Integrated Functional Electrical Stimulation-Ankle Foot Orthosis Training System

Jennifer Hadley, Jonathan Steer, Kristi Tanouye

ABSTRACT

Cerebral Palsy (CP) is a non-progressive neurological disorder which develops in-utero or after birth. Current treatment for CP includes physical therapy and braces used to increase ambulation. Ankle-Foot Orthoses (AFOs) are lightweight plastic braces that secure the lower leg, ankle, and foot in a predetermined position, commonly used to aide dorsiflexion in CP patients. Another common treatment, Functional Electrode Stimulation (FES), is administered by physical therapists in order to build muscle tone and improve dorsiflexion. FES uses low energy electrical stimulation to excite either the common peroneal nerve or the tibialis anterior muscle, causing the patient to actively dorsiflex, increasing foot-ground clearance. Our device integrates an FES unit with a hinged AFO, to automate and improve the current physical therapy processes used to treat CP patients. This allows for the rapid and accurate placement of FES electrodes, which removes the major barrier to at-home administration of this therapy.

Keywords:

Cerebral Palsy, Physical Therapy, Electrical Stimulation, Ankle-Foot Orthosis

BACKGROUND

Cerebral Palsy is a non-progressive neurological disorder which develops in-utero or after birth, affecting approximately 0.2% of all children born in the United States(1). Cerebral Palsy patients are extremely diverse, and are assigned a Gross Motor Function Classification Score (GMFCM), ranging from I to V(1).

Current Methods

Current treatment for Cerebral Palsy includes physical therapy and a combination of braces and orthotics used to correct motor impairment and increase ambulation. AFOs are lightweight plastic braces that secure the lower leg, ankle, and foot in a predetermined position, and aide in dorsiflexion(2). AFOs can be custom built from plaster molds of a patient’s leg, or bought “off the shelf” according to shoe size and calf circumference(3).  Physical therapists can also use FES devices to build muscle tone and decrease spasticity in patients with CP. FES uses low energy electrical stimulation to generate a muscle contraction by exciting either the common peroneal nerve or the tibialis anterior muscle. Unlike the use of AFOs, FES causes the patient to actively dorsiflex, thus activating and training their underused muscles.

Statement of the Problem

The use of FES devices requires accurate placement of the stimulating electrodes in a specific region of the patients’ lower leg(5). The difficulty associated with caregivers placing these electrodes has prevented these devices from gaining widespread use away from physical therapists’ offices(4). Electrical stimulation from an FES device can be triggered either by a sensor, usually placed beneath the patient’s heel, or manually triggered with a hand-held switch. Many patients with CP walk in a raised “tip-toe” style gait, thus heel sensors may not be activated during their normal walking pattern(4). Therefore, the less-specific manual triggering is more commonly used. Manual triggering is difficult to time to the patient’s gait cycle; this difficulty in triggering leads to imprecise therapy, which translates in to patients not receiving the maximal benefit from this treatment(5).

Scope

Our device integrates an FES unit with an AFO, to automate and improve the current physical therapy processes used to treat patients with CP. Our target patients have been diagnosed with a mild case of CP (GMFCS level I or II) and are not afflicted with a severe crouch-type gait. Ideally, they will have 5° to 25° of passive ankle dorsiflexion, so that when their muscle is activated, the foot has the required range of motion to dorsiflex.

DESIGN AND DEVELOPMENT

This image shows a CAD drawing (left) and photo (right) of the completed AFO design.  This demonstrates that the AFO will be hinged and grooves will be created during manufacturing to place the wires within the AFO. Figure 1. (Click for larger view)

Through conversations with clinicians and orthotists, we set our to determine a set of design requirements for our device. We choose our final design through a system of weighting various categories and scoring options, choosing the option which ranked highest for all categories, reflected in the Pugh charts below.

Design Requirements

Our original qualitative requirements specified that the device be safe, comfortable, customizable, reproducible, and modular. It was also required that the device be easy to apply so that the parent or caregiver be able to easily place and control the device without the supervision of a physical therapist. Quantitative design specifications are presented in Table 1, and provide the technical specifications for this device.

Table 1 Design Specifications: This table displays the quantitative design requirements of the AFO and FES components of the device.
Design Specifications Applicable Metric (AFO) Applicable Metric (FES)
Small Thickness of plastic: 3mm-5mm 25mm x 70mm x 150mm
Lightweight Does not impede patient’s gait 200g with battery
Low cost ≤ $800 per brace ≤ $1250 per system
Accurate placement of electrodes -------------- ± 1cm around PT’s suggested placement
Patient sensitivity/Signal level Does not change the fit of AFO At least 10 discrete amplitude settings
Length of use During normal activity Up to full day, as determined by PT
Reliable Last ≥ 3 years (or until outgrown) 95% accuracy of stimulation firing
Durable Withstand ≥ 2.2 kN Withstand 2N of force if dropped
Battery Output -------------- 9V
Lifespan of electrodes -------------- ~ 2-3 weeks
Lifespan of sensor -------------- Withstand ≥ 2.2 kN
Number of channels -------------- ≥ 1 channels
Force can withstand (footswitch) -------------- ≥ force of patient during normal activity
Repetition (footswitch) -------------- Withstand normal daily activity
Current Amplitude per channel -------------- 15 to 100mA into a 1k ohm load with a asymmetrical biphasic output, 10mA to 70mA in symmetrical biphasic mode
Waveform type -------------- Asymmetrical or symmetrical biphasic voltage driven wave form
Pulse Frequency -------------- 40Hz
Pulse Width -------------- 3 to 350 microsec
Output time -------------- 0.5 to 6 sec
Extension time -------------- 0 to 1.5 sec
Ramping times -------------- 0 to 4 sec
AFO Strength Will sufficiently support patient --------------
AFO Durability Last ≥ 3 yrs or until outgrown --------------
AFO flexibility Provides support but does not fail --------------
Heat strength of wires and coverings (during production/alterations) -------------- Can withstand temperatures of hot polypropylene 180⁰-200⁰C
Lifespan of Velcro ≥ lifespan of AFO ≥ lifespan of FES
Lifespan of snaps ≥ lifespan of AFO ≥ lifespan of FES
Lifespan of wires -------------- ≥ 6 months
Lifespan of FES device (internal components) -------------- ≥ 10 years
Battery Life -------------- ≥ 2 weeks
Operating temperature range of everything -18⁰ through 93⁰ C 0⁰ through 38⁰ C
Minimum electrode separation (based on diameter) -------------- ≥ 1.25”

Design Alternatives and Prototype

This image shows a CAD drawing (left) and photo (right) of the completed Electrode Flap design. The flap will be custom fit to the patient and the electrode placement will be determined by the physical therapist.  The electrodes will attach to the flap with Velcro. The flap will attach to the AFO with a nylon strap and snap on one side for precise electrode placement and a Velcro strap on the other to insure a snug fit to the patient’s leg. Figure 2. (Click for larger view)

In order to choose the most appropriate design, several options were considered for each of component of the device (FES, AFO, and integration). Each option was evaluated using a weighted Pugh analysis, shown in Tables 2-6, which ultimately determined the final design. The final design incorporates a custom-made, hinged AFO into which grooves for the sensor and the wires of the FES device are molded. A small, rectangular plate was added to the anterior face of the shin to attach the surface muscle electrodes. This mechanism allows for electrode positioning to be pre-set by a physical therapist prior to use of the device. The sensor was placed beneath the metatarsal line of the affected foot. Wires run along the inside of the AFO in pre-molded groves, connecting the sensor and electrodes to the commercially available FES unit, which is attached to the proximal, posterior side of the AFO using Velcro. A summary of this design is shown in the CAD drawings and photos in Figures 1-3. A primary prototype was manufactured for a group member who does not have CP, according to the specifications outlined above.

Table 2  AFO Fabrication Pugh Chart: This table is a Pugh chart comparing the possible AFO fabrication methods.  Since this design is highly customized to the patient, a custom-made AFO will be used.

Category

weight

Custom-made AFO

Pre-fabricated AFO

Safe (for our patient group) 5 5 3
Ease of Integration 5 4 2
Ease of Movement 5 5 5
Comfort 4 4 2
Ease of Use 4 4 5
Cost 4 2 5
Applicability 4 5 2
Reproducibility 3 3 5
Size (small) 3 4 4
Lightweight 3 4 5
Reliable 3 5 3
Durable 3 5 4
Customizable 2 5 1
Removable when not in use 1 5 5
Total
  206 125

 

Table 3 AFO Type Pugh Chart: This table is a Pugh chart comparing the possible types of AFOs.  In order to allow movement of the foot a hinged AFO must be used.
Category weight Ulraflex Hinged AFO Unhinged AFO Leaf Spring
Safe (for our patient group)
5
3
5
5
1
Ease of Integration
5
2
3
3
3
Ease of Movement
5
1
5
1
5
Movement Training
5
1
5
1
4
Comfort
4
1
4
3
4
Ease of Use
4
3
4
4
4
Cost
4
2
3
4
4
Reproducibility
3
5
3
4
3
Size (small)
3
1
4
4
4
Lightweight
3
1
4
4
4
Reliable
3
5
5
5
3
Durable
3
5
4
5
1
Customizable
2
1
5
5
5
Removable
1
3
5
5
3
Total
117
213
178
173

 

Table 4 Electrode Type Pugh Chart: This table is a Pugh chart comparing the possible electrode types.  Surface electrodes are non-invasive and the clear choice for this design.

Category

weight

Surface Electrodes

Implanted Electrodes

Safety
5
5
3
Ease of Use
5
4
5
Integration
5
3
5
Reproducibility
5
4
5
Cost
4
5
1
Applicability
4
5
1
Comfort
4
4
3
Maintenance
4
4
1
Control of Movement
3
5
3
Energy Use
3
3
4
Appearance
2
3
4
Total
182
143

 

Table 5 Stimulation Location Pugh Chart: This table is a Pugh chart comparing the possible FES stimulation locations.  The muscle is the superior choice.

Category

weight

Muscle

Peroneal Nerve

Safety

5
5
2

Ease of Use

5
5
3

Integration

5
5
3

Reproducibility

5
4
3

Cost

4
5
4

Applicability

4
5
2

Comfort

4
3
4

Maintenance

4
5
5

Control of Movement

3
5
3

Energy Use

3
3
5

Appearance

2
4
3

Total

199
145

 

Table 6 Sensor Type Pugh Chart: This table is a Pugh chart comparing the possible types of sensors that can be used with the FES device.  The pressure sensor is the best choice for this design.

Category

weight

Pressure Sensors

Tilt Sensors

Accelerometer

EMG

Accuracy

5
3
3
3
2

Safety

5
5
5
5
3

Reliability

5
5
3
4
2

Applicability

5
5
3
5
4

Ease of Integration

5
5
5
5
3

Cost

4
5
3
3
2

Durability

4
3
5
5
5

Movement Training

4
1
1
1
5

Size

3
5
3
3
3

Total

166
137
155
127

 

Figures 1-3 go here

 

EVALUATION

Performance

This image shows the completed prototype on the user.  This demonstrates that the AFO and electrode flap fits snugly on the patient’s leg and foot. The FES control unit is attached to the back of the AFO and the amount of free wires is limited.  The sensor and wire within the AFO are not visible when the device is in use. Figure 3. (Click for larger view)

Testing of our device included verifying that the FES device worked after shortening and embedding the wires, sensor, and stimulating electrodes. We found this to be the case, and demonstrated that persons unfamiliar with our device could easily apply the device so that accurate electrical stimulation was achieved.

Safety Analysis

A thorough analysis of the safety of this device during both production and patient use was performed using DesignSafe (Design Safety Engineering); a summary of this analysis is shown in Table 7. Our analysis shows that this device is safe to produce and to use. Additionally, there are simple steps that can be implemented to further reduce risks, detailed in Table 7.

Cost

Because medical devices can be prohibitively expensive, we took great care to keep costs of our modifications reasonable. Table 8 details the actual cost of building our prototype, and estimates the cost for producing this device for patients. Additionally, while our modifications added time to the production of the AFO, this was not significant compared to the total production time, and is not reflected in Table 8.

Table 8 Cost Chart: This table displays the actual cost to manufacture one device
Component Price Comments

Odstock ODFSIII + Foot Switch

$1,250.00

 

Metal Snaps

$2.92

 

Velcro Strips

$2.79

 

Wire Connectors

$1.90

 

Dummy Wire

$1.50

 

Electrodes

$0.00

Included with FES

Battery

$0.00

Included with FES

AFO Production and Labor

$0.00

Donated (est. cost: $315.00)

 

$1,259.11

 

NEXT STEPS

We are continuing to pursue approval for human studies through our Institutional Review Board; after receiving approval, we will test our device on a small cohort of patients and evaluate its efficacy using gait analysis. After evaluating our device’s use on these patients, we plan on publishing our results in order that the entire orthopedic community could benefit from this research.

REFERENCES

  1. Rosenbaum et. al. “Development of the Gross Motor Function Classification System: Reliability and Validity Results.” Neurodevelopmental Clinical Research Unit. 2005
  2. “Ankle Foot Orthoses” Cascade Dynamic Ankle Foot Orthoses.  Accessed: September 16 2007. <http://www.dafo.com>
  3. Smith CO LO, Keith. Interview, October 20, 2007. Orthotics & Prosthetics Labs, Inc.
  4. Brunstrom MD, Janice. Interview, September 15, 2007. Associate Professor, Washington University School of Medicine, Director, Pediatric Neurology Cerebral Palsy Clinic.
  5. Lyons.  “A Review of Portable FES-Based Neural Orthoses for the Correction of Drop Foot.” IEEE Transactions on Neural Systems and Rehabilitation Engineering.  Vol.  10, No.  4, Pgs 260-276.  December 2002.

AKNOWLEGEMENTS

We would like to thank Janice Brunstrom, MD and Keith Smith, CO LO for their generous financial support of this project, as well as Joseph Klaesner, PhD, and Freda Branch for all of their assistance.

CONTACT INFORMATION

Jennifer Hadley, 7899 West FM 321, Tennessee Colony, TX 75861

(903) 920-1311, jahadley@gmail.com