Novel Epigallocatechin-3-Gallate (EGCG)-Loaded Mesoporous Bioglass Scaffolds for Bone Recruitment Applications

Bioglass-based material has been widely used in the field of biomedical science. In this study, the proper concentration of epigallocatechin-3-gallate (EGCG) for a mesoporous bioglass (MBG) scaffold was determined based on the sponge replication method. The fabrication procedure performed using a foam exchange technique resulted in an interconnected network of pores scaffolds with no cracks. In the minimum bactericidal concentrations of the bacteria assessed, the antibacterial concentration of EGCG against E. coli (200 μg/mL) was higher than that against S. aureus (25 μg/mL). The MBG and EGCG-MBG scaffolds exhibited excellent apatite mineralization and drug release abilities (the highest cumulative drug release from the EGCG-MBG scaffold was 75.37%). Thus, a 200 μg/mL EGCG can prevent cell apoptosis and directly enhance cell proliferation. Hence, a low-dose EGCG-MBG scaffold is another option for bone recruitment material.


Introduction
Using suitable substitutes for damaged bone will improve the recruitment effect in clinical treatment. Bioceramics members that maintain the function of bone regeneration include bioglass, hydroxyapatite (HA), and tricalcium phosphate (TCP). Such different types of bioceramics have been used to prove that Ca 2+ and (PO 4 ) 3− ions released from the surface of materials enhance apatite performance [1,2]. The cells such as mesenchymal stem cells, osteoblasts, and osteocytes perform the process of bone formation. The bioceramic graft plays the most important platform for wound healing and osteoinductive ability. Unlike other ceramics materials, the bioglass composition (SiO 2 , CaO, and P 2 O 5 ) has a stronger bond with bone tissue due to rapid ion exchange. According to the tissue engineering principle, the porous shape of scaffolds possesses excellent properties, including cell performance and drug release abilities for inducing bone regeneration [3]. The fabricating methods of porous ceramics include solvent-casting particle leaching, freeze-drying, and the foam exchange technique. These manufacturing processes can replicate the 3D porous structure in bone tissue engineering [4][5][6]. Among these methods, the foam exchange technique is a simple strategy which can provide a highly interconnected structure.
An ideal bio-scaffold should possess antibacterial activity (at the former stage) and induce bone formation (at the latter stage) of the recruitment process after implantation. Based on the characteristics of bioglass, many studies have attempted to improve their abilities, specifically their mechanical loading, biological properties, and drug delivery Appl. Sci. 2021, 11, 243 2 of 9 rate [7][8][9]. The metal ions and medication combined with scaffolds have been proven to effectively increase antibacterial action. Using the photochemical generation method, Calabrese et al. synthesized silver particles (approximately 20 nm) with an Mg-HA scaffold. The nonfunctionalized scaffold displayed antibacterial activity of up to 99% (including against Gram-negative bacteria and Gram-positive bacteria) and excellent cell proliferation [10]. Similarly, the nano-copper deposition on 3D graphene scaffolds was fabricated by Zhang et al. [11]. Conversely, some antibiotics such as gentamicin, vancomycin, and chlorhexidine gluconate (CHX) are commonly used to load the scaffold. Ballarre et al. developed a multifunctional layer (chitosan-gelatin/silica-gentamicin) coating system for implant application. Another study by Rajabi investigated vancomycin and BMP-2included tricalcium phosphate (β-TCP)/gelatin/bioglass scaffold and reported that a concentration of 5 mgL −1 level could reduce Gram-positive bacterial infections by 80% [12][13][14]. Nevertheless, the general toxicities and drug release rates of these various additives are still being evaluated. As we know, epigallocatechin-3-gallate (EGCG) is the major ingredient (approximately 50-63%) of catechins in green tea [15]. It is present in plant-based diets and offers many health benefits. Given its molecular structure, EGCG has positive functions, such as anti-oxidative, anti-inflammatory, and antimicrobial, and it can be used for medical development (as shown in Figure 1). The unique chemical structure (comprising eight hydroxyl groups (OH)) can help to remove the free radicals in the human body. The lesser the free radicals, the better and healthier are the cells. Forouzideh et al. showed that EGCG combined with silk fibroin nanofibers (SFNFs) using the electrospinning method can be used to engineer corneal tissue. Drug release from EGCG scaffolds was slow and controlled for over 144 h. Additionally, these scaffolds could inhibit the proliferation of human umbilical vein endothelial cells (HUVEC) for limbal cells and avoid blindness [16]. Kuhne et al. compared the effects of EGCG and EGCG-PEGylated-PLGA nanoparticle systems for neuro-developmental treatment [17]. Many previous studies found green tea extracts would reduce the aging-induced bone loss. With a focus on bone graft reconstruction, cross-linked EGCG-modified collagen membranes have been created under freeze-dried conditions. The experimental group clearly prevented the migration of keratinocytes and did not affect osteoblast viability. After four weeks, the remodeling phase of bone healing (new bone formation) was demonstrated in rats [18]. Chen et al. has demonstrated that 1 and 10 µmol/L EGCG can enhance the expression of osteogenic genes [19]. The ovariectomized rats injected with 3.4 mg/kg/day EGCG for 3 months had improved bone structure and increased bone morphogenetic proteins expression [20]. The treatment with 10 µM EGCG can enhance bone volume via the de novo bone formation [21]. Mah et al. also proved that a small amount of EGCG positively affected bone recruitment. Conversely, a higher concentration (>0.5 mg/mL) can reduce hard-tissue formation [22]. Based on the characteristics of bioglass, many studies have attempted to improve their abilities, specifically their mechanical loading, biological properties, and drug delivery rate [7][8][9]. The metal ions and medication combined with scaffolds have been proven to effectively increase antibacterial action. Using the photochemical generation method, Calabrese et al. synthesized silver particles (approximately 20 nm) with an Mg-HA scaffold. The nonfunctionalized scaffold displayed antibacterial activity of up to 99% (including against Gram-negative bacteria and Gram-positive bacteria) and excellent cell proliferation [10]. Similarly, the nano-copper deposition on 3D graphene scaffolds was fabricated by Zhang et al. [11]. Conversely, some antibiotics such as gentamicin, vancomycin, and chlorhexidine gluconate (CHX) are commonly used to load the scaffold. Ballarre et al. developed a multifunctional layer (chitosan-gelatin/silica-gentamicin) coating system for implant application. Another study by Rajabi investigated vancomycin and BMP-2-included tricalcium phosphate (β-TCP)/gelatin/bioglass scaffold and reported that a concentration of 5 mgL −1 level could reduce Gram-positive bacterial infections by 80% [12][13][14]. Nevertheless, the general toxicities and drug release rates of these various additives are still being evaluated. As we know, epigallocatechin-3-gallate (EGCG) is the major ingredient (approximately 50%-63%) of catechins in green tea [15]. It is present in plantbased diets and offers many health benefits. Given its molecular structure, EGCG has positive functions, such as anti-oxidative, anti-inflammatory, and antimicrobial, and it can be used for medical development (as shown in Figure 1). The unique chemical structure (comprising eight hydroxyl groups (OH)) can help to remove the free radicals in the human body. The lesser the free radicals, the better and healthier are the cells. Forouzideh et al. showed that EGCG combined with silk fibroin nanofibers (SFNFs) using the electrospinning method can be used to engineer corneal tissue. Drug release from EGCG scaffolds was slow and controlled for over 144 h. Additionally, these scaffolds could inhibit the proliferation of human umbilical vein endothelial cells (HUVEC) for limbal cells and avoid blindness [16]. Kuhne et al. compared the effects of EGCG and EGCG-PEGylated-PLGA nanoparticle systems for neuro-developmental treatment [17]. Many previous studies found green tea extracts would reduce the aging-induced bone loss. With a focus on bone graft reconstruction, cross-linked EGCG-modified collagen membranes have been created under freeze-dried conditions. The experimental group clearly prevented the migration of keratinocytes and did not affect osteoblast viability. After four weeks, the remodeling phase of bone healing (new bone formation) was demonstrated in rats [18].
Chen et al. has demonstrated that 1 and 10 μmol/L EGCG can enhance the expression of osteogenic genes [19]. The ovariectomized rats injected with 3.4 mg/kg/day EGCG for 3 months had improved bone structure and increased bone morphogenetic proteins expression [20]. The treatment with 10 μM EGCG can enhance bone volume via the de novo bone formation [21]. Mah et al. also proved that a small amount of EGCG positively affected bone recruitment. Conversely, a higher concentration (>0.5 mg/mL) can reduce hard-tissue formation [22].  Therefore, the bioglass material is similar to the composition of natural bone. Choosing the material for preparing mesoporous scaffold is beneficial for its use as a drug carrier and bone regeneration. A highly interconnected porous scaffold can reproduce by foam exchange technique completely. Because the EGCG-MBG scaffold has not been applied to clinical studies before, this study has attempted to evaluate the effects of EGCG (the minimum inhibitory concentrations, MIC) on the proliferation of MG63 cells cultured in MBG scaffolds. It is believed that the functional scaffolds can be clinically applied for a novel bone recruitment method.

MBG Scaffold
The MBG scaffolds were produced by the sponge replication method. In a nitric acid (HNO 3 ) solution system, the bioglass (molar ratios: Si/Ca/P= 60/36/4) precursor included 13.2 mL of tetraethoxysilane (TEOS), 0.7 mL of triethyl phosphate (TEP), and 5.8 g of calcium nitrate tetrahydrate (Ca(NO 3 ) 2 ·4H 2 O) in 9.5 mL of deionized water that was wellstirred to maintain a uniform solution. All chemical reagents were purchased from Sigma Corporation (St. Louis, MO, USA). The polyurethane (PU) foam was purchased from a local market (approximately 5-mm cubic size) and used as the template in the bioglass slurry. After impregnation, the foam was removed and centrifuged to remove the extra precursor solution. These dips and compressing steps were repeated four times to ensure uniform coating on the struts. Then, the block was dried at 60 • C for 1 h. These coating procedures were repeated four times until the bioglass slurry was completely absorbed. Finally, the PU foam was heated to 700 • C (5 • C/min) and maintained for 0.5 h in a sintering furnace.

Characterization
The crystalline phases and microstructures of the scaffolds were analyzed using X-Ray diffractometer (XRD; Rigaku, TTRAXIII, Tokyo, Japan). An X-ray diffractometer with a monochromatic Cu Kα radiation (45 kV and 40 mA) was used and XRD patterns were recorded between the 2θ interval ranges from 20 • to 60 • (scan speed: 4 • /min, step scan: 0.03 • ). The crystalline phases were identified using a Joint Committee on Powder Diffraction Standards (JCPDS) card. The structure of the scaffold was observed by scanning electron microscopy (SEM; SU3500, HITACHI, Tokyo, Japan). After copper coating for 1 min, the microstructure of the scaffolds was observed at 40 kV. Additionally, the scaffolds were dried and placed in isotherm system under 120 • C for 4 h to degas. The porous classification of the bioglass scaffolds was measured with a nitrogen (77 K) adsorption/desorption isotherm system (Belsorp max, Microtrac, Montgomeryville, USA). On the other hand, the pore volume and diameter were determined using the Barett-Joyner-Halenda method (BJH) method from the adsorption branches.

Antibacterial Activity of EGCG
The antibacterial activity (MIC) of EGCG (Sigma, St. Louis, MO, USA) was determined by the microdilution method. E. coli (BCRC 11849) and S. aureus (BCRC 10781) were purchased from the Bioresource Collection and Research Center (Hsinchu, Taiwan). Before the experiment, the tools and media were autoclaved at 121 • C for 15 min with standard atmosphere (1 atm). In the agar dilution method, 4 mL of Luria-Bertani agar (LA, Sigma, St. Louis, MO, USA) solution containing 1 mL of EGCG doubling diluting agent was solidified in a 6-cm dish plate. The bacterial colonies of E. coli and S. aureus from the stock solutions were separately incubated in 2 mL of nutrient broth overnight at 37 • C. The next day, 50 µL of the diluted bacterial suspension (1 × 10 4 cell/mL) was added to the agar plate, spread thoroughly, and incubated for 24 h. After incubation, the number of colonies were observed at each concentration of EGCG.

EGCG-MBG Scaffold
The scaffolds fabricated by the sponge replication method were divided into two groups. Unlike the control groups, the experimental groups were immersed in the antibiotic concentration of the EGCG solution (200 µg/mL) for 24 h. After being sieved through a filter paper, the EGCG-modified scaffolds were rinsed three times with deionized water and then dried overnight. To determine the bioactivity behaviors, both scaffolds were immersed in simulated body fluid (SBF) for 14 and 28 days. The SBF composition was made according to the protocol described by Kokubo et al. [23]. After immersing, the phase structure was characterized by the XRD pattern.

Release of EGCG
In order to understand the encapsulate of EGCG-MBG scaffolds, the calibration curves with different EGCG concentrations were initially evaluated. The absorbance value of 0.002, 0.004, 0.0078, 0.0156, 0.0312, 0.0625, and 0.125, 0.25 mg/mL concentration in the phosphate-buffered saline (PBS) solution was recorded using the Varioskan Flash reader (Thermo Fisher Scientific, Massachusetts, USA).
Based on the calibration curve information, we could estimate the encapsulation and cumulative release efficiency of EGCG-MBG scaffolds. To simulate the in vivo placement, the 20-mg EGCG-MBG scaffolds were immersed in 10 mL of PBS solution at 37 • C. At every measuring time point (2,4,10,24,48,72,96,120,240, and 360 h), 5 mL of buffer solution was withdrawn and replaced with the same amount of fresh solution. Then, the EGCG released scaffold was recorded using the absorbance reader with a 274 nm wavelength. The cumulative release of EGCG was calculated as follows: Cumulative release efficiency (%) = A/B × 100 where A is the encapsulated number of scaffolds during the measurement time and B is the encapsulated number of scaffolds before immersion.

Cell Live Assay
The proliferation of the MG63 cells was analyzed with the Cell Counting Kit-8 (CCK-8; Sigma, Taipei, Taiwan) assay. In this assay, a highly water-soluble tetrazolium salt solution containing 2-(2-methoxy-4-nitrophenyl)-3-(4-nitrophenyl)-5-(2,4-disulfophenyl)-2Htetrazolium is reduced to Formazan dye (yellow) by dehydrogenase. The color of the Formazan dye depends on the cell viability. Thus, 100 µL of 1 × 10 4 cell/mL of the MG63 cell suspension was cultured on a 96-well plate at 37 • C (5% CO 2 in the humidified incubator) for 24 h. Before the CCK-8 test, the MBG and EGCG-MBG scaffolds immersed in Dulbecco's Modified Eagle Medium (DMEM) solution for 24 h. After 1 day, the medium was centrifuged (2000 rpm, 10 min) and sieved through a 0.22-µm filter. The extraction medium was prepared with the MBG and EGCG-MBG scaffolds as the experimental group. Furthermore, the same amount of medium (no cells) was present to indicate background performance and the medium with cells in a well as the control group. After adding 100 µL of the medium for 1 day, 10 µL of the CCK solution was provided to each well and incubated for 2 h. The absorbance was measured at different time intervals (24 and 48 h) using a microplate reader (BioTek Epoch, Winooski, VT, USA) at 450 nm. The percentage of cell viability was estimated by the following equation: in which A is the mean absorbance value of the experimental group in the culture plate, B is the mean absorbance value of the background group (only medium without cells in a well) in the culture plate, and C is the mean absorbance value of the control group (medium and cells in a well) in the culture plate.

Statistical Analysis
Cell viability was analyzed with SPSS 19.0 software (Released 2010, IBM, Armonk, New York). The Mann-Whitney U test was used to compare the bioactivity and viability of the cells with different treatments. A significant difference was considered when p < 0.05.

Characterization of the MBG Scaffold
The crystalline phases of the mesoporous scaffolds are shown on the XRD patterns in Figure 2A. The figure indicates that the MBG scaffolds could be successfully fabricated Appl. Sci. 2021, 11, 243 5 of 9 by the sponge replication method. The standard amorphous silica peak was observed at 2θ = 22 • (JCPDS No. 29-0085). Figure 2A(a,b) shows the morphology of the scaffolds before and after being sintered at 700 • C. The PU foam possesses a microporous structure between the neighboring struts of approximately 300-480 µm. After being impregnated with the bioglass slurry and sintered procedure, the scaffolds had an interconnected network of pores; these were preserved and no cracks appeared on the surface. These pores should be adequate to allow cell penetration and control the rate of drug release [24]. The nitrogen adsorption measurement is used to characterize porous material (as shown in Figure 2B). According to the classical approach, the capillary condensation was observed from the corresponding Type IV isotherm at relative pressure. It was assumed that the mesoporous behavior that always accompanies the hysteresis model occurred. The hysteresis loop from the desorption cycle of the MBG scaffold contributed to the disk-shaped (H3) silts. The BJH analysis can be employed to determine the pore size distribution of the MBG scaffold. The small image in Figure 2B has shown the mesoporous material of the MBG scaffold sample containing pores in the range 10-20 nm. This pore size has proven advantageous for the uptake and release of drugs, growth factors, and improved cell attachment [25].

Characterization of the MBG Scaffold
The crystalline phases of the mesoporous scaffolds are shown on the XRD patterns in Figure 2A. The figure indicates that the MBG scaffolds could be successfully fabricated by the sponge replication method. The standard amorphous silica peak was observed at 2θ = 22° (JCPDS No. 29-0085). Figure 2A(a,b) shows the morphology of the scaffolds before and after being sintered at 700°C. The PU foam possesses a microporous structure between the neighboring struts of approximately 300-480 μm. After being impregnated with the bioglass slurry and sintered procedure, the scaffolds had an interconnected network of pores; these were preserved and no cracks appeared on the surface. These pores should be adequate to allow cell penetration and control the rate of drug release [24]. The nitrogen adsorption measurement is used to characterize porous material (as shown in Figure 2B). According to the classical approach, the capillary condensation was observed from the corresponding Type IV isotherm at relative pressure. It was assumed that the mesoporous behavior that always accompanies the hysteresis model occurred. The hysteresis loop from the desorption cycle of the MBG scaffold contributed to the disk-shaped (H3) silts. The BJH analysis can be employed to determine the pore size distribution of the MBG scaffold. The small image in Figure 2B has shown the mesoporous material of the MBG scaffold sample containing pores in the range 10-20 nm. This pore size has proven advantageous for the uptake and release of drugs, growth factors, and improved cell attachment [25].

Antibacterial Assessment of EGCG
The agar dilution method was used to examine the minimum bactericidal concentration of E. coli and S. aureus. Figure 3 illustrates the relationship between the colony growth of E. coli and the EGCG concentration. When the EGCG concentration reached 200 μg/mL, the number of bacteria decreased significantly. The growth of S. aureus (Gram-positive)

Antibacterial Assessment of EGCG
The agar dilution method was used to examine the minimum bactericidal concentration of E. coli and S. aureus. Figure 3 illustrates the relationship between the colony growth of E. coli and the EGCG concentration. When the EGCG concentration reached 200 µg/mL, the number of bacteria decreased significantly. The growth of S. aureus (Gram-positive) compared with the Gram-negative bacteria group is shown in Figure 4. The MIC to antibiotics with EGCG was 25 µg/mL. The antibacterial concentration against S. aureus was lower than that against E. coli. These results may have occurred because Gram-negative bacteria have cell wall (outer membrane) components [26]. In this study, a concentration of 200 µg/mL (the highest antibiotic concentration) was chosen for the fabricated EGCG-MBG scaffold.
compared with the Gram-negative bacteria group is shown in Figure 4. The MIC to antibiotics with EGCG was 25 μg/mL. The antibacterial concentration against S. aureus was lower than that against E. coli. These results may have occurred because Gram-negative bacteria have cell wall (outer membrane) components [26]. In this study, a concentration of 200 μg/mL (the highest antibiotic concentration) was chosen for the fabricated EGCG-MBG scaffold.

The Bioactivity of the EGCG-MBG Scaffold
The bioglass-based material has excellent osteoconductive ability because its composition leads to the formation of HA. Generally, the bioactivity of scaffolds can be evaluated by immersion in SBF solution. Figure 5a shows the phase patterns of the MBG and EGCG- compared with the Gram-negative bacteria group is shown in Figure 4. The MIC to antibiotics with EGCG was 25 μg/mL. The antibacterial concentration against S. aureus was lower than that against E. coli. These results may have occurred because Gram-negative bacteria have cell wall (outer membrane) components [26]. In this study, a concentration of 200 μg/mL (the highest antibiotic concentration) was chosen for the fabricated EGCG-MBG scaffold.

The Bioactivity of the EGCG-MBG Scaffold
The bioglass-based material has excellent osteoconductive ability because its composition leads to the formation of HA. Generally, the bioactivity of scaffolds can be evaluated by immersion in SBF solution. Figure 5a shows the phase patterns of the MBG and EGCG-

The Bioactivity of the EGCG-MBG Scaffold
The bioglass-based material has excellent osteoconductive ability because its composition leads to the formation of HA. Generally, the bioactivity of scaffolds can be evaluated by immersion in SBF solution. Figure 5a shows the phase patterns of the MBG and EGCG-MBG scaffolds after soaking in SBF for 14 and 28 days. The MBG scaffolds presented an amorphous structure before the bioactivity investigation. At the beginning of the study, the peak intensity depended on the soaking time. The apatite peaks at 2θ = 32 • (211) and 46.7 • (222) appeared on all of the scaffold surfaces. The apatite peaks have a significant difference between MBG and EGCG-MBG groups (p < 0.05). The morphology of the apatite was observed by SEM (as shown in Figure 5b,c). The amount of nano-structured apatite formed on the surface of the scaffolds after being immersed in SBF for 28 days was determined. Therefore, the MBG and EGCG-MBG scaffolds exhibited apatite mineralization abilities.
MBG scaffolds after soaking in SBF for 14 and 28 days. The MBG scaffolds presented an amorphous structure before the bioactivity investigation. At the beginning of the study, the peak intensity depended on the soaking time. The apatite peaks at 2θ = 32° (211) and 46.7° (222) appeared on all of the scaffold surfaces. The apatite peaks have a significant difference between MBG and EGCG-MBG groups (p < 0.05). The morphology of the apatite was observed by SEM (as shown in Figure 5b,c). The amount of nano-structured apatite formed on the surface of the scaffolds after being immersed in SBF for 28 days was determined. Therefore, the MBG and EGCG-MBG scaffolds exhibited apatite mineralization abilities.

Drug release of EGCG-MBG
The absorbance value with different EGCG concentration was measured at 274 nm. After calibration, it was noted to have a linear relationship with R 2 value of 0.9999 ( Figure  6a). The drug release properties of the EGCG-MBG scaffold were monitored through immersion in PBS solution at 37 °C. As shown in Figure 6b, the release rate was high during the initial 24 h. The cumulative drug release rate reached 68.71%. By contrast, the release efficiency was lower and displayed a stable performance. The highest release rate of the EGCG-MBG scaffold was 75.37%. More importantly, the mesoporous structure offered the possibility of maintaining the EGCG concentration at an effective dose for a long time.

Drug Release of EGCG-MBG
The absorbance value with different EGCG concentration was measured at 274 nm. After calibration, it was noted to have a linear relationship with R 2 value of 0.9999 (Figure 6a). The drug release properties of the EGCG-MBG scaffold were monitored through immersion in PBS solution at 37 • C. As shown in Figure 6b, the release rate was high during the initial 24 h. The cumulative drug release rate reached 68.71%. By contrast, the release efficiency was lower and displayed a stable performance. The highest release rate of the EGCG-MBG scaffold was 75.37%. More importantly, the mesoporous structure offered the possibility of maintaining the EGCG concentration at an effective dose for a long time.

Cytocompatibility of Scaffolds
The cytotoxicity of the MBG and EGCG-MBG scaffolds was evaluated by the CCK-8 assay. Figure 7 shows the effect of these scaffolds on cell viability. The survival rate of the MBG scaffold was 90.15% and 97.44% at 24 and 48 h, respectively. Whereas, the EGCG-

Cytocompatibility of Scaffolds
The cytotoxicity of the MBG and EGCG-MBG scaffolds was evaluated by the CCK-8 assay. Figure 7 shows the effect of these scaffolds on cell viability. The survival rate of the MBG scaffold was 90.15% and 97.44% at 24 and 48 h, respectively. Whereas, the EGCG-MBG scaffold displayed a higher proliferation than the MBG scaffold (104.36% and 107.52% for 1 and 2 days, respectively). The cell proliferation results of MG63 behavior showed a significant difference between MBG and EGCG-MBG groups (p < 0.05) [27]. Therefore, the proper concentration of EGCG (200 µg/mL) can prevent cell apoptosis and directly enhance cell proliferation. It could be speculated that the chemical structure of EGCG with MBG scaffolds would remove the free radicals quickly and protect the cell viability.

Cytocompatibility of Scaffolds
The cytotoxicity of the MBG and EGCG-MBG scaffolds was evaluated by the CCK-8 assay. Figure 7 shows the effect of these scaffolds on cell viability. The survival rate of the MBG scaffold was 90.15% and 97.44% at 24 and 48 h, respectively. Whereas, the EGCG-MBG scaffold displayed a higher proliferation than the MBG scaffold (104.36% and 107.52% for 1 and 2 days, respectively). The cell proliferation results of MG63 behavior showed a significant difference between MBG and EGCG-MBG groups (p < 0.05) [27]. Therefore, the proper concentration of EGCG (200 μg/mL) can prevent cell apoptosis and directly enhance cell proliferation. It could be speculated that the chemical structure of EGCG with MBG scaffolds would remove the free radicals quickly and protect the cell viability.

Conclusions
In this study, we fabricated the EGCG-MBG scaffolds successfully using the sponge replication method. These newly fabricated scaffolds possess an interconnected network of pores and have a smoother surface. The EGCG-MBG scaffolds also exhibited apatite mineralization abilities in SBF solution for 28 days. Furthermore, 200 µg/mL EGCG can prevent cell apoptosis and directly enhance cell proliferation in vitro. The release rate of EGCG was burst within 24 h and displayed a stable performance for 360 h. Although the activity of EGCG is concerning, the release rate of the EGCG-MBG scaffold can reach a stable situation for 15 days. Hence, it is believed that EGCG-MBG scaffolds are promising materials for clinical applications.

Funding:
The authors acknowledge the technical support provided by TMU Core Facility. This research was also supported in part by Grant MOST 108-2221-E-038-016-MY2.

Data Availability Statement:
The data presented in this study are available on request from the corresponding author.