588346 research-article2015
POI0010.1177/0309364615588346Prosthetics and Orthotics InternationalArazpour et al.
INTERNATIONAL SOCIETY FOR PROSTHETICS AND ORTHOTICS
Literature Review
The gait and energy efficiency of stance control knee–ankle–foot orthoses: A literature review
Prosthetics and Orthotics International 1–13 © The International Society for Prosthetics and Orthotics 2015 Reprints and permissions: sagepub.co.uk/journalsPermissions.nav DOI: 10.1177/0309364615588346 poi.sagepub.com
Masoud Rafiaei1, Mahmood Bahramizadeh1, Mokhtar Arazpour1,2, Mohammad Samadian3, Stephen W Hutchins4 Farzam Farahmand5 and Mohammad A Mardani1
Abstract Background: The use of knee–ankle–foot orthoses with drop locked knee joints produces some limitations for walking in subjects with quadriceps muscle weakness. The development of stance control orthoses can potentially improve their functionality. Objectives: The aim of this review was to compare the evidence of the effect of stance control orthoses to knee–ankle– foot orthoses with drop locked knee joints in improving kinematic variables and energy efficiency of walking by subjects with quadriceps muscle weakness caused by different pathologies. Study design: Literature review. Methods: Based on selected keywords and their composition, a search was performed in Google Scholar, PubMed, ScienceDirect, and ISI Web of Knowledge databases. In total, 18 articles were finally chosen for review. Results: The results of this study demonstrated that this type of orthosis can improve the walking parameters of subjects with quadriceps muscle weakness and spinal cord injury patients when compared to a locked knee–ankle–foot orthosis. Conclusion: There is evidence to show that stance control orthosis designs improve the gait kinematics but not energetic of knee–ankle–foot orthosis users. Development of new designs of stance control orthoses to provide a more normal pattern of walking is still required. Clinical relevance Stance control orthoses are a new generation of orthotic intervention that could potentially be significant in assisting to improve the gait kinematics by knee–ankle–foot orthosis users. Keywords Stance control knee joint, knee–ankle–foot orthoses, gait analysis, energy consumption Date received: 29 October 2014; accepted: 19 April 2015
1Department
Background Knee–ankle–foot orthoses (KAFOs) are lower extremity devices which extend over the knee, ankle, and foot. KAFOs are prescribed for people with lower limb muscle weakness; particularly in quadriceps muscles.1–3 KAFOs are prescribed for varying muscular weakness of the lower limb including poliomyelitis, post-polio syndrome, cerebrovascular accident (CVA), cerebral palsy (CP), spinal cord injury (SCI), and multiple sclerosis (MS) to provide stability of the lower limb during locomotion.2 Lower limb weakness, especially knee extensor weakness, is a condition that alters normal gait
of Orthotics and Prosthetics, University of Social Welfare and Rehabilitation Sciences, Tehran, Islamic Republic of Iran 2Pediatric Neurorehabilitation Research Center, University of Social Welfare and Rehabilitation Sciences, Tehran, Iran 3Loghman Hakim Hospital, Shahid Beheshti University of Medical Sciences, Tehran, Islamic Republic of Iran 4IHSCR, Faculty of Health & Social Care, University of Salford, Salford, UK 5Mechanical Engineering Department, Sharif University of Technology, Tehran, Islamic Republic of Iran Corresponding author: Mokhtar Arazpour, Department of Orthotics and Prosthetics, University of Social Welfare and Rehabilitation Sciences, Kodakyar st., Daneshjo Blvd., Evin, Tehran 1985713834, Iran. Email: [email protected]
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
2
Prosthetics and Orthotics International
Table 1. Keywords and combinations of keywords used in the study based on population intervention comparison outcome method. P: Population
I: Intervention
C: Comparison
O: Outcome measure
Lower limb weakness, poliomyelitis, post-polio syndrome, SCI, MS, and CP
Stance control knee joint orthosis, SCKAFO
Conventional KAFOs
Energy consumption, speed of walking, cadence, step length, knee ROM, pelvic obliquity, vertical and lateral displacement
patterns,4 and this condition may result in decreased stability during daily tasks.5 Conventional KAFOs provide stability during walking by locking the knee joint in a fully extended position during both stance and swing phases. This requires excessive energy consumption and induces abnormal gait events such as circumduction, hip hiking, and vaulting during gait.6,7 Walking with conventional KAFOs can also lead to premature exhaustion during ambulation, as well as limited mobility, pain, and a decreased range of motion (ROM) in lower limb joints.3,8 It has been reported that using a conventional KAFO reduces gait efficiency by 24%, increases vertical displacement of the center of mass (COM) by up to 65%, and also increases energy expenditure.9 Due to these factors, the rejection rate of using KAFOs in patients with muscular weakness of the lower limb due to conditions such as poliomyelitis, post-polio syndrome, CVA, CP, SCI, and MS has been reported as being between 60% and 100%.9 Stance control KAFOs (SCKAFOs) are a new generation of KAFO which have been developed to prevent knee flexion during stance phase and permit free knee motion during swing phase of gait.10 Mechanical SCKAFOs are usually activated by ankle ROM mechanisms or limb inclination. The UTX, stance control orthosis (SCO) knee joint, swing phase lock (SPL), Horton, Otto Bock Free Walk, and the Otto Bock Sensor Walk are all examples of SCKAFOs.8,11 Using a SCKAFO produces an increased acceptance rate for wearing orthoses by patients with poliomyelitis, CP, CVA, and leg muscle weakness because of the ability to control knee flexion in stance and the provision of free knee flexion during swing phase of gait.3,8,12 Studies have demonstrated that velocity, cadence, stride length, and step length can increase when walking with a SCKAFO versus a locked knee KAFO.2,3,8,12 Irby et al.11 reported that KAFO users showed improvements in velocity, cadence, and stride length after 6 months of walking with the dynamic knee brace system (DKBS). SCKAFOs improve gait by encouraging more normal gait patterns, improving mobility, reducing the energy cost of walking, and reducing compensatory strategies that may lead to chronic pain and loss of motion.2,12–14 Unfortunately, current commercial SCKAFOs are often noisy, bulky, heavy, and expensive and in some cases are not effective in improving kinematic variables and energy
expenditure. Davis et al.12 reported that there was no difference in the energy cost of walking or physiological cost index (PCI) between a SCO and walking with the locked knee joint orthosis. Bernhardt et al.1 reported that it was slightly more difficult to sit down and stand up with the new SCKAFO. Zissimopoulos et al.8 showed that differences in oxygen cost could not be detected between the auto and locked modes of a SCKAFO. Only one study analyzed the engineering structure of this type of orthosis.15 The effects on all walking parameters while using this type of orthosis in comparison to a conventional KAFO are not clear. Therefore, the aim of this literature review was to summarize the research on walking parameters while using these orthoses in various patient groups.
Research questions Energy expenditure and kinematic variables were used as a framework to define the following research questions: •• With regard to energy expenditure: do subjects with quadriceps muscle weakness caused by different pathologies achieve reduced energy expenditure immediately and over time when using SCKAFOs compared with conventional KAFOs? •• With regard to kinematic variables: do persons with quadriceps muscle weakness caused by different pathologies achieve a higher speed of walking, cadence, step length, knee ROM, reduced pelvic obliquity, and vertical and lateral displacement immediately and over time when using SCKAFOs compared with conventional KAFOs?
Method Search strategy An extensive electronic search was carried out through internationally published scholarly articles in Google Scholar, PubMed, ScienceDirect, and ISI Web of Knowledge (from 1950 to 2013) with the selected keywords (Table 1): stance control knee joint orthosis, stance control knee ankle foot orthosis, energy consumption, and temporal spatial parameters. The aforementioned keywords were also searched in combination with lower limb weakness, poliomyelitis, post-polio syndrome, spinal cord
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
3
Rafiaei et al. injury, multiple sclerosis, and cerebral palsy. Search by selected keywords was organized following the population intervention comparison outcome (PICO) model. In order to provide a specific selection of previous studies, different combinations of the topics can be made with the use of AND, OR, and NOT. To prepare a more accurate and comprehensive search, the references of primary resultant articles were also included to find more suitable articles. The strategy includes medical subject headings (MeSH) and text words. The title and abstract of each individual study were screened by authors. The first criterion to select appropriate articles was whether the title has addressed the research questions of interest. The second step in acquiring proportional articles was performed based on the following criteria: 1. Studies which were considered for inclusion were randomized controlled trials (RCTs), case–control trials, cohort studies, case series studies, and single-case studies. 2. The article was written in English. 3. The study evaluated motorized (powered) or mechanical SCO using over training time in poliomyelitis subjects. 4. The study investigated individuals with a lower limb weakness (poliomyelitis, post-polio, and SCI) and able-bodied subjects. 5. The main outcome measures of the article were balance, gait, energy consumption, kinetics, kinematics, and tempo-spatial parameters. The PICO was used to define the included studies. Figure 1 depicts the article selection procedure utilized. Ultimately, 18 studies were included in the review. All the subjects in these studies were persons with polio, postpolio, SCI patients, and able-bodied subjects.
Results Table 2 summarizes the characteristics (participants, parameters, procedure, and results) of studies which evaluated SCOs compared to KAFO when worn during ambulation.
Research question 1: the energy efficiency of SCKAFOs Interestingly, only three studies evaluated energy consumption in non-disabled subjects, subjects with lower limb pathology, and a patient with post-poliomyelitis when using a SCO.8,11,13 A trend to improved energy efficiency has been demonstrated in two studies (0.447 beats/min in using a SCO compared to 0.554 beats/min in locked KAFO, and 0.21 beats/min in using SCO compared to
Google scholar =17 ISI Web of Knowledge =12 Pub Med =18 Science direct =14 Total= 61
Screening articles based on inclusion criteria
32 articles accepted in quality assessment of papers
18 accepted articles carefully considered to fulfill the criteria
Figure 1. The article selection procedure utilized in this study.
0.25 beats/min in locked KAFO).8,13 However, one study reported an increased PCI when using a SCO compared to a locked KAFO (0.70 beats/min compared to 0.65 beats/ min, respectively).11
Research question 2: the kinematic efficiency of SCKAFOs Speed of walking. Typical walking speed has been reported as being 1.3 m/s during normal walking in healthy subjects.16 When using a powered SCO, this can reduce to only 0.57 m/s.16 The mean of this variable has been shown to be 1.18,8 0.82,2 0.8,13 0.59,11 0.63,20 1.04,3 and 0.6117 in various subjects when using a non-powered SCO for ambulation. Only three studies demonstrated an increase in walking speed compared to walking with a locked KAFO,8,11,12 while five studies reported a reduction in this parameter when wearing a SCO.3,16,17,19,20 An improvement in walking velocity has also been reported when
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Arazpour et al. (2013)17
Arazpour et al. (2013)16
Ref.
A 54-year-old male subject suffering from poliomyelitis.
Five healthy subjects of mean age of 26 ± 5.6 years, weight of 66 ± 3.8 kg, and height of 176 ± 4.6 cm participated in this study.
Participants
Method
Speed of walking, step length, total range of lateral compensatory motion, total range of vertical compensatory motion were all evaluated.
Lateral and vertical compensatory motion
Gait analysis: horizontal and vertical excursions of the hips, maximum knee flexion angle, spatiotemporal gait parameters.
Parameters
A motion analysis system was used to collect lower limb kinematics. The person with poliomyelitis used the KAFO with powered knee joints for walking therapy and gait training.
Gait data were acquired in a motion analysis laboratory using a calibrated six-camera video-based motion analysis. Walking trials were randomly performed in three test conditions: normal walking without an orthosis, walking with a conventional KAFO unilaterally, and also with a new powered KAFO applied to the same leg.
Procedure
Walking speed (conventional KAFO = 0.85 ± 0.06 m/s, new powered KAFO = 0.61 ± 0.04 m/s), step length (conventional KAFO = 0.66 ± 0.05 m, new powered KAFO = 0.52 ± 0.03 m), and vertical (conventional KAFO = 9.8 ± 0.04 cm, new powered KAFO = 7.2 ± 0.02 cm) and horizontal displacement of the pelvis (conventional KAFO = 8.6 ± 0.06 cm, new powered KAFO = 5.8 ± 0.04 cm) decreased when walking with the powered SCKAFO compared to the KAFO. When using the powered SCKAFO, the knee flexion achieved during swing and also the overall pattern of walking more closely matched with that of normal human walking. The reduced walking speed may have caused the smaller compensatory motions detected when the powered SCKAFO was used
The means of walking speed (conventional KAFO = 0.78 ± 0.029 m/s, new powered KAFO = 0.57 ± 0.034 m/s), cadence (conventional KAFO = 81 ± 5 steps/min, new powered KAFO = 68 ± 3 steps/min), and knee flexion during swing (conventional KAFO = 6.6° ± 0.89°, new powered KAFO = 40.2° ± 1.30°) and step length (conventional KAFO = 0.57 ± 0.019 cm, new powered KAFO = 0.50 ± 0.040 cm) were all decreased. Lateral compensatory motions (conventional KAFO = 8.2 ± 0.63 cm, new powered KAFO = 5.8 ± 0.22 cm) and vertical compensatory motions (conventional KAFO = 9.8 ± 0.55 cm, new powered KAFO = 7.1 ± 0.23 cm) were increased by both orthoses compared to normal walking. More knee flexion was observed in both swing and stance phases when walking with the powered KAFO compared to the conventional KAFO.
Results
Table 2. The characteristics (participants, parameters, procedure, and results) of studies that evaluated the stance control orthosis on knee–ankle–foot orthosis users.
4 Prosthetics and Orthotics International
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Kinematic parameters, velocity, cadence, and step width were evaluated in this study.
Spatio-temporal, kinematic, and kinetic parameters.
Spatio-temporal and kinematics.
Twenty-one subjects (15 males; 6 females) with weak or absent quadriceps. The average age was 53 + 15 years and body mass indices (BMIs) ranged from 19 to 40.
Three male KAFO users with knee extensor weakness (mean age: 56.3 years).
Davis et al. (2010)12
Yakimovich et al. (2006)20
Spatial-temporal and kinematics gait parameters.
Parameters
Nine subjects (7 males, 2 females, average age: 61 ± 9 years) with inclusion body myositis.
A 70-kg man with T-9, ASIA A class SCI consented to participate in this study.
Participants
Method
Bernhardt et al. (2011)19
To et al. (2012)18
Ref.
Table 2. (Continued)
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Three walking trials were performed with the subjects’ current KAFO and then the new SCKAFO (non-randomized before-after trial). Subjects completed a questionnaire about the new SCKAFO and current KAFO.
Comparison between novice and experienced users that use DKBS, an electromechanical release, and sensors at the knee and footplate, all fit to a conventional KAFO. Objective gait measurements were acquired with a motion analysis system utilizing 10 infrared cameras.
All patients had objective testing of their strength and gait and completed a questionnaire at baseline in 6 months. Subjects were fitted with a Sensor Walk (Otto Bock Health Care, Minneapolis, MN) SCO by a certified orthotist. Gait was assessed using a 10-camera motion analysis system and four force platforms. Gait analysis was performed both with and without the orthosis.
A motion analysis system was used. The upper limb loads applied to the walker during gait with the HNP were compared with three control cases: walking with (a) FNS only; (b) IRGO only, with hips reciprocally coupled, knees locked in extension, and ankles locked at neutral; and (c) IRGO with hips reciprocally coupled, knees freed (i.e., drop locks of the standard KAFO unlatched), ankles locked at neutral, and joints driven by preprogrammed muscle stimulation pattern.
Procedure
(Continued)
Increased knee flexion during swing (KAFO with locked knee joint = 7.9° and SCKAFO = 29.03°), a greater total knee ROM in new SCKAFO users and improved gait kinematics and provided more natural gait.
Novice users demonstrated increased velocity (from 55.3 to 59.0 m/s) and cadence (from 86.3 to 99.2 steps/ min) when using the DKBS over the traditional locked KAFO. Experienced KAFO users tended to have reduced velocity and cadence measures when using the SCO. Knee ROM was significantly greater for the novice group than for the experienced group. Peak knee extension moments tended to be greater for the experienced group.
Velocity (p = 0.025) and cadence (p = 0.007) were lower and step width was higher (p = 0.035) with the SCO than when using an alternative orthosis. There was significant difference (p = 0.021) on peak knee flexion between unbraced condition and walking with SCO (unbraced = 74.4°. SCO = 62.9°), but there was no significant difference (p = 0.355) between unbraced condition and walking with SCO in peak hip flexion).
The HNP reduced the average vertical upper limb forces on the walking aid. The HNP was also capable of reducing the stimulation duty cycle of the knee extensor muscles. The additional mass and internal friction of the SCKM was shown to have minimal effect on knee angle trajectory during swing. These results show that the HNP can significantly reduce the user’s upper limb loading and the amount of muscle stimulation, potentially enabling individuals with paraplegia to walk longer distances and with less effort than with either bracing or FNS alone.
Results
Rafiaei et al. 5
Parameters Kinematics: knee flexion and total knee ROM, pelvic obliquity, and hip abduction angle.
Spatio-temporal gait parameters and kinematics included: knee flexion angles. Two force plates were used to measure ground reaction forces.
Spatio-temporal gait parameters. Kinematic: trunk flexion/ extension, lateral flexion, and rotation. Excursion, hip, and knee flexion/extension ROM.
Three healthy adults (male; age, 35.3 ± 19.7 years) and three KAFO users with knee extensor weakness in at least one limb (male; mean age, 56.3 years).
Four female poliomyelitis patients were selected as experimental subjects. Their mean age, height, and weight were as follows: 37 ± 4.8 years, 159 ± 6.4 cm, and 56 ± 9.7 kg, respectively and all subjects were unilateral KAFO users.
A patient with a T10 SCI (30-year-old man)
Yakimovich et al. (2006)14
Hwang et al. (2008)21
Rasmussen et al. (2007)10
Method
Participants
Ref.
Table 2. (Continued)
A 3-D gait analysis was used. The authors report the use of SCKAFOs in combination with an IRGO. A comparison is made between the scenarios of having the knees locked during the entire gait cycle to that of allowing the knees to flex freely during the swing phase, yet still be locked for stability during stance.
A gait analysis was performed on each subject using a three-dimensional (3-D) motion analysis system with six infrared cameras and two force plates in order to compare gait patterns in two orthotic conditions: an electromechanical KAFO with the locked knee (walking with a KAFO with the clutch locked over the whole period of the gait cycle), and controlled knee gait (walking with a KAFO with the clutch electromechanically controlled).
Evaluation of a new electromechanical SCKAFO and compared to their prescribed KAFO during gait.
Procedure
The addition of stance control to an IRGO in this subject doubled his walking speed (IRGO with locked knee joints = 0.11 ± 0.04 m/s and IRGO with SC knee joints = 0.23 ± 0.02 m/s) and stride length (IRGO with locked knee joints = 0.44 ± 0.27 m and IRGO with SC knee joints = 0.92 ± 0.05 m) with a slight reduction in cadence (IRGO with locked knee joints = 38.4 ± 17.6 steps/min and IRGO with SC knee joints = 30.37 ± 1.32 steps/min) so that this is more in line with the length of his strides. The subject ambulated with a faster, more efficient gait pattern with the stance control feature activated. This orthotic option afforded him the ability to walk safely and smoothly with both knees flexing during swing and with less upper body compensation.
This resulted in approximately 33% less energy consumption than in locked knee gait. It provided both stability in the stance and free swinging of the knee.
All subjects had considerably higher maximum knee flexion during swing phase for controlled knee gait (locked KAFO = 2.9° and controlled KAFO = 32.6°). The pattern of pelvic obliquity during controlled knee gait was very similar to normal gait, but there were some deviations. There were no significant differences in heart rate and minute ventilation.
KAFO users had a mean increase in knee flexion of 21.1° (SD = 8.2) during swing, and a greater total knee ROM when walking with the new SCKAFO compared to their prescribed KAFO. Two KAFO users experienced a reduction in pelvic obliquity and hip abduction angle abnormalities when walking with the SCKAFO compared to their prescribed KAFO.
Results
6 Prosthetics and Orthotics International
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Spatio-temporal data. Kinematic data: ankle dorsiflexion, knee flexion, and pelvic obliquity. Energy expenditure parameters.
Spatio-temporal kinematics: pelvic obliquity, hip flexion, hip extension, and hip abduction. Kinetics: peak contralateral hip abduction in swing and ipsilateral extension moments during stance, average knee extensor moments during stance, knee moment at foot-off, and peak contralateral ankle plantarflexion moment during stance.
14 research participants (11 males; 3 females). Nine research participants had polio while the remaining patients had other pathologies or trauma including neuropathies, incomplete SCIs, spina bifida, MS, and muscular dystrophy. Average age was 51 + 17 years.
Irby et al. (2007)2
Parameters
Nine able-bodied (five females and four males). Subjects had a mean age 25 ± 2 years.
Participants
Method
Zissimopoulos et al. (2007)8
Ref.
Table 2. (Continued)
A motion analysis system (DKBS) was used during a prospective openenrollment 6-month clinical field trial. The “experienced” group routinely used a locked KAFO for ambulation. The “novice” group had been prescribed but did not regularly use a locked KAFO for ambulation.
Subjects walked with KAFOs that incorporated the Hortons stance control orthotic knee joint (SCOKJ) in the locked, unlocked, and auto modes to investigate the biomechanical and energetic effects of SCOs. The study consisted of three stages: fabrication, dynamic adjustment and training, and data collection. For the energy expenditure evaluation, data were collected with a Cosmed K4b2 portable spirometer on treadmill. Gait analysis data were processed with motion analysis system.
Procedure
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
(Continued)
Walking velocity (before = 79 ± 19 m/s and after 6 months = 82 ± 16 m/s), cadence (before = 78 ± 13 steps/min and after 6 months = 83 ± 8 steps/min), and stride length (before = 107 ± 18 cm and after 6 months = 117 ± 15 cm) increased at the initial test to 6 months. Single-limb support time remained unchanged throughout this field trial. Results showed that all subjects significantly increased peak knee flexion between the initial and 6-month tests (before = 49.0 ± 15.5° and after 6 months = 55.9° ± 11.4°).
Gait kinematics for the auto and unlocked modes were more similar than for the auto and locked modes. Oxygen cost was not different between the auto and locked modes (p > 0.99).
Results
Rafiaei et al. 7
Parameters Gait analysis concentrated on orthosis activities such as donning and doffing the orthosis, assuming a sitting or standing position, use of assistive devices, orthosis aesthetics, stability during walking and standing, walking ability over distance and various terrain, and self-reported daily use of the orthosis. Physical examination including bilateral lower limb strength and ROM, and a functional 6-min walk test. Temporal and spatial gait characteristics
Energy expenditure and spatio-temporal gait characteristics were measured in this study.
Kinematic gait analysis.
20 subjects (14 males; 6 females). The majority of the participants were affected by polio (12/20), but diagnoses also included incomplete SCI, MS, industrial or other injury, spina bifida, muscular dystrophy, inclusive body myositis, and weakness of unknown origin. The age of the research participants was 53.2 + 14.8 (range: 11–76) years, with a BMI of 28.7 + 6.1 (range: 19.2–40.1.
A 71-year-old polio patient.
10 subjects (lower limb pathology)
Three able-bodied subjects and three KAFO users.
Bernhardt et al. (2006)1
Ferris et al. (2006)22
Irby et al. (2005)11
Yakimovich et al. (2005)9
Method
Participants
Ref.
Table 2. (Continued)
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
An evaluation of an electromechanical SCKAFO conducted to determine its functional and clinical effectiveness during gait.
A Gait Rite walkway was used to measure temporospatial gait characteristics. A Cosmed K4b2 portable metabolic system was used to measure energy expenditure and heart rate during walking. Two conditions were tested: walking with stance control active (Hortons SCO) and walking with the knee joint locked.
This case study outlined the successful prescription of a KAFO that incorporated a stance control knee joint (E-Knee, Becker Orthopedic, USA).
This study was a component of an overall project design including 6 months at home field trial of the DKBS, with laboratory testing at times 0, 3, and 6 months. Participants were free to choose between the DKBS and their personal orthosis during the trial.
Procedure
The SCKAFO permitted a mean increase in sagittal knee motion during swing for the three KAFO users and a reduction in pelvic obliquity and hip abduction angle abnormalities during terminal stance and swing for two KAFO users.
This case study outlined the successful prescription of a KAFO that incorporated a stance control knee joint (E-Knee, Becker Orthopedic, USA). It also outlined how the use of orthotic diagnostic tools aid prescription and demonstrate improvements in temporal and spatial gait characteristics with SCKAFO. Walking velocity was significantly increased in the stance control condition (SCKAFO = 72.9 ± 25.7 cm/s and locked KAFO = 65.0 ± 24.5 cm/s). There was no difference in the oxygen cost of walking (SCKAFO = 0.213 ± 0.081 mL/kg/min and locked KAFO = 0.224 ± 0.069 mL/kg/min) or PCI between conditions (SCKAFO = 0.65 ± 0.32 beats/min and locked KAFO = 0.70 ± 0.34 beats/min).
Stability while standing and walking with the DKBS was rated as acceptable to excellent and slightly better than other braces. It was slightly more difficult to sit down and stand up with the DKBS. This study shows that wearing a stance control knee orthosis can be a positive experience for an orthosis user.
Results
8 Prosthetics and Orthotics International
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Kinematics: ankle and knee joint angles, shank rate velocity, foot tangential acceleration, and activation period.
Two post-polio syndrome patients. Subject 1 (S1) was a woman (42 years old). Subject 2 (S2) was a male (46 years old).
Tokuhara et al. (2000)23
Each KAFO could be adapted to test two different conditions: (a) control by dorsiflexion (CD) and (2) cyclical controller (CC). Five walking trials (assisted by crutches) through a 10 m path were performed.
All three subjects completed gait analysis, then obstacle course trials, then treadmill trials within 1 day, taking a break before treadmill trials to rest and eat to determine whether individuals with lower limb weakness walk more efficiently when using the SCOKJ than when using a conventional KAFO with the knee locked in extension.
The subject was fitted with a right KAFO with an automatic Hortons stance control knee joint that allowed free flexion of the knee in the swing phase, with automatic locking of the knee at the initiation of stance phase. Instrumented gait analysis was conducted 6 months after the patient received the new KAFO. All data types were recorded simultaneously during each of two ambulatory conditions: walking with the brace in locked knee mode and then in automatic stance control mode.
Procedure
The results from immediate inspection indicate an important improvement of the gait patterns (knee flexion in swing in subject 1 = 50° ± 3° and in subject 2 = 61° ± 3°) in two patients with proximal leg weakness by means of compensations applied by the wearable orthosis.
Improved temporospatial parameters when walking with SCOKJ was noted. Increased speed and cadence, increased stride and step lengths, and fewer compensatory movements at the hip, pelvis, and trunk when walking with the SCOKJ than when walking with the conventional KAFO was noted. Two subjects showed lower energy expenditure when walking with the SCOKJ.
Improved gait biomechanics in use of stance control mode compared with a locked mode. There was a trend toward improved energy efficiency in the stance control mode versus the locked knee mode.
Results
SCKM: stance control knee mechanism; FNS: functional neuromuscular stimulation; HNP: hybrid neuroprosthesis; IRGO: isocentric reciprocating gait orthosis.
Spatio-temporal parameters: walking speed, cadence stride, and step length. Kinematics: knee flexion/ extension, hip, pelvic, and trunk movement. Heart rate
Three subjects with lower limb weakness. Subject 1 was a 56-yearold man with post-polio syndrome who had worn a KAFO with the SCOKJ for 2 years. Subject 2 was a 59-year-old man with post-polio syndrome who had worn the SCOKJ KAFO for 6 weeks and Subject 3 was a 30-yearold male with a nerve root injury (L4 level) secondary to trauma.
McMillan et al. (2004)3
Parameters Kinematic and kinetic gait analyses and PCI in the locked knee and stance control modes. Electromyographic data were recorded from the non-braced limb only by using a surface electrode system.
Participants
Method
A 61-year-old male volunteer with postpoliomyelitis
Hebert and Liggins (2005)13
Ref.
Table 2. (Continued)
Rafiaei et al. 9
10
Prosthetics and Orthotics International
using a stance control knee joint compared to drop locked knee joint in wearing an RGO in SCI patients (0.12 and 0.23 m/s).10,18 Cadence. Six studies noted an increase in cadence during walking with a SCO compared to walking with locked KAFO.2,3,8,11,12,21 However, Hebert et al. when using an automatic SCO and Arazpour et al. when using a powered KAFO both detected a reduction in this parameter compared to walking with locked KAFOs.13,16 Using a SCO associated with an RGO caused a reduction in this parameter in SCI patients.10 The mean cadence in these studies was between 53 and 102 steps/min. Step length. Nine studies analyzed step length in various subjects (poliomyelitis subjects, SCI patients, other pathologies, and able bodied) while walking with a SCO. An increase in this parameter was reported in three studies.2,3,12 However, three studies reported reduction in this parameter when using a SCO compared to a locked KAFO.16,17,20 One study reported similar results when ‘using a joint that can be switched between locked knee and stance control modes’ (mean: 0.6 m),8 but a second study demonstrated a reduction in step length compared to a locked KAFO.13 The mean of step length reported in these studies was between 50 and 70 cm. Two studies using a SCO in combination with an RGO by SCI patients demonstrated the mean of this parameter to be 0.46 and 0.36 m.10,18 Knee ROM. The knee joint needs 67° of flexion during swing phase in healthy subjects during normal walking.16 Using a SCO reduces this mean to 40° in healthy subjects.16 The reported mean of this parameter was 62.9°,1 47°,24 50°, 61°,21 and 43°25 when SCOs are used compared to KAFO with drop locked knee joints (2°–5°). The mean knee joint ROM during swing phase was 50° when walking with a SCO associated with an RGO in SCI subjects compared to RGO with drop locked knee joints.10 Pelvic obliquity. Pelvic obliquity was analyzed in three studies when SCO was compared to KAFO with drop locked knee joint in able-bodied, poliomyelitis, and various subjects.2,8,14 Irby et al.2 in gait evaluation of SCOs by 14 SCO users during a 6-month clinical field trial announced that all subjects had significantly lower pelvic obliquity, 2.8 mm (p = 0.04) compared to baseline. Zissimopoulos et al.8 studied the biomechanical and energetic effects of a SCO knee joint on the gait of nine non-disabled persons and reported significant differences between the locked mode and unlocked mode (p = 0.003) and auto mode and locked mode (p = 0.01). Yakimovich et al. evaluated the kinematics of a new SCKAFO on three male KAFO users with knee extensor weakness. The new SCKAFO improved
pelvic obliquity and provided a more natural gait for orthosis users compared to conventional KAFOs.14 Vertical and lateral displacement. Reduction in the mean of lateral displacement has been reported when using SCO compared to locked KAFO. Arazpour et al.,16 in using a SCO in healthy subjects, demonstrated the decreased rate of this parameter from 8.2 to 5.8 mm. In other study, Arazpour et al.17 in evaluation of powered SCO on one poliomyelitis subject reported a reduction in lateral displacement from 8.6 to 5.8 mm. Hwang et al.21 in an evaluation of electromechanical SCOs worn by four poliomyelitis subjects demonstrated a reduction in this parameter from 292.8 to 196.7 mm. Similar to lateral displacement, reduction in vertical displacement has been demonstrated when walking with a SCO compared to a locked KAFO in poliomyelitis subjects. Both Arazpour et al.17 and Hwang et al.21 reported a reduction in this parameter from 64.7 to 54.2 and from 9.8 to 7.2 mm, respectively. This reduction, in another study by Arazpour et al.,16 was confirmed on healthy subjects when using a SCO compared to locked KAFO (from 9.8 to 7.1 mm). The optimal level of this parameter was reported as being 4.7° for lateral displacement and 5° for vertical displacement.16
Discussion The aim of this study was to evaluate the effect of SCO use on walking efficacy in users of this type of orthosis. Recommended indications are different for SCKAFOs compared to KAFOs. Subjects with lower limb weakness can use a KAFO with drop locked knee joints. Users who have sufficient hip strength can benefit from a SCKAFO, and the criterion for using a SCKAFO is the presence of hip strength of at least Grade 3. Impaired cognition, kneeflexion contracture >10°, moderate to severe spasticity of the hamstrings, lack of hip abductors in bilateral patients, uncorrectable genu varum/valgum >10°, lack of motivation or inappropriate expectations, and body weight >300 lbs are all contraindications for using SCKAFOs.25 The provision of reduced energy consumption has been quoted as one of the main aims and reasons for subjects with lower limb weakness to walk with a SCO. Due to paralysis of the lower limb muscles, KAFO users are forced to walk with the knee in a locked position, hip hiking strategy, leg circumduction, or a vaulting gait.6,7 This can cause soft tissue injury, an increased effort to walk, and a high rate of energy consumption in KAFO users.3,8 Only three studies evaluated this parameter in poliomyelitis subjects when wearing SCO compared to a locked KAFO.8,12,13 Despite the advantages of walking with a SCO, this type of orthosis has not demonstrated a significant improvement by producing decreased energy consumption.8,13 It would be expected that based on the free swing in the knee joint
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
11
Rafiaei et al. during swing phase made available by this device, the users effort would be decreased and therefore this would cause less energy consumption during ambulation. However, the number of participants was small, as few subjects participated in these studies, so the results cannot be generalized for the larger population. More studies are therefore needed to further analyze this effect. Increased knee joint flexion and extension during swing when walking with a SCO compared to a KAFO in subjects with lower limb paralysis is a positive function for such individuals. In using SCO, walking with the knee locked provides stance phase stability, but provides free flexion in swing phase during ambulation, and the development of the SCO was based on this concept. The knee joint must have approximately 70° of flexion available in normal walking, but SCOs have not demonstrated that they can provide this amount of flexion. Future designs of SCOs must consider this limitation by providing more knee joint flexion. In addition, stance phase flexion must be developed in new designs of SCO to provide flexion during loading response and late stance. This is because flexion of the knee joint in stance phase plays a shockabsorbing role and smoothes the COM trajectory during normal walking. SCOs therefore also need to provide a near-normal walking pattern for subjects with less lower limb muscle strength than healthy subjects. Using a powered SCO may provide this, but the slow walking speed provided by these orthoses needs to be improved,16,17 and therefore, more research is needed in this field to provide more advanced powered SCO designs. Using SCOs has been shown to provide improvement in frontal plane pelvic motions. Pelvic obliquity and vertical and lateral displacement have all improved with less abnormal gait deviations being noted (such as circumduction, hip hiking, and vaulting gait) during walking, but the number of participants in these studies has been low. Improvements in hip and pelvic motions were small and did not occur consistently among all studies, making it difficult to generalize this point of using SCOs compared to a locked KAFO. Future longitudinal studies involving more subjects and with longer training times with this type of orthosis may demonstrate whether the SCOs improve hip and pelvic kinematics. The mean speed of walking when using SCOs has demonstrated lower walking speeds compared to a locked KAFO. Gait training with SCOs is also needed to produce a successful outcome in improving temporal spatial and kinematics during walking in KAFO users. Using a SCO needs a small knee extension moment to disengage knee joint locking in late stance. Experience of users during walking with the SCOs must be increased over time to provide more ability in controlling the orthosis. The concentration required for SCKAFO control may be the cause of the shorter stride lengths demonstrated, associated with longer stride times, and therefore slower walking speeds
compared to walking with a locked KAFO. Another reason why SCO use does not improve walking speed is that studies have compared experienced KAFOs users with subjects who only had a short time to acclimatize to walking with the SCOs. Consequently, gait training with SCOs should be performed for several days or weeks to become experienced in walking to increase ability and confidence of users to control the SCOs and improve gait function before being compared to other devices. Production of SCKAFOs started in the early 1970s, and since then there have been continuous improvements and modifications in their design, including the use of hydraulic24 friction,26 elastic27 or impingement28,29 clutches,30,31 and brake mechanisms23 to provide the stance control concept. In commercially available SCKAFOs such as the E-Knee from Becker Orthopedics, the Horton stance control knee joint, and the Sensor Walk from Otto Bock, weight-activated control is used. In the E-MAG Active from Otto Bock and SPL, the control of knee joint is position sensor activated. The Free Walk, UTX, and Full Stride/ Safety Stride are ankle activated. According to cost, size, weight, or poor functionality, some of these designs have not led to clinical and commercial production, and development was based on mechanical and electromechanical mechanisms. New technologies can, however, be used to improve function of SCKAFOs; for instance, the use of actuators and sensors in lower limb orthoses have introduced new capabilities for adaptive control in SCOs.22,32,33 The selected studies are not analyzed according to the PEDro scale. This point was the main limitation of this study. The studies’ flaws included lack of randomization procedures, lack of control group, no masking of examiners and patients, and also there was lack of similarity among groups. These more recent studies have not substantially improved the quality of the research. There is a continuing need for high-quality experimental studies in this area. Future studies should therefore include the following: •• A study includes meta-analyses to produce improved and more reliable conclusions according to speed, cadence, pelvic obliquity, and step length; •• A comparison between the different types of SCKAFOs; •• A comparison of SCOs and locked KAFOs in their effect on energy consumption and endurance of walking in KAFO users to add more clarification on the effect of this type of orthosis in the rehabilitation of walking; •• The design and construction of more advanced SCOs to further improve structural characteristics of orthosis in KAFO users is recommended; •• The design and construction of more advanced powered SCOs as future designs of orthosis for use in rehabilitation of walking in KAFO users;
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
12
Prosthetics and Orthotics International
•• An investigation into the effect of gait training with SCOs on walking parameters in future designs of studies; •• An investigation into the effect of SCOs on COM displacement and stability in quiet standing; •• Although cosmesis was not evaluated in using SCOs on KAFO users, consideration should be given to improve cosmesis of walking when KAFO users wear this type of orthoses; •• The effect of SCOs on quality-of-life measures and social participation compared to KAFOs.
Conclusion SCKAFOs have been shown to support the knee joint during stance phase and provide free knee movement during swing phase successfully in all the walking studies analyzed.15 SCKAFO designs have provided improved gait kinematics for KAFO users. Using SCOs has been shown to provide improvement in pelvic obliquity and vertical and lateral displacement during walking. Despite the advantages of wearing a SCO, this type of orthosis has not demonstrated a significant improvement in producing decreased energy consumption.8,13 Lower walking speeds have been reported when using SCOs compared to a locked KAFO. Development of new design of SCO that provides more normal patterns of walking is required in this field. To improve walking, additional gait training and accommodation periods are needed before walking with SCOs by KAFO users. Author contribution All authors contributed equally in the preparation of this manuscript.
Declaration of conflicting interests The authors did not have any conflicts of interest with regard to the study presented in this article.
Funding We thank the Iran National Science Foundation for financial support (grant number 92001422) for this research.
References 1. Bernhardt KA, Irby SE and Kaufman KR. Consumer opinions of a stance control knee orthosis. Prosthet Orthot Int 2006; 30(3): 246–256. 2. Irby SE, Bernhardt KA and Kaufman KR. Gait changes over time in stance control orthosis users. Prosthet Orthot Int 2007; 31(4): 353–361. 3. McMillan AG, Kendrick K, Michael JW, et al. Preliminary evidence for effectiveness of a stance control orthosis. J Prosthet Orthot 2004; 16(1): 6–13. 4. Kepple TM, Siegel KL and Stanhope SJ. Relative contributions of the lower extremity joint moments to forward
progression and support during gait. Gait Posture 1997; 6(1): 1–8. 5. Peethambaran A. The relationship between performance, satisfaction, and well being for patients using anterior and posterior design knee-ankle-foot-orthosis. J Prosthet Orthot 2000; 12(1): 33–45. 6. Sulzer JS, Gordon KE, Dhaher YY, et al. Preswing knee flexion assistance is coupled with hip abduction in people with stiff-knee gait after stroke. Stroke 2010; 41(8): 1709–1714. 7. Lemaire ED, Goudreau L, Yakimovich T, et al. Angularvelocity control approach for stance-control orthoses. IEEE Trans Neural Syst Rehabil Eng 2009; 17(5): 497–503. 8. Zissimopoulos A, Fatone S and Gard SA. Biomechanical and energetic effects of a stance-control orthotic knee joint. J Rehabil Res Dev 2007; 44(4): 503–513. 9. Yakimovich T, Kofman J and Lemaire E (eds). Design, construction and evaluation of an electromechanical stancecontrol knee-ankle-foot orthosis. In: 2005 IEEE-EMBS 2005 27th annual international conference of the engineering in medicine and biology society, Shanghai, China, 1–4 September 2005. New York: IEEE. 10. Rasmussen AA, Smith KM and Damiano DL. Biomechanical evaluation of the combination of bilateral stance-control knee-ankle-foot orthoses and a reciprocating gait orthosis in an adult with a spinal cord injury. J Prosthet Orthot 2007; 19(2): 42–47. 11. Irby SE, Bernhardt KA and Kaufman KR. Gait of stance control orthosis users: the dynamic knee brace system. Prosthet Orthot Int 2005; 29(3): 269–282. 12. Davis PC, Bach TM and Pereira DM. The effect of stance control orthoses on gait characteristics and energy expenditure in knee-ankle-foot orthosis users. Prosthet Orthot Int 2010; 34(2): 206–215. 13. Hebert JS and Liggins AB. Gait evaluation of an automatic stance-control knee orthosis in a patient with postpoliomyelitis. Arch Phys Med Rehabil 2005; 86(8): 1676–1680. 14. Yakimovich T, Lemaire ED and Kofman J (eds). Gait evaluation of a new electromechanical stance-control knee-anklefoot orthosis. In: 2006 EMBS’06 28th annual international conference of the IEEE engineering in medicine and biology society, New York, 30 August–3 September 2006. New York: IEEE. 15. Yakimovich T, Lemaire ED and Kofman J. Engineering design review of stance-control knee-ankle-foot orthoses. J Rehabil Res Dev 2009; 46(2): 257–267. 16. Arazpour M, Ahmadi F, Bani MA, et al. Gait evaluation of new powered knee-ankle-foot orthosis in able-bodied persons: a pilot study. Prosthet Orthot Int. Epub ahead of print 9 May 2013. DOI: 10.1177/0309364613486917. 17. Arazpour M, Chitsazan A, Bani MA, et al. The effect of a knee ankle foot orthosis incorporating an active knee mechanism on gait of a person with poliomyelitis. Prosthet Orthot Int 2013; 37: 411–414. 18. To CS, Kobetic R, Bulea TC, et al. Sensor-based stance control with orthosis and functional neuromuscular stimulation for walking after spinal cord injury. J Prosthet Orthot 2012; 24(3): 124–132. 19. Bernhardt K, Oh T and Kaufman K. Stance control orthosis trial in patients with inclusion body myositis. Prosthet Orthot Int 2011; 35(1): 39–44.
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
13
Rafiaei et al. 20. Yakimovich T, Lemaire ED and Kofman J. Preliminary kinematic evaluation of a new stance-control knee-ankle-foot orthosis. Clin Biomech 2006; 21(10): 1081–1089. 21. Hwang S, Kang S, Cho K, et al. Biomechanical effect of electromechanical knee-ankle-foot-orthosis on knee joint control in patients with poliomyelitis. Med Biol Eng Comput 2008; 46(6): 541–549. 22. Ferris DP, Gordon KE, Sawicki GS, et al. An improved powered ankle-foot orthosis using proportional myoelectric control. Gait Posture 2006; 23(4): 425–428. 23. Tokuhara Y, Kameyama O, Kubota T, et al. Biomechanical study of gait using an intelligent brace. J Orthop Sci 2000; 5(4): 342–348. 24. Raftopoulos DD, Armstrong CW, Poulos L, et al. A novel design of a knee-ankle-foot orthosis and its evaluation. In: ASME Advances in Bioengineering Conference, Anaheim, CA, 1986, pp.128–129. 25. Otto Bock. E-MAG active coding justification. Available at: www.ottobock.com 26. Weddendorf BC. Automatic locking orthotic knee device. Patent US 5267950 A, 1993.
27. Kofman J, Allard P, Duhaime M, et al. A functional kneeankle orthosis for Duchenne muscular dystrophy patients using a spring-loaded knee joint mechanism. Orthop Tech 1985; 6(85): 403–407. 28. Harris AI. Automatically releasing knee brace. Patent US 4632096 A, 1986. 29. Goudsmit JA and Nijenbanning G. Gravity operated locking hinge. Patent US 6979304 B2, 2005. 30. Harrison R, Lemaire E, Jeffreys Y, et al. Design and pilot testing of an orthotic stance-phase control knee joint. Orthop Tech 2001; 111: 2–4. 31. Myers N. Releasable conical roller-clutch for knee brace. New York: NASA Tech Briefs, 2002, p. 56. 32. Moreno JC, Brunetti F, Rocon E, et al. Immediate effects of a controllable knee ankle foot orthosis for functional compensation of gait in patients with proximal leg weakness. Med Biol Eng Comput 2008; 46(1): 43–53. 33. Blaya JA and Herr H. Adaptive control of a variable-impedance ankle-foot orthosis to assist drop-foot gait. IEEE Trans Neural Syst Rehabil Eng 2004; 12(1): 24–31.
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
POI0010.1177/0309364615588346Prosthetics and Orthotics InternationalArazpour et al.
INTERNATIONAL SOCIETY FOR PROSTHETICS AND ORTHOTICS
Literature Review
The gait and energy efficiency of stance control knee–ankle–foot orthoses: A literature review
Prosthetics and Orthotics International 1–13 © The International Society for Prosthetics and Orthotics 2015 Reprints and permissions: sagepub.co.uk/journalsPermissions.nav DOI: 10.1177/0309364615588346 poi.sagepub.com
Masoud Rafiaei1, Mahmood Bahramizadeh1, Mokhtar Arazpour1,2, Mohammad Samadian3, Stephen W Hutchins4 Farzam Farahmand5 and Mohammad A Mardani1
Abstract Background: The use of knee–ankle–foot orthoses with drop locked knee joints produces some limitations for walking in subjects with quadriceps muscle weakness. The development of stance control orthoses can potentially improve their functionality. Objectives: The aim of this review was to compare the evidence of the effect of stance control orthoses to knee–ankle– foot orthoses with drop locked knee joints in improving kinematic variables and energy efficiency of walking by subjects with quadriceps muscle weakness caused by different pathologies. Study design: Literature review. Methods: Based on selected keywords and their composition, a search was performed in Google Scholar, PubMed, ScienceDirect, and ISI Web of Knowledge databases. In total, 18 articles were finally chosen for review. Results: The results of this study demonstrated that this type of orthosis can improve the walking parameters of subjects with quadriceps muscle weakness and spinal cord injury patients when compared to a locked knee–ankle–foot orthosis. Conclusion: There is evidence to show that stance control orthosis designs improve the gait kinematics but not energetic of knee–ankle–foot orthosis users. Development of new designs of stance control orthoses to provide a more normal pattern of walking is still required. Clinical relevance Stance control orthoses are a new generation of orthotic intervention that could potentially be significant in assisting to improve the gait kinematics by knee–ankle–foot orthosis users. Keywords Stance control knee joint, knee–ankle–foot orthoses, gait analysis, energy consumption Date received: 29 October 2014; accepted: 19 April 2015
1Department
Background Knee–ankle–foot orthoses (KAFOs) are lower extremity devices which extend over the knee, ankle, and foot. KAFOs are prescribed for people with lower limb muscle weakness; particularly in quadriceps muscles.1–3 KAFOs are prescribed for varying muscular weakness of the lower limb including poliomyelitis, post-polio syndrome, cerebrovascular accident (CVA), cerebral palsy (CP), spinal cord injury (SCI), and multiple sclerosis (MS) to provide stability of the lower limb during locomotion.2 Lower limb weakness, especially knee extensor weakness, is a condition that alters normal gait
of Orthotics and Prosthetics, University of Social Welfare and Rehabilitation Sciences, Tehran, Islamic Republic of Iran 2Pediatric Neurorehabilitation Research Center, University of Social Welfare and Rehabilitation Sciences, Tehran, Iran 3Loghman Hakim Hospital, Shahid Beheshti University of Medical Sciences, Tehran, Islamic Republic of Iran 4IHSCR, Faculty of Health & Social Care, University of Salford, Salford, UK 5Mechanical Engineering Department, Sharif University of Technology, Tehran, Islamic Republic of Iran Corresponding author: Mokhtar Arazpour, Department of Orthotics and Prosthetics, University of Social Welfare and Rehabilitation Sciences, Kodakyar st., Daneshjo Blvd., Evin, Tehran 1985713834, Iran. Email: [email protected]
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
2
Prosthetics and Orthotics International
Table 1. Keywords and combinations of keywords used in the study based on population intervention comparison outcome method. P: Population
I: Intervention
C: Comparison
O: Outcome measure
Lower limb weakness, poliomyelitis, post-polio syndrome, SCI, MS, and CP
Stance control knee joint orthosis, SCKAFO
Conventional KAFOs
Energy consumption, speed of walking, cadence, step length, knee ROM, pelvic obliquity, vertical and lateral displacement
patterns,4 and this condition may result in decreased stability during daily tasks.5 Conventional KAFOs provide stability during walking by locking the knee joint in a fully extended position during both stance and swing phases. This requires excessive energy consumption and induces abnormal gait events such as circumduction, hip hiking, and vaulting during gait.6,7 Walking with conventional KAFOs can also lead to premature exhaustion during ambulation, as well as limited mobility, pain, and a decreased range of motion (ROM) in lower limb joints.3,8 It has been reported that using a conventional KAFO reduces gait efficiency by 24%, increases vertical displacement of the center of mass (COM) by up to 65%, and also increases energy expenditure.9 Due to these factors, the rejection rate of using KAFOs in patients with muscular weakness of the lower limb due to conditions such as poliomyelitis, post-polio syndrome, CVA, CP, SCI, and MS has been reported as being between 60% and 100%.9 Stance control KAFOs (SCKAFOs) are a new generation of KAFO which have been developed to prevent knee flexion during stance phase and permit free knee motion during swing phase of gait.10 Mechanical SCKAFOs are usually activated by ankle ROM mechanisms or limb inclination. The UTX, stance control orthosis (SCO) knee joint, swing phase lock (SPL), Horton, Otto Bock Free Walk, and the Otto Bock Sensor Walk are all examples of SCKAFOs.8,11 Using a SCKAFO produces an increased acceptance rate for wearing orthoses by patients with poliomyelitis, CP, CVA, and leg muscle weakness because of the ability to control knee flexion in stance and the provision of free knee flexion during swing phase of gait.3,8,12 Studies have demonstrated that velocity, cadence, stride length, and step length can increase when walking with a SCKAFO versus a locked knee KAFO.2,3,8,12 Irby et al.11 reported that KAFO users showed improvements in velocity, cadence, and stride length after 6 months of walking with the dynamic knee brace system (DKBS). SCKAFOs improve gait by encouraging more normal gait patterns, improving mobility, reducing the energy cost of walking, and reducing compensatory strategies that may lead to chronic pain and loss of motion.2,12–14 Unfortunately, current commercial SCKAFOs are often noisy, bulky, heavy, and expensive and in some cases are not effective in improving kinematic variables and energy
expenditure. Davis et al.12 reported that there was no difference in the energy cost of walking or physiological cost index (PCI) between a SCO and walking with the locked knee joint orthosis. Bernhardt et al.1 reported that it was slightly more difficult to sit down and stand up with the new SCKAFO. Zissimopoulos et al.8 showed that differences in oxygen cost could not be detected between the auto and locked modes of a SCKAFO. Only one study analyzed the engineering structure of this type of orthosis.15 The effects on all walking parameters while using this type of orthosis in comparison to a conventional KAFO are not clear. Therefore, the aim of this literature review was to summarize the research on walking parameters while using these orthoses in various patient groups.
Research questions Energy expenditure and kinematic variables were used as a framework to define the following research questions: •• With regard to energy expenditure: do subjects with quadriceps muscle weakness caused by different pathologies achieve reduced energy expenditure immediately and over time when using SCKAFOs compared with conventional KAFOs? •• With regard to kinematic variables: do persons with quadriceps muscle weakness caused by different pathologies achieve a higher speed of walking, cadence, step length, knee ROM, reduced pelvic obliquity, and vertical and lateral displacement immediately and over time when using SCKAFOs compared with conventional KAFOs?
Method Search strategy An extensive electronic search was carried out through internationally published scholarly articles in Google Scholar, PubMed, ScienceDirect, and ISI Web of Knowledge (from 1950 to 2013) with the selected keywords (Table 1): stance control knee joint orthosis, stance control knee ankle foot orthosis, energy consumption, and temporal spatial parameters. The aforementioned keywords were also searched in combination with lower limb weakness, poliomyelitis, post-polio syndrome, spinal cord
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
3
Rafiaei et al. injury, multiple sclerosis, and cerebral palsy. Search by selected keywords was organized following the population intervention comparison outcome (PICO) model. In order to provide a specific selection of previous studies, different combinations of the topics can be made with the use of AND, OR, and NOT. To prepare a more accurate and comprehensive search, the references of primary resultant articles were also included to find more suitable articles. The strategy includes medical subject headings (MeSH) and text words. The title and abstract of each individual study were screened by authors. The first criterion to select appropriate articles was whether the title has addressed the research questions of interest. The second step in acquiring proportional articles was performed based on the following criteria: 1. Studies which were considered for inclusion were randomized controlled trials (RCTs), case–control trials, cohort studies, case series studies, and single-case studies. 2. The article was written in English. 3. The study evaluated motorized (powered) or mechanical SCO using over training time in poliomyelitis subjects. 4. The study investigated individuals with a lower limb weakness (poliomyelitis, post-polio, and SCI) and able-bodied subjects. 5. The main outcome measures of the article were balance, gait, energy consumption, kinetics, kinematics, and tempo-spatial parameters. The PICO was used to define the included studies. Figure 1 depicts the article selection procedure utilized. Ultimately, 18 studies were included in the review. All the subjects in these studies were persons with polio, postpolio, SCI patients, and able-bodied subjects.
Results Table 2 summarizes the characteristics (participants, parameters, procedure, and results) of studies which evaluated SCOs compared to KAFO when worn during ambulation.
Research question 1: the energy efficiency of SCKAFOs Interestingly, only three studies evaluated energy consumption in non-disabled subjects, subjects with lower limb pathology, and a patient with post-poliomyelitis when using a SCO.8,11,13 A trend to improved energy efficiency has been demonstrated in two studies (0.447 beats/min in using a SCO compared to 0.554 beats/min in locked KAFO, and 0.21 beats/min in using SCO compared to
Google scholar =17 ISI Web of Knowledge =12 Pub Med =18 Science direct =14 Total= 61
Screening articles based on inclusion criteria
32 articles accepted in quality assessment of papers
18 accepted articles carefully considered to fulfill the criteria
Figure 1. The article selection procedure utilized in this study.
0.25 beats/min in locked KAFO).8,13 However, one study reported an increased PCI when using a SCO compared to a locked KAFO (0.70 beats/min compared to 0.65 beats/ min, respectively).11
Research question 2: the kinematic efficiency of SCKAFOs Speed of walking. Typical walking speed has been reported as being 1.3 m/s during normal walking in healthy subjects.16 When using a powered SCO, this can reduce to only 0.57 m/s.16 The mean of this variable has been shown to be 1.18,8 0.82,2 0.8,13 0.59,11 0.63,20 1.04,3 and 0.6117 in various subjects when using a non-powered SCO for ambulation. Only three studies demonstrated an increase in walking speed compared to walking with a locked KAFO,8,11,12 while five studies reported a reduction in this parameter when wearing a SCO.3,16,17,19,20 An improvement in walking velocity has also been reported when
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Arazpour et al. (2013)17
Arazpour et al. (2013)16
Ref.
A 54-year-old male subject suffering from poliomyelitis.
Five healthy subjects of mean age of 26 ± 5.6 years, weight of 66 ± 3.8 kg, and height of 176 ± 4.6 cm participated in this study.
Participants
Method
Speed of walking, step length, total range of lateral compensatory motion, total range of vertical compensatory motion were all evaluated.
Lateral and vertical compensatory motion
Gait analysis: horizontal and vertical excursions of the hips, maximum knee flexion angle, spatiotemporal gait parameters.
Parameters
A motion analysis system was used to collect lower limb kinematics. The person with poliomyelitis used the KAFO with powered knee joints for walking therapy and gait training.
Gait data were acquired in a motion analysis laboratory using a calibrated six-camera video-based motion analysis. Walking trials were randomly performed in three test conditions: normal walking without an orthosis, walking with a conventional KAFO unilaterally, and also with a new powered KAFO applied to the same leg.
Procedure
Walking speed (conventional KAFO = 0.85 ± 0.06 m/s, new powered KAFO = 0.61 ± 0.04 m/s), step length (conventional KAFO = 0.66 ± 0.05 m, new powered KAFO = 0.52 ± 0.03 m), and vertical (conventional KAFO = 9.8 ± 0.04 cm, new powered KAFO = 7.2 ± 0.02 cm) and horizontal displacement of the pelvis (conventional KAFO = 8.6 ± 0.06 cm, new powered KAFO = 5.8 ± 0.04 cm) decreased when walking with the powered SCKAFO compared to the KAFO. When using the powered SCKAFO, the knee flexion achieved during swing and also the overall pattern of walking more closely matched with that of normal human walking. The reduced walking speed may have caused the smaller compensatory motions detected when the powered SCKAFO was used
The means of walking speed (conventional KAFO = 0.78 ± 0.029 m/s, new powered KAFO = 0.57 ± 0.034 m/s), cadence (conventional KAFO = 81 ± 5 steps/min, new powered KAFO = 68 ± 3 steps/min), and knee flexion during swing (conventional KAFO = 6.6° ± 0.89°, new powered KAFO = 40.2° ± 1.30°) and step length (conventional KAFO = 0.57 ± 0.019 cm, new powered KAFO = 0.50 ± 0.040 cm) were all decreased. Lateral compensatory motions (conventional KAFO = 8.2 ± 0.63 cm, new powered KAFO = 5.8 ± 0.22 cm) and vertical compensatory motions (conventional KAFO = 9.8 ± 0.55 cm, new powered KAFO = 7.1 ± 0.23 cm) were increased by both orthoses compared to normal walking. More knee flexion was observed in both swing and stance phases when walking with the powered KAFO compared to the conventional KAFO.
Results
Table 2. The characteristics (participants, parameters, procedure, and results) of studies that evaluated the stance control orthosis on knee–ankle–foot orthosis users.
4 Prosthetics and Orthotics International
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Kinematic parameters, velocity, cadence, and step width were evaluated in this study.
Spatio-temporal, kinematic, and kinetic parameters.
Spatio-temporal and kinematics.
Twenty-one subjects (15 males; 6 females) with weak or absent quadriceps. The average age was 53 + 15 years and body mass indices (BMIs) ranged from 19 to 40.
Three male KAFO users with knee extensor weakness (mean age: 56.3 years).
Davis et al. (2010)12
Yakimovich et al. (2006)20
Spatial-temporal and kinematics gait parameters.
Parameters
Nine subjects (7 males, 2 females, average age: 61 ± 9 years) with inclusion body myositis.
A 70-kg man with T-9, ASIA A class SCI consented to participate in this study.
Participants
Method
Bernhardt et al. (2011)19
To et al. (2012)18
Ref.
Table 2. (Continued)
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Three walking trials were performed with the subjects’ current KAFO and then the new SCKAFO (non-randomized before-after trial). Subjects completed a questionnaire about the new SCKAFO and current KAFO.
Comparison between novice and experienced users that use DKBS, an electromechanical release, and sensors at the knee and footplate, all fit to a conventional KAFO. Objective gait measurements were acquired with a motion analysis system utilizing 10 infrared cameras.
All patients had objective testing of their strength and gait and completed a questionnaire at baseline in 6 months. Subjects were fitted with a Sensor Walk (Otto Bock Health Care, Minneapolis, MN) SCO by a certified orthotist. Gait was assessed using a 10-camera motion analysis system and four force platforms. Gait analysis was performed both with and without the orthosis.
A motion analysis system was used. The upper limb loads applied to the walker during gait with the HNP were compared with three control cases: walking with (a) FNS only; (b) IRGO only, with hips reciprocally coupled, knees locked in extension, and ankles locked at neutral; and (c) IRGO with hips reciprocally coupled, knees freed (i.e., drop locks of the standard KAFO unlatched), ankles locked at neutral, and joints driven by preprogrammed muscle stimulation pattern.
Procedure
(Continued)
Increased knee flexion during swing (KAFO with locked knee joint = 7.9° and SCKAFO = 29.03°), a greater total knee ROM in new SCKAFO users and improved gait kinematics and provided more natural gait.
Novice users demonstrated increased velocity (from 55.3 to 59.0 m/s) and cadence (from 86.3 to 99.2 steps/ min) when using the DKBS over the traditional locked KAFO. Experienced KAFO users tended to have reduced velocity and cadence measures when using the SCO. Knee ROM was significantly greater for the novice group than for the experienced group. Peak knee extension moments tended to be greater for the experienced group.
Velocity (p = 0.025) and cadence (p = 0.007) were lower and step width was higher (p = 0.035) with the SCO than when using an alternative orthosis. There was significant difference (p = 0.021) on peak knee flexion between unbraced condition and walking with SCO (unbraced = 74.4°. SCO = 62.9°), but there was no significant difference (p = 0.355) between unbraced condition and walking with SCO in peak hip flexion).
The HNP reduced the average vertical upper limb forces on the walking aid. The HNP was also capable of reducing the stimulation duty cycle of the knee extensor muscles. The additional mass and internal friction of the SCKM was shown to have minimal effect on knee angle trajectory during swing. These results show that the HNP can significantly reduce the user’s upper limb loading and the amount of muscle stimulation, potentially enabling individuals with paraplegia to walk longer distances and with less effort than with either bracing or FNS alone.
Results
Rafiaei et al. 5
Parameters Kinematics: knee flexion and total knee ROM, pelvic obliquity, and hip abduction angle.
Spatio-temporal gait parameters and kinematics included: knee flexion angles. Two force plates were used to measure ground reaction forces.
Spatio-temporal gait parameters. Kinematic: trunk flexion/ extension, lateral flexion, and rotation. Excursion, hip, and knee flexion/extension ROM.
Three healthy adults (male; age, 35.3 ± 19.7 years) and three KAFO users with knee extensor weakness in at least one limb (male; mean age, 56.3 years).
Four female poliomyelitis patients were selected as experimental subjects. Their mean age, height, and weight were as follows: 37 ± 4.8 years, 159 ± 6.4 cm, and 56 ± 9.7 kg, respectively and all subjects were unilateral KAFO users.
A patient with a T10 SCI (30-year-old man)
Yakimovich et al. (2006)14
Hwang et al. (2008)21
Rasmussen et al. (2007)10
Method
Participants
Ref.
Table 2. (Continued)
A 3-D gait analysis was used. The authors report the use of SCKAFOs in combination with an IRGO. A comparison is made between the scenarios of having the knees locked during the entire gait cycle to that of allowing the knees to flex freely during the swing phase, yet still be locked for stability during stance.
A gait analysis was performed on each subject using a three-dimensional (3-D) motion analysis system with six infrared cameras and two force plates in order to compare gait patterns in two orthotic conditions: an electromechanical KAFO with the locked knee (walking with a KAFO with the clutch locked over the whole period of the gait cycle), and controlled knee gait (walking with a KAFO with the clutch electromechanically controlled).
Evaluation of a new electromechanical SCKAFO and compared to their prescribed KAFO during gait.
Procedure
The addition of stance control to an IRGO in this subject doubled his walking speed (IRGO with locked knee joints = 0.11 ± 0.04 m/s and IRGO with SC knee joints = 0.23 ± 0.02 m/s) and stride length (IRGO with locked knee joints = 0.44 ± 0.27 m and IRGO with SC knee joints = 0.92 ± 0.05 m) with a slight reduction in cadence (IRGO with locked knee joints = 38.4 ± 17.6 steps/min and IRGO with SC knee joints = 30.37 ± 1.32 steps/min) so that this is more in line with the length of his strides. The subject ambulated with a faster, more efficient gait pattern with the stance control feature activated. This orthotic option afforded him the ability to walk safely and smoothly with both knees flexing during swing and with less upper body compensation.
This resulted in approximately 33% less energy consumption than in locked knee gait. It provided both stability in the stance and free swinging of the knee.
All subjects had considerably higher maximum knee flexion during swing phase for controlled knee gait (locked KAFO = 2.9° and controlled KAFO = 32.6°). The pattern of pelvic obliquity during controlled knee gait was very similar to normal gait, but there were some deviations. There were no significant differences in heart rate and minute ventilation.
KAFO users had a mean increase in knee flexion of 21.1° (SD = 8.2) during swing, and a greater total knee ROM when walking with the new SCKAFO compared to their prescribed KAFO. Two KAFO users experienced a reduction in pelvic obliquity and hip abduction angle abnormalities when walking with the SCKAFO compared to their prescribed KAFO.
Results
6 Prosthetics and Orthotics International
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Spatio-temporal data. Kinematic data: ankle dorsiflexion, knee flexion, and pelvic obliquity. Energy expenditure parameters.
Spatio-temporal kinematics: pelvic obliquity, hip flexion, hip extension, and hip abduction. Kinetics: peak contralateral hip abduction in swing and ipsilateral extension moments during stance, average knee extensor moments during stance, knee moment at foot-off, and peak contralateral ankle plantarflexion moment during stance.
14 research participants (11 males; 3 females). Nine research participants had polio while the remaining patients had other pathologies or trauma including neuropathies, incomplete SCIs, spina bifida, MS, and muscular dystrophy. Average age was 51 + 17 years.
Irby et al. (2007)2
Parameters
Nine able-bodied (five females and four males). Subjects had a mean age 25 ± 2 years.
Participants
Method
Zissimopoulos et al. (2007)8
Ref.
Table 2. (Continued)
A motion analysis system (DKBS) was used during a prospective openenrollment 6-month clinical field trial. The “experienced” group routinely used a locked KAFO for ambulation. The “novice” group had been prescribed but did not regularly use a locked KAFO for ambulation.
Subjects walked with KAFOs that incorporated the Hortons stance control orthotic knee joint (SCOKJ) in the locked, unlocked, and auto modes to investigate the biomechanical and energetic effects of SCOs. The study consisted of three stages: fabrication, dynamic adjustment and training, and data collection. For the energy expenditure evaluation, data were collected with a Cosmed K4b2 portable spirometer on treadmill. Gait analysis data were processed with motion analysis system.
Procedure
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
(Continued)
Walking velocity (before = 79 ± 19 m/s and after 6 months = 82 ± 16 m/s), cadence (before = 78 ± 13 steps/min and after 6 months = 83 ± 8 steps/min), and stride length (before = 107 ± 18 cm and after 6 months = 117 ± 15 cm) increased at the initial test to 6 months. Single-limb support time remained unchanged throughout this field trial. Results showed that all subjects significantly increased peak knee flexion between the initial and 6-month tests (before = 49.0 ± 15.5° and after 6 months = 55.9° ± 11.4°).
Gait kinematics for the auto and unlocked modes were more similar than for the auto and locked modes. Oxygen cost was not different between the auto and locked modes (p > 0.99).
Results
Rafiaei et al. 7
Parameters Gait analysis concentrated on orthosis activities such as donning and doffing the orthosis, assuming a sitting or standing position, use of assistive devices, orthosis aesthetics, stability during walking and standing, walking ability over distance and various terrain, and self-reported daily use of the orthosis. Physical examination including bilateral lower limb strength and ROM, and a functional 6-min walk test. Temporal and spatial gait characteristics
Energy expenditure and spatio-temporal gait characteristics were measured in this study.
Kinematic gait analysis.
20 subjects (14 males; 6 females). The majority of the participants were affected by polio (12/20), but diagnoses also included incomplete SCI, MS, industrial or other injury, spina bifida, muscular dystrophy, inclusive body myositis, and weakness of unknown origin. The age of the research participants was 53.2 + 14.8 (range: 11–76) years, with a BMI of 28.7 + 6.1 (range: 19.2–40.1.
A 71-year-old polio patient.
10 subjects (lower limb pathology)
Three able-bodied subjects and three KAFO users.
Bernhardt et al. (2006)1
Ferris et al. (2006)22
Irby et al. (2005)11
Yakimovich et al. (2005)9
Method
Participants
Ref.
Table 2. (Continued)
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
An evaluation of an electromechanical SCKAFO conducted to determine its functional and clinical effectiveness during gait.
A Gait Rite walkway was used to measure temporospatial gait characteristics. A Cosmed K4b2 portable metabolic system was used to measure energy expenditure and heart rate during walking. Two conditions were tested: walking with stance control active (Hortons SCO) and walking with the knee joint locked.
This case study outlined the successful prescription of a KAFO that incorporated a stance control knee joint (E-Knee, Becker Orthopedic, USA).
This study was a component of an overall project design including 6 months at home field trial of the DKBS, with laboratory testing at times 0, 3, and 6 months. Participants were free to choose between the DKBS and their personal orthosis during the trial.
Procedure
The SCKAFO permitted a mean increase in sagittal knee motion during swing for the three KAFO users and a reduction in pelvic obliquity and hip abduction angle abnormalities during terminal stance and swing for two KAFO users.
This case study outlined the successful prescription of a KAFO that incorporated a stance control knee joint (E-Knee, Becker Orthopedic, USA). It also outlined how the use of orthotic diagnostic tools aid prescription and demonstrate improvements in temporal and spatial gait characteristics with SCKAFO. Walking velocity was significantly increased in the stance control condition (SCKAFO = 72.9 ± 25.7 cm/s and locked KAFO = 65.0 ± 24.5 cm/s). There was no difference in the oxygen cost of walking (SCKAFO = 0.213 ± 0.081 mL/kg/min and locked KAFO = 0.224 ± 0.069 mL/kg/min) or PCI between conditions (SCKAFO = 0.65 ± 0.32 beats/min and locked KAFO = 0.70 ± 0.34 beats/min).
Stability while standing and walking with the DKBS was rated as acceptable to excellent and slightly better than other braces. It was slightly more difficult to sit down and stand up with the DKBS. This study shows that wearing a stance control knee orthosis can be a positive experience for an orthosis user.
Results
8 Prosthetics and Orthotics International
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
Kinematics: ankle and knee joint angles, shank rate velocity, foot tangential acceleration, and activation period.
Two post-polio syndrome patients. Subject 1 (S1) was a woman (42 years old). Subject 2 (S2) was a male (46 years old).
Tokuhara et al. (2000)23
Each KAFO could be adapted to test two different conditions: (a) control by dorsiflexion (CD) and (2) cyclical controller (CC). Five walking trials (assisted by crutches) through a 10 m path were performed.
All three subjects completed gait analysis, then obstacle course trials, then treadmill trials within 1 day, taking a break before treadmill trials to rest and eat to determine whether individuals with lower limb weakness walk more efficiently when using the SCOKJ than when using a conventional KAFO with the knee locked in extension.
The subject was fitted with a right KAFO with an automatic Hortons stance control knee joint that allowed free flexion of the knee in the swing phase, with automatic locking of the knee at the initiation of stance phase. Instrumented gait analysis was conducted 6 months after the patient received the new KAFO. All data types were recorded simultaneously during each of two ambulatory conditions: walking with the brace in locked knee mode and then in automatic stance control mode.
Procedure
The results from immediate inspection indicate an important improvement of the gait patterns (knee flexion in swing in subject 1 = 50° ± 3° and in subject 2 = 61° ± 3°) in two patients with proximal leg weakness by means of compensations applied by the wearable orthosis.
Improved temporospatial parameters when walking with SCOKJ was noted. Increased speed and cadence, increased stride and step lengths, and fewer compensatory movements at the hip, pelvis, and trunk when walking with the SCOKJ than when walking with the conventional KAFO was noted. Two subjects showed lower energy expenditure when walking with the SCOKJ.
Improved gait biomechanics in use of stance control mode compared with a locked mode. There was a trend toward improved energy efficiency in the stance control mode versus the locked knee mode.
Results
SCKM: stance control knee mechanism; FNS: functional neuromuscular stimulation; HNP: hybrid neuroprosthesis; IRGO: isocentric reciprocating gait orthosis.
Spatio-temporal parameters: walking speed, cadence stride, and step length. Kinematics: knee flexion/ extension, hip, pelvic, and trunk movement. Heart rate
Three subjects with lower limb weakness. Subject 1 was a 56-yearold man with post-polio syndrome who had worn a KAFO with the SCOKJ for 2 years. Subject 2 was a 59-year-old man with post-polio syndrome who had worn the SCOKJ KAFO for 6 weeks and Subject 3 was a 30-yearold male with a nerve root injury (L4 level) secondary to trauma.
McMillan et al. (2004)3
Parameters Kinematic and kinetic gait analyses and PCI in the locked knee and stance control modes. Electromyographic data were recorded from the non-braced limb only by using a surface electrode system.
Participants
Method
A 61-year-old male volunteer with postpoliomyelitis
Hebert and Liggins (2005)13
Ref.
Table 2. (Continued)
Rafiaei et al. 9
10
Prosthetics and Orthotics International
using a stance control knee joint compared to drop locked knee joint in wearing an RGO in SCI patients (0.12 and 0.23 m/s).10,18 Cadence. Six studies noted an increase in cadence during walking with a SCO compared to walking with locked KAFO.2,3,8,11,12,21 However, Hebert et al. when using an automatic SCO and Arazpour et al. when using a powered KAFO both detected a reduction in this parameter compared to walking with locked KAFOs.13,16 Using a SCO associated with an RGO caused a reduction in this parameter in SCI patients.10 The mean cadence in these studies was between 53 and 102 steps/min. Step length. Nine studies analyzed step length in various subjects (poliomyelitis subjects, SCI patients, other pathologies, and able bodied) while walking with a SCO. An increase in this parameter was reported in three studies.2,3,12 However, three studies reported reduction in this parameter when using a SCO compared to a locked KAFO.16,17,20 One study reported similar results when ‘using a joint that can be switched between locked knee and stance control modes’ (mean: 0.6 m),8 but a second study demonstrated a reduction in step length compared to a locked KAFO.13 The mean of step length reported in these studies was between 50 and 70 cm. Two studies using a SCO in combination with an RGO by SCI patients demonstrated the mean of this parameter to be 0.46 and 0.36 m.10,18 Knee ROM. The knee joint needs 67° of flexion during swing phase in healthy subjects during normal walking.16 Using a SCO reduces this mean to 40° in healthy subjects.16 The reported mean of this parameter was 62.9°,1 47°,24 50°, 61°,21 and 43°25 when SCOs are used compared to KAFO with drop locked knee joints (2°–5°). The mean knee joint ROM during swing phase was 50° when walking with a SCO associated with an RGO in SCI subjects compared to RGO with drop locked knee joints.10 Pelvic obliquity. Pelvic obliquity was analyzed in three studies when SCO was compared to KAFO with drop locked knee joint in able-bodied, poliomyelitis, and various subjects.2,8,14 Irby et al.2 in gait evaluation of SCOs by 14 SCO users during a 6-month clinical field trial announced that all subjects had significantly lower pelvic obliquity, 2.8 mm (p = 0.04) compared to baseline. Zissimopoulos et al.8 studied the biomechanical and energetic effects of a SCO knee joint on the gait of nine non-disabled persons and reported significant differences between the locked mode and unlocked mode (p = 0.003) and auto mode and locked mode (p = 0.01). Yakimovich et al. evaluated the kinematics of a new SCKAFO on three male KAFO users with knee extensor weakness. The new SCKAFO improved
pelvic obliquity and provided a more natural gait for orthosis users compared to conventional KAFOs.14 Vertical and lateral displacement. Reduction in the mean of lateral displacement has been reported when using SCO compared to locked KAFO. Arazpour et al.,16 in using a SCO in healthy subjects, demonstrated the decreased rate of this parameter from 8.2 to 5.8 mm. In other study, Arazpour et al.17 in evaluation of powered SCO on one poliomyelitis subject reported a reduction in lateral displacement from 8.6 to 5.8 mm. Hwang et al.21 in an evaluation of electromechanical SCOs worn by four poliomyelitis subjects demonstrated a reduction in this parameter from 292.8 to 196.7 mm. Similar to lateral displacement, reduction in vertical displacement has been demonstrated when walking with a SCO compared to a locked KAFO in poliomyelitis subjects. Both Arazpour et al.17 and Hwang et al.21 reported a reduction in this parameter from 64.7 to 54.2 and from 9.8 to 7.2 mm, respectively. This reduction, in another study by Arazpour et al.,16 was confirmed on healthy subjects when using a SCO compared to locked KAFO (from 9.8 to 7.1 mm). The optimal level of this parameter was reported as being 4.7° for lateral displacement and 5° for vertical displacement.16
Discussion The aim of this study was to evaluate the effect of SCO use on walking efficacy in users of this type of orthosis. Recommended indications are different for SCKAFOs compared to KAFOs. Subjects with lower limb weakness can use a KAFO with drop locked knee joints. Users who have sufficient hip strength can benefit from a SCKAFO, and the criterion for using a SCKAFO is the presence of hip strength of at least Grade 3. Impaired cognition, kneeflexion contracture >10°, moderate to severe spasticity of the hamstrings, lack of hip abductors in bilateral patients, uncorrectable genu varum/valgum >10°, lack of motivation or inappropriate expectations, and body weight >300 lbs are all contraindications for using SCKAFOs.25 The provision of reduced energy consumption has been quoted as one of the main aims and reasons for subjects with lower limb weakness to walk with a SCO. Due to paralysis of the lower limb muscles, KAFO users are forced to walk with the knee in a locked position, hip hiking strategy, leg circumduction, or a vaulting gait.6,7 This can cause soft tissue injury, an increased effort to walk, and a high rate of energy consumption in KAFO users.3,8 Only three studies evaluated this parameter in poliomyelitis subjects when wearing SCO compared to a locked KAFO.8,12,13 Despite the advantages of walking with a SCO, this type of orthosis has not demonstrated a significant improvement by producing decreased energy consumption.8,13 It would be expected that based on the free swing in the knee joint
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
11
Rafiaei et al. during swing phase made available by this device, the users effort would be decreased and therefore this would cause less energy consumption during ambulation. However, the number of participants was small, as few subjects participated in these studies, so the results cannot be generalized for the larger population. More studies are therefore needed to further analyze this effect. Increased knee joint flexion and extension during swing when walking with a SCO compared to a KAFO in subjects with lower limb paralysis is a positive function for such individuals. In using SCO, walking with the knee locked provides stance phase stability, but provides free flexion in swing phase during ambulation, and the development of the SCO was based on this concept. The knee joint must have approximately 70° of flexion available in normal walking, but SCOs have not demonstrated that they can provide this amount of flexion. Future designs of SCOs must consider this limitation by providing more knee joint flexion. In addition, stance phase flexion must be developed in new designs of SCO to provide flexion during loading response and late stance. This is because flexion of the knee joint in stance phase plays a shockabsorbing role and smoothes the COM trajectory during normal walking. SCOs therefore also need to provide a near-normal walking pattern for subjects with less lower limb muscle strength than healthy subjects. Using a powered SCO may provide this, but the slow walking speed provided by these orthoses needs to be improved,16,17 and therefore, more research is needed in this field to provide more advanced powered SCO designs. Using SCOs has been shown to provide improvement in frontal plane pelvic motions. Pelvic obliquity and vertical and lateral displacement have all improved with less abnormal gait deviations being noted (such as circumduction, hip hiking, and vaulting gait) during walking, but the number of participants in these studies has been low. Improvements in hip and pelvic motions were small and did not occur consistently among all studies, making it difficult to generalize this point of using SCOs compared to a locked KAFO. Future longitudinal studies involving more subjects and with longer training times with this type of orthosis may demonstrate whether the SCOs improve hip and pelvic kinematics. The mean speed of walking when using SCOs has demonstrated lower walking speeds compared to a locked KAFO. Gait training with SCOs is also needed to produce a successful outcome in improving temporal spatial and kinematics during walking in KAFO users. Using a SCO needs a small knee extension moment to disengage knee joint locking in late stance. Experience of users during walking with the SCOs must be increased over time to provide more ability in controlling the orthosis. The concentration required for SCKAFO control may be the cause of the shorter stride lengths demonstrated, associated with longer stride times, and therefore slower walking speeds
compared to walking with a locked KAFO. Another reason why SCO use does not improve walking speed is that studies have compared experienced KAFOs users with subjects who only had a short time to acclimatize to walking with the SCOs. Consequently, gait training with SCOs should be performed for several days or weeks to become experienced in walking to increase ability and confidence of users to control the SCOs and improve gait function before being compared to other devices. Production of SCKAFOs started in the early 1970s, and since then there have been continuous improvements and modifications in their design, including the use of hydraulic24 friction,26 elastic27 or impingement28,29 clutches,30,31 and brake mechanisms23 to provide the stance control concept. In commercially available SCKAFOs such as the E-Knee from Becker Orthopedics, the Horton stance control knee joint, and the Sensor Walk from Otto Bock, weight-activated control is used. In the E-MAG Active from Otto Bock and SPL, the control of knee joint is position sensor activated. The Free Walk, UTX, and Full Stride/ Safety Stride are ankle activated. According to cost, size, weight, or poor functionality, some of these designs have not led to clinical and commercial production, and development was based on mechanical and electromechanical mechanisms. New technologies can, however, be used to improve function of SCKAFOs; for instance, the use of actuators and sensors in lower limb orthoses have introduced new capabilities for adaptive control in SCOs.22,32,33 The selected studies are not analyzed according to the PEDro scale. This point was the main limitation of this study. The studies’ flaws included lack of randomization procedures, lack of control group, no masking of examiners and patients, and also there was lack of similarity among groups. These more recent studies have not substantially improved the quality of the research. There is a continuing need for high-quality experimental studies in this area. Future studies should therefore include the following: •• A study includes meta-analyses to produce improved and more reliable conclusions according to speed, cadence, pelvic obliquity, and step length; •• A comparison between the different types of SCKAFOs; •• A comparison of SCOs and locked KAFOs in their effect on energy consumption and endurance of walking in KAFO users to add more clarification on the effect of this type of orthosis in the rehabilitation of walking; •• The design and construction of more advanced SCOs to further improve structural characteristics of orthosis in KAFO users is recommended; •• The design and construction of more advanced powered SCOs as future designs of orthosis for use in rehabilitation of walking in KAFO users;
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
12
Prosthetics and Orthotics International
•• An investigation into the effect of gait training with SCOs on walking parameters in future designs of studies; •• An investigation into the effect of SCOs on COM displacement and stability in quiet standing; •• Although cosmesis was not evaluated in using SCOs on KAFO users, consideration should be given to improve cosmesis of walking when KAFO users wear this type of orthoses; •• The effect of SCOs on quality-of-life measures and social participation compared to KAFOs.
Conclusion SCKAFOs have been shown to support the knee joint during stance phase and provide free knee movement during swing phase successfully in all the walking studies analyzed.15 SCKAFO designs have provided improved gait kinematics for KAFO users. Using SCOs has been shown to provide improvement in pelvic obliquity and vertical and lateral displacement during walking. Despite the advantages of wearing a SCO, this type of orthosis has not demonstrated a significant improvement in producing decreased energy consumption.8,13 Lower walking speeds have been reported when using SCOs compared to a locked KAFO. Development of new design of SCO that provides more normal patterns of walking is required in this field. To improve walking, additional gait training and accommodation periods are needed before walking with SCOs by KAFO users. Author contribution All authors contributed equally in the preparation of this manuscript.
Declaration of conflicting interests The authors did not have any conflicts of interest with regard to the study presented in this article.
Funding We thank the Iran National Science Foundation for financial support (grant number 92001422) for this research.
References 1. Bernhardt KA, Irby SE and Kaufman KR. Consumer opinions of a stance control knee orthosis. Prosthet Orthot Int 2006; 30(3): 246–256. 2. Irby SE, Bernhardt KA and Kaufman KR. Gait changes over time in stance control orthosis users. Prosthet Orthot Int 2007; 31(4): 353–361. 3. McMillan AG, Kendrick K, Michael JW, et al. Preliminary evidence for effectiveness of a stance control orthosis. J Prosthet Orthot 2004; 16(1): 6–13. 4. Kepple TM, Siegel KL and Stanhope SJ. Relative contributions of the lower extremity joint moments to forward
progression and support during gait. Gait Posture 1997; 6(1): 1–8. 5. Peethambaran A. The relationship between performance, satisfaction, and well being for patients using anterior and posterior design knee-ankle-foot-orthosis. J Prosthet Orthot 2000; 12(1): 33–45. 6. Sulzer JS, Gordon KE, Dhaher YY, et al. Preswing knee flexion assistance is coupled with hip abduction in people with stiff-knee gait after stroke. Stroke 2010; 41(8): 1709–1714. 7. Lemaire ED, Goudreau L, Yakimovich T, et al. Angularvelocity control approach for stance-control orthoses. IEEE Trans Neural Syst Rehabil Eng 2009; 17(5): 497–503. 8. Zissimopoulos A, Fatone S and Gard SA. Biomechanical and energetic effects of a stance-control orthotic knee joint. J Rehabil Res Dev 2007; 44(4): 503–513. 9. Yakimovich T, Kofman J and Lemaire E (eds). Design, construction and evaluation of an electromechanical stancecontrol knee-ankle-foot orthosis. In: 2005 IEEE-EMBS 2005 27th annual international conference of the engineering in medicine and biology society, Shanghai, China, 1–4 September 2005. New York: IEEE. 10. Rasmussen AA, Smith KM and Damiano DL. Biomechanical evaluation of the combination of bilateral stance-control knee-ankle-foot orthoses and a reciprocating gait orthosis in an adult with a spinal cord injury. J Prosthet Orthot 2007; 19(2): 42–47. 11. Irby SE, Bernhardt KA and Kaufman KR. Gait of stance control orthosis users: the dynamic knee brace system. Prosthet Orthot Int 2005; 29(3): 269–282. 12. Davis PC, Bach TM and Pereira DM. The effect of stance control orthoses on gait characteristics and energy expenditure in knee-ankle-foot orthosis users. Prosthet Orthot Int 2010; 34(2): 206–215. 13. Hebert JS and Liggins AB. Gait evaluation of an automatic stance-control knee orthosis in a patient with postpoliomyelitis. Arch Phys Med Rehabil 2005; 86(8): 1676–1680. 14. Yakimovich T, Lemaire ED and Kofman J (eds). Gait evaluation of a new electromechanical stance-control knee-anklefoot orthosis. In: 2006 EMBS’06 28th annual international conference of the IEEE engineering in medicine and biology society, New York, 30 August–3 September 2006. New York: IEEE. 15. Yakimovich T, Lemaire ED and Kofman J. Engineering design review of stance-control knee-ankle-foot orthoses. J Rehabil Res Dev 2009; 46(2): 257–267. 16. Arazpour M, Ahmadi F, Bani MA, et al. Gait evaluation of new powered knee-ankle-foot orthosis in able-bodied persons: a pilot study. Prosthet Orthot Int. Epub ahead of print 9 May 2013. DOI: 10.1177/0309364613486917. 17. Arazpour M, Chitsazan A, Bani MA, et al. The effect of a knee ankle foot orthosis incorporating an active knee mechanism on gait of a person with poliomyelitis. Prosthet Orthot Int 2013; 37: 411–414. 18. To CS, Kobetic R, Bulea TC, et al. Sensor-based stance control with orthosis and functional neuromuscular stimulation for walking after spinal cord injury. J Prosthet Orthot 2012; 24(3): 124–132. 19. Bernhardt K, Oh T and Kaufman K. Stance control orthosis trial in patients with inclusion body myositis. Prosthet Orthot Int 2011; 35(1): 39–44.
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
13
Rafiaei et al. 20. Yakimovich T, Lemaire ED and Kofman J. Preliminary kinematic evaluation of a new stance-control knee-ankle-foot orthosis. Clin Biomech 2006; 21(10): 1081–1089. 21. Hwang S, Kang S, Cho K, et al. Biomechanical effect of electromechanical knee-ankle-foot-orthosis on knee joint control in patients with poliomyelitis. Med Biol Eng Comput 2008; 46(6): 541–549. 22. Ferris DP, Gordon KE, Sawicki GS, et al. An improved powered ankle-foot orthosis using proportional myoelectric control. Gait Posture 2006; 23(4): 425–428. 23. Tokuhara Y, Kameyama O, Kubota T, et al. Biomechanical study of gait using an intelligent brace. J Orthop Sci 2000; 5(4): 342–348. 24. Raftopoulos DD, Armstrong CW, Poulos L, et al. A novel design of a knee-ankle-foot orthosis and its evaluation. In: ASME Advances in Bioengineering Conference, Anaheim, CA, 1986, pp.128–129. 25. Otto Bock. E-MAG active coding justification. Available at: www.ottobock.com 26. Weddendorf BC. Automatic locking orthotic knee device. Patent US 5267950 A, 1993.
27. Kofman J, Allard P, Duhaime M, et al. A functional kneeankle orthosis for Duchenne muscular dystrophy patients using a spring-loaded knee joint mechanism. Orthop Tech 1985; 6(85): 403–407. 28. Harris AI. Automatically releasing knee brace. Patent US 4632096 A, 1986. 29. Goudsmit JA and Nijenbanning G. Gravity operated locking hinge. Patent US 6979304 B2, 2005. 30. Harrison R, Lemaire E, Jeffreys Y, et al. Design and pilot testing of an orthotic stance-phase control knee joint. Orthop Tech 2001; 111: 2–4. 31. Myers N. Releasable conical roller-clutch for knee brace. New York: NASA Tech Briefs, 2002, p. 56. 32. Moreno JC, Brunetti F, Rocon E, et al. Immediate effects of a controllable knee ankle foot orthosis for functional compensation of gait in patients with proximal leg weakness. Med Biol Eng Comput 2008; 46(1): 43–53. 33. Blaya JA and Herr H. Adaptive control of a variable-impedance ankle-foot orthosis to assist drop-foot gait. IEEE Trans Neural Syst Rehabil Eng 2004; 12(1): 24–31.
Downloaded from poi.sagepub.com at The University of Iowa Libraries on June 16, 2015
