key: cord-0070375-m35uia7u
authors: Li, Pengfei; Ruan, Liming; Wang, Ruofan; Liu, Tianqi; Song, Gao; Gao, Xiaofei; Jiang, Guohua; Liu, Xiaoyan
title: Electrospun Scaffold of Collagen and Polycaprolactone Containing ZnO Quantum Dots for Skin Wound Regeneration
date: 2021-11-22
journal: J Bionic Eng
DOI: 10.1007/s42235-021-00115-7
sha: 5a1a97cc70a45a03f32aaf28b2c57b74205a4464
doc_id: 70375
cord_uid: m35uia7u

Nanofibers (NFs) have been widely used in tissue engineering such as wound healing. In this work, the antibacterial ZnO quantum dots (ZnO QDs) have been incorporated into the biocompatible poly (ε-caprolactone)/collagen (PCL/Col) fibrous scaffolds for wound healing. The as-fabricated PCL-Col/ZnO fibrous scaffolds exhibited good swelling, antibacterial activity, and biodegradation behaviors, which were beneficial for the applications as a wound dressing. Moreover, the PCL-Col/ZnO fibrous scaffolds showed excellent cytocompatibility for promoting cell proliferation. The resultant PCL-Col/ZnO fibrous scaffolds containing vascular endothelial growth factor (VEGF) also exhibited promoted wound-healing effect through promoting expression of transforming growth factor-β (TGF-β) and the vascular factor (CD31) in tissues in the early stages of wound healing. This new electrospun fibrous scaffolds with wound-healing promotion and antibacterial property should be convenient for treating wound healing. SUPPLEMENTARY INFORMATION: The online version contains supplementary material available at 10.1007/s42235-021-00115-7.

Skin is the largest organ in the human body and provides us from external aggressions and pathogens [1, 2] . However, skin injuries, including burns, diabetic ulcers, and other accidents, are considerable challenges in dermatology and skin care. Due to their vital functions as a physical, chemical, and bacterial barrier, the selection of skin woundhealing agents or dressings plays an important role in tissue restoration, prevention of dermal or systemic infections, and ultimately in the aesthetic outcome of wound healing [3] . During the past few decades, the development of electrospun fibrous scaffolds as wound dressings or matrices has been introduced as alternatives to traditional wound care products because of the simple electrospinning process, which does not require expensive or complex fabrication instruments, and the scaffolds porous structure similar to the human native extracellular matrix (ECM) [4, 5] . In addition, the electrospun nanofiber scaffolds have high porosity and high specific surface area, which are conducive to absorbing wound exudate and preventing the invasion of bacteria from the external environment [6] . The highly porous threedimensional (3D) structure of electrospun fibrous scaffolds can facilitate the exchange of cellular nutrients and create an ideal cellular micro-environment for wound healing [7] [8] [9] . Therefore, electrospun fibrous scaffolds have remarkable potential in both ECM-biomimetic structures and the ability to adsorb bioactive factors, and have thus emerged as essential applications in the field of skin wound repair [5, 10] .

Skin wound healing is a complex process and involves several successive but overlapping phases, including hemostasis, inflammation, proliferation, and maturation (remodeling) [11] [12] [13] [14] . Usually, electrospun fibrous scaffolds have been developed to cover wounds with the purpose to negate the occurrence of infections and avoid dehydration. However, this kind of passive dressings also can induce new lesions during replacement and are not effective against bacteria contaminations [15] . Therefore, it is urgent to develop the smart wound dressings, which should be able to support the human body to heal a wound as fast as possible with less scarring, patient pain, and discomfort [16] .

In recent years, the use of biodegradable and biocompatible natural polymers, in combination with the electrospinning technique, has been widely investigated to obtain more and more efficient smart wound dressings [17] [18] [19] . For example, Col is a natural biological material and the major component of ECM. Collagen has been widely used in skin tissue engineering due to its excellent biocompatibility and weak antigenicity [20] [21] [22] . Although collagen can mimic native tissues best, and often lack sufficient mechanical strength to support a large number of cells, and collagen in particular is quickly consumed by enzymes in the body [23] , thus hampering their efficient usage in large-scale wound treatments. This limitation might be overcome by combining collagen with other artificial polymers to form hybrid structures. PCL is a synthetic semi-crystalline linear polyester with good biocompatibility, biodegradable, and mechanical strength. And it is widely used in tissue engineering that approved by the U.S. Food and Drug Administration (FDA) as a biomedical material [24] . Although PCL exhibits significant mechanical strength and biocompatibility, it is inherently hydrophobic which negatively affects its biological properties such as cell adhesion and proliferation. Therefore, a combination of PCL with a natural hydrophilic polymer such as collagen is utilized as an ideal tissue engineering scaffold for wound healing [25] . Therefore, a combination of PCL with collagen can be utilized as an ideal scaffold for skin tissue regeneration.

In addition, any open skin wound is under the risk of microbial infection and provide potential invasion site for microbial growth and colonization, which result in trauma and delayed wound healing [26] . Therefore, immediate care of skin wounds with active wound dressings impregnated with antimicrobials is vital for prevention of microbial infection for acceleration of wound regeneration. Electrospun fibrous membranes are excellent soft scaffolds, delivering advanced therapeutic agents directly to the wound [27, 28] . Recently, the studies on incorporation of micro-and nanoparticles as additives into the wound dressing materials for the care of wounds are increasing. Especially, ZnO has widely used in biomedical engineering due to its good anti-inflammatory and antibacterial properties [29, 30] . As previous reports [31] [32] [33] , ZnO QDs as a cheap nanomaterial with low toxicity have shown great potential for application in wound healing. Because the ZnO QDs are decomposed completely at pH 5 in aqueous solution, and the release of Zn 2+ helps to promote wound repair by participating in the hair follicle regeneration, blood vessel formation, and wound-healing properties [34] [35] [36] [37] .

In the present work, the electrospun fibrous scaffolds have been fabricated by combination of PCL and Col. ZnO QDs and VEGF are further incorporated into the PCL/Col fibrous scaffolds for acceleration wound healing (Fig. 1) . The objectives of the present work are: (1) to design and fabricate ZnO QDs-loaded PCL/Col electrospun fibrous scaffolds as wound dressings; (2) to evaluate structure, morphology, mechanical, swelling, and degradation, and antibacterial properties of as-prepared ZnO QDs-loaded PCL/Col electrospun fibrous scaffolds; (3) to determine the biological mechanism of wound healing. 

ZnO QDs were prepared by a sol-gel method and subsequently functionalized by (3-aminopropyl) triethoxysilane (APTEs) to form amino-functionalized ZnO QDs (NH 2 -ZnO QDs, see Supplementary Material) [29, 30] . Then, different amounts of NH 2 -ZnO QDs (0, 0.25, 0.5 and 0.75% w/v) were added to a PCL/Col (PCL: Col = 2:1, 1:1, 1:2 and 1:3) solution in HFIP solution and then stirred slowly in a 20 mL vial about 24 h at room temperature. The high electrical voltage (10-12 kV) was applied across a fixed distance of 12 cm between the needle tip and the collector. The feeding rate of the solutions was set at 1 mL·h −1 . The electrospinning process was carried out under controlled conditions (25 ± 5 °C and 40 ± 10% RH). All electrospun fibrous scaffolds were vacuum dried for 48 h to completely remove the solvent. Then, the fiber was soaked in 10 μg·ml −1 VEGF solution for 1 h, and then dried for later use.

The scanning electron microscope (SEM) is used to observe the fibrous scaffolds microstructure. Water contact angle, mechanical property, Fourier transform infrared spectroscopy (FTIR spectra), swelling, porosity, and biodegradability tests were used to investigate the chemical and physical characterizations of composite films. The fiber diameter distribution of the different scaffolds was determined from the SEM micrographs using Image Analysis software (Image J, National Institutes of Health, Bethesda, USA). The details are available in Supplementary Material.

To evaluate the cytotoxicity of the as-fabricated electrospun fibrous scaffolds, mouse fibroblast L929 cells and mouse embryonic fibroblast 3T3 cells were selected as model cells [38, 39] . To evaluate the adhesion ability of the as-fabricated electrospun fibrous scaffolds, the cell morphology was tested by scanning and laser confocal (C2, Nikon, Japan). The detailed experimental process is provided in the Supplementary Material.

The electrospun fibrous scaffolds were cut into circles with a diameter of 10 mm plated on agar medium and treated with UV sterilization for 24 h. S. aureus and E. coli (1 × 10 8 CFU·mL −1 ) were used to test the antibacterial ability of fibrous scaffolds [40, 41] . The zone of inhibition method was adopted to evaluate the bactericidal effect [42] . And the flat colony counting method was used to further evaluate the antibacterial strength after co-culture of fibrous scaffolds and S. aureus and E. coli at 37 °C for 24 h. Then, 100 μL of the mixed cultured bacteria solution was evenly spread on the agar medium and cultured at 37 °C for 24 h. After 24 h, the number of colonies was marked to assess the antibacterial properties of the fibrous scaffolds.

The mouse full-thickness skin injury closure experiments were performed to assess the wound-healing properties of the as-fabricated electrospun fibrous scaffolds. First, male SD rats weighing about 200 g were anesthetized and shaved their back hair. Then, a full-thickness skin wound with a diameter of 10 mm was excised on the back of SD rats. Four different wound dressings (Group 1: gauze (control), Group 2: PCL-Col, Group 3: PCL-Col/Zn-0.75, and Group 4: PCL-Col/Zn-0.75 + VEGF) after UV sterilization were immediately applied to the wound surface. The wound area was recorded at different intervals time. Use Image J software to analysis calculate the wound rate, and then calculate wound-healing rate. The wound-healing ratio was calculated as (A i − A u )/A i × 100%, where A i is the initial area of the wound surface, and A u is the area of the wound surface that did not recover.

The healed wound tissues were harvested and stained with hematoxylin and eosin (H&E) and Masson's trichrome (Masson) for histology examination [43] . Then, immunohistochemistry analysis was performed to assess fibroblast differentiation and new blood vessels restore. The immunostaining for transforming growth factor-β (TGF-β) and vascular factor (CD31) in wound tissue sections after different fibrous scaffolds treatments were performed at day 6 and 12 [44] . The details can be found in the Supporting Information.

The statistical analysis was performed using the statistical software Origin Pro 2016 (OriginLab, Berkeley, CA, USA) and GraphPad Prism 8 (GraphaPad Software, San Diego, California, USA). The results above each data are compared and analyzed with the control group. All values were expressed as the mean ± standard deviation (SD). Statistical comparisons were analyzed by a one-way ANOVA followed by Tukey test. A p value less than 0.05 was considered statistical significance.

The pure ZnO QDs are synthesized by sol-gel method. Then, to improve the stability of ZnO QDs in aqueous solution, ZnO QDs are functionalized by APTEs to form NH 2 -ZnO QDs. Figure 2a (Fig. 2c) [45, 46] . Under UV light (λ = 365 nm), the obvious yellow fluorescence can be observed for the ZnO and NH 2 -ZnO QDs aqueous solution (Fig. 2d) .

FTIR spectra of ZnO and NH 2 -ZnO QDs are recorded on a Fourier transformation infrared spectrometer (Bruker, Germany) and the results are shown in Fig. 2e . In the case of ZnO QDs, peaks at 458, 832, 1393, and 1509 cm −1 can be attributed to Zn-O stretching [47] . After functionalized [30, 48] . The absorption peak at 1002 cm −1 can be assigned to the stretching vibration of Si-O band from APTEs. Therefore, the APTEs have been successfully modified on the surface of ZnO QDs [49] . Zeta potential measurements are conducted to confirm the surface electrokinetic potential of the synthesized ZnO QDs and NH 2 -ZnO QDs in aqueous solutions. The zeta potential of ZnO QDs is found to be − 3.85 mV. After functionalization, the positive zeta potential (~ 27.5 mV) is obtained for NH 2 -ZnO QDs (Fig. 2f) . The fluorescence excitation spectrum of the ZnO QDs, with an emission maximum at 365 nm, exhibited a broad peak with a maximum at approximately 525 nm. In fluorescence excitation spectrum of the NH 2 -ZnO QDs, suffers an enhancement along with the red shift (Fig. 2g) .

Electrospun fibrous scaffolds are fabricated using mixed solutions of PCL (10 w/v%) and Col (10 w/v%) in HFIP as raw materials under low relative humidity (RH) (35%) and low temperature (25 °C) conditions [50] (Fig. 3a) . Representative morphological images of fabricated electrospun fibrous scaffolds are shown in Fig. 3b . All scaffolds show randomly oriented uniform nanofibers with interconnected pores. Figure 3c -f presents SEM images of electrospun PCL-Col fibrous scaffolds with different volume ratio (PCL/ Col = 2:1, 1:1, 1:2, and 1:3, respectively) of PCL and Col together with the corresponding size distribution graphs (Fig. 3g-j) . The fiber diameters of electrospun PCL-Col fibrous scaffolds are 360 ± 80, 530 ± 110, 360 ± 80, and 630 ± 230 nm with volume ratio of PCL and Col at 2:1, 1:1, 1:2, and 1:3, respectively.

The surface hydrophilicity of nanofibrous scaffolds has a great influence on cell attachment and growth [19, 51] . The hydrophobicity of the composite films is evaluated by the values of water contact angles. As shown in Fig. 4a , b, all electrospun PCL-Col fibrous scaffolds exhibit a good hydrophilicity with water contact angles ranged from 50 to 80°. And the water contact angles can be decreased to 20 ~ 55 o after the water drops placed on composite film for 90 s. It implies the electrospun PCL-Col fibrous scaffolds can absorb exudates during the wound-healing process [52, 53] . Among them, the electrospun PCL-Col fibrous scaffold prepared by PCL/COL = 1:1 shows the best hydrophilicity, which facilitates cell adhesion as well as cell-matrix interactions. Tensile properties of PCL-Col fibrous scaffolds are measured by universal testing machine (KSM-bx5450ST, Osaka Kato-tech, Japan). The stress-strain curves of PCL-Col fibrous scaffolds are shown in Fig. 4c . Under a dry state, electrospun PCL-Col fibrous scaffolds with mass ratio of PCL and Col at 1:1 and 1:2 show higher force at break and elasticity, while the other scaffolds were characterized by significantly lower ones. The elongation at break electrospun PCL-Col fibrous scaffolds with mass ratio of PCL and Col at 1:1 and 1:2 are ~ 94.31% and 68.84%, respectively. While, only ~ 1.82% and 1.48% of elongation at break can be obtained for the scaffolds with mass ratio of PCL and Col at 2:1 and 3:1 (Fig. 4d) . The tensile strength of scaffolds also exhibits the similar trend with ~ 2.05 and 2.01 MPa for the first two samples and ~ 1.13 and 0.43 MPa for the latter two noes (Fig. 4e) . Therefore, the presence of PCL in the scaffolds seems to weaken the scaffold structure. Based on above results, the electrospun PCL-Col fibrous scaffold with PCL and Col at 1:1 has high tensile strength and good water-absorption properties which would be beneficial for wound dressing.

To enhance the antibacterial properties, 0.25, 0.50, or 0.75% of NH 2 -ZnO QDs relative to mass of PCL-Col are incorporated into electrospun PCL-Col fibrous scaffolds, denoted as PCL-Col/ZnO-0.25, PCL-Col/ZnO-0.5, and PCL-Col/ZnO-0.75, respectively. Compared with electrospun PCL-Col fibrous scaffold with smooth surface, the (Fig. 5a-d) . However, the diameter of the electrospun PCL-Col/ZnO composite nanofibers is lower than that of PCL-Col nanofibers (Fig. 5e-h) . The presence of ZnO QDs in the fibrous scaffold was evaluated by the energy-dispersive spectrometer (EDS) elemental analysis. The results show that O, C, and Zn elements in mapping images are uniformly distributed on the fibrous scaffold (Fig. 5i) . FTIR spectra of PCL, Col, NH 2 -ZnO QDs, and PCL-Col/ZnO-0.75 also proved that NH 2 -ZnO QDs are successfully incorporated into electrospun PCL-Col fibrous scaffolds (Fig. S2 ).

The porosity of the wound dressing facilitates the absorption of wound tissue exudate and the maintenance of the extracellular environment at the wound [54] . As shown in Fig. 5j , the porosity of the as-prepared electrospun PCL-Col/ZnO fibrous scaffold is ~ 82%, which is higher than that of pure PCL (55.3%) and PCL-Col composite nanofibers (75.5%). It indicates that the incorporation of NH 2 -ZnO QDs facilitates the increasing the porosity of fibrous scaffolds. In addition, electrospun fibrous scaffolds should have good water absorption and moisture capability to prevent wound infection and accelerate the wound healing. The swelling rates of PCL-Col/ZnO fibrous scaffolds are significantly higher than that of pure PCL, and the swelling in the presence of ZnO QDs has a sharp increase in the first 25 min and shows higher water retention capacities in comparison with PCL-Col (Fig. 5k) . These results indicate the good moisture capability of the PCL-Col/ZnO fibrous scaffolds. At the same time, the biodegradability of the wound dressing is also crucial. When the pH at 7.4 and 5.5, the biodegradation rates of the electrospun PCL-Col/ZnO-0.75 fibrous scaffolds can be reached to 48.98 and 48.37% after 15 days, respectively, which indicates that the PCL-Col/ZnO fibrous scaffold has good biodegradability (Fig. S3 ).

To determine the antibacterial efficiencies of PCL-Col/ ZnO fibrous scaffolds against S. aureus and E. coli, inhibiting the growth of bacteria is analyzed by a plate counting method. Figure 6a , b shows the inhibiting the growth of S. aureus and E. coli with the concentration of PCL/Col, PCL-Col/ZnO-0.25, PCL-Col/ZnO-0.5, and PCL-Col/ZnO-0.75 at 10 μg mL −1 . After 24 h co-culture, the number of bacteria is decreased significantly for the PCL-Col/ZnO samples, and almost no S. aureus and E. coli can be found for PCL-Col/ ZnO-0.75, indicating that the antibacterial properties can be improved by incorporation of ZnO QDs into fibrous scaffolds. Figure 6c , d shows the quantitative statistical analysis results, showing the best antibacterial effect for PCL-Col/ ZnO-0.75. This result also is confirmed by the inhibition zone tests (Fig. S4) . The degree of antibacterial activity depends upon the amount of ZnO QDs in the fibrous scaffolds [55] .

Cytotoxicity assay is done to estimate the cell viability of L929 and 3T3 cells lines with different substrate scaffolds. Figure 6e , f shows that PCL-Col and PCL-Col/ ZnO fibrous scaffolds have no significant negative impact on cell viability after 24 h culture in comparison with PCL. Higher amount of PCL-Col/ZnO-0.75 only causes a slight decline on cell viability, as shown in Fig. 6g, h. To evaluate the in vitro cell proliferation on fibrous scaffold, L929 cell is chosen to be co-cultured with PCL-Col/ ZnO-0.75 fibrous scaffolds. Figure 6i , j shows the SEM images of L929 adhesion and proliferation on the surface of PCL-Col/ZnO-0.75 fibrous scaffold after culture for 24 and 48 h. These is significant increases in the number of L929 cell over time. In addition, the morphology of L929 cells shows a clear preference spreading along the direction of nanofibers. 24 h (a, b, c and d) . 

To evaluate the ability of ZnO QDs incorporated fibrous scaffolds on the wound healing, a full-thickness skin wound (10 mm in diameter) is established on the back of mice. The medical gauze-treated wounds, the wounds treated with PCL-Col, PCL-Col/ZnO-0.75, and PCL-Col/ ZnO-0.75 + VEGF fibrous scaffold are observed. On the day of implantation and each day after the implantation until the wound completely healed, photographs are taken and shown in Fig. 7a . The wound-healing rates are significantly different among all groups at each time point. On the 6th day, wound-healing rates are ~ 29, 53, 63, and 78% for gauze, PCL-Col, PCL-Col/ZnO-0.75, and PCL-Col/ZnO-0.75 + VEGF groups, respectively. On the 12th day, it can also be observed, from the image, that the wound tissue restored almost completely in PCL-Col/ZnO-0.75 + VEGF group and a very small portion of the wound remained unhealed in other groups. Wound contraction was also quantified in terms of percentage and the results are expressed in Fig. 7b . The PCL-Col/ZnO-0.75 + VEGF fibrous scaffold can significantly promote wound healing. On the day 4th, the percentage of wound area treated with PCL-Col/ZnO-0.75 + VEGF is 66%, and it can be decreased to ~ 22 and 3% after 6 and 12 day treatments. The wound closure rate also can be increased to ~ 95.4% in comparison with ~ 92 and 88% for PCL-Col/ZnO-0.75 and PCL-Col groups, and significantly higher than that of the gauze group at 77% (Fig. 7c ).

Histological studies are used to evaluate the efficiency of the treatments on the wound-healing process; based on the histological observations stained with H&E shown in Fig. 8a . At day 6, many inflammatory cells (black arrow) and few neovascularization (red arrow) can be observed on the control group. However, fewer inflammatory cells can be founded in the PCL-Col/ZnO-0.75 and PCL-Col/ZnO-0.75 + VEGF group due to the effective antibacterial ability of ZnO QDs in vivo. The quantitative analysis of the inflammatory cell number is presented in Fig. 8b . On the 6th day, the number of inflammatory cells can be decreased from 195 for gauze group to 118, 102 and 75 for PCL-Col, PCL-Col/ZnO-0.75, and PCL-Col/ZnO-0.75 + VEGF groups on 1 mm 2 wound area (Fig. 8c) . After 12 day treatment, the number of inflammatory cell can be further decreased to 23. While, the number of new blood vessels and granulation tissue exhibits an opposite trend (Fig. 8d, e) . The most of new blood vessels and granulation tissue can be formed in the PCL-Col/ZnO-0.75 + VEGF groups, which can establish a sufficient blood supply that provides a favorable microenvironment for epidermal and dermal cell migration and proliferation [56, 57] .

To further investigate the mechanism of skin wound healing, the wound collagen deposition, inflammation condition, and angiogenesis are evaluated by Masson trichrome staining, TGF-β1, and CD31 immunohistochemical staining. Figure 9a shows the results of Masson's trichrome staining to assess the collagen deposition in the wound site. A large number of collagen fibers and myofibrils are appeared in the PCL-Col/ZnO-0.75 + VEGF group. The quantitative analysis results are provided in Fig. 9b . The collagen area ratio in the PCL-Col/ZnO-0.75 + VEGF group can be increased to 29.1 after 6 days of treatment compared with PCL-Col/ ZnO-0.75 at 25.8% and PCL-Col at 24.9%. This indicates that the ZnO and VEGF can accelerate the production of collagen fibers to promote wound closure. On 12th day, the collagen index can be further increased to 39.8% for PCL-Col/ZnO-0.75 + VEGF group, showing the highest collagen content in all groups (Fig. 9b) .

In addition, the immunohistochemistry assessment of transforming growth factor and vascular factor is performed. TGF-β1 can promote the contraction of fibroblasts on the collagen matrix, thereby accelerating collagen deposition, wound healing, and re-epithelialization [58] [59] [60] . On the 6th day, the TGF-β expression levels in the gauze, PCL-Col, PCL-Col/ZnO-0.75, and PCL-Col/ZnO-0.75 + VEGF are 0.12 ± 0.01, 0.14 ± 0.02, 0.15 ± 0.01, and 0.17 ± 0.02, respectively. On the 12th day, the expression levels of the same three groups are 0.10 ± 0.01, 0.11 ± 0.02, 0.12 ± 0.02, and 0.13 ± 0.01 (Fig. 9c, d) . There is reduced TGF-β expression after 12 day treatment in comparison with that in 6 day treatment. It indicates that PCL-Col/ZnO-0.75 + VEGF can promote the secretion of TGF-β in the initial stage of wound healing, and decrease its expression in the final stage. CD31 is a marker of vascular endothelial cells which is one of the criteria for evaluation of wound tissue recovery [61] [62] [63] . After treatment for 6 days, the CD31 expression levels in the gauze, PCL-Col, PCL-Col/ZnO-0.75, and PCL-Col/ZnO-0.75 + VEGF are 0.02 ± 0.00, 0.23 ± 0.01, 0.24 ± 0.01, and 0.25 ± 0.02, respectively. On the 12th day, the expression levels of the same three groups are 0.13 ± 0.01, 0.14 ± 0.01, 0.15 ± 0.01, and 0.16 ± 0.02 (Fig. 9e, f) . These results show that the PCL-Col/ZnO-0.75 + VEGF stimulates expression of CD31 in the initial stage of wound healing, and decreases its expression in the final stage of wound healing as well. It also implies PCL-Col/ZnO-0.75 + VEGF can promote angiogenesis in the early stages of wound healing and should decrease it in the later stages. 

In this work, we have successfully integrated antibacterial ZnO QDs into the biocompatible PCL/Col fibrous scaffolds by elecspining method to achieve synergistic wound-healing effect. The designed and prepared electrospun PCL-Col/ZnO fibrous scaffolds exhibited well mechanical performance. Also, these fibrous scaffolds performed good swelling and biodegradation behaviors, which were all beneficial for the applications as wound healing. Moreover, the as-fabricated PCL-Col/ZnO fibrous scaffolds showed excellent cytocompatibility and promoting cell proliferation. Besides, the existence of ZnO QDs endowed the fibrous scaffolds with high-efficient antibacterial properties in vitro against S. aureus and E. coli. The resultant electrospun PCL-Col/ ZnO-0.75 + VEGF fibrous scaffolds also exhibited promoted wound-healing effect through promoting expression of TGF-β and CD31 in tissues in the early stages of wound healing. This new electrospun fibrous scaffolds with wound-healing promotion and antibacterial property should be convenient for treating wound healing.

The online version contains supplementary material available at https:// doi. org/ 10. 1007/ s42235-021-00115-7. 

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Acknowledgements This work was supported by the Natural Science Foundation of Zhejiang Province (LBY20H110001, LY18E030006) and National Natural Science Foundation of China (51873194).

The authors declare that they have no conflicts of interest to this work.