Because falls among the elderly can cause serious injury leading to a bedridden state, methods to maintain motor function in the elderly and prevent falls are important. Among falls by the elderly are tripping falls, in which the forefoot gets caught on the floor to cause the fall. Minimum foot clearance (MFC), the smallest distance between the floor and the foot during the swing phase of gait, has been given attention as a cause of tripping falls, as elderly people at risk of falling have been reported to have low MFC. No research has been done, however, to examine what geriatric factors determine MFC. In this study, various measurements were taken on muscle strength, joint angles, and other characteristics as factors possibly influencing the height of MFC, a multiple regression analysis was performed with MFC as the dependent variable, and those factors with high degrees of influence were extracted. The results revealed that the height of MFC is highly influenced by strength of the hip flexors and angle of ankle dorsiflexion. The results of this study should be taken into consideration when having elderly people do fall prevention training.
Japan has already reached an aging of society, with attendant costs of social security ascending steeply [
Ways to suppress medical costs of the elderly have thus become a matter of interest. Among the various illnesses involved, injury from falls can be preventable and reports have come out on effectiveness of prevention efforts [
Many factors contribute to the risk of falling as one ages, such as deterioration of the motor apparatus, dizziness or other symptoms due to poor function of sensory receptors, effects of medications, and lack of sleep [
Fractures reportedly occur in 17.6% of falls by the elderly, caused by changes in gait due to aging [
To lower the incidence of falls in the elderly, a number of exercises have been reported [
Knowing which variables strongly affect MFC would be promising in developing well focused exercise programs to prevent tripping falls by elderly people.
The purpose of this study was to kinesiologically clarify the strength factors and joint angle factors that influence MFC.
Fifty-four community-dwelling elderly people answered our call for participation. Participants were to sign the agreement.
None of them had problems with cognitive function or had undergone surgery in the lower extremities, so they were regarded as healthy (
The present study was conducted after receiving the approval of the Tohoku Fukushi University research ethics committee (approval no.: RS1307124).
Movements of the right leg during gait were measured with a three-dimensional movement data capture system at a sampling rate of 100 Hz. The collected data were imported into a movement analysis software system and gait cycles were determined from identifying instances of heel contact and toe off. Gait data and MFC were then extracted from this information.
The walkway for analysis was 11 m long, with the first 4 m used for acceleration, the next 4 m used for actual measurement, and the final 3 m for deceleration. The participants walked with socks on, practicing walking on the walkway a few times before being requested to walk at usual speed, which they did three times for data collection.
Reflective markers 25 mm in diameter were applied to 27 locations: top of the head, forehead, occiput, both shoulders, both elbows, both wrists, both anterior superior iliac spines, the sacrum, both greater trochanters, both knees, both lateral malleoli, the metatarsophalangeal joints of both second metatarsals, both heels, the back, both
| Variable | Participants (n = 54) |
|---|---|
| Female (%) | 78 |
| Age (years) | 69.61 (5.47) |
| Height (cm) | 156.59 (7.80) |
| Weight (kg) | 63.86 (10.98) |
| Body mass index (BMI) | 25.93 (3.20) |
| Motor fitness scale (MFS) | 11.86 (2.32) |
Values are mean (standard deviation).
femora, and both lower legs.
In the gait cycle, based on right leg movement, initial contact was the lowest point of the heel marker at the end of swing phase and pre-swing was the point when the marker over the dorsum of the second metatarsal just began to ascend after reaching its lowest point at the end of stance phase. Data were extracted for the left leg in the same manner. Four strides taken during gait on the platform were used as gait data.
All measurements of range of motion were performed by one physical therapist, who had over 30 years of clinical experience. With the parts to be measured exposed, the participant lay supine on a bed while knee extension and ankle dorsiflexion were measured with a goniometer. Considering the effect of two-joint muscles, two different measurements were made for range of ankle dorsiflexion, one with the knee extended and the other with the knee flexed [
At the beginning, with the participant in a relaxed standing position, the height from the floor of the reflective marker on the dorsum of the right metatarsophalangeal joint was measured. Then, after the gait data were collected, the height from the floor of the reflective marker on the dorsum of the right metatarsophalangeal joint during relaxed standing was subtracted from the height of the same marker seen from the sagittal view during right swing phase, and MFC was determined from that.
With a force sensor, strength was measured for hip flexion, knee flexion and extension, and ankle dorsiflexion. Data from the force sensor were obtained from an analysis apparatus via an amplifier. The sampling rate was 1 KHz.
The force sensor was affixed to a metal folding chair with wire, and then connected via a cuff to the body part to be measured. The cuff and wiring were adjusted so that strength could be measured midway between the extremes of the range of motion of the joint concerned. For each strength measurement, three repetitions were obtained of maximal effort over about five seconds. Each strength determination was preceded by a few practice trials. The values obtained were normalized by dividing by the participant’s body weight.
Hip flexion: The participant sat in the folding chair and a cuff was wrapped around the mid-thigh of the side to be measured. A cable attached to the cuff went vertically downward and was routed by a pulley at the bottom of the chair to the force sensor. The participant placed the contralateral foot on the floor and used that foot and the seat of the chair for support while flexing the ipsilateral hip. The participant was instructed not to let the trunk flex laterally or extend at that time.
Knee extension: With the participant sitting on the folding chair, the force sensor was bound to the frame of the chair with wire. With the knee at 90˚, a cuff was placed around the distal part of the lower leg on the side to be measured. A cable of adjusted length was run between the cuff and the force sensor. The contralateral leg was placed on the floor to provide firm support while the ipsilateral foot was slightly raised and ipsilateral knee extension was attempted. The participant was cautioned at that time about compensatory movements such as trunk lateral flexion.
Ankle Dorsiflexion: The participant sat on the floor with the legs out in front in a long sitting position. The chair with the force sensor was placed directly in front of the foot to be measured and fixed firmly there. A cuff connected to the force sensor was placed around the forefoot, contraction of the tibialis anterior was confirmed, and the participant dorsiflexed at the ankle. The participant was cautioned about compensatory movements such as trunk extension, and a cushion was placed beneath the popliteal fossa, putting the knee in slight flexion.
Bilateral differences in strength and range of motion were examined with paired t-tests.
Pearson’s product moment correlation coefficients were then calculated to ascertain relationships among the variables. After that, stepwise multiple regression was used with MFC as the dependent variable and the other variables as independent variables to find factors that influence MFC.
SPSS software was used for statistical analysis with the level of significance set at p = 0.05. The probabilities for stepwise insertion were set at F ≤ 0.05 and for removal at F ≤ 0.10.
MFC was found by looking for the valley between two peaks. Mean MFC was 24.67 mm ± 5.83 mm, occurring at 58.81% ± 7.03% of swing phase in the gait cycle (
No bilateral differences were seen in ROM, although knee extension was −1.48˚ ± 4.08˚ on the right and −1.76˚ ± 4.77˚ on the left (
The only bilateral difference seen in isometric strength was hip flexion being significantly stronger on the right than on the left (p = 0.01) (
| Variable | Participants (n = 54) |
|---|---|
| Velocity (m/min) | 133.94 (17.45) |
| Frequency (Hz) | 0.97 (0.08) |
| Cadence (/min) | 124.65 (11.19) |
| Stance phase (sec) | 0.60 (0.06) |
| Swing phase (sec) | 0.37 (0.03) |
| Double stance phase (sec) | 0.12 (0.02) |
| Stride (cm) | 130.16 (11.88) |
| Minimum foot clearance (mm) | 24.67 (5.83) |
Values are mean (standard deviation).
| Variable | Right | Left | p values* Right vs Left |
|---|---|---|---|
| Ankle dorsiflexion Knee bended (deg) | 20.28 (7.62) | 20.93 (7.60) | 0.31 |
| Ankle dorsiflexion Knee extended (deg) | 7.41 (5.81) | 7.60 (5.39) | 0.64 |
| Knee extension (deg) | −1.48 (4.08) | −1.76 (4.77) | 0.37 |
Values are mean (standard deviation)*paired t-test.
| Variable | Right | Left | p values* Right vs Left |
|---|---|---|---|
| Hip flexion (% KgBW) | 18.27 (5.88) | 17.06 (5.41) | <0.01 |
| Knee extension (% KgBW) | 31.33 (11.65) | 29.92 (11.60) | 0.13 |
| Knee flexion (% KgBW) | 17.12 (5.50) | 17.13 (5.70) | 0.98 |
| Ankle dorsiflexion (% KgBW) | 21.71 (6.13) | 21.68 (8.71) | 0.96 |
Values are mean (standard deviation)*paired t-test.