Effects of Walking Endurance Reduction on Gait Stability in Patients with Stroke

Abstract

Control of gait is usually altered following stroke, and it may be further compromised by overexertion and fatigue. This study aims to quantitatively assess patients' gait stability during six-minute walking, measuring upper body accelerations of twenty patients with stroke (64 ± 13 years old) and ten age-matched healthy subjects (63 ± 10 years old). Healthy subjects showed a steady gait in terms of speed and accelerations over the six minutes. Conversely, the patients unable to complete the test (n = 8) progressively reduced their walking speed (−22 ± 11%, confidence interval CI_95%: −13, −29%, P = 0.046). Patients able to complete the test (n = 12) did not vary their walking speed over time (P = 0.493). However, this ability was not supported by an adequate capacity to maintain their gait stability, as shown by a progressive increase of their upper body accelerations (+5 ± 11%, CI_95%: −1; +12%, P = 0.010). Walking endurance and gait stability should be both quantitatively assessed and carefully improved during the rehabilitation of patients with stroke.

1. Introduction

The recovery of walking ability is one of the most relevant functional targets after a cerebrovascular event, but this goal is generally obtained by only 50–60% of patients [1]. In particular, Paolucci and colleagues showed that at discharge from a rehabilitation hospital about 5% of patients with stroke were independent even in stair climbing and 9% were able to walk outside, 14% to walk inside, and 27% to walk with cane or other aid, while 45% remained in wheelchair [2].

Prolonged walking in living environment is even more challenging than short distances walked in hospital settings. Furthermore, overexertion can be detrimental for physical and mental conditions of people with stroke: for these patients, fatigue prevalence has been estimated to be up to 70% [3, 4]. Fatigue can be defined as a feeling of lack of energy and weariness following a period of exertion, and it is characterized by a decreased capacity of work and reduced efficiency to respond to stimuli [5]. All these factors put the individuals with stroke at great risk of falling during prolonged walking [6]. Despite that the effects of fatigue, induced by extended effortful activity, have been investigated in relationship to spatiotemporal gait parameters [7, 8] and oxygen consumption [5] in people with stroke, far too little attention has been paid to the relationship between walking endurance and gait stability.

Gait dynamic stability could be defined as the capacity to move the body segments in a coordinated fashion so that the body could be displaced with a proper speed (i.e., functional to the required task, such as crossing the road safely) minimizing upper body oscillations [9, 10]. So, gait stability can be suitably assessed by measuring upper body accelerations [9], in terms of their dispersion and smoothness of upper body walking patterns [10–12]. In fact, in an unstable gait, walking speed fluctuates, causing higher accelerations and hence inertial forces and perturbations that need to be controlled.

The aim of this study is to quantify the potential effects of fatigue, induced by effortful walking, on gait dynamic stability of patients with stroke. The hypothesis that we wanted to test was if gait stability is reduced during prolonged walking in people with subacute stroke. To achieve this goal, we have measured upper body accelerations during the six-minute walking test performed by ambulatory inpatients.

2. Material and Methods

2.1. Participants

Twenty patients with stroke and ten age-matched healthy subjects were enrolled in this study (see Table 1 reporting their demographic and clinical characteristics). The patients were tested the day before their dismissal from a rehabilitation hospital. Exclusion criteria were inability to walk, severe cognitive impairment, medical contraindications to exercise training, other chronic disabling pathologies (such as osteoarthritis and chronic inflammatory rheumatic diseases), orthopedic injuries, and hemispatial neglect. This study was approved by the Local Ethical Committee, and informed consent was obtained from each participant.

Table 1.

Demographic and clinical characteristics of participants. Mean ± standard deviation (95% confidence interval) or median (first and third quartiles) of demographic characteristics, clinical features and scale scores at the moment of the 6MWT. The fourth and the last columns report the P values obtained by t test for continuous measures, Mann-Whitney u test for BI and FAC, and χ² test for side of hemiparesis and types of stroke.

Characteristics	CG	PG	P	PG1	PG2	P
	(n = 10)	(n = 20)	CG versus PG	(n = 12)	(n = 8)	PG1 versus PG2
Age (years old)	62.8 ± 9.7 (56.8; 68.8)	64.4 ± 13.0 (58.7; 70.1)	0.734	62.7 ± 14.7 (54.4; 70.1)	67.0 ± 10.0 (59.8; 74.2)	0.468
Height (m)	1.68 ± 0.10 (1.61; 1.74)	1.69 ± 0.11 (1.64; 1.74)	0.795	1.69 ± 0.13 (1.62; 1.76)	1.69 ± 0.09 (1.63; 1.75)	0.975
Body mass Index (kg/m2)	25.5 ± 2.4 (24.0; 27.0)	26.29 ± 4.17 (24.5; 28.1)	0.594	26.86 ± 4.33 (24.4; 29.3)	25.43 ± 4.04 (22.6; 28.2)	0.469
Women	5	6	0.284	4	2	0.690
Men	5	14		8	6
Time from the event (days)	—	132 ± 103 (86.9; 177.1)	—	101 ± 36 (80.6; 121.4)	180 ± 149 (76.7; 283.3)	0.091
Length of stay (days)	—	92 ± 41 (74.0; 110.0)	—	83 ± 32 (64.9; 101.1)	104 ± 51 (68.7; 139.3)	0.277
Barthel index	—	60	—	70	46	0.341
		(44; 88)		(50; 88)	(38; 73)
Functional Ambulation Classification	—	4	—	4	3	0.327
		(2; 5)		(3; 5)	(2; 4)
Right	—	12	—	7	5	0.852
Left hemiparesis		8		5	3
Ischemic	—	18	—	11	7	0.761
haemorrhagic		2		1	1

2.2. Clinical Assessment

To assess the independency in activities of daily living and the walking ability of our patients, we administered them the Barthel Index (BI) and the Functional Ambulation Classification (FAC), respectively. BI is one of the best known and commonly used scales to assess the degree of independence a patient demonstrates in various activities of daily living, including mobility and transfers (in particular, bowel and bladder function, grooming, toilet use, feeding, transfers, mobility, dressing, climbing stairs, and bathing). Its total score ranges from 0 (total dependence) to 100 (total independence) [13]. FAC is a six-point hierarchical rating scale that reflects the amount of assistance a person requires to walk. This scale allows to easily classify patients in respect of their walking ability, with maximum score identifying a person able to ambulate independently on nonlevel surfaces [14]. The median values (first, third quartiles) of these scales are reported in Table 1.

2.3. Walking Endurance Assessment

The six-minute walking test (6MWT) was used to measure walking endurance, as usually done in clinical settings [6, 8, 15, 16]. Participants were asked to cover the maximum distance in six minutes self-selecting their speed to do it. They were instructed that they could slow down and rest if necessary and then start again to walk. Patients were allowed to use a cane or a walker and/or to perform the test under physiotherapist supervision, if needed (slight contact might have been required at times). All the participants (patients and healthy subjects) were asked to walk with their common shoes for 6 minutes along a 20 m level walkway, from one extreme to another, in the rehabilitation gym of our hospital. They were told about the lasting time at the third and fifth minute of walking [8]. At the end of test, the walked distance was measured. This distance and the distances walked at the end of each one of the six minutes were evaluated using tape strips fixed on the ground every 2.5 m of the walkway. Patients able to walk for 6 minutes were grouped in PG1, whereas patients unable to complete the test were grouped in PG2.

2.4. Gait Stability Assessment

During the 6MWT, the participants wore an elastic belt including a light wearable inertial sensor device (FreeSense, Sensorize s.r.l., Rome; sampling frequency = 100 Hz, weight = 93 g) located on their back in correspondence of L2-L3 spinous processes, close to their body centre of mass. This device contains a triaxial accelerometer to separately measure three accelerations, each one along one of the three body axes (anteroposterior AP, laterolateral LL, and craniocaudal CC).

Accelerometer signals were 20 Hz low-pass filtered, transformed to give a mean equal to zero, and summarized in their root mean square (RMS) [10–12]. RMS is a measure of acceleration dispersion and therefore of the smoothness of movement patterns. This makes RMS the parameter most commonly used to assess gait stability by means of accelerometry [9].

For each one of the six minutes of walking, the mean walking speed was computed as the meters walked in that minute divided into 60 s, and the mean RMS was computed on the accelerometric signals recorded in a central part of the linear walking performed in that minute (see Figure 1). Conversely, accelerometric data recorded during the two turning parts of the walkway were not analysed.

Figure 1.

The acceleration signal along laterolateral direction of a patient. The grey large bands highlight the analysed part of the signal for each one of the 6 minutes of the test. The thin red lines indicate the end of each 20 m lap.

2.5. Statistical Analysis

Mean ± standard deviation and 95% confidence interval (CI_95%) have been computed for continuous measures and median and 1st and 3rd quartiles for scale scores. Analogously, t-test was used for comparisons between two continuous measures (age, days, height, and body mass index), Mann-Whitney u test for scale scores (BI and FAC), and χ² test for binary variables (gender, side of hemiparesis, and types of stroke). The differences between walking speeds recorded at the 1st minute and the 6th minute for each subgroup of participants were assessed by means of paired t-tests.

An analysis of variance (ANOVA) was performed in order to compare the values of walked distance and walking speeds among the three groups (between subjects factor), followed by post hoc comparison performed with Tukey's test (see Table 2).

Table 2.

Gait parameters. Mean ± standard deviation (CI_95%) of gait parameters recorded during 6MWT for the three groups of participants. The last two columns reported the statistical analyses. For PG2, the last minute walking speed was the minute before stopping.

Gait parameters	PG1 (n = 12)	PG2 (n = 8)	CG (n = 10)	Analysis
				ANOVA	Post-hoc
				PG1, PG2, CG	PG1 versus PG2
Walked distance (m)	226 ± 111	94 ± 73	413 ± 57	F = 31.03	P = 0.007
	(163; 289)	(43; 144)	(378; 448)	P < 0.001
Walking speed (m/s)	0.63 ± 0.31	0.37 ± 0.25	1.15 ± 0.16	F = 22.72	P = 0.082
	(0.45; 0.81)	(0.20; 0.54)	(1.04; 1.26)	P < 0.001
1st minute	0.62 ± 0.30	0.43 ± 0.30	1.17 ± 0.18	F = 19.69	P = 0.271
Walking speed (m/s)	(0.45; 0.79)	(0.22; 0.64)	(1.05; 1.29)	P < 0.001
last minute	0.64 ± 0.32	0.32 ± 0.18	1.16 ± 0.13	F = 28.29	P = 0.019
Walking speed (m/s)	(0.46; 0.82)	(0.20; 0.44)	(1.07; 1.25)	P < 0.001

A repeated measure ANOVA was performed on the RMS values of participants able to complete the test (PG1 and CG) to assess the changes over time (within-factor: 1, 2, 3, 4, 5, and 6 minutes) and the effects of group (between-factor: PG1, CG) and body axis (between-factor: AP, LL, and CC). Conversely, for PG2, in which not all subjects walked for the same time, paired t-test was performed to compare the RMS values recorded at the 1st and at the last minute of their test. The linear fit and relevant determination coefficient (R²) were computed for assessing the relationship between RMSs and time. For all the tests, the significance level was set at 0.05.

3. Results

3.1. Clinical Tests, Gait Speed, and Walking Endurance

Twelve of the twenty patients were able to complete the 6MWT (subgroup PG1) and eight patients asked to definitively stop the test before its planned conclusion (PG2). The clinical characteristics of PG1 and PG2 are summarized in Table 1. No significant clinical differences were found between these two groups, although the clinical picture of PG2 was quite worse (older, lower BI and FAC scores).

In terms of gait performance, a significant difference was observed in terms of walked distance among the three groups (Table 2). Healthy subjects covered a significantly longer distance than that covered by PG1 (P < 0.001) and PG2 (P < 0.001), and PG1 walked significantly more than PG2 (P = 0.007). On the other hand, the mean walking speed, computed over the entire test, was not statistically different between the two groups of patients (but both lower than that of CG, P < 0.001). This may be explained by the fact that the higher distance covered by PG1 in respect of PG2 was mainly due to the longer time spent walking (360 s for PG1 versus 245 ± 67 s for PG2). However, the walking speed recorded in the last minute of the test was significantly lower in PG2 than in PG1 (see Table 2). It was due to a speed reduction observed in all the subjects of PG2 between the first and the last minutes of walking (mean: −22 ± 11%; P = 0.046, paired t-test). The same analysis performed on PG1 (+1 ± 11%, P = 0.493) and CG (−1 ± 7%, P = 0.537) did not show any significant change in terms of walking speed over the course of the test.

3.2. Gait Stability Assessment

Despite the reduction of walking speed observed in PG2, their acceleration RMSs were not reduced between the first and the last minutes of the test (P > 0.05 for all the three RMSs measured along the three body axes). Conversely, 8 out of 12 patients able to complete the test showed an increase of accelerations at least along 2 body axes between the 1st and the 6th minutes of the test. It resulted in a mean progressive increment of all the RMS values of PG1 (about +5%, significant for RMS_LL: +7 ± 11%, P = 0.048), not observed in CG (about −1%). Figure 2 clearly shows this mean increment of acceleration in PG1; however 5 out of these 12 patients showed a reduction of their walking speed during the last minute of the test. A repeated measure ANOVA performed on all the participants who walked for all the 6 minutes (PG1 and CG) showed that the interaction between time and group significantly affected the RMS values (F = 3.082, P = 0.010), whereas neither the main factor time (F = 1.981, P = 0.081) nor its interaction with body axis has a significant effect on the acceleration RMSs (F = 1.810, P = 0.058).

Figure 2.

Acceleration RMS for PG1 ((a), (c), and (e)) and CG ((b), (d), and (f)) along anteroposterior ((a) and (b)), laterolateral ((c) and (d)) and craniocaudal ((e) and(f)) directions. Regression lines and relevant coefficient of determination R² are also reported.

4. Discussion

In this study, we observed a progressive reduction of gait dynamic stability in patients with stroke during prolonged walking. To test the relationship between walking endurance and gait stability, we compared the performances of inpatients with those of an age- and height-matched group of healthy subjects, combining the 6-minute walking test with the measure of upper body accelerations.

As expected, the walked distance at the end of the test and the mean walking speed were both lower in patients than in healthy subjects. The lower walking speed of patients implied lower accelerations, facilitating their control of upper body stability [9, 11]. In this study, the need of RMS normalization to compare populations walking at different speeds [12] has been avoided by analyzing the within-subject variations of RMS values along the test.

During the six minutes of the test, neither walking speed nor trunk accelerations significantly varied for control subjects. Conversely, patients showed a progressive reduction of their walking speed and/or gait stability.

In healthy subjects, it was already found that a reduced gait velocity results in a corresponding reduction of acceleration amplitudes [9]. However, this association between velocity and acceleration was found altered in our patients during the 6MWT. In fact, despite the systematic speed reduction observed in PG2, their trunk accelerations were not reduced during the test. On the other hand, this association resulted reduced also in patients able to complete the test (PG1). In fact, they were able to maintain their self-selected walking speed over the entire test, but many of them also showed a progressive increment of upper body accelerations. The speed reduction observed in PG2 without any acceleration decrease and the increase of upper body accelerations mainly observed in PG1 keeping constant their walking speed indicate that the patients' walking endurance and gait stability were challenged during this test [17].

Our results suggest that patients used two possible alternative strategies to perform the 6MWT. Some of them were able to keep their speed quite constant during walking, despite a slight but progressive reduction of their upper body stability. These subjects were mainly those of PG1, that is, the group able to complete the test. Other subjects seemed to apply a compensation strategy based on the reduction of their walking speed. It probably facilitated the management of their progressive reduction of gait stability during this effortful walking task. As stated above, the reduction of walking speed is, in fact, a suitable strategy for reducing upper body accelerations [9, 11]. This last strategy has been observed especially in those patients who asked to stop the test before its planned conclusion.

In previous studies, for patients with chronic stroke performing the 6MWT, neither differences in velocities for each 1-minute interval [18] nor differences in energy consumption [5] were found significant over the course of the walk. The effects of fatigue were probably not highlighted by these measures [18]. Conversely, changes in gait symmetry [7] and in unaffected lower limb extensor power [5] were found associated with fatigue mechanisms over some minutes of walking.

However, far too little attention has been paid to the reduction of gait stability during prolonged walking, which may potentially increase the risk of falls [9]. In fact, the correlations between upper body accelerations and fall risk have been proven [19]. Falls are one of the most important problems among people after stroke, implying physical and psychological consequences associated with restricted activity as a result of fractures [20] and fear of new falls [21]. During level walking, the main causes of falling are quick walking speed in respect of the actual patient's locomotor capacity, anterior body mass carriage, and step timing delays [22, 23]. In daily living environment, it is conceivable that the patients who self-selected to keep constant their walking speed in spite of an increase of their upper body instabilities may be exposed to a high risk of fall.

In fact, in this study, we found an increment of patients' upper body accelerations, especially along anteroposterior and laterolateral directions over six-minute walking. These accelerations have already been showed as the most informative for assessing the gait stability and also the most correlated with the risk of fall [11, 23]. These findings seem to be consistent with the changes in kinematic [7] and kinetic [5] gait parameters already observed during 6MWT performed by people with stroke. Further studies on wider samples of patients should investigate whether this reduction of gait stability is progressive, as our results seem to show, or it happens only after an identifiable threshold. On the other hand, the reduction of walking speed probably used by some patients to compensate the reduction of gait stability could be anyway dangerous during outdoor walking. By way of example, an adequate gait velocity can be needed to perform some specific tasks, such as crossing the street during the green phase of traffic lights [24].

The main limitation of our study is the reduced size of healthy and patient samples especially in respect of the many features of stroke. Wider samples are needed in future studies to further explore the differences between patients who could and those who could not complete the 6-minute walking test. Another important aspect that needs to be further investigated is the stabilizing effect of the use of a cane or of the therapist's touch during walking. It should be noted that in our study the needs of external helps were similar in the two subgroups of patients (as shown by similar autonomy walking level: see values of FAC scores in Table 1), affecting the upper body accelerations in a similar manner. Finally, the difficulties encountered by participants turning at the end of each lap and the upper body accelerations during turning have been not taken into account in this study. Further researches should deeply investigate this aspect of walking component that can lead to differences in upper body accelerations. Despite these limitations, our study provided important information about the relationship between upper body dynamic stability and walking endurance.

Our results should be read in conjunction with those of Lerdal and colleagues in which it has been shown how an increased mobility may increase exposure to fall opportunities [3]. Walking speed, gait stability, and endurance should be hence quantitatively assessed and improved during rehabilitation in order to allow patients to walk in a functional and safe manner. Furthermore, accelerometry has been recently proposed for assessing the patients' performances during robotic gait training [25] and daily life activities [26]. The quantitative assessment of ability and stability of gait can improve the effectiveness of an intensive training designed around the actual patient's locomotor capacity [27] and the “locomotor awareness” of the patients about his/her abilities and limits.

5. Conclusion

Patients with stroke showed a reduction of walking speed and/or a reduction of gait stability during prolonged walking. In particular, the patients able to complete the six-minute walking test maintained a steady speed over the course of the walk, but their upper body accelerations progressively increased, exposing them to the risk of falling.