Synergistic Effect of Micro-Nano-Hybrid Surfaces and Sr Doping on the Osteogenic and Angiogenic Capacity of Hydroxyapatite Bioceramics Scaffolds

Introduction

Bone transplantation is a crucial method to reconstruct bone defects caused by trauma, tumors, and other diseases, and autologous bone grafts remain the “gold standard” for bone transplantation. However, the limitation of insufficient bone mass and related postoperative complications have facilitated the development of substitute materials.^1,2 Bioceramic materials are widely used as a physiological scaffold for bone defect repair because of its excellent biocompatibility and bioactivity, and are currently considered as the most promising alternative to autologous bone grafting. The porous structure of bioceramics facilitates the adhesion of osteoblasts, transport of nutrients, and speeds up the process of bone resorption and reconstruction,³ which makes it better for repairing large bone defects.⁴

The inorganic minerals in human bone tissue have a multilevel ordered structure and contain many microelements. From the viewpoint of bio mimics, we can tune the osteoinduction ability of materials by controlling the surface microstructure and element doping. The ideal scaffold materials for bone regeneration require an appropriate three-dimensional microporous structure for cell growth and nutrient metabolism.^2,5 For bioceramics scaffolds, the pores are 150 ~ 500 μm in diameter and over 50% in porosity are appropriate to stimulate cell response, and nanostructured surfaces and high connectivity between pores is also important.^1,6–8 The results of our recent study confirmed that the HAp bioceramics with nanostructured modified topography significantly enhanced cell viability, spreading, and osteogenic differentiation of BMSCs and bone formation, mineralization and vascularization in vivo.⁹ Moreover, suitable surface chemistry plays critical roles in cell viability, spreading, proliferation, and osteogenic differentiation.^2,5 Biomaterials can be modified by the introduction of functional inorganic ions. Recently, more attention has been given to strontium (Sr), which is an important trace element in the human body, and 99% of Sr exists in bones. Sr can improve the mechanical properties and modify the bone balance toward osteosynthesis.¹⁰ Recent studies¹¹ have found that Sr can enhance the proliferation of osteoblasts during bone metabolism. Yang et al¹² suggested that the surface of Sr-doped hydroxyapatite can significantly increase the growth of osteoblasts. The results of Wang et al¹³ confirmed that the Sr-HAp coatings significantly promoted osteoblast attachment and proliferation as the Sr content increased. Recently, researchers focused on the preparation of strontium-substituted bioceramics and their application in bone regeneration.^14–16 However, few studies have focused on the synergistic promotion of nanostructures and Sr doping on bone regeneration.

Therefore, based on the above research and our previous results,^9,17 we proposed that the combination of nanostructure surfaces and Sr-doping might lead to synergistic enhancement of osteogenesis and angiogenesis.^18,19 Herein, HAp bioceramics with micro-nano-hybrid surfaces and different strontium (Sr) doping contents of 2.5, 5, 10, and 20% (Sr_x-mnHAp, x: 2.5, 5, 10 and 20%) were fabricated via the hydrothermal transformation method. The effect on cell adhesion, proliferation, and ALP activity and the expression of genes involved in osteogenesis and angiogenesis were investigated to determine the optimal Sr doping content, followed by calvarial defect experiments to evaluate bone regeneration and vascularization in vivo.

Materials and Methods

Preparation of Micro-Nano-Hybrid HAp (mnHAp) and Sr-Doped mnHAp (Sr_x-mnHAp) Bioceramics

The micro-nano-hybrid HAp (mnHAp) and Sr-doped mnHAp (Sr_x-mnHAp, x: 2.5, 5, 10 and 20%) bioceramics were prepared by the hydrothermal transformation method. First, ɑ-tricalcium phosphate (ɑ-TCP) and Sr-doped ɑ-TCP with different doping contents of 2.5, 5, 10, and 20% (Sr_x-ɑ-TCP, x: 2.5, 5, 10 and 20%) powders were synthesized by chemical precipitation.²⁰ Then, the synthesized ɑ-TCP and Sr_x-ɑ-TCP powders were mixed with 7 wt% polyvinyl alcohol (PVA), dry-pressed into discs 10 mm in diameter and 2 mm in thickness under a pressure of 5 MPa, and further calcined at 1050 °C for 5 h to obtain ɑ-TCP and Sr_x-ɑ-TCP bioceramics, respectively.²¹ Finally, the mnHAp and Sr_x-mnHAp bioceramics were prepared using ɑ-TCP and Sr-ɑ-TCP discs as precursors via hydrothermal reaction in pH=7 aqueous solution at 180 °C for 72 h.^17,20 In addition, HAp bioceramics with dense and flat surfaces were used as controls and labeled S0.⁹

Samples Characterization

HAp (S0), mnHAp (S3), and Sr_x-mnHAp (x: 2.5, 5, 10 and 20%) were incubated in 1 mL of α-Minimum Essential Medium (ɑ-MEM, Gibco, USA) for 1 and 4 d, respectively. The medium of each sample changed daily and the concentrations of Sr, Ca, and P ions released from HAp, mnHAp, and Sr_x-mnHAp at each timepoint were evaluated using inductively coupled plasma-atomic emission spectrometry (ICP-AES). The crystal phase compositions of the samples were determined with XRD (Rigaku, Japan), and the surface microstructures were observed by SEM (JEOL, Japan).¹⁷

Cell Extraction and Culture

Bone marrow stem cells (BMSCs) were harvested as previously described.¹⁷ Briefly, Sprague–Dawley (SD) rats (4 weeks old) were selected and injected intraperitoneally with an overdose of pentobarbital sodium. The scalp was separated for exposure, and both femora were cut off. Fresh marrow was flushed out and cultured in ɑ-MEM (Gibco, USA) containing 10% FBS (Gibco, USA) and 1% penicillin and streptomycin (Hyclone, USA). The culture medium was maintained at 37 °C in a 5% CO₂ incubator and renewed 3 times a week. The cells were passaged after reaching 90% confluence, and passages 2–4 were used in the following experiment. All animal experiments and procedures received approval from the Animal Ethics Committee of the Shanghai Ninth People’s Hospital Affiliated to Shanghai Jiaotong University, School of Medicine and conducted in compliance with the guidelines of Institutional Animal Care and Use Committee of Shanghai Ninth People’s Hospital Affiliated to Shanghai JiaoTong University, School of Medicine [SYXK (Hu) 2016–0016].

Cell Morphology and Adhesion

Phalloidin staining was performed to evaluate the morphology and spreading of the BMSCs seeded onto samples S0, S3, 2.5Sr, 5Sr, 10Sr, and 20Sr at an initial density of 1×10⁴ cells per mL in 24-well plates. At 6 h after seeding, all specimens were fixed with 4% formaldehyde for 10 min, and then treated with 1% Triton X-100 for 5 min. Next, these specimens were incubated with phalloidin (Sigma, USA) for 30 min, followed by DAPI (Sigma, USA) for approximately 30s. Finally, actin cytoskeletons were observed by fluorescence microscopy (Leica, Germany).

Cell Proliferation

The proliferation of BMSCs in the samples was investigated by MTT assay, with a cell density of 1×10⁴ cells per mL in 24-well plates. After culturing for 1, 4, and 7 d, the culture medium was replaced, and the BMSC-seeded bioceramics were rinsed and incubated with sterile MTT (Amresco, USA) at 37 °C for 4 h. DMSO solution (Sigma, USA) was then added and incubated for 10 min to dissolve formazan. The OD value was read at 490 nm by a microplate Reader (Biotek, USA). All experiments were repeated 3 times.

ALP Staining and Activity

BMSCs were cultured onto S0, S3, 2.5Sr, 5Sr, 10Sr, and 20Sr samples at a cell density of 1×10⁴ cells per mL in 24-well plates. After culturing for 10 d, ALP staining was performed with a BCIP/NBT Alkaline Phosphatase Color Development Kit (Beyotime, China). The ALP activity was then assessed at 4, 7, and 10 d.²² Briefly, all samples were lysed in 1% Triton X-100 for 30 min at 4 °C, and the cellular lysate of each well was collected and centrifuged at 4 °C (12,000 rpm × 10 min). Then, the OD value was determined at 520 nm with a microplate Reader (Bio-Tek, USA), and total cellular protein was determined by a BCA protein kit (Beyotime, China) at 562 nm. Finally, ALP activity was evaluated by normalizing to total protein content. All experiments were repeated 3 times.

Quantitative Real-Time PCR (qRT-PCR) and Western Blot Experiment

qRT-PCR was carried out to assess the expression of osteogenic and angiogenic factors in BMSCs cultured in samples S0, S3, 2.5Sr, 5Sr, 10Sr, and 20Sr. After culturing for 4 and 7 d, total RNA of the samples was isolated according to our previous study.²¹ Briefly, the cells cultured in the bioceramics were lysed in TRIzol Reagent (Life Technologies, USA) and reverse transcribed to cDNA by PrimeScript^TM RT reagent Kit (TaKaRa, Japan). The expression levels of osteogenesis- and angiogenesis-related genes were further evaluated by qRT-PCR analysis, including COL1, BSP, BMP-2, OPN, VEGF, and ANG-1. GAPDH was selected as a housekeeping gene to normalize the expression level. The primer sequences selected are listed in Table 1. All experiments were repeated 3 times.

Table 1 Primer Sequences of the Selected Genes

Western blot experiment was applied to assess expression of BMP-2. BMSCs were cultured in samples S0, S3, 2.5Sr, 5Sr, 10Sr, and 20Sr for 7 d. Total protein was extracted and centrifuged at 12,000 rpm for 15 minutes. Then, the samples were separated via sodium dodecyl sulfate polyacrylamide gel electrophoresis (SDS-PAGE) at 80 volts for 20 minutes and 120 volts for 50 minutes, and transferred to polyvinylidene fluoride membranes (PVDF, Millipore, USA). The PVDF membranes were incubated with primary antibody (Abcam, UK) at 37 °C for 2h. After that, the membranes were incubated with HRP-conjugated secondary antibody (Abcam, UK) for 1 h at room temperature. The protein bands were visualized, and the images were captured by an automated luminescent image analysis system (Tanon, China).

Animal Experiment

Calvarial defects were established in twelve 6-week-old SD rats as previously described.¹⁷ Animal experiments and procedures received approval from the Animal Ethics Committee of the Shanghai Ninth People’s Hospital Affiliated to Shanghai Jiaotong University, School of Medicine. All rats were randomly divided into the following 3 groups: S0, S3, and 10Sr (n = 4 for each group). Briefly, all rats were injected intraperitoneally with pentobarbital (3.5 mg/100 g). Under sterile conditions, a 2 cm longitudinal incision was made, and two symmetrical round defects (5 mm in diameter) were created using the implant drill at each rat. Subsequently, the HAp, mnHAp, and Sr₁₀-mnHAp were placed into the defects, and the operation incision was carefully sutured with absorbable sutures.

Micro-CT Analyses

At the 8th week after implantation, all rats were sacrificed and perfused with Microfil (Flowtech, USA) to observe new blood vessels.²³ The samples were decalcified using EDTA for 1 month and then scanned by microcomputed tomography (Scanco, Switzerland), the percentages of new blood vessels were quantitatively determined with Image-Pro 5.0 (Media Cybernetic, USA). For the observation of new bone, the specimens were fixed in 4% paraformaldehyde for 2 d and then transferred to 75% alcohol. Finally, the samples were scanned by microcomputed tomography. Bone volume fraction (BV/TV) and trabecular thickness (Tb. Th) were calculated with auxiliary software (Scanco, Switzerland).²⁴

Histological Analyses

All specimens were decalcified with 10% EDTA, dehydrated in increased concentrations of ethanol (75% to 100%) and embedded in PMMA for 3 weeks. Tissue blocks were sectioned by a microtome (Leica, Germany) and further ground to approximately 40 μm. Next, the sections were subjected to Van Gieson staining for histological analysis, and the proportion of bone regeneration in the defect area was quantitatively determined with Image-Pro 5.0 (Media Cybernetic, USA).^17,25

Statistical Analyses

All data are expressed as the means ± standard deviation (SD), and statistical analysis was performed using SPSS 17.0 software (SPSS Inc., USA). A p value <0.05 was considered statistically significant.

Results

Characterization of the Samples

XRD results of mnHAp and Sr_x-mnHAp (x: 2.5, 5, 10 and 20%) are shown in Figure 1. All the diffraction peaks confirmed that these samples were converted into HAp without any other phases after the hydrothermal transformation method. The obvious micro-nanorods topography surfaces of mnHAp (Figure 2B) and Sr_x-mnHAp (Figure 2C–F) could be observed by SEM, and Sr₁₀-mnHAp possessed the densest rod-shaped structure (Figure 2E). The lengths of the microrods and nanorods were approximately 10~20 μm, while the diameters were approximately 1~4 μm and 80~120 nm, respectively. As a comparison, a dense and flat surface with a particle size of approximately 0.9 µm was observed on control sample S0 (Figure 2A).

Figure 1 XRD results of mnHAp (S3) and Srx-mnHAp bioceramics (2.5Sr, 5Sr, 10Sr, 20Sr).

Figure 2 SEM micrographs of topographic surface for HAp (A), mnHAp (B), and Srx-mnHAp (C–F): (A) scale bar=500 nm, (B-F) scale bar=20 μm.

The results of ICP-AES analysis revealed that the release of Sr ions could be detected in Sr_x-mnHAp bioceramics and showed an ascending trend with increasing Sr content at each timepoint (Figure 3C). No significant differences in the release amount of Ca and P could be found among HAp, mnHAp, and Sr_x-mnHAp (Figure 3A and B).

Figure 3 The release of Ca (A), P (B), and Sr (C) ions at 1 and 4 d.

The Morphology of BMSCs

As shown in Figure 4, the actin cytoskeleton was stained red, and the nucleus was stained blue. After being cultured for 6 h, fluorescence microscopy images showed that the cells seeded in sample S0 spread slightly and almost had a round shape (Figure 4A1). Meanwhile, as a comparison, the cells seeded on the mnHAp (S3, 2.5Sr, 5Sr, 10Sr, and 20Sr) exhibited better early cell attachment and demonstrated a typical polygonal morphology with apparent stretch tentacles. No significant differences in the cell morphology and quantity could be found with increasing Sr content. This experiment showed that the nanostructure surface could promote the early cell attachment of BMSCs instead of the concentrations of Sr ions.

Figure 4 Fluorescence microscopy images of the cells in samples S0, S3, 2.5Sr, 5Sr, 10Sr, and 20Sr after 6 h: red represents the actin cytoskeleton (A1–F1), blue represents the nucleus (A2–F2), and the merged images of the actin cytoskeleton and the nucleus (A3–F3): scale bar=50 μm.

Cell Proliferation

The cells adhered to the HAp, mnHAp and Sr_x-mnHAp bioceramics proliferated through the MTT assay (Figure 5). The cells cultured on mnHAp (S3, 2.5Sr, 5Sr, 10Sr, and 20Sr) displayed higher proliferation than control samples on days 4 and 7. (p<0.05) In addition, among the Sr_x-mnHAp with different Sr contents, proliferation significantly proceeded on Sr₁₀-mnHAp and Sr₂₀-mnHAp on days 4 and 7 (p<0.05).

Figure 5 MTT analysis of the cells seeded in samples S0, S3, 2.5Sr, 5Sr, 10Sr and 20Sr. (* indicates a significant difference with S0, Δ indicates a significant difference with S3, p<0.05).

ALP Activity Assay

The cells cultured on mnHAp bioceramics possessed more intensive ALP staining, with control samples (dense and flat surface) compared (Figure 6A). Moreover, the staining became deeper with Sr doping (2.5Sr, 5Sr, 10Sr, and 20Sr). In particular, the deepest staining was found on the Sr₁₀-mnHAp sample. The ALP semi-quantification assay on days 4, 7 and 10 further confirmed the staining results (Figure 6B). The ALP activity increased throughout the whole assay period, and the mnHAp bioceramics possessed higher cellular ALP activity. More importantly, the samples with Sr doping achieved better ALP activity on days 4 and 7 (p<0.05). When the experiment time was extended to 10 d, compared to mnHAp, only Sr₁₀-mnHAp and Sr₂₀-mnHAp further enhanced ALP activity.

Figure 6 ALP activity measurement: (A) ALP staining of BMSCs seeded onto samples S0, S3, 2.5Sr, 5Sr, 10Sr, and 20Sr at 10 d. (B) ALP quantitative analysis of cells seeded in samples S0, S3, 2.5Sr, 5Sr, 10Sr and 20Sr for 4, 7 and 10 d. (*indicates a significant difference with S0, Δ indicates a significant difference with S3, p<0.05).

qRT–PCR Assay and Western Blot Experiment

qRT–PCR was carried out to analyze the expression of osteogenesis and angiogenesis factors in the cells cultured on HAp, mnHAp and Sr_x-mnHAp at days 4 and 7. As shown in Figure 7, the mnHAp bioceramics (S3, 2.5Sr, 5Sr, 10Sr, and 20Sr) could strengthen the expression of COL1, BSP, BMP-2, OPN, VEGF and ANG-1 with sample S0 (dense and flat surface) compared at 4 and 7 d. Furthermore, Sr doping improved the mRNA levels of COL1, BSP, and OPN at 4 and 7 d and ANG-1 at 7 d. The western bolt result of day 7 confirmed the enhanced expression of BMP-2 in the Sr_x-mnHAp, especially in the Sr₁₀-mnHAp. More importantly, the promotion effect of Sr doping occurred in a dose-dependent manner, and Sr₁₀-mnHAp achieved the best stimulation ability.

Figure 7 qRT–PCR analysis of the expression of COL1 (A), BMP-2 (B), BSP (C), OPN (D), VEGF (E), and ANG-1 (F) and Western blot result of BMP-2 (G). (*indicates a significant difference with S0, Δ indicates a significant difference with S3, p<0.05).

Micro-CT Measurement

Micro-CT scanning and analysis were performed to assess the bone regeneration of the calvarial defect areas. From Figure 8A, we can see that more bone formation in the surface and pores of the mnHAp bioceramics at the 8^th week after implantation (p<0.05) and Sr₁₀-mnHAp achieved the best repair effect with S0 and S3 compared (p<0.05). Morphometric analysis further proved that the BV/TV ratio (Figure 8B) and Tb. Th (Figure 8C) in mnHAp bioceramics were higher than that of pure HAp. Moreover, significant differences were found between mnHAp and Sr₁₀-mnHAp (p<0.05). Figure 9 showed the angiographic results, more blood vessels were found in the implant site of the mnHAp bioceramics (p<0.05), and the Sr₁₀-mnHAp groups possessed the most newly formed blood vessels. The results of quantitative analysis also confirmed that samples S3 and 10Sr possessed more blood vessels, and the differences between samples 10Sr and S3 were remarkable (p<0.05).

Figure 8 Micro-CT assessment at 8 weeks after implantation. (A) 3D and 2D images of newly formed bone of groups S0, S3, and 10Sr. Quantitative measurement of the BV/TV ratio (B) and Tb. Th (C). (*indicates a significant difference with S0, Δ indicates a significant difference with S3, p<0.05).

Figure 9 Micro-CT angiography at the 8th week after implantation. (A) Images of new blood vessels in groups S0, S3, and 10Sr. (B) Quantitative measurement of the new blood vessel area. (*indicates a significant difference with S0, Δ indicates a significant difference with S3, p<0.05).

Histological and Histomorphometric Analysis

Van Gieson staining was applied to observe bone regeneration in the surface and pores of the HAp bioceramics. As shown in Figure 10A, bone formation was only found on the edge of the defect in group S0, while groups S3 and 10Sr achieved more new bone formation from the margins to the Center, especially group 10Sr. As shown in Figure 10B, the results of bone histomorphometric analysis further confirmed that groups S3 and 10Sr possessed more newly formed bone areas. More importantly, remarkable differences could be found between groups S3 and 10Sr, which indicates that Sr₁₀-mnHAp has the best effect on promoting bone formation (p<0.05).

Figure 10 Histological and histomorphometric analysis: (A) Images of Van Gieson’s staining of bone formation at the 8th week after implantation. (B) Quantitative measurement of the new bone area. (*indicates a significant difference with S0, Δ indicates a significant difference with S3, p<0.05).

Discussion

The skeleton is an integral part of the human body and has a limited capacity to regenerate after large bone defects caused by acute injuries, fall fractures, or tumors. The repair of bone defects and bone regeneration remain challenging problems in clinical treatment.² Currently, reconstruction of these skeletal defects is often achieved by autogenous and allogeneic bone transplantation, although they have drawbacks separately. The emergence and development of tissue engineering offers tremendous potential. HAp ceramics are a multifunctional biological material with good biocompatibility and bioactivity but are limited in Clinical application because of their insufficient osteoinduction ability.⁴ Osteoblast/material interactions play a fundamental role in the biological response of host cells and can be modified by the surface characteristics of bone grafts.²⁶

Numerous studies have shown that controlling the surface morphology and roughness of materials is a direct and effective strategy to improve biological properties, and surface topography can affect cell attachment and subsequent proliferation and differentiation.^9,27–29 Our previous study demonstrated that the microstructure surface can support cell adhesion, which is critical for osteogenic proliferation and differentiation.⁹ Changing the chemical compositions of the surface by element doping can also improve the osteogenic properties of biomaterials.²¹ Trace elementSr has been applied to the preparation of bone tissue engineering scaffolds, which can promote bone regeneration and inhibit bone resorption.³⁰ Previous studies showed that appropriate release of Sr ions could activate osteogenesis-related signal transduction pathways, stimulate osteogenesis gene expression and ultimately new bone formation in a dose-dependent manner.^31,32 Most of the previous studies mainly focused on the effects and underlying mechanisms of surface modification or chemical composition changes on the biological characteristics. Whether osteogenic differentiation and angiogenesis could be promoted by topographic modification and element doping is still lacking and requires further evaluation.

Herein, HAp bioceramics with micro-nano-hybrid surfaces and different Sr doping contents (Sr_x-mnHAp, x: 2.5, 5, 10 and 20%) were synthesized using Sr_x-α-TCP as a precursor via hydrothermal transformation.²⁰ The XRD patterns confirmed that all the samples were completely transformed into HAp, and the visible micro-nanorods structure on the surface of mnHAp and Sr_x-mnHAp could be observed by SEM. According to the ICP-AES analysis, the release of Sr ions could be detected in the Sr_x-mnHAp bioceramics, and the concentration was between 0.2 and 1.0 ug mL⁻¹. Previous Research suggested that the suitable concentration of Sr ions varies from 0.2107 to 21.07 μg mL⁻¹, which indicated that the release of Sr is in an appropriate range.³³

Subsequently, the effects of mnHAp and Sr_x-mnHAp bioceramics on BMSCs were evaluated in vitro. Previous studies have suggested that the physical properties of biomaterial scaffolds can affect adhesion, migration, and differentiation into osteoblasts.^34–37 The cytoskeleton staining assay showed that the cells cultured on the mnHAp exhibited better cell attachment, with typical fibroblastic morphology. However, Sr doping did not significantly promote cell attachment or extension. It indicates that the nanostructure surface, instead of Sr ions, is the Key promotion factor of cellular responses in the early stages. ALP is considered to be an indicator of osteogenic differentiation and an important index of bone formation and turnover. BMP-2 is the strongest osteoinduction cytokine and can promote bone formation and growth. OCN is tightly related to the maturation of osteoblasts,³⁸ and COL1 and BSP are vital genes involved in osteoblastic differentiation. VEGF is the most important factor in angiogenesis, and ANG-1 plays a basic role in promoting maturity and maintaining vascular stabilization. According to the results of MTT, ALP activity, and PCR assays, the mnHAp bioceramics could facilitate proliferation ability, ALP activity and mRNA expression of COL1, BSP, BMP-2, OPN, VEGF, and ANG-1, which is consistent with our previous results.^22,39 More importantly, Sr doping furthers promoted cellular osteogenic activity, while Sr₁₀-mnHAp possessed the best stimulatory effect. In addition, the results of calvarial defects confirmed that the mnHAp bioceramics could promote bone and blood vessel regeneration with the control samples (dense and flat surface). More importantly, Sr doping further promoted bone and blood vessel regeneration, while Sr₁₀-mnHAp possessed the most stimulatory effect. All the above results proved our hypothesis that micro-nano-hybrid surface and Sr doping had synergistic promotion effects on bone regeneration, the Sr_x-mnHAp bioceramics can be a promising material for bone defect repair. Meanwhile, its multifunctional properties make it a good candidate for potential biomedical applications, including targeted drug delivery applications, and the stable and controlled release of drugs is worthy of further investigation.

Conclusion

Surface structure and chemical composition are considered to be the key clues to regulate the biological response of biomaterials. Herein, HAp bioceramics with micro-nano-hybrid surface and different Sr doping contents (Sr_x-mnHAp, x: 2.5, 5, 10 and 20%) were successfully fabricated via a hydrothermal transformation method using Sr_x-ɑ-TCP powder as a precursor without additives. The nanostructure surface can support cell adhesion, and Sr-doping could further enhance osteogenic differentiation with an optimal doping concentration of 10%. Finally, the calvarial defect model showed that the Sr₁₀-mnHAp bioceramics scaffolds possessed better bone regeneration capacity. All of the results confirmed our hypothesis that micro-nano-hybrid surface and Sr doping have synergistic effects on bone regeneration and provided a new strategy for improving the osteoinduction ability of traditional bioceramics.