The reviewed record of science sign in
Pith

arxiv: 2606.04222 · v1 · pith:LI57KYCS · submitted 2026-06-02 · cs.RO

Towards Estimating Normal and Shear Interface Pressures in Prosthetic Sockets via Least Squares and Mechanics Modeling

Reviewed by Pith2026-06-28 09:35 UTCgrok-4.3pith:LI57KYCSopen to challenge →

classification cs.RO
keywords prosthetic socketsinterface pressureshear stressleast squaresmechanical modelingresidual limbsensor validation
0
0 comments X

The pith

A quasi-static spring-mass model fitted by two-stage least squares explains both global wrench and sparse local normal and shear pressures once bias terms are estimated.

A machine-rendered reading of the paper's core claim, the machinery that carries it, and where it could break.

The paper introduces a testbed and analysis method to evaluate whether a mechanical model can recover interface pressures, including shear, from limited measurements in prosthetic sockets. It fits a quasi-static spring-mass contact model to two kinds of data: the total forces and moments transmitted through the socket and the decoupled normal and shear readings from small clusters of capacitance sensors. Parameters are found by solving a convex least-squares problem in two stages. Under controlled static loads, adding constant bias terms to the fit reduces steady offsets in the global channels and brings the model outputs closer to the local sensor readings. The work also maps how the balance between matching global and local data shifts when bias is included.

Core claim

A quasi-static spring-mass contact model whose parameters are recovered via two-stage convex least-squares, together with constant bias terms, accounts for both the global wrench transmitted through an artificial residual limb and the local normal and shear pressures recorded at sparse instrumented sites, as evidenced by reduced offsets and improved point-wise agreement under static loading.

What carries the argument

Two-stage convex least-squares identification of the parameters of the quasi-static spring-mass contact model, performed once with and once without constant bias terms.

If this is right

  • Estimating constant bias terms reduces steady offsets in the wrench channels.
  • Including bias terms improves agreement between model predictions and local normal and shear measurements.
  • A Pareto-front sensitivity analysis shows that the trade-off between global and local fitting objectives changes when bias terms are added.
  • The approach provides a quantitative way to assess candidate mechanical models against both global and local validation signals under sparse sensing.

Where Pith is reading between the lines

These are editorial extensions of the paper, not claims the author makes directly.

  • The same fitting procedure could be tested on dynamic or walking loads to check whether the quasi-static assumption still holds.
  • If the bias terms prove repeatable across users, they might be pre-calibrated rather than re-estimated for each socket fitting session.
  • The method supplies shear estimates without requiring shear sensors at every location, which could be combined with finite-element socket design tools.
  • Extending the sensor clusters to more sites would allow direct comparison of the model's full-field predictions against denser ground truth.

Load-bearing premise

The quasi-static spring-mass contact model is an adequate representation of the residual limb-socket interface mechanics for the controlled static loading conditions tested.

What would settle it

Under the same static loading protocol, the model predictions after bias estimation still show large systematic mismatches with the measured local normal and shear pressures at the instrumented sites.

Figures

Figures reproduced from arXiv: 2606.04222 by Axel Gonz\'alez Cornejo, Chi Hwan Lee, Edgar Bol\'ivar-Nieto, Tianhao Yu.

Figure 1
Figure 1. Figure 1: Testbed for controlled socket–limb contact, allowing synchronous [PITH_FULL_IMAGE:figures/full_fig_p002_1.png] view at source ↗
Figure 2
Figure 2. Figure 2: Pressure-sensing on the socket interior (Brim–Lateral, Mid– [PITH_FULL_IMAGE:figures/full_fig_p002_2.png] view at source ↗
Figure 3
Figure 3. Figure 3: Schematic of the lumped-parameter contact model (shown in 2D [PITH_FULL_IMAGE:figures/full_fig_p003_3.png] view at source ↗
Figure 4
Figure 4. Figure 4: Global wrench: measured (gray) vs. model (red) for the stiffness [PITH_FULL_IMAGE:figures/full_fig_p005_4.png] view at source ↗
Figure 5
Figure 5. Figure 5: Global wrench: measured vs. model for the stiffness-plus-bias [PITH_FULL_IMAGE:figures/full_fig_p005_5.png] view at source ↗
Figure 6
Figure 6. Figure 6: Local forces at the four pressure-sensor clusters: measured (gray) vs. model (red) for the stiffness-only estimator (bias [PITH_FULL_IMAGE:figures/full_fig_p006_6.png] view at source ↗
Figure 7
Figure 7. Figure 7: Local forces for the stiffness-plus-bias estimator over the same trial. Plot conventions match Fig. 6. [PITH_FULL_IMAGE:figures/full_fig_p006_7.png] view at source ↗
Figure 9
Figure 9. Figure 9: Pareto front for the stiffness-plus-bias estimator. Axes are zoomed [PITH_FULL_IMAGE:figures/full_fig_p007_9.png] view at source ↗
read the original abstract

Prosthetic socket fitting remains largely manual and iterative, and objective fit metrics are still limited. Part of the challenge is the lack of long-term real-life pressure data at the residual limb--socket interface. Traditional pressure sensors are prone to drift over time, and capture only normal pressures at sparse locations within the socket, missing a critical component for biomechanical analysis: shear. Although some sensors can report both normal and shear interface stresses, these components are often difficult to decouple because of measurement crosstalk. One potential path forward is to develop models that can augment available measurements. This work introduces a testbed to evaluate model performance under sparse pressure sensing using two complementary validation signals: (i) the global wrench (\ie, total forces and moments expressed in an orthonormal frame) transmitted through the socket, by an artificial residual-limb, and (ii) local interface loads (\ie, decoupled normal and shear pressure components in a right-hand-rule orthogonal frame that lives in each instrumented location) measured by sparse sensing clusters, each composed of four capacitance-sensing channels. Rather than presenting full-field pressure estimates, the focus is on an analysis sequence that quantifies how well candidate mechanical models explain both global and local measurements under controlled conditions. A quasi-static spring--mass contact model is evaluated, and its parameters are identified via a two-stage convex least-squares problem. Validation under static loading shows that estimating constant bias terms reduces steady offsets in the wrench channels and improves agreement with local measurements. A Pareto-front sensitivity analysis further illustrates how the trade-off between global and local objectives changes when bias terms are included.

Editorial analysis

A structured set of objections, weighed in public.

Desk editor's note, referee report, simulated authors' rebuttal, and a circularity audit. Tearing a paper down is the easy half of reading it; the pith above is the substance, this is the friction.

Referee Report

0 major / 3 minor

Summary. The manuscript introduces a testbed for evaluating mechanical models of the residual limb-socket interface under sparse sensing. It proposes a quasi-static spring-mass contact model whose parameters are recovered via a two-stage convex least-squares procedure. Validation under static loading demonstrates that estimating constant bias terms reduces steady offsets in the global wrench channels and improves agreement with local normal and shear measurements obtained from instrumented sensor clusters. A Pareto-front sensitivity analysis is presented to examine trade-offs between global and local fitting objectives when bias terms are included or omitted.

Significance. If the reported improvements hold, the work supplies a concrete, model-augmented route to estimating both normal and shear interface stresses from limited sensors, directly addressing sensor drift and crosstalk limitations in prosthetic fitting. The dual validation against independent global wrench and local cluster signals, together with the convex two-stage identification procedure, provides a reproducible and falsifiable evaluation framework that strengthens the central claim for controlled static conditions.

minor comments (3)
  1. §3 (model identification): the two-stage convex least-squares procedure is described at a high level; explicit statement of the objective functions, constraints, and how the bias terms enter the first versus second stage would improve reproducibility.
  2. Figure 4 (Pareto fronts): the axes and the precise global/local objective functions being traded off should be labeled with the same symbols used in the text to avoid ambiguity when comparing the bias and no-bias cases.
  3. §4.2 (validation metrics): while qualitative improvement is stated, quantitative values (RMSE or correlation) for wrench and local pressure channels with versus without bias terms should be tabulated for direct comparison.

Simulated Author's Rebuttal

0 responses · 0 unresolved

We thank the referee for the positive evaluation of the manuscript, the recognition of its contributions to model-augmented pressure estimation under sparse sensing, and the recommendation for minor revision. No major comments were provided in the report.

Circularity Check

0 steps flagged

No significant circularity identified

full rationale

The paper identifies parameters of a quasi-static spring-mass contact model via two-stage convex least-squares and validates the effect of adding constant bias terms by direct comparison of model outputs against two independent measurement signals (global wrench and sparse local normal/shear clusters) under static loading. These validation signals are external to the fitted bias parameters and are not defined by the model equations themselves. No self-definitional steps, fitted-input predictions, load-bearing self-citations, or ansatz smuggling appear in the described derivation or validation sequence. The central claim of improved agreement therefore retains independent content relative to its inputs.

Axiom & Free-Parameter Ledger

2 free parameters · 0 axioms · 0 invented entities

Abstract-only review supplies almost no information on free parameters, background axioms, or new entities; bias terms and spring-mass parameters are mentioned but not enumerated or justified.

free parameters (2)
  • constant bias terms
    Estimated to reduce steady offsets in wrench channels; fitted during the two-stage least-squares procedure.
  • spring-mass model parameters
    Identified via convex least-squares; exact count and values not stated in abstract.

pith-pipeline@v0.9.1-grok · 5835 in / 1141 out tokens · 26384 ms · 2026-06-28T09:35:26.237194+00:00 · methodology

discussion (0)

Sign in with ORCID, Apple, or X to comment. Anyone can read and Pith papers without signing in.

Reference graph

Works this paper leans on

41 extracted references

  1. [1]

    C. W. Radcliffe,Functional considerations in the fitting of above-knee prostheses. Biomechanics Laboratory, University of California, 1955

  2. [2]

    The biomechanics of below-knee prostheses in normal, level, bipedal walking

    R. CW, “The biomechanics of below-knee prostheses in normal, level, bipedal walking.”Artificial limbs, vol. 6, pp. 16–24, 1962

  3. [3]

    Concepts of Pressure in an Ischial Containment Socket: Perception:,

    E. S. Neumann, J. S. Wonget al., “Concepts of Pressure in an Ischial Containment Socket: Perception:,”JPO Journal of Prosthetics and Orthotics, vol. 17, no. 1, pp. 12–20, 2005

  4. [4]

    Patient-specific analyses of deep tissue loads post transtibial amputation in residual limbs of multiple prosthetic users,

    S. Portnoy, I. Siev-Neret al., “Patient-specific analyses of deep tissue loads post transtibial amputation in residual limbs of multiple prosthetic users,”Journal of Biomechanics, vol. 42, no. 16, pp. 2686– 2693, 2009

  5. [5]

    Reamputation after Minor Foot Amputation in Diabetic Patients: Risk Factors Leading to Limb Loss,

    V . S. Nerone, K. D. Springeret al., “Reamputation after Minor Foot Amputation in Diabetic Patients: Risk Factors Leading to Limb Loss,” The Journal of Foot and Ankle Surgery, vol. 52, no. 2, pp. 184–187, 2013

  6. [6]

    Lower extremity amputations and long-term outcomes in diabetic foot ulcers: A systematic review,

    A. Rathnayake, A. Sabooet al., “Lower extremity amputations and long-term outcomes in diabetic foot ulcers: A systematic review,” World Journal of Diabetes, vol. 11, no. 9, pp. 391–399, 2020

  7. [7]

    Stump-socket pressure in lower extrem- ity prostheses,

    F. Appoldt, L. Bennettet al., “Stump-socket pressure in lower extrem- ity prostheses,”Journal of Biomechanics, vol. 1, no. 4, pp. 247–257, 1968

  8. [8]

    Dynamic pressure measurements at the interface between residual limb and socket–the relationship between pressure distribution, comfort, and brim shape,

    M. Naeff and T. van Pijkeren, “Dynamic pressure measurements at the interface between residual limb and socket–the relationship between pressure distribution, comfort, and brim shape,”Bull Prosthet Res, no. 10-33, pp. 35–50, 1980

  9. [9]

    Interface pressures during ambulation using suction and vacuum-assisted prosthetic sockets

    T. L. Beil, G. M. Streetet al., “Interface pressures during ambulation using suction and vacuum-assisted prosthetic sockets.”Journal of Rehabilitation Research & Development, vol. 39, no. 6, 2002

  10. [10]

    Automated and Data-driven Com- putational Design of Patient-Specific Biomechanical Interfaces,

    K. M. Moerman, D. Solavet al., “Automated and Data-driven Com- putational Design of Patient-Specific Biomechanical Interfaces,” 2016

  11. [11]

    Transfemoral Prosthetic Socket Designs: A Review of the Literature,

    M. Brodie, L. Murrayet al., “Transfemoral Prosthetic Socket Designs: A Review of the Literature,”JPO Journal of Prosthetics and Orthotics, vol. 34, no. 2, pp. e73–e92, 2022

  12. [12]

    Prosthetic socket fit comfort score,

    R. Hanspal, K. Fisheret al., “Prosthetic socket fit comfort score,” Disability and Rehabilitation, vol. 25, no. 22, pp. 1278–1280, 2003, publisher: Informa UK Limited

  13. [13]

    Performance of a Sensor to Monitor Socket Fit: Comparison With Practitioner Clinical Assessment,

    B. G. Larsen, K. J. Allynet al., “Performance of a Sensor to Monitor Socket Fit: Comparison With Practitioner Clinical Assessment,”JPO Journal of Prosthetics and Orthotics, vol. 33, no. 1, pp. 3–10, 2021

  14. [14]

    Automatic Control of Prosthetic Socket Size for People WithTranstibial Amputation: Implementation and Evaluation,

    E. J. Weathersby, J. L. Garbiniet al., “Automatic Control of Prosthetic Socket Size for People WithTranstibial Amputation: Implementation and Evaluation,”IEEE Transactions on Biomedical Engineering, vol. 68, no. 1, pp. 36–46, 2021

  15. [15]

    State-of-the-art research in lower-limb prosthetic biomechanics- socket interface: A review,

    A. F. T. Mak, M. Zhanget al., “State-of-the-art research in lower-limb prosthetic biomechanics- socket interface: A review,”J Rehabil Res Dev, vol. 38, no. 2, pp. 161–174, 2001

  16. [16]

    The impact of limited prosthetic socket documentation: A researcher perspective,

    J. Olsen, S. Turneret al., “The impact of limited prosthetic socket documentation: A researcher perspective,”Frontiers in Rehabilitation Sciences, vol. 3, p. 853414, 2022

  17. [17]

    A Scoping Review of Pressure Mea- surements in Prosthetic Sockets of Transfemoral Amputees during Ambulation: Key Considerations for Sensor Design,

    S.-T. Ko, F. Asplundet al., “A Scoping Review of Pressure Mea- surements in Prosthetic Sockets of Transfemoral Amputees during Ambulation: Key Considerations for Sensor Design,”Sensors, vol. 21, no. 15, p. 5016, 2021

  18. [18]

    Piezoelectric Bimorphs’ Charac- teristics as In-Socket Sensors for Transfemoral Amputees,

    A. El-Sayed, N. Hamzaidet al., “Piezoelectric Bimorphs’ Charac- teristics as In-Socket Sensors for Transfemoral Amputees,”Sensors, vol. 14, no. 12, pp. 23 724–23 741, 2014

  19. [19]

    Conductive Fiber-Based Ultrasensitive Tex- tile Pressure Sensor for Wearable Electronics,

    J. Lee, H. Kwonet al., “Conductive Fiber-Based Ultrasensitive Tex- tile Pressure Sensor for Wearable Electronics,”Advanced Materials, vol. 27, no. 15, pp. 2433–2439, 2015

  20. [20]

    Textile-Based Pressure Sensors for Mon- itoring Prosthetic-Socket Interfaces,

    J. Tabor, T. Agcayaziet al., “Textile-Based Pressure Sensors for Mon- itoring Prosthetic-Socket Interfaces,”IEEE Sensors Journal, vol. 21, no. 7, pp. 9413–9422, 2021

  21. [21]

    Scientific validation of two com- mercial pressure sensor systems for prosthetic socket fit,

    A. A. Polliack, R. C. Siehet al., “Scientific validation of two com- mercial pressure sensor systems for prosthetic socket fit,”Prosthetics & Orthotics International, vol. 24, no. 1, pp. 63–73, 2000

  22. [22]

    Calibration problems encountered while monitoring stump/socket interface pressures with force sensing resistors: Techniques adopted to minimise inaccuracies,

    A. W. P. Buis and P. Convery, “Calibration problems encountered while monitoring stump/socket interface pressures with force sensing resistors: Techniques adopted to minimise inaccuracies,”Prosthetics and Orthotics International, vol. 21, no. 3, pp. 179–182, 1997

  23. [23]

    Frictional action at lower limb/prosthetic socket interface,

    M. Zhang, A. Turner-Smithet al., “Frictional action at lower limb/prosthetic socket interface,”Medical Engineering & Physics, vol. 18, no. 3, pp. 207–214, 1996, publisher: Elsevier BV

  24. [24]

    A pressure and shear sensor system for stress measurement at lower limb residuum/socket interface,

    P. Laszczak, M. McGrathet al., “A pressure and shear sensor system for stress measurement at lower limb residuum/socket interface,” Medical Engineering & Physics, vol. 38, no. 7, pp. 695–700, 2016

  25. [25]

    Wireless sensors for continuous, multi- modal measurements at the skin interface with lower limb prostheses,

    J. W. Kwak, M. Hanet al., “Wireless sensors for continuous, multi- modal measurements at the skin interface with lower limb prostheses,” Science Translational Medicine, vol. 12, no. 574, p. eabc4327, 2020

  26. [26]

    Machine-knitted washable sensor array textile for precise epidermal physiological signal monitoring,

    W. Fan, Q. Heet al., “Machine-knitted washable sensor array textile for precise epidermal physiological signal monitoring,”SCIENCE ADVANCES, 2020

  27. [27]

    Highly Sensitive Multifilament Fiber Strain Sensors with Ultrabroad Sensing Range for Textile Electronics,

    J. Lee, S. Shinet al., “Highly Sensitive Multifilament Fiber Strain Sensors with Ultrabroad Sensing Range for Textile Electronics,”ACS Nano, vol. 12, no. 5, pp. 4259–4268, 2018

  28. [28]

    A Modular Design for Distributed Measurement of Human–Robot Interaction Forces in Wearable De- vices,

    K. Ghonasgi, S. N. Yousafet al., “A Modular Design for Distributed Measurement of Human–Robot Interaction Forces in Wearable De- vices,”Sensors, vol. 21, no. 4, p. 1445, 2021

  29. [29]

    Development and validation of a 3D- printed interfacial stress sensor for prosthetic applications,

    P. Laszczak, L. Jianget al., “Development and validation of a 3D- printed interfacial stress sensor for prosthetic applications,”Medical Engineering & Physics, vol. 37, no. 1, pp. 132–137, 2015

  30. [30]

    Interface Pressure System to Compare the Functional Performance of Prosthetic Sockets during the Gait in People with Trans-Tibial Amputation,

    S. Ibarra Aguila, G. J. S ´anchezet al., “Interface Pressure System to Compare the Functional Performance of Prosthetic Sockets during the Gait in People with Trans-Tibial Amputation,”Sensors, vol. 20, no. 24, p. 7043, 2020

  31. [31]

    Static and dynamic pressure profiles of a patellar-tendon-bearing (ptb) socket,

    J. C. H. Goh, P. V . S. Leeet al., “Static and dynamic pressure profiles of a patellar-tendon-bearing (ptb) socket,”Proc Inst Mech Eng H, vol. 217, no. 2, pp. 121–126, 2003

  32. [32]

    Pressure distribution at the stump/socket interface in transtibial amputees during walking on stairs, slope and non-flat road,

    P. Dou, X. Jiaet al., “Pressure distribution at the stump/socket interface in transtibial amputees during walking on stairs, slope and non-flat road,”Clinical Biomechanics, vol. 21, no. 10, pp. 1067–1073, 2006

  33. [33]

    Pressure characteristics at the stump/socket interface in transtibial amputees using an adaptive pros- thetic foot,

    S. I. Wolf, M. Alimusajet al., “Pressure characteristics at the stump/socket interface in transtibial amputees using an adaptive pros- thetic foot,”Clinical Biomechanics, vol. 24, no. 10, pp. 860–865, 2009

  34. [34]

    A Review of Prosthetic Interface Stress Investigations,

    M. B. Silver-Thorn, J. W. Steegeet al., “A Review of Prosthetic Interface Stress Investigations,”J Rehabil Res Dev, vol. 33, no. 3, pp. 253–266, 1996

  35. [35]

    Subject-Exoskeleton Contact Model Calibration Leads to Accurate Interaction Force Predictions,

    G. Serrancoli, A. Falisseet al., “Subject-Exoskeleton Contact Model Calibration Leads to Accurate Interaction Force Predictions,”IEEE Transactions on Neural Systems and Rehabilitation Engineering, vol. 27, no. 8, pp. 1597–1605, 2019

  36. [36]

    A combined kinematic and kinetic analysis at the residuum/socket interface of a knee-disarticulation amputee,

    J. Tang, M. McGrathet al., “A combined kinematic and kinetic analysis at the residuum/socket interface of a knee-disarticulation amputee,”Medical Engineering & Physics, vol. 49, pp. 131–139, 2017

  37. [37]

    Embroidered textile sensors for real- time multiaxial force mapping in prosthetics,

    T. Yu, A. Gonz ´alez C.et al., “Embroidered textile sensors for real- time multiaxial force mapping in prosthetics,” 2026, manuscript under review atScience Advances

  38. [38]

    S. P. Boyd and L. Vandenberghe,Convex Optimization. Cambridge New York Melbourne New Delhi Singapore: Cambridge University Press, 2023, version 29

  39. [39]

    Marker-based method to measure movement between the residual limb and a transtibial prosthetic socket,

    W. L. Childers and S. Siebert, “Marker-based method to measure movement between the residual limb and a transtibial prosthetic socket,”Prosthetics & Orthotics International, vol. 40, no. 6, pp. 720– 728, 2016

  40. [40]

    A pressure and shear sensing liner for prosthetic sockets,

    J. Wheeler, A. Mazumdaret al., “A pressure and shear sensing liner for prosthetic sockets,” in2016 38th Annual International Conference of the IEEE Engineering in Medicine and Biology Society (EMBC). Orlando, FL, USA: IEEE, 2016, pp. 2026–2029

  41. [41]

    Residual limb volume change: Sys- tematic review of measurement and management,

    J. E. Sanders and S. Fatone, “Residual limb volume change: Sys- tematic review of measurement and management,”The Journal of Rehabilitation Research and Development, vol. 48, no. 8, p. 949, 2011