# Osteoconductivity and Biodegradability of Collagen Scaffold Coated with Nano-β-TCP and  Fibroblast Growth Factor 2

Authors: Asako Ibara; Hirofumi Miyaji; Bunshi Fugetsu; Erika Nishida; Hiroko Takita; Saori Tanaka; Tsutomu Sugaya; Masamitsu Kawanami
Journal: Journal of Nanomaterials
 (2013)

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## Abstract

Nanoparticle bioceramics have become anticipated for biomedical applications. Highly bioactive and biodegradable scaffolds would be developed using nanoparticles ofβ-tricalcium phosphate (β-TCP). We prepared collagen scaffolds coated by nano-β-TCP and fibroblast growth factor 2 (FGF2) and evaluated the effects on new bone augmentation and biodegradation. The collagen sponge was coated with the nano-TCP dispersion and freeze-dried. Scaffold was characterized by SEM, TEM, XRD, compressive testing and cell seeding. Subsequently, the nano-β-TCP/collagen scaffold, collagen sponge, and each material loaded with FGF2 were implanted on rat cranial bone. As a control, no implantation was performed. Nano-TCP particles were found to be attached to the fibers of the collagen sponge by SEM and TEM observations. Scaffold coated with nano-TCP showed higher compressive strength and cytocompatibility. In histological evaluations at 10 days, inflammatory cells were rarely seen around the residual scaffold, suggesting that the nano-TCP material possesses good tissue compatibility. At 35 days, bone augmentation and scaffold degradation in histological samples receiving nano-β-TCP scaffold were significantly greater than those in the control. By loading of FGF2, advanced bone formation is facilitated, indicating that a combination with FGF2 would be effective for bone tissue engineering.


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## Body

## 1. Introduction

Tissue engineering strategies involving three major elements: cells, growth and differentiation factors, and natural or artificial scaffolds have been developed for use in various tissues of the human body. Scaffolds in regenerative medicine provide the base for repopulation and specialization of stem cells, blood vessels, and extracellular matrices [1]. In previous studies, bioceramic scaffolds such as calcium phosphate, hydroxyapatite (HA) [2, 3], and bioactive glass [4] have been applied in various artificially synthesized forms in bone tissue engineering [5]. It was reported that the scaffold of β-tricalcium phosphate (β-TCP) and bioceramic composites possessed mechanical integrity, microstructural properties, and biocompatibility. Furthermore, degradation of TCP was demonstrated when compared to the HA scaffold [6–8], suggesting that regenerating cells and tissues may receive inorganic ions for osteogenesis. The β-TCP scaffold in combination with various growth factors has been shown to stimulate bone augmentation [9, 10]. For clinical trials, bone graft substitutes using β-TCP have been used in the orthopedic and dental fields [11, 12].Regenerative scaffolds require rapid replacement by reformed tissue in the healing site. Degradation ofβ-TCP has revealed, however, that the resorption rate of β-TCP is relatively slow compared to tissue regrowth. It was frequently demonstrated that a large amount of residual β-TCP material was surrounded by regenerated bone [10, 11]. Low degradability of bioceramics including β-TCP has been reported in animal and human studies [6, 8, 13, 14], suggesting that aberrant healing using bioceramics will be increased by exposure to and contamination by residual materials.Recently, nanoparticle bioceramics have been introduced and expected to have a use for biomedical applications due to quantum size effects and a large surface area [15, 16]. Scaffolds with nanomaterial exhibited higher compressive strength, degradation rate, osteoconductivity, and protein absorption compared to scaffolds of submicron bioceramics [17, 18]. Although HA is a nonresorbable material, nanosized HA is resorbed in association with new bone formation [19]. Thus, high degradability as well as osteoconductivity might be provided to regenerative scaffolds for bone tissue engineering by the use of nanosized TCP. Replacement and maturation of engineered tissue are supposedly stimulated by a rapid remodeling process induced by nano-ceramics. When using synthetic nanoparticles as biomaterials, it is very important to regulate the aggregation/dispersion of nanoparticles. Nanoparticle of β-TCP as a biological scaffold have been combined with other material [20] and sintered for coagulation [18, 21]; however, dispersing effect will be insufficient. In this study, the easy regulatory process was performed; the biocompatible collagen sponge was immersed in an aqueous dispersion of nano-β-TCP using zwitterionic surfactants, for suppressing of nanosize particle agglutination [22, 23]. This easy method may be widely used for clinical trials. In addition, morphology of the biomaterial surface strongly affected attachment to cells and tissue after implantation [24, 25]. Nanostructure should be exposed at the surface of the base material. Early contact between regenerative cells or tissues and the nanosized effective factors will facilitate the tissue-reforming process. The nano-coating method will be developed for synthesizing a higher surface area of the scaffold and be conducive to novel bone-forming-related products.Fibroblast growth factor-2 (FGF2) stimulates cell proliferation, migration, and differentiation associated with wound healing [26]. FGF2 also regulates proliferation of osteogenic cells, such as osteoblasts and bone marrow stromal cells, resulting in bone augmentation [27, 28] and periodontal regeneration [29]. Based on animal results, a clinical trial of multiwall defects in patients with periodontitis was performed [30]. Thus, we hypothesized that the nano β-TCP/collagen scaffold in combination with FGF2 might accelerate bone tissue healing. However, the relation of nano-β-TCP and FGF2 use has not yet been investigated. The aim of the present study was to evaluate whether implantation of the nano-β-TCP/collagen scaffold with or without FGF2 loading induced bone augmentation in rat. We also examined the effect of nano β-TCP modifying on biodegradation.


## 2. Materials and Methods

### 2.1. Preparation of Collagen Sponge

Collagen sponge, an average porosity of 96%, was provided by Olympus Terumo Biomaterials (Tokyo, Japan). Atelocollagen in a dilute HCl solution (pH 3.0) was neutralized by adding concentrated phosphate buffer in NaCl to a final concentration of 0.1% collagen, 30 mM Na2HPO4, and 0.1 M NaCl. This collagen solution was incubated at 37°C for 4 h. The resulting fibrous precipitate was referred to as fibrillar collagen. Heat-denatured collagen was prepared from atelocollagen in a dilute HCl solution by heating at 60°C for 30 min. A composite of fibrillar and heat-denatured collagen was prepared by mixing the two at a ratio of 9 : 1 (w/w), respectively. This composite material was made into the form of a sponge by lyophilization at −30°C. This sponge was dehydrothermally cross-linked at 110°C for 2 h and used as a collagen sponge (Figure 1(a)).Figure 1
(a) Collagen sponge (A) and nano-β-TCP/collagen scaffold (B). (b) Surgical procedure: the samples were placed on the cranial bone. (c) Measurement of particle size distribution analysis for nano-TCP. (d) SEM micrograph of the β-TCP particles. (e) SEM micrograph of the nanopulverized β-TCP particles. Scale bars represent 5 mm (a), 10 mm (b), 10 μm (d), and 1 μm (e).


### 2.2. Preparation and Characterization of Nanoβ-TCP/Collagen Scaffold

β-TCP (average particle size: 2.3 μm) was provided by Tomita Pharmaceuticals (Naruto, Japan). Morphology of β-TCP particles was evaluated using a scanning electron microscope (SEM, S-4000, Hitachi, Tokyo, Japan) at an accelerating voltage of 10 kV after coating with a thin layer of Pt-PD (Figure 1(d)). β-TCP particles were pulverized to nanosized particles using a pulverizer (Nanomizer, Yokohama, Japan). Nano β-TCP particles along with the surfactant sodium cholate (0.2 wt%) were dispersed in distilled water. The particle size of nano-TCP was detected by SEM and particle size distribution analysis (LB-550, Horiba, Kyoto, Japan). Subsequently, the collagen sponge was immersed in a nano-β-TCP dispersion (1 wt%) for 24 h at 10°C. After rinsing in 70% ethanol and freeze-drying, the nano-β-TCP/collagen scaffold was configured (Figure 1(a)). Scaffold was characterized using SEM and transmission electron microscope (TEM, HD-2000, Hitachi, Tokyo, Japan) at 200 kV acceleration voltage. The porosity of the scaffold was calculated according to the following equation: porosity =100×(1-ρ1/ρ2), where ρ1 = bulk density and ρ2 = theoretical density of the scaffold. The scaffold was also characterized using X-ray diffraction (XRD, RINT2000, Rigaku, Tokyo, Japan). Cu Kα radiation at 40 kV and 40 mA was used. Diffractograms were obtained from 2θ = 10° to 90° with an increment of 0.02°, at a scanning speed of 4°/minute. The compression test was performed using a universal testing machine (EZ-S, Shimadzu, Kyoto, Japan). The cross-head loading speed was set at 0.5 mm/min.


### 2.3. Cytocompatibility of Nanoβ-TCP/Collagen Scaffold

In order to evaluate the cytocompatibility, nano-β-TCP/collagen scaffolds and collagen sponges were seeded with 1 × 104 mouse osteoblastic MC3T3-E1 cells and cultured in humidified 5% CO2 at 37°C, using medium (MEM alpha-GlutaMAX-I, Life Technologies, Grand Island, NY, USA) supplemented with 10% fetal bovine serum (FBS, Qualified, Life Technologies) and 1% antibiotics (Pen Strep, Life Technologies). After 24 and 48 h culture, cytotoxicity was detected by the cell counting kit-8 (CCK-8, Dojindo Laboratories, Kumamoto, Japan), following the manufacturer’s instructions. Optical density was measured on a microplate reader (ETY-300, Toyo Sokki, Yokohama, Japan) using an absorbance of 450 nm. Some samples were fixed in 2.5% glutaraldehyde in 0.1 M sodium cacodylate buffer (pH 7.4) for 30 min and rinsed in cacodylate buffer solution. Scaffolds were then dehydrated in increasing concentrations of ethanol and analyzed by SEM.


### 2.4. FGF2 Implant Preparation

FGF2 (Fiblast spray 500, Kaken Pharmaceutical, Tokyo, Japan) was diluted with distilled water (Otsuka distilled water, Otsuka Pharmaceutical, Tokyo, Japan) to produce stock solution of 0.5μg/μL. In the FGF2-loading group, nano-β-TCP/collagen scaffold and collagen sponge (size 6 × 6 × 3 mm) were injected with 100 μL FGF2 solution (loading dose; 50 μg) under vacuum. In the other groups, each material received distilled water alone.


### 2.5. Surgical Procedure for Bone Forming Effect and Biodegradability of Scaffold

The experimental protocol followed the institutional animal use and care regulations of Hokkaido University (Animal Research Committee of Hokkaido University, Approval number 10-42). Forty-eight 10-week-old male Wistar rats weighing 190 to 210 g were given general anesthesia by inhalation of diethyl ether and intraperitoneal injections of 0.6 mL/kg sodium pentobarbital (Somnopenthyl, Kyoritsu Seiyaku, Tokyo, Japan), as well as a local injection of 2% lidocaine hydrochloride with 1 : 80,000 epinephrine (Xylocaine Cartridge for Dental Use, Dentsply-Sankin K.K. Tokyo, Japan). After a skin incision was made in the scalp, a flap was made. Decortication of a 4 mm2 area was performed in front of the coronal suture in the cranial bone using a rotating round bur under water irrigation. Subsequently, four types of samples: nano-β-TCP/collagen scaffold, collagen sponge, and each material loaded with FGF2 were placed on the cranial bone with decortication (Figure 1(b)). As a control, no implantation was performed. Skin flaps were sutured (Softretch 4-0, GC, Tokyo, Japan) and tetracycline hydrochloride ointment (Achromycin Ointment, POLA Pharma, Tokyo, Japan) was applied to the wound.


### 2.6. Histological Procedure

Rats were euthanized using an overdose of diethyl ether and sodium pentobarbital (2.0 mL/kg). Specimens were collected from the wound 10 and 35 days after surgery. The tissue blocks including the cranial bone and surrounding soft tissue were fixed in 10% buffered formalin, decalcified in 10% EDTA, embedded along the frontal plane in paraffin wax, and cut into 6μm sections located every 300 μm. Sections were prepared and stained with hematoxylin-eosin (HE) and Masson’s trichrome.


### 2.7. Histomorphometric and Statistical Analysis

One section was taken for histomorphometric measurement from the midsection of the scaffold. The following measurements (Figure2): the height and the area of both newly formed bone and residual material were performed for each stained section after 35 days using a software package (Image J 1.41, National Institute of Health, Bethesda, MD, USA). The means and standard deviations of each parameter were calculated for each group.Figure 2
Schematic drawing of histomorphometric analysis. The frontal plane view indicating the following parameters: the area of newly formed bone (1), the area of residual material (2), the height of newly formed bone (3), and the height of residual material (4).Statistical analysis was performed using the Mann-WhitneyU test for porosity and compressive strength and Bonferroni’s multiple comparison for CCK-8 assay and each histometric measurement. P values < 0.05 were considered statistically significant. All statistical procedures were performed using a software package (DR. SPSS 11.0, SPSS Japan, Tokyo, Japan).


## 2.1. Preparation of Collagen Sponge

Collagen sponge, an average porosity of 96%, was provided by Olympus Terumo Biomaterials (Tokyo, Japan). Atelocollagen in a dilute HCl solution (pH 3.0) was neutralized by adding concentrated phosphate buffer in NaCl to a final concentration of 0.1% collagen, 30 mM Na2HPO4, and 0.1 M NaCl. This collagen solution was incubated at 37°C for 4 h. The resulting fibrous precipitate was referred to as fibrillar collagen. Heat-denatured collagen was prepared from atelocollagen in a dilute HCl solution by heating at 60°C for 30 min. A composite of fibrillar and heat-denatured collagen was prepared by mixing the two at a ratio of 9 : 1 (w/w), respectively. This composite material was made into the form of a sponge by lyophilization at −30°C. This sponge was dehydrothermally cross-linked at 110°C for 2 h and used as a collagen sponge (Figure 1(a)).Figure 1
(a) Collagen sponge (A) and nano-β-TCP/collagen scaffold (B). (b) Surgical procedure: the samples were placed on the cranial bone. (c) Measurement of particle size distribution analysis for nano-TCP. (d) SEM micrograph of the β-TCP particles. (e) SEM micrograph of the nanopulverized β-TCP particles. Scale bars represent 5 mm (a), 10 mm (b), 10 μm (d), and 1 μm (e).


## 2.2. Preparation and Characterization of Nanoβ-TCP/Collagen Scaffold

β-TCP (average particle size: 2.3 μm) was provided by Tomita Pharmaceuticals (Naruto, Japan). Morphology of β-TCP particles was evaluated using a scanning electron microscope (SEM, S-4000, Hitachi, Tokyo, Japan) at an accelerating voltage of 10 kV after coating with a thin layer of Pt-PD (Figure 1(d)). β-TCP particles were pulverized to nanosized particles using a pulverizer (Nanomizer, Yokohama, Japan). Nano β-TCP particles along with the surfactant sodium cholate (0.2 wt%) were dispersed in distilled water. The particle size of nano-TCP was detected by SEM and particle size distribution analysis (LB-550, Horiba, Kyoto, Japan). Subsequently, the collagen sponge was immersed in a nano-β-TCP dispersion (1 wt%) for 24 h at 10°C. After rinsing in 70% ethanol and freeze-drying, the nano-β-TCP/collagen scaffold was configured (Figure 1(a)). Scaffold was characterized using SEM and transmission electron microscope (TEM, HD-2000, Hitachi, Tokyo, Japan) at 200 kV acceleration voltage. The porosity of the scaffold was calculated according to the following equation: porosity =100×(1-ρ1/ρ2), where ρ1 = bulk density and ρ2 = theoretical density of the scaffold. The scaffold was also characterized using X-ray diffraction (XRD, RINT2000, Rigaku, Tokyo, Japan). Cu Kα radiation at 40 kV and 40 mA was used. Diffractograms were obtained from 2θ = 10° to 90° with an increment of 0.02°, at a scanning speed of 4°/minute. The compression test was performed using a universal testing machine (EZ-S, Shimadzu, Kyoto, Japan). The cross-head loading speed was set at 0.5 mm/min.


## 2.3. Cytocompatibility of Nanoβ-TCP/Collagen Scaffold

In order to evaluate the cytocompatibility, nano-β-TCP/collagen scaffolds and collagen sponges were seeded with 1 × 104 mouse osteoblastic MC3T3-E1 cells and cultured in humidified 5% CO2 at 37°C, using medium (MEM alpha-GlutaMAX-I, Life Technologies, Grand Island, NY, USA) supplemented with 10% fetal bovine serum (FBS, Qualified, Life Technologies) and 1% antibiotics (Pen Strep, Life Technologies). After 24 and 48 h culture, cytotoxicity was detected by the cell counting kit-8 (CCK-8, Dojindo Laboratories, Kumamoto, Japan), following the manufacturer’s instructions. Optical density was measured on a microplate reader (ETY-300, Toyo Sokki, Yokohama, Japan) using an absorbance of 450 nm. Some samples were fixed in 2.5% glutaraldehyde in 0.1 M sodium cacodylate buffer (pH 7.4) for 30 min and rinsed in cacodylate buffer solution. Scaffolds were then dehydrated in increasing concentrations of ethanol and analyzed by SEM.


## 2.4. FGF2 Implant Preparation

FGF2 (Fiblast spray 500, Kaken Pharmaceutical, Tokyo, Japan) was diluted with distilled water (Otsuka distilled water, Otsuka Pharmaceutical, Tokyo, Japan) to produce stock solution of 0.5μg/μL. In the FGF2-loading group, nano-β-TCP/collagen scaffold and collagen sponge (size 6 × 6 × 3 mm) were injected with 100 μL FGF2 solution (loading dose; 50 μg) under vacuum. In the other groups, each material received distilled water alone.


## 2.5. Surgical Procedure for Bone Forming Effect and Biodegradability of Scaffold

The experimental protocol followed the institutional animal use and care regulations of Hokkaido University (Animal Research Committee of Hokkaido University, Approval number 10-42). Forty-eight 10-week-old male Wistar rats weighing 190 to 210 g were given general anesthesia by inhalation of diethyl ether and intraperitoneal injections of 0.6 mL/kg sodium pentobarbital (Somnopenthyl, Kyoritsu Seiyaku, Tokyo, Japan), as well as a local injection of 2% lidocaine hydrochloride with 1 : 80,000 epinephrine (Xylocaine Cartridge for Dental Use, Dentsply-Sankin K.K. Tokyo, Japan). After a skin incision was made in the scalp, a flap was made. Decortication of a 4 mm2 area was performed in front of the coronal suture in the cranial bone using a rotating round bur under water irrigation. Subsequently, four types of samples: nano-β-TCP/collagen scaffold, collagen sponge, and each material loaded with FGF2 were placed on the cranial bone with decortication (Figure 1(b)). As a control, no implantation was performed. Skin flaps were sutured (Softretch 4-0, GC, Tokyo, Japan) and tetracycline hydrochloride ointment (Achromycin Ointment, POLA Pharma, Tokyo, Japan) was applied to the wound.


## 2.6. Histological Procedure

Rats were euthanized using an overdose of diethyl ether and sodium pentobarbital (2.0 mL/kg). Specimens were collected from the wound 10 and 35 days after surgery. The tissue blocks including the cranial bone and surrounding soft tissue were fixed in 10% buffered formalin, decalcified in 10% EDTA, embedded along the frontal plane in paraffin wax, and cut into 6μm sections located every 300 μm. Sections were prepared and stained with hematoxylin-eosin (HE) and Masson’s trichrome.


## 2.7. Histomorphometric and Statistical Analysis

One section was taken for histomorphometric measurement from the midsection of the scaffold. The following measurements (Figure2): the height and the area of both newly formed bone and residual material were performed for each stained section after 35 days using a software package (Image J 1.41, National Institute of Health, Bethesda, MD, USA). The means and standard deviations of each parameter were calculated for each group.Figure 2
Schematic drawing of histomorphometric analysis. The frontal plane view indicating the following parameters: the area of newly formed bone (1), the area of residual material (2), the height of newly formed bone (3), and the height of residual material (4).Statistical analysis was performed using the Mann-WhitneyU test for porosity and compressive strength and Bonferroni’s multiple comparison for CCK-8 assay and each histometric measurement. P values < 0.05 were considered statistically significant. All statistical procedures were performed using a software package (DR. SPSS 11.0, SPSS Japan, Tokyo, Japan).


## 3. Results

### 3.1. Characterization of Nano-β-TCP/Collagen Scaffold

The size range of nano-β-TCP particles was 20 to 500 nm and the mean particle size was 127 nm (Figures 1(c) and 1(e)). From SEM and TEM observation, nanosized β-TCP particles attached to the surface of collagen sponge fibers (Figures 3(a), 3(b), 3(c), 3(d), and 3(e)). The nanobiomodified surface was also confirmed on the cross section of the material (Figure 3(b)). It could be observed that the sample consisted of well-dispersed particles; however, at higher magnification, particles were partly composed of many nanoscale particles of β-TCP, suggesting secondary particles, while aggregation of nano-β-TCP was partially caused by the freeze-drying procedure (Figure 3(d)).(a) SEM micrograph of the nano-β-TCP/collagen scaffold. (b) SEM micrograph on the inner surface of the nano-β-TCP/collagen scaffold. (c) Higher magnification of the nano-β-TCP/collagen scaffold. Dispersed β-TCP particles attached to fibers of collagen sponge. (d) Higher magnification of the nano-β-TCP/collagen scaffold. Aggregated forms of nano β-TCP particles are partly exhibited (arrow). (e) TEM micrograph of nano-β-TCP/collagen scaffold. Nano β-TCP particles are distinctly recognized (arrows). (f) XRD patterns of β-TCP (A) and nano-β-TCP/collagen scaffold (B). Abbreviations: Col, collagen sponge. Scale bars represent 100 μm ((a), (b)), 10 μm (c), 200 nm (d), and 100 nm (e).
(a)
(b)
(c)
(d)
(e)
(f)The porosity was calculated to be >95% (Table1). XRD investigations detected a peak profile of nano-β-TCP/collagen scaffold overlapped with the product of β-TCP powder (Figure 3(f)). The compressive strength of nano-β-TCP/collagen scaffold was approximately 2-fold greater than that of the collagen sponge and this difference was statistically significant (Table 1).Table 1
Structural parameters of the material (N=6, mean ± SD).
Collagen sponge
Nano-β-TCP/collagen scaffold
Porosity (%)
96.05
±
0
.
11
95.89
±
0
.
05
*
Compressive strength (MPa)
0.11
±
0.02
0.22
±
0.1
*
*Statistical difference compared to collagen sponge.


### 3.2. Cytocompatibility of Nano-β-TCP/Collagen Scaffold

Osteoblastic MC3T3-E1 cells were significantly proliferated on the nano-β-TCP/collagen scaffold compared to the collagen sponge and the culture plate as control (Figure 4(a)). SEM observation revealed that cells attached to the collagen sponge coated with nano β-TCP. In addition, cell spreading with cell process elongation was also indicated, suggesting that nano-β-TCP/collagen scaffolds possess good cytocompatibility (Figure 4(b)).(a) CCK-8 assays of MC3T3-E1 cell proliferation after 24 and 48 h incubation (N=6, mean ± SD). Ctrl, Col, and TCP indicate control, collagen sponge, and nano-β-TCP/collagen scaffold, respectively. P*<0.05. (b) SEM micrograph of MC3T3-E1 cells seeded on the nano β-TCP/collagen scaffold after 24 h incubation. Cell spreading is shown on the scaffold (arrows). Scale bar represents 10 μm (b).
(a)
(b)


### 3.3. Histological Observations at 10 Days

In the collagen sponge group, cell and tissue ingrowth was rarely demonstrated in implanted material. Furthermore, collagen sponge appeared to be considerably compressed and could not maintain the cell-invading and regenerative space (Figures5(a) and 5(b)). Nano-β-TCP/collagen scaffolds caused various bioactivities in rat. Ingrowth of fibroblastic and osteoblastic cells and blood vessels was frequently observed at peripheral areas of implanted nano-β-TCP/collagen (Figure 5(c)). Giant cells associated with resorption of materials appeared around the nanoparticle aggregates in the scaffold (Figure 5(d)). Some inflammatory cells were seen around the residual material, indicating that the material possessed high biocompatibility. On the other hand, specimens receiving FGF2-loaded material provoked a more active tissue response. Formation of new bone as well as tissue ingrowth were prominently stimulated by FGF2 loading. New bone was composed of narrow trabeculae comprising osteoblasts and osteocytes (Figures 5(e), 5(f), 5(g), and 5(h)).Histological findings at 10 days. (a) Specimen receiving collagen sponge application. Cell and tissue ingrowth were rarely demonstrated in the collagen sponge. (b) Higher magnification of the framed area in (a). Collagen sponge was frequently compressed on the cranial bone. (c) Specimen receiving implantation of the nano-β-TCP/collagen scaffold. Ingrowth of regenerative tissue was observed at peripheral areas of implanted nano-β-TCP/collagen scaffolds on the skull of the rat. (d) Higher magnification of the framed area in (c). Macrophage-like cells (arrows) appeared around the agglutination of β-TCP particles (asterisks) of the scaffold. (e) Specimen receiving FGF2-loaded collagen sponge. New bone augmentation was highly promoted. (f) Higher magnification of the framed area in (e). Osteoblasts and osteocytes were found in newly formed woven bone. (g) Specimen receiving FGF2-loaded nano β-TCP/collagen scaffold. Formation of new bone as well as tissue ingrowth was prominently stimulated. (h) Higher magnification of the framed area in (g). Residual material was fractionated by newly formed connective tissue. Development of trabecular bone containing osteoblasts was evident. Abbreviations: NB, new bone; RM, residual material. Scale bars represent 1 mm ((a), (c), (e), (g)) and 100 μm ((b), (d), (f), (h)). Staining: HE.
(a)
(b)
(c)
(d)
(e)
(f)
(g)
(h)


### 3.4. Histological Observations at 35 Days

Histological specimens with only collagen sponge exhibited evidence of residual material (Figure6(a)). Slight cell infiltration in the inner side of the residual collagen sponge was observed, suggesting low degradation and tissue replacement of collagen sponge by remodeling processes (Figure 6(b)). New bone augmentation frequently occurred by the application of nano-β-TCP/collagen scaffold (Figure 6(c)). Although some residual large particles of β-TCP were observed in the newly augmented bone, most of the collagen sponge scaffolds had disappeared compared to collagen sponge group (Figure 6(d)). It seems likely that degradability of collagen sponge was promoted by the application of nano-β-TCP coating. In the FGF2-receiving group, considerable bone formation continuous with the preexisting bone was clearly detectable (Figures 6(e) and 6(g)). However, evidence of residual grafted material was slightly observed in the group of collagen sponge in combination with FGF2 (Figure 6(f)). In contrast, in the control, there was little evidence of bone augmentation (Figure 6(h)).Histological findings at 35 days. (a) Group of collagen sponge implantation. Bone formation was localized near the preexisting bone, whereas residual material was obviously evident on the cranial bone. (b) Higher magnification of the framed area in (a). Cell ingrowth was sparse in the collagen sponge. (c) Specimen receiving implantation of nanoβ-TCP/collagen scaffold. New bone augmentation occurred and residual material was rarely observed. (d) Higher magnification of histological section with nano-β-TCP/collagen scaffold implantation. Residual large aggregation of β-TCP (asterisks) was mildly observed in newly formed bone and connective tissue. (e) Specimen receiving FGF2-loaded collagen sponge. Bone augmentation was observed at the material implantation area. (f) Higher magnification of framed area of (e). Residual collagen sponge was slightly detected in the connective tissue around the newly formed bone. (g) Specimen receiving FGF2-loaded nano-β-TCP/collagen scaffold. Advanced bone formation was demonstrated similarly to the FGF2-loaded collagen sponge. However, residual implanted material was scarcely detectable. (h) Control. There was little evidence of bone augmentation. Abbreviations: NB, new bone; RM, residual material. Scale bars represent 1 mm ((a), (c), (e), (g), (h)) and 100 μm ((b), (d), (f)). Staining: HE ((a)–(c), (e)–(h)) and Masson’s trichrome (d).
(a)
(b)
(c)
(d)
(e)
(f)
(g)
(h)


### 3.5. Histomorphometric Analysis

The degree of bone augmentation after implantation of each material is presented in Figures7(a) and 7(b). In specimens that received nano-β-TCP/collagen, bone augmentation was significantly accelerated at 35 days, approximately 1.5-fold greater than that of the control. FGF2-loaded materials also significantly stimulated bone formation compared to nonloading. Nano-β-TCP/collagen in combination with FGF2 had the highest osteoconductivity among all groups. Regarding bone height measurement, a significant difference was found between the application of scaffolds with and without FGF2. From these results, biological function of nanoparticles of β-TCP would be expected to be exerted under FGF2 application.Histomorphometric analysis at 35 days (N=8, mean ± SD). (a) New bone area. (b) New bone height. (c) Residual material area. (d) Residual material height. Ctrl, Col, TCP, Col + FGF and TCP + FGF, indicate control, collagen sponge, nano-β-TCP/collagen scaffold, FGF2/collagen sponge, and FGF2/nano-β-TCP/collagen scaffold, respectively. P*<0.05.
(a)
(b)
(c)
(d)The amount of residual material in histological specimens is shown in Figures7(c) and 7(d). The area of residual nano-β-TCP/collagen scaffold was significantly lower compared to that of residual collagen sponge, suggesting that the former scaffold exhibited high biodegradability. Addition of FGF2 to each material stimulated material resorption. Regarding the height of residual material, there were no significant differences among all groups. Samples coated with a nano-TCP dispersion showed a tendency to increased degradation after implantation, regardless of FGF2 loading.


## 3.1. Characterization of Nano-β-TCP/Collagen Scaffold

The size range of nano-β-TCP particles was 20 to 500 nm and the mean particle size was 127 nm (Figures 1(c) and 1(e)). From SEM and TEM observation, nanosized β-TCP particles attached to the surface of collagen sponge fibers (Figures 3(a), 3(b), 3(c), 3(d), and 3(e)). The nanobiomodified surface was also confirmed on the cross section of the material (Figure 3(b)). It could be observed that the sample consisted of well-dispersed particles; however, at higher magnification, particles were partly composed of many nanoscale particles of β-TCP, suggesting secondary particles, while aggregation of nano-β-TCP was partially caused by the freeze-drying procedure (Figure 3(d)).(a) SEM micrograph of the nano-β-TCP/collagen scaffold. (b) SEM micrograph on the inner surface of the nano-β-TCP/collagen scaffold. (c) Higher magnification of the nano-β-TCP/collagen scaffold. Dispersed β-TCP particles attached to fibers of collagen sponge. (d) Higher magnification of the nano-β-TCP/collagen scaffold. Aggregated forms of nano β-TCP particles are partly exhibited (arrow). (e) TEM micrograph of nano-β-TCP/collagen scaffold. Nano β-TCP particles are distinctly recognized (arrows). (f) XRD patterns of β-TCP (A) and nano-β-TCP/collagen scaffold (B). Abbreviations: Col, collagen sponge. Scale bars represent 100 μm ((a), (b)), 10 μm (c), 200 nm (d), and 100 nm (e).
(a)
(b)
(c)
(d)
(e)
(f)The porosity was calculated to be >95% (Table1). XRD investigations detected a peak profile of nano-β-TCP/collagen scaffold overlapped with the product of β-TCP powder (Figure 3(f)). The compressive strength of nano-β-TCP/collagen scaffold was approximately 2-fold greater than that of the collagen sponge and this difference was statistically significant (Table 1).Table 1
Structural parameters of the material (N=6, mean ± SD).
Collagen sponge
Nano-β-TCP/collagen scaffold
Porosity (%)
96.05
±
0
.
11
95.89
±
0
.
05
*
Compressive strength (MPa)
0.11
±
0.02
0.22
±
0.1
*
*Statistical difference compared to collagen sponge.


## 3.2. Cytocompatibility of Nano-β-TCP/Collagen Scaffold

Osteoblastic MC3T3-E1 cells were significantly proliferated on the nano-β-TCP/collagen scaffold compared to the collagen sponge and the culture plate as control (Figure 4(a)). SEM observation revealed that cells attached to the collagen sponge coated with nano β-TCP. In addition, cell spreading with cell process elongation was also indicated, suggesting that nano-β-TCP/collagen scaffolds possess good cytocompatibility (Figure 4(b)).(a) CCK-8 assays of MC3T3-E1 cell proliferation after 24 and 48 h incubation (N=6, mean ± SD). Ctrl, Col, and TCP indicate control, collagen sponge, and nano-β-TCP/collagen scaffold, respectively. P*<0.05. (b) SEM micrograph of MC3T3-E1 cells seeded on the nano β-TCP/collagen scaffold after 24 h incubation. Cell spreading is shown on the scaffold (arrows). Scale bar represents 10 μm (b).
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## 3.3. Histological Observations at 10 Days

In the collagen sponge group, cell and tissue ingrowth was rarely demonstrated in implanted material. Furthermore, collagen sponge appeared to be considerably compressed and could not maintain the cell-invading and regenerative space (Figures5(a) and 5(b)). Nano-β-TCP/collagen scaffolds caused various bioactivities in rat. Ingrowth of fibroblastic and osteoblastic cells and blood vessels was frequently observed at peripheral areas of implanted nano-β-TCP/collagen (Figure 5(c)). Giant cells associated with resorption of materials appeared around the nanoparticle aggregates in the scaffold (Figure 5(d)). Some inflammatory cells were seen around the residual material, indicating that the material possessed high biocompatibility. On the other hand, specimens receiving FGF2-loaded material provoked a more active tissue response. Formation of new bone as well as tissue ingrowth were prominently stimulated by FGF2 loading. New bone was composed of narrow trabeculae comprising osteoblasts and osteocytes (Figures 5(e), 5(f), 5(g), and 5(h)).Histological findings at 10 days. (a) Specimen receiving collagen sponge application. Cell and tissue ingrowth were rarely demonstrated in the collagen sponge. (b) Higher magnification of the framed area in (a). Collagen sponge was frequently compressed on the cranial bone. (c) Specimen receiving implantation of the nano-β-TCP/collagen scaffold. Ingrowth of regenerative tissue was observed at peripheral areas of implanted nano-β-TCP/collagen scaffolds on the skull of the rat. (d) Higher magnification of the framed area in (c). Macrophage-like cells (arrows) appeared around the agglutination of β-TCP particles (asterisks) of the scaffold. (e) Specimen receiving FGF2-loaded collagen sponge. New bone augmentation was highly promoted. (f) Higher magnification of the framed area in (e). Osteoblasts and osteocytes were found in newly formed woven bone. (g) Specimen receiving FGF2-loaded nano β-TCP/collagen scaffold. Formation of new bone as well as tissue ingrowth was prominently stimulated. (h) Higher magnification of the framed area in (g). Residual material was fractionated by newly formed connective tissue. Development of trabecular bone containing osteoblasts was evident. Abbreviations: NB, new bone; RM, residual material. Scale bars represent 1 mm ((a), (c), (e), (g)) and 100 μm ((b), (d), (f), (h)). Staining: HE.
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## 3.4. Histological Observations at 35 Days

Histological specimens with only collagen sponge exhibited evidence of residual material (Figure6(a)). Slight cell infiltration in the inner side of the residual collagen sponge was observed, suggesting low degradation and tissue replacement of collagen sponge by remodeling processes (Figure 6(b)). New bone augmentation frequently occurred by the application of nano-β-TCP/collagen scaffold (Figure 6(c)). Although some residual large particles of β-TCP were observed in the newly augmented bone, most of the collagen sponge scaffolds had disappeared compared to collagen sponge group (Figure 6(d)). It seems likely that degradability of collagen sponge was promoted by the application of nano-β-TCP coating. In the FGF2-receiving group, considerable bone formation continuous with the preexisting bone was clearly detectable (Figures 6(e) and 6(g)). However, evidence of residual grafted material was slightly observed in the group of collagen sponge in combination with FGF2 (Figure 6(f)). In contrast, in the control, there was little evidence of bone augmentation (Figure 6(h)).Histological findings at 35 days. (a) Group of collagen sponge implantation. Bone formation was localized near the preexisting bone, whereas residual material was obviously evident on the cranial bone. (b) Higher magnification of the framed area in (a). Cell ingrowth was sparse in the collagen sponge. (c) Specimen receiving implantation of nanoβ-TCP/collagen scaffold. New bone augmentation occurred and residual material was rarely observed. (d) Higher magnification of histological section with nano-β-TCP/collagen scaffold implantation. Residual large aggregation of β-TCP (asterisks) was mildly observed in newly formed bone and connective tissue. (e) Specimen receiving FGF2-loaded collagen sponge. Bone augmentation was observed at the material implantation area. (f) Higher magnification of framed area of (e). Residual collagen sponge was slightly detected in the connective tissue around the newly formed bone. (g) Specimen receiving FGF2-loaded nano-β-TCP/collagen scaffold. Advanced bone formation was demonstrated similarly to the FGF2-loaded collagen sponge. However, residual implanted material was scarcely detectable. (h) Control. There was little evidence of bone augmentation. Abbreviations: NB, new bone; RM, residual material. Scale bars represent 1 mm ((a), (c), (e), (g), (h)) and 100 μm ((b), (d), (f)). Staining: HE ((a)–(c), (e)–(h)) and Masson’s trichrome (d).
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## 3.5. Histomorphometric Analysis

The degree of bone augmentation after implantation of each material is presented in Figures7(a) and 7(b). In specimens that received nano-β-TCP/collagen, bone augmentation was significantly accelerated at 35 days, approximately 1.5-fold greater than that of the control. FGF2-loaded materials also significantly stimulated bone formation compared to nonloading. Nano-β-TCP/collagen in combination with FGF2 had the highest osteoconductivity among all groups. Regarding bone height measurement, a significant difference was found between the application of scaffolds with and without FGF2. From these results, biological function of nanoparticles of β-TCP would be expected to be exerted under FGF2 application.Histomorphometric analysis at 35 days (N=8, mean ± SD). (a) New bone area. (b) New bone height. (c) Residual material area. (d) Residual material height. Ctrl, Col, TCP, Col + FGF and TCP + FGF, indicate control, collagen sponge, nano-β-TCP/collagen scaffold, FGF2/collagen sponge, and FGF2/nano-β-TCP/collagen scaffold, respectively. P*<0.05.
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(d)The amount of residual material in histological specimens is shown in Figures7(c) and 7(d). The area of residual nano-β-TCP/collagen scaffold was significantly lower compared to that of residual collagen sponge, suggesting that the former scaffold exhibited high biodegradability. Addition of FGF2 to each material stimulated material resorption. Regarding the height of residual material, there were no significant differences among all groups. Samples coated with a nano-TCP dispersion showed a tendency to increased degradation after implantation, regardless of FGF2 loading.


## 4. Discussion

The present study focused on the effects of nanobioceramic coating of biomaterials for developing an osteoconductive scaffold. Histological findings revealed that the nanoβ-TCP-coated scaffold enhanced augmentation of rat cranial bone. It was known that β-TCP has the potential to induce osteoconductivity in animal and human studies [31, 32]. Recently, many investigators have demonstrated that implanted β-TCP is resorbed by macrophage-like cells without cytotoxicity or inflammatory response [33, 34]. β-TCP degradation promotes concentration of calcium ions released into the regenerative space and alkaline phosphatase activity of osteoblastic cells [35, 36]; these phenomena allow environmental changes for osteogenesis to occur. Histological specimens treated with the nano-TCP scaffold at 10 days revealed foreign-body giant cells around the relatively large particles of β-TCP in the scaffold. Although the particle size of β-TCP covers a wide range, large particles might be resorbed by macrophages while small particles would be dissolved in tissue fluid at the early healing stage. It seems likely that bone augmentation was facilitated by providing early a high concentration of mineralizing elements from nano-TCP degradation, compared to conventional TCP-only grafting materials. On the other hand, the long-term residue of bioceramics absolutely prevented active tissue remodeling, resulting in immature tissue reformation [37, 38]. β-TCP also remained for a long period in the healing tissue [10, 11]. However, we found in this examination at 35 days that residual β-TCP particles were rarely seen in the regenerative tissue. Interestingly, 35-day specimens displayed residual collagen sponge, but the collagen composition in the nano-β-TCP/collagen scaffold synchronously disappeared with degradation of nano β-TCP particles. Further evidence that resorption of nano-β-TCP/collagen was significantly greater than that of collagen sponge being given by the histological measurements. Conceivably, the base material, collagen modified by nano-β-TCP, was simultaneously phagocytosed by macrophages activated by the effect of nano-TCP application. Therefore, the coating procedure using the nanosized ceramic substance lent tissue-replacing activity to the collagen sponge as well as osteoconductivity. In vivo regulation of material degradation possibly leads to the controlled release of medicine and growth factors, and a process of selective tissue rebuilding. Therefore, it will be necessary to elucidate the mechanisms regarding the degree of nano-β-TCP application associated with biological degradation.The mechanical properties of the regenerative scaffold play a facilitative role in maintaining the regenerative space following application in the body [1]. It was revealed that the compressive strength of collagen sponge was reinforced by coating with a nano β-TCP dispersion. Ordinarily, design of regenerative scaffolds requires a highly porous structure for cell invasion and proliferation; however, a higher porosity of biomaterial causes lower mechanical strength [39]. Nanomodification of β-TCP will provide advantages for tissue engineering, such as physical properties and porosity, based on current evidence. In SEM images, collagen sponge foam coated with a nano β-TCP dispersion did not fill the inner space with nanoceramic particles, the maintaining cell infiltration area, indicating that high porosity of the scaffold was exhibited. At 10 days after implantation of the nano-β-TCP/collagen scaffold, cells that invaded into the scaffold were noted. Furthermore, sufficient regenerative space was displayed by implantation of this scaffold compared to collagen sponge.As to the reason for promoting cell migration and material degradability, we speculated that collagen sponge coated with nanoparticles would have the property of protein adsorption as well as a physical effect. Recent studies demonstrated that various types of nanoparticle promote protein adsorption and cell adhesion [40, 41]. Nanomaterials would be beneficial in the healing of tissue because the regenerative space could retain several growth, differentiation, and nutritional factors that promote cell activity and tissue healing. Consistently, FGF2 application significantly assured stimulation of bone augmentation, although there was a significant difference between FGF-loaded samples with nano-β-TCP coating and without coating. We speculate that different biological effects are involved in nano-β-TCP coating such as supplementary regulation of osteoconductive function and adsorption of FGF2 molecules. Eventually, we found dramatic effects of FGF2 on woven bone formation at 10 days and rapid degradation of FGF2-loaded samples. These findings are consistent with the mechanisms supported by previous studies, in which FGF2 was shown to promote cell proliferation [42], vascularization [43], and wound healing [44, 45]. The combination use of FGF2 and nano-β-TCP as a well-degradable and osteoconductive scaffold presumably facilitated the wound healing associated with bone tissue engineering.The biocompatibility of nanomaterials is an important problem; however, evaluation of a systematic testing method of safety for nanomaterials is not currently established. In this study, we evaluated biocompatibility in vitro and in vivo through proliferation assay, SEM observation, and histopathologic evaluation of scaffolds. After cell seeding, good cell viability and spreading on the sample were confirmed. By histological observation, inflammatory cells were rarely seen around the nano-modified sample. Based on this evidence, we propose that the nano-β-TCP/collagen scaffold has good biocompatibility. In addition, collagen sponge, consisting of atelocollagen, was recognized as a compatible material [46, 47]. Recently, many studies have demonstrated the high compatibility of nanobioceramics in vitro [48, 49]. On the other hand, intravenous injection of nanohydroxyapatite resulted in vacuolar degeneration of nephric tubule epithelium, indicating that size of particle might play a significant role in biocompatibility [50]. Furthermore, there was evidence of long-term residue of nonabsorbable nanomaterials in the cell lysosomes following phagocytosis [51]. Although aberrant healing was not detected in this study, negative biological action resulting from nanomaterial use is an important point to be considered in the future.


## 5. Conclusion

Collagen scaffolds coated with a nano-β-TCP dispersion displayed good biocompatibility and osteoconductivity. FGF2-loaded nano-β-TCP/collagen scaffold had the highest bone-forming effects. Moreover, degradation of the material was accelerated by modification of the nano-β-TCP application regardless of FGF2 loading. The bioactivity of nano-β-TCP/collagen scaffolds has thus proved to be useful as a biomaterial for rebuilding and regenerating bone tissue.



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*Source: 639502-2013-06-12.xml*