Search tips
Search criteria 


Logo of nihpaAbout Author manuscriptsSubmit a manuscriptHHS Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
PM R. Author manuscript; available in PMC 2017 April 1.
Published in final edited form as:
Published online 2015 September 25. doi:  10.1016/j.pmrj.2015.08.017
PMCID: PMC4808474

Accuracy of clinical techniques for evaluating lower limb sensorimotor functions associated with increased fall risk



In prior work laboratory-based measures of hip motor function and ankle proprioceptive precision were critical to maintaining unipedal stance and fall/fall-related injury risk. However, the optimal clinical evaluation techniques for predicting these measures are unknown.


To evaluate the diagnostic accuracy of common clinical maneuvers in predicting laboratory-based measures of frontal plane hip rate of torque development (HipRTD) and ankle proprioceptive thresholds (AnkPRO) associated with increased fall risk.


Prospective, observational study.


Biomechanical research laboratory.


Forty-one older subjects (age 69.1 ± 8.3 years), 25 with varying degrees of diabetic distal symmetric polyneuropathy and 16 without.


Clinical hip strength was evaluated by manual muscle testing (MMT) and lateral plank time (LPT), defined as the number seconds the laterally lying subject could lift hips from the support surface. Foot/ankle evaluation included Achilles reflex, and vibratory, proprioceptive, monofilament, and pinprick sensations at the great toe.

Main Outcome Measures

HipRTD, abduction and adduction, using a custom whole-body dynamometer. AnkPRO determined with subjects standing using a foot cradle system and a staircase series of 100 frontal plane rotational stimuli.


Pearson correlation coefficients (r) and receiver operator characteristic (ROC) curves revealed that LPT correlated more strongly with HipRTD (r/p = .61/<.001 and .67/<.001, for abductor/adductor, respectively) than did hip abductor MMT (r/p = .31/.044). Subjects with greater vibratory and proprioceptive sensation, and intact Achilles reflexes, monofilament, and pin sensation had more precise AnkPRO. LPT of < 12 seconds yielded a sensitivity/specificity of 91%/80% for identifying HipRTD < .25 (body size in Newton-meters), and vibratory perception of < 8 seconds yielded a sensitivity/specificity of 94%/80% for the identification of AnkPRO > 1.0 degree.


LPT is a more effective measure of HipRTD than MMT. Similarly, clinical vibratory sense and monofilament testing are effective measures of AnkPRO, whereas clinical proprioceptive sense is not.


Given the importance of maintaining the ability to walk for function and exercise,1, 2 clinicians need bedside techniques for measuring lower limb neuromuscular capacities. However, many clinical techniques for determining lower limb function are unsupported by objective measures. In prior work we found that frontal plane hip strength and ankle proprioception were critical to the ability to maintain unipedal balance, which in turn has been associated with frailty,3 aging,4 and risk of injury from falls.5 In addition, human biomechanical studies suggest that in the whole-body inverted pendulum model of bipedal walking, the hip exerts a primary influence on equilibrium.6 Further, hip adduction/abduction controls foot placement which is the primary method for managing frontal plane balance.7 As such, rapidly available frontal plane strength at the hip is essential for safely traversing obstacles and avoiding falls,8, 9 particularly lateral falls which have the greatest likelihood of being associated with hip fracture.10 Ankle proprioceptive precision (AnkPRO) also plays a critical role in balance, independent of hip strength.11, 12 Moreover, AnkPRO becomes less precise with age13 and diabetic polyneuropathy (DPN),14 both of which are potent risk factors for falls.

The usual clinical technique for measuring hip strength, manual muscle testing (MMT), is criticized due to its ordinal scale, difficulty with positioning to isolate the hip ab/adductors, and lack of adjustment for body mass.15, 16 Accordingly, MMT of the lower limbs lacks sensitivity to strength impairments, resulting in poor diagnostic accuracy.17 Although hand held dynamometers are an option, lower limb strength measurement with these devices is subject to error due to difficulties with stabilization.18

AnkPRO is often estimated clinically by an examiner passively moving the ankle, or great toe, in the sagittal plane out of the patient's view while the patient states the direction of motion,19 however, the accuracy and precision of this subjective technique is not known. Laboratory-based techniques for assessing AnkPRO are laborious, requiring excessive time and a dedicated hardware and software rendering them unsuitable for clinical use.11 Functional measures of coordination such as one-legged stance are often considered measures of proprioceptive ability; however, they are confounded by muscle motor performance and as such do not accurately reflect proprioceptive abilities.12, 20 In prior work, we found that fibular motor amplitude was strongly associated with ankle proprioceptive thresholds,21 but this may require a consulting physician and is not immediately available at the bedside. We found no work validating bedside means for evaluating proprioceptive function; however, give that proprioceptive information is related to large fiber afferent function,22 we elected to see how well clinical tests of distal large fiber afferent function, and the commonly performed pinprick sensation, predicted AnkPRO.

Therefore we performed a secondary analysis of clinical and laboratory-based measures of lower limb neuromuscular function in a group of older subjects with a spectrum of peripheral neurologic health and function. The goal of this research was to evaluate the diagnostic accuracy of clinical measures of hip strength and foot/ankle neuromuscular function to predict laboratory-based measures of hip motor function (in the form of frontal plane hip rate of torque development; HipRTD) and AnkPRO associated with increased fall risk.9 More specifically, we hypothesized that increased HipRTD would be associated with (H1): a) increased manual muscle test score; and b) number of seconds that subjects can maintain a lateral plank posture. We also hypothesized that decreased (that is, more precise or better) AnkPRO would be associated with (H2): a) presence of an Achilles reflex; b) longer clinical vibratory perception; c) increased accuracy of clinical great toe proprioceptive sensation; d) increased accuracy of great toe monofilament perception; and e) presence of great toe pinprick sensation.



As described in prior work,9 41 subjects (16 healthy old and 25 subjects with DPN) were recruited under a protocol approved by the Institutional Review Board. Written informed consent was obtained from all participants. Subjects were recruited consecutively from July of 2009 to January of 2011, from the XXXXX

Inclusion criteria for DPN subjects

Inclusion criteria for DPN subjects included an age 50 – 85 years, weight < 136 kg, known history of diabetes mellitus, ability to walk household distances without assistance/assistive device, ankle dorsiflexion and inversion/eversion of at least anti-gravity (grade ≥3 by manual muscle testing), symptoms and signs consistent with DPN including: symmetrically altered sensation in lower extremities, Michigan Diabetes Neuropathy Score (MDNS) ≥10;23 and electrodiagnostic evidence consistent with DPN as evidenced by bilaterally abnormal fibular motor nerve conduction studies (absent or amplitude < 2 mV and/or latency > 6.2 msec and/or conduction velocity < 41.0 m/s) stimulating 9 centimeters from recording site over the extensor digitorum brevis distally, and distal to the fibular head proximally.

Exclusion criteria for DPN subjects

Subjects were excluded if they had an accidental fall one month or less prior to testing, a history or evidence of any significant central nervous system dysfunction (i.e. hemiparesis, myelopathy or cerebellar ataxia), a neuromuscular disorder other than DPN, evidence of vestibular dysfunction, angina or angina-equivalent symptoms with exercise, plantar skin sore or joint replacement within the previous year, symptomatic postural hypotension, significant musculoskeletal deformity, lower limb or spinal arthritis or pain that limits standing to less than 10 minutes; walking to less than one block.

The remainder of the cohort were older adults were without a history of diabetes mellitus, had no neuropathic symptoms, had normal electrodiagnostic studies, and an MDNS < 10. They otherwise met the same inclusion criteria as the DPN subjects.

Independent Variables (H1)

Independent variables were measured one to two weeks prior to laboratory-based evaluations so that evaluators (TD and JKR) were blinded to laboratory-based dependent variables.

Manual Muscle Testing (MMT)

Hip abduction muscle strength was evaluated by MMT using standard techniques19 by an experienced physical therapist. (TD).

Lateral Plank Time (LPT)

The subjects lay on a flat, cushioned surface with their right side down, the lateral aspect of the right foot in full contact with the horizontal surface and left foot directly atop or behind the right. The right upper limb was placed under the shoulder with the elbow at 90 degrees and directly under the shoulder with the forearm and palm in neutral or pronated per subject preference. Pillows were placed under the axillary region as needed for shoulder support. The left arm was placed along the left lateral trunk and hips. The thighs were aligned with the trunk in the sagittal plane with the knees fully extended. Upon signal, the subject lifted hips and trunk from the support surface so as to align the trunk and thighs in the frontal plane, keeping the shoulders perpendicular to the support surface. The endpoint was when the thighs and trunk were no longer aligned despite one verbal reminder. The number of seconds this position could be maintained was measured by stopwatch. If the position could not be achieved with knees extended, the procedure was repeated with knees flexed (Figure 1.a. and b.) The number of seconds the subject achieved bridging with knees flexed was multiplied by 0.5 given the greater ease of that task. One brief practice trial to check understanding and positioning was allowed, then one minute of rest, followed by the data acquisition trial. The procedure was repeated on the left, and the mean of the two responses used for analyses.

Figure 1
a. and b. Posture subjects achieved for lateral plank time with knees extended (a.) and flexed (b.)

Independent variables (H2)

Achilles reflex

The presence of Achilles reflex was determined using the standard percussion over the Achilles tendon, and also the plantar strike technique.24 Facilitation included Jendrassik maneuvers and gentle plantar flexion. Reflexes were scored as a “two” if consistently present without enhancing maneuvers, a “one” if present intermittently or only with maneuvers, and “zero” if never present. Vibratory sense: Clinical vibratory perception was determined using a 128 Hz tuning fork. The fork was first maximally struck against the palm and placed on the subject's clavicle for familiarization, with the subject saying “Now” when the vibration was no longer perceived. The procedure was then repeated on the left and right on the dorsal aspects of the great toes just proximal to the nailbeds.25 The means of the two responses were used for analyses.

Proprioceptive sense

Great toe proprioceptive sense was determined with the subjects seated with their legs hanging freely. The examiner held the medial and lateral aspects the distal phalanx of the great toe with thumb and index finger. The toe was moved up and down with the subject watching to confirm understanding of the task. Then, with eyes closed, the toe was moved randomly by small increments of approximately 1 to 2 centimeters, with movements occurring at random intervals varying from a few seconds to ten seconds. The subject responded “up” or “down” in response to the toe motion.26 There were five trials on each side. Incorrect responses included indicating the wrong direction or not responding to a movement. The number of correct responses of the 10 trials was used for analysis.

Monofilament testing

Great toe monofilament perception was determined by touching a 1.28 monofilament to the dorsum of the great toe at random intervals five times on both sides. Incorrect responses included not responding to a touch, or indicating a touch when none had occurred.

Pinprick sensation

Great toe pinprick sensation was evaluated by using a standard safety pin to prick the skin over the dorsum of the great toes bilaterally. The subject responded by saying “sharp” or “not sharp”.

Dependent Variables (H1)

HipRTD was determined, as per prior work, using a custom, whole-body dynamometer (BioLogic Engineering, Inc.).9,12 To determine the moment arm, the location of the (vertical) axis of the center of rotation of the dynamometer's low inertia torque arm was marked with a white cross on the black colored horizontal bed of the dynamometer. One axis of the cross spanned the width of the bed forming a ‘reference line,’ the other ran along the midline of the long axis of the bed. The bed was made of a firm pad as found on clinical examination tables. The subject was asked to lie down supine along the long axis bed of the dynamometer. The location of the greater trochanter was palpated and the subject was asked to position themselves with their greater trochanter directly over the reference line. The midsagittal plane of the subject's pelvis was then moved 10 cm off the centerline, based on two separate works of hip anthropometric data,27-28 of the dynamometer bed so that the contralateral side of the pelvis pressed against a vertical padded support and was held there with seat belt. The weight of the distal part of the subject's ipsilateral test leg was placed into an ‘L-shaped’ support pad at the end of the torque arm, where it was strapped in place. Next, the experimenter made slow ab-adduction movements with the torque arm and test leg while (s)he watched the movement of the ipsilateral hip joint relative to the bed. With the ankle held firmly at the distal end of the torque arm, the cranio-caudal position of the subject on the bed was then adjusted in a caudal direction until the pelvis no longer migrated cranially or caudally as the test leg (on the torque arm) was ab- and adducted back and forth. Once craniocaudal movement of the pelvis was minimized relative to the bed, the hip joint center was by definition coincident with the rotation axis of the torque arm, at least in the craniocaudal direction (which is the most critical adjustment for measuring hip abduction torque). The dynamometer was fitted with internal hardware to automatically measure the lever arm from the center of the ankle support pad to the torque arm axis of rotation to the nearest mm. The dynamometer was fitted with internal hardware to automatically measure the lever arm from the center of the ankle support pad to the torque arm axis of rotation to the nearest mm. When used to measure isometric torque, the dynamometer measured the maximum isometric force and rate of torque that the subject exerted against the ankle pad in Newtons. Its software then multiplied that force by the machine-measured lever arm (in meters) to obtain the resulting maximum isometric hip abduction strength (in units of Nm) and rate of torque development (in Nm/s). Subjects exerted a hip abduction force against the lever arm, given the instruction to perform it “as fast and as hard as possible” for three seconds. Subjects received verbal encouragement. Three trials were performed with one-minute rest between trials. Subjects performed analogous maneuvers in the opposite direction for hip adduction testing. Signals were amplified to volt levels before being acquired using a 12 bit analog-to-digital converter sampling at 100 Hz. The maximal rate of torque development measures were normalized for individual body size by dividing by each subject's body height multiplied by weight in units of Nm.29 The peak value of rate of torque development was found following the methods we described in Thelen et al30 whereby five point numerical differentiation was used for the torque-time data under isometric conditions. The mean peak value obtained from the three trials for each test type was used for the statistical analyses.

Dependent Variable (H2)

To determine AnkPRO subjects stood with the (dominant) test foot in a 40 × 25 cm cradle that was rotated by an Aerotech 1000 servomotor equipped with an 8,000 line rotary encoder as described by Son et al.11 (Figure 2) After an audible cue, a single ankle inversion or eversion rotation of 0.1 to 3° magnitude was randomly presented at 5°/s. The subject then pressed a joystick handle in the direction of the perceived foot rotation. Four blocks of 25 trials (randomly, 10 eversion, 10 inversion, and 5 dummy trials) were presented interspersed with 2 to 5 minute rest intervals. The outcome measure was the ankle proprioception threshold (TH100), defined as the smallest rotational displacement of the ankle that a subject could reliably detect with 100% accuracy.11 A summary measure of ankle proprioception was found from the sum of the inversion and eversion proprioception thresholds.

Figure 2
Apparatus for determining ankle inversion/eversion proprioceptive thresholds (AnkPRO)

Statistical Analyses

Statistics were performed using SPSS for Windows (version 20.0; SPSS, Inc., Chicago Illinois). All data were included in the analyses, with no exclusion of outliers. The following analyses were used to determine the strength of relationships between the independent/clinical and dependent/laboratory-based variables:


The relationships hip MMT (H1a) score and LPT (H1b) with HipRTD were evaluated with Pearson correlation coefficients (r).


AnkPRO differences between categories of Achilles reflex (H2a) were determined using analysis of variance. AnkPRO differences between categories of monofilament perception (H2d) and pinprick sensation (H2e) were determined using standard t tests. The relationships between AnkPRO and great toe vibratory (H2b) and proprioceptive sense (H2c) were determined using Pearson correlation coefficients.

Multivariate linear regression analyses were used to compare the relative strengths of clinical variables with respect to predicting HipRTD and AnkPRO.

Receiver operating characteristic (ROC) curves were generated to identify continuous variable thresholds that most reliably identified subjects with strong vs. weak HipRTD as defined by .25, and precise vs. imprecise AnkPRO as defined by 1.0 degree. These points were chosen because of prior research identifying these values as those which best identified patients' at increased risk for fall and injury.9



Of the original ninety-one subjects considered for the study, 21 failed initial telephone screening and 18 declined participation. Of the remaining 52 subjects, 5 failed the screen and 3 had scheduling conflicts. Of those 44 subjects, 2 dropped out due to medical concerns. The remaining 42 subjects were enrolled and evaluated. AnkPRO data were lost for one subject and so 41 subjects remained (20 (49%) women, age 69.1 ± 8.3 years), including 25 with diabetic neuropathy of varying severity and 16 without diabetes or neuropathy. There were no adverse events related to the evaluations.


MMT hip abductor strength showed significant, but relatively weak, associations with HipRTD (r/p values = .313/.044 and .356/.021 for hip abductor and adductormotion, respectively; Figure 3.a). LPT demonstrated a strong, positive relationship with HipRTD, (r = .61 and .67 for hip abductor and adductor motion, respectively; p < .001 for both; scatter plot depicted for the latter in Figure 3.b.). When MMT and LPT were entered into a regression model, MMT was not a significant predictor of HipRTD (Beta and p values = .689/<.001 and -.063/.664 for LPT and MMT, respectively). ROC analysis demonstrated that LPT of 12 seconds yielded a sensitivity of 91% and a specificity of 80% for identifying HipRTD < .25, with the corresponding AUC = .91 (95% Confidence Interval = .82, 1.0)

Figure 3
a. – d. Scatter plots of continuous clinical variables and frontal plane hip RTD (a. and b., top left and right) and AnkPRO (c. and d. bottom left and right). Pearson correlation coefficient (r)/p values for Figure 3.a. = .31/.044; 3.b. = .67/<.001; ...


Subjects with normal Achilles reflexes demonstrated significantly more precise AnkPRO than subjects without reflexes (1.0 ± .8 vs. 2.9 ± 1.3 degrees; p < .001) or with reflexes obtained with maneuvers (2.1 ± 1.1 degrees; p =.008; Figure 4.a). Vibratory sensation at the great toe correlated strongly with AnkPRO (r = -.704; p < .001; Figure 3.c). The association was negative, with longer times of vibration perception correlating with smaller (more precise/better) AnkPRO. Great toe proprioceptive sense correlated significantly and negatively with AnkPRO (r = -.534; p < .001; Figure 3.d), with a greater number of correct responses correlating with smaller AnkPRO. Of note, 11 subjects with accurate responses on 8 or more trials demonstrated imprecise AnkPRO (> 1.0 degrees). Subjects with intact sensation to monofilament testing had significantly smaller (more precise) AnkPRO values as compared to subjects who did not (.8 ± .3 vs. 2.3 ± 1.0 degrees, respectively; p < .001; Figure 4.b. (Two subjects were intact on one side only and were excluded from analysis.) Subjects with intact pin sensation (N = 18) demonstrated more precise AnkPRO than subjects without (N = 19; 1.0 ± .8 vs. 2.6 ± 1.3 degrees; p < .001; Figure 4.c).

Figure 4
a. – c. Boxplots demonstrating between group AnkPRO differences for categorical clinical variables (a. and b. top left and right). p values for differences depicted are: 4.a. p < .001 for subjects with versus without Achilles reflexes, ...

Multivariate analyses demonstrated that the best model prediction of AnkPRO was the combination of vibratory and monofilament sensations (Beta/p values were -.327/.037 and -.456/.005, respectively). The overall model fit (R2) was 0.519. ROC analysis showed that vibratory perception time at the great toe of 8 seconds yielded a sensitivity of 94% and a specificity of 80% for the identification of AnkPRO > 1.0 degree, with an area under the curve (AUC) value of .95 (95% Confidence Interval = .88, 1.0).


In this study, we have found statistically and clinically significant correlates to lab-measured HipRTD and AnkPRO data obtained in a cohort of older subjects with a range of peripheral neurologic function. LPT was the strongest predictor of HipRTD, and notably, a better predictor than MMT, which was a relatively weak predictor. Vibratory and monofilament perception at the great toe were most strongly predictive of precise AnkPRO. An intact Achilles reflex also predicted more precise AnkPRO, and any two of the three tests predicted approximately 50% of AnkPRO variability. The presence of pinprick sensation at the great toe was also associated with more precise AnkPRO, but there were several cases of coarse proprioception in subjects with intact pin sensation. Surprisingly, great toe position sense was only weakly predictive of AnkPRO.

Few studies have compared MMT with more objective measures of hip strength. Aitkens et al.31 compared hip flexion/extension MMT with quantitative isometric strength using a force transducer and peak maximum voluntary force. Subjects with full (5/5) strength by MMT demonstrated widely varying isometric strength values, and there were no differences in strength between muscle groups with MMT grades 5/5 and 4/5. These findings parallel our data in which 5/5 MMT strength represented a broad range of HipRTD (Figure 3.a). Of interest, hip abduction MMT score also demonstrated a similarly weak relationship with laboratory-based hip abduction maximal voluntary torque (r and p value p .354 and .021, respectively; unpublished data). Taken together the data suggest that MMT scores are only weakly related to laboratory-based strength measures, particularly when scores are in the 4 and 5 range.

In prior work we found fibular motor amplitude accounted for nearly 60% of AnkPRO variability.21 The current study builds on this by providing additional clinical options for assessing AnkPRO. To our knowledge, no other studies have evaluated the ability of bedside clinical techniques to predict AnkPRO. However, Simmons et al.32 found balance impairments in diabetic patients with sensory cutaneous deficits (as measured by monofilament testing), but not in diabetic subjects with preserved cutaneous sensation. Our results may provide a mechanism for these findings by identifying a direct relationship between monofilament testing and ankle proprioceptive precision. Others have found that clinical proprioceptive testing, which poorly predicted AnkPRO, is of uncertain efficacy in identifying proprioceptive function. For example, Beckmann et al.33 found no difference in great toe movement sense in a group of subjects with known proprioceptive dysfunction related to multiple sclerosis or vasculitis as compared to control subjects. Moreover, poor clinical position sense re-test reliability at the wrists in healthy subjects has been noted, prompting the suggestion that clinical position sense testing is inherently flawed.34

LPT offers some advantages to MMT that may explain its superior prediction of frontal plane HipRTD. Positioning is less a concern as the lateral plank posture is known to activate frontal plane hip and trunk musculature.35 LPT exploits Rohmert's Law,36 which describes the exponential decrease in a maximum isometric force with time. Put another way, Rohmert's Law states that a patient with strong hip muscles will be able to hold the lateral plank position for much longer than a patient with weak hips. Therefore, the time that LPT is held is directly related to the initial maximum strength. Furthermore, LPT provides more reliable long-lever arm conditions37 and a more continuous measure that is inherently adjusted for body mass, whereas MMT offers none of these advantages. The potential clinical utility of lower limb clinic strength measurements that intrinsically adjust for body mass is further suggested by Rainville et al.38 who demonstrated that unilateral quadriceps weakness due to L3/L4 radiculopathy was best detected by a single leg sit-to-stand test.

The strong relationships identified between clinical vibratory and light touch sensation, Achilles reflex, and AnkPRO are consistent with all being measures of distal large fiber sensory function. In contrast, pin sensation was less strongly related to AnkPRO with several subjects demonstrating intact pin sensation but coarse AnkPRO. These data are consistent with pin sensation being more related to small fiber afferent function, which can be relatively preserved in the setting of large fiber neuropathy.

The study has potential clinical implications. Despite its disadvantages17 MMT is the most commonly used method for evaluating muscle strength. However, the data presented suggest that LPT is superior to standard MMT, and that a cutoff of 12 seconds yields good specificity and sensitivity for detecting diminished frontal plane HipRTD. The results also suggest that clinical toe proprioceptive sense testing imprecisely determines AnkPRO. However, semi-quantified vibratory sensation and monofilament testing as described are reasonable estimates of AnkPRO, with a vibratory threshold of 8 seconds achieving reasonable sensitivity and specificity for AnkPRO of 1.0 degree.

Although the study has strengths, including novel results and strong correlations that allow a more efficient and precise bedside evaluation of lower limb neuromuscular functions that influence fall/injury risk,9 the work has limitations as well. We exclusively evaluated frontal plane function so that no comment can be made regarding sagittal plane strength or proprioceptive function. We evaluated older subjects with diabetic neuropathy, so the extension of our findings to other patient populations is uncertain. It should also be noted that when determining LPT, subjects performing the test with knees flexed had their recorded plank time reduced by 50% to account for the greater ease of the task. Although the knees flexed LPT is unquestionably an easier task, the designated value of 0.5 was an estimate and thus represents a limitation. A small but apparent ceiling effect was noticed in LPT as our cutoff for maximum performance was 30 seconds. Greater correlations might have been obtained if the LPT maximum was increased to 60 seconds. Additionally, three subjects were omitted from pinprick analysis as they had discrepant responses between right and left sides. While our results suggest novel approaches to assess patient hip strength and ankle proprioceptive precision, they do not suggest therapeutic strategies for improvement in these measures. Prior work suggests that improvement in proprioceptive thresholds may not be feasible19 but that hip strength can compensate for poor proprioception in preserving unipedal stance time.12 In this way, those with distal polyneuropathy may benefit from hip strengthening exercises. Lateral planks may not only be beneficial in predicting weak hips, as our results suggest, but also in strengthening them.39


The data suggest that LPT is an effective clinical measure of laboratory-based frontal plane hip motor function, HipRTD, whereas MMT is not. Further, a LPT of 12 seconds appears to discriminate between patients with and without sufficient HipRTD to influence fall risk in this population. The data also suggest that clinical vibratory sense and monofilament testing are effective clinical measures of AnkPRO, whereas clinical position sense is not. Vibratory sensation of 8 seconds appears to differentiate between patients with AnkPRO greater or less than 1.0 degree, a threshold associated with fall risk. These techniques may allow a more efficient and accurate bedside evaluation of lower limb neuromuscular attributes critical to the assessment of fall risk in the population evaluated.


Publisher's Disclaimer: This is a PDF file of an unedited manuscript that has been accepted for publication. As a service to our customers we are providing this early version of the manuscript. The manuscript will undergo copyediting, typesetting, and review of the resulting proof before it is published in its final form. Please note that during the production process errors may be discovered which could affect the content, and all legal disclaimers that apply to the journal pertain.


1. Manson JE, Hu FB, Rich-Edwards JW, et al. A prospective study of walking as compared with vigorous exercise in the prevention of coronary heart disease in women. N Engl J Med. 1999;341(9):650–658. doi: 10.1056/NEJM199908263410904. [PubMed] [Cross Ref]
2. Yaffe K, Barnes D, Nevitt M, Lui LY, Covinsky K. A prospective study of physical activity and cognitive decline in elderly women: women who walk. Arch Intern Med. 2001;161(14):1703–1708. [PubMed]
3. Hurvitz EA, Richardson JK, Werner RA, Ruhl AM, Dixon MR. Unipedal stance testing as an indicator of fall risk among older outpatients. Arch Phys Med Rehabil. 2000;81(5):587–591. [PubMed]
4. Bohannon RW, Larkin PA, Cook AC, Gear J, Singer J. Decrease in timed balance test scores with aging. Phys Ther. 1984;64(7):1067–1070. [PubMed]
5. Richardson JK. Factors associated with falls in older patients with diffuse polyneuropathy. J Am Geriatr Soc. 2002;50(11):1767–1773. [PubMed]
6. MacKinnon CD, Winter DA. Control of whole body balance in the frontal plane during human walking. J Biomech. 1993;26(6):633–644. [PubMed]
7. Bauby CE, Kuo AD. Active control of lateral balance in human walking. J Biomech. 2000;33(11):1433–1440. [PubMed]
8. Hilliard MJ, Martinez KM, Janssen I, et al. Lateral balance factors predict future falls in community-living older adults. Arch Phys Med Rehabil. 2008;89(9):1708–1713. doi: 10.1016/j.apmr.2008.01.023. [PMC free article] [PubMed] [Cross Ref]
9. Richardson JK, Demott T, Allet L, Kim H, Ashton-Miller JA. Hip strength: Ankle proprioceptive threshold ratio predicts falls and injury in diabetic neuropathy. Muscle Nerve. 2013 doi: 10.1002/mus.24134. [PMC free article] [PubMed] [Cross Ref]
10. Cummings SR, Nevitt MC. Non-skeletal determinants of fractures: the potential importance of the mechanics of falls. Study of Osteoporotic Fractures Research Group. Osteoporos Int. 1994;4(Suppl 1):67–70. [PubMed]
11. Son J, Ashton-Miller JA, Richardson JK. Frontal plane ankle proprioceptive thresholds and unipedal balance. Muscle Nerve. 2009;39(2):150–157. doi: 10.1002/mus.21194. [PMC free article] [PubMed] [Cross Ref]
12. Allet L, Kim H, Ashton-Miller J, De Mott T, Richardson JK. Frontal plane hip and ankle sensorimotor function, not age, predicts unipedal stance time. Muscle & Nerve. 2012;45(4):578–585. doi: 10.1002/mus.22325. [PMC free article] [PubMed] [Cross Ref]
13. Deshpande N, Connelly DM, Culham EG, Costigan PA. Reliability and validity of ankle proprioceptive measures. Arch Phys Med Rehabil. 2003;84(6):883–889. [PubMed]
14. Van den Bosch CG, Gilsing MG, Lee SG, Richardson JK, Ashton-Miller JA. Peripheral neuropathy effect on ankle inversion and eversion detection thresholds. Arch Phys Med Rehabil. 1995;76(9):850–856. [PubMed]
15. Frese E, Brown M, Norton BJ. Clinical reliability of manual muscle testing. Middle trapezius and gluteus medius muscles. Phys Ther. 1987;67(7):1072–1076. [PubMed]
16. Noreau L, Vachon J. Comparison of three methods to assess muscular strength in individuals with spinal cord injury. Spinal Cord. 1998;36(10):716–723. [PubMed]
17. Bohannon RW. Manual muscle testing: does it meet the standards of an adequate screening test? Clin Rehabil. 2005;19(6):662–667. [PubMed]
18. Agre JC, Magness JL, Hull SZ, et al. Strength testing with a portable dynamometer: reliability for upper and lower extremities. Arch Phys Med Rehabil. 1987;68(7):454–458. [PubMed]
19. Braddom RL. Physical Medicine and Rehabilitation. Elsevier Health Sciences; 2010.
20. Ashton-Miller JA, Wojtys EM, Huston LJ, Fry-Welch D. Can proprioception really be improved by exercises? Knee Surg Sports Traumatol Arthrosc. 2001;9(3):128–136. [PubMed]
21. Richardson JK, Allet L, Kim H, Ashton-Miller JA. Fibular motor nerve conduction studies and ankle sensorimotor capacities. Muscle Nerve. 2013;47(4):497–503. doi: 10.1002/mus.23618. [PMC free article] [PubMed] [Cross Ref]
22. Apfel SC, Arezzo JC, Lipson L, Kessler JA. Nerve growth factor prevents experimental cisplatin neuropathy. Ann Neurol. 1992 Jan;31(1):76–80. [PubMed]
23. Feldman EL, Stevens MJ, Thomas PK, Brown MB, Canal N, Greene DA. A practical two-step quantitative clinical and electrophysiological assessment for the diagnosis and staging of diabetic neuropathy. Diabetes Care. 1994 Nov;17(11):1281–9. [PubMed]
24. O'Keefe ST, Smith T, Valacio R, Jack CL, Playfer JR, Lye M. A comparison of two techniques for ankle jerk assessment in elderly subjects. Lancet. 1994 Dec 10;344(8937):1619–20. [PubMed]
25. Oyer DS, Saxon D, Shah A. Quantitative assessment of diabetic peripheral neuropathy with use of the clanging tuning fork test. Endocr Pract. 2007 Jan-Feb;13(1):5–10. [PubMed]
26. O'Dell MW, Lin CD, Ponago A. The physiatric history and physical examination. In: Braddom, editor. Physical Medicine and Rehabilitation. 94. Elsevier/Saunders; 2011. p. 14.
27. Brinckmann P, Hoefert H, Jongen HT. Sex differences in the skeletal geometry of the human pelvis and hip joint. J Biomech. 1981;14(6):427–30. [PubMed]
28. McConville JT, Churchill TD, Caleps I, Clauser CE, Cuzzi J. Anthropometric Relationship of Body and Body Segment Moments of Inertia. Air Force Aerospace Medical Research Laboratory Report AFAMRL-TR-80-119. 1980
29. Moisio KC, Sumner DR, Shott S, Hurwitz DE. Normalization of joint moments during gait: a comparison of two techniques. J Biomech. 2003 Apr;36(4):599–603. [PubMed]
30. Thelen DG, Schultz AB, Alexander NB, Ashton-Miller JA. Effects of age on rapid ankle torque development. J Gerontol A Biol Sci Med Sci. 1996 Sep;51(5):M226–32. [PubMed]
31. Aitkens S, Lord J, Bernauer E, Fowler WM, Jr, Lieberman JS, Berck P. Relationship of manual muscle testing to objective strength measurements. Muscle Nerve. 1989;12(3):173–177. doi: 10.1002/mus.880120302. [PubMed] [Cross Ref]
32. Simmons RW, Richardson C, Pozos R. Postural stability of diabetic patients with and without cutaneous sensory deficit in the foot. Diabetes Res Clin Pract. 1997;36(3):153–160. [PubMed]
33. Beckmann YY, Çiftçi Y, Ertekin C. The detection of sensitivity of proprioception by a new clinical test: the dual joint position test. Clin Neurol Neurosurg. 2013;115(7):1023–1027. doi: 10.1016/j.clineuro.2012.10.017. [PubMed] [Cross Ref]
34. Khamwong P, Nosaka K, Pirunsan U, Paungmali A. Reliability of muscle function and sensory perception measurements of the wrist extensors. Physiother Theory Pract. 2010;26(6):408–415. doi: 10.3109/09593980903300470. [PubMed] [Cross Ref]
35. Ekstrom RA, Donatelli RA, Carp KC. Electromyographic analysis of core trunk, hip, and thigh muscles during 9 rehabilitation exercises. J Orthop Sports Phys Ther. 2007;37(12):754–762. doi: 10.2519/jospt.2007.2471. [PubMed] [Cross Ref]
36. Rohmert W. Ermittlung von erholungspausen fur statische arbeit des menschen. Internationale Zeitschrift fur angewandte Physiologie. 1960;18:123–64. [PubMed]
37. Krause DA, Schlagel SJ, Stember BM, Zoetewey JE, Hollman JH. Influence of lever arm and stabilization on measures of hip abduction and adduction torque obtained by hand-held dynamometry. Arch Phys Med Rehabil. 2007;88(1):37–42. doi: 10.1016/j.apmr.2006.09.011. [PubMed] [Cross Ref]
38. Rainville J, Jouve C, Finno M, Limke J. Comparison of four tests of quadriceps strength in L3 or L4 radiculopathies. Spine. 2003;28(21):2466–2471. doi: 10.1097/01.BRS.0000090832.38227.98. [PubMed] [Cross Ref]
39. Allen BA, Hannon JC, Burns RD, Williams SM. Effect of a Core Conditioning Intervention on Tests of Trunk Muscular Endurance in School-Aged Children. J Strength Cond Res. 2013 doi: 10.1519/JSC.0000000000000352. [PubMed] [Cross Ref]