level of NO production by ECs on the gelatinized PCL surface. The P-selectin expression on the endothelialized pristine PCL and PCL-NH2 surfaces was higher than those on the bare substrates (Fig. 13b), which is line with the well-established fact that subconfluent EC layers were more thrombogenic in na‐ ture [13]. The platelet activation was significantly enhanced on the endothelialized P(GMA) grafted PCL surfaces, as observed by the high levels of P-selectin expression, which is an indication of an increased risk of thrombogenesis for those surfaces. Overall, the above re‐ sults showed that the thrombogenicity of a biomaterial is influenced by both EC confluency and the surface properties of the biomaterial. Consequently, it can be concluded that the im‐ mobilization of gelatin on the P(GMA) brushes prevented platelet activation, but that the presence of the P(GMA) brushes alone led to a pro-thrombogenic surface.

#### *3.5.5. Expression and activity of vWF and MMP-2 of EC on the surface-functionalized PCL samples*

In order to further investigate the thrombogenicity of endothelialized surfaces, we per‐ formed real-time PCR tests and protein immunoblotting on factors that mediate platelet ad‐ hesion to ECs. The expression of von Willebrand factor (vWF) on endothelial cells promotes platelet adhesion and high or abnormal expression of vWF has been implicated in pathologi‐ cal conditions such as thrombosis [58]. Matrix metalloproteinase-2 (MMP-2) is another factor known to be involved in platelet aggregation, as well as to have important roles in the deg‐ radation and remodeling of the endothelial extracellular matrix [59, 60]. 7 days after the seeding of ECs, the relative expression of both vWF and MMP-2 mRNA in the EC on both PCL-*g*-P(GMA)1-*c*-gelatin and PCL-*g*-P(GMA)2-*c*-gelatin surfaces were downregulated when compared to the ECs on PCL-*g*-P(GMA) surfaces and gelatin-coated coverslips (Fig. 14a and 14c). Immunoblotting of the vWF protein produced in ECs, also, suggest that it is lower in ECs on PCL-*g*-P(GMA)- *c*-gelatin surfaces in comparison to PCL-*g*-P(GMA) surfa‐ ces but differed where the vWF expression of ECs on the pristine PCL surface and gelatincoated coverslip could not be detected (Fig. 14b). Nevertheless, these results suggest that pro-thrombogenic factors could be increased on bare PCL-*g*-P(GMA) surfaces and the conju‐ gation of gelatin could help to reduce thrombogenicity.

Amelioration of Blood Compatibility and Endothelialization of Polycaprolactone Substrates by… http://dx.doi.org/10.5772/52646 199

**Figure 14.** Real-time qPCR revealed that the expression of (a) vWF and (c) MMP-2 in ECs on PCL-*g*-P(GMA)-*c*-gelatin surfaces is lower when compared to PCL-*g*-P(GMA) surfaces and gelatin-coated coverslips. Expression levels are nor‐ malized using the housekeeping gene rpl27 and taken relative to ECs on pristine PCL (dotted line) (mean ± SD, n=3). Endothelial cells treated with TNF-αfor 6 h were used as a positive control for the expression of both genes. (c) Immu‐ noblotting of vWF protein expressed in ECs on PCL-*g*-P(GMA)-*c*-gelatin is also reduced when compared to PCL-*g*-P(GMA) surfaces, thus corroborating the real-time PCR results.

#### **4. Conclusion**

ported previously that the biological motifs immobilized on the polymers could not bind effectively with the platelet integrin unless their separation distances was between 1.48-2.2 nm [56], and that polymers with small spacer, such as lauric acid-conjugated GRGDS, ex‐ hibited no increase in activation [57]. Here, the gelatin was directly conjugated onto the grafted P(GMA) brushes (small spacer), and thus the gelatin motif could not gain access to the binding sites of the platelet integrin (such as α2β1). In addition, it is probable that the other surface properties (e.g. enhanced hydrophilicity) were also responsible for re‐

In the case of the endothelialized PCL substrates, the amount of activated platelets on the gelatin-immobilized PCL surfaces was significantly reduced with respect to the other endo‐ thelialized PCL substrates (Fig. 13b), indicative of good anti-thrombogenic behavior of the EC confluent layer. This result is consistent with the high level of NO production by ECs on the gelatinized PCL surface. The P-selectin expression on the endothelialized pristine PCL and PCL-NH2 surfaces was higher than those on the bare substrates (Fig. 13b), which is line with the well-established fact that subconfluent EC layers were more thrombogenic in na‐ ture [13]. The platelet activation was significantly enhanced on the endothelialized P(GMA) grafted PCL surfaces, as observed by the high levels of P-selectin expression, which is an indication of an increased risk of thrombogenesis for those surfaces. Overall, the above re‐ sults showed that the thrombogenicity of a biomaterial is influenced by both EC confluency and the surface properties of the biomaterial. Consequently, it can be concluded that the im‐ mobilization of gelatin on the P(GMA) brushes prevented platelet activation, but that the

presence of the P(GMA) brushes alone led to a pro-thrombogenic surface.

gation of gelatin could help to reduce thrombogenicity.

*3.5.5. Expression and activity of vWF and MMP-2 of EC on the surface-functionalized PCL samples*

In order to further investigate the thrombogenicity of endothelialized surfaces, we per‐ formed real-time PCR tests and protein immunoblotting on factors that mediate platelet ad‐ hesion to ECs. The expression of von Willebrand factor (vWF) on endothelial cells promotes platelet adhesion and high or abnormal expression of vWF has been implicated in pathologi‐ cal conditions such as thrombosis [58]. Matrix metalloproteinase-2 (MMP-2) is another factor known to be involved in platelet aggregation, as well as to have important roles in the deg‐ radation and remodeling of the endothelial extracellular matrix [59, 60]. 7 days after the seeding of ECs, the relative expression of both vWF and MMP-2 mRNA in the EC on both PCL-*g*-P(GMA)1-*c*-gelatin and PCL-*g*-P(GMA)2-*c*-gelatin surfaces were downregulated when compared to the ECs on PCL-*g*-P(GMA) surfaces and gelatin-coated coverslips (Fig. 14a and 14c). Immunoblotting of the vWF protein produced in ECs, also, suggest that it is lower in ECs on PCL-*g*-P(GMA)- *c*-gelatin surfaces in comparison to PCL-*g*-P(GMA) surfa‐ ces but differed where the vWF expression of ECs on the pristine PCL surface and gelatincoated coverslip could not be detected (Fig. 14b). Nevertheless, these results suggest that pro-thrombogenic factors could be increased on bare PCL-*g*-P(GMA) surfaces and the conju‐

duced platelet activation activity.

198 Advances in Biomaterials Science and Biomedical Applications

This study described the successful biofunctionalization of PCL substrates with tunable sur‐ face densities of covalently-immobilized gelatin by surface-initiated ATRP of glycidyl meth‐ acrylate (GMA). Kinetics studies revealed that the grafting yield of the functional P(GMA) brushes increased linearly with polymerization time, and the amount of immobilized gelatin increased with the concentration of epoxide groups on the P(GMA) brushes. The significant improvement in the adhesion and proliferation of ECs on the gelatin-immobilized PCL sub‐ strates were found to be positively correlated to the amount of covalently immobilized gela‐ tin. Blood compatibility tests demonstrated that the ECs cultured on the gelatinimmobilized-P(GMA) surfaces exhibited low platelet activation and significantly increased nitric oxide (NO) production, although the coagulation pathways were not affected both be‐ fore and after EC coverage. Overall, the high surface-density of immobilized gelatin ob‐ tained by surface-initiated ATRP on the PCL surfaces is favorable for EC attachment and proliferation. The attached ECs maintained an unactivated and non-thrombogenic pheno‐ type that mimics the EC lining of a healthy blood vessel. Hence, such a surface may have huge potential for vascular graft applications.
