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Pediatric Physical Therapy:
doi: 10.1097/PEP.0b013e318206eefa
Research Article

Impact of Enhanced Sensory Input on Treadmill Step Frequency: Infants Born With Myelomeningocele

Pantall, Annette PhD; Teulier, Caroline PhD; Smith, Beth A PT, PhD; Moerchen, Victoria PT, PhD; Ulrich, Beverly D. PhD

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Author Information

Developmental Neuromotor Control Laboratory, School of Kinesiology, University of Michigan, Ann Arbor, Michigan (Drs Pantall and Ulrich); Department of Physical Education and Sport Sciences, University of Limerick, Limerick, Ireland (Dr Teulier); Balance Disorders Laboratory, Department of Neurology, Oregon Health & Science University, Portland, Oregon (Dr Smith); and Pediatric Neuromotor Laboratory, Department of Human Movement Sciences, University of Wisconsin-Milwaukee, Milwaukee, Wisconsin (Dr Moerchen).

Correspondence: Annette Pantall, PhD, Developmental Neuromotor Control Laboratory, CCRB 4740, 401 Washtenaw Avenue, Ann Arbor, MI 48109 ().

Grant Support: Funding for this study was received from NIH/NICHD, RO1HD047567 awarded to Dr Ulrich.

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Abstract

Purpose: To determine the effect of enhanced sensory input on the step frequency of infants with myelomeningocele (MMC) when supported on a motorized treadmill.

Methods: Twenty-seven infants aged 2 to 10 months with MMC lesions at, or caudal to, L1 participated. We supported infants upright on the treadmill for 2 sets of 6 trials, each 30 seconds long. Enhanced sensory inputs within each set were presented in random order and included baseline, visual flow, unloading, weights, Velcro, and friction.

Results: Overall friction and visual flow significantly increased step rate, particularly for the older subjects. Friction and Velcro increased stance-phase duration. Enhanced sensory input had minimal effect on leg activity when infants were not stepping.

Conclusions: Increased friction via Dycem and enhancing visual flow via a checkerboard pattern on the treadmill belt appear to be more effective than the traditional smooth black belt surface for eliciting stepping patterns in infants with MMC.

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INTRODUCTION

Myelomeningocele (MMC) is the most common neural tube defect in the United States.1 Although the incidence of neural tube defects has decreased considerably in the last decade with the introduction of folic acid and improved prenatal care, approximately 1500 to 2000 of 4 million live births still present with spina bifida.2 The physical health–related quality of life for individuals with MMC remains significantly lower compared with individuals with typical development (TD), particularly for children who are not ambulatory.3

Whereas spinal cord lesions emerge very early in gestation, physical stimuli also surround the embryo and fetus, and during this period, babies with MMC move as frequently as those with TD.4 This may be because they are stimulated by the movement of the surrounding fluid systems, sporadic uterine contractions, or maternal motor activity.5 The neonate enters a world with less-continuous extrinsic motor stimulation, which may partially account for the diminished movements observed in infants with MMC during the first weeks of life.6 Recovery from spinal surgery, in addition to possible shunt surgery, will also contribute to reduced movement in the newborn with MMC. In addition, greater muscle force is required for all neonates to generate antigravity movements since they no longer have the advantage of buoyancy provided by amniotic fluids, but this is particularly taxing for babies with MMC. Development of the control of the lower limbs is also difficult, given that most lesions occur in the lumbar and sacral regions from which nerves arise that innervate the pelvis and legs. Infants with MMC who develop locomotor skills begin to walk on an average 2 years later than infants with TD.7 The presence of clubfeet, dislocated or subluxed hips, and muscle contracture will further impede the onset of ambulation. Approximately 20% of infants with a high lumbar-level lesion, 80% of infants with a low lumbar-level lesion, and more than 90% of infants with a sacral-level lesion achieve independent walking.7,8 In addition to lesion level, spasticity, poor balance, and the number of shunt revisions add to a poor prognosis for independent walking.9,10 The kinematics of gait in children with MMC differs from that of children with TD. For example, children with MMC show more trunk rotation, anterior-pelvic tilt, and increased pelvic movements.11 The majority of ambulatory children with MMC walk with aids; many also lose the ability to walk or choose not to walk independently during late childhood.8 Health risks are also associated with reduced ambulation and gait problems, such as lower physical activity and increased risk for obesity.3,11–16

Improving the activity and gait outcomes for children born with MMC depends on creating a strong foundation of motor strength and control of pelvis and legs. Currently, there is no general agreement on the best management of infants with MMC, unlike traumatic spinal cord injuries. For such cases, accepted practice is that gait therapy is initiated as quickly as possible after surgical repair to facilitate recovery of damaged and development of new neural pathways.17 Early introduction of rehabilitation provides a better prognosis for independent ambulation for adults with spinal cord injury.17 Whereas the mechanisms of spinal cord injuries due to trauma versus neural tube defects are different, as are the contexts in which they occur (well-developed neuromuscular system or very early in development), an important process for improving neuromuscular control is the same, the need to move the limbs in as close to functional patterns as possible.18 But how does one engage infants with developmental spinal cord injuries in leg activity that promotes strength and neuromotor control and that is functionally relevant to walking?

One potential option is presented by research conducted with infants with TD and those with Down syndrome in which babies were supported upright on a pediatric treadmill. Practice stepping on the treadmill, 3 to 5 times a week in their homes, resulted in significantly increased step frequency and led to an earlier onset of walking for those with Down syndrome.19,20 We know that new skills and neuromotor control develop through exploration and the repetitive process of moving or acting, and perceiving the consequences of that effort, particularly in a functional context.21 Increasing the frequency of motor output and afferent input to the nervous system stimulates the development of new networks through the growth of dendritic connections, changes in sensitivity of neural membranes, and alterations in neurotransmitters.22–24 In infants, neural plasticity is maximal, and therefore, early therapeutic intervention is imperative to tap this feature of neuroplasticity.25,26 Studies indicate that lower motor neurons caudal to the lesion are indeed functional and hence have the potential to respond to increased afferent input, as Geerdink et al27 demonstrated when lumbar magnetic stimulation was applied to segments caudal to the lesion. However, the same authors reported that transcranial stimulation did not produce any discernible motor activity.27 Stark and Baker28 theorized that there were different levels of neurological functionality of spinal cord segments caudal to the lesion, ranging from a normal cord, a partially functioning cord, an isolated functioning cord to a functionless cord.28 An added impetus to commence treatment early is that muscle cells have the greatest potential to hypertrophy at a young age when protein accretion rates are highest.29

Infants with MMC exhibit less-spontaneous movement than infants with TD, resulting in less opportunity than their peers with TD to develop organized motor patterns, such as those needed for walking.30 However, previously we demonstrated that infants with MMC will respond to being supported on a motorized treadmill by producing steps, although at a lower rate than that performed by infants with TD.31 This activity can, ultimately, be tested for its capacity to assist babies with MMC in building the strength and control needed to walk. The use of a treadmill to promote the stepping response in infants may present an early therapeutic intervention, exploiting the high degree of neuroplasticity previously described. But, to do so, we must be confident that the context optimizes the potential for babies to improve. Ulrich et al32 showed that modifications made to the baseline treadmill context could significantly increase step frequency in infants with Down syndrome, if presented during periods when stepping on the treadmill was low or unstable. Here, we followed that strategy, testing infants with MMC at chronological ages during which their treadmill-stepping responses were relatively low. Furthermore, our modifications targeted sensory systems particularly relevant to this specific population, tapping into their existing capacities, enhancing the input to sensory systems that are compromised, and attempting to maintain the sole of the foot in contact with the treadmill belt to increase the sensation of motion.

Our purpose in this study was to determine whether enhancing the sensory input to infants with MMC would increase their step frequency over baseline. The specific enhancements we used were as follows: (1) visual flow; (2) abrupt unloading of ankle and hip joints in stance; (3) increasing mass—increased input to pressure receptors in the foot; (4) Velcro sock—increased time in stance; and (5) friction (Dycem; Dycem ltd, Bristol, UK)—during stance.

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METHODS

Participants

We enrolled infants with MMC at, or caudal to, the level of L1. Eleven were aged 2 to 5 months corrected age (CA) and 16 were aged 7 to 10 months CA. We chose these 2 age groups to represent distinct periods during the first year related to the development of motor patterns. The 2- to 5-month period is when milestones for upper-body control are more commonly achieved and the 7- to 10-month period tends to include increasing numbers of trunk, pelvis, and lower-body control behaviors.33 We excluded infants who had neuromotor abnormalities other than those associated with MMC (eg, Arnold Chiari II, hydrocephalus) or who had a gestational age at birth less than 28 weeks. We recruited infants through fliers and spina bifida clinics in hospitals in southeast Michigan, northeast Ohio, and southeast Wisconsin. Approval for the study was granted through the institutional review board at the University of Michigan. Parents provided written informed consent for their infants to participate in this study and completed a medical status and history survey (including shunt status, level of spinal fusion surgery, and subsequent surgeries). Table 1 presents participant characteristics.

Table 1
Table 1
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Procedure

We conducted the testing in the developmental neuromotor control laboratory (44%), or to increase sample diversity and numbers, we accommodated families by offering to perform all testing in families' homes (56%). To prepare infants for testing, we removed clothing and placed reflective markers (8-mm diameter) over the iliac crest, greater trochanter, lateral knee-joint line, lateral malleolus, and ventral surface of the third metatarsophalangeal joint of the right lower extremity. We positioned bipolar surface electrodes over the muscle bellies of the lateral gastrocnemius/soleus, tibialis anterior, quadriceps femoris, and lateral hamstring muscles on both legs. We placed a ground electrode over the right patella. We recorded electromyography signals at 1000 Hz via 8 channels of a Myosystem 1400A unit (Noraxon Inc, Scottsdale, AZ).

The custom-designed treadmill (Carlin's Creations, Sturgis, MI) was 18-cm high, 42-cm wide, and 82-cm long, and we placed it on top of a table 73-cm high. We used 2 digital camcorders (Panasonic PV-GS 35; Panasonic, Osaka, Japan) recording at 60 Hz to document the position of the infants' lower limbs. We positioned camcorders on tripods lateral to the right side of the baby, the optical axes forming an angle of 70o to 90o. We calibrated the camcorders before testing with a small calibration frame (Peak Motus; Vicon, OMG plc, Oxford, UK) and synchronized them with a signal. We also used the same signal to synchronize the electromyography with the camcorders.

We manually held infants upright so that their feet rested on the belt of the treadmill in a partial body-weight-supported position for twelve 30-second trials. The treadmill testing lasted a total of 6 minutes, with rest intervals between trials. Some of the weight of the infants was supported by the tester, thereby subjecting the infants' lower limbs to varying amounts of pressure because of their individual differences in weight acceptance and degree of inward or outward foot rotation (eg, clubfoot). The tester observed the foot position of the infant and increased support if there was prolonged lateral contact of the foot with the treadmill surface, which was observed to occur in 48% of infants with clubfoot and 11% of those with structurally normal feet. Trials were presented in 2 sets of the 6 conditions; within each set, conditions were presented in random order. We set the belt speed at 0.16 m/s because it proved to be an optimal speed in our previous longitudinal study of treadmill stepping in infants with MMC.31 Conditions were as follows: (1) baseline—smooth black belt surface; (2) visual flow—black and white checker-board–patterned belt used to elicit visual flow sensation; this condition was selected because research shows that infants often respond to visual flow that suggests movement by initiating trunk or limb movements34; (3) unloading—infant was held near the end of the treadmill, so the child's feet abruptly dropped off the surface, rapidly unloading the hip and ankle joints35; biomechanists propose that unloading at the hip and ankle activates joint receptors that cause motor units to fire and initiate the swing phase of stepping36; (4) weights—attached to the infant's shanks, tailored to their individual weight, and equal to approximately 50% of shank mass; to enhance the normal contribution of passive pendular motion in swing phase and to increase the input to pressure receptors in the foot during stance phase37; (5) Velcro—infants wore socks with strips of Velcro sewn on, and the treadmill was covered with a felt-like material; Velcro maintains the infant's foot in contact with the treadmill surface for a longer period during which the extensor muscles are expected to be active; greater contraction of the flexor muscles is then necessary to draw the foot away from the treadmill; Ulrich et al32 demonstrated that Velcro resulted in the greatest number of steps for infants with Down syndrome; (6) friction—belt made of Dycem (a nonslip surface); the goal was to prevent the infants' feet from sliding on the surface and not moving backward with the belt, as we observed in previous studies when infants did not support much of their own weight.

Subsequent to treadmill training, we took anthropometric measurements, including body length, weight, greater trochanter to lateral malleolus length, thigh length, foot length, thigh circumference, and leg circumference. The purpose of these measurements was to determine whether some were a factor in the stepping response and also for normalization and further analysis in future studies. We recorded the aspects of the infant's medical history, including lesion level, surgeries, and musculoskeletal conditions. We assessed concurrent motor skill–development level by administering the motor items from the Bayley Scales of Infant Development III (BSID III).38 Table 1 presents medical and anthropometric characteristics of the participants.

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Data Reduction

We behavior coded the videotapes to determine stepping patterns. Frame-by-frame analysis of each trial was made with Peak Motus Version 8 software. The coders (n = 4) had to achieve a coefficient of agreement of 0.85 (interobserver reliability coefficient, κ) through comparison of their work with that of previously validated coders for the same set of trials by using training tapes. We extracted the following parameters from the videos.

Interlimb stepping patterns: Four types of steps: alternating (a step preceded or followed by a step of the contralateral limb with overlap), single (not preceded or followed by a step of the contralateral limb), parallel (both legs swing forward simultaneously), and double (“stutter” step within a sequence of alternating steps).

Step rate: Total number of steps per trial divided by the trial duration in seconds.

Step events: Video frame number for toe off, touch down, and end of stance for alternating steps and single steps. We normalized the total cycle, stance, and swing durations calculated from these events by dividing the parameters by (lo/go)1/2, where lo is the segment length and go is standard gravity, 9.81 m/s2.39

Leg activity rate (LAR): We coded leg activity during frames in which no steps were present, every 5 seconds with dichotomous values: 0 = no leg movement and 1 = clear leg movement. We divided the total points accumulated by the number of frames and multiplied the index by 60 to obtain the LAR.

Ponderal Index (PI): Indicator of body proportion commonly calculated for infants.40 We calculated the PI by using the formula, PI = (weight (g) / length (cm)3) × 100.

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Data Analyses

We used SAS version 9.2 (SAS Inc, Cary, NC) for statistical analyses. We applied the mixed-model procedure to conduct analyses of variance (ANOVA) with repeated measures. We performed pairwise comparison tests to determine significant differences between parameters. We set statistical significance a priori at α < .10 because of the high performance variability in this population; the wide range in ages, lesion levels, and shunt surgery; cerebellar malformations; and orthopedic complications. We have presented statistics mainly for those results that achieved statistical significance and on occasion for those without statistical significance, where we consider this lack of significance to be of interest. The lesion groupings were low-level lesions (L5 and caudally), middle-lesion level (L4), and high-level lesions (L1-L3). The rationale for these divisions is based on the likelihood of the infants becoming community walkers into adulthood.31,41

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RESULTS

We organized our results into 2 sections. In part 1, we provide a simple overview of the overall motor development status of this sample and the role of PI and age in days in step and leg movement rates. We list the values of the Bayley raw motor score and PI in Table 1. In part 2, we focus on the main questions of interest, the effect of enhanced sensory input on step rate and quality, and leg activity.

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Part 1: Developmental Overview
Bayley Motor Scale

We used the raw total scores (number of items passed) to reflect each infant's motor performance on the Bayley Scale. Overall, the motor scores increased significantly with age as shown in Figure 1, with a steeper increase for infants with a low-level lesion compared with those with a high-level lesion. While the mid-level lesion sample was too small and narrowly defined by age to conduct a regression analysis, Figure 1 suggests less-clear change in motor outcomes related to age for this subgroup. The increase in Bayley score with age was less pronounced than that we previously observed for infants with TD who also displayed a higher R2 value. We divided the Bayley score into 5 levels (10-19, 20-29, 30-39, 40-49, and 50-59) and applied a 5 (Bayley score) × 6 (condition) ANOVA to examine the effect of Bayley score and condition on total steps produced with repeated measures on condition. We found no significant relation between concurrent motor skill performance and step response reflected in the Bayley scores.

Figure 1
Figure 1
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PI and Step Rate, LAR

The relation between PI and overall step rate is illustrated in Figure 2. We observed a trend for step frequency to decrease as PI increased, but this was true primarily for infants with middle- and low-level lesions, with no obvious effect for those with high-level lesions. We observed a decrease in LAR as PI increased for infants with a low-level lesion (Figure 3). However, for infants with middle- and high-level lesions, the opposite trend emerged, LAR increased as PI increased.

Figure 2
Figure 2
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Figure 3
Figure 3
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Step Types Produced

Both the younger and older age groups generated all 4 types of stepping patterns (Figures 4A and B). However, for younger infants, the predominant step type was single, followed by parallel, alternating, and double. With age, alternating steps more than doubled in percentage of all steps, as did parallel steps, while single steps reduced by half and double steps nearly disappeared.

Figure 4
Figure 4
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Part 2: Context Effect on Step Frequency, Temporal Parameters, and LAR

Because there were, particularly for the younger infants, only a small number of steps in each of the 4 step categories for each of the conditions, we pooled the step types together to increase the power of subsequent statistical tests.

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Step Frequency
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Absolute Step Rate

To examine the effect of age, lesion level, and conditions on total steps produced, we used a 2 (age) × 3 (lesion) × 6 (condition) ANOVA for repeated measures on condition. We found a significant age effect (F1,23 = 6.76, P = .016), a significant lesion level effect (F2,23 = 3.13, P = .063), a significant condition effect (F5,115 = 2.38, P = .043), a significant age × condition interaction (F5,115 = 3.13, P = .011), and a lesion × condition interaction (F10,115 = 1.99, P = .040). Figure 5 plots step rate by age and condition, within each lesion level, A (low), B (middle), and C (high). These figures illustrate that the significant age × condition effect reflected that while conditions effectively increased step responses over baseline, the level of effect varied by age, showing a greater effect for older infants than younger ones. Furthermore, the effect of conditions presented was different across lesion levels, being greater for low than high lesion levels. For those in the middle-lesion group, no conditions showed clear improvement over baseline, though the age effect could not be examined because our sample included infants aged only 7 to 10 months.

Figure 5
Figure 5
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First, to examine more closely the age × conditions interaction, we compared the most effective conditions for younger babies with those of older babies. For younger infants, friction produced the greatest increase in step rate (0.16 steps per second ± 0.18) compared with the baseline condition (0.11 steps per second ± 0.10), although the paired comparison post hoc did not reach statistical significance. For older babies, visual flow elicited the most steps (0.26 steps per second ± 0.23) compared with the baseline condition (0.19 steps per second ± 0.15), but both visual flow and friction achieved statistical significance: visual flow (df = 75, t = −2.37, P = .021) and friction (df = 75, t = −1.92, P = .058) compared with the baseline for the older group.

To examine the lesion level × condition interaction, we began by conducting a post hoc 2 (age) × 6 (condition) ANOVA with repeated measures on condition for the low-level lesion group. We did this because, as Figure 5A illustrates, this subgroup had both the most participants (and thus statistical power) and the largest overall step response. Results showed a significant condition effect (F5,55 = 2.21, P = .066), age effect (F1,11 = 5.87, P = .034), and an age × condition interaction (F5,55 = 2.68, P = .031). Figure 5A suggests that whereas for older infants, all enhanced sensory conditions produced more steps than baseline, for younger infants, only friction seemed to elicit more steps. Post hoc–paired comparison tests among conditions showed statistically significant results for visual flow (df = 60, t = −1.71, P = .092) and friction (df = 60, t = −2.81, P = .007) compared with baseline.

Figure 5B suggests that for infants in the middle lesion level (L4), no enhanced sensory conditions improved their step frequency, though we observed a statistically significant decrease in responses for unloading (df = 25, t = 2.35, P = .027) and weights (df = 25, t = 2.16, P = .041) compared with baseline.

Infants with high-level lesions responded more to friction (0.10 steps per second ± 0.05) compared with the baseline (0.09 steps per second ± 0.05), though visual flow also showed a slightly higher mean response compared with the baseline for only the older infants. However, these changes did not achieve statistical significance.

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Normalized Step Rate

The variability in mean step rate across infants was high, ranging from 0.03 to 0.67 steps per second. Therefore, we normalized step rates for each infant to his/her own mean (across conditions). Normalized responses (see Figure 6) show more clearly that, generally, visual flow and friction were the conditions most effective in eliciting steps when infants with MMC were supported on a pediatric treadmill. We plotted normalized responses as a function of age and lesion level. For the youngest infants, only friction increased step rate over baseline. For those with middle-level lesions, no conditions significantly increased step response compared with baseline; unloading and weights, in particular, significantly reduced step responses.

Figure 6
Figure 6
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Step Cycle Effects

To determine the effect of conditions on step cycle duration, we used a 2 (age) × 3 (lesion) × 6 (condition) ANOVA, with repeated measures on condition. Cycle duration, normalized to leg length, was the dependent variable. We found significant age (F1,6 = 6.77, P = .041) and condition (F5,15 = 4.83 P = .008) effects. Figure 7 shows that, with age, normalized cycle durations reduced across all conditions. The absolute cycle were higher in infants with longer legs, and they demonstrated increased strength; when normalized to leg length, the cycle duration decreased. The effect of condition was less clear-cut, though overall, Velcro tended to increase cycle duration, while unloading tended to decrease cycle duration. A 2 (age) × 3 (lesion) × 6 (condition) ANOVA with repeated measures on condition for swing- and stance-phase durations resulted in statistically significant effects for stance-phase durations for condition (F5,15 = 3.65 P = .023).

Figure 7
Figure 7
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LAR

Figure 8 illustrates the very-high variability across infants in LAR to all conditions and across age groups and lesion levels. When tested in a 2 (age) × 3 (lesion) × 6 (condition) ANOVA for repeated measures on condition with LAR as the dependent variable, we obtained only a significant age effect (F1,23 = 4.35, P = .048). Older infants produced more leg activity when not stepping than younger infants. Nevertheless, the comparison to Figure 5 shows some parallels that may guide selection of conditions that elicit maximal action. For example, Figure 8A suggests that for older infants with low-level lesions, visual flow and friction seem to work better than baseline. For young infants, this effect is limited to friction. All conditions reduced the response compared with baseline for infants with middle-level lesions, with unloading and weights showing the most marked effects. For infants with high-level lesions, in both age groups, little improvement was evident across enhanced sensory conditions, though notably, none of these conditions appeared to reduce leg activity compared with baseline. We found for the infant group as a whole that the condition of unloading decreased LAR from 5.88 per seconds ± 6.40 at baseline to 3.65 per seconds ± 3.79. However, no condition produced a marked increase in LAR.

Figure 8
Figure 8
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DISCUSSION

Our purpose in this experiment was to determine whether we could enable infants with MMC to increase their step rate when supported on a pediatric treadmill by enhancing the sensory input during test trials over that of typical treadmill belt conditions. Overall, our results show that we can do so, and that of the 5 sensory enhancements we created, friction and visual flow worked optimally to increase step frequency.

We chose to increase friction by covering the treadmill belt with Dycem to avoid a response observed in some infants with MMC in our previous work.31 That is, if they accepted minimal weight on their feet, or foot contact was on the side or ball of the foot, their feet moved backward with the belt only a small amount, and steps were less likely to result. We used Dycem to reduce slippage. In this context, it increased the opportunity for the treadmill dynamics to be effective. When the foot touched down, it created a more stable base for greater weight acceptance on the foot and kept the foot in contact longer. When leg joints and muscles are extended and then unloaded at the end of stance, passive pendular dynamics and viscoelastic muscle properties can assist with forward motion and joint flexion.

Visual flow has been shown by numerous researchers to elicit motor responses in infants.34,42,43 We chose this condition to access a sensory system that was not diminished by the neural tube defect and thus could, and did, facilitate infants' initiation of body movement. However, this condition was less effective for younger babies than for older babies. This might have been because younger babies failed either to “perceive” the motion implied or simply failed to attend to it. Although we did not specifically assess babies' looking time, Moerchen and Saeed44 showed that babies with TD who spent more time looking directly toward the belt in this context, rather than looking away or closing their eyes, stepped more frequently.

Like friction, Velcro also helped to maintain greater foot contact after touchdown, and this was the condition Ulrich et al32 found to be optimal for infants with Down syndrome. The difference here seemed to be the strength required to pull their feet off the belt, which was particularly reduced for young infants with MMC and those with high lesion levels. Similarly, adding weights might have increased proprioceptive input, but these infants simply did not have sufficient strength to overcome this added mass.

In addition, the responses that we observed to friction and visual flow were affected by age and lesion levels. Infants who were in the older group stepped more frequently, and responses increased as group lesion level lowered. In fact, those infants in the older age group with the lowest lesion levels responded more to all enhanced sensory conditions than to baseline. The question remains, why was the effect on younger infants and those with higher lesion levels so small? We propose 2 factors. First, these infants responded to baseline with a low number of steps, a finding that we had demonstrated in a previous study.31 These are the most fragile infants of this population, for whom lifting the legs and stepping may be a particularly difficult and energy-demanding response. Thus, expecting any real-time modification that does not reduce the muscle force demands may be unrealistic. First, more effective may be efforts to increase strength before expecting infants to use their muscles and step. Second, our design allowed infants only 30 seconds to adjust to each new test trial, and we moved fairly quickly from one trial to the next. We did this to avoid tiring infants and allow examination of several enhanced sensory conditions, since all data were collected on a single day. Unfortunately, by doing so, we may not have allowed this inherently unstable response to settle into each new sensory enhancement before the trial ended. Future studies should consider examining the most promising conditions by presenting them for longer periods of time and comparing responses of stronger infants, those who generate more extensor force when supported on the treadmill, with those less able to do so. In addition, more than 37% of our infants presented with bilateral clubfeet. These infants made initial contact with the lateral aspect of the foot in 47.2% of cases, which reduced during mid stance. However, even those infants without clubfeet made initial lateral foot contact in 19.6% of their steps, compared with about 8% lateral foot contact for infants with TD with structurally normal feet. The effect of clubfoot on the posture was to reduce the treadmill surface area in contact with the foot in addition to limiting weight bearing through the lower limbs, with the tester subsequently providing more body weight support. This decrease in sensory enhancement in infants with clubfeet may account for the reduction in number of steps elicited overall in infants with MMC.

Interestingly, in this study, we observed an age effect that was only minimally observed toward the end of the first year in our previous longitudinal study.31 We believe that this occurred because in the previous study, only the baseline condition was used. Here, by increasing the opportunities for sensory input to engage the motor system, greater overall stepping emerged with age.

As a group, infants with middle lesion levels differed in several respects from the pattern shown by the lower and higher lesion level groups. They did not increase step frequency in response to any enhanced sensory input conditions, and step frequency diminished during unloading and weight conditions. We do not have a definitive argument for this divergence, but 1 contributing factor may be the very-small subsample size, coupled with its very-high variability. The middle lesion level group was represented by half as many participants as the other 2 groups and comprised only 6 infants. Individual profiles showed that 3 of the infants in this group showed means for visual flow and friction that were equal to or higher than their baseline means. For only 2 infants in this group did the baseline condition produce the most steps, and for only 1 of them was that number more than 25% higher. Overall, in such a small sample, these less-common response patterns can overwhelm a group mean. A larger sample of infants with an L4 lesion level diagnosis will be needed to examine this subsample behavior more definitively.

We did not observe a significant increase in leg activity beyond steps as a function of enhanced sensory input, although the means for friction and visual flow were a bit higher than other conditions, paralleling the more significant outcomes that we found for step rate under these conditions. Previously, we showed that when infants with MMC were supported upright on a moving belt that was like our baseline belt in this study, infants moved their legs more even when not stepping than they did when supported upright on the treadmill and the belt did not move. The explanation for this lack of increase is not obvious; although perhaps when increased sensory flow reached a sufficient level to stimulate activity, this presented as a patterned motor response, a step, rather than random leg activity.

As we observed previously, the step patterns of infants with MMC produced at younger ages tended to be dominated by single steps and these decreased with age, while the proportion of alternating steps increased with age.31 The amount of increase in alternating steps was less than expected from previous work, to about 20% here and 40% previously. We propose that the increase in response frequency may first come in the form of the simplest patterns, single, or parallel steps and require greater control and practice to more consistently respond with alternating steps.

Our results also showed a negative correlation between PI and step rate for the low- and middle-level lesions. A higher PI indicates increased adipose tissue for body size. Luo et al45 also reported a negative correlation between the number of alternating steps and the percentage of total body fat, as determined by skinfold thickness. Our interpretation for our findings is that infants with increased adipose tissue per body size have more difficulty initiating step cycles, because of the relatively heavier lower limb without concomitantly greater muscle force. For infants with high lesion levels who stepped significantly less, we observed no effects of PI.

We found no statistical relation between infants' step frequency and their scores on the BSID. This may be because the BSID is heavily weighted toward upper limb and trunk motor skills, and thus, may be insufficiently sensitive to neuromotor delays primarily occurring in the lower limbs. Perhaps, a scale such as the Alberta Infant Motor Scale46 would have identified a relation. Alternatively, the capacity for the dynamics of the treadmill to assist and elicit stepping patterns may occur before babies are able independently to create the functional motor patterns of sitting, crawling, and cruising. Previous studies provide limited insights. For example, Thelen and Ulrich47 found no relation between BSID scores and the onset of improved treadmill stepping in infants with TD, whereas Ulrich et al19 found for babies with Down syndrome that specific BSID items were associated with improved treadmill stepping but not an overall score. In future studies, we will investigate this issue further by employing a more sensitive set of items to reflect concurrent levels of lower limb function (skill).

Although our results show that enhancing sensory input can increase motor output and that infants with lower-level lesions and older infants responded to this input more than young infants and the ones with higher lesions; the variability among infants must also be emphasized. Scatterplots and standard deviations illustrate this, as does the very-high variability among infants in step rate. These reflect that behavioral outcomes are influenced by many factors, including other complications due to this neural tube defect, such as clubfeet (reduced contact area), hydrocephalus, or hip subluxation or dislocation, degree of damage to ascending and descending neural tracts, level of medical care and physical therapy, and family support networks.

It is important to note that in the future, the possible use of treadmill practice for early intervention for children with MMC would need to be paired with close monitoring of its effect on muscle imbalance around the hips and knees. Infants and children with MMC, especially those with lumbar lesions, are prone to show muscle imbalances in this region. Thus, careful attention to pelvis, hip, and spine alignment would be critical to avoid the potential development of muscle contracture and bony deformities.

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LIMITATIONS

In this study, we presented each enhanced sensory condition for only 30 seconds and moved infants quickly from one context to another. Future studies should examine the effect of longer exposure time to allow infants to adapt to each context. Furthermore, we enrolled only a small number of infants when sorted by age group and lesion levels; the mid-lesion level subgroup included only older infants and half as many in total as the lower and higher lesion level subgroups. Future studies of this nature should increase the sample within subgroups. We utilized the same sensory enhancements for the youngest and oldest infants. Future studies should test whether other modifications to the treadmill context can improve responses for younger infants and those with the highest lesion levels.

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CONCLUSIONS

Our results showed that when supported upright on a pediatric treadmill, infants with MMC produced more steps when the context was modified to enhanced sensory input compared with the baseline condition of a typical smooth black belt. Generally, friction and visual flow elicited a greater number of steps than other conditions, producing increases of 47% and 20%, respectively, compared with baseline. We observed significant individual variability as well. Future studies should investigate the effect of enhancing sensory input by combining friction and visual flow, with opportunities to practice, thus allowing infants to adapt and, perhaps, settle into more stable response patterns.

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ACKNOWLEDGMENTS

We thank the participants and their families for taking part in this study. In addition, we thank the physicians and staff, especially of the University of Michigan Hospital and the Children's Hospital of Michigan Myelomeningocele Care Center at Detroit Medical Centre.

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REFERENCES

1. Bowman RM, Boshnjaku V, McLone DG. The changing incidence of myelomeningocele and its impact on pediatric neurosurgery: a review from the Children's Memorial Hospital. Child Nerv Syst. 2009;25(7):801–806.

2. Spina bifida fact sheet. In: National Institute of Neurological Disorders and Stroke, ed. NIH Publication No. 07-309. Bethesda, MD: NIH; 2007:886–894.

3. Buffart LM, van den Berg-Emonsrita JG, van Meeteren J, Stam JV, Roebroek M. Lifestyle, participation, and health-related quality of life in adolescents and young adults with myelomeningocele. Dev Med Child Neurol. 2009;51(11):886–894.

4. Sival DA, Begeer JH, Staal-Schreinemachers AL, Vos-Niel JM, Beekhuis JR, Prechtl HF. Perinatal motor behaviour and neurological outcome in spina bifida aperta. Early Hum Dev. 1997;50(1):27–37.

5. Reid GM. Sudden infant death syndrome (SIDS): microgravity and inadequate sensory stimulation. Med Hypotheses. 2006;66(5):920–924.

6. Sival DA, van Weerden TW, Vles JS, et al. Neonatal loss of motor function in human spina bifida aperta. Pediatrics. 2004;114(2):427–434.

7. Iborra J, Pages E, Cuxart A. Neurological abnormalities, major orthopaedic deformities and ambulation analysis in a myelomeningocele population in Catalonia (Spain). Spinal Cord. 1999;37(5):351–357.

8. Williams EN, Broughton NS, Menelaus MB. Age-related walking in children with spina bifida. Dev Med Child Neurol. 1999;41(7):446–449.

9. Bartonek Á, Gutierrez EM, Haglund-Ákerlind Y, Saraste H. The influence of spasticity in the lower limb muscles on gait pattern in children with sacral to mid-lumbar myelomeningocele: a gait analysis study. Gait Posture. 2005;22(1):10–25.

10. Bartonek A, Saraste H. Factors influencing ambulation in myelomeningocele: a cross-sectional study. Dev Med Child Neurol. 2001;43(4):253–260.

11. Gutierrez EM, Bartonek Á, Haglund-Ákerlind Y, Saraste H. Characteristic gait kinematics in persons with lumbosacral myelomeningocele. Gait Posture. 2003;18(3):170–177.

12. Schoenmakers MA, de Groot JF, Gorter JW, Hillaert JL, Helders PJ, Takken T. Muscle strength, aerobic capacity and physical activity in independent ambulating children with lumbosacral spina bifida. Disabil Rehabil. 2009;31(4):259–266.

13. Moore CABS, Nejad BBA, Novak RAMS, Dias LSMD. Energy cost of walking in low lumbar myelomeningocele. J Pediatr Orthoped. 2001;21(3):388–391.
14. Asher M, Olson J. Factors affecting the ambulatory status of patients with spina bifida cystica. J Bone Joint Surg. 1983;65(3):533–539.
15. Morrison KM, Atkinson SA, Yusuf S, et al. The Family Atherosclerosis Monitoring in Early Life (FAMILY) study: rationale, design, and baseline data of a study examining the early determinants of atherosclerosis. Am Heart J. 2009;158(4):533–539.

16. Buffart LM, van den Berg-Emons RJ, Burdorf A, Janssen WG, Stam HJ, Roebroeck ME. Cardiovascular disease risk factors and the relationships with physical activity, aerobic fitness, and body fat in adolescents and young adults with myelomeningocele. Arch Phys Med Rehabil. 2008;89(11):2167–2173.

17. Dobkin B, Barbeau H, Deforge D, et al. The evolution of walking-related outcomes over the first 12 weeks of rehabilitation for incomplete traumatic spinal cord injury: the multicenter randomized Spinal Cord Injury Locomotor Trial. Neurorehabil Neural Re. 2007;21(1):25–35.

18. Ulrich B. Opportunities for early intervention based on theory, basic neuroscience, and clinical science. Phys Ther. 2010;90:839–845.

19. Ulrich DA, Ulrich BD, Angulo-Kinzler RM, Yun J. Treadmill training of infants with Down syndrome: evidence-based developmental outcomes. Pediatrics. 2001;108(5):E84.

20. Wu J, Looper J, Ulrich BD, Ulrich DA, Angulo-Barroso RM. Exploring effects of different treadmill interventions on walking onset and gait patterns in infants with Down syndrome. Dev Med Child Neurol. 2007;49(11):839–845.

21. Ulrich BD, Ulrich DA. Spontaneous leg movements of infants with Down syndrome and nondisabled infants. Child Dev. 1995;66(6):1844–1855.

22. Macias M, Nowicka D, Czupryn A, et al. Exercise-induced motor improvement after complete spinal cord transection and its relation to expression of brain-derived neurotrophic factor and presynaptic markers. BMC Neurosci. 2009;10(1):130–145.

23. Scott ALM, Ramer MS. Differential regulation of dendritic plasticity by neurotrophins following deafferentation of the adult spinal cord is independent of p75NTR. Brain Res. 2010;1323:48–58.

24. Gazula V-R, Roberts M, Luzzio C, Jawad AF, Kalb RG. Effects of limb exercise after spinal cord injury on motor neuron dendrite structure. J Compar Neurol. 2004;476(2):130–145.

25. Karmiloff-Smith A, Thomas M. What can developmental disorders tell us about the neurocomputational constraints that shape development? The case of Williams syndrome. Dev Psychopathol. 2003;15(4):969–990.

26. Chiaretti A, Ausili E, Di Rocco C, et al. Neurotrophic factor expression in newborns with myelomeningocele: preliminary data. Eur J Paediatr Neurol. 2008;12(2):113–118.

27. Geerdink N, Pasman JW, Roeleveld N, Rotteveel JJ, Mullaart RA. Responses to lumbar magnetic stimulation in newborns with spina bifida. Pediatr Neurol. 2006;34(2):101–105.

28. Stark GD, Baker GCW. The neurological involvement of the lower limbs in myelomeningocele. Dev Med Child Neurol. 1967;9:359–374.

29. Maltin C, Delday M, Sinclair K, Steven J, Sneddon A. Impact of manipulations of myogenesis in utero on the performance of adult skeletal muscle. Reproduction. 2001;122(3):359–374.

30. Rademacher N, Black DP, Ulrich BD. Early spontaneous leg movements in infants born with and without myelomeningocele. Pediatr Phys Ther. 2008;20(2):137–145.

31. Teulier C, Smith BA, Kubo M, et al. Stepping responses of infants with myelomeningocele when supported on a motorized treadmill. Phys Ther. 2009;89(1):60–72.

32. Ulrich BD, Ulrich DA, Angulo-Kinzler RM. The impact of context manipulations on movement patterns during a transition period. Hum Mov Sci. 1998;17:8–14.

33. World Health Organization Multicentre Growth Reference Study Group. WHO motor development study: windows of achievement for six gross motor development milestones. Acta Paediatr Suppl. 2006;450:8–14.

34. Barbu-Roth M, Anderson DI, Despres A, Provasi J, Cabrol D, Campos JJ. Neonatal stepping in relation to terrestrial optic flow. Child Dev. 2009;80(1):8–14.

35. Ivanenko YP, Grasso R, Macellari V, Lacquaniti F. Control of foot trajectory in human locomotion: role of ground contact forces in simulated reduced gravity. J Neurophysiol. 2002;87(6):3070–3089.

36. Conway BA, Hultborn H, Kiehn O. Proprioceptive input resets central locomotor rhythm in the spinal cat. Exp Brain Res. 1987;68(3):643–656.

37. Yang JF, Gorassini M. Spinal and brain control of human walking: implications for retraining of walking. Neuroscientist. 2006;12(5):379–389.

38. Bayley N. Bayley Scales of Infant and Toddler Development. 3rd ed. San Antonio, TX: Pearson; 2005.

39. Hof AL. Scaling gait data to body size. Gait Posture. 1996;4:480–493.

40. Lehingue L, Remontet L, Munoz MJ, Faber-Krol MC, Mamelle N. Birth Ponderal Index and body mass index reference curves in a large population. Am J Hum Biol. 1998;10:327–340.

41. Forssberg H. Ontogeny of human locomotor control. I. Infant stepping, supported locomotion and transition to independent locomotion. Exp Brain Res. 1985;57(3):480–493.

42. Barbu-Roth M, Trujillo M, Desprès A, et al. 1.1 The coupling between optical flow and neonatal stepping. Gait Posture. 2005;21(Suppl 1):S1.

43. Lejeune L, Anderson DI, Campos JJ, Witherington DC, Uchiyama I, Barbu-Roth M. Responsiveness to terrestrial optic flow in infancy: does locomotor experience play a role? Hum Mov Sci. 2006;25(1):4–17.

44. Moerchen VA, Saeed ME. Visual attention and step responsiveness to visual flow during treadmill stepping in infants with typical development. Infant Beh Dev. In submission.

45. Luo HJ, Chen PS, Hsieh WS, et al. Associations of supported treadmill stepping with walking attainment in preterm and full-term infants. Phys Ther. 2009;89(11):1215–1225.

46. Barbosa VM, Campbell SK, Sheftel D, Singh J, Beligere N. Longitudinal performance of infants with cerebral palsy on the test of infant motor performance and on the Alberta Infant Motor Scale. Phys Occup Ther Pediatr. 2003;23(3):7–29.

47. Thelen E, Ulrich BD. Hidden skills: a dynamic systems analysis of treadmill stepping during the first year. Monogr Soc Res Child. 1991;56(1):1–98.

age factors; ambulation; body weight; child development/physiology; early ambulation; gait disorders/neurologic; infants; lumbar vertebrae; meningomyelocele; motion perception; motor activity; proprioception; treadmill test; weight bearing

© 2011 Lippincott Williams & Wilkins, Inc.

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