臺灣博碩士論文加值系統

摘 要
目的：探討足內八、足外八及自然著地等三種不同著地角度，赤腳於60公分高度下著地，對下肢關節角度調節的機轉、地面反作用力與肌電訊號之影響。方法：以北市國小五年級女性學童，足內八、足外八及自然步態各5名(年齡11.2±0.4歲、身高145.3±7.2公分、體重39.8±8.5公斤 )為受試對象。以一部Mega speed 30k高速攝影機 (100Hz) 、一台AMTI測力板 (1000Hz) 和Biovision肌電儀器 (1000Hz) 以同步方法擷取人體著地動作。影片利用Kwon3D動作分析系統處理，經人體肢段參數 (BSP )建置、直接線性轉換 ( DLT ) 獲得運動學參數。測力板原始訊號透過DasyLab 6.0分析軟體，經濾波、模組 (電壓-力量) 校正得到原始三維反作用力，再經由積分運算取得衝量參數。原始肌電訊號經由DASYLab 6.0軟體分析，進行10~500HZ的band -pass濾波處理、10Hz低通濾波 (low pass) 與全波整流上翻後，經積分運算後，可得積分肌電值（iEMG），並除以積分區間之作用時間，得肌電訊號的平均肌電振幅，並以EMG最大自主性收縮值進行標準化處理( ％MVC)。在統計方法上，採用統計軟體SPSS for windows 12.0版，以獨立樣本單因子變異數分析 (one-way ANOVA) 考驗，其顯著水準定為α＝.05。結果：一、足內八及足外八組在重心最低時下肢髖、膝關節角度明顯大於自然著地組（p＜.05）；緩衝期下肢膝關節角位移、膝關節最大角速度、重心垂直位移及緩衝時間在足內八及足外八組皆明顯小於自然著地組（p＜.05）；且足內八組在緩衝期下肢髖關節角位移、髖關節最大角速度及軀幹前傾角度明顯小於自然著地組（p＜.05）。二、足內八組在最大負荷率、垂直分力峰值及50 毫秒內的被動衝量明顯大於自然著地組（p＜.05）。三、股直肌活化程度在足內八及足外八組明顯大於自然著地組（p＜.05）。結論：不同的足部著地角度（足內八、足外八及自然著地）是影響著地動作的因子之一。足內八、足外八組是以較直立的僵直型態著地，因此在著地緩衝能力上，自然著地組較佳，比其他兩組運用較多軀幹、髖、膝關節的彎曲及位移和時間來進行緩衝，及徵召較少股直肌運動單位來穩定膝關節屈曲角度，即能夠有效減弱落地時對下肢所產生的巨大撞擊力量。建議在著地動作上，應注意落地後的足部角度，採以足尖向前的自然著地方式，避免因足內八或足外八而增加受傷的機率。

Abstract
Objctive: The aim of this research is to study the effects of different landing angles toe-in, toe-out, and neutral barefoot gait from the height of 60cm on the lower limb joints, ground reaction forces and EMG signals.Methods: 15 female fifth graders respectively with toe-in, toe-out, and neutral gait (five in each group) are selected from Taipei City to participate in this study.(age: 11.2±0.4 years old, height: 145.3±7.2 cm, weight: 39.8±8.5 kg). A Mega speed 30k high speed camera (100Hz), an AMTI force plate (1000Hz),and four Biovision EMG system (1000Hz) are used to synchronously capture kinematical , dynamics and lower limbs EMG parameters of landing. The film undergoes Kwon3D movement analysis and human limb sections of parameter organizational system and Direct Linear Transformation in order to possess the physical parameters. The primitive signal from the force plate is processed by DasyLab 6.0 software, low-pass filtering (10Hz) and calibrates modular to calculate the primitive three dimension counterforce, and then obtain the impulse value through integration analysis. The primitive signals of EMG is processed by DasyLab 6.0 software, band-pass filtering, low-pass filtering (10Hz) and full-wave rectification, also obtain the integration EMG through integration analysis. MVC is used to normalize signals of EMG. The resulting data undergoes one-way ANOVA via SPSS 12.0 statistics software. The level of significance for this experiment is set to α=.05.Results: 1.The angles of the hip and knee joints of the both the toe-in and toe-out gait groups at their lowest center of gravity are significantly greater than that of the neutral gait group. (p <.05). Knee joint angles displacement at buffer phase, the greatest angular velocities of knee joints, center of gravity vertical displacement, and buffering time are significantly smaller than that of the neutral landing group. The hip joint displacement at buffer phase, the greatest angular velocities of hip joint, and the forward inclination angle of the torso of the toe-in gait group are significantly smaller than that of the neutral landing. 2.The greater loading rate, the rate of peak vertical reaction force, and 50ms passive impulse of the toe-in gait group are greater than that of the neutral landing group. (p <.05). 3.The degrees of rectus femoris activation of the toe-in and toe-out gait groups are significantly greater than that of the neutral landing group. (p <.05).Conclusion: The angle of different landing position (toe-in, toe-out, and neutral landing gait) is one of the factors affecting the drop landing action. With regards to landing buffer capacity. The neutral gait group shows better performance than the toe-in group since the latter lands with a more erect stiffness. The neutral gait group engages more time and movement of the torso, hip, and knee joints for buffering than do the other two groups. By using less rectus femoris units to stabilizing the knee flexion of the joints, the tremendous friction produced while landing is therefore effectively reduced. In order to avoid injury caused by toe-in or toe-out gait, it is suggested that one takes the neutral landing position with the tip of the feet pointing forward.

目 次
中文摘要........................................................................................................i
英文摘要......................................................................................................iii
目次.............................................................................................................. v
表次............................................................................................................viii
圖次..............................................................................................................ix
第一章 緒論…………………………………………………………….01
第一節 問題背景…………………………………………………...01
第二節 研究目的…………………………………………………...05
第三節 研究範圍與限制…………………………………………...06
第四節 研究假定…………………………………………………...06
第五節 名詞操作性定義…………………………………………...07
第二章 文獻探討………………………………………………………...10
第一節 足部結構異常之相關文獻………………………………...11
第二節 足內八與足外八之相關文獻……………………………...14
第三節 著地動作之生物力學研究………………………………...17
第四節 著地動作之肌電相關文獻………………………………...23
第五節 文獻總結…………………………………………………...24
第三章 研究方法與步驟……………………………………………….25
第一節 實驗對象…………………………………………………...25
第二節 實驗時間與地點…………………………………………...26
第三節 研究架構…………………………………………………...26
第四節 實驗儀器與設備…………………………………………...27
第五節 實驗場地與儀器架設……………………………………...30
第六節 實驗方法與步驟…………………………………………...33
第七節 資料收集與處理…………………………………………...41
第八節 統計方法…………………………………………………...43
第四章 結果……………………………………………………………44
第一節 足內八與足外八對著地緩衝能力運動學參數之影響…..44
第二節 足內八與足外八對著地緩衝能力動力學參數之影響…..50
第三節 足內八與足外八對著地緩衝能力之下肢肌群肌電（EMG）
分析………………………………………………………...51
第四節 足內八與足外八對著地緩衝能力之特性分析…………...53
第五章 討論…………………………………………………………….56
第一節 足內八與足外八著地緩衝能力之運動學與動力學參數分
析…………………………………………………………...56
第二節 足內八與足外八著地緩衝能力之標準化積分肌電量參數
分析………………………………………………………….60
第三節 綜合討論…………………………………………………...62
第六章 結論與建議…………………………………………………….63
參考文獻………………………………………………………………….64
一、中文部分…………………………………………………………...64
二、英文部分…………………………………………………………...66
附錄一…………………………………………………………………….70

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