幾丁聚醣(chitosan, CS) 奈米粒子是利用電噴灑法所製作。但CS分子 量對於電灑上的影響仍須被探討，CS的分子量對CS粒子的尺寸與型態的影響很大。除此之外，在電灑的過程中，也同樣探究了幾丁聚醣濃度、電場、醋酸的濃度及溶液進料的速率所帶來的影響。CS電灑奈米粒子可應用於藥物輸送及金屬離子的吸附上。
為了探討CS電灑奈米粒子在藥物輸送上所具有的潛力，先以吲哚美辛(indomethacin, ID)作為標準藥物，其中包埋的效率、承載能力及釋放曲線已被測定過。利 用電灑方法所製成的球狀CS-ID奈米粒子平均粒徑為340 nm，並且根據CS-ID奈米粒子的 zeta 電位顯示該粒子在懸浮液中相當穩定。在ID的包埋效率上，電灑的方法 所製成的CS粒子比起其他方法製成的CS粒子效率較好，其中利用電灑法製CS粒子中，150-KDa CS對ID之包埋效率及負載能力比310-KDa CS來得高。而 藥物釋放的曲線所顯示的是釋放分為兩個階段，並在第二個階段得到較長時間的藥物輸送。綜合以上結果，此研究最佳化了CS奈米粒子的製作方法及表現出CS電灑奈米粒子是為有潛力的藥物載體。
CS 粒子同樣可應用於去除水溶液中的二價銅離子。金屬離子的去除與 二價銅離子溶液的pH值、吸附劑的量及接觸時間有極大的關聯。因此在去除水溶液中二價銅離子實驗之中，將會測定pH值、吸附劑的量及接觸時間所帶來的影響。利用glutaraldehyde與CS電灑奈米粒子交聯可增強電灑CS奈米粒子在酸性水溶液中的穩定性。從等溫的模組中可分析得到吸附達穩態時的數據，吸附二價銅離子最大的吸附能力為192.3 mg/g。為了回收吸附劑，使用 鹽酸及EDTA來脫附二價銅離子。
幾丁聚醣(chitosan, CS)奈米纖維是以電紡技術所製備的。CS溶液與 腔體的溫度會大幅影響CS電紡奈米纖維的型態。此外，在此研究中也同時測定施加電壓、CS溶液濃度、溶劑、共溶劑及注射針尖到收集板之間距離所帶來的影響。而為了能得到均相的CS奈米纖維，需最佳化電紡製備的參數。製備為的CS奈米纖維使用SEM來檢視型態。另外，利用氫氧基磷灰石(Hydroxyapatite, HA)修飾CS電紡奈米纖維的表面型態，有兩種方法，一是浸泡模擬人 體體液(SBF)，二是濕式合成法。
在浸泡SBF程序之中，CS電紡奈米纖維會在SBF中以不同的時間培養，以生成HA層在CS奈米纖維表面上。之後會以SEM、EDS、FTIR及XRD測定CS電紡奈米纖維表面HA的生成及其型態。由SEM的圖像可得知，CS奈米纖維上所的HA為均勻生成於其上。根據EDS及XRD的結果指出，在奈米纖維上需經六天SBF的培養使HA生成，並且HA的鈣磷比與自然骨相似。接下來為了檢測CS/HA奈米纖維的生物相容性，將大鼠骨瘤細胞(UMR-106)培養CS/HA奈米纖維支架上。
與CS奈米纖維、CS薄膜及CS/HA薄膜相比，CS/HA奈米纖維在細胞的增生及早期的分化有較好的表現。使用複合材料的奈米纖維會增加生物相容性及細胞的親和力。總而言之，CS/HA電紡支架在骨組織工程中是相當具潛力的材料。
另外在濕式合成法中，CS奈米纖維會先與GA交聯，再與Ca(NO3)2 和 (NH4)2NO3產生礦化反應。在製備CS/HA電紡奈米纖維中，反應會經過三個循環，以最佳化製備的時間。濕式合成法中礦化的時間約為三個小時，而使用SBF處理的礦化程序最少需144個小時 (六天)。同樣以XRD、SEM、FTIR 及EDS測定HA的生成，結果發現合成的HA相當接近自然骨。與CS奈米纖維相比，CS/HA奈米纖維對UMR細胞的貼附與延展較好，且電紡CS/HA奈米纖維支架相當適合骨細胞。

Chitosan (CS) nanoparticles were fabricated by an electrospraying method. The effects of CS molecular weight on electrospraying were investigated. The size and morphology of CS particles were strongly influenced by CS molecular weight. Moreover, CS concentration, electrical field, acetic acid concentration, and solution flow rate in the electrospraying process were also studied. The electrosprayed CS nanoparticles were applied for drug delivery and metal-ion adsorption.
To evaluate the potential of electrosprayed CS nanoparticles in drug delivery, indomethacin (ID) was used as a model drug, where the encapsulation efficiency, the loading capacity, and the releasing profiles were identified. The spherical CS-ID nanoparticles were fabricated by the electrospraying technique with an average diameter of 340 nm. Zeta potential of the ID-CS particles indicated that the particles were stable in suspension. The encapsulation efficiency (EE) and loading capacity (LC) of ID were higher for 150-kDa CS than for 310-kDa CS. The EE of ID in electrosprayed CS particles was higher than that in particles prepared by other methods. The release profiles revealed that there were two stages for releasing and the long-term delivery could be obtained in the second stage. In summary, this research optimized the electrospraying process for the fabrication of CS nanoparticles and demonstrated the potential of electrosprayed CS nanoparticles as a drug carrier.
The CS nanoparticles were also applied for the removal of Cu(II) ions from a bath aqueous solution. The electrosprayed CS nanoparticles were cross-linked by glutaraldehyde to enhance the stability in an acidic medium. In the removal process, the effects of pH, adsorbent amounts, and contact time were also studied. The metal removal strongly depended on the pH of the Cu (II) solution, the contact time, and the adsorbent amounts. The equilibrium data were analyzed by an isotherm model. The maximum adsorption capacity for Cu(II) ions was 192.3 mg/g. Hydrochloric acid (HCl) and ethylenediaminetetraacetic acid (EDTA) with various concentrations were used for the desorption of Cu(II) ions to recycle the adsorbent.
Chitosan (CS) nanofibers were prepared by an electrospinning technique. The main parameters of the electrospinning process were optimized to obtained homogeneous CS nanofibers. The temperature of CS solutions as well as the chamber strongly affected on the morphology of electrospun CS nanofibers. Moreover, the effects of applied voltage, CS concentration, solvent, co-solvent, CS molecular weight, and tip-to-collector distance were all investigated in this research. The morphology of electrospun CS nanofibers was observed by SEM. The surface of the electrospun CS nanofibers were modified the surface by hydroxyapatite (HA), which was produced by two methods: in situ precipitation in a stimulated body fluid (SBF) and a wet chemical process.
In SBF process, CS nanofibers were incubated in SBF for various times to form HA layers on the surface of CS nanofibers. The CS/HA nanofibers were characterized by SEM, EDS, FTIR, and XRD for confirming the HA formation as well as checking the morphology of the nanofibrous scaffolds. From the SEM image, the distribution of HA on the CS nanofibers was homogeneous. The results from EDS and XRD indicated that HA was formed on the nanofibrous surfaces after 6-day incubation in the SBF with a Ca/P ratio close to that of natural bones. To identify biocompatibility, CS/HA scaffolds were applied for the culture of rat osteosarcoma cells (UMR–106). Cell proliferation and early differentiation on the CS/HA nanofibers were better than those on the CS nanofibers, the CS/HA film, and the CS films. Biocompatibility and cell affinity were enhanced by using the composite nanofibers. Conclusively, the electrospun CS/HA scaffolds would be a potential material in bone tissue engineering.
In the wet chemical process, the CS nanofibers were cross-linked by GA before mineralization by the reaction of Ca(NO3)2 and (NH4)2NO3. The time of reaction with three cycles (C3) was optimized for the preparation of electrospun CS/HA nanofibers. The time of mineralization by using wet process was about 3 hours. Meanwhile, the time of mineralization by using SBF treatment was at least 144 hours (6 days). HA XRD, SEM, FTIR, EDS analyses confirmed the formation of HA, which was similar to HA found in nature bone. The attachment and spreading of UMR cells on CS/HA nanofibers were better than those on CS nanofibers. The scaffolds of electrospun CS/HA nanofiber were suitable for bone cells.

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