Volume 48 Number 2, 2011
Pages 135 — 146
Abstract — Electromechanically assisted gait training is a promising task-oriented approach for gait restoration, especially for people with subacute stroke. However, few guidelines are available for selecting the parameter values of the electromechanical Gait Trainer (GT) (Reha-Stim; Berlin, Germany) and none is tailored to a patient's motor capacity. We assessed 342 GT sessions performed by 20 people with stroke who were stratified by Functional Ambulatory Category. In the first GT session of all patients, the body-weight support (BWS) required was higher than that reported in the literature. In further sessions, we noted a slow reduction of BWS and a fast increment of walking speed for the most-affected patients. Inverse trends were observed for the less-affected patients. In all the patients, the heart rate increment was about 20 beats per minute, even for sessions in which the number of strides performed was up to 500. In addition, the effective BWS measured during GT sessions was different from that initially selected by the physiotherapist. This difference depended mainly on the position of the GT platforms during selection. Finally, harness acceleration in the anteroposterior direction proved to be higher in patients with stroke than in nondisabled subjects. Our findings are an initial step toward scientifically selecting parameters in electromechanically assisted gait training.
Key words: accelerometry, ambulation recovery, assessment, body-weight support, gait training, heart rate, parameter selection, rehabilitation, stroke, walking speed.
Over the last decade, devices for electromechanically assisted gait training have been developed that allow nonambulatory patients to perform intensive, task-oriented exercise [1-2]. The effectiveness of these devices has been investigated in patients with subacute [3-5] and chronic [6-7] stroke, but their overall efficacy has been questioned [8-9]. The absence of a general agreement may be due to differences among patients enrolled in these studies, as well as the lack of a unified approach to integrating these devices into rehabilitation programs . The effectiveness of these devices may therefore depend heavily on the ability of the rehabilitation team to most effectively tailor the selection of their parameters to each patient.
Information about the criteria used to select parameters for these devices, including the reasons for choosing the amount of body-weight support (BWS) or imposed walking speeds (WSs), is not usually stated in the literature or user manuals. Currently, therefore, training protocols vary widely among clinical trials. Low percentages of BWS and fast WSs may activate the relevant weight-bearing muscles and improve locomotor efficiency [11-12] but can overstrain patients . Despite every physi-otherapist's concern for selecting the maximum parameter values that each patient can achieve without discomfort, clear guidelines and/or scientific analyses of these values are still lacking, as well as knowledge of their interrelationships and their effects on over-ground walking performance. This absence of guidelines may explain the lack of general agreement about the effectiveness of robotic devices for gait recovery [10,13], the absence of a well-defined optimal training plan for each level of patients' walking dependency , and the skepticism sometimes expressed by physicians and physiotherapists toward the use of robotic aids in rehabilitation . Deeper knowledge may increase awareness of the potential of electromechanical-assisted walking training in rehabilitation.
The most common electromechanically assisted gait devices for gait restoration are a treadmill with BWS , the Lokomat?? (Hocoma, AG; Volketswil, Switzerland) , and the Gait Trainer?? (GT) (Reha-Stim; Berlin, Germany) . On treadmills, only the percentage of BWS and the WS can be selected. The Lokomat has many more options; the rehabilitation team can even decide the proper joint kinematics. The GT lies between these two extremes (Figure 1). It includes a system for BWS and a controller of endpoint feet trajectories. During a GT session, each of the patient's feet is fixed by straps to a plate moved by the GT engine, which simulates swing (40%) and stance (60%) gait phases, by means of a crank and rocker system that includes a planetary gear system [1-2]. The result is a gait-like movement, in which the values of the spatiotemporal parameters are selected by the physiotherapist and imposed on the patients by the device [1-2]. Joint kinetics and kinematics are not imposed but can be influenced by the selection of the values discussed earlier.
Figure 1. Click Image to Enlarge
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During the initial preparation phase, the physiotherapist (two physiotherapists are often required for the most severely affected patients) has to harness the patient and help him to rise on the GT platforms, previously placed in a proper position. Then the physiotherapist should select the following parameters: the needed BWS, the step length (SL), and the WS.
BWS is the essential ingredient, the conditio sine qua non, for nonambulatory patients to practice the exercises intensively and safely. BWS permits a greater number of steps within a training session than conventional therapy, in which body weight is manually supported by one or two physiotherapists and/or a walker [3,13]. The physi-otherapist initially selects the BWS value in a static posture (BWSs). However, a common standing posture with both lower limbs extended is impossible on the GT, because when one plate is down (simulating the stance phase) the other is up (simulating the swing phase). Furthermore, the effective BWS (BWSe) varies during the session, depending on the patient's capacity to sustain his/her own unsupported percentage of weight [5,17]. Despite these features, all previous studies on the GT have reported BWSs only, without describing the position at which it was selected. Moreover, these studies have tacitly assumed that BWSs is a reference value around which the BWSe falls during the GT session. However, whether this implicit assumption is true is still not proven.
Evidence is emerging that the prescription of certain parameters in treadmill training with BWS can affect treatment outcome in people with hemiparesis due to stroke. This evidence has motivated investigations of the scientific basis for the proper selection of the device parameters . In this study, we have retrospectively documented the selection of GT parameters based on clinical judgment during almost 400 sessions. We have also analyzed the relationships among selected values, measured quantities, and clinically observed a patient's locomotor capacity. This analysis is in accordance with similar previous investigations on the effects of BWS, WS, and support system stiffness in treadmill training . Our aim was to contribute to the development of a scientific rationale useful in the selection of GT parameters.
We used three different experimental protocols: (1) a retrospective study of 20 patients, each of whom was included in a training program of 20 GT sessions; (2) kinematics (acceleration) and kinetics (force) measured during 6 brief GT sessions performed by 8 nondisabled patients each, with BWS measured in 3 different initial positions; and (3) the same kinematic and kinetic parameters measured during GT sessions performed by 7 patients. The inclusion criteria for patients were hemiparesis in the subacute phase with significant gait deficit (Functional Ambulatory Category [FAC] score ≤3) due to first-ever stroke with lesion confirmed by neuroimaging. Exclusion criteria included the presence of subarachnoid hemorrhage, sequelae of previous cerebrovascular accidents and/or other chronic disabling pathologies, orthopedic injury that may impair locomotion, important neglect, or a high level of spasticity or cognitive impairment.
Particular attention was paid to BWS, WS, and harness accelerations, similar to the review by Chen and Patten of treadmill training . The selected WS (WSs) should be equal to the effective WS (WSe). However, the WS selector of the GT actually acts as a selector of step duration (Figure 1), which leads to the use of the following formula to evaluate the WSe: WSe = WSs × SL/0.48 (SL in meters) . This step cadence can range from 0 to 70 steps/minute, allowing for a maximum WSe of 2 km/h (0.56 m/s) achievable only with SL = 0.48 m. In this article, unless otherwise defined, WS indicates WSe, expressed in kilometers per hour as on the GT control panel, and the corresponding value in meters per second is also given in parentheses. Furthermore, by dividing the distance virtually covered during the session (nstrides × SL × 2, where nstrides = number of strides performed) by the session duration, we could calculate mean WS during the entire GT session (WSmean). This parameter, when compared with WSe, can be helpful in understanding the effects of transitory and rest phases.
We retrospectively analyzed parameter values recorded in GT sessions of 20 patients with subacute stroke (mean age ± standard deviation [SD]: 59 ± 17 years, 5 females). At admission, 18 patients had an FAC score = 0 and 2 had an FAC score = 1; their mean Rivermead Mobility Index was 1.8 ± 1.1. Their rehabilitation program consisted of two conventional physiotherapy sessions a day for 2 or 3 months. Starting about 1.5 months after the stroke event, one daily session was replaced by a GT session for 4 consecutive weeks. At the first GT session, seven patients (age: 63 ± 11 years) had an FAC score = 0 (no functional ambulation); seven (age: 68 ± 6 years) had an FAC score = 1 (requiring another person to support their body weight while walking); and six (age: 46 ± 22 years) had an FAC score ≥2 (4 with an FAC score = 2 [i.e., requiring slight manual contact], and 2 with an FAC score = 3 [i.e., requiring supervision during walking]). For each session, the WSs and BWSs were selected according to the patient's motor ability, as visually assessed by the physiotherapist. BWSs was selected with the two plate anterior borders aligned (see next section, "Protocol 2: Initial Position," for details). These values could be modified during the first part of the session if judged inappropriate. SL was selected primarily in accord-ance with the values usually achieved by patients with chronic stroke  and patient stature and was therefore quite fixed among patients and sessions (SL = 39 ± 2 cm). Thus, we did not analyze it further. We should note that the choice of an SL lower than the maximum possible (48 cm) implied a WSelower than the device's maximum because of the limit on step cadence mentioned earlier.
During the first GT session, BWSs was selected to be about 40 to 60 percent and WSs about 1.2 to 1.8 km/h, corresponding to a WSe of 1.0-1.5 km/h (0.28-0.42 m/s), according to each patient's capacity. The BWSs was reduced as soon as the patient could take his/her full weight, and the WSs was increased as soon as the patient could perform the task without overstraining and/or experiencing discomfort . The physiotherapist involved in the GT treatment prepared the patients, chose the parameters, provided verbal feedback to the patient during the GT session, and manually controlled the patients' paretic knee, if needed.
During each session, the physiotherapist recorded the following parameters: session duration (maximum: 20 min); the number of strides performed (clearly depending on session duration and WSe); heart rate (HR) increment (ΔHR = HRpost - HRpre, where ΔHR = HR increment, HRpost = HR after the session, and HRpre = HR before the session); its percentage relative to maximum safe increment of cardiovascular rate (c = ΔHR/(HRmax - HRpre) × 100, where c = percentage of maximum safe increment of cardiovascular rate and HRmax = 190 - age ); and the FAC score of the patient.
The BWSs and BWSe values were measured in static and training conditions, respectively, with the GT dynamometer (Figure 1), with a sampling frequency of about 3 Hz. BWSs was 20 percent of the body weight of each subject (corresponding to a vertical force of 161 ± 27 N), and it was measured in three different initial platform positions: position A, at maximum sagittal distance (0.48 cm); position B, with anterior borders 24 cm apart; and position C, with anterior borders aligned. The measure-ments were recorded twice with the left and right limb forward (positions A and B) and in the standing position (position C). Then, BWSe was recorded during 20 steps performed by eight nondisabled subjects (mean age: 34 ± 4 years; mean body mass: 82 ± 14 kg) in the middle of six brief GT sessions. For all eight subjects, WS was 2 km/h (0.56 m/s) and SL was 0.48 cm. At the same time, the accelerations of the apex of the patient's harness (the horizontal bar to which the harness clamps were fixed [Figure 1]) were measured with a triaxial accelerometer (Vibracting??, Sensorize s.r.l.; Rome, Italy) with a sampling frequency of 100 Hz. The root-mean-square (RMS) of acceleration measured in the anteroposterior (AP), laterolateral (LL), and craniocaudal (CC) directions was evaluated.
The BWSe and acceleration RMS were also recorded for seven patients with hemiplegia due to subacute stroke (mean age: 64 ± 7 years, mean body mass: 71 ± 12 kg) during an early GT session. For them, we recorded BWSs in position C with the nonparetic limb extended. We normalized the measured values to account for differences in WS and SL according to this formula: RMSn = RMS/WS2 × SL, where RMSn = normalized RMS . We compared these normalized values with the relevant values of nondisabled subjects recorded at position C. All participants could request that the sessions be stopped at any time so they could rest.
Mean ± SD was computed for each of the recorded parameters. We used repeated measures analyses of variance (ANOVAs) to assess the effects of session repetition (within factor) and the FAC score recorded at the first GT session (fixed factor, three levels: 0, 1, or ≥2) on BWSs, WSe, number of strides performed, and ΔHR (dependent variables). Because not all patients performed 20 GT sessions, we conducted this ANOVA on the first 15 GT sessions, which 18 of the 20 patients completed. These ANOVA calculations were followed by post hoc analyses with the Tukey test.
We used an exponential function (y = a + b??es/t, where y = the function approximating the investigated parameter at which the fit is applied; the parameters of the exponential fit are a = constant, b = coefficient, e = Eulerian number, ?? = constant time, and s = the number of the GT session) to fit the parameter values recorded during progressive GT session. We used coefficient of determination R2 to assess the goodness of this fit. We computed Pearson (R) and Spearman (r) coefficients to evaluate correlations among recorded values for continuous and ordinal measurements, respectively.
We performed linear regression to assess the correlation between BWSe and the position at which BWSs was selected in protocol 2. Finally, in protocol 3, we used t-tests to compare patients and nondisabled subjects in both mean BWSe and acceleration RMS.
The first GT session was performed 48 ± 18 days after the stroke event. The 20 patients performed 342 of the 400 planned GT sessions (85%), with 17 ± 3 sessions per patient. Only 6 subjects performed all 20 prescribed sessions. In accordance with the defined protocol (see "Methods" section), at the first session the mean value of BWSs was 52.6 ± 15.7 percent of the patient's body weight and the mean WSs was 1.3 ± 0.2 km/h (0.35 ± 0.05 m/s).
Repeated measures ANOVA (performed on the first 15 GT sessions) showed that the number of the session significantly affected BWSs (F2,14 = 45.65, p < 0.001), WSe (F2,14 = 17.15, p < 0.001), and number of strides performed (F2,14 = 12.95, p = 0.001), but not ΔHR (F2,14 = 0.74, p = 0.732). The FAC score recorded at the first GT session significantly affected BWSs (F2,14 = 10.32, p = 0.002), but not WSe (F2,14 = 0.348, p = 0.712), number of strides performed (F2,14 = 0.53, p = 0.600), or ΔHR (F2,14 = 0.908, p = 0.424). Post hoc analyses showed significant differences in BWSs for patients with an FAC score = 0 compared with patients with an FAC score = 1 and ≥2 ( p ≤0.005 each), but not between the latter two groups (p = 0.99).
Figure 2 shows the progressive reduction of BWSs and the progressive increment of WSe averaged among patients grouped by FAC score recorded at the first GT session. Because not all 400 sessions were performed, the values for the last sessions were not computed for all patients. All parameters except ΔHR were well fitted by an exponential function (mean R2 = 0.83 ± 0.16).
Figure 2. Click Image to Enlarge
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Patients with an initial FAC score = 0 showed low t values for number of strides performed (τ = 1.6 sessions), WS (τ = 2), and FAC score (τ = 8.6), indicating quick variations in these parameters. However, these patients also showed the slowest BWSs decrement (τ = 67.5), whereas a quick decrement of BWSs (corresponding to lower values of τ) was recorded for patients with an FAC score = 1 (τ = 10.3) or ≥2 (τ = 6.6), despite the similar BWSs selected for all patients at the first GT session.
For patients with an FAC score ≥2 at the first GT session, the increment of performed strides (τ = 14.4 sessions), WS (τ = 16.8), and overall FAC score (τ = 73.1) were slow and quite linear. This slow, linear increment occurred despite the patients' fast decrement of BWSs and their capacity to complete the 20-minute sessions, even at the second session. Furthermore, the asymptote of the exponential fit for their WS was 2.2 km/h (0.61 m/s), over the limit of the selectable WS, which was 2 km/h (0.56 m/s) for SL = 0.48 cm and 1.7 km/h (0.47 m/s) for SL = 0.40 cm.
The WSmean computed over all 342 sessions was 18 percent less than WSe among all patients. Moreover, these two parameters were greatly but not perfectly related (R = 0.87).
The ΔHR did not vary greatly among sessions, with a mean of 16.8 ± 15.7 beats per minute (bpm) (higher for patients with higher initial FAC scores [Figure 2]). The mean c was 18.3 ± 8.0 percent. The ΔHR was not significantly related to BWSs (R = -0.04, p = 0.42), WSe (R = 0.07, p = 0.22), the number of the session (R = -0.02, p = 0.78), or the FAC score (r = 0.06, p = 0.27); however, it was slightly but significantly correlated only with the number of strides performed (R = 0.14, p = 0.01).
At dismissal, these 20 patients had a mean FAC score of 3.9 ± 1.0 and a mean Rivermead Mobility Index of 8.8 ± 3.5, and they were able to walk a mean 161 ± 83 m in 6 min. This performance corresponds to a WSmean of 1.61 ± 0.83 km/h (0.45 ± 0.23 m/s). These values were similar for all three subgroups of patients with an FAC score of 0, 1, and ≥2 recorded at the first GT session. Some correlations were found between the values of selected parameters in the last GT session and clinical scores at dismissal. The Rivermead Mobility Index related to the last WSe (r = 0.54, p = 0.02) and BWSs (r = -0.45, p = 0.048), whereas the FAC score related only to BWSs (r = -0.55, p = 0.01). The distance covered in 6 min, even if related to the Rivermead Mobility Index (r = 0.60, p = 0.01), was poorly and not significantly correlated with the parameter values recorded at the last GT session: BWSs (R = -0.32, p = 0.21), WSe (R = 0.27, p = 0.29), and number of strides performed (R = 0.19, p = 0.46).
The mean values of the differences between BWSe and BWSs measured during 10 strides starting from three different initial positions are shown in Figure 3. The linear relationship between this difference and the initial plate distance can identify an optimal position for plates. This optimal position is with their anterior borders positioned 12 cm apart, at which mean BWSe roughly coincides with BWSs. In contrast, position C, probably the easiest to reproduce, implied an overestimation of BWSe of about 4 percent of each subject's weight.
Figure 3. Click Image to Enlarge
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The representative results of a patient with left hemiparesis are shown in Figure 4. An asymmetric pattern is evident: all the minima of BWSe corresponded to extension of the nonparetic limb (i.e., its stance phase), whereas the higher maxima were close to the beginning of the paretic step, i.e., when the paretic limb accepts the load. Similar patterns were observed for acceleration, with higher peak-to-peak values for acceleration in the LL direction (aLL) and acceleration in the AP direction (aAP) during the step of the paretic leg (dark gray bands in Figure 4).
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The mean values of the selected parameters measured for the seven patients were BWSs = 31 ± 11 percent, WSe = 1.5 ± 0.3 km/h (0.42 ± 0.08 m/s), SL = 0.38 ± 0.05 m, and BWSe = 27 ± 16 percent. Despite the high variability in patient data, the mean difference between BWSe and BWSs, -4 percent, did not differ from that of nondisabled subjects (p = 0.94). Although the normalized acceleration RMS was higher in patients than in nondisabled subjects (Figure 5), this difference was significant only in the AP direction (p = 0.03), not in the LL (p = 0.23) and CC (p = 0.06) directions.
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This study provides a systematic documentation of selectable GT parameter values, measured parameters, and their relationships. Similar to a previous study on the selection of parameters for treadmill training , this study on the GT, a device used for electromechanically assisted gait training, pays particular attention to WS, harness oscillations, and BWS. Moreover, it introduces and quantifies the difference between selected and effective parameter values, which is usually omitted in GT studies.
The results obtained for FAC score agreed with previously reported results on the effectiveness of robotic devices for gait recovery . We progressively reduced BWSs in successive GT sessions: slowly (high value of τ) for the most-affected patients (initial FAC score = 0), and quickly for the less-affected patients (FAC score ≥2), despite similar values recorded at the first GT session among all patients. Notably, the BWSs selected in the first GT session was about 45 to 60 percent of body weight; that is higher than the 30 percent previously described . The GT Handbook suggested a maximum BWS of 35 percent for nonambulatory patients with hemiparesis and a maximum of 10 percent in patients walking with aid, including support . Furthermore, clinical studies have recommended BWS limits of 30 percent on the treadmill  and 40 percent on the Lokomat??  for maintaining the activity of antigravitational muscles. In contrast, a review on treadmill parameter selection stated that adequate support was 35 to 50 percent . Ivanenko et al. have shown that lower-limb kinematics can be accurately controlled over a wide range of BWS and WS. Despite obvious changes in limb kinetics recorded for very high BWS, shown by recorded reaction forces and muscle activity, the authors stated that a high level of BWS may help severely affected patients with spinal cord injuries . Our results suggest that this approach can be extended to patients with subacute stroke. In fact, the high BWS values observed in our study allowed the patients to begin performing task-oriented, intensive exercises without joint overloading .
These high BWSs values observed during the first GT session in all patients could be left to the discretion of physiotherapists in the first training sessions. The value probably depends also on a patient's need for a familiarization period with the GT task that induces gait-like movements, simulating stance and swing phases . For the patients with an FAC score ≥1, about five GT sessions were needed before recommended BWS levels were assumed (about 30%). Conversely, we recorded a slow reduction of BWSs and a fast increment of WSe for the most-affected patients (FAC score = 0), which presumably indicates physiotherapists' preference for intensive training on kinematics (WS and number of strides performed) more than kinetics (BWSs). Our results showed that this preference resulted in patients performing training under safe cardiovascular conditions.
Protocol 2 showed the effects of different positions of measuring BWSs on BWSe. Although the position at which the anterior borders of the plates are aligned resulted in an overestimation of BWSe, that position was the easiest to reproduce during the GT sessions. Furthermore, this position allows the patient to extend one limb, the less-affected limb, to support his/her body weight. During the GT session, if the BWSe is >4 percent lower than the BWSs measured in the same position, then the patient's motor ability may have been underestimated. Conversely, if BWSe is consistently higher than BWSs, the patient is not actively working and one should consider the possibility of a BWSs increment.
In protocol 3, when we further analyzed patients' performances, we found that BWSe and body accelerations varied between the two limb steps. This asymmetric pattern was due to the different capacities of the paretic and nonparetic limbs to support body weight. For this reason, continuous monitoring by the physiotherapist of BWSe during the GT session can reveal information about patients' compliance with exercise. Overload may cause hyperflexion, hyperextension, and/or a varus knee.
Higher accelerations were observed for patients with stroke than for nondisabled subjects; this was particularly evident in the AP direction, probably because this direction is the less mechanically constrained. In fact, vertical movements are controlled by a vertical rope supporting the patient's body weight, whereas the lateral chains partially drive the LL movements (Figure 1). These results indicate that GT can roughly assist in controlling patient oscillations during therapeutic sessions.
We observed two important results related to WS. First, for less-affected patients, the WS limit of 2 km/h (0.55 m/s) may be too low. A recent study based on accelerometric measurement has also shown that walking at low speed can provide altered proprioceptive inputs . Second, we found that WSmean was about 20 percent lower than WSe, indicating that transitory and rest phases are not negligible and should be considered when the WSe for the next session is selected.
The number of strides performed by our patients during the 20 min GT session was similar to that previously reported by Pohl et al. (mean 425 strides during the first 2 weeks of therapy and 538 during the following 2 weeks) . This number is higher than that reported in a previous study on the number of strides performed during over-ground walking by patients manually supported by physiotherapists (about 100 strides) . Four hundred strides, with a mean SL of 0.39 m (i.e., stride length of 0.78 m) corresponds to a covered distance of 312 m performed by all our patients in <20 min. So, the WSmean during a GT session was about 0.94 km/h, with peaks of WSe of about 1.6 km/h. Similar mean velocity (0.84 km/h) was reported by Mehrholz et al. during the 6-minute walk test (6MWT) for the less-affected patients only (FAC score = 2.0 ± 1.5) . Conversely, the WSmean achieved during GT training by our patients was much higher than the over-ground velocities recorded in the most-affected patients in the Mehrholz et al. study (0.16 km/h for patients with an FAC score = 0.4 ± 0.7 and 0.51 km/h for an FAC score = 1.2 ± 1.3) . At dismissal, our patients performed the 6MWT with a WSmean similar to the maximum achieved on the GT (about 1.6 km/h).
The patient's locomotor abilities at dismissal were found to be only partially related to the BWSs and WSe recorded in the last GT session. This limited relationship was probably due to all the patients' GT parameter values converging to the ideal values at the end of the GT training (BWSs = 0%, WSe = 2 km/h, number of strides performed = 700 = 35 strides/min in 20 min).
Moreover, by measuring the ΔHR, we noticed that the patients performed all these steps under safe cardi-ovascular conditions. In fact, the ΔHR was about 20 bpm and poorly correlated with number of strides performed.
In light of these results, one could conceivably hypothesize that the limit on the selectable WS (due to the limit on SL) could restrain the functional walking patterns in the less-affected patients. This limit of the machine, therefore, could contrast with the physiotherapist's choice of an intensive kinematic training. For these patients, the GT can be helpful to guarantee safe conditions in the first part of their gait-oriented rehabilitative program. But then, the over-ground walking training is presumably more ecological and appropriate because it allows a more functional gait.
The main limitation of this study is the retrospective design of protocol 1. And, in fact, a rigorous analysis of the relationship of patients' over-ground walking perform-ance with the values of selected GT parameters is lacking in this study and should be investigated in further studies. Another limit is the small sample size of protocols 2 and 3. Future clinical trials should be specifically designed to provide guidance on which parameters to select in specific clinical situations. Also, they should include control groups receiving only conventional therapy. Despite the interesting results of this study, further investigations would be required to highlight the effects of parameter selection on joint kinematics. Furthermore, other parameters should be considered, including SL, physiotherapist manual assistance, handrail hold, and frequency of GT sessions per week.
Our results provide a rational framework for selecting GT parameter values, although additional studies are needed. These studies could improve the effectiveness of electromechanically assisted gait training devices based on effective choices of their kinematic and kinetic parameters. The main clinical findings of this study are (1) early, safe, and kinematically intensive training can require the use of high BWS, i.e., a low kinetic demand; (2) for the less-affected patients, intensive training can be restrained by the limit of 2 km/h for the GT WS, implying the need for another form of intervention; (3) BWSs should be selected with the two plates aligned; and (4) BWSe and the width of patients' sways during the GT session should be monitored and the initially selected parameters should be changed where necessary.
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Last Reviewed or Updated Thursday, February 10, 2011 3:30 PM