• Journal of Biomedical Engineering Research
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• v.36 no.5
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• pp.235-239
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• 2015

The purpose of this study was to investigate the unstable plate system for the advanced balance ability. 7 male volunteers (age $33.7{\pm}1.2$ years, height $174.7{\pm}3.8cm$, weight $86.0{\pm}3.6kg$, BMI $28.2{\pm}2.0kg/m^2$) performed the partial squat motion on the shape of CAP type(${\cap}$) and BOWL type(${\cup}$) plate system. The range of motion (ROM) and muscle activation were acquired by the motion analysis system and the EMG system. Results of ROMs of the CAP type plate system were shown the widely range of the deviation in the ankle joint on the sagittal plane (sagittal plane - hip joint $10.7^{\circ}$ > $5.4^{\circ}$, knee joint $16.3^{\circ}$ > $6.4^{\circ}$, ankle joint $18.8^{\circ}$ > $6.3^{\circ}$ ; transverse plane - hip joint $3.5^{\circ}$ > $1.8^{\circ}$, knee joint $5.3^{\circ}$ > $3.4^{\circ}$, ankle joint $11.3^{\circ}$ > $5.3^{\circ}$ ; frontal plane - hip joint $0.9^{\circ}$ > $0.5^{\circ}$, knee joint $0.8^{\circ}$ > $0.6^{\circ}$, ankle joint $4.8^{\circ}$ > $3.7^{\circ}$). Muscle activation results of the CAP type plate system were indicated higher in major muscles for balance performance than the BOWL type plate system (vastus lateralis 0.90 > 0.62, peroneus longus 0.49 > 0.21, biceps femoris 0.38 > 0.14, gastrocnemius 0.11 > 0.05). These findings may indicate that the CAP type plate system would expect better effectiveness in perform the balance training. This paper is primary study for developing balance skills enhancement training device.

• Korean Journal of Applied Biomechanics
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• v.16 no.3
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• pp.137-148
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• 2006

The purpose of this study was to compare muscle activity in the lower extremity during walking wearing jogging and roller shoes. Twelve male middle school students (age: 15.0 yrs, height 173.7 cm, weight 587.7 N) who have no known musculoskeletal disorders were recruited as the subjects. Seven pairs of surface electrodes (QEMG8, Laxtha Korea, gain = 1,000, input impedance >$1012{\Omega}$, CMMR >100 dB) were attached to the right-hand side of the body to monitor the rectus femoris (RF), vastus medialis (VM), vastus lateralis (VL), biceps femoris (BF), tibialis anterior (TA), and medial (GM) and lateral gastrocnemius (GL) while subjects walked wearing roller and jogging shoes in random order at a speed of 1.1 m/s. An event sync unit with a bright LED light was used to synchronize the video and EMG recordings. EMG data were filtered using a 10 Hz to 350 Hz Butterworth band-passdigital filter and further normalized to the respective maximum voluntary isometric contraction EMG levels. For each trial being analyzed, five critical instants and four phases were identified from the recording. Averaged IEMG and peak IEMG were determined for each trial. For each dependent variable, paired t-test was performed to test if significant difference existed between shoe conditions (p<.05). The VM, TA, BF, and GM activities during the initial double limb stance and the initial single limb stance reduced significantly when going from jogging shoe to roller shoe condition. The decrease in EMG levels in those muscles indicated that the subjects locked the ankle and knee joints in an awkward fashion to compensate for the imbalance. Muscle activity in the GM for the roller shoe condition was significantly greater than the corresponding value for the jogging shoe condition during the terminal double limb stance and the terminal single limb stance. Because the subjects tried to keep their upper body weight in front of the hip to prevent falling backward, the GM activity for the roller shoe condition increased. It seems that there are differences in muscle activity between roller shoe and jogging shoe conditions. The differences in EMG pattern may be caused primarily by the altered position of ankle, knee, and center of mass throughout the walking cycle. Future studies should examine joint kinematics during walking with roller shoes.

• Korean Journal of Applied Biomechanics
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• v.18 no.4
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• pp.171-177
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• 2008

This work intends to investigate the effects of pedaling directions on the muscle actions during the bicycle's uphill propulsion. A test rig was developed that consists of a bicyle with a special planetary geartrain, a height-adjustable treadmill, a rear-wheel support and a magnetic brake. A three-dimensional motion analysis was performed for measuring kinematic characteristics of the forward backward pedaling and the electromygraphy(EMG) measurements were simultaneously performed for estimating the muscle actions of the leg. In this work, four muscles are considered including Gastrocnemius muscle(GM), Vastus lateralis(VL), Tibialis anterior(TA) and Soleus(SOL) while the uphill slope is varied from $0^{\circ}$ to $6^{\circ}$. Raw EMG signals were first processed through the root-mean-square(RMS) averaging and then ensemble curves were derived by averaging the EMG RMS envelopes over 50 consecutive cycles. Results show that both the kinemactic characteristics and the muscle actions are significantly affected by the pedaling direction. The crank speed of the forward pedaling is higher but the difference in speed is reduced as the slope is increased. The ensemble curves of the :ac signals clearly exhibit some differences in their patterns, peak values and the corresponding locations with respect to the crank angle. The peak values of most EMG signals are higher for the forward pedaling regardless of the slope magnitude. However, the averages of the EMG signals are not observed to have a similar relationship with the pedaling direction, which seems to be affected by several factors such as less experience of the participants' backward pedaling. inappropriate bicycle design for the backward pedaling. These limitations will be further considered in future work.

• Physical Therapy Korea
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• v.19 no.1
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• pp.28-36
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• 2012

This study used an unstable platform to change the support surface type and position of both lower limbs in order to determine changes in weight distribution and muscle including the vastus medialis, tibialis anterior, lateral hamstring, and lateral gastrocnemius of both lower limbs were evaluated during knee joint flexing and extending in a semi-squat movement in 32 hemiplegic patients. The support surface conditions applied to the lower limbs were divided into four categories: condition 1 had a stable platform for both lower limbs; condition 2 had an unstable platform for the non-hemiplegic side and a stable platform for the hemiplegic side; condition 3 had a stable platform for the non-hemiplegic side and an unstable platform for the hemiplegic side; and condition 4 had an unstable platform for both sides. The normalized EMG activity levels of muscles and weight bearing ratio of both sides in the four surface conditions were compared using repeated measures ANOVA. A significant increase was found in the weight support distribution for the hemiplegic side in flexing and extending sessions in condition 2 compared to the other conditions (p<.05). A statistically significant decrease in significant decrease in asymmetrical weight bearing in flexing and extending sessions was observed for condition 2 compared to the other conditions (p<.05). A similar significant decrease was found in differences in muscular activity for both lower limbs in condition 2 (p<.05). The muscular activity of the hemiplegic side, based on the support surface for each muscle showed a significantly greater increase in condition 2 (p<.05). An unstable platform for the non-hemiplegic side and a stable platform for the hemiplegic side therefore increased symmetry in terms of the weight support distribution rate and muscle activity of lower limbs in hemiplegic patients. The problem of postural control due to asymmetry in hemiplegic patients should be further studied with the aim of developing continuous effects of functional training based on the type and position of the support surfaces and functional improvement.

• The Journal of Korean Physical Therapy
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• v.23 no.4
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• pp.29-36
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• 2011

Purpose: The purpose of this study was to evaluate the effect of 6-week sensorimotoor training on balance ability and lower limb muscle activation during gait in older adults. Methods: Twenty-four community-dwelling older adults between 65 and 90 years of age participated in this study. In the older adults of the experimental group (n=12), the sensorimotor training program was performed bare feet. General exercise was performed in the control group (n=12). Then, both groups exercised three times a week for forty minutes over a 6-week period. Balance ability was evaluated by One leg stand (OLS) test for determining the static balance and Timed Up & Go (TUG) test for determining the dynamic balance. In addition, muscle activation of the dominant lower limb tibialis anterior and gastrocnemius medialis muscles were measured by surface EMG to evaluate muscle activation during gait. Results: A significant improvement was seen in the one leg standing (OLS) time after exercise in both the sensorimotor training (SMT) group and general exercise (GE) group (p<0.05) and the change in the SMT group was greater than that in the GE group (p<0.05). A significant reduction was seen in the Timed Up & Go (TUG) test time after exercise in both the SMT group and GE group (p<0.05). Also, a significant increase was seen in muscle activation of tibialis anterior muscle after exercise in the SMT group (p<0.05), but no such significant increase was seen in the GE group (p>0.05). Conclusion: These results suggest that sensorimotor training improves the balance in older adults and has a more positive effect on muscular strength and gait. Sensorimotor training provided a variance of training environment and COG exercise of the body is thought to be a more effective exercise program that improves balance and gait ability in older adults.

• Korean Journal of Applied Biomechanics
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• v.26 no.1
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• pp.11-20
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• 2016

Objective: This study aimed to compare biomechanical data between elite and beginner cyclists during cycle pedaling by performing a comparative analysis and to provide quantitative data for both pedaling performance enhancement and injury prevention. Methods: The subjects of this study included 5 elite cyclists (age: $18{\pm}0years$, body mass: $64.8{\pm}9.52kg$, height: $173.0{\pm}4.80cm$) and 5 amateur cyclists (age: $20{\pm}0years$, mass: $66.6{\pm}2.36kg$, height: $175.6{\pm}1.95cm$). The subjects pedaled on a stationary bicycle mounted on rollers of the same gear (front: 50 T and rear: 17 T = 2.94) and cadence of 90. The saddle height was adjusted to fit the body of each subject, and all the subjects wore shoes with cleats. In order to obtain kinematic data, 4 cameras (GR-HD1KR, JVC, Japan) were installed and set at 60 frames/sec. An electromyography (EMG) system (Telemyo 2400T, Noraxon, USA) was used to measure muscle activation. Eight sets of data from both the left and right lower extremities were obtained from 4 muscles (vastus medialis oblique [VMO], vastus lateralis oblique [VLO], and semitendinosus [Semitend], and lateral gastrocnemius [Gastro]) bilaterally by using a sampling frequency of 1,500 Hz. Five sets of events ($0^{\circ}$, $90^{\circ}$, $180^{\circ}$, $270^{\circ}$, and $360^{\circ}$) and 4 phases (P1, P2, P3, and P4) were set up for the data analysis. Imaging data were analyzed for kinematic factors by using the Kwon3D XP computer software (Visol, Korea). MyoResearch XP Master Edition (Noraxon) was used for filtering and processing EMG signals. Results: The angular velocity at $360^{\circ}$ from the feet was higher in the amateur cyclists, but accelerations at $90^{\circ}$ and $180^{\circ}$ were higher in the elite cyclists. The amateur cyclists had greater joint angles at $270^{\circ}$ from the ankle and wider knee joint distance at $0^{\circ}$, $180^{\circ}$, and $360^{\circ}$ than the elite cyclists. The EMG measurements showed significant differences between P2 and P4 from both the right VLO and Semitend. Conclusion: This study showed that lower body movements appeared to be different according to the level of cycle pedaling experience. This finding may be used to improve pedaling performance and prevent injuries among cyclists.

• Korean Journal of Veterinary Research
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• v.16 no.2
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• pp.205-219
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• 1976

한국재래산양(韓國在來山羊) 12마리의 후지근(後肢筋)을 절개하여 관찰하였던 바 다음과 같은 결과를 얻었다. 1. 한국재래산양(韓國在來山羊)의 후지근(後肢筋)에서는 다음과 같은 근(筋)들을 관찰할 수 있었다 : 소요근(小腰筋) M. psoas minor, 대요근(大腰筋) M. psoas major, 장골근(腸骨筋) M. iliacus, 요방형근(腰方形筋) M. quadratus lumborum, 대퇴근막장근(大腿筋膜張筋) M. tensor fasciae lata, 중둔근(中臀筋) M. gluteus medius, 심둔근(深臀筋) M. gluteus profundus, 둔이두근(臀二頭筋) M. gluteobiceps, 반건양근(半腱樣筋) M. semitendinosus, 반막양근(半膜樣筋) M. semimbranosus, 봉공근(縫工筋) M. sartorius, 박근(薄筋) M. gracilis, 치골근(恥骨筋) M. pectineus, 내전근(內轉筋) M. adductor, 대퇴방형근(大腿方形筋) M. quadratus femoris, 외폐쇄근(外閉鎖筋) M. obturatorius externus, 내폐쇄근(內閉鎖筋) M. obturatorius internus, 쌍자근(雙子筋) M. gemelli, 대퇴사두근(大腿四頭筋) M. quadriceps femoris, 제삼비골근 M. fibularis tertius, 내측지신근(內側趾伸筋) M. extensor digitorum medialis, 장지신근(長趾伸筋) M. extensor digitorum longus, 전경골근(前脛骨筋) M. tibialis cranialis, 장비골근 M. fibularis longes, 외측지신근(外側趾伸筋) M. extensor digitorum lateralis, 비복근 M. gastrocnemius, 가제미근(筋) M. soleus, 천지굴근(淺趾屈筋) M. flexor digitorum superficialis, 심지굴근(深趾屈筋) M. flexor digitorum profundus, 슬와근(膝窩筋) M. popliteus, 골간근(骨間筋) M. interosseus medius. 2. 천둔근(淺臀筋)의 전부(前部)는 대퇴근막장근(大腿筋膜張筋)과 융합된 것 같고, 후부(後部)는 대퇴이두근(大腿二頭筋)과 융합된 것 같다. 그러나 천둔근(淺臀筋)의 후부(後部)와 대퇴이두근(大腿二頭筋)이 결합된 것으로 생각되는 부분에는 완전융합이 일어나지 않고 천둔근(淺臀筋)을 구분(區分)할 수 있을 정도로 표면으로 2근(筋)을 분리(分離)할 수 있었다. 3. 외측지신근(外側趾伸筋)과 내측지신근(內側趾伸筋)의 건(腱)은 부전골의 원위(遠位) 1/3부(部)에서 서로 건막성(腱膜性)띠에 의하여 서로 연결 되었는데, 이 건막성(腱膜性) 띠는 건섬유(腱纖維)의 방향(方向)으로 보아 외측지신근(外側趾伸筋)의 건(腱)에서 분리(分離)되어 나온 한 가지 (branch)가 내측지신근(內側趾伸筋)의 건(腱)으로 이행되고 있었다. 4, 양(羊)에서 볼 수 있는 이상근(梨狀筋) M. piriformis과 장모지신근(長母趾伸筋) M. extensor hallucis longus은 나타나지 않았다.

• Physical Therapy Korea
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• v.15 no.1
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• pp.38-45
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• 2008

This study investigated gait characteristics, kinematics, and kinetics in the lower extremities between two different shoe conditions (high heeled shoes (7 cm), and high heeled shoes with a total contact insert (TCI)) after lower extremity muscle fatigue. Although TCI shave been applied in high heeled shoes to increase comfort and to decrease foot pressure, no study has attempted to identify the effects of TCI in fatigue conditions. The purpose of this study was to determine the effects of walking in high heeled shoes with TCI after lower extremity muscle fatigue was induced. This study was carried out in a motion analysis laboratory at Hanseo University. A volunteer sample of 14 healthy female subjects participated. All in fatigue conditions, the subjects were divided into two groups. The muscle fatigue was induced by 40 voluntary dorsi- and plantar-flexion exercises and 40 heel-rise exercises of the dominant foot. Surface electromyography was used to confirm the localized muscle fatigue using power spectral analysis of three muscles (tibialis anterior, gastrocnemius medialis and lateralis). The results were as follows: (1) In muscle fatigue conditions, the use of TCI decreased the peak flexion angle of the hip joint significantly in the early stance phase (p<.05) and increased the peak hip flexion moment in the terminal stance phase (p<.05). (2) In muscle fatigue conditions, the application of TCI also increased peak hip power generation in the early stance phase and peak hip power absorption in the terminal stance phase (p<.05). (3) In muscle fatigue conditions, the use of TCI reduced the impact force significantly and increased the secondary peak vertical GRF. These findings suggest that the TCI may provide beneficial effects when muscle fatigue occurs for a high heeled shoe gait. Future research employing the patient population and various types of TCI materials are required to clarify the effects of TCI.

• PNF and Movement
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• v.4 no.1
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• pp.45-50
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• 2006

Purpose : This study shows the movements of the ankle and the foot in walking stages, and helps to diagnose and treat the problems of the ankle and the foot. The foot in human is a mean of the transportation, body support, and shock absorber. However, the slightest changes in the anatomical position can cause a significant increase of the stress and force in the ankle and the foot. The regular compressive force in the ankle of the normal person is generated by the contraction of the gastrocnemius and popliteus muscles, and transmitted to the achilles tendon. The plantar flexion about 10 degrees occurs immediately after the heel strike, getting ready for the weight acceptance. The shear force about 80 % of the body weight is generated immediately after the heel off of the mid stance phase. In those who have a problem in the ankle, the compression force at the ankle decreased to 1/3 of the body weight, and the shear force decreased, and the compressive force was reached at their maximum level earlier than the normal people. Conclusion : Analysis of the movements at the ankle and the foot in walking phase can make the effort to diagnose and treat the ankle and foot with the problems. However, the further study is necessary.

• Korean Journal of Acupuncture
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• v.20 no.4
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• pp.65-75
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• 2003

This study was carried to identify the component of Spleen Meridian Muscle in human, dividing into outer, middle, and inner part. Lower extremity and trunk were opened widely to demonstrate muscles, nerve, blood vessels and the others, displaying the inner structure of Spleen Meridian Muscle. We obtained the results as follows; 1. Spleen Meridian Muscle is composed of the muscle, nerve and blood vessels. 2. In human anatomy, it is present the difference between a term of nerve or blood vessels which control the muscle of Meridian Muscle and those which pass near by Meridian Muscle. 3. The inner composition of meridian muscle in human arm is as follows ; 1) Muscle; ext. hallucis longus tend., flex. hallucis longus tend.(Sp-1), abd. hallucis tend., flex. hallucis brevis tend., flex. hallucis longus tend.(Sp-2, 3), ant. tibial m. tend., abd. hallucis, flex. hallucis longus tend.(Sp-4), flex. retinaculum, ant. tibiotalar lig.(Sp-5), flex. digitorum longus m., tibialis post. m.(Sp-6), soleus m., flex. digitorum longus m., tibialis post. m.(Sp-7, 8), gastrocnemius m., soleus m.(Sp-9), vastus medialis m.(Sp-10), sartorius m., vastus medialis m., add. longus m.(Sp-11), inguinal lig., iliopsoas m.(Sp-12), ext. abdominal oblique m. aponeurosis, int. abd. ob. m., transversus abd. m.(Sp-13, 14, 15, 16), ant. serratus m., intercostalis m.(Sp-17), pectoralis major m., pectoralis minor m., intercostalis m.(Sp-18, 19, 20), ant. serratus m., intercostalis m.(Sp-21) 2) Nerve; deep peroneal n. br.(Sp-1), med. plantar br. of post. tibial n.(Sp-2, 3, 4), saphenous n., deep peroneal n. br.(Sp-5), sural cutan. n., tibial. n.(Sp-6, 7, 8), tibial. n.(Sp-9), saphenous br. of femoral n.(Sp-10, 11), femoral n.(Sp-12), subcostal n. cut. br., iliohypogastric n., genitofemoral. n.(Sp-13), 11th. intercostal n. and its cut. br.(Sp-14), 10th. intercostal n. and its cut. br.(Sp-15), long thoracic n. br., 8th. intercostal n. and its cut. br.(Sp-16), long thoracic n. br., 5th. intercostal n. and its cut. br.(Sp-17), long thoracic n. br., 4th. intercostal n. and its cut. br.(Sp-18), long thoracic n. br., 3th. intercostal n. and its cut. br.(Sp-19), long thoracic n. br., 2th. intercostal n. and its cut. br.(Sp-20), long thoracic n. br., 6th. intercostal n. and its cut. br.(Sp-21) 3) Blood vessels; digital a. br. of dorsalis pedis a., post. tibial a. br.(Sp-1), med. plantar br. of post. tibial a.(Sp-2, 3, 4), saphenous vein, Ant. Med. malleolar a.(Sp-5), small saphenous v. br., post. tibial a.(Sp-6, 7), small saphenous v. br., post. tibial a., peroneal a.(Sp-8), post. tibial a.(Sp-9), long saphenose v. br., saphenous br. of femoral a.(Sp-10), deep femoral a. br.(Sp-11), femoral a.(Sp-12), supf. thoracoepigastric v., musculophrenic a.(Sp-16), thoracoepigastric v., lat. thoracic a. and v., 5th epigastric v., deep circumflex iliac a.(Sp-13, 14), supf. epigastric v., subcostal a., lumbar a.(Sp-15), intercostal a. v.(Sp-17), lat. thoracic a. and v., 4th intercostal a. v.(Sp-18), lat. thoracic a. and v., 3th intercostal a. v., axillary v. br.(Sp-19), lat. thoracic a. and v., 2th intercostal a. v., axillary v. br.(Sp-20), thoracoepigastric v., subscapular a. br., 6th intercostal a. v.(Sp-21)