Fabrication of Poly(pentaerythritol tetrakis (3-mercaptopropionate) / dipentaerythritol penta- / hexa-acrylate)HIPEs Macroporous Sca ﬀ old with Alpha Hydroxyapatite via Photopolymerization for Fibroblast Regeneration

: Synthetic biomaterials that can be structured into porous sca ﬀ olds for support cell growth have played a role in developing the ﬁeld of tissue engineering. This research focused on combination of biodegradable emulsion template along with the assisting of low-cost polymerization reaction. The appendage of ester-based surfactant, Hypermer B246, played a vital role which gave an outstanding dispersion in HIPEs system and degradability. PolyHIPEs were prepared by using domestic ultraviolet light source for producing a multiscale porosity material. The morphology showed a promising result of poly(pentaerythritol tetrakis (3-mercaptopropionate) / dipentaerythritol penta- / hexa-acrylate)HIPEs with varied Hypermer B246 surfactant concentration resulting in the pores size increased in between 51.2 ± 9.8 µ m to 131.4 ± 26.32 µ m. Cellular moieties of poly(TT / DPEHA) HIPEs were conﬁrmed by using SEM while inclusion of hydroxyapatite were conﬁrmed by SEM, FTIR and EDX-SEM and quantiﬁed by thermogravimetric analysis. The maximum stress and compressive modulus of the obtained materials were signiﬁcantly enhanced with HA up to ﬁve percent by weight. Poly(TT / DPEHA)HIPEs with HA showed the ability for the cell attachment and the adhesion / proliferation of the cells, suggested that poly(TT / DPEHA) HIPEs with HA were suitable for biomaterial application. M.I.A., N.K., J.P., M.N., P.S.; M.I.A., N.K., J.P., M.N.,


Introduction
Emulsions are heterogeneous mixtures of at least one immiscible liquid dispersed in another in the form of droplets [1]. In most cases, at least one of the liquids will be water or an aqueous solution. An emulsion is often described as oil-in-water (O/W) or water-in-oil (W/O) where the first phase mentioned refers to the internal (or dispersed) phase. Emulsion templating is one of the methods for developing porous materials stabilized by the presence of surfactant. This method always involved for the formation of high-internal-phase-emulsions (HIPEs) which comprised of the internal phase more than 74% of the total volume of the system [2]. Emulsion templating is a flexible and easily controlled method for fabrication of mesopore and macropore materials (pore size range 5-100 µm). If a less of HA concentration towards the biocompatibility, mechanical strength, thermal stability degradability and morphologic properties of the polyHIPEs. The feasibility of adding hydroxyapatite towards polyHIPEs improve biocompatibility of the polyHIPEs and mechanical properties which are vital for the better tissue engineering research. As far as we concern, this research emphasizes the usage of degradable monomers such as DPEHA and TT is shown in Figure 1. Interestingly, this research also emphasized the incorporation of ester-based surfactant Hypermer B246 due to its dispersion behavior in the emulsion system and abundance of ester bonds which make it easy to degrade. The surfactant Hypermer B246 was chosen not only because of its chemical nature, but it also emulsified efficiently in the polyHIPEs system. In addition, ultraviolet (UV) light was favored because of the more rapid radical polymerization and able to complete the reaction in a shorter time compared to the conventional method. It was very interesting to further explore the preparation of degradable polyHIPEs using photopolymerization such as UV light for bone cell cultures template.
Crystals 2020, 10, x FOR PEER REVIEW 3 of 18 The aim of this study is to demonstrate the preparation of degradable polyHIPEs from thiol-ene reaction for bone tissue template. In addition, the main purpose of this study is to investigate the effect of HA concentration towards the biocompatibility, mechanical strength, thermal stability degradability and morphologic properties of the polyHIPEs. The feasibility of adding hydroxyapatite towards polyHIPEs improve biocompatibility of the polyHIPEs and mechanical properties which are vital for the better tissue engineering research. As far as we concern, this research emphasizes the usage of degradable monomers such as DPEHA and TT is shown in Figure 1. Interestingly, this research also emphasized the incorporation of ester-based surfactant Hypermer B246 due to its dispersion behavior in the emulsion system and abundance of ester bonds which make it easy to degrade. The surfactant Hypermer B246 was chosen not only because of its chemical nature, but it also emulsified efficiently in the polyHIPEs system. In addition, ultraviolet (UV) light was favored because of the more rapid radical polymerization and able to complete the reaction in a shorter time compared to the conventional method. It was very interesting to further explore the preparation of degradable polyHIPEs using photopolymerization such as UV light for bone cell cultures template.

Methodology
Preparation of Poly(TT/DPEHA/HA)HIPEs The required amount of Hypermer B246 (2.5, 2.7, and 3 wt% of organic phase) was dissolved by 1,2-dichloroethane in a multi-neck flask. Then, TT and DPEHA (organic phase) were added in the ratio of 60:40 by volume and stirred at 300 rpm with a magnetic bar. Diphenyl (2,4,6-trimethylbenzoyl) phosphine oxide/2-hydroxy-2-methylpropiophenone (initiator) was added to the solution and stirred well. After that, the aqueous phase which composed of distilled water, CaCl 2 and HA (0, 5, 10, 15 wt%) was added dropwise into the multi-neck flask. The emulsion was homogenized for 10-15 min. The emulsion of organic phase and aqueous phase was poured into a cylindrical glass vial and further polymerized in the UV chamber with a power output 25 W/cm 2 . Polymerized material was removed from the vials and the remained monomers were extracted using methanol for 6 h before dried in a convection oven at 60 • C for 48 h.

Morphologic and Chemical Properties
Surface morphology of the polyHIPEs was investigated by FE-SEM (Hitachi S-4800, Tokyo, Japan) at the voltage of 2.0-5.0 kV. Samples were coated with platinum on a sputter coater prior to the analysis. ATR-FTIR spectra of the samples were obtained by using the Thermo Scientific Nicolet iS5. The selected spectrum resolution and scanning range employed were 4 cm −1 and 4000-600 cm −1 , respectively. The FTIR spectra with percentage transmittance versus wavelength (cm −1 ) were acquired after the scanning process. In addition, thermal properties with DTG data were collected by using NETZSCH STA 449 F3 Jupiter instrument. Samples were placed in the alumina crucible and heated from 40 to 800 • C, at heating rate of 10 • C/min under N 2 flow of 100 mL/min. The degradation temperature was determined at weight loss of 50% from weight loss versus temperature curve.

Mechanical Properties
Lloyd Universal Testing Machine (Lloyd Ametek LRX Tensile Tester, San Diego, CA, USA) was used to measure the mechanical properties of all samples in compression mode. Cylinder shape test specimens, 2.54-cm-diameter × 2.54-cm in length, were prepared. A speed of 0.127 cm/min and 500-N load cells were used for all measurements. The value of the compression stress and Young's modulus were determined from an average of five samples. Degradation test of polyHIPEs was investigated according to ASTM F1635. The samples were cut into 0.5 × 0.5 × 0.5 cm for the tests. The samples were fully dried for 48 h and weighed prior to immersed into phosphate buffer saline (PBS) solution in a beaker. The beakers with the samples inside were placed in a water bath at 37 • C for 55 days. The samples were taken off from the water bath and dabbed dry with tissue paper to remove excess water from the surface of the samples. After this, the samples were dried in an oven for 48 h and reweighed every week. Mass loss of a sample was determined by the following Equation (1): where W a and W b are weights after and before immersed into distilled water, respectively.

Cell Toxicity and Proliferation
Cell cytotoxicity test was carried out by using MTT (Sigma Aldrich, St. Louis, MO, USA) assay. L-929 cells (fibroblast cell, L929: ECACC, Salisbury, UK) were seeded at 1.5 × 10 4 in a 48-well plate overnight (total volume 200 µL/well). The samples were incubated for one night. MTT solution was added (concentration 5 mg/mL) 20 µL/well and incubated at 37 • C for 4 h in CO 2 Incubator. Purple formazan was dissolved using isopropanol with HCl. Measurements were carried out at 540-nm by microplate and the calculation of cell viability is shown in Equation (2).
Cell proliferation of L-929 cells (fibroblast cell) were seeded at 5000 cells in 48-well plates and 3 plates were employed (total volume 200 µL/well). The cells were treated with bioactive and the 1st, 2nd and 3rd plate were incubated for 2 h, 24 h and 48 h, respectively. Cell cytotoxicity measurements were recorded. MTT solution was added (concentration 5 mg/mL) 20 µL/well and incubated at 37 • C for 4 h in CO 2 incubator. The solution was moved to 96-well plates (100 µL/well). Measurements were carried out using UV light at 540-nm wavelength by a microplate reader [17]. The obtained poly(TT/DPEHA)HIPEs with the ratio 60:40 of TT/DPEHA monomer and 80% porosity were characterized by using a scanning electron microscope (SEM) to determine the average pore size and morphology. Poly(TT/DPEHA)HIPEs morphology in Figure 2a-c showed spherical pore, homogenous pore structure with interconnected pore. In order to improve polyHIPEs properties, there are many factors that could affect pore size and interconnected pore and one of these factors is the surfactant concentration. Figure 2 showed the effect of surfactant concentration on the pore size and interconnected pore. Average pore size of poly(TT/DPEHA)HIPEs was analyzed and estimated by measuring the diameter of 50 randomly chosen pores using SemAfore software. SEM micrographs also showed that decreasing amount of Hypermer B246 at 3 wt%, 2.7 wt% and 2.5 wt% affected the average pore size of the poly(TT/DPEHA)HIPEs, the average pore size increased from 51.2 ± 9.8 µm, 103 ± 10.7 µm and 131.4 ± 26.3 µm, respectively. This was because of the destabilization of emulsion led to the coalescence of the droplets in the aqueous phase resulted in the larger average pore size [18]. The poly(TT/DPEHA)HIPEs were successfully prepared using various amount of aqueous phases (80 vol%, 90 vol% and 92 vol%) with the same monomer ratios and surfactant concentration at 60:40 and 3 wt%, respectively. Morphology of poly(TT/DPEHA)HIPEs in Figure 3(a1-c2) also showed spherical pore, homogenous pore structure with interconnected pore. Average pore size prepared from 80 vol%, 90 vol% and 92 vol% of aqueous phase were 51.2 ± 9.8 µm, 63 ± 14.6 µm and 99.9 ± 27.6 µm, respectively. These results suggested that at the same amount of surfactant and increased of aqueous phase led to the increased of the average pore size of the polyHIPEs. This was due to the number of surfactant molecules in the emulsion was insufficient to stabilize the increased amount of aqueous phase resulted in a larger droplet hence the larger pores size [19].

Effect of Aqueous Phase on Poly(TT/DPEHA)HIPEs Morphology
The poly(TT/DPEHA)HIPEs were successfully prepared using various amount of aqueous phases (80 vol%, 90 vol% and 92 vol%) with the same monomer ratios and surfactant concentration at 60:40 and 3 wt%, respectively. Morphology of poly(TT/DPEHA)HIPEs in Figure 3(a1-c2) also showed spherical pore, homogenous pore structure with interconnected pore. Average pore size prepared from 80 vol%, 90 vol% and 92 vol% of aqueous phase were 51.2 ± 9.8 µm, 63 ± 14.6 µm and 99.9 ± 27.6 µm, respectively. These results suggested that at the same amount of surfactant and increased of aqueous phase led to the increased of the average pore size of the polyHIPEs. This was due to the number of surfactant molecules in the emulsion was insufficient to stabilize the increased amount of aqueous phase resulted in a larger droplet hence the larger pores size [19].
This phenomenon related to the Ostwald ripening which explains accordingly about the average droplet sizes and distribution of droplet sizes displayed a growingly uneven trend with the addition of the aqueous phase fraction as all the samples were prepared using the same amount of surfactant, hence the increment of internal phase fraction caused the surplus amount of droplets which were available for the surfactant molecules in the HIPE system thermodynamically driven spontaneous process [18]. The increasing of aqueous phase of polyHIPE from 80 vol% to 92 vol%, increasing size of water droplets, affected to low stability (or destabilization) of emulsion, water droplets coalescence and Ostwald ripening thus the thickness of walls. On the other hand, the aqueous phase of polyHIPE at 80 vol% or the high organic: aqueous ratio, small water droplets, low degree of overlapping among voids affected the small size of the interconnected pores [20]. This phenomenon related to the Ostwald ripening which explains accordingly about the average droplet sizes and distribution of droplet sizes displayed a growingly uneven trend with the addition of the aqueous phase fraction as all the samples were prepared using the same amount of surfactant, hence the increment of internal phase fraction caused the surplus amount of droplets which were available for the surfactant molecules in the HIPE system thermodynamically driven spontaneous process [18]. The increasing of aqueous phase of polyHIPE from 80 vol% to 92 vol%, increasing size of water droplets, affected to low stability (or destabilization) of emulsion, water droplets coalescence and Ostwald ripening thus the thickness of walls. On the other hand, the aqueous phase of polyHIPE at 80 vol% or the high organic: aqueous ratio, small water droplets, low degree of overlapping among voids affected the small size of the interconnected pores [20].

Effect of Hydroxyapatite on Poly(TT/DPEHA)HIPEs Morphology
Poly(TT/DPEHA/HA)HIPEs filled with hydroxyapatite (HA) were successfully prepared. The amount of HA added to poly(TT/DPEHA/HA)HIPEs resulted in a non-homogeneous pore structure or the pore size distribution and the pores were randomly distributed (See Figure (a1-d2)). As the amount of HA increased up to 5 wt%, pore sizes of poly(TT/DPEHA/HA)HIPEs were increased from

Effect of Hydroxyapatite on Poly(TT/DPEHA)HIPEs Morphology
Poly(TT/DPEHA/HA)HIPEs filled with hydroxyapatite (HA) were successfully prepared. The amount of HA added to poly(TT/DPEHA/HA)HIPEs resulted in a non-homogeneous pore structure or the pore size distribution and the pores were randomly distributed (See Figure 4(a1-d2)). As the amount of HA increased up to 5 wt%, pore sizes of poly(TT/DPEHA/HA)HIPEs were increased from 99.9 ± 27.6 µm to 107.78 ± 57.4 µm as shown in Figure 4(b1,b2) because of the destabilization of emulsion [21]. Moreover, the increase amount of hydroxyapatite gave a larger pore size, rough surface and more distinctly interconnected pores which could affect cellular infiltration in scaffolds [22]. As the amount of HA increased to more than 5 wt%, poly(TT/DPEHA/HA)HIPEs showed nonhomogeneous dispersions of aqueous phase caused by high viscosity of the emulsion. In addition, with the increment amount of HA, leading to the high shear stress of mixing, emulsion was unable to break up the large droplets. It means that by lowering the concentration of HA to a certain level, coalescence would decrease between droplets of the emulsion which ultimately would obstruct the size that they grow to and resulted in smaller size pores [23]. On the other hand, heightening amount of HA caused abundance of phosphorus and calcium clots covered on surface of the polyHIPEs and led to local stress on the sample.
surface and more distinctly interconnected pores which could affect cellular infiltration in scaffolds [22]. As the amount of HA increased to more than 5 wt%, poly(TT/DPEHA/HA)HIPEs showed nonhomogeneous dispersions of aqueous phase caused by high viscosity of the emulsion. In addition, with the increment amount of HA, leading to the high shear stress of mixing, emulsion was unable to break up the large droplets. It means that by lowering the concentration of HA to a certain level, coalescence would decrease between droplets of the emulsion which ultimately would obstruct the size that they grow to and resulted in smaller size pores [23]. On the other hand, heightening amount of HA caused abundance of phosphorus and calcium clots covered on surface of the polyHIPEs and led to local stress on the sample.  Scanning electron microscopy (SEM) and energy dispersive X-ray analysis (EDX) were used to identify the dispersion and the distribution of the HA added to poly(TT/DPEHA/HA)HIPEs. HA is a calcium phosphate compound which has calcium and phosphorus as the major compositional elements. The distribution of the elements from the hydroxyapatite on the surface of poly(TT/DPEHA/HA)HIPEs is shown in Figure 5a   PO − from HA which corresponded to the phosphate moiety [24]. Poly(TT/DPEHA/HA)HIPEs spectra also show a sharp peaks at 1730 cm −1 corresponded to the C=O stretching and 1100 cm −1 which is corresponded to C-O bond peak stretching and C-H stretching at 2853 cm −1 transmittance [25]. When comparing between spectra of poly(TT/DPEHA)HIPEs with spectra from poly(TT/DPEHA/HA)HIPEs the presence of phosphate at 1020 cm −1 wavelength were clearly observed in poly(TT/DPEHA/HA)HIPEs and not in poly(TT/DPEHA)HIPEs spectra.

Thermogravimetric Analysis
Thermogravimetric analysis or TGA was used to analyze the decomposition temperature of poly(TT/DPEHA/HA)HIPEs and confirmed the presence of HA particles in the polyHIPEs. The results showed facile conclusion about negative decomposition of HA within the range of thermal testing as shown accordingly. For the polyHIPEs with different amount of HA, the results illustrated that the polymer degraded approximately within the range of temperature between 300-460 °C. In comparison between poly(TT/DPEHA)HIPEs and poly(TT/DPEHA/HA)HIPEs, the results revealed that poly(TT/DPEHA)HIPEs showed a higher onset temperature compared to the poly(TT/DPEHA/HA)HIPEs (see Table 1 and Figure 7). The polymer degradation started between 330-322 °C because HA particles embedded in the polymer matrix were non-homogenous which influenced the onset to be slightly different [26]. Table 1 also shows that the decomposition of polyHIPEs gradually decreased as increasing of HA weight percentage between 0-15 wt% at 94.21%, 90.31%, 84.22% and 77.15%. From the decomposition results, it could be concluded that increasing of HA weight percent in the polyHIPEs led to the high amount of unscathed residues as the polyHIPEs were composed of organic and inorganic compounds [27].

Thermogravimetric Analysis
Thermogravimetric analysis or TGA was used to analyze the decomposition temperature of poly(TT/DPEHA/HA)HIPEs and confirmed the presence of HA particles in the polyHIPEs. The results showed facile conclusion about negative decomposition of HA within the range of thermal testing as shown accordingly. For the polyHIPEs with different amount of HA, the results illustrated that the polymer degraded approximately within the range of temperature between 300-460 • C. In comparison between poly(TT/DPEHA)HIPEs and poly(TT/DPEHA/HA)HIPEs, the results revealed that poly(TT/DPEHA)HIPEs showed a higher onset temperature compared to the poly(TT/DPEHA/HA)HIPEs (see Table 1 and Figure 7). The polymer degradation started between 330-322 • C because HA particles embedded in the polymer matrix were non-homogenous which influenced the onset to be slightly different [26]. Table 1 also shows that the decomposition of polyHIPEs gradually decreased as increasing of HA weight percentage between 0-15 wt% at 94.21%, 90.31%, 84.22% and 77.15%. From the decomposition results, it could be concluded that increasing of HA weight percent in the polyHIPEs led to the high amount of unscathed residues as the polyHIPEs were composed of organic and inorganic compounds [27].

Degradation Test
Currently, various methodologies have been developed to prepare biodegradable porous polymeric materials. A large number of researchers predesigned greener templates which at least avoided the use of hazardous inorganic material or poisonous solvents [28,29]. Figure 8 revealed the percentage mass loss (%) and days taken to degrade towards different volume percentage of the aqueous phase of poly(TT/DPEHA)HIPEs. The plot illustrated the increased degradation in 55-day period, which explains that the effect of hydrolytic degradation has been taken place in those period. Moreover, poly(TT/DPEHA)HIPEs with 90 vol% aqueous phase displayed the higher percentage of mass loss (%) due to the higher amount of porosity and the larger surface area which enhanced the degradation of the sample. In biodegradable poly(TT/DPEHA)HIPEs with lower surface area, they tended not to breakdown easily and did not experienced any rapid degradation [29]. In tissue engineering application, it was suggested that biodegradable materials used in the application needed to maintain their integrity from degradation during the bone regenerating periods so that they can optimize the rejuvenation of the treated bone and then gradually degrade as needed [29]. In this respect, it explains why the degradation of the sample must be slow and consistence throughout the material. Cells need more time to generate while adapt with the co-culture environment, so it may be explained the need for poly(TT/DPEHA/HA)HIPEs with the moderate rate of degradation. The degradation test of poly(TT/DPEHA/HA)HIPEs showed the slow mass loss rate and the maximum mass loss at 7% was suitable for the scaffolds application as stated by Christopher and coworker whose research on the evaluation of polycaprolactone scaffold degradation required gentle and late mass loss combined with long term biocompatibility and bone regeneration [30].

Degradation Test
Currently, various methodologies have been developed to prepare biodegradable porous polymeric materials. A large number of researchers predesigned greener templates which at least avoided the use of hazardous inorganic material or poisonous solvents [28,29]. Figure 8 revealed the percentage mass loss (%) and days taken to degrade towards different volume percentage of the aqueous phase of poly(TT/DPEHA)HIPEs. The plot illustrated the increased degradation in 55-day period, which explains that the effect of hydrolytic degradation has been taken place in those period. Moreover, poly(TT/DPEHA)HIPEs with 90 vol% aqueous phase displayed the higher percentage of mass loss (%) due to the higher amount of porosity and the larger surface area which enhanced the degradation of the sample. In biodegradable poly(TT/DPEHA)HIPEs with lower surface area, they tended not to breakdown easily and did not experienced any rapid degradation [29]. In tissue engineering application, it was suggested that biodegradable materials used in the application needed to maintain their integrity from degradation during the bone regenerating periods so that they can optimize the rejuvenation of the treated bone and then gradually degrade as needed [29]. In this respect, it explains why the degradation of the sample must be slow and consistence throughout the material. Cells need more time to generate while adapt with the co-culture environment, so it may be explained the need for poly(TT/DPEHA/HA)HIPEs with the moderate rate of degradation. The degradation test of poly(TT/DPEHA/HA)HIPEs showed the slow mass loss rate and the maximum mass loss at 7% was suitable for the scaffolds application as stated by Christopher and coworker whose research on the evaluation of polycaprolactone scaffold degradation required gentle and late mass loss combined with long term biocompatibility and bone regeneration [30]. Crystals 2020, 10, x FOR PEER REVIEW 12 of 18

Compression Test
One of the important properties of polyHIPEs for tissue engineering is the ability to withstand force without breaking. The mechanical property of porous poly(TT/DPEHA)HIPEs were determined by stress/strain curves (see Figure 9). All the poly(TT/DPEHA)HIPEs exhibited uniaxial tensile stressstrain profiles were classified as ductile materials [31]. Table 2 shows that mechanical properties the poly(TT/DPEHA/HA)HIPEs enhanced with hydroxyapatite were able to withstand compressive modulus between 4.8-6.2 MPa which is suitable for supporting mandible trabecular bones. From the earlier research, it was stated that trabecular bone ultimate compressive strength range is from 0.22 to 10.44 MPa. Meanwhile, the suitable young's modulus mean value range from 3.9-199.5 MPa depending on the bone types. It was observed that the stress at maximum load and compressive modulus were significantly enhanced with the increasing of HA up to 5 wt% due to the reinforcement induced by the inclusion of HA into polyHIPEs [21,32]. Conversely, excessive amount of HA particles (>5 wt%) showed decreasing both the stress at maximum load and the compressive modulus. This may due to two main factors, one factor was agglomeration of HA creating the weak point in porous structure [33] and another one was the larger pore size led to the lower stress transfer [34].

Compression Test
One of the important properties of polyHIPEs for tissue engineering is the ability to withstand force without breaking. The mechanical property of porous poly(TT/DPEHA)HIPEs were determined by stress/strain curves (see Figure 9). All the poly(TT/DPEHA)HIPEs exhibited uniaxial tensile stress-strain profiles were classified as ductile materials [31]. Table 2 shows that mechanical properties the poly(TT/DPEHA/HA)HIPEs enhanced with hydroxyapatite were able to withstand compressive modulus between 4.8-6.2 MPa which is suitable for supporting mandible trabecular bones. From the earlier research, it was stated that trabecular bone ultimate compressive strength range is from 0.22 to 10.44 MPa. Meanwhile, the suitable young's modulus mean value range from 3.9-199.5 MPa depending on the bone types. It was observed that the stress at maximum load and compressive modulus were significantly enhanced with the increasing of HA up to 5 wt% due to the reinforcement induced by the inclusion of HA into polyHIPEs [21,32]. Conversely, excessive amount of HA particles (>5 wt%) showed decreasing both the stress at maximum load and the compressive modulus. This may due to two main factors, one factor was agglomeration of HA creating the weak point in porous structure [33] and another one was the larger pore size led to the lower stress transfer [34].

Cell Cytotoxicity by Using MTT Assay
Result in Figure 10 shows

Cell Cytotoxicity by Using MTT Assay
Result in Figure 10

Cell Cytotoxicity by Using MTT Assay
Result in Figure 10 shows

Cell Proliferation by Using MTT Assay
Typically, the L-929 cells are approximately 5-10 µm. Where the average pore size of poly(TT/DPEHA)HIPEs with 0-HA was 99.9 ± 27.6 µm and 5-HA was 107.78 ± 57.4 µm. The L-929 cells were able to penetrate though the pores and the interconnected pores of poly(TT/DPEHA)HIPEs. In this test, the effect of HA on the cell proliferation could be determined by MTT assay. In the bioanalysis of cell proliferation test, usually the fibroblast will first come in contact with the surface of culture media and they will incessantly attach, adhere and spread on it. The L-929 fibroblast cells were extracted from the cell grown on polyHIPEs samples and were continued to feed in medium at 24 and 48 h. Figure 11 shows

Cell Proliferation by Using MTT Assay
Typically, the L-929 cells are approximately 5-10 µm. Where the average pore size of poly(TT/DPEHA)HIPEs with 0-HA was 99.9 ± 27.6 µm and 5-HA was 107.78 ± 57.4 µm. The L-929 cells were able to penetrate though the pores and the interconnected pores of poly(TT/DPEHA)HIPEs. In this test, the effect of HA on the cell proliferation could be determined by MTT assay. In the bioanalysis of cell proliferation test, usually the fibroblast will first come in contact with the surface of culture media and they will incessantly attach, adhere and spread on it. The L-929 fibroblast cells were extracted from the cell grown on polyHIPEs samples and were continued to feed in medium at 24 and 48 h. Figure 11 shows the results of cell proliferation in poly(TT/DPEHA)HIPEs with different amount of HA within 24 and 48 h period. In 24 h, cell proliferation were recorded, 0-HA of poly(TT/DPEHA)HIPE disclosed the cell proliferation of 0.90 ± 0.06 in 24 h and 0.86 ± 0.06 in 48 h. In contrast, poly(TT/DPEHA)HIPEs with 5% of HA showed constructive cell growth with cell proliferation at 1.10 ± 0.00 and increased after 48 h to 2.12 ± 0.21. Nevertheless, chemical nature and topography of the materials used for the development of cell in this study favored cell-material interactions (See Figure 12(a1-b3)). The abundancy of open cell fabricated in poly(TT/DPEHA/HA)HIPEs sample body were able to increase the cell growth. This can be attributed to the nanodimensions of the HA as well as the compatibility for both the HA and poly(TT/DPEHA)HIPEs. These behaviors helped to correlate protein adsorption and contributed for the cellular adhesion [35]. The incorporation of 5-HA in poly(TT/DPEHA)HIPEs really benefits for L-929 cell proliferation as shown in Figure 12(b3). It shows the changed of fibroblast cell shape from round-like and flattened Figure 12(b1) to more elongated spindle-like shaped cells. In addition, Figure 12(b3) possessing extending out from the ends of the cell body. Nevertheless, chemical nature and topography of the materials used for the development of cell in this study favored cell-material interactions (See Figure 12(a1-b3)). The abundancy of open cell fabricated in poly(TT/DPEHA/HA)HIPEs sample body were able to increase the cell growth. This can be attributed to the nanodimensions of the HA as well as the compatibility for both the HA and poly(TT/DPEHA)HIPEs. These behaviors helped to correlate protein adsorption and contributed for the cellular adhesion [35]. The incorporation of 5-HA in poly(TT/DPEHA)HIPEs really benefits for L-929 cell proliferation as shown in Figure 12(b3). It shows the changed of fibroblast cell shape from round-like and flattened Figure 12(b1) to more elongated spindle-like shaped cells. In addition, Figure 12(b3) possessing extending out from the ends of the cell body. The applications of porous HA are wildly used in the biomedical field. Moreover, they have been used for the hard tissue scaffolding, cell loading and drug releasing agents. The experiment was set up in order to distinguish the effect of the polyHIPEs enhanced with content of HA towards the adhesion/proliferation rate of the cells. Generally, for the tissue engineering, porous HA scaffold were used as filling materials for bone defects and augmentation, artificial bone graft material and prosthesis revision surgery. Its high surface area and porosity led to excellent cell conductivity and reabsorption ability favored for fast cell in growth [36]. It shows the cell proliferation result of the poly(TT/DPEHA/HA)HIPEs. From the data presented it resembled an excellent cell growth as shown accordingly.

Conclusions
This study systematically examined thiol-ene-based polymers as the raw material by polymerizing an aqueous in oil phase of high-internal-phase-emulsion (HIPEs) and a series of porous materials were prepared. Although polymerization of thiol-ene groups monomers such as DPEHA and TT has been reported in the past, but in this study, exclusively focused on the incorporation of The applications of porous HA are wildly used in the biomedical field. Moreover, they have been used for the hard tissue scaffolding, cell loading and drug releasing agents. The experiment was set up in order to distinguish the effect of the polyHIPEs enhanced with content of HA towards the adhesion/proliferation rate of the cells. Generally, for the tissue engineering, porous HA scaffold were used as filling materials for bone defects and augmentation, artificial bone graft material and prosthesis revision surgery. Its high surface area and porosity led to excellent cell conductivity and reabsorption ability favored for fast cell in growth [36]. It shows the cell proliferation result of the poly(TT/DPEHA/HA)HIPEs. From the data presented it resembled an excellent cell growth as shown accordingly.

Conclusions
This study systematically examined thiol-ene-based polymers as the raw material by polymerizing an aqueous in oil phase of high-internal-phase-emulsion (HIPEs) and a series of porous materials were prepared. Although polymerization of thiol-ene groups monomers such as DPEHA and TT has been reported in the past, but in this study, exclusively focused on the incorporation of different concentrations of alpha hydroxyapatite (HA) towards poly(TT/DPEHA)HIPEs for cell proliferation application was carry out. The first stage of this research emphasizes the use of Hypermer B246 as the conventional surfactant for poly(TT/DPEHA/HA)HIPEs stabilization. Moreover, we succeed on fabricated a high-porosity thiol-ene polymer foams with tunable morphology (open pores). The investigation furthered by investigating the concentrations of surfactant, amount of crosslinker and the aqueous phase volume. The studies were broadened by demonstrating the inclusions of HA nanoparticle for the biologic application. The content of the formulation gave significant effects on the morphology of the poly(TT/DPEHA/HA)HIPEs formed with a relatively high particle loading negatively affecting the stability of the emulsion and also increase the mechanical strength. Poly(TT/DPEHA/HA)HIPEs with 5% of HA portrayed a very promising cell proliferation towards the fibroblast (L-929) cell with total cell proliferation up to 2.12. From the results, it could be concluded that the finest ratios of the poly(TT/DPEHA/HA)HIPEs Hypermer B246 with 5% HA. Further work was strategically planned for tailoring polyHIPEs template using other source of radiation which could use less energy and reduce polymerization time and thus shorten the preparation time.