本文選題：肌肉 + 力矩　； 參考：《魯東大學(xué)》2015年碩士論文

【摘要】：肌肉收縮產(chǎn)生力從而為人體運(yùn)動(dòng)提供動(dòng)力,研究肌肉的力學(xué)特性有助于深化了解人體運(yùn)動(dòng)的本質(zhì)和規(guī)律。在肌肉評(píng)定這方面的信息是多方面、多維度的,首先,在肌肉收縮力學(xué)方面,肌肉收縮使關(guān)節(jié)發(fā)生轉(zhuǎn)動(dòng)從而產(chǎn)生力矩,力矩是評(píng)價(jià)肌肉功能的定量指標(biāo)。另外,還包括肌肉運(yùn)動(dòng)時(shí)的電生理指標(biāo),例如表面肌電,表面肌電是肌肉收縮在時(shí)間上產(chǎn)生的一系列電信號(hào),對(duì)表面肌電的相應(yīng)參數(shù)進(jìn)行分析可以評(píng)定肌肉的活動(dòng)狀態(tài)。基于統(tǒng)計(jì)學(xué)理論對(duì)以上兩者進(jìn)行力學(xué)建模,數(shù)學(xué)計(jì)算,以及人體實(shí)驗(yàn)相結(jié)合的方法可以獲得運(yùn)動(dòng)時(shí)人體下肢控制肌群的力-電關(guān)系。通過以上運(yùn)動(dòng)信息的獲得有助于對(duì)人體下肢鞭打動(dòng)作的特點(diǎn)進(jìn)行研究,確定動(dòng)作實(shí)現(xiàn)的理論依據(jù),評(píng)定動(dòng)作的正確模式。同時(shí)還可以建立起相應(yīng)的力-電關(guān)系方程,這樣在得到表面肌電的情況下就可以預(yù)測(cè)相應(yīng)的關(guān)節(jié)力矩,因?yàn)殛P(guān)節(jié)力矩的獲取比較復(fù)雜費(fèi)時(shí),而表面肌電的獲取則相對(duì)容易,這對(duì)分析動(dòng)作技術(shù)和關(guān)節(jié)力矩?fù)p傷有非常重要的意義。 在動(dòng)力學(xué)方面,本實(shí)驗(yàn)建立了下肢環(huán)節(jié)鏈模型,通過三維錄像與解析系統(tǒng)對(duì)實(shí)驗(yàn)錄像進(jìn)行解析,對(duì)解析后的數(shù)據(jù)使用自編寫的Matlab語言程序包進(jìn)行分析,從而計(jì)算出下肢各關(guān)節(jié)的關(guān)節(jié)肌力矩。在肌電學(xué)方面,本研究運(yùn)用時(shí)頻分析指標(biāo)對(duì)肌電信號(hào)進(jìn)行分析,這彌補(bǔ)了以往在表面肌電分析方面只能對(duì)時(shí)域參數(shù)或者頻域參數(shù)進(jìn)行分析的不足。時(shí)頻分析是結(jié)合時(shí)間和頻率兩方面的指標(biāo),通過建立兩者問的函數(shù)關(guān)系來描述信號(hào)的,可以反映信號(hào)頻率在時(shí)間上的變化趨勢(shì)。在傳統(tǒng)表面肌電分析中運(yùn)用的諸如平均頻率、中值頻率的肌電學(xué)指標(biāo)通常適用于肌肉的靜態(tài)收縮過程,但往往在實(shí)際運(yùn)動(dòng)中肌肉的收縮都處于動(dòng)態(tài)收縮的過程,靜態(tài)收縮過程中,肌肉的肌電信號(hào)屬于平穩(wěn)的電信號(hào),可以運(yùn)用中值頻率等指標(biāo),但動(dòng)態(tài)收縮的過程中肌電信號(hào)是非平穩(wěn)的電信號(hào),此時(shí)就需要結(jié)合時(shí)頻分析法對(duì)動(dòng)態(tài)收縮過程中的肌電信號(hào)進(jìn)行分析。 通過對(duì)下肢前擺性鞭打關(guān)節(jié)力矩的計(jì)算以及表面肌電的分析,本文采用逐步回歸的方法對(duì)下肢髖、膝關(guān)節(jié)力矩、控制肌群的表面肌電及關(guān)節(jié)角度建立回歸方程,具體方程如下 1、髖關(guān)節(jié)方程無預(yù)擺下肢前擺性鞭打方程:Y=108.985+0.143X5-340.914X6+2.469X7被動(dòng)預(yù)擺下肢前擺性鞭打方程:Y=127.367-0.033X5+9285.734X6+5.287X7主動(dòng)預(yù)擺下肢前擺性鞭打方程:Y=180.837+0.113X5+135.710X6+9.479X7Y：髖關(guān)節(jié)力矩15：股直肌瞬時(shí)平均功率16：股直肌瞬時(shí)平均頻率17：髖關(guān)節(jié)角度 2、膝關(guān)節(jié)方程無預(yù)擺下肢前擺性鞭打方程：Y=77.475+0.209X1-0.029X3-0.575X5-3.901X7被動(dòng)預(yù)擺下肢鞭打方程：Y=154.945-2327.52X2+1169.86X4-847.07X6-3.033X7主動(dòng)預(yù)擺下肢前擺性鞭打方程：Y=54.730+732.971X2-688.835X4-1.711X7Y：膝關(guān)節(jié)力矩X1：股直肌瞬時(shí)平均功率X2：股直肌瞬時(shí)平均頻率X3：股內(nèi)側(cè)肌瞬時(shí)平均功率14：股內(nèi)側(cè)肌瞬時(shí)平均頻率15：股外側(cè)肌瞬時(shí)平均功率16：股外側(cè)肌瞬時(shí)平均頻率17：膝關(guān)節(jié)角度
[Abstract]:Muscle contraction produces force to provide power for human motion. The study of the mechanical properties of muscles helps to deepen the understanding of the nature and laws of human motion. The information in this aspect is multidimensional and multidimensional. First, in the muscle contraction mechanics, muscle contraction causes the joints to turn to produce torque, and the torque is the evaluation of the muscles. The quantitative index of meat function. In addition, it also includes electrophysiological indexes of muscle movement, such as surface electromyography, surface electromyography is a series of electrical signals produced by muscle contraction in time. The analysis of the corresponding parameters of surface electromyography can evaluate the active state of muscles. Based on the theory of unified theory, the above two are mechanic modeling and mathematics. The calculation, and the method of combining the human body, can obtain the force electric relation of the muscle group in the lower limbs of the human body when the movement is exercised. The acquisition of the above motion information is helpful to the study of the characteristics of the movement of the leg whipping, the theoretical basis of the realization of the action and the positive mode of the action, and the corresponding force electricity can also be established. The equation of relation can predict the corresponding joint torque in the case of surface electromyography, because the acquisition of joint torque is more complex and time-consuming, and the acquisition of surface electromyography is relatively easy, which is of great significance for the analysis of action technology and joint torque damage.
In the field of dynamics, the lower limb link chain model was established in this experiment. The experimental video was analyzed by the three-dimensional video and analytical system, and the analytic data was analyzed by the Matlab language program package which was compiled and written by ourselves. Thus the joint muscle torque of the joints of the lower extremities was calculated. In the field of electromyography, the time frequency analysis index was used in this study. The analysis of EMG signal makes up for the deficiency that can only analyze the time domain parameters or frequency domain parameters in the surface electromyography analysis. The time frequency analysis is a combination of two aspects of time and frequency, which describes the signal by establishing the function relation of the two questions, which can reflect the change trend of the signal frequency in time. The electromyography indexes, such as average frequency and median frequency, are usually applied to the static contraction process of muscle, but the contraction of muscle is always in the process of dynamic contraction during the actual movement. In the process of static contraction, the signal of muscle electromyography is a stationary signal and can be used in the middle value frequency and so on. However, in the process of dynamic contraction, the EMG signal is a non-stationary signal. At this time, it is necessary to analyze the EMG signal during the dynamic contraction with the time frequency analysis.
Through the calculation of the torque of the anterior pendulum of the lower limbs and the analysis of the surface electromyography, the regression equation of the hip, knee torque, the surface electromyography and the joint angle of the muscle group is established by stepwise regression. The specific equations are as follows.
1, the hip equation had no pre pendulum whipping equation: Y=108.985+0.143X5-340.914X6+2.469X7 passive pre pendulum front pendulum whipping equation: Y=127.367-0.033X5+9285.734X6+5.287X7 active pre pendulum anterior pendulum whipping equation: Y=180.837+0.113X5+135.710X6+9.479X7Y: hip torque 15: the instantaneous average power of the rectus femoris is 16: stock The instantaneous average frequency of the rectus muscle 17: the hip joint angle
2, the knee joint equation has no pre pendulum front swing equation: Y=77.475+0.209X1-0.029X3-0.575X5-3.901X7 passive pre pendulum lower leg whip equation: Y=154.945-2327.52X2+1169.86X4-847.07X6-3.033X7 active pre pendulum anterior pendulum whipping equation: Y=54.730+ 732.971X2-688.835X4-1.711X7Y: knee torque X1: instantaneous averages of the rectus femoris Power X2: the instantaneous average frequency of the rectus femoris is X3: the instantaneous average power of the medial femoral muscle is 14: the instantaneous average frequency of the medial femoral muscle is 15, the instantaneous average power of the lateral femur muscle is 16: the instantaneous average frequency of the lateral femur muscle is 17: the knee joint angle.
【學(xué)位授予單位】：魯東大學(xué)
【學(xué)位級(jí)別】：碩士
【學(xué)位授予年份】：2015
【分類號(hào)】：G804.6

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