請用此 Handle URI 來引用此文件：
http://tdr.lib.ntu.edu.tw/jspui/handle/123456789/77870完整後設資料紀錄
| DC 欄位 | 值 | 語言 |
|---|---|---|
| dc.contributor.advisor | 蔡偉博(Wei-Bor Tsai) | |
| dc.contributor.author | Wen-Hsuan Chen | en |
| dc.contributor.author | 陳玟璇 | zh_TW |
| dc.date.accessioned | 2021-07-11T14:36:22Z | - |
| dc.date.available | 2022-08-31 | |
| dc.date.copyright | 2017-08-31 | |
| dc.date.issued | 2017 | |
| dc.date.submitted | 2017-08-17 | |
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| dc.identifier.uri | http://tdr.lib.ntu.edu.tw/jspui/handle/123456789/77870 | - |
| dc.description.abstract | 在高齡人口增加且醫療支出增加的趨勢下，醫療器材產業蓬勃發展，大多數的醫療器材都需要與人類血液抑或是體液接觸，表面容易吸附非特定性蛋白質或微生物的累積，導致器材效能低落、靈敏度下降，因此在表面修飾抗貼附塗層以阻擋非特異性蛋白質吸附，更進一步抵抗細胞貼附。在本研究中，首先藉由自由基聚合合成含有雙離子性的sulfobetaine的共聚物 (pSBMA-co-AEMA)，並開發一步驟AMN 塗佈的方式將兩性分子之共聚物修飾表面，使其能夠達到抗血清蛋白吸附及纖維母細胞 (fibroblast) 貼附的效果。
本研究首先探討共聚物濃度、SBMA/AEMA比例以及反應時間對修飾表面的影響，藉由纖維母細胞(L929)貼附實驗找到最佳抗貼附條件，接著利用石英微量天平測量血清蛋白吸附進行表面分析，本研究中抗貼附表面可減少80%蛋白質吸附量，並將此表面修飾方法運用在PDMS及玻璃上，證明此方法能夠廣泛應用在不同基質上。不僅如此，長期穩定性也是抗貼附表面非常重要的一環，經由穩定性實驗得知，此表面抗貼附功能能維持至少45天，證實此修飾方法能夠在長時間中仍保持穩定。 PDMS是醫療器材中常見的一種生醫材料，為了模擬醫療器材製備流程，因此將PDMS表面修飾之後，進行環氧二烷及高壓釜滅菌以確保其抗貼附的穩定性。從研究結果顯示，相較於未修飾的PDMS，沒有任何細胞貼附在修飾後的表面，由此可知，經滅菌之後的表面仍然表現出高度抗貼附的能力。在未來研究中，欲將此表面進行動物實驗，觀察是否在動物體內產生異物反應。 | zh_TW |
| dc.description.abstract | Due to the increased elderly population and the trend of medical expenses increasing, the medical device industry is growing rapidly. Most of the medical devices need to contact with human blood or body fluids, so the surface is easy to adsorb the nonspecific proteins and cause accumulation of microorganisms, resulting in low efficiency of devices, and the decreased sensitivity. Therefore, surface modification by antifouling coating is necessary to repel protein adsorption, and further resist the cell attachment. In this study, we synthesized the zwitterionic sulfobetaine containing copolymers (P(SBMA-co-AEMA) via free radical polymerization first. One step AMN assisted zwitterionic copolymers coating was developed for surface modification to achieve the resistance to serum protein adsorption and fibroblast adhesion.
In our research, we explored the effects of copolymer concentration, SBMA / AEMA ratio and coating time on the modified surface, and found the optimal condition for antifouling performance through L929 cell adhesion experiments. Then, using quartz crystal microbalance (QCM) to measure serum protein adsorption, it reduced 80% of the amount protein adsorbed. Further, the coating is also applied to PDMS and glass, which proved that the method can be widely used on different substrates. Moreover, long-term stability is also a key point of the antifouling surface; through the stability experiments, the antifouling function can be maintained at least 45 days, confirmed that this modified method remains stable for a long time. PDMS is a common used biomaterial for medical devices; in order to mimic the medical device preparation process, thus we sterilized antifouling modified PDMS by ethylene oxide gas and autoclaving to verify its antifouling stability. The results showed that no cell attached on the modified surface compared to unmodified PDMS. We demonstrated that modified surface displayed highly antifouling performance after sterilization. In the future, we will carry on the animal experiments to observe whether modified PDMS induce the foreign body reaction after implanted into rat model or not. | en |
| dc.description.provenance | Made available in DSpace on 2021-07-11T14:36:22Z (GMT). No. of bitstreams: 1 ntu-106-R04524050-1.pdf: 2264753 bytes, checksum: 9af0b798f70691f388a2b6bd4bd0084a (MD5) Previous issue date: 2017 | en |
| dc.description.tableofcontents | 致謝 I
摘要 III Abstract V Content VII List of figures X List of tables XIV Chapter 1 Introduction 1 1.1 Antifouling surface 3 1.2 Antifouling materials 5 1.2.1 polyHEMA (poly(hydroxyethyl methacrylate)) 6 1.2.2 PEG (poly(ethylene glycol)) 7 1.2.3 Zwitterionic polymers 9 1.3 Surface modification by antifouling materials 17 1.3.1 Grafting from method 18 1.3.2 Grafting to method 19 1.4 Research motivation 30 1.5 Research objective 32 Chapter 2 Materials and Methods 33 2.1 Chemicals 33 2.1.1 Synthesis of P(SBMA-co-AEMA) & P(MPC-co-AEMA) 33 2.1.2 AMN assisted coating 33 2.1.3 Cell culture 33 2.2 Experimental instrument 35 2.3 Experimental materials 35 2.4 Solution formula 36 2.5 Methods 38 2.5.1 Synthesis of zwitterionic copolymers 38 2.5.2 AMN-assisted deposition of P(SBMA-co-AEMA) onto various substrates 39 2.5.3 Dynamic water contact angle (WCA) 40 2.5.4 QCM measurement 40 2.5.5 Cell culture 43 2.5.6 Cytotoxicity evaluation of antifouling coatings 44 2.5.7 Stability test 46 2.5.8 Sterilization 46 2.5.9 In vivo study for implantation of PDMS 48 2.5.10 Harvest of capsule formation and histological analysis 48 2.5.11 Statistic Analysis 49 Chapter 3 Characterization of antifouling properties for modified surface 55 3.1 Synthesis and characterization of P(SBMA-co-AEMA) 55 3.2 Measurement and evaluation of antifouling properties on P(SBMA-co-AEMA)/AMN modified surfaces by cell adhesion 56 3.3 Evaluation of cytotoxicity to antifouling surface 62 3.4 Surface characterization 63 3.5 The amount of protein adsorption. 67 3.6 Antifouling properties of coating on various substrates 69 3.7 Stability test 70 3.8 Sterilization process 71 3.9 Discussion 74 Chapter 4 Conclusions 80 Chapter 5 Future work 81 Reference 83 List of figures Figure 1-1. Evolution of antifouling materials. 6 Figure 1-2 The composition of cell membrane. 10 Figure 1-3. The chemical structure of MPC. 11 Figure 1-1. The chemical structure of SBMA monomer [58]. 14 Figure 1-5. The chemical structure of CBMA monomer [33]. 16 Figure 1-6. Schematic illustration of different methods for immobilizing zwitterionic polymers on solid surfaces [65]. 18 Figure 1-7. Schematic illustration of LBL deposition to repel protein adsorption [70]. 22 Figure 1-8. Dopamine structure. 24 Figure 1-9. Dopamine coating process on virtually any material surface. 24 Figure 1-10. Routes for the formation of HCN-derived polymers [81]. 29 Figure 2-1. The synthesis process of P(SBMA-co-AEMA) 50 Figure 2-2. AMN assisted of zwitterionic copolymers coating. 51 Figure 2-3. The scheme of dynamic water contact angle measurement. 52 Figure 2-4. The coating process of QCM chip. 53 Figure 3-1. The 1H NMR spectrums of P(SBMA-co-AEMA) with different SBMA/AEMA ratios. (A) at 4.25 ppm refers to O-CH2, while (B) at 3.34 refers to CH2-NH2 from AEMA segments. 56 Figure 3-2. Cell morphology of L929 fibroblast cultured for 24 h on TCPS modified by different SBMA/AEMA ratio polymers with AMN. (a) AMN, (b) PSB, (c) PSB-AE0.1, (d) PSB-AE0.5, (e) PAEMA, and (f) TCPS. 59 Figure 3-3. Cell morphology of L929 fibroblast cultured for 24 h on TCPS modified by PSB-AE0.1/AMN at different coating time. (a) 2 h, (b) 4 h, (c) 6 h, (d) 8 h, (e) 12 h, (f) 24 h, and (g) TCPS 60 Figure 3-4. Cell morphology of L929 fibroblast cultured for 24 h on TCPS modified by AMN with different PSB-AE0.1 concentrations. PSB-AE0.1/AMN = (a) 1/1, (b) 3/1, (c) 5/1, (d) AMN, and (e) TCPS. 61 Figure 3-5. Cell density of L929 fibroblast cultured for 24 h on TCPS modified by PSB10-AE1/AMN with different (a) SBMA/AEMA ratios, (b) coating time, and (c) polymer concentration. Values = mean ± standard deviation, n = 4. *** represents p < 0.001 vs. TCPS. 61 Figure 3-6. Toxicity of PSB-AE0.1/AMN surface extracts and control standards against L929 fibroblasts (*** represents p < 0.001 vs medium). Viability = sample OD/ medium OD. The values = mean ± standard deviation, n = 4. 63 Figure 3-7. SEM images of the zwitterionic polymers/AMN coating morphology. Scale bar: 10 μm 65 Figure 3-8. The dynamic water contact angles of PSB-AE0.1 coating on TCPS. (a, b) Advancing and receding angles of unmodified TCPS, (c, d) Advancing and receding angles of modified TCPS. 65 Figure 3-9. The dynamic water contact angles of PSB10-AE1 coating on PDMS. (a, b) Advancing and receding angles of unmodified PDMS, (c, d) Advancing and receding angles of modified PDMS. 65 Figure 3-10. The dynamic contact angles of PSB-AE0.1 coating on glass. (a, b) Advancing and receding angles of unmodified glass, (c, d) Advancing and receding angles of modified glass. 66 Figure 3-11. Frequency shifts in QCM adsorption experiment of 300 μL 10% serum at flow rate 36.5 μL/min on PSB-AE0.1/AMN modified surface. 68 Figure 3-12. Cell density of L929 fibroblast cultured for 24 h on modified glass and PDMS. Values = mean ± standard deviation, n = 4. **, *** represent p < 0.05, 0.001 vs. unmodified substrates. 69 Figure 3-13. Cell number ratio to TCPS for long-term stability of antifouling surface. (Normalization = cell number of sample / cell number of TCPS group.) Values = mean ± standard deviation, n = 4. 71 Figure 3-14. Cell morphology of L929 fibroblast cultured for 24 h on zwitterion modified PDMS with (a) EO sterilization, and (b) autoclaving. 72 Figure 3-15. Cell density of L929 fibroblast cultured for 24 h on zwitterion modified PDMS with (a) EO sterilization, and (b) autoclaving. Values = mean ± standard deviation, n = 4. *** represents p < 0.001 vs. unmodified PDMS with sterilization. 73 | |
| dc.language.iso | zh-TW | |
| dc.title | 利用一步驟氨基丙二腈輔助兩性離子之共聚物的塗佈於抗污之應用 | zh_TW |
| dc.title | A One-step Aminomalononitrile Assisted Coating of Zwitterionic Copolymers for Antifouling Applications | en |
| dc.type | Thesis | |
| dc.date.schoolyear | 105-2 | |
| dc.description.degree | 碩士 | |
| dc.contributor.oralexamcommittee | 游佳欣(Jiashing Yu),鍾仁傑(Ren-Jei Chung) | |
| dc.subject.keyword | 兩性高分子,AMN,抗污,塗佈,植入物,異物反應, | zh_TW |
| dc.subject.keyword | zwittorionic polymer,aminomalononitrile,antifouling,coating,implant,foreign body reaction, | en |
| dc.relation.page | 98 | |
| dc.identifier.doi | 10.6342/NTU201703399 | |
| dc.rights.note | 有償授權 | |
| dc.date.accepted | 2017-08-17 | |
| dc.contributor.author-college | 工學院 | zh_TW |
| dc.contributor.author-dept | 化學工程學研究所 | zh_TW |
| 顯示於系所單位： | 化學工程學系 | |
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