Volume 48 Number 5, 2011
Pages 577 — 586
Abstract — Tendon reflexes are widely used in clinics to conveniently evaluate various neurological disorders. This study characterized neuromuscular dynamics of tendon reflexes at the elbow with multiple quantitative measures in both patients with stroke and nondisabled controls. We employed a handheld instrumented hammer to tap the triceps muscle tendon at various elbow flexion angles and measured the tapping force, triceps electromyography, and elbow extension torque to characterize neuromuscular dynamics of tendon reflexes quantitatively in terms of the tendon reflex gain, contraction rate, half relaxation rate, reflex loop delay, and reflex threshold in tapping force. We found that the tendon reflex gain, contraction rate, and half relaxation rate were significantly higher while the reflex threshold was significantly lower across different joint angles in patients with stroke than in nondisabled controls (p < 0.05), indicating hyperactive neurological state and muscle contraction dynamics poststroke. This study presents a convenient and quantitative method to evaluate reflex excitability and muscle contraction dynamics.
Key words: contraction rate, half relaxation rate, neurological disorder, reflex gain, reflex loop delay, reflex threshold, rehabilitation, spasticity, stroke, tendon reflex.
Stroke is the leading cause of adult disability and the third leading cause of death in the United States, with 730,000 strokes occurring each year [1-2]. Spasticity is a complicated clinical symptom, characterized by a velocity-dependent increase in tonic stretch reflexes (muscle tone) with exaggerated tendon jerks, resulting from hyperexcitability of the stretch reflex . Spasticity is a major source of disability in many patients with brain or spinal cord injuries of many different etiologies, including stroke, traumatic spinal cord injury, multiple sclerosis, and cerebral palsy . The hypertonus and reflex hyperexcitability associated with spasticity disrupt the remaining functional use of muscles, impede motion, and may cause severe pain. Prolonged spasticity may be accompanied by structural changes in muscle fibers and connective tissue, which may reduce joint range of motion and lead to clinical contracture. Many therapeutic paradigms, such as antispastic medication [4-5], physical modalities [6-7], botulinum toxin injection [8-9], intrathecal baclofen pumps , and novel surgical techniques , were developed and applied for reducing spasticity and improving function. Even though such techniques can benefit patients, their effects on spasticity have not been well quantified because accurate and convenient measures of hyperactive reflexes that are suitable for clinical practice are lacking .
Mechanisms underlying spasticity are still not clearly understood. The increased resistance to passive movement in a spastic limb can be caused by of nonreflex changes like contracture as well as reflexive changes like hyperactive reflexes [13-14]. Reflex and nonreflex mediated contributions to the increased resistance must be separated to evaluate and understand the mechanisms underlying spasticity. Furthermore, it is not clear whether the hyperactive reflexes associated with spasticity are caused by an increase in tendon reflex gain (Gs)  or a decrease in reflex threshold [16-17]. For assessing the severity of the spastic state and identifying its key characteristics poststroke, evaluating hyperactive reflexes quantitatively in terms of Gs and reflex threshold in people with stroke is important.
The purposes of this study were investigating the mechanisms underlying spasticity in stroke and quantitatively evaluating hyperactive reflexes. Our hypothesis is that hypereflexia and spasticity poststroke are associated with significantly increased Gs, increased contraction rate (Rc), and decreased reflex threshold. We performed the experiment isometrically at the elbow joint to both minimize nonreflex contributions and manifest and characterize hyperactive reflexes accurately.
Ten patients with chronic stroke and elbow impairment (age: 51.9 ± 8.3 yr [mean ± standard deviation], height: 171.3 ± 4.5 cm, weight: 76.6 ± 15.8 kg, 6 male and 4 female) and eleven nondisabled controls with no prior history of neurological disorders (age: 43.1 ± 10.9 yr, height: 171.6 ± 6.6 cm, weight: 66.7 ± 7.3 kg, 10 male and 1 female) participated in the study. We examined each patient with stroke at the beginning of the experiment using the clinical tendon reflex scale ranging from 0 to 4, with 0 = no response, 1 = low average, 2 = average normal, 3 = brisker than average, and 4 = hyperactive and association with clonus. The patients with stroke were not using antispastic medication during the study.
Each subject sat upright with their trunk strapped to the seat backrest and shoulder abducted 80?? and flexed 10?? (Figure 1). We cast and mounted the distal forearm, wrist, and proximal hand onto the distal end of an aluminum beam and mounted the other end of the beam onto a motor shaft through a torque sensor that measured the elbow extension torque. We aligned the elbow flexion-extension axis with the motor shaft and locked the motor at the selected elbow flexion angle during tendon taps, restricting the elbow at an isometric condition.
Experimental setup for evaluating tendon reflexes at elbow joint. Motor is mounted on supporting frame with motor shaft aligned with elbow flexion axis. Torque sensor is mounted between motor shaft and aluminum beam to measure reflex elbow extension torque. Cast is fixed to aluminum beam through coupling. Motor is fixed at selected joint flexion angle to keep elbow at isometric condition. Rubber pad is mounted at most sensitive spot on triceps tendon, which is tapped with instrumented tendon hammer with force sensor mounted at its tip.
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Using a traditional tendon reflex mallet, we located the most sensitive spot on the triceps tendon with the strongest reflex response. We pressed a 10 mm-diameter hemisphere self-adhesive rubber pad onto the triceps tendon at the most sensitive spot. We used an instrumented tendon hammer with a force sensor mounted at its head to tap the rubber pad. The flat impact surface of the instrumented tendon hammer hit the dome-shaped rubber pad, which made the tapping force transmission onto the tendon more accurate and consistent, reducing variations of the tendon reflexes .
During the experiment, the subject was seated comfortably and asked to fully relax and not react to or anticipate the taps. If the subject felt inclined to move or change the posture, we would wait until he or she relaxed again. At the beginning, we adjusted the tapping force so that a triceps muscle contraction was clearly evoked. We then tapped the triceps tendon at approximately that level about seven times during a trial, with a random interval averaging about 2.5 s. We collected three trials at each joint angle and repeated the tapping at 60??, 90??, and 120?? elbow flexion. We sampled the tendon tapping force, triceps electromyography (EMG) signals, and elbow joint extension torque at 500 Hz after low-pass filtering (8th-order Butterworth filter at 230 Hz cutoff).
The sampled EMG signals were full-wave rectified. We filtered the tendon tapping force, rectified EMG , and elbow extension torque signals digitally using a finite impulse response low-pass filter with a cutoff frequency of 150 Hz. The signals were then processed interactively. We inspected the elbow extension torque and triceps EMG signals to see whether any random voluntary contraction or marked noise occurred. If so, the relevant taps would not be selected. We then segmented the force, EMG , and torque signals into multiple taps, aligned by the tapping force peak moment. Each data segment was about 670 ms long, starting from 70 ms before the tapping force peak and ending 600 ms after the peak.
Because the reflex torque is induced by the tendon tapping force and varied with the tapping force, treating them as output and input of the tendon reflex system, respectively, is appropriate . We used the system impulse response to characterize the reflex torque as the output of a system excited by the tendon tapping force. We identified the impulse response (the input-output relationship) from the experimental data as follows: because the tapping force was rather brief, it could be approximated as a pulse. Therefore, we approximated the impulse response as the reflex torque response scaled by the area of the corresponding tapping force pulse .
We used several physiologically meaningful parameters to characterize the impulse response of the tendon reflex system (Figure 2). Within a certain range, the Gs reflex torque varied with the tendon tapping force in that a stronger tapping force elicited a stronger reflex torque. In system analysis, Gs was the gain measure of the tendon reflex system at zero frequency, calculated as the area of the impulse response.
Representative impulse responses of tendon reflex from patient with stroke (red line) and nondisabled control (blue line). Vertical lines correspond to (1) start of tapping impact, (2) onset of reflex-mediated torque response, (3) peak torque response, and (4) 50% of peak response. Notice that spike after line 1 was because of tapping-induced mechanical impact transmitted to torque sensor.
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Rc characterized the slope of the ascending segment of the impulse response (calculated over period from onset to peak instant of impulse response). Rc characterized the muscle contraction dynamics with a unit of in meters per second. Similarly, the half relaxation rate (Rhr) characterized the slope of the descending segment of the impulse response, the dynamic rate of muscle relaxation (over period from peak instant of impulse response to instant of 50% of peak).
In addition to the above parameters characterizing the system impulse response, we used the peak tendon tapping force that was used to elicit tendon reflexes for each subject to characterize the reflex threshold in tapping force (fth), which characterizes the reflex excitability. Finally, we characterized the reflex loop delay (td) quantitatively as the delay from the start of the tapping force to the onset of the reflex-mediated torque response, which was also shown in the impulse response (Figure 2).
We used the Student t-test to determine whether the Gs, Rc, Rhr , fth, and td were different between the patients with stroke and nondisabled controls. We compared Gs, Rc, Rhr , fth, and td between the two different subject groups across the three different elbow joint angles using the repeated measures analysis of variance (ANOVA) (2 ?? 3, two different groups and three different joint angles). We set the significance level at a = 0.05.
The patients with stroke showed considerable spasticity and hyperactive reflex as indicated by the clinical scales. Their clinical tendon reflex scale score was 3.0 ± 0.6 and their Modified Ashworth Scale [4,7-8] score (ranging from 0 to 4) was evaluated as 2.3 ± 1.1. They were 8.4 ± 4.6 yr poststroke.
Compared with the nondisabled controls, patients with stroke had significantly different neuromuscular dynamics in tendon reflexes. As shown in the representative cases (Figure 3), the threshold in tapping force for the patients with stroke (12 ± 2 N) was much lower than that for the nondisabled controls (41 ± 4 N) (p = 0.01). On the other hand, the reflex-mediated EMG response and elbow extension torque in the patients with stroke were much higher and changed much quicker than their counterparts in the nondisabled controls.
Representative tendon tapping results over multiple taps of triceps tendon with elbow joint at 90° flexion in (a) nondisabled controls and (b) patients with stroke. Blue solid lines and red dashed lines represent mean ± standard deviation, respectively. EMG = electromyography.
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The impulse responses characterized the dynamic relationship between the tapping force and reflex-mediated torque response in system analysis (Figure 2). Compared with the nondisabled controls, the spastic elbow showed a much stronger tendon reflex impulse response with much higher amplitude and quicker increased amplitude, indicating stronger and quicker reflex responses associated with hyperactive reflexes.
The Gs in patients with stroke was much higher than that in nondisabled controls (Figure 4(a)). The Gs of the patients with stroke was 0.66 ± 0.66 m??ms, 2.52 ± 1.55 m??ms, and 3.13 ± 2.15 m??ms at 60°, 90°, and 120° elbow flexions, respectively. In contrast, the Gs of the nondisabled controls was 0.23 ± 0.19 m??ms, 0.59 ± 0.28 m??ms, and 0.51 ± 0.25 m??ms at 60°, 90°, and 120° elbow flexions, respectively.
Comparison of (a) tendon reflex gain (Gs), (b) contraction rates (Rc), (c) half relaxation rate (Rhr), (d) reflex threshold in peak tendon tapping force (fth), and (e) reflex-loop delay (td) between patients with stroke and nondisabled controls across three elbow flexion angles. Vertical bars represent standard deviation across subjects.
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ANOVA with repeated measures showed that the Gs of the patients with stroke was significantly higher than that of the nondisabled controls across the different angles (F1,7 = 54.895 and p = 0.01). There also was a significant difference across the different angles in the patients with stroke (F2,6 = 10.185 and p = 0.01), but there was no effect of interaction between the subject groups and angles.
The ANOVA procedure with repeated measures showed that the tendon reflex Rc of patients with stroke was significantly higher than that of the nondisabled controls across the different angles (F1,7 = 7.123, p = 0.03). The Rc of patients with stroke versus nondisabled controls at 60°, 90°, and 120° elbow flexions were 0.34 ± 0.2 versus 0.15 ± 0.10 m/s, 0.96 ± 0.94 versus 0.20 ± 0.10 m/s, and 1.29 ± 1.48 versus 0.15 ± 0.10 m/s, respectively (Figure 4(b)).
Similarly, the Rhr of the patients with stroke was significantly higher than that of nondisabled controls (F1,7 = 14.014, p = 0.01) (Figure 4(c)). The Rhr of the patients with stroke versus nondisabled controls at 60°, 90°, and 120° elbow flexions were 0.32 ± 0.26 versus 0.078 ± 0.04 m/s, 0.33 ± 0.29 versus 0.09 ± 0.05 m/s, and 0.41 ± 0.31 versus 0.11 ± 0.06 m/s, respectively.
The threshold in tapping force in the spastic limbs in patients with stroke was significantly lower than that in nondisabled controls (F1,7 = 18.017, p = 0.01) across all different elbow joint angles. The fth for the patients with stroke versus nondisabled controls at 60°, 90°, and 120° elbow flexions were 16.5 ± 8.4 versus 28.3 ± 8.3 N, 18.0 ± 11.1 versus 30.7 ± 11.6 N, and 17.9 ± 10.9 versus 31.3 ± 10.9 N, respectively, indicating more reduced reflex threshold and more increased reflex excitability in the patients with stroke than in the nondisabled controls (Figure 4(d)). Furthermore, no difference existed in the threshold in tapping force across different joint angles in either of the two groups. This indicates that the threshold is not sensitive to joint angle change in the patients with stroke and nondisabled controls. On the other hand, the manually delivered taps were not controlled as precisely as a servomotor controlled tapping, which may also have contributed to the insignificant dependence on joint angle.
The mean values of the td for the patients with stroke versus nondisabled controls at 60°, 90°, and 120° elbow flexions were 38.7 ± 4.5 versus 40.4 ± 3.3 ms, 38.4 ± 3.0 versus 39.5 ± 2.4 ms, and 37.8 ± 3.0 versus 38.4 ± 3.0 ms, respectively, showing a trend of more reduced td in the patients with stroke than in the nondisabled controls and a trend of reduction in td with decreasing elbow flexion (Figure 4(e)). However, neither of the reductions was significantly different (F1,8 = 1.457, p = 0.26).
Reflex responses can be extremely variable, especially in patients with neurological disorders. Clinical tendon reflex scales cannot characterize the dynamic changes in large ranges and may be misleading if used on their own . This study provides a useful tool for making accurate measurements of both taps to the tendon and reflex-mediated responses and characterize their dynamic relationship in terms of Gs, Rc, and Rhr , and reflex threshold in tapping force. The results showed markedly increased system gain, Rc, and Rhr , and decreased reflex threshold in tapping force provided quantitative measures to characterize hyperactive reflexes poststroke. Practically, the tendon reflex evaluation is easy to do and can potentially provide convenient and quantitative measures in clinical settings.
Spasticity is a complicated clinical symptom with multiple contributing reflex and nonreflex components. Convenient quantification tools suitable for its evaluations in clinical practice are lacking. Some investigators consider that spastic muscle hypertonus exists primarily because of an increase in reflex excitability [11,14-15]. Others argue that increased stiffness in a spastic limb could not be directly interpreted as the evidence of a hyperactive reflex because the increased resistance to a stretch could be attributed to passive tissue stiffness (from connective tissue, tendons, and passive muscle properties) and intrinsic stiffness of contracting muscle fibers, as well as reflex-mediated stiffness [16-19]. They suggest that spasticity is a complex phenomenon consisting of the reflex and nonreflex components, each of which need to be quantified related to its corresponding clinical facet for one to explain and understand the multifaceted clinical features of spasticity and to evaluate its mechanisms reliably [19-24]. Accordingly, we evaluated tendon reflexes in this study under the isometric condition, which effectively minimized the mechanical contributions of joint stiffness, viscosity, and limb inertia. Therefore, the reflex contribution was manifested and readily separated from intrinsic and passive contributions to joint torque [10,11,20-25].
This study shows that the triceps tendon reflex was much more excitable in patients with stroke than that in nondisabled controls, which was consistent with previous findings in the literature [10,26]. On the other hand, different from previous studies , this study focused on the elbow in the upper limb instead of the knee in the lower limb, and it addressed the dependence of tendon reflex on joint angles instead of at one knee position. Furthermore, this study evaluated the hyper-reflexia in a group of patients with stroke instead of in patients with multiple sclerosis, and considering different neurological disorders may involve different changes in tendon reflexes.
The Gs was the system gain calculated through system identification relating the input of tapping forces to the output of the resultant reflex-mediated torque response. The system parameters quantified the input and output simultaneously and gave more reliable measures than did the input or output parameters alone. The increased Gs could be caused by higher excitability of motoneurons, and it could be related to increased muscle tone poststroke so that muscle activation was converted to quicker and stronger muscle contraction. Possible neural mechanisms for spastic hypertonia in stroke included increased excitatory synaptic input and increased spindle afferent discharge rates so that motoneuronal excitability increased and excitatory postsynaptic potential from group Ia and II muscle spindle afferents might also be enhanced related to motoneuron dysfunction. Another possible change in stroke is that inhibitory synaptic input is reduced, namely, presynaptic inhibition initiated by descending fiber input is reduced. Descending tracts could possibly contribute to spastic muscle hypertonia, either by monosynaptic excitatory projections to lower motoneurons or indirectly by inhibition of facilitation of interneurons within spinal reflex pathways.
Despite the longer contraction time and longer Rhr associated with the higher peak of the tendon reflex torque response in the patients with stroke, the Rc and Rhr poststroke were significantly higher than those in nondisabled controls. The Rc and Rhr characterized the dynamic characteristics of tendon reflexes-how forceful and quick the reflex-mediated muscle contraction responses were. These dynamic characteristics suggest that the excitatory synaptic input such as excitation of group Ia afferents is enhanced, while inhibitory synaptic input like group Ia inhibitory interneurons is reduced in stroke.
There are changes of the reflex threshold in stroke. The reduced reflex threshold in tapping force could be caused by a reduced threshold in motoneuron excitability and/or peripheral changes of tighter coupling and force transmission from tendon tapping to stretching on muscle spindles poststroke. The motoneuron activity could possibly have been enhanced poststroke. The motoneuron plays a role in changing the length of the intrafusal fibers and adjusting sensitivity of the muscle spindles. In an impaired arm poststroke, muscle spindles with the inappropriate length of intrafusal fibers under all different conditions could increase group Ia sensory afferent signals and decrease reflex threshold in tendon tapping force. For example, Figure 5 shows the tapping forces and peak reflex-mediated elbow extension torques on both the impaired and unimpaired limbs in a patient with stroke, which showed obviously reduced reflex threshold on the impaired side poststroke.
Comparison of peak tapping force and peak reflex-mediated torque between impaired (Δ) and unimpaired (*) upper limbs of patient with stroke at several selected elbow flexion angles (60°, 75°, 90°, 105°, 120°, and 135°).
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This study has limitations. One is that the nonreflex contribution to the increased joint stiffness poststroke was not characterized separately. Instead, the experiment was conducted isometrically at the elbow joint so that nonreflex contributions were minimized. Another limitation is that the sample was small. Further study with more subjects is needed.
With simplification, the methods described in this article can potentially be used for clinical diagnosis and evaluations. Clinicians can potentially use them to diagnose the symptom quantitatively with higher accuracy than the clinical tendon reflex scale score of 0 to 4. The quantitative tendon reflex evaluations would also be useful for evaluating treatment outcome more accurately. Clinicians could then track the outcome more accurately and prescribe a better treatment plan. Practically, further work must be done to simplify the setup, especially the tapping-induced output responses, and substitute them with more convenient measures, such as reflex-mediated limb movement or tendon bounce-back force . This will likely make tendon reflex evaluations more suitable for the clinical setting and more conveniently performed.
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Last Reviewed or Updated Wednesday, May 25, 2011 11:24 AM