负载银和重组人碱性成纤维细胞生长因子的甲基丙烯酸酐化明胶水凝胶对兔深Ⅱ度烧伤创面的影响

陈向军; 吴兴; 林欢欢; 刘肇兴; 刘沙

doi:10.3760/cma.j.cn501120-20210726-00260

负载银和重组人碱性成纤维细胞生长因子的甲基丙烯酸酐化明胶水凝胶对兔深Ⅱ度烧伤创面的影响

doi: 10.3760/cma.j.cn501120-20210726-00260

解放军联勤保障部队第969医院烧伤整形科，呼和浩特　　010051

基金项目:

内蒙古自治区自然科学基金 2018MS08002

详细信息

通讯作者:
陈向军，Email：1301579255@qq.com

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出版历程
- 收稿日期: 2021-07-26
- 网络出版日期: 2022-08-12
- 刊出日期: 2022-08-17

Effects of methacrylic anhydride gelatin hydrogel loaded with silver and recombinant human basic fibroblast growth factor on deep partial-thickness burn wounds in rabbits

Department of Burn Orthopaedics, the 969th Hospital of PLA Joint Logistic Support Force, Hohhot 010051, China

Funds:

Natural Science Foundation of Inner Mongolia Autonomous Region of China 2018MS08002

More Information

Corresponding author: Chen Xiangjun, Email: 1301579255@qq.com

摘要

摘要:
目的探讨负载银和重组人碱性成纤维细胞生长因子（rh-bFGF）的甲基丙烯酸酐化明胶（GelMA）水凝胶对兔深Ⅱ度烧伤创面的影响。
方法采用实验研究方法。制备含不同浓度甲基丙烯酸酐（MA）的低浓度MA明胶（GelMA）材料、中浓度GelMA材料和高浓度GelMA材料，加入光引发剂后分别制得低浓度GelMA水凝胶、中浓度GelMA水凝胶和高浓度GelMA水凝胶。采用核磁共振波谱仪检测前述3种浓度GelMA材料的氢核磁共振谱并根据波谱图计算其取代度，采用场发射扫描电子显微镜（FESEM）检测前述3种浓度GelMA水凝胶的三维微观结构及孔径，样本数均为9。根据前述筛选出的MA浓度合成含10种浓度银的GelMA（含银GelMA）溶液，将每种浓度的含银GelMA溶液均分为3份，加入光引发剂后分别暴露于紫外光下持续20、25、35 s，制得相应的含银GelMA水凝胶。采用胶原酶降解法测定不同光交联时间含银GelMA水凝胶降解12、24、36、48 h的降解剩余率及彻底降解所需时长，样本数为5。测定前述筛选出光交联时间下含10种浓度银GelMA水凝胶对金黄色葡萄球菌的抑菌圈直径反映其抑菌能力，样本数均为5。以与含最低浓度银（即不含银）GelMA水凝胶抑菌圈直径相比有统计学意义的含银GelMA水凝胶为有抑菌活性。选取具有抑菌活性的且载药浓度最低的含银GelMA水凝胶，采用FESEM检测其三维微观结构及孔径，采用能谱仪检测其内部银元素的存在情况，样本数均为9。将冻干单纯GelMA水凝胶和冻干含银GelMA水凝胶分别浸没于磷酸盐缓冲液中24 h，通过称重法计算并比较2种水凝胶的溶胀率，样本数为5。根据预实验及前述实验结果，制备含银和rh-bFGF的GelMA水凝胶（简称复合水凝胶）。大体观察复合水凝胶的外观，并采用FESEM检测其三维微观结构与孔径。取30只4~6个月龄、雌雄各半日本大耳兔，在其背部制作深Ⅱ度烧伤创面。以兔头侧为基准，将脊柱左侧创面作为复合水凝胶治疗组，右侧作为纱布对照组，2组创面分别作相应处理。观察伤后3、7、14、21、28 d创面愈合情况；记录伤后7、14、21、28 d创面愈合面积并计算其愈合率，样本数为30。对数据行重复测量方差分析、单因素方差分析、独立样本t检验。
结果低浓度GelMA材料、中浓度GelMA材料及高浓度GelMA材料的取代度，差异明显（F=1 628.00，P<0.01）。低浓度GelMA水凝胶存在疏松、不规则三维空间网状结构，孔径为（60±17）μm；中浓度GelMA水凝胶的三维空间网络、孔径大小均较均匀规则，孔径为（45±13）μm；高浓度GelMA水凝胶的三维空间网状结构致密、层次混乱，孔径为（25±15）μm。3种GelMA水凝胶孔径大小差异有统计学意义（F=12.20，P<0.01），选取（MA）中浓度为后续材料制作浓度。相同光交联时间下的含不同浓度银GelMA水凝胶的降解性基本一致；20、25、35 s光交联时间下含银GelMA水凝胶降解12 h的降解剩余率分别为（74.2±1.7）%、（85.3±0.9）%、（93.2±1.2）%，降解24 h的降解剩余率分别为（58.3±2.1）%、（65.2±1.8）%、（81.4±2.6）%，降解36 h的降解剩余率分别为（22.4±1.9）%、（45.2±1.7）%、（68.1±1.4）%，降解48 h的降解剩余率分别为（8.2±1.7）%、（32.4±1.3）%、（54.3±2.2）%；20、25、30 s光交联时间下含银GelMA水凝胶彻底降解所需时间分别为（50.2±2.4）、（62.4±1.4）、（72.2±3.2）h，差异有统计学意义（F=182.40，P<0.01），选取25 s作为后续光交联时间。低浓度至高浓度的10种含银GelMA水凝胶对金黄色葡萄球菌的抑菌圈直径依次为（2.6±0.4）、（2.5±0.4）、（3.2±0.4）、（12.1±0.7）、（14.8±0.7）、（15.1±0.5）、（16.2±0.6）、（16.7±0.5）、（16.7±0.4）、（16.7±0.6）mm，基本呈浓度依赖性升高趋势，总体比较差异有统计学意义（F=428.70，P<0.01），与含最低浓度银GelMA水凝胶相比，其他有抑菌活性的含低浓度至高浓度银GelMA水凝胶的抑菌圈直径均明显增大（t值分别为26.35、33.84、43.65、42.17、49.24、55.74、43.72，P<0.01）。对金黄色葡萄球菌抑菌圈直径为（12.1±0.7）mm的含银GelMA水凝胶具有抑菌活性且载药浓度最低，选取该含银浓度为后续材料制作浓度。含银GelMA水凝胶的微观形貌为规律的趋于平行线性的条索状结构，孔径为（45±13）μm，且含有银元素。浸没24 h，含银GelMA水凝胶的溶胀率与单纯GelMA水凝胶相近（P>0.05）。复合水凝胶呈无色清亮透明状；其三维结构为规则、均匀的网格状，内部存在细丝网状结构，孔径为（40±21）μm。伤后3 d，复合水凝胶组兔创面可见大量坏死组织及渗出物；纱布对照组兔创面可见散在结痂，亦可见少量坏死组织及渗出物。伤后7 d，复合水凝胶组兔创面已明显缩小，纱布对照组兔出现创面存在与纱布粘连情况。伤后14 d，复合水凝胶组兔创面红润、可见肉芽组织生长；纱布对照组兔创面基底呈苍白色、血运差。伤后21 d，复合水凝胶组兔创面完全愈合，纱布对照组兔创面出现愈合趋势。伤后28 d，复合水凝胶组兔创面部位可见新生毛发，纱布对照组兔仍残存椭圆形创面。伤后7、14、21、28 d，复合水凝胶组兔创面愈合率均明显大于纱布对照组（t值分别为2.24、4.43、7.67、7.69，P<0.05或P<0.01）。
结论中浓度GelMA水凝胶在溶胀性、可降解性方面具有良好的理化特性，筛选出的含银GelMA水凝胶具有抑菌活性且载药浓度最低，制得的复合水凝胶可明显缩短兔深Ⅱ度烧伤创面愈合时间。
- 敷料，水胶体 /
- 成纤维细胞生长因子 /
- 伤口愈合 /
- 皮肤 /
- 甲基丙烯酸酐化明胶 /
- 纳米银
Abstract:
Objective To investigate the effects of methacrylic anhydride gelatin (GelMA) hydrogel loaded with silver and recombinant human basic fibroblast growth factor (rh-bFGF) on deep partial-thickness burn wounds in rabbits.
Methods The experimental research method was adopted. Low-concentration GelMA materials, medium-concentration GelMA materials and high-concentration GelMA materials containing different concentrations of methacrylic anhydride (MA) were prepared, after adding photoinitiator, low-concentration GelMA hydrogels, medium-concentration GelMA hydrogels, and high-concentration GelMA hydrogels were obtained, respectively. The nuclear magnetic resonance spectroscopy was performed to detect the hydrogen nuclear magnetic resonance spectra of the above-mentioned three concentrations of GelMA materials, and to calculate the degree of substitution according to the spectrum diagram. The three-dimensional microstructure and pore size of 3 types of above-mentioned GelMA hydrogels were detected by field emission scanning electron microscopy (FESEM), with 9 samples measured. According to the selected concentration of MA, ten kinds of solutions of GelMA with different concentration of silver (silver-containing GelMA) were synthesized, and the silver-containing GelMA solution of each concentration was divided into three parts, and then exposed to ultraviolet light lasting for 20, 25, and 35 s, respectively. After adding photoinitiator,the corresponding silver-containing GelMA hydrogels were obtained. The residual degradation rate of silver-containing GelMA hydrogel with different photocrosslinking times was detected by collagenase degradation method at degradation of 12, 24, 36, and 48 h; and the time required for complete degradation was detected, and the sample number was 5. The inhibition zone diameter of GelMA hydrogel under above screened photocrosslinking times containing 10 concentrations of silver against Staphylococcus aureus was measured to reflect its antibacterial ability, and the sample numbers were all 5. The silver-containing GelMA hydrogel with statistical significance compared with the antibacterial circle diameter of the silver-containing GelMA hydrogel containing the lowest concentration (no silver) was considered as having antibacterial activity. The three-dimensional microstructure and pore size of the silver-containing GelMA hydrogels with antibacterial activity and the lowest drug concentration selected were detected by FESEM, and the sample numbers were all 9. The freeze-dried alone GelMA hydrogel and the freeze-dried silver-containing GelMA hydrogel were soaked in phosphate buffer solution for 24 h, respectively, then the swelling rate of the two GelMA hydrogel were calculated and compared by weighing method, and the sample number was 5. GelMA hydrogel containing silver and rh-bFGF, namely compound hydrogel for short, was prepared according to the preliminary experiment and the above experimental results. The appearance of the composite hydrogel was observed in general, and its three-dimensional microstructure and pore size were detected by FESEM. The deep partial-thickness burn wound was made on the back of 30 rabbits (aged 4-6 months, female half and half). Meanwhile, with the rabbit head as the benchmark, the wounds on the left side of the spine were treated as composite hydrogel treatment group, and the wounds on the right side were treated as gauze control group, and which were treated accordingly. On post injury day (PID) 3, 7, 14, 21, and 28, the healing of wounds in the two groups was observed. On PID 7, 14, 21, and 28, the wound healing area was recorded and the healing rate was calculated, with a sample number of 30. Data were statistically analyzed with analysis of variance for repeated measurement, one-way analysis of variance, and independent sample t test.
Results The substitution degree among low-concentration GelMA materials, medium-concentration GelMA materials, and high-concentration GelMA materials was significantly different (F=1 628.00, P<0.01). The low-concentration GelMA hydrogel had a loose and irregular three-dimensional spatial network structure with a pore size of (60±17) μm; the medium-concentration GelMA hydrogel had a relatively uniform three-dimensional spatial network and pore size with a pore size of (45±13) μm; the high-concentration GelMA hydrogel had the dense and disordered three-dimensional spatial network with a pore size of (25±15) μm, the pore sizes of 3 types of GelMA hydrogels were significantly differences (F=12.20, P<0.01), and medium concentration of MA was selected for the concentration of subsequent materials. The degradability of silver-containing GelMA hydrogels with different concentrations of the same photocrosslinking time was basically same. The degradation residual rates of silver-containing GelMA hydrogels with 20, 25, and 35 s crosslinking time at 12 h were (74.2±1.7)%, (85.3±0.9)%, and (93.2±1.2)%, respectively; the residual rates of degradation at 24 h were (58.3±2.1)%, (65.2±1.8)%, and (81.4±2.6)%, respectively; the residual rates of degradation at 36 h were (22.4±1.9)%, (45.2±1.7)%, and (68.1±1.4)%, respectively; the residual rates of degradation at 48 h were (8.2±1.7)%, (32.4±1.3)%, and (54.3±2.2)%, respectively, and 20, 25, and 30 s photocrosslinking time required for complete degradation of silver-containing GelMA hydrogels were (50.2±2.4), (62.4±1.4), and (72.2±3.2) h, and the difference was statistically significant (F=182.40, P<0.01), 25 s were selected as the subsequent photocrosslinking time. The antibacterial diameters of 10 types of silver-containing GelMA hydrogels against Staphylococcus aureus from low to high concentrations were (2.6±0.4), (2.5±0.4), (3.2±0.4), (12.1±0.7), (14.8±0.7), (15.1±0.5), (16.2±0.6), (16.7±0.5), (16.7±0.4), and (16.7±0.6) mm, respectively, and which basically showed a concentration-dependent increasing trend, and the overall difference was statistically significant (F=428.70, P<0.01). Compared with the silver-containing GelMA hydrogel with the lowest concentration, the antibacterial circle diameters of other silver-containing GelMA hydrogels with antibacterial ability from low to high concentration were significantly increased (with t values of 26.35, 33.84, 43.65, 42.17, 49.24, 55.74, and 43.72, respectively, P<0.01). The silver-containing GelMA hydrogel with the antibacterial diameter of (12.1±0.7) mm had the lowest antibacterial activity against Staphylococcus aureus and the lowest drug loading concentration, and the concentration of silver was selected for the concentration of subsequent materials. The microscopic morphology of the silver-containing GelMA hydrogel containing silver element with a pore size of (45±13) μm had a regular and linear strip-like structure. After soaking for 24 h, the swelling ratio of silver-containing GelMA hydrogel was similar to that of alone GelMA hydrogel. The composite hydrogel was colorless, clear and transparent, and its three-dimensional microstructure was a regular and uniform grid, with a filament network structure inside, and the pore size of (40±21) μm. On PID 3, a large amount of necrotic tissue and exudate of rabbit wound in composite hydrogel group were observed, and scattered scabs, a small amount of necrotic tissue and exudate of rabbit wound in gauze control group were observed. On PID 7, the area of rabbit wound in composite hydrogel group was significantly reduced, and adhesion of rabbit wound and gauze in gauze control group was observed. On PID 14, In composite hydrogel group, the rabbit wound surface was ruddy, and the growth of granulation tissue was observed, and in gauze control group, the rabbit wound base was pale, and the blood supply was poor. On PID 21, the rabbit wounds in composite hydrogel group healed completely, and rabbit wound in gauze control group had healing trend. On PID 28, new hair could be seen on rabbit wound surface in composite hydrogel group; oval wound of rabbit in gauze control group still remained. On PID 7, 14, 21, and 28, the wound healing areas of rabbit in composite hydrogel group were significantly larger than those in gauze control group (with t values of 2.24, 4.43, 7.67, and 7.69, respectively, P<0.05 or P<0.01).
Conclusions The medium-concentration GelMA hydrogel has good physical and chemical properties in terms of swelling and degradability. The screened silver-containing GelMA hydrogels had the lowest antibacterial activity and the lowest drug loading concentration. Composite hydrogel can significantly shorten the healing time of deep partial-thickness burn wounds in rabbits.
- Bandages, hydrocolloid /
- Fibroblast growth factors /
- Wound healing /
- Skin /
- Methacrylic anhydride gelatin /
- Nanosilver
陈向军：研究设计、实施与论文撰写；吴兴、林欢欢、刘肇兴、刘沙：实验实施与资料收集

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1 3种浓度甲基丙烯酸酐化明胶（GelMA）冻干材料的氢核磁共振波谱描记图。1A、1B、1C.分别为低浓度GelMA、中浓度GelMA和高浓度GelMA，均在5.63、5.68 ppm处存在连续的波峰Ⅰ，在4.14 ppm处存在波峰Ⅱ

注：红色箭头指示波峰

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2 3种浓度甲基丙酸烯酐化明胶（GelMA）水凝胶微观形貌场发射扫描电子显微镜×600，图中标尺为50 μm。2A.低浓度GelMA水凝胶支架存在疏松、不规则三维空间网状结构；2B.中浓度GelMA水凝胶三维空间网络、孔径大小均较均匀规则；2C.高浓度GelMA水凝胶支架三维空间网状结构致密、层次混乱

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3 3种不同光交联时间的含银甲基丙烯酸酐化明胶水凝胶降解12、24、36、48 h的降解剩余率比较

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4 含不同浓度银GelMA水凝胶对金黄色葡萄球菌的抑菌圈直径

注：GelMA为甲基丙烯酸酐化明胶；横坐标轴下方的1、2、3、4、5、6、7、8、9、10依次代表从低至高的10种含不同浓度银GelMA水凝胶；与最低浓度含银GelMA水凝胶相比，^aP<0.01

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5 含银甲基丙烯酸酐化明胶（GelMA）水凝胶微观形貌观察及银元素检测结果。5A.含银GelMA水凝胶为规律的趋于平行线性的条索状结构场发射扫描电子显微镜×200，图中标尺为50 μm；5B.能谱仪检测结果描记图显示，含银GelMA水凝胶含有银元素

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6 负载银和重组人碱性成纤维细胞生长因子的复合水凝胶敷料成品外观

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7 不同观察倍数下负载银和重组人碱性成纤维细胞生长因子的复合水凝胶微观形貌场发射扫描电子显微镜。7A.2 000倍放大倍数下复合水凝胶呈规则均匀的网格状，图中标尺为25 μm；7B.10 000倍放大倍数下复合水凝胶内部存在细丝网状结构，图中标尺为5 μm

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8 2组兔各时间点创面愈合情况比较。8A.伤后3 d，复合水凝胶组创面可见大量坏死组织及渗出物；8B.伤后7 d，复合水凝胶组创面仍可见少量渗出及坏死组织；8C.伤后14 d，复合水凝胶组创面坏死组织减少、痂皮逐渐脱落，创面红润可见肉芽组织生长；8D.伤后21 d，复合水凝胶组创面完全愈合；8E.伤后28 d，复合水凝胶组创面部位可见新生毛发；8F.伤后3 d，纱布对照组创面可见散在结痂，亦可见少量坏死组织及渗出物；8G.伤后7 d，纱布对照组创面出现与纱布粘连情况；8H.伤后14 d，创面基底呈苍白色、血运差，仍有少量渗出物；8I.伤后21 d，纱布对照组创面也出现愈合趋势，创面基底红润；8J.伤后28 d，纱布对照组仍残存椭圆形创面

注：复合水凝胶指负载银和重组人碱性成纤维细胞生长因子的甲基丙烯酸酐化明胶水凝胶

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表1 2组兔深Ⅱ度烧伤创面各时间点愈合率比较（%， $\bar{x} \pm s$ ）

组别	兔数（只）	伤后7 d	伤后14 d	伤后21 d	伤后28 d
复合水凝胶组	30	34±7	70±8	89±6	100±3
纱布对照组	30	29±10	59±11	75±8	88±8
t值		2.24	4.43	7.67	7.69
P值		0.030	<0.001	<0.001	<0.001
注：复合水凝胶指负载银和重组人碱性成纤维细胞生长因子的甲基丙烯酸酐化明胶；处理因素主效应，F=104.40，P<0.001；时间因素主效应，F=699.50，P<0.001；两者交互作用，F=3.55，P=0.015

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参考文献(33)

[1]	PereiraRF, BártoloPJ. Traditional therapies for skin wound healing[J]. Adv Wound Care (New Rochelle), 2016,5(5):208-229. DOI: 10.1089/wound.2013.0506.
[2]	罗高兴, 刘梦龙. 应用功能材料促进皮肤创面修复[J].中华烧伤杂志,2021,37(11):1005-1010. DOI: 10.3760/cma.j.cn501120-20210930-00340.
[3]	Van Den Bulcke AI, BogdanovB, De RoozeN, et al. Structural and rheological properties of methacrylamide modified gelatin hydrogels[J]. Biomacromolecules, 2000,1(1):31-38. DOI: 10.1021/bm990017d.
[4]	OhwadaK. Body surface area of the golden Syrian hamster[J]. Jikken Dobutsu, 1992,41(2):221-224. DOI: 10.1538/expanim1978.41.2_221.
[5]	胥杰龙改性明胶/聚丙烯酰胺复合水凝胶及其用于软骨缺损修复的研究成都西南交通大学2016 胥杰龙.改性明胶/聚丙烯酰胺复合水凝胶及其用于软骨缺损修复的研究[D].成都:西南交通大学,2016.
[6]	YueK, Trujillo-de SantiagoG, AlvarezMM, et al. Synthesis, properties, and biomedical applications of gelatin methacryloyl (GelMA) hydrogels[J]. Biomaterials, 2015,73:254-271. DOI: 10.1016/j.biomaterials.2015.08.045.
[7]	BessaLJ, FaziiP, Di GiulioM, et al. Bacterial isolates from infected wounds and their antibiotic susceptibility pattern: some remarks about wound infection[J]. Int Wound J, 2015,12(1):47-52. DOI: 10.1111/iwj.12049.
[8]	LokCN, HoCM, ChenR, et al. Silver nanoparticles: partial oxidation and antibacterial activities[J]. J Biol Inorg Chem, 2007,12(4):527-534. DOI: 10.1007/s00775-007-0208-z.
[9]	董云青, 李琳琳, 朱宣儒, 等. 含银黏性水凝胶的制备及其在小鼠细菌定植全层皮肤缺损创面愈合中的作用[J].中华烧伤杂志,2021,37(11):1036-1047. DOI: 10.3760/cma.j.cn501120-20210906-00304.
[10]	XuR, LuoG, XiaH, et al. Novel bilayer wound dressing composed of silicone rubber with particular micropores enhanced wound re-epithelialization and contraction[J]. Biomaterials, 2015,40:1-11. DOI: 10.1016/j.biomaterials.2014.10.077.
[11]	Xavier MendesA, Moraes SilvaS, O'ConnellCD, et al. Enhanced electroactivity, mechanical properties, and printability through the addition of graphene oxide to photo-cross-linkable gelatin methacryloyl hydrogel[J]. ACS Biomater Sci Eng, 2021,7(6):2279-2295. DOI: 10.1021/acsbiomaterials.0c01734.
[12]	ArmatoU,FreddiG.Editorial: biomaterials for skin wound repair: tissue engineering, guided regeneration, and wound scarring prevention[J]. Front Bioeng Biotechnol, 2021, 9:722327. DOI: 10.3389/fbioe.2021.722327.
[13]	XiaoY, ReisLA, FericN, et al. Diabetic wound regeneration using peptide-modified hydrogels to target re-epithelialization[J]. Proc Natl Acad Sci U S A, 2016,113(40):E5792-E5801. DOI: 10.1073/pnas.1612277113.
[14]	EkeG, MangirN, HasirciN, et al. Development of a UV crosslinked biodegradable hydrogel containing adipose derived stem cells to promote vascularization for skin wounds and tissue engineering[J]. Biomaterials, 2017,129:188-198. DOI: 10.1016/j.biomaterials.2017.03.021.
[15]	ZhaoX, SunX, YildirimerL, et al. Cell infiltrative hydrogel fibrous scaffolds for accelerated wound healing[J]. Acta Biomater, 2017,49:66-77. DOI: 10.1016/j.actbio.2016.11.017.
[16]	宋知仁, 郑建锋, 成路, 等. 同型新鲜冰冻血浆联合负压封闭引流在压疮修复中的效果[J].中华烧伤杂志,2017,33(3):171-172. DOI: 10.3760/cma.j.issn.1009-2587.2017.03.009.
[17]	SamaniMK, SaberiBV, Ali TabatabaeiSM, et al. The clinical evaluation of platelet-rich plasma on free gingival graft's donor site wound healing[J]. Eur J Dent, 2017,11(4):447-454. DOI: 10.4103/ejd.ejd_76_17.
[18]	SridharanK, SivaramakrishnanG. Growth factors for diabetic foot ulcers: mixed treatment comparison analysis of randomized clinical trials[J]. Br J Clin Pharmacol, 2018,84(3):434-444. DOI: 10.1111/bcp.13470.
[19]	中国老年医学学会烧创伤分会. 胶原类创面材料临床应用全国专家共识(2018版)[J].感染、炎症、修复,2018,19(4):200-203. DOI: 10.3969/j.issn.1672-8521.2018.04.002.
[20]	陈秋东中等纯度重组人表皮生长因子(rhEGF)的分离纯化及在美容产品中的应用杭州浙江大学2003 陈秋东.中等纯度重组人表皮生长因子(rhEGF)的分离纯化及在美容产品中的应用[D].杭州:浙江大学,2003.
[21]	SubravetiSN, RaghavanSR. A simple way to synthesize a protective "skin" around any hydrogel[J]. ACS Appl Mater Interfaces, 2021,13(31):37645-37654. DOI: 10.1021/acsami.1c09460.
[22]	KoH, SuthiwanichK, MaryH, et al. A simple layer-stacking technique to generate biomolecular and mechanical gradients in photocrosslinkable hydrogels[J]. Biofabrication, 2019,11(2):025014. DOI: 10.1088/1758-5090/ab08b5.
[23]	SunX,LangQ,ZhangH,et al. Cell scaffolds: electrospun photocrosslinkable hydrogel fibrous scaffolds for rapid in vivo vascularized skin flap regeneration[J]. Adv Funct Mater, 2017,27(2).DOI: 10.1002/adfm.201770008
[24]	JannaschM, GroeberF, BrattigNW, et al. Development and application of three-dimensional skin equivalents for the investigation of percutaneous worm invasion[J]. Exp Parasitol, 2015,150:22-30. DOI: 10.1016/j.exppara.2015.01.005.
[25]	WuJ, ZhuJ, HeC, et al. Comparative study of heparin- poloxamer hydrogel modified bFGF and aFGF for in vivo wound healing efficiency[J]. ACS Appl Mater Interfaces, 2016,8(29):18710-18721. DOI: 10.1021/acsami.6b06047.
[26]	ZhaoL, LiX, ZhaoJ, et al. A novel smart injectable hydrogel prepared by microbial transglutaminase and human-like collagen: its characterization and biocompatibility[J]. Mater Sci Eng C Mater Biol Appl, 2016,68:317-326. DOI: 10.1016/j.msec.2016.05.108.
[27]	LiuM, LuoG, WangY, et al. Optimization and integration of nanosilver on polycaprolactone nanofibrous mesh for bacterial inhibition and wound healing in vitro and in vivo[J]. Int J Nanomedicine, 2017,12:6827-6840. DOI: 10.2147/IJN.S140648.
[28]	LiuY, Chan-ParkMB. A biomimetic hydrogel based on methacrylated dextran-graft-lysine and gelatin for 3D smooth muscle cell culture[J]. Biomaterials, 2010,31(6):1158-1170. DOI: 10.1016/j.biomaterials.2009.10.040.
[29]	HuangR, HuJ, QianW,et al. Recent advances in nano- therapeutics for the treatment of burn wounds[J]. Burns Trauma,2021,9:tkab026[2022-04-02]. https://pubmed.ncbi.nlm.nih.gov/34778468/.DOI: 10.1093/burnst/tkab026.
[30]	ZhangX, ShuW, YuQ, et al. Functional biomaterials for treatment of chronic wound[J]. Front Bioeng Biotechnol, 2020,8:516. DOI: 10.3389/fbioe.2020.00516.
[31]	ChenG, YuY, WuX, et al. Wound healing: bioinspired multifunctional hybrid hydrogel promotes wound healing[J/OL]. Adv Funct Mater,2021,28(33):1870233[2021-09-30]. https://doi. org/10.1002/adfm.202105749. DOI: 10.1002/adfm.201870233.
[32]	焦建强, 李烨, 黄喆, 等. 重组人表皮生长因子凝胶联合纳米银敷料对烧伤后瘢痕的影响[J].中国组织工程研究,2015,(25):4007-4011. DOI: 10.3969/j.issn.2095-4344.2015.25.014.
[33]	KamalyN, YameenB, WuJ, et al. Degradable controlled- release polymers and polymeric nanoparticles: mechanisms of controlling drug release[J]. Chem Rev, 2016,116(4):2602-2663. DOI: 10.1021/acs.chemrev.5b00346.