生物材料的機械性質影響著許多生物反應的途徑（Biological process），例如細胞形態的改變及遷移、自我修復能力和機械信號的傳導。而原子力顯微鏡 （Atomic Force Microscope, AFM）有著能在生理環境下對生物體進行即時、非破壞性量測的優勢，因此近年來生物、醫學以及藥物學領域開始廣泛地運用AFM對生物材料進行力學分析。然而，由AFM獲得之Force-Distance curve需要透過接觸模型計算楊氏模數（Young’s modulus, E），在轉換的過程中有諸多因素得納入考量，尤其是樣品與探針間的接觸行為與接觸模型之間的適用性，以及因基板影響導致的量測到的值遠高於材料本身的E值，這兩者均會造成量測結果出現嚴重的誤差且準確度下降，使得不同材料的力學性質及各團隊的研究成果難以比較並整合。
為此本研究除了藉由各種材料的Force-Distance curve討論接觸模型之適用性外，也透過製備不同厚度的高分子PDMS（Polydimethylsiloxane）薄膜於兩種E值基板PMMA和玻璃進行AFM nanoindentation實驗，討論基板效應與軟性材料薄膜間的關係。而後依據實驗結果統整出初步的黏附接觸模型選用圖，從中判斷軟性高分子材料適合以Johnson-Kendall-Roberts（JKR）模型計算其E值；也發現量測到的薄膜E值之所以會高於本身的材料性質，除了基板給予的影響（此研究稱其為Elastic field effect）外，也存在著Surface effect、Stiffening effect以及Substrate deformation，且每一種效應對探針下壓深度都有不同程度上的依賴性。與材料表面性質有關的Surface effect發生的區間介於下壓深度30 ~ 500 nm；基板造成的Elastic field effect以及因樣品有限厚度產生的Stiffening effect則是從探針接觸薄膜起，便會一直存在的影響；而Substrate deformation發生的下壓深度取決於薄膜本身之E值，以4.40 MPa的PDMS為例，該效應發生於下壓深度2 μm，此時下層基板已共同抵抗探針施加的力。
最後本研究藉由高分子薄膜的結果與討論建立一套簡單的分析流程，實際應用於小鼠細胞的力學分析，探討L929正常細胞與B16F10惡性細胞的機械性質之差異，並根據評估之結果進行流程的修正。其中，驗證AFM能夠辨識相似形貌但不同細胞種之機械性質，又B16F10之E值相較於L929來得高，推測與其細胞形貌以及胞質內部結構較為相關。另外，量測到的細胞力學性質取決於實驗手法與使用的假設接觸模型，例如：彈性、黏彈性和張力等，因此事先擬定目標量測之細胞力學性質及實驗方法，亦對於統整各團隊研究成果至關重要。

We propose the adhesive contact model selection map which suggested soft biological materials are suitable to be calculated by the Johnson-Kendall-Roberts model. It is also found that the reason why using AFM nanoindentation to measure the Young’s modulus of thin soft film is often overestimated. Because there are surface effect, stiffening effect, substrate deformation and the influence of the substrate (is also called elastic field effect), each effect is indentation depth dependent. Moreover, it is assumed that the impact of elastic field effect is in proportion to substrate with different Young's modulus, while surface effect is determined by material properties of the sample surface.

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