Search

O&P Library > POI > 1996, Vol 20, Num 2 > pp. 132 - 137

ISPO

The International Society for Prosthetics and Orthotics (ISPO), is a multi-disciplinary organization comprised of persons who have a professional interest in the clinical, educational and research aspects of prosthetics, orthotics, rehabilitation engineering and related areas.


ISPO Home



You can help expand the
O&P Virtual Library with a
tax-deductible contribution.

View as PDF

with original layout

Stiffness control in posterior-type plastic ankle-foot orthoses: effect of ankle trimline Part 2: orthosis characteristics and orthosis/patient matching

T. SUMIYA*
Y. SUZUKI*
T KASAHARA*

Abstract

The hingeless plastic ankle-foot orthosis (AFO) changes stiffness largely depending on how much plastic is trimmed around the ankle. To support proper selection of the orthosis and final adjustment of the orthotic stiffness, the correlation between the posterior upright width and the resistance to dorsi- and plantar flexion movements was measured in 30 posterior-type plastic AFOs. Hie posterior upright width was varied by regularly trimming around the ankle in nine stages. The resistance to dorsi- and plantar flexion movements was measured by bending the plastic AFOs 15 with the measuring device described in Part l. All the plastic AFOs decreased in their resistance to both movements in proportion to the reduction of the posterior upright width. The maximum resistance to plantar flexion movement was about 28 Nm, which was strong enough to assist dorsiflexion in patients with severe spasticity. On the other hand, the maximum resistance to dorsiflexion movement measured was about 10 Nm, which was insufficient to stabilise the ankle in patients who lacked in plantar flexion strength. These findings suggested that this type of plastic AFO should be prescribed for patients who predominantly require dorsiflexion assist, and that the orthotic stiffness could be finally adjusted by trimming to exactly meet individual requirements.

Introduction

The plastic ankle-foot orthosis (AFO) assists the swing phase by maintaining the ankle in a neutral position, controlling plantar flexion immediately after heel contact to absorb the impact of body weight, and supporting forward propulsion of the body by stabilising the ankle during terminal stance. It also controls eversion and inversion to provide adequate mediolateral stability.

Plastic AFOs without ankle joint articulations provide these functions in relation to the stiffness of the plastic around the Achilles tendon region. The ankle trimline is the most important among the several factors which affect the stiffness (Stills, 1975; Stills, 1977). Final adjustment of the ankle trimline is needed to meet the individual patient's requirements exactly even with proper selection of orthosis.

There are prescription criteria provided for plastic AFOs without quantitative data to define the final adjustment (LeBlanc, 1973; Lehmann, 1979; Lehneis et al ., 1973; Sarno and Lehneis, 1971; Sarno, 1973). The influence of the ankle trimline on orthotic stiffness has been evaluated without consistently regulating the trimming form (Condie and Meadows, 1977; Lehmann et al ., 1983; Rubin and Dixon, 1973) The objective of this research was to analyse quantitatively the change in orthotic stiffness corresponding with regulated ankle trimlines, and to advance prescription criteria. The posterior-type of AFO was selected for analysis because of its high frequency of prescription (Ofir and Sell, 1980; Sumiya etal, 1993).

Materials and methods

Laboratory experiments
Two experienced orthotists fabricated 30 posterior type plastic AFOs, 24 for patients and 6 for healthy adults, from 3 mm thick standard grade polypropylene using the vacuum forming technique. The proximal trimline was set 3 cm below the fibular head and the distal trimline was extended to the end of the toes.

The ankle axis was positioned as shown in Fig. 1 to serve as a fulcrum for bending the orthosis with a lever. Although this axis did not coincide with the anatomical ankle axis (Isman and Inman, 1969), it was considered from previous test experience to be appropriate. The following opinions support this consideration. The talocrural and subtalar joints act together to create a universal joint-like linkage between the leg and the foot (Wright et al , 1964). However, the orthotic ankle axis allows the talocrural joint alone to move. Accordingly, orthotic and anatomical ankle axes should not be congruent (Kubota, 1981).

Ankle trimlines consisted of circular arcs and their tangents ( Fig. 2 a). The centres of the arcs were placed on the ankle axis as defined above. The tangents and other straight lines were extended to complete the entire trimline according to the dimensions of the orthosis. The nine different radii, 20%, 25%, 30% . . . , 60% of the lateral malleolus height, provided the nine-stage trimlines.

Endoskeleton below-knee models were prepared for each plastic AFO to be dorsi- and plantar flexed artificially in a manner which resembles actual deformation during walking ( Fig. 2 b). The leg and foot parts were moulded from plaster and fixed to the plastic AFO with a calf-strap and screws. The leg part slid smoothly along the pipe by using a lubricant.

The orthosis-model complex was placed horizontally , as described in Part 1, to eliminate the influence of gravity on the ankle movements ( Fig. 3 ). The ankle was dorsi- and plantar flexed 15 at intervals of 2.5, similar to the normal ankle angle range during walking (Peizer et al , 1969; Stauffer et al ., 1977; Sutherland et al , 1980). The ankle movement was measured 10 times at each angle. The orthosis was permitted to recover by leaving appropriate intervals between the measurements.

Simultaneous clinical assessment
A 55 year-old male with left sided hemiplegia, one of the 24 patients, wore the nine-stage trimmed orthosis. He had severe spasticity in the affected limbs with limited ankle dorsiflexion range. Careful observation of gait patterns and interview questions were made at each trimline stage to determine the optimal trimline for this particular patient.

Results

Laboratory experiments
A mean of 10 measurements was taken at each deflection throughout the experiments. The ankle moment measured with this device represents an approximately static situation.

The results of tests on 30 plastic AFOs are summarised in Figure 4, displaying the resistance to 5 and 15 of dorsi- and plantar flexion corresponding to each trimline stage. The results showed variation in the stiffness of the plastic AFOs. Both resistance to dorsi- and plantar flexion movements decreased almost in inverse proportion to the trimline stages.

The maximum resistance to plantar flexion movement measured was 27.5 Nm, SD 7.2 Nm when plantar flexed 15, whereas that to dorsiflexion movement was measured as 10.5 Nm, SD 2.7 Nm when dorsiflexed 15.

Clinical assessment
The subject displayed changes in his gait pattern with changing trimline. Without an orthosis, the stance phase started with toe-contact. With a 20% trimmed orthosis, the stance phase started with heel-contact accompanied by rapid knee flexion. With 30% trimming, plantar flexion occurred immediately after heel-contact and dorsiflexion during the terminal stance became apparent. With 40%, he progressed forward smoothly with the ankle dorsiflexed during the terminal stance. With 50%, he could achieve heel-off just before pre- swing. With 60%, the stride length on the sound side increased, but stability during the stance phase on the affected side decreased and toe-dragging appeared at pre-swing.

Discussion

The above statements offer the biomechanical grounds for the interpretation of the results.

A locked ankle orthosis provides good toe clearance during the swing phase and spasticity inhibition for hemiplegics (Perry, 1969). However, the rigid plantar flexion stop makes the knee unstable by producing a flexion moment at heel strike. The dorsiflexion assist with spring reduces the knee flexion moment by plantar flexing at heel strike without accelerating spasticity (Lee and Johnston, 1973; Lee and Johnston, 1974). The requirements for dorsiflexion assist for toe clearance during the swing phase and for knee stabilisation at heel strike complement each other. The former should be set at a minimum to permit the latter in flaccid paralysis (Lehmann et al ., 1970; Lehmann, 1979; Lehmann et al , 1986). These findings suggest that the orthotic dorsiflexion assist should be minimised such that the swing phase can be carried out safely.

The triceps surae muscle resists dorsiflexion to stabilise the ankle and the knee during the midstance (Perry, 1992; Simon et al , 1978; Sutherland et al , 1980), which contributes to forward propulsion of the body during the terminal stance (Brandel, 1976; Dubo et al , 1976; Inman, 1966; Perry, 1974; Winter, 1983). The orthosis with anterior stop successfully substitutes for this muscle function in flaccid paralysis (Lehmann and Delateur et al ., 1980; Lehmann et al ., 1985; Perry et al ., 1995).

On the other hand there is no established indication for plantar flexion assist in spastic paralysis. Hemiplegic patients exhibit weak plantar flexors (Peat et al ., 1976). The anterior stop assists them to achieve heel-off, resulting in push-off phase elongation (Lehmann et al ., 1987). On the contrary, the hinged plastic APO with free dorsiflexion reduces spasticity in children with cerebral palsy by stretching the Achilles tendon and saves quadriceps muscle energy consumption (Middleton et al , 1988). Therefore, the orthotic plantar flexion assist should be determined comprehensively on the basis of muscle tone, gait pattern, and energy consumption.

The results can be interpreted based on the above considerations ( Fig. 4 ). Curve-pfl5 indicates the dorsiflexion assist at heel-strike for controlled plantar flexion, curve-pf5 curve the moment necessary for toe clearance during the swing phase, curve-df5 the resistance to dorsiflexion during the midstance for knee stabilisation, and curve-dfl5 the moment opposing free dorsiflexion during the terminal stance. These four requirements must be considered in matching the orthosis to the individual.

The maximum resistance to plantar flexion movement, about 28 Nm in curve-pfl5, is strong enough to control plantar flexion immediately after heel strike in patients with severe spasticity. However, the maximum resistance to dorsiflexion movement, about 10 Nm in curve-dfl5, is insufficient to prevent the ankle from breaking down into dorsiflexion during the terminal stance in patients with complete plantar flexor paralysis (Lehmann et al , 1985). In this case, reinforcement of the orthosis will be necessary to provide sufficient ankle support (Clark and Lunsford, 1978; Fillauer, 1981).

The availability of the four moment curves for the final adjustment of the ankle trimline is illustratively demonstrated in the case of the hemiplegic patient ( Fig. 5 ). He required dorsiflexion assist exceeding 1.6 Nm (50% trimline) for toe clearance during the swing phase, but less than 14.4 Nm (40% trimline) for controlled plantar flexion at heel strike. Therefore, the trimlines from 40% to 50% produced the optimal dorsiflexion assist for this patient. On the other hand, he required as much ankle dorsiflexion as possible to transfer the centre of gravity forward during the midstance, overcoming the structural ankle stiffness (Thilman et al , 1991). Consequently, the 50% trimline created the best condition in the posterior-type plastic AFO, and fortunately was a good match. An articulated plastic AFO with free dorsiflexion could possibly replace the posterior-type if the same resistance to plantar flexion was available.

Conclusion

The posterior-type plastic AFO decreased in resistance to dorsi- and plantar flexion movements nearly in proportion to the reduction of posterior upright width. The maximum resistance to plantar flexion movement was sufficient to assist dorsiflexion even under severe spasticity, but that to dorsiflexion movement was only about a third of the former. Accordingly plastic AFOs of this type should be prescribed for patients who predominantly require dorsiflexion assist, and the ankle stiffness must be adjusted by trimming to provide the optimal degree of support.

Acknowledgements

This work was supported by the Japanese Labour Welfare corporation. The authors wish to acknowledge their gratitude to Dr Kyu-Ha Lee, Veterans Administration Medical Centre, New York, USA, for his helpful comments for this study.

References:

  1. Brandel BR (1977). Functional roles of the calf and vastus muscles in locomotion. Am J Phys Med 56 , 59-74.
  2. Clark DR, Lunsford TR (1978). Reinforced lower-limb orthosis-design principles. Orthot Prosthet 32(2) , 35-45.
  3. Condie DN, Meadows CB (1977). Some biomechanical considerations in the design of ankle-foot orthoses. Orthot Prosthet 31(3) , 45-52,
  4. Dubo HIC, Peat M, Winter DA, Quanbury AO, Hobson
  5. DA, Steinke T, Reimer G (1976). Electromyographic temporal analysis of gait: normal human locomotion. Arch Phys Med Rehabil 57 , 415-420.
  6. Fillauer C (1981). A new ankle foot orthosis with a moldable carbon composite insert. Orthot Prosthet 35(3) , 13-15.
  7. Inman VT (1966). Human locomotion. Can Med Assoc J 94 , 1047-1054.
  8. Isman RE, Inman VT (1969). Anthropometric studies of the human foot and ankle. Bull Prosthet Res 10(11) , 97-129.
  9. Kubota T (1981). Abnormal gait patterns in stroke patients with hemiplegia and their correction with lower-extremity orthotics: biomechanical considerations. In: Lower-extremity orthotics for stroke patients with hemiplegia./edited by the Japanese Society of Prosthetics and Orthotics. -Tokyo: Ishiyakushuppan. p 33-48.
  10. LeBlanc MA (1973). Clinical evaluation of a comprehensive approach to below-knee orthotics. Orthot Prosthet 27(2) , 20-29.
  11. Lee K, Johnston R (1973). Bracing below the knee for hemiplegia: biomechanical analysis. Arch Phys Med Rehabil 54 , 466-470.
  12. Lee K, Johnston R (1973). Biomechanical comparison of 90-degree plantar- flexion stop and dorsiflexion-assist ankle braces. Arch Phys Med Rehabil 54 , 302-306.
  13. Lee K, Johnston R (1974). Effect of below-knee bracing on knee movement: biomechanical analysis. Arch Phys Med Rehabil 55 , 179-182.
  14. Lehmann JF, Warren CG, Delateur BJ (1970). A biomechanical evaluation of knee stability in below knee braces. Arch Phys Med Rehabil 51 , 688-695.
  15. Lehmann JF (1979). Biomechanics of ankle-foot orthoses: prescription and design. Arch Phys Med Rehabil 60 , 200-207.
  16. Lehmann JF, Ko MJ, Delateur BJ (1980). Double-stopped ankle-foot orthosis in flaccid peroneal and tibial paralysis: evaluation of function. Arch Phys Med Rehabil 61 , 536-541.
  17. Lehmann JF, Esselman PC, Ko MJ, Smith JC, Delateur BJ, Dralle AJ (1983). Plastic ankle-foot orthoses: evaluation of function. Arch Phys Med Rehabil 64 , 402-407.
  18. Lehmann JF, Condon SM, Delateur BJ, Smith JC (1985). Ankle-foot orthoses: effect on gait abnormalities in tibial nerve paralysis. Arch Phys Med Rehabil 66 , 212-218.
  19. Lehmann JF, Condon SM, Delateur BJ, Price R (1986). Gait abnormalities peroneal nerve paralysis and their corrections by orthoses: a biomechanical study. Arch Phys Med Rehabil 67 , 380-386.
  20. Lehmann JF, Condon SM, Price R, Delateur BJ (1987). Gait abnormalities hemiplegia: their correction by ankle-foot orthoses. Arch Phys Med Rehabil 68 , 763-771.
  21. Lehneis HR, Marx HW, Sowell TT (1973). Bioengineering design and development of lower-extremity orthotic devices. Bull Prosthet Res 10(20) , 132-202.
  22. Middleton EA, Hurley GRB, McIlwain JS (1988). The role of rigid and hinged polypropylene ankle-foot -orthoses in the management of cerebral palsy: a case study Prosthet Orthot Int 12 , 129-135.
  23. Ofir R, Sell H (1980). Orthoses and ambulation in hemiplegia: a ten year retrospective study. Arch Phys Med Rehabil 61 , 216-220.
  24. Peat M, Dubo HIC, Winter DA, Quanbury AO, Steinke T, Grahame R (1976). Electromyographic temporal analysis of gait: hemiplegic locomotion. Arch Phys Med Rehabil 57 , 421-425.
  25. Peizer E, Wright DW, Mason C (1969). Human locomotion. Bull Prosthet Res 10(12) , 48-105.
  26. Perry J (1969). Lower-extremity bracing in hemiplegia. Clin Orthop 63 , 32-38.
  27. Perry J (1974). Kinesiology of lower extremity bracing. Clin Orthop 102 , 18-31.
  28. Perry J (1992). Gait analysis: normal and pathological function. - New York: Slack.
  29. Perry J, Fontaine JD, Mulroy S (1995). Findings in post-poliomylitis syndrome. J Bone Joint Surg 77A , 1148-1153.
  30. Rubin G, Dixon M (1973). The modem ankle-foot orthoses (AFO's). Bull Prosthet Res 10(19) , 20-41.
  31. Sarno JE, Lehneis HR (1971). Prescription considerations for plastic below-knee orthoses. Arch Phys Med Rehabil 52 , 503-510.
  32. Sarno JE (1973). Below-knee orthoses: a system for prescription. Arch Phys Med Rehabil 54 , 548-552.
  33. Simon SR, Mann RA, Hagy JL, Larsen LJ (1978) Role of the posterior calf muscles in normal gait. J Bone Joint Surg 60A , 465-472.
  34. Stauffer RN, Chao EYS, Brewster RC (1977). Force and motion analysis of the normal, diseased and prosthetic ankle joint. Clin Orthop 127 , 189-196.
  35. Stills M (1975). Thermoformed ankle-foot orthoses. Orthot Prosthet 29(4) , 41-51.
  36. Stills M (1977). Lower-limb orthotics. Orthot Prosthet 31(4) , 21-30.
  37. Sumiya T, Kasahara T, Suzuki Y (1993). A trend study of plastic ankle-foot orthoses in Japan. Bull Jap Soc Prosthet Orthot 9 , 427-431.
  38. Sutherland DH, Olshen R, Cooper L, Woo SLY (1980). The development of mature gait. J Bone Joint Surg 62A , 336-353.
  39. Sutherland DH, Cooper L, Daniel D (1980). The role of the ankle plantar flexors in normal walking J Bone Joint Surg 62A , 354-363.
  40. Thilmann AF, Fellows SJ, Ross HF (1991). Biomechanical changes at the ankle joint after stroke J Neurol Neurosurg Psychiatry 54 , 134-139.
  41. Winter DA (1983). Energy generation and absorption at the ankle and knee during fast, natural, and slow cadences. Clin Orthop 175 , 147-154.
  42. Wright DG, Desai SM, Henderson WH (1964). Action of the subtalar and ankle-joint complex during the stance phase of walking. J Bone Joint Surg 46 , 361-382.

O&P Library > POI > 1996, Vol 20, Num 2 > pp. 132 - 137

The O&P Virtual Library is a project of the Digital Resource Foundation for the Orthotics & Prosthetics Community. Contact Us | Contribute