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Atelocollagen Enhanced Osteogenesis in a Geometric Structured Beta-TCP Scaffold by VEGF Induction | OMICS International
ISSN: 2157-7552
Journal of Tissue Science & Engineering

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Atelocollagen Enhanced Osteogenesis in a Geometric Structured Beta-TCP Scaffold by VEGF Induction

Kimitoshi Yagami1*, Sunao Sadaoka1, Hiroshi Nakamura1, Saho Komatsu1, Jun Onodera2, Masahiko Suzuki3 and Yoshinori Kuboki4

1Division of Oral Health Promotion, Institute for Oral Science, Matsumoto Dental University, Shiojiri, Japan

2Koken Co., Ltd., Tokyo, Japan

3Pilot Co., Ltd., Tokyo, Japan

4Graduate School of Environmental Earth Science, Hokkaido University, Sapporo, Japan

Corresponding Author:
Kimitoshi Yagami
Division of Oral Health Promotion Institute
for Oral Science, Matsumoto Dental University
1780 Hirohoka Gohobara, Shiojiri, Nagano, 399-0781, Japan
Tel: +81-0263-51-2153
[email protected]

Received date: November 25, 2015; Accepted date: January 11, 2016; Published date: January 18, 2016

Citation: Yagami K, Sadaoka S, Nakamura H, Komatsu S, Onodera J, et al. (2016) Atelocollagen Enhanced Osteogenesis in a Geometric Structured Beta-TCP Scaffold by VEGF Induction. J Tissue Sci Eng 7:162. doi:10.4172/2157-7552.1000162

Copyright: © 2016 Yagami K, et al. This is an open-access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.

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In order to establish the convertibility of a host for bone augmentation, we herein developed a new honeycombshaped β-tricalcium phosphate (37H) using atelocollagen as a scaffold, which exhibited unique geometric properties for in vitro and in vivo studies.
Human mesenchymal stem cells (MSC) were cultured with 37H or atelocollagen-coated honeycomb-shaped β-tricalcium phosphate (Col37H), and their osteoblastic differentiation was then analyzed. Atelocollagen promoted cell adhesion and formation of vessel-like structures in the tunnels of scaffolds of cultured MSC. The mRNA expression levels of type I collagen, osteocalcin, and VEGF were greater in MSC cultured with Col37H than with 37H. Bone generation with Col37H in the rat calvaria was greater than with 37H, and this was attributed to early vessel construction. A large number of blood vessels invaded tunnels from the periosteum and existing bone surface. A strong VEGF signal was detected immediately before the new bone surface in the tunnels of Col37H.
These results indicate that the addition of atelocollagen to Col37H has potential in the construction of functional artificial bone.


Honeycomb-shaped β-TCP; Atelocollagen; VEGF; Bone marrow mesenchymal stem cells; Blood vessels; Bone regeneration


The early replacement of host bone with bone-filling materials is essential in bone regeneration therapy. The development of Harversian canals and angiogenesis are necessary to maintain normal bone metabolism in biomaterials at the site of bone regeneration, so that metabolism continues in the bone that forms, thereby contributing to its maintenance. Various bone-filling materials and bone formationaccelerating agents have been developed and successfully applied to clinical settings [1]. However, the histological structure of bone regenerated using current filling materials often differs from that by normal bone metabolism [2]. In the beginning of osteogenesis, the extracellular matrix proteins, such as collagen, gives an optimal environment structure for cell proliferation and differentiation to histogenesis following cell aggregation. Furthermore, some difficulties associated with complete treatments for bone defects have not yet been overcome. Delay of normal bone remodeling due to HA, premature absorption of collagen and TCP [3], and difficulty of controlling the regeneration volume with platelet-rich plasma (PRP) [4] and bone morphogenic protein-2 (BMP-2) [5] have been reported. These cytokines have been used in combination with scaffolds in order to stimulate the differentiation of a certain number of immature cells present in the bone microenvironment in the local tissues surrounding bone. However, controlling the quantity of cells and their activities at local sites is challenging, which may result in adverse effects in patients, and these cytokines are also expensive.

Previous findings [6-8] prompted us to consider the importance of an effective artificial extracellular matrix (ECM) in the induction of bone. Matrices have been categorized according to their (a) physical, (b) chemical, and (c) biochemical properties. A fourth property, (d) geometry, has also been proposed [9]. The superiority of honeycombshaped structures with numerous straight tunnels with diameters of 0.3-0.4 mm made from hydroxyapatite ceramics and collagenous preparations has indicated the suitability of this geometry for bone formation. We previously reported that less bone was generated in the absence of a cell transfer scaffold with an appropriate geometric structure [8]. Bone must form in a uniform manner, and achieving this represents a challenge in the field of biological tissue engineering.

Supply of cytokines to osteoblastic progenitor cells by neovascularization is important for satisfactory bone formation. Vascular endothelial growth factor (VEGF) has recently been shown to regulate perichondrial vascularity and early stage osteoblast differentiation in bone development [10]. This study demonstrated that progenitor-derived VEGF was required for blood vessel recruitment in the differentiation of osteoblast precursors in mice. Ogose et al. [11] showed that β-TCP scaffolds promoted early resorption by osteoclasts, the vascular invasion of macropores, and osteoblastic cell attachment on the surface on ceramic surfaces. They also detected reticular collagen fibrils in β-TCP micropore structures, which were directly connected to lamellar bone.

In order to determine the effects between angiogenesis and type I collagen during osteogenesis, we herein devised a new artificial ECM consisting of H-β-TCP with atelocollagen, and predicted that the tunnel structure in this scaffold may guide the initial stages of bone formation in vitro and ex vivo.

Materials and Methods

Preparation of scaffolds

Honeycomb-shaped beta-tricalcium phosphate (37H: height: 1.0 mm, outer diameter: 3.0 mm, inner diameter: 300 μm) was provided for this study by Pilot Corporation (Tokyo, Japan) [12] by pushing out molding, and burned at 1,050 degrees. Atelocollagen-coated honeycomb-shaped beta-tricalcium phosphate discs (Col37H) were provided by Koken Co., LTD. (AteloCell?RR, Tokyo, Japan) (Figure 1). As for the Col37H preparation, 37H was rinsed with ethanol/acetone (1:1) three times and was dried after washing three times in H2O for five minutes. And then, it was sterilized by gamma beam after collagen crosslinking by UV irradiation (UV Crosslinker, CL-1000, UVP inc., CA, USA).


Figure 1: Photomicrogram (A) and structure (B) of honeycomb-shaped betatricalcium phosphate with or without atelocollagen. Scaffolds had 37 parallel tunnels that made the honeycomb shape. 37H was prepared with a special nozzle device as previously described [6]. A paste of hydroxyapatite powder was extruded through a multi-nozzled disc, in the form of multiple rods, into a condensation space of taped conical tubing. The cylindrical products were sintered at 1,000°C and cut to the required lengths.

MSC cultures with scaffolds

Human mesenchymal stem cells (MSC) were purchased commercially (Lonza Co., Ltd, Visp, Switzerland). These cells were cultured in mesenchymal stem cell basal medium (MSCBM) with mesenchymal cell growth supplement (MCGS), according to the manufacturer’s protocol. The medium in the flask was replaced every other day with the same volume of fresh medium.

In order to investigate the osteogenic differentiation of MSC, 5 × 105 cells/cm2 were combined with 37H or Col37H in osteogenic medium (Lonza Walkersville Inc., MD, USA) and cultured according to the manufacturer’s protocol. After each differentiation culture period, the cells were fixed and stained with alkaline phosphatase (APase) using previously described methods [13]. After the indicated culture periods, three parallel sets of cell samples were employed to determine APase activities using histochemical and gene expression analyses.

Immunocytochemistry, APase activity, and extracellular matrix synthesis

The expression of type I collagen by hMSC cells on each scaffold was assessed using indirect immunostaining by a streptavidinperoxidase system (Nichirei, Tokyo, Japan) with an anti-type I collagen antibody or anti-vascular endothelial growth factor (VEGF) (Abcam, Cambridge, UK). After the experiment, cells were rinsed with PBS and fixed with 4% paraformaldehyde at 4ºC for 15 minutes. The antibody signal was detected using a peroxidase anti-fluorescein detection kit (Vector laboratories Inc., Burlingame, CA, U.S.A). In order to detect APase activity, fixed samples were rinsed twice in saline and incubated in 50 mM Tris-HCl (pH 9.5) containing 0.5 mg/ml of naphthol AS-BI phosphate (Sigma, St. Louis, USA) and 1 mg/ml of fast red trisodium salt (Sigma, St. Louis, USA) at 37ºC for 20 min. All cell nuclei were stained with 4’, 6-diamidino-2-phenylindole (DAPI) (Vector Laboratories Inc., Burlingame, CA, U.S.A.).

Measurement of APase activity

APase activity was also determined biochemically after the solubilization of cells with 1.5 M Tris buffer containing 1% Triton X-100, as described previously [13]. The substrate used was 5 mM p-nitrophenylphosphate (Sigma, St. Louis, MO) and activity was expressed as nmol of p-nitrophenol (p-NP) formed/min/μg protein assuming 1 A410=64 nmol of the product. Protein levels were determined using the Lowry protein assay (Bio-Rad Laboratories, Inc., Tokyo, Japan).

Quantitative RT-PCR analysis

The expression of type I collagen, osteocalcin, and VEGF mRNA in MSC was determined by RT-PCR (TaqMan® Gene Expression Assays, Thermo Fisher Scientific, USA). Total RNA was isolated from the H-β-TCP/MSC complex using One-Step Real-Time RTPCR Master Mixes® (Invitrogen, USA), followed by an amplification step using the Single Cell-to-CT Kit® (Life Technologies, USA). PCR amplification was performed using sense- and anti-sense-specific primers for human osteocalcin (the bone gamma-carboxyglutamate (gla) protein: Hs01587814_g1), vascular endothelial growth factor (VEGF: Hs00900055_m1), type I collagen (collagen, type I, alpha 1: Hs00164004_ml), and glyceraldehyde-3-phosphate dehydrogenase (GAPDH: Hs02758991_g1) according to the manufacturer’s protocol.

Transplantation of scaffolds and in vivo conditions

Thirty six Sprague Dawley rats (six weeks old, male), each weighing between 160 and 180 g (Japan SLC, Shizuoka, Japan), were fed a normal diet in an optimal environment. The animals were randomly allocated into 1- to 6-week groups with 6 rats in each group. All animal procedures were performed in accordance with The Guidelines of The Ministry of Education, Culture, Sports, Science and Technology Japan. All experiments using rats were approved by the Matsumoto Dental University Experimental Animal Committee and conducted in accordance with their guidelines for studies with laboratory animals for the accomplishment of 3Rs. 37H or Col37H was transplanted onto the rat calvaria, as shown in Figures 2A and 2B, under general anesthesia. Calcein blue (day 0) and alizarin complexion (24 h before each experimental period) were injected subcutaneously for labeling bone generation. Animals were sacrificed under general anesthesia 1 to 6 weeks after implantation. Scaffolds were removed with the surrounding soft tissues and bone and then fixed with 10% neutral-buffered formalin at 4ºC for 72 hours.


Figure 2: 37H and Col37H were applied symmetrically and horizontally as a pair to the surface of the calvaria and covered with periosteum (A, Insert shows a cross-sectional drawing of the setting). Design of the analysis for bone mineral density and histological findings in the tunnels of the scaffolds (B). XCT image of ROI (Yellow square, 3.0 x 1.0 mm, top left panel), a sliced image (top middle panel), and slice thickness (top right panel, 1.0 mm) (C). Details of the ROI area for total bone density (bottom left), trabecular density (bottom left), and cortical density (bottom right).

Peripheral quantitative computed tomography analysis

Before histological analyses were conducted, all 37H and Col37H samples were analyzed using peripheral quantitative computed tomography (pQCT: XCT Research SA+, Stratec Medizintechnik GmbH, Pforzheim, Germany) to evaluate bone mineral density (BMD), according to the manufacturer’s protocol. Fixed samples were prepared for a coronal section of scaffold tunnels on XCT (Figure 2C). Analyses included BMD measurements of two regions: cortical bone (the β-TCP area of 37H or Col37H) and trabecular bone (the tunnel area of 37H or Col37H), as shown in Figure 2C. The area of ROI for each measurement was determined to be 3 mm3 (width 3.0 mm x height 1.0 mm × thickness 1.0 mm) with total bone density (TB). The CT density values measured reflected the summed effects of new bone and β-TCP.

Histological analysis

Tissue samples were embedded in polyester resin (Technovit 8100 Heraeus Kulzer, Germany) to prepare undecalcified sections according to the manufacturer’s protocol. Three-μm-thick sections along the tunnel of the scaffold were prepared. Sections were stained with an anti- VEGF antibody and Villanueva osteochrome bone stain (Polysciences, Inc., Warrington, PA, USA).

Statistical analysis

Unless otherwise noted, MSC from each of the rats were characterized using the assays described above, and representative data sets are shown. Quantitative results are presented as the mean ± standard deviation. In culture assays, means were compared using an unpaired, two-tailed Student’s t-test and significance was indicated by *: p<0.01, **: p<0.05.


Evaluation of osteoblastic differentiation and VEGF on MSC

MSC adhered to and grew normally on 37H and Col37H. The cell layers constructed in the tunnels were larger in Col37H (Figure 3B, 3D, 3F and 3H) than in 37H (Figure 3A, 3C and 3E). Thicker cells formed and larger amounts of type I collagen and VEGF were produced in the tunnels in Col37H than in 37H after 7 days of cultivation. APasepositive cells (arrows) were observed on day 14 on Col37H (Figure 3G), and changes in APase activity were significantly higher in Col37H than in 37H on the 7th and 14th days (Figure 3H, *p<0.01). The expression levels of type I collagen, osteocalcin, and VEGF were significantly higher in MSC cultured with Col37H than with 37H. These expression levels gradually increased after 3 days of cultivation (Figure 4, RQ: p<0.01). Furthermore, type I collagen mRNA rose 7 times as compared with contrast in day 3 and peaked in day 7 (Figure 4A). Osteocalcin mRNA was hardly detected by the contrast, but it was detected in day 3 in Col37H and the expression increasing to day 14 (Figure 4B). VEGF mRNA rose 6 times as compared with contrast in day 3, and the expression continued increasing to day 14 (Figure 4C).


Figure 3: Osteogenic induction of MSC on Col37H and 37H. Microscopic findings of MSC cultured on 37H (a, c, e) and Col37H (b, d, f). Samples were stained with DAPI (a and b), type I collagen (c and d), VEGF (e and f) on day 7, and APase (g) on day 14 of the culture. Bars, a-e: 100μm, g: 20μm. The APase-stained cell layer on the inside of the tunnel of Col37H (g, arrows). APase activities were determined on days 3, 7, 14, and 21 of the culture with 37H () or Col 37H () (h). Values represent means ± SE of 6 sets of cultures. Each significant difference was tested between 37H and Col 37H at each time point (*p<0.01) (h). S: Scaffold, T: Tunnel.


Figure 4: Comparison between osteogenic gene expression on MSC in Col37H and 37H. Total RNA was extracted from cells that adhered to a scaffold after the culture with Col37H and 37H in hMSC for 3, 7, and 14 days (n=9). The value of RT-PCR was calculated with adjustment for the GAPDH level in 37H and at an RQ min/max confidence level of 95% (p<0.01). Note: The expression levels of type I collagen, osteocalcin, and VEGF were significantly higher in Col37H than in 37H. An increase in gene expression levels was noted on the 3rd day of the culture.

Quantification of bone formation

The whole bone densities of implanted samples increased in proportion to the experimental period in Col37H and 37H (Figure 5). Bone density was greater in Col37H than in 37H from the first week. However, we were unable to quantify osteogenesis in each honeycomb tunnel. Therefore, we compared the bone area formed in the tunnels in each section. New bone areas increased in size in Col37H and 37H in a time-dependent manner. The quantity of bone that formed in the honeycomb tunnels was greater in Col37H than in 37H from the first week (Figure 6A). The bone that formed in the tunnels was longer in 37H than in Col37H after 4-6 weeks (Figure 6B). In contrast, the bone that formed in the tunnels was wider in Col37H than in 37H after 3-6 weeks (Figure 6C).


Figure 5: Quantification of whole bone densities on Col37H (black) and 37H (white). Total bone density was measured using the longitudinal area of ROI in each scaffold (n=6). *p<0.01


Figure 6: New bone area in Col37H and 37H tunnels.The total bone area (A), length (B), and width (C) of bones that formed in the tunnel were analyzed in undecalcified sections (n=6). *p<0.01.

Histological evaluation of 37H vs. Col37H in vivo

More well-formed soft tissue and extensive angiogenesis were observed in Col37H than in 37H in the first week (Figures 7A and 7B). Tissue density was higher in Col37H than in 37H in the third week, and new bone had formed in all tunnels following angiogenesis (Figures 7C and 7D). The new bone penetrated the tunnels in the direction of the periosteum and continued to grow in a time-dependent manner. Maturated bone with marrow formed along the tunnel wall surface in Col37H after six weeks (Figures 7E and 7F). After 6 weeks, new bone formed directly on the inner surface of the tunnel in Col37H (Figure 7F, n). At 1 week, VEGF was localized from the orifice to the interior of the tunnel. Capillary vessels at the entrance of the tunnel entered the interior of the tunnel (Figures 8A and 8B, v). Three weeks after transplantation, many capillary vessels were formed in the fibrotic tissue (f) in Col37H, and osteoblasts were regularly arranged on the surface of newly formed bone (Figures 8C and 8D, V).


Figure 7: Histology of time-course changes in bone formation on scaffolds in the rat calvaria.37H (A, C, and E) and Col37H (B, D, and F) were implanted for one (A and B), 3 (C and D), and six (E and F) weeks. Non decalcified sections were stained with VB. T: tunnel, S: β-TCP, c: calvaria, n: new bone, Bar: 100μm.


Figure 8: Microscopic findings on the relationship between blood vessels and new bone formation in a tunnel of Col 37H. Sections were obtained 1 and 3 weeks after implantation. Undecalcified sections were stained with Villanueva bone stain (A and C), and immunological staining was performed with an anti-VEGF antibody (B and D, brown). s: β-TCP, c: calvaria, n: new bone, v: vascular, f: fibrous tissue. Bar: 100μm.

VEGF was stained on the surface of the new bone that penetrated the tunnels as well as on blood vessels and tissues surrounding the mesenchymal tissue (Figures 8C and 8D, arrow heads). Many capillary vessels containing blood cells were observed at the forefront of new bone formation.

Evaluation of changes in the expression of VEGF with osteogenesis in the presence or absence of atelocollagen

A large number of blood vessels invaded tunnels from the periosteum and existing bone surface-independent sites (Figure 9A, red). A strong VEGF signal (Figure 9B, brown) was detected around the blood vessels and the surface of the generated bone (Figure 9A, blue), which had progressed from bone. The expression of VEGF increased similarly in Col37H and 37H until after 4 weeks. The VEGF signal was stronger in Col37H than in 37H from the first week (Figure 9C).


Figure 9: Evaluation of changes in the expression of VEGF with osteogenesis in the presence or absence of collagen. (A) The fluorescence microscopy photograph shows a calcein and alizarin-labeled new bone front in the tunnel. (B) A light microscope photograph showing angiogenesis in tunnels stained with VEGF on same section of A. (C) A comparison (mm2/tunnel) of the area of angiogenesis (stained brown) per tunnel (inside of each yellow-dotted line) in 37H and Col37H (*p<0.01).


We previously reported that honeycomb-shaped β-TCP (37H) with BMP-2-treated MSC was advantageous in terms of the initial induction of bone generation by blood vessels, which is essential for MSC to differentiate into osteoblasts. However, there is little evidence concerning the relationship between angiogenesis and the tunnel structure in the osteogenic mechanism. It currently remains unclear whether cells and blood vessels are necessary for the earlier formation of bone. Thus, we compared angiogenesis and bone generation in tunnels using VEGF. The longitudinal increase observed in the expression of VEGF supports the osteoblastic differentiation of hMSC in proportion to elevations in APase activity (Figures 3G and 3H). Furthermore, the gene expression of VEGF in MSC was higher in Col37H than in 37H (Figure 3C). In the differentiation of MSC to osteoblasts, transcription factors such as Runx2 [14] and osteocalcin [13] play major roles in determining cell fate. We previously demonstrated that MSC increased the expression of Runx2, APase, and osteocalcin genes when cultured in H-β-TCP with BMP-2 [7]. In the present study, we focused on the relationship between blood vessels and osteogenesis and their effects on bone quantity with or without atelocollagen. In our in vitro experiment, we showed that the gene expression of type I collagen, osteocalcin, and VEGF by MSC was enhanced in cells cultured with Col37H (Figure 4). Furthermore, MSC formed more tubular structures along the tunnel walls of Col37H than in those of 37H (Figures 3E and 3F). These results indicate that MSC induced vascularization to maintain the base with collagen scaffold. Our results also indicated that some MSC differentiate into endothelial cells in order to construct vessels (Figures 3F and 8). Kang et al. [14] found that factors other than the potential of cells were necessary for the control of ECM and growth factors in inducing angiogenesis by co-culture of BMSC and HUVEC on b-TCP. Regarding our geometric theory, the tunnel structure and presence of atelocollagen were identified as key factors of ECM for the induction and regeneration of bone.

The bone mineralization process was previously confirmed to start with the formation of nanocrystal nuclei in collagen fibrils [14]. The abilities of phosphorylated proteins, such as collagen, osteopontin, osteonectin, bone sialoprotein, and osteocalcin, to nucleate and grow calcium phosphate crystals has already been reported [15]. Growth or mineralization then occurs along the collagen fibrils, eventually interconnecting all collagen fibrils. An increase in the phosphorus concentration by matrix vesicle, epitaxial nuclei, and APase are essential for calcification [16]. The results of the present study suggested that APase produced by MSCs that differentiated into osteoblasts induced deposition of calcium phosphate in matrices such as collagen fibrils (Figures 3H and 3G). Tunnels had been filled with APase-positive cells by day 14 (Figure 3A). These results indicated that the specific structure of H-β-TCP with atelocollagen attracted a large number of MSC, and induced their differentiation and maturation to osteoblasts, thereby promoting the formation of ECM.

Maturated bone with marrow formed along the tunnel wall surfaces in Col37H and 37H 3 weeks after implantation. However, the presence or absence of atelocollagen affected some bone morphogenetic aspects. Extensive angiogenesis and increases in bone in the tunnel walls were observed earlier in Col37H than in 37H. The local administration of atelocollagen alone without any ECM carrier did not initiate bone formation [12,17]. Our previous findings clearly showed that these carriers were not only drug delivery systems (DDS), but also functioned as an artificial ECM, on which cells grew and differentiated to form a continuous organized tissue [8]. Brkovic et al. [18] demonstrated the ability of a β-TCP-collagen material to prevent alveolar atrophy following tooth extraction in a case report.

The periosteum is indispensable to the formation of the bone. However, bone regeneration in the scaffold tunnels occurred only from the existing bone side and not from the periosteal side. The periosteum is a tissue on which osteoblasts arrange on the bone surface directly under the fibrous membrane. Previous studies reported that the formation of bone on the periosteum depended on BMP-2 and VEGF [19-22]. However, even if a periosteum is not present, bone was found to form ectopically in the presence of BMP-2 [13]. Also, while pluripotent MSCs form tissues other than bone in the fracture healing process, no cartilaginous or adipose tissue was detected in this study. VEGF regulates early stage osteoblastic differentiation, and the loss of VEGF expression has been shown to decrease perichondrial vascularity and osteoblast precursor numbers [10]. Bone density was greater in Col37H than in 37H in the third week, and bone had formed in all tunnels following angiogenesis (Figures 5 and 6). However, the presence or absence of aterocollagen affected some bone morphogenetic aspects. Extensive angiogenesis and the adherence of new bone to the tunnel wall were observed earlier in Col37H than in 37H (Figures 7 and 8). Bone formation in the tunnel started from the original bone side (Figures 7-9); we previously reported that it did not form on a gingival flap side with a periosteum [8]. The distribution of VEGF expression changed to areas in agreement with the calcein- and alizarin-labeled new bone front in the tunnel (Figure 9).

The above results suggest that Col37H promotes the early differentiation of host MSCs to osteoblasts by inducing angiogenesis. This method is a simple and effective technique that may be applied to the future treatment of major bone defects in clinical settings. Further investigations are necessary to clarify the reason for the occurrence of bone formation from the existing bone rather than the periosteum and the role of VEGF in this process.


We herein obtained novel insights into the relationship between bone regeneration and VEGF using the unique geometric properties of H-β-TCP with atelocollagen in vitro and in vivo. Early vessel formation and osteogenesis were observed in Col 37H tunnels. These results indicate that Col37H has potential in the construction of functional artificial bone.

Conflict of Interest

Kimitoshi Yagami, Sunao Sadaoka, Hiroshi Nakamura, Saho Komatsu, Jun Onodera, Masahiko Suzuki, and Yoshinori Kuboki declare that they have no conflict of interest in this study.


We thank Dr. Mariko Kimura (Pilot Corporation, Tokyo, Japan) for the fabrication of H-β-TCP. This work was supported by a Grant-in-Aid for scientific research from the Ministry of Education, Culture, Sports, Science and Technology of Japan, and a Grant-in-Aid for Scientific Research from the Japan Society for the Promotion of Science No. 19592315 (to K. Yagami).


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