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Analyzing the forces within
transtibial prosthetic sockets
and design of an improved
force minimizing socket
Christine Bronikowski, Amanda Chen, Jared
Mulford, Amy Ostrowski
Advisor: Aaron Fitzsimmons, The Surgical Clinic
Problem Statement
Lack of research in the socket interface between
the artificial limb and the residual limb,
specifically force profiles
Majority of the research focused on components
with higher potential financial gains
Problems with skin irritation, varying degrees of
pain, tissue breakdown, pressure ulcerations,
and resultant infections at the socket interface
develop
Project Goals
Acquire accurate measurements of the forces
acting on the residual limb of an amputee
during various movements
Determine areas of highest force
Design a socket system in which the forces
are optimally distributed throughout the crosssection of the surface between the residual
limb and socket
Increase overall patient comfort
Current Socket Designs
Designed on a case-by-case basis for individual
patients
Method of Force Analysis
Force Sensing Resistor (FSR) placed directly in socket
Very thin-will not cause variation in force determination
Change in resistance when force is applied, converted
to a voltage difference
QuickTime™ and a
TIFF (Uncompressed) decompressor
are needed to see this picture.
Current Work
Circuit design: current to voltage converter
QuickTime™ and a
TIFF (Uncompressed) decompressor
are needed to see this picture.
QuickTime™ and a
TIFF (Uncompressed) decompressor
are needed to see this picture.
Design/Safety Considerations
Sensitivity/saturation of FSR may not be
within desired force range
Wire thickness: thin enough to prevent
interference with force data
Thick enough to not break during
movement/walking
FSR-wire connection: must be durable due to
movement of limb
Low temperature solder: must not melt FSR plastic
Future Work
Insertion of ~15 FSRs into limb-socket interface of
“model” patient, Cody
Test run: determine if FSR saturates, stays intact,
comfort and safety of Cody
Repeat with ~10 patients
Rotate FSRs within socket to cover entire area
Test multiple surfaces (incline, flat, stair)
Analyze results, determine location of maximum force
Design and develop a new socket: provide more
flexibility in areas of greatest force
Determination of Success
Design is patient-driven
Survey and level of comfort pre and post
new socket
References
Engsberg, J.R., Springer, M.J.N., and J.A. Harder. (1992). Quantif ying interface
pressures in below-knee-amputee sockets. J Assoc Child Prosthet Orthot Clin 27(3),
81-88.
Houston, V. L., Mason, C.P., LaBlanc, K.P., Beattie, A.C., Garbarini, M.A., and E.J.
Lorenze. Prelim ary results with the DVA-Tekscan BK prosthetics socket: residual
lim b stress measurement system. In: Proceedings fo the 20t h Ann ual Meeting
American Academy of Orthotist and Prosthetist, Nashvill e TN. P 8-9
Jendrzejczyk, D. J. (1985). Flexible Socket Systems. Cli n. Prosthet. Orthot. 9 (4), 27-31.
Lee, W.C., and M. Zhang. Using computational sim ulation to aid in the prediction of
socket fit: a prelimi nary study. Med Eng Phys. 2007 Oct;29(8):92 3-9.
Polli ack, A.A., Sieh, R.C., Craig, D.D., Landsberger, S., Mcneil , D.R., and E. Ayyappa.
Scientifi c vali dation of two comm ercial pressure sensor systems for prosthetic socket
fit. Prosthetics and Orthotics International, 2000, 24, 63-73.
Sanders, J.E., Daly , C.H., and E.M. Burgess (1993). Cli nical measurement o f normal
shear stresses on a transtibial stump: Characteristics of wave-form shapes during
walking. Prosthet Orthot Int 17, 38-48.