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Additional file 1: Figure S1. a 1H NMR spectraof GelMA and gelatin in D2O. Figure S2. a Optical images of@MNs. b, c Cross-sectional SEM images of theMN tips. Scale bars are 2 mm in, 200 µm in, and 50 µm in. Figure S3. a, b Digital photosand H&E staining images of the puncture of the@MNs on skinandlivertissues in rats. Scale bars are 2mm, 2 mm, and 200 µm from left toright in. Figure S4. UV spectra of BSP,BY, and Carbomer hydrogels. Figure S5. The pro-activatingplatelet ability. a SEM images of platelets activated by the@MNs. b Immunofluorescence staining of CD62p indicating the activation of platelets bythe@MNs. Scale bars are 50 µm, 25 µm, 10 µm, 2.5 µm from left to rightin, and 50 µm in. Figure S6. a Visualization images of activated partialthromboplastin timein different groups. b Quantitative analysis ofAPPT. Figure S7. Respective photographs and corresponding quantitativeanalysis of hemocompatibility for the a EGF, b BY and c @MNs. Figure S8. Cytocompatibility ofthe@MNs. a CCK-8 assay of the NIH3T3 cells cultured with the@MNsfor 3 days. b Live/dead staining images ondays 1, 2, and 3. The scale bar is 100 µm in. Figure S9. a Representativeoptical images of the scratch assay of the NIH3T3 cells cultured in gradientEGF solutions. b Quantification of closure rates in the scratch assay. The scale bar is100 µm in. Figure S10. Quantitative analysisof a AST and b ALT on day 28. Figure S11. a Representative immunofluorescent stainingimages and b semi-quantitative analysis of α-SMA. Figure S12. a Representative immunofluorescent stainingimages and b semi-quantitative analysis of α-SMA. The α-SMA isindicated in green. Scale bar are 200 µm in.

Supplementary Material 1

Additional file 1: Figure S1. SEM images of (a) the silica colloidal crystal template, (b) the PS hybrid colloidal crystal template, (c) the PS inverse opal film. Scale bars are 500 nm. Figure S2. Different stretching degrees. (a) 3-times, (b) 6-times, (c) 9-times, (d) 12-times stretched PS inverse opal films. Scale bars are 1 ��m. Figure S3. (a) MTT assays and (b) adhesion properties of PC12 cells cultured on ordinary glass slides, PS substrates stretched at 0��, 15��, 30��, 45�� for 1 day, 2 days, and 3 days, respectively. Error bars represent SD. Figure S4. (a) Immunofluorescence image, (b) SEM image, (c) angle distribution of neurites of PC12 cells cultured on ordinary glass slides. Scale bars are 50 ��m. Figure S5. Orientation angle frequency distribution of PC12 cells cultured on PS inverse opal films stretched at different angles. �� or ����� means the angle between the direction of neurite (the red dotted line) and the stretching orientation (the black solid line), respectively. Figure S6. Raman spectrum of PEDOT:PSS-doped PAAm hydrogels. Figure S7. (a) MTT assays and (b) adhesion properties of PC12 cells cultured on ordinary glass slides, PS inverse opal films, composite films for 1 day, 2 days, and 3 days, respectively. Error bars represent SD. Figure S8. (a) Differentiation rates of PC12 cells cultured on ordinary glass slides, PS inverse opal films and composite films on the 7th day. (b) Orientation angle frequency distribution of PC12 cells on PS inverse opal films and composite films.

Additional file 1: Figure S1. (a) pH-driven deprotonation equilibria of PAA polymers. (b) The change of the volume and structure color of the IOF under pH-stimulus. (c) The red shift of the reflection peak during the pH increasing process. Figure S2. Optical images of the pH-responsive structural color change of the IOFs fabricated by templates with different nanoparticle sizes. Figure S3. The photographs of pH indicator paper and IOF put onto (a) normal skin and (b) infected wounds of SD rats. (c) the reference for pH values in the range of 1–14. The scale bars are 5 mm. Figure S4. Photographs of E. coli and S. aureus colonies treated with PBS, and IOF loaded with 4% CS. Scale bars are 2 cm. Figure S5. (a) The standard curve of FITC-BSA in the PBS buffer solution, R2 > 0.999. (b) Cumulative release curve of FITC-BSA in IOF loaded with 4% CS. Figure S6. Live staining of NIH-3T3 cells on (a) glass dish, (b) IOF and (c) IOF loaded with 4% CS and VEGF. (d) The statistical graph of cell viability. Scale bars are 100 μm. Figure S7. Hemolysis tests of IOF and IOF + CS + VEGF. Figure S8. (a) Representative photographs of the wound closure process treated with commercial dressing (CD), and IOF + CS + VEGF. (b) The statistical graph of the wound closure situation (n = 4). Figure S9. In vivo antibacterial test of (a) control group and IOF + CS + VEGF group. Scale bars are 2 cm. Figure S10. (a) Immunostaining of PCNA of granulation tissues in different groups. (c) Immunostaining of E-cadherin of granulation tissues in different groups. Scare bars are 50 μm. Figure S11. Double immunofluorescence staining of neovascularization, CD31(+) structures (red) were surrounded by α‐smooth muscle actin positive cells (green) in different groups: (a) Control, (b) IOF, (c) IOF + CS + VEGF. Scale bars are 50 μm. (d) Statistical analysis of vessel density in different groups after 9 days of wound repair. NS not significant, 0.01 < *p < 0.05, **p < 0.01 (n = 4). Figure S12. Photographs of the skin wounds treated with (a) PBS solution (control), (b) IOF, (c) the IOF loaded with both CS and VEGF. Scale bar is 5 mm.

Polymer microparticles with various compositions and morphologies have recently received much attention. Their surface-roughness significantly affects the physical and chemical properties, which especially counts in regulating the interaction between biological materials and living systems. In this paper, we design a polystyrene microsphere with controllable surface textures. At first, a microfluidic device is used to generate droplets with uniform size containing the hydrophobic polymer and a co-surfactant. During the volatilization of the organic solvent, the shrinking droplets appear to be unstable at the interface. Thus, the surface area increases spontaneously, and microspheres with wrinkles on the surface are obtained after being solidified. The results show that tuning the concentration of the co-surfactant and the rate of solvent evaporation can effectively regulate the surface roughness of the microspheres. Circulating tumor cell capture experiments reveal that this textured structure can facilitate the cell adhesion and increase the number of the captured cells. These features indicate that the coarse microspheres possess a promising application prospect in the field of biomedical analysis.