The Microdamage and Expression of Sclerostin in Peri-implant Bone under One-time Shock Force Generated by Impact

ScienTiFic REPORTS | The Microdamage and Expression of Sclerostin in Peri-implant Bone under One-time Shock Force Generated by Impact Xiaoou Diao Zhirui Li Baili An Haitao Xin Yulu Wu Kai Li Fan Feng Chenyun Dou OPEN Osseointegration is the key to implant stability and occlusal support. Biomechanical response and remodeling of peri-implant bone occurs under impact loading. Sclerostin participates in bone formation and resorption through Wnt and RANKL pathways. However the mechanism of microdamage and expression of sclerostin in peri-implant bone under impact load is still unclear. In present study, specific impact forces were applied to the implants with favorable osseointegration in rabbits. The microdamage of peri-implant bone and the expression of sclerostin, β-catenin and RANKL during the process of bone damage and remodeling were investigated by micro-CT, histology, immunofluorescence and RT-qPCR analysis. Interface separation and trabecular fracture were found histologically, which were consistent with micro-CT analyses. Throughout remodeling, bone resorption was observed during the first 14 days after impact, and osseointegration and normal trabecular structure were found by 28 d. The expression of sclerostin and RANKL increased after impact and reached a maximum by 14 d, then decreased gradually to normal levels by 28 d. And β-catenin expression was opposite. Results indicated that sclerostin may involve in the peri-implant bone damage caused by impact and remodeling through Wnt/β-catenin and RANKL/RANK pathways. It will provide a new insight in the diagnosis and treatment for patients suffering impact. - Implant dentures are supported by dental implants, which are inserted into the alveolar bone and connect directly to the bone without intervening soft tissue, following osseointegration1–3. Osseointegration is very important for an implant to maintain its stability and provide occlusal support4. Occlusal force is transmitted from the implant to the alveolar bone by functional loading during mastication. The biomechanical response of the bone to proper occlusal force determines the osseointegration of the implant and bone remodeling after implantation5–8. A failed osseointegration would decrease the stability of the implant and cause the failure of the restoration. Implant dentures may suffer from impact, particularly during activities such as sports and physical training. Impact is a complex phenomenon that occurs when two or more bodies undergo a collision9. Characteristics of impact are very brief duration, high force levels reached, rapid dissipation of energy and large accelerations and decelerations present9. When the pulse duration of the impact load is in the range of microseconds, the force is transmitted and reflected, usually in the form of stress waves, through the composite structure consisting of the implant, the interface and the alveolar bone, in which each has the different impedance. If the dental implant and alveolar bone are unable to buffer the impact through deformation of their structure, the osseointegration at the implant-bone interface and the bone microstructure around the implant would be damaged. However, the mechanism of trauma is still unclear. The bone is a functional remodeling biomaterial. Bone remodeling is usually defined as a process where bone gradually alters its morphology when mechanical signals are sensed and conducted by osteocytes through the lacunar-canalicular system to adapt to the biomechanical environment10–16. Bone remodeling includes two opposing processes: resorption and deposition. Sclerostin secreted by osteocytes is a glycoprotein encoded by the SOST gene17, 18. Several studies have reported that sclerostin plays important roles in the anabolic response of bone to mechanical stimulation through the Wnt/β-catenin pathway and the catabolic response of bone to mechanical stimulation through the RANK/RANKL pathway19–22. However, the expression of sclerostin in peri-implant bone following impact is still unclear, and the correlation between the expression of sclerostin and bone remodeling needs to be studied. In order to address these questions, we established an animal model with implants under impact load. The characteristics of the microdamage and the expression of sclerostin, β-catenin and RANKL were investigated to explore the mechanism of impact damage and the subsequent repair of bone around the implant. These results could help in the evaluation of alveolar bone trauma around implants and provide guidance for the management of dental implants following impact. Materials and Methods Animal Studies. Animal Preparation. Thirty 20- to 22-week-old female New Zealand rabbits weighting approximately 3.5–4.0 kg were purchased from the animal centre of the Fourth Military Medical University (Shaanxi, China) and housed for 1 month. The animals were allowed access to water and pelleted commercial diet ad libitum. The weights were monitored weekly in whole research. Implant Insertion. Femoral distal condyles were chosen as a standard site to insert implants as previously described23, and the implantation surgeries were performed under general anesthesia. A skin incision was made over the lateral femur-tibia joint, the femoral distal condyle was exposed after the muscle and fascia tissues were peeled away. The implant, which was 2.3mm in diameter and 5 mm in length, was inserted into the prepared hole with an implant placement torque of 5–10 N·cm. The incision was closed with sutures in a single layer. An intramuscular injection of penicillin (200 thousand IU kg−1) was given to each animal once daily for 5 days postoperatively to prevent infection, and the animals were allowed unrestricted activity. Impact Loading. Three months later, impact experiments were performed after favorable osseointegration occurred. The animals were randomly divided into two experimental groups suffering impact load and one control group without impact. The impact protocol24, 25 is illustrated in the Supplementary Fig. S1. During impact loading, a 25 g or 50 g impact mass was dropped from a height of 1 m onto a pressure sensor attached to an implant. The masses were arrested immediately to prevent multiple impacts. The voltage signals received from the pressure sensor were magnified by a charge amplifier (10N/V), and the impulse waveforms were captured with an oscilloscope. Animals in experimental groups received a final impact load of 500 or 1000 N in 0.2 ms in order to observe the trabecular microdamage around the implant, meanwhile, prevent the detachment of the implant based on the results of our pre-experiments (Fig. 1). Then, animals were sacrificed on day 0, 7, 14, or 28, and the implants and surrounding bone were harvested for micro-CT, histomorphometry, immunofluorescence (IF) and RT-qPCR analysis. The sample sizes at each time point are illustrated in Table 1. In the experiment, one femur was dissected for micro-CT, histomorphometry and immunofluorescence randomly, and another femur from the same animal was used for RT-qPCR. So the total sample size was 60, and n (Table 1) indicates the numbers of the femurs from different rabbits. In order to investigate the characteristics of microdamage, the samples of the two experimental groups at 0d were only used for micro-CT and histomorphometry analysis. The 1000N group was chosen for the study of peri-implant bone remodeling following impact due to its more typical microdamage. The sample size of the control group for statistical analysis was the sum of that at every time point, for the control group was not treated with an impact load. Micro-computed Tomography Analysis. Bones containing implants were dissected, fixed in 4% paraformaldehyde and scanned by micro-CT (Inveon Research Workplace 2.2, Siemens Inc., Germany) at a resolution of 19.64 μm with an X-ray voltage of 80 kV and a current of 50 μA. The scanner software (Inveon Acquisition Workplace 2.2, Siemens Inc., Germany) was applied for image reconstruction and analyses. The bone around the implant with 0.5 mm thickness and 5.5 mm length (including 5 mm length of implant and 0.5 mm length of bone under the implant) was chosen as the region of interest (ROI) in each sample for microstructure analyses26 Day 0 7 14 28 Analysis Micro-CT & Histology & IF/RT-qPCR Micro-CT & Histology & IF/RT-qPCR Micro-CT & Histology & IF/RT-qPCR Micro-CT & Histology & IF/RT-qPCR n (Fig. 2a), and parameters such as trabecular bone volume/total volume (Tb.BV/TV, %), trabecular number (Tb.N, mm−1), trabecular thickness (Tb.Th, mm), trabecular separation (Tb.Sp, mm) and bone mineral density (BMD, mg/cc) were measured. Histomorphometry and Immunofluorescence. Undecalcified samples were prepared for subsequent histomorphometry studies. Samples were cleaned of soft tissue, dehydrated in graded alcohols and embedded in methyl methacrylate. Then, sections of 200μm in thickness were cut longitudinally, ground to 20 μm and stained with Van Gieson (VG) and Hematoxylin-Eosin (H&E) for microscopic examination. Images were observed and captured with a light microscope (DMI6000, Leica Inc., Germany). For sclerostin immunofluorescence, sections were washed in phosphate buffered saline (PBS) and blocked in goat serum for 10 min at room temperature. Endogenous peroxidases were quenched with 3% H2O2, and sections were incubated in rabbit sclerostin polyclonal antibody (Bioss Inc., China) for 24 h at 4 °C. After washing in PBS, sections were incubated with secondary antibody labeled with FITC. Images were captured with a confocal laser scanning microscope (CLSM) (Fluo View FV-1000, Olympus Inc., Japan). Fluorescence intensity was measured in five areas of each section using the CLSM software, and the average was calculated for statistical analyses. RNA Extraction and RT-qPCR. Bone tissue at the base of the implant was snap frozen and crushed in liquid N2. According to the manufacturer’s instructions, total RNA was extracted using Trizol reagent and was dissolved in DEPC H2O. cDNA was synthesized using a 10 μl reverse transcription reaction mixture composed of 0.5 μg total RNA, 2 μl 5× PrimeScriptTM Buffer, 0.5 μl PrimeScriptTM RT Enzyme Mix I and 0.5 μl random primer. Partial sequences of SOST, β-catenin, RANKL and β-actin in the reverse transcribed cDNA were amplified using a fluorescence RT-qPCR instrument (RG-3000, Gene Inc., Australia). The forward and reverse primer sequences used for amplification are listed in Supplementary Table S2. Relative mRNA expression levels were standardized to β-actin expression for quantified analyses using the ∆Ct method. Ethics. This study was carried out in strict accordance with the recommendations in the Guide for the Care and Use of Laboratory Animals of the Animal Center of the Fourth Military Medical University. The protocol was approved by the Laboratory Animal Care & Welfare Committee, Fourth Military Medical University (No: 20150201). All surgeries were performed under sodium pentobarbital anesthesia, and all efforts were made to minimize suffering. Statistical Analysis. The data were presented as mean± standard deviation and analyzed using SPSS19.0 (IBM Inc., USA) for one-way ANOVA statistical analyses. Statistical significance was considered as p < 0.05. Results Bone-implant Osseointegration. Implants inserted into the rabbit femoral distal condyle were stable by 3 months after implantation. Micro-CT scan was performed to study the osseointegration at this time. The image showed that the areas around the implant were full of trabeculae. The intact and thick trabeculae were arranged regularly and distributed around and at the bottom of the implant. A good interface was observed between the implant and the bone (Fig. 2a). The Microdamage of Bone around the Implant and the Failure of the Implant-bone Interface. Histological Study. No obvious change in the cortical bone around the implant was observed after impact (Fig. 3a). However, histological study showed that the osseointegration failed at the interface between the bone and the implant. Fractured trabeculae were observed around and at the bottom of the implant. The implant and bone stained with VG are shown in Fig. 3b. In this figure, new bone appeared around the implant threads and at the bottom of implant by 3 months after insertion, and trabeculae were regularly arranged in the control group, which indicated that the osseointegration was favorable. After impact loading, bone tissues in some areas were broken away from the implant, and the trabeculae at the bottom of implant were fractured. This demonstrated that the interface between the implant and the surrounding tissues was incomplete in the experimental groups. Similar microdamage in peri-implant bone is shown in Fig. 3c with H&E staining. Trabeculae around the implant were fractured and disordered under impact loading, while trabeculae in the control group were regularly arranged. Damage photography of interface and surrounding bone was more severe in group 1000 N than in group 500 N. Micro-CT Analyses. The image of micro-CT shows similar failed osseointegration and fractured trabeculae around and at the bottom of the implant (Fig. 2b). To describe the microdamage quantitatively, micro-CT analyses were performed in this study. The results demonstrated that BV/TV and Tb.Th decreased, while Tb.Sp and BMD increased compared with the control group (p < 0.05). The results indicated that the bone mass decreased after impact damage, but BMD increased when the trabeculae were fractured and compressed. There were statistically significant differences in BV/TV and Tb.Sp between the test groups (p< 0.05), which indicated that the damages were different under impact load (Fig. 2c). The Peri-implant Bone Healing Process: From Impact Damage to Remodeling. To investigate the remodeling of peri-implant bone after impact damage, bone structures along the interface between the implant and the bone were studied at different time points. Cancellous bones around the implant are shown in Fig. 4. At day 7 after impact, the gap between the implant and the bone was observed in VG stained sections and the structure of the trabeculae stained with H&E was broken (Fig. 4). The gaps attributed to impact damage were extended, and the trabeculae were scattered at day 14, which indicated that bone absorption may have occurred in this area. By the last time point, the gaps disappeared, and regularly arranged trabeculae were observed. There was no significant difference in the microstructure compared with the control group, which demonstrated that the osseointegration had completely reformed by day 28. Micro-CT scanning and analyses were applied to quantify the changes in trabecular microstructure (Fig. 5). It could be observed that BV/TV, Tb.N decreased while Tb.Sp increased 14 days after impact (p < 0.05). And BMD decreased at day 7 and 14 after temporary increasing at day 0. There was no significant difference in these parameters between the experimental and control group by day 28. These results were consistent with the histomorphological results. Immunofluorescence Staining of Sclerostin in Trabeculae after Impact. Immunofluorescence staining was used to study the expression of sclerostin during the process of remodeling following bone impact damage. Immunofluorescence images are shown in Fig. 6a. In this figure, the sclerostin protein staining is indicated by the green fluorescence points, and sclerostin protein expression is measured as fluorescence intensity in Fig. 6d. From the results (Fig. 6d), it can be observed that the expression of sclerostin was higher than that in the control group on days 7 and 14 after impact (p < 0.05). During the process of remodeling after damage, it increased significantly from day 7 to 14 (p < 0.05). However, there was no obvious difference in expression of sclerostin between the experimental and control group by day 28. The Expression of SOST, β-catenin and RANKL mRNA in Bone Tissue around the Implant after Impact. RT-qPCR was used to quantify the expression of SOST and to correlate sclerostin expression with β-catenin and RANKL. Figure 6b shows the extracted total RNA in agarose gel electrophoresis and Fig. 6c illustrates the SOST PCR amplification curve. The expression of SOST, β-catenin and RANKL mRNA was quantified using the value of 2−∆Ct in Fig. 6e. In the figure, the expression of SOST and RANKL mRNA increased rapidly after impact compared with the control group, and the values reached a maximum at day 14 (p < 0.05). Then, the expression of SOST and RANKL mRNA decreased gradually to the control group levels at day 28. The expression of SOST mRNA was similar to sclerostin protein expression based on the immunofluorescence staining results. The expression of β-catenin mRNA was opposite to that of SOST and RANKL mRNA, and it did not return to the level of the control group completely until day 28 (p < 0.05). Discussion When an implant denture experiences an impact load, there will be microdamages in the peri-implant bone and failure of the implant-bone interface. In addition, the expression of proteins will be changed to modify the bone structure correspondingly. In this study, implants were inserted into the femoral distal condyles of New Zealand white rabbit, and an impact load was applied to the implants after osseointegration occurred. The features of bone damage around the implant and the remodeling of bone were studied through micro-CT analyses and hard tissue slicing with VG and H&E staining. Further, the expression of sclerostin, β-catenin and RANKL were analyzed by immunofluorescence and RT-qPCR during the process of remodeling following bone damage. The results showed that there was no significant change in the cortical bone around the implant, but debonding at the interface and impaired osseointegration in specific areas around the implant were observed. Microdamage in cancellous bone was also observed around the implant. The expression of sclerostin, β-catenin and RANKL correlated with the bone damage and process of remodeling. These data indicate that sclerostin may be involved in bone formation and resorption caused by impact through regulating the Wnt/β-catenin and RANKL/RANK pathways. The results of this study reveal the characteristics of the impact damage to the bone around the implant, and provide a reference for damage assessment and clinical treatment of patients with impact loading. Impact load is a transient load that transmits through or reflects between an implant and bone in stress waves when the pulse duration of the load is in the microsecond range. The stress waves not only spread through the implant-bone interface but also reflect at the interface when they pass through the anisotropic composite structure of the implant and bone9, 27. The impact energy is spread and dissipated quickly along the interface, which may cause the failure of the implant-bone interface and surrounding bone when the energy cannot be absorbed and buffered by this composite structure. However, the characteristics of impact damage in the bone around the implant have not been reported. In this study, microdamage of peri-implant bone under impact was investigated. The results showed that the bone tissue was broken away from the implant and fractured trabeculae around significant difference in the bone mass and BMD compared with the control group. The microstructure of the peri-implant bone returned to normal morphology, and a favorable osseointegration reformed. These results indicate that bone formation is dominated in the process of bone remodeling from day 14 to 28. From these results, it could be observed that the characteristics of the impact damage of bone around the implant were different than that of clinically normal surgical insertion, but the processes of bone remodeling were similar for the formation of the osseointegration around the implant. Therefore, the principles for treatment after insertion surgery could be used as a reference for the management of impact-loaded patients. Sclerostin encoded by the SOST gene is a glycoprotein secreted by osteocytes28–30. Previous studies have reported that there are alterations in its expression in animal models of bone defects or fractures31–34. Changes in the microstructure could cause fluid flow in the bone matrix, which would change the mechanical environment surrounding the osteocytes11. This mechanical signal is sensed and conducted by osteocytes though the lacunar-canalicular system15, 35, 36, and then sclerostin is secreted by osteocytes to adapt to the biomechanical environment37–39. In this study, the expression of sclerostin continued to increase after impact and reached a maximum at day 14. Then, it decreased gradually to normal levels at day 28. From the results above, it can be observed that the expression of sclerostin is related with the process of bone damage and remodeling. Other studies have reported that sclerostin is an effective antagonist of bone formation40–42. The nodular cystine domain in sclerostin allows the protein to competitively bind to the Wnt co-receptor LRP5/6 of the osteoblast. This reduces β-catenin nuclear translocation. As a result, osteoblast activity is decreased, and new bone formation and mineralization are inhibited43, 44. Meanwhile, sclerostin could promote the secretion of RANKL from osteoblasts, which would stimulate the differentiation of osteoclasts from precursors and accelerate bone resorption22. The relationship of sclerostin with the Wnt/β-catenin and RANKL/RANK pathways is illustrated in Fig. 7. In this study, the expression of RANKL mRNA continued to increase with the increase of SOST, while β-catenin decreased over the first 14 days after impact. Then, the expression of RANKL and SOST mRNA decreased gradually to the level of the control group, while, in contrast, β-catenin increased by day 28. The aforementioned changes in protein expression and mRNA levels were consistent with the behavior of peri-implant bone absorption and formation in the micro-CT and histological results. These results suggest that sclerostin may be involved in both bone anabolism and catabolism in response to mechanical stimulation by regulating the Wnt/β-catenin and RANKL/RANK pathways, respectively. The lower expression of β-catenin than that of control group at day 28 in this study indicated that it didn’t reach the normal value. The main reason might be that it will take longer for the cancellous bone to return to normal completely, and β-catenin may continue to increase during this process. In future experiments, the expression of β-catenin and RANKL should be investigated when the expression of sclerostin is down-regulated, and the change in bone microstructure should also be analyzed to determine that whether sclerostin serves as a potential target to regulate bone remodeling under damage through Wnt/β-catenin and RANKL/RANK pathways, which would provide a new therapeutic target for patients with dental implant to improve the osseointegration by regulating the expression of sclerostin. Acknowledgements This study was supported by National Natural Science Foundation of China (Contract no. 11672327). Author Contributions D.X. and X.H. contributed to the design of the study. D.X., L.Z., A.B., F.F. and D.C. contributed to the acquisition, collection and assembly of data. D.X. and X.H. contributed to the statistical analyses of data and wrote the main manuscript text. D.X., X.H., W.Y. and L.K. contributed in revising the manuscript. All authors reviewed the manuscript and approved the final version to be submitted. Competing Interests: The authors declare that they have no competing interests. Publisher's note: Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations. Open Access This article is licensed under a Creative Commons Attribution 4.0 International License, which permits use, sharing, adaptation, distribution and reproduction in any medium or format, as long as you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The images or other third party material in this article are included in the article’s Creative Commons license, unless indicated otherwise in a credit line to the material. If material is not included in the article’s Creative Commons license and your intended use is not permitted by statutory regulation or exceeds the permitted use, you will need to obtain permission directly from the copyright holder. To view a copy of this license, visit http://creativecommons.org/licenses/by/4.0/. 1. Southam , J. C. & Selwyn , P. Structural changes around screws used in the treatment of fractured human mandibles . Br J Oral Surg . 8 , 211 - 221 ( 1971 ). 2. Branemark , R. , Branemark , P. I. , Rydevik , B. & Myers , R. R. Osseointegration in skeletal reconstruction and rehabilitation: a review . J Rehabil Res Dev . 38 , 175 - 181 ( 2001 ). 3. Palmquist , A. , Snis , A. , Emanuelsson , L. , Browne , M. & Thomsen , P. Long-term biocompatibility and osseointegration of electron beam melted, free-form-fabricated solid and porous titanium alloy: experimental studies in sheep . J Biomater Appl . 27 , 1003 - 1016 ( 2013 ). 4. Adell , R. Tissue integrated prostheses in clinical dentistry . Int Dent J . 35 , 259 - 265 ( 1985 ). 5. Isidor , F. Loss of osseointegration caused by occlusal load of oral implants. A clinical and radiographic study in monkeys . Clin Oral Implants Res . 7 , 143 - 152 ( 1996 ). 6. Stanford , C. M. & Brand , R. A. Toward an understanding of implant occlusion and strain adaptive bone modeling and remodeling . J Prosthet Dent . 81 , 553 - 561 ( 1999 ). 7. Leucht , P. et al. Effect of mechanical stimuli on skeletal regeneration around implants . Bone . 40 , 919 - 930 ( 2007 ). 8. Jing , D. et al. Effect of low-level mechanical vibration on osteogenesis and osseointegration of porous titanium implants in the repair of long bone defects . Sci Rep . 5 , 17134 , doi:10.1038/srep17134 ( 2015 ). 9. Gilardi , G. & Sharf , I. Literature survey of contact dynamics modelling . Mech and Mach Theory . 37 , 1213 - 1239 ( 2002 ). 10. Rubin , C. T. Skeletal strain and the functional significance of bone architecture . Calcif Tissue Int . 36 , S11 - 8 ( 1984 ). 11. Turner , C. H. , Forwood , M. R. & Otter , M. W. Mechanotransduction in bone: do bone cells act as sensors of fluid flow? FASEB J . 8 , 875 - 878 ( 1994 ). 12. Ehrlich , P. J. & Lanyon , L. E. Mechanical Strain and Bone Cell Function: A Review . Osteoporos Int . 13 , 688 - 700 ( 2002 ). 13. Bonewald , L. F. Generation and function of osteocyte dendritic processes . J Musculoskelet Neuronal Interact . 5 , 321 - 324 ( 2005 ). 14. Klein-Nulend , J. , Bacabac , R. G. & Mullender , M. G. Mechanobiology of bone tissue . Pathol Biol . 53 , 576 - 580 ( 2005 ). 15. Klein-Nulend , J. et al. Sensitivity of osteocytes to biomechanical stress in vitro . FASEB J . 9 , 441 - 445 ( 1995 ). 16. Xiong , J. et al. Matrix-embedded cells control osteoclast formation . Nat Med . 17 , 1235 - 1241 ( 2011 ). 17. Veverka , V. et al. Characterization of the structural features and interactions of sclerostin: molecular insight into a key regulator of Wnt-mediated bone formation . J Biol Chem . 284 , 10890 - 10900 ( 2009 ). 18. Costa , A. G. , Bilezikian , J. P. & Lewiecki , E. M. Update on romosozumab: a humanized monoclonal antibody to sclerostin . Expert Opin Biol Ther . 14 , 697 - 707 ( 2014 ). 19. van Bezooijen, R. L. et al. Wnt but not BMP signaling is involved in the inhibitory action of sclerostin on BMP-stimulated bone formation . J Bone Miner Res . 22 , 19 - 28 ( 2007 ). 20. van Dinther, M. et al. Anti-Sclerostin antibody inhibits internalization of Sclerostin and Sclerostin-mediated antagonism of Wnt/ LRP6 signaling . PLoS One . 8 , e62295 , doi:10.1371/journal.pone. 0062295 ( 2013 ). 21. Poole , K. E. et al. Sclerostin is a delayed secreted product of osteocytes that inhibits bone formation . FASEB J . 19 , 1842 - 1844 ( 2005 ). 22. Wijenayaka , A. R. et al. Sclerostin stimulates osteocyte support of osteoclast activity by a RANKL-dependent pathway . PLoS One . 6 , e25900 , doi:10.1371/journal.pone. 0025900 ( 2011 ). 23. An , B. et al. In vitro and in vivo studies of ultrafine-grain Ti as dental implant material processed by ECAP . Mater Sci Eng C . 67 , 34 - 41 ( 2016 ). 24. Dudli , S. , Haschtmann , D. & Ferguson , S. J. Prior storage conditions and loading rate affect the in vitro fracture response of spinal segments under impact loading . J Biomech . 44 , 2351 - 2355 ( 2011 ). 25. Barr , L. , Getgood , A. , Guehring , H. , Rushton , N. & Henson , F. M. The effect of recombinant human fibroblast growth factor-18 on articular cartilage following single impact load . J Orthop Res . 32 , 923 - 927 ( 2014 ). 26. Sasaki , M. , Kuroshima , S. , Aoki , Y. , Inaba , N. & Sawase , T. Ultrastructural alterations of osteocyte morphology via loaded implants in rabbit tibiae . J Biomech . 48 , 4130 - 4141 ( 2015 ). 27. Lee , N. et al. The geometric effects of a woodpecker's hyoid apparatus for stress wave mitigation . Bioinspir Biomim . 11 , 066004 ( 2016 ). 28. Balemans , W. et al. Increased bone density in sclerosteosis is due to the deficiency of a novel secreted protein (SOST) . Hum Mol Genet . 10 , 537 - 543 ( 2001 ). 29. Brunkow , M. E. et al. Bone dysplasia sclerosteosis results from loss of the SOST gene product, a novel cystine knot-containing protein . Am J Hum Genet . 68 , 577 - 589 ( 2001 ). 30. Collette , N. M. et al. Targeted deletion of Sost distal enhancer increases bone formation and bone mass . Proc Natl Acad Sci USA . 109 , 14092 - 14097 ( 2012 ). 31. Morse , A. et al. Endochondral fracture healing with external fixation in the Sost knockout mouse results in earlier fibrocartilage callus removal and increased bone volume fraction and strength . Bone . 71 , 155 - 163 ( 2015 ). 32. Li , C. et al. Increased callus mass and enhanced strength during fracture healing in mice lacking the sclerostin gene . Bone . 49 , 1178 - 1185 ( 2011 ). 33. McGee-Lawrence , M. E. et al. Sclerostin deficient mice rapidly heal bone defects by activating β-catenin and increasing intramembranous ossification . Biochem Biophys Res Commun . 441 , 886 - 890 ( 2013 ). 34. Gao , F. , Zhang , C. Q. , Chai , Y. M. & Li , X. L. Systemic administration of sclerostin monoclonal antibody accelerates fracture healing in the femoral osteotomy model of young rats . Int Immunopharmacol . 24 , 7 - 13 ( 2015 ). 35. Thompson , W. R. et al. Osteocyte specific responses to soluble and mechanical stimuli in a stem cell derived culture model . Sci Rep . 5 , 11049 , doi:10.1038/srep11049 ( 2015 ). 36. Thompson , W. R. , Rubin , C. T. & Rubin , J. Mechanical regulation of signaling pathways in bone . Gene . 503 , 179 - 193 ( 2012 ). 37. Morse , A. et al. Mechanical load increases in bone formation via a sclerostin-independent pathway . J Bone Miner Res . 29 , 2456 - 2467 ( 2014 ). 38. Spatz , J. M. et al. Sclerostin antibody inhibits skeletal deterioration due to reduced mechanical loading . J Bone Miner Res . 28 , 865 - 874 ( 2013 ). 39. Robling , A. G. et al. Mechanical stimulation of bone in vivo reduces osteocyte expression of Sost/sclerostin . J Biol Chem . 283 , 5866 - 5875 ( 2008 ). 40. Tu , X. L. et al. Sost downregulation and local Wnt signaling are required for the osteogenic response to mechanical loading . Bone . 50 , 209 - 217 ( 2012 ). 41. Tu , X. L. et al. Osteocytes mediate the anabolic actions of canonical Wnt/beta-catenin signaling in bone . Proc Natl Acad Sci U S A . 112 , E478 - 486 ( 2015 ). 42. Suen , P. K. et al. Sclerostin Antibody Treatment Increases Bone Formation, Bone Mass, and Bone Strength of Intact Bones in Adult Male Rats . Sci Rep . 5 , 15632 , doi:10.1038/srep15632 ( 2015 ). 43. Semenov , M. , Tamai , K. & He , X. SOST is a ligand for LRP5/LRP6 and a Wnt signaling inhibitor . J Biol Chem . 280 , 26770 - 26775 ( 2005 ). 44. Glass , D. A. II & Karsenty , G. Molecular Bases of the Regulation of Bone Remodeling by the Canonical Wnt Signaling Pathway . Curr Top Dev Biol . 73 , 43 - 84 ( 2006 ). Additional Information Supplementary information accompanies this paper at doi:10.1038/s41598-017-06867-9