在生物體內的細胞除了受到許多生理因子的調控外，亦受到不同機械應力的刺激，使其生長與功能上有顯著的影響。然而，在傳統的細胞培養過程中並無法提供這些機械力刺激，因而在生物體內的細胞與傳統細胞培養間產生的差異。
本研究於無菌操作台中架設了一組自動化監控的生物反應器系統來模擬生物體內的合適環境培養脂肪幹細胞於體外的層流場刺激下，如此一來可達到最低的細胞染菌率，同時亦提供了實驗操作上的便利性。而在此流場下產生穩態的流體剪應力刺激脂肪幹細胞的生長，並計算流場狀態和流道內剪應力以再次確認系統改良後的可用性，從測試結果中得知，於穩態的3 dyne/cm2剪應力下進行1、5、10小時的刺激後，量測得平均溫度為37.01  0.074、37.02  0.075、37.00  0.075 ℃ 及平均剪應力為3.02  0.001、3.02  0.003、3.02  0.004 dyne/cm2，證明此系統中的溫度與流量控制確實達到高度的精準度與穩定度。
單晶片的C程式語言軟體進行的流量校正確實可以克服幫浦運轉過程中先天性的缺陷，實際上可達到的即時監控性更優於以往微軟作業系統的程式軟體控制法，而在程式軟體介面的設計上，亦提供更多實驗參數設定的選擇性，以利未來在流體腔改良後程式中數值的設定。
另外亦利用光學顯微鏡圖和染色的螢光圖與量化圖表闡明細胞的生長狀況，實驗進行前預先培養脂肪幹細胞於PDMS上24小時，然後再分別於靜態的體外培養10小時或在穩態的3 dyne/cm2剪應力下進行10小時的刺激。最後由細胞生長狀況的結果呈現，相對於靜態培養組別，受到穩態流場刺激後的細胞會有部分流失，且在後續兩組實驗結果的細胞生長方向角度與細胞形狀指標的圖表中，亦顯示並無特徵性差異存在於各組實驗前後或各組實驗間，讓我們瞭解此改良的生物反應器系統仍尚未達到體外培植脂肪幹細胞所預期的生理條件，希望能在未來修正此生物反應器系統達到最佳仿生條件趨近於生物體內的生理環境。

Besides many physiological factors regulating the cells in vivo, mechanical stress also has the obvious influences on cell growth and function. However, it can’t supply these mechanical stimuli through the traditional cell culture process, thus it makes the differences between the cells in vivo and the traditional cell culture.
In this study, we constructed a set of auto-controlled bioreactor system in the hood to supply the mechanical stress on cells, and let the adipose-derived stem cells (ADSCs) of the fluid-stimulated experiments under a minimum possibility of contamination through the barrier property of the hood. Meanwhile, it was also convenient for operating experiments in the hood. After stimulating ADSCs under the laminar flow field, calculating the flow field mode and the fluid shear stress (FSS) to ensure the availability of the improved bioreactor system. The examined results showed that the average temperatures were 37.01  0.074, 37.02  0.075, and 37  0.075 ℃ and the average FSS were 3.02  0.001, 3.02  0.003, and 3.02  0.004 dyne/cm2 after during the stimulations of 1, 5, and 10 hours under a steady flow of 3 dyne/cm2. It indicated the temperature and flow rate control exactly achieved high accuracy and stability.
However, the calibration of flow rate conducted by the programming language C in microcontroller could conquer the potential operating defects of the peristaltic pump. The programming language C in microcontroller could achieve more precise instantaneous control than the program software control on the Windows Microsoft operating system. Besides, the design of LabVIEW program interface could also supply more selections of the parameters for the newly-designed flow chamber in the future.
On the other hand, we clarified the growth condition of ADSCs via the optical microscopy images, the fluorescent images, and the quantitative charts. ADSCs could culture on the polydimethylsiloxane (PDMS) for 24 hours and then separately cultured in two conditions, under the static-state cultivation for 10 hours and the shear stress stimulus of 3 dyne/cm2 for 10 hours. Furthermore, the reaction of ADSCs after stimulation by the laminar flow was observed through the above experiments. The results of optical microscopy images and fluorescent images showed that there were some parts of ADSCs lost after the steady FSS stimuli compared with the static culture group. On the other hands, the elongation with the flow direction of cell cytoskeleton and cell morphology had the insignificantly tendency between the comparisons of the pre-test and post-test in each experimental group and the two groups.
Above all of the results in the study, our improved bioreactor system didn’t achieve the expected physiological conditions in cultivating the ADSCs in vitro. We hope that we can modify the bioreactor system to achieve optimal conditions which are closer to the real in vivo condition in the future.

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