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REVIEW 3 major objections 6 minor 58 references

Active Lubrication of Transluminal Medical Instruments

T0 review · 3 major / 6 minor · reviewed 2026-08-07 · deepseek-v4-flash

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Pith's one-line read Vibrating catheter sheath cuts friction on demand, up to 42% on tissue

desk verdict Solid engineering validation of a known principle, with new ex-vivo data; the clinical extrapolation is ahead of the evidence because the prototype hasn't been tested in the intended submerged environment. read the letter →

arxiv 2506.07225 v2 pith:6D3CI5HH submitted 2025-06-08 physics.med-ph cs.RO

Mostafa A. Atalla , Jelte Nieuwenhuis , Alan Martin , Xuan Wang , Ahranee Canden , Matt J. Carré , Roger Lewis , Aimée Sakes
show 1 more author
Michaël Wiertlewski
This is my paper · ORCID
classification physics.med-phcs.RO
keywords activelubricationultrasonicsqueeze-filmlevitationtransluminalcatheterfrictionmodulationbiotribologyporcineaortabucklingthermalsafety
verification ladder T0 review T1 audit T2 compute T3 formal

The pith

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

The reading

This paper tries to establish that ultrasonic squeeze-film levitation can serve as active lubrication for transluminal instruments, letting a single catheter switch between low-friction navigation and high-friction anchoring by turning vibrations on or off. It reports a prototype sheath whose discrete ring modules vibrate at about 22.7 kHz, generating a pressurized fluid film at the instrument–tissue interface. In ex-vivo porcine aorta, active lubrication reduced friction by up to 42%, and on rigid substrates by up to 82%; the same mechanism prevented friction-induced buckling during insertion. If true, it would give clinicians real-time friction control that passive hydrophilic coatings and liquid lubricants cannot provide, potentially reducing tissue damage, perforation risk, and buckling while preserving stable anchoring for surgical tasks.

What carries the argument

The load-bearing mechanism is squeeze-film levitation produced by a resonating ring module. Four piezoelectric plates drive a ring in its second flexural resonance at 22.7 kHz (simulation) and 22.9 kHz (measured), with surface amplitudes of about 3.7 microns per 100 V in air and an active area covering roughly 84–85% of the ring. The transverse vibration nonlinearly compresses trapped fluid into a pressurized film that separates the module from the counter-surface; friction decreases monotonically with amplitude up to a saturation point. The paper also leans on the model $\mu_\mathrm{on} = \beta\, \mu_\mathrm{off}\, \exp(\alpha/N)$, which predicts that the on-state friction is proportional to the off-state friction, so the controllable friction range widens when both the starting friction and the vibration amplitude are maximized.

What would settle it

A closed-loop, perfused vessel phantom at 37 degrees Celsius with flowing blood-mimicking fluid, curved anatomy, and continuous sliding, measuring friction reduction and interface temperature: if the vibration-on friction reduction falls to the level of passive PBS lubrication alone, or the steady-state temperature rise exceeds the reported figure by more than the stated variance, the central claim that active lubrication provides clinically useful on-demand friction control would be refuted.

Watch

Extended reading notes

Core claim

The paper's central claim is that friction between a transluminal instrument and the luminal wall can be actively modulated in real time by vibrating the instrument surface at ultrasonic frequencies, without changing the surface chemistry or adding external lubricant. The authors demonstrate this with an active lubrication sheath containing discrete modules that vibrate in their second flexural mode; the vibrations create a squeeze film that levitates the module away from the tissue, decoupling the surface asperities. In a cardiac catheterization use case, the measured friction reduction reached up to 42% on ex-vivo porcine aorta hydrated with PBS and up to 82% on rigid substrates, with an average temperature rise of 6.2 degrees Celsius at the module–tissue interface. They also show that activating the module eliminated the buckling observed in a deliberately misaligned catheter insertion. The paper concludes that the same device can therefore provide low-friction navigation and, when vibrations are switched off, friction-based anchoring.

Load-bearing premise

The load-bearing premise is that an open, flattened, PBS-hydrated ex-vivo porcine aorta tested at room temperature without blood flow or sliding reproduces the friction and heat behavior of a real vessel during catheterization; if blood-flow convection, body temperature, vessel curvature, or multi-point shaft contact changes the squeeze film, the measured 42% reduction and 6.2 degrees Celsius rise may not transfer to patients.

Editorial extensions

If this is right

  • Catheters and endoscopes could switch from low-friction navigation to high-friction anchoring by simply toggling the vibration, addressing the current passive-coating trade-off.
  • Reducing friction-induced buckling lowers the risk of sudden elastic-energy release that can dissect or perforate the luminal wall.
  • The average interface temperature rise of 6.2 degrees Celsius, extrapolated to about 44 degrees Celsius at body temperature, suggests the approach sits within published thermal-safety thresholds, pending in-vivo confirmation.
  • Rigid, calcified regions may benefit most, since the 82% friction reduction on rigid substrates is roughly twice the value measured on soft ex-vivo tissue.
  • Because friction reduction is robust across load and curvature and improves on curved interfaces, modules can be distributed along the shaft to handle the variable contact geometry of real anatomy.

Reading between the lines

Editorial extensions of the paper, not claims the author makes directly.

  • Beyond the paper's ex-vivo demonstration, the same friction-modulation law implies that the on/off friction ratio is set by vibration amplitude and normal load, so a control loop that adjusts voltage in real time could trade stability against tissue force during a procedure, a capability the paper motivates but does not implement.
  • The finding that liquid-lubricated interfaces need roughly seven times less vibration amplitude than dry ones suggests that in blood-filled vessels the squeeze film is dominated by incompressible fluid, so minimizing module damping may matter more than maximizing raw amplitude.
  • A testable extension is to mount an accelerometer or impedance sensor on the drive circuit to estimate the load carried by the squeeze film, letting clinicians detect when a module loses levitation before friction rises.
  • The thermal measurement was taken with no sliding in a dry room-temperature environment; a sliding, perfused measurement would likely show a lower equilibrium temperature but also a different heat distribution along the shaft, so thermal safety should be re-checked at full insertion forces.
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Editorial analysis

A structured set of objections, weighed in public.

Desk editor's note, referee report, and a circularity audit.

Referee Report

3 major / 6 minor

Summary. The manuscript presents an active lubrication sheath for transluminal instruments, in which discrete ring-shaped modules vibrate ultrasonically to create a squeeze film that reduces friction when activated. The authors characterize the vibration amplitude and mode shape of a 10 mm prototype, measure friction reduction on rigid substrates in dry and liquid-lubricated contact under varying load and curvature, validate the system on ex-vivo porcine aorta tissue, measure the temperature rise at the module-tissue interface with a thermal camera, and demonstrate prevention of catheter buckling in a benchtop insertion experiment. The central quantitative claims are a friction reduction of up to 42% on ex-vivo tissue and up to 82% on rigid substrates, an average temperature rise of 6.2 degrees Celsius, and effective prevention of buckling during catheter insertion.

Significance. If the bench measurements transfer to the intended clinical environment, this work would provide a new capability: on-demand, reversible friction modulation for transluminal instruments, overcoming the main limitation of passive hydrophilic coatings and add-on lubricants. The manuscript has several strengths: friction and vibration data are repeated with reported standard deviations; the finite-element predictions of resonance frequency and mode shape agree with laser vibrometry; the 1 N normal load matches a clinically relevant catheter load; and the authors explicitly disclose the main limitations of their test configurations and list waterproofing and in-vivo studies as future work. The paper is therefore best read as a proof-of-concept and bench characterization study rather than as a demonstration of clinical efficacy.

major comments (3)
  1. [Methods, ex-vivo tissue validation experiment; Fig. 5] The 42% friction reduction on porcine aorta is measured on a flattened, cut-open tissue sample in open air, with contact restricted to a single module and with free-surface PBS as the liquid. This configuration is not the boundary-value problem of a catheter inside a blood-filled, perfused, curved vessel: squeeze-film levitation in liquids depends on confinement and replenishment of the fluid film, so the measured reduction may not transfer. The Discussion acknowledges the need for a waterproof design, but the Abstract's phrase 'cardiac catheterization use case' overstates the evidence. A submerged, liquid-filled lumen test with a blood-mimicking fluid, or at least a confined-channel variant, is needed to make the central claim load-bearing.
  2. [Thermal imaging experiment; Fig. 6] The 6.2 degrees Celsius rise and the statement that the temperature is 'within safe limits' are obtained from a dry, stationary, room-temperature test without sliding and without blood-flow convection. The Discussion correctly states that blood flow would dissipate heat and that real conditions would differ, but the Abstract states that 'thermal imaging confirmed that temperature at the tissue-catheter interface remained within safe limits.' This is too strong for a stationary dry test: the measured value is not a bound on the in-vivo interface temperature. Either a sliding and/or submerged thermal measurement, a heat-transfer model including perfusion, or a softened claim in the Abstract is required.
  3. [Catheter buckling experiment; Fig. 7] The claim that 'the system effectively prevented buckling' rests on a single qualitative demonstration with one friction-control module at the tip in a 3D-printed lumen. No insertion force versus insertion distance data, no repeated trials, and no comparison with a multi-module sheath configuration are reported. As presented, the experiment supports feasibility but does not quantitatively support the system-level buckling-prevention claim. The authors should report at least force-displacement traces with and without activation, repeated trials, and ideally a measure of the buckling load or the stored elastic energy released.
minor comments (6)
  1. [Fig. 3 caption] The caption says 'Each experiment was repeated repeated six times'; the word 'repeated' is duplicated.
  2. [Ex-vivo tissue validation experiment, Results] The sentence 'The testing samples dried out over time which caused the a slight increase coefficient of friction' contains a typo ('the a') and should read 'caused a slight increase in the coefficient of friction.'
  3. [Discussion] The word 'experiements' is misspelled; it should be 'experiments.'
  4. [Results, Ex-vivo tissue validation] The effective vibration area is reported as approximately 84% in the Results and approximately 85% in the Discussion; the numbers should be reconciled.
  5. [Methods, Friction characterization experiment] The sentence 'loading the resonating ring onto the friction substrate to (1 N)' is incomplete; it should state the target load explicitly, such as 'to a normal load of 1 N.'
  6. [Results, Ex-vivo tissue validation; Eq. (2)] Equation (2) is invoked to explain the linear mu_on-mu_off correlation, but no fitted parameters or goodness-of-fit statistics are reported for the data in Fig. 5(c); reporting the slope, intercept, and R^2 would make the interpretation more rigorous.

Circularity Check

0 steps flagged · score 1.0 of 10

No significant circularity: the headline friction-reduction, temperature-rise, and buckling results are direct measurements, not fitted predictions.

full rationale

The central quantitative claims are direct experimental measurements: the 42% friction reduction on ex-vivo porcine aorta and 82% on rigid substrates come from tribometer force readings (Figs. 3–5), the 6.2 °C temperature rise comes from thermal-camera data (Fig. 6), and the buckling-prevention result is a direct comparison of insertion with and without vibration (Fig. 7). None of these is obtained by fitting a parameter to one subset of data and then predicting a closely related quantity. The only interpretive equation, µ_on = β·µ_off·exp(α/N), is quoted from Wiertlewski et al. (Ref. 36), a paper co-authored by one of the present senior authors; however, it is used after the fact to rationalize the measured linear correlation between µ_off and µ_on, not to generate the reported friction reductions, and its parameters are not fitted to the tissue data in this paper. The other self-citations (Refs. 41 and 42) provide background theory and an earlier prototype demonstration, but the current prototype's friction, thermal, and insertion performance is independently measured here. The finite-element 'prediction' of resonance frequency and mode shape is a model-experiment comparison validated by vibrometry, not a re-labeling of measured data as a forecast. The acknowledged limitations—open-channel rather than fully submerged tests, dry stationary thermal measurements, and deferral of in-vivo studies—are external-validity concerns, not circular derivations; no load-bearing step reduces to its own inputs by construction.

Assumptions & free parameters 1 free parameters · 6 assumptions · 0 invented entities

The central claims rest on established ultrasonic lubrication theory and on the representativeness of the ex-vivo tissue model. The incompressible squeeze-film model [41] and the partial levitation model [36] are the main physical axioms. The most fragile premise is the ex-vivo tissue setup, which lacks blood flow, body temperature, and full lumen geometry. The thermal safety extrapolation adds an additional untested assumption. The only hand-chosen numeric parameter is the 2-micrometer effective-area threshold.

free parameters (1)
  • Effective-area amplitude threshold = 2 µm
    The paper defines the effective lubrication surface as regions with vibration amplitude equal to or exceeding 2 micrometers, chosen by hand as the threshold for effective ultrasonic lubrication, aligning with technological specifications. This threshold affects the reported 84% active surface area but is not a fitted parameter to the friction data.
assumptions (6)
  • domain assumption Incompressible squeeze-film levitation theory (Atalla et al., Appl. Phys. Lett. 2023 [41]) holds for the liquid films at the tissue interface.
    Invoked in the friction modulation and curvature results to explain higher friction reduction capacity in liquid and its dependence on film geometry and load.
  • domain assumption Wiertlewski et al. model (Eq. 2) mu_on = beta * mu_off * exp(alpha/N) correctly describes partial squeeze-film levitation.
    Used in ex-vivo tissue validation to interpret the observed linear correlation between mu_on and mu_off; the model is from prior work and is not re-derived or fitted in this paper.
  • domain assumption Ultrasonic lubrication requires frequencies above 20 kHz and amplitudes above 2 micrometers.
    Stated as key requirements for ultrasonic lubrication, citing refs [43, 44], and used to set the design targets for the resonating ring.
  • standard math Friction force is independent of the apparent area of contact (Amontons-Coulomb law).
    Used in the curvature experiment to argue that increasing curvature (contact area) increases squeeze-film force without increasing friction force.
  • domain assumption Ex-vivo porcine aorta tissue, frozen, thawed, cut open, and hydrated with PBS, is representative of in vivo vascular tissue for friction measurements.
    Basis of the ex-vivo tissue validation; the authors acknowledge flattening and lack of blood flow as deviations from clinical reality.
  • domain assumption A temperature rise of 6.2 degrees Celsius at room temperature extrapolates to approximately 44 degrees Celsius in the human body, and this is within thermal safety thresholds.
    Used in the thermal imaging discussion to claim potential thermal safety; the extrapolation assumes a 37 degrees Celsius body baseline and no additional heating or cooling effects, which the authors partially acknowledge.

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Cite this review

Pith. "Pith review of Active Lubrication of Transluminal Medical Instruments." pith.science (2026). https://pith.science/paper/6D3CI5HH

@misc{pith2026250607225,
  author       = {Pith},
  title        = {Pith review of: Active Lubrication of Transluminal Medical Instruments},
  year         = {2026},
  howpublished = {\url{https://pith.science/paper/6D3CI5HH}},
  note         = {Machine review of arXiv:2506.07225}
}
read the original abstract

Transluminal minimally invasive surgery uses natural orifices and small incisions to access internal anatomical structures, promoting quicker recovery and reduced morbidity. However, navigating instruments such as catheters and endoscopes through anatomical pathways creates frictional interactions with luminal walls, risking complications such as perforation, poor haptic feedback, and instrument buckling. This paper presents an active lubrication sheath that controls friction on demand through discrete friction control modules distributed along its shaft. These modules employ ultrasonic vibrations at the instrument surface to generate a pressurized fluid layer at the contact interface, lubricating the interface and thereby reducing friction. We implemented these modules in a prototype catheter, which we validated under dry and liquid-lubricated conditions, across rigid and soft interfaces, and along varied anatomical curvatures. In a cardiac catheterization use case, active lubrication reduced friction by up to 42% on ex vivo porcine aorta tissue hydrated with phosphate-buffered saline, and thermal imaging measured an average temperature rise of 6.2 degrees Celsius at the module-tissue interface due to vibration, confirming its potential thermal safety. In a catheter insertion demonstration, active lubrication reduced friction-induced buckling and enabled smoother advancement through the lumen, further showcasing its potential impact. By minimizing injury risk and enhancing procedural stability, active lubrication can drastically enhance the safety and efficacy of transluminal interventions.

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Reference graph

Works this paper leans on

58 extracted references · 58 canonical work pages

  1. [1]

    Surgery insight: natural orifice transluminal endo- scopic surgery—an analysis of work to date,

    M. S. Wagh and C. C. Thompson, “Surgery insight: natural orifice transluminal endo- scopic surgery—an analysis of work to date,” Nature Clinical Practice Gastroenterology & Hepatology, vol. 4, no. 7, pp. 386–392, 2007

    work page 2007

  2. [2]

    A Review on Flexi- ble Robotic Systems for Minimally Invasive Surgery,

    O. M. Omisore, S. Han, J. Xiong, H. Li, Z. Li, and L. Wang, “A Review on Flexi- ble Robotic Systems for Minimally Invasive Surgery,”IEEE Transactions on Systems, Man, and Cybernetics: Systems, vol. 52, no. 1, pp. 631–644, 2022

    work page 2022

  3. [3]

    Soft robotics in minimally invasive surgery,

    M. Runciman, A. Darzi, and G. P. Mylonas, “Soft robotics in minimally invasive surgery,” Soft Robotics, vol. 6, no. 4, pp. 423–443, 2019. PMID: 30920355

    work page 2019

  4. [4]

    Bio- tribology of Vascular Devices: A Review of Tissue/Device Friction Research,

    R. M. Wagner, R. Maiti, M. J. Carr´ e, C. M. Perrault, P. C. Evans, and R. Lewis, “Bio- tribology of Vascular Devices: A Review of Tissue/Device Friction Research,”Biotribol- ogy, vol. 25, no. October 2020, 2021

    work page 2020

  5. [5]

    A review of the bio-tribology of medical devices,

    X. Zhang, Y. Zhang, and Z. Jin, “A review of the bio-tribology of medical devices,”Fric- tion, vol. 10, no. 1, pp. 4–30, 2022. 15

    work page 2022

  6. [6]

    A scoping review of important urinary catheter induced complications,

    K. H. Dellimore, A. R. Helyer, and S. E. Franklin, “A scoping review of important urinary catheter induced complications,” Journal of Materials Science: Materials in Medicine, vol. 24, no. 8, pp. 1825–1835, 2013

    work page 2013

  7. [7]

    A Review of Catheter Related Com- plications During Minimally Invasive Tran- scatheter Cardiovascular Intervention with Implications for Catheter Design,

    K. H. Dellimore, S. E. Franklin, and A. R. Helyer, “A Review of Catheter Related Com- plications During Minimally Invasive Tran- scatheter Cardiovascular Intervention with Implications for Catheter Design,”Cardio- vascular Engineering and Technology, vol. 5, no. 3, pp. 217–232, 2014

    work page 2014

  8. [8]

    Evaluation of catheter-induced tribological damage to porcine aorta using infra-red spectroscopy,

    K. H. Dellimore, A. J. Mank, J. Wojnowski, C. Noble, and S. E. Franklin, “Evaluation of catheter-induced tribological damage to porcine aorta using infra-red spectroscopy,” Biotribology, vol. 7, pp. 11–21, 2016

    work page 2016

Show all 58 references
  1. [9]

    Measurement of Friction-induced Changes in Pig Aorta Fibre Organization by Non-invasive Imaging as a Model for Detecting the Tissue Response to Endovascular Catheters,

    L. E. Bostan, C. Noble, N. Smulders, R. Lewis, M. J. Carr´ e, S. Franklin, N. H. Green, and S. MacNeil, “Measurement of Friction-induced Changes in Pig Aorta Fibre Organization by Non-invasive Imaging as a Model for Detecting the Tissue Response to Endovascular Catheters,”Biot...

    2017

  2. [10]

    Role of endothelial glycocalyx in sliding friction at the catheter-blood vessel interface,

    C. Lin, H. J. Kaper, W. Li, R. Splinter, and P. K. Sharma, “Role of endothelial glycocalyx in sliding friction at the catheter-blood vessel interface,”Scientific Reports, vol. 10, no. 1, p. 11855, 2020

    2020

  3. [11]

    Friction injury of the central vein caused by catheter for hemodialysis: an in vitro study,

    Z. Wang, K. Wang, and Y. Xu, “Friction injury of the central vein caused by catheter for hemodialysis: an in vitro study,”Scientific Reports, vol. 14, no. 1, p. 5836, 2024

    2024

  4. [12]

    Inves- tigation on friction trauma of small intestine in vivo under reciprocal sliding conditions,

    W. Li, L. Shi, H. Deng, and Z. Zhou, “Inves- tigation on friction trauma of small intestine in vivo under reciprocal sliding conditions,” Tribology Letters, vol. 55, no. 2, pp. 261–270, 2014

    2014

  5. [13]

    Complications of diagnostic upper Gastrointestinal endoscopy: common and rare – recognition, assessment and management,

    W. Waddingham, U. Kamran, B. Kumar, N. J. Trudgill, Z. P. Tsiamoulos, and M. Banks, “Complications of diagnostic upper Gastrointestinal endoscopy: common and rare – recognition, assessment and management,”BMJ Open Gastroenterology, vol. 9, no. 1, p. e000688, 2022

    2022

  6. [14]

    Adverse events related to colonoscopy: Global trends and future challenges,

    S. Y. Kim, H. S. Kim, and H. J. Park, “Adverse events related to colonoscopy: Global trends and future challenges,”World Journal of Gastroenterology, vol. 25, no. 2, pp. 190–204, 2019

    2019

  7. [15]

    Friction behavior between endoscopy and esophageal internal surface,

    C. X. Lin, Q. Y. Yu, J. Wang, W. Ji, W. Li, and Z. R. Zhou, “Friction behavior between endoscopy and esophageal internal surface,” Wear, vol. 376-377, pp. 272–280, 2017

    2017

  8. [16]

    Friction behavior of esophageal mucosa under axial and circumferential extension,

    C. Lin, W. Li, H. Deng, K. Li, and Z. Zhou, “Friction behavior of esophageal mucosa under axial and circumferential extension,” Tribology Letters, vol. 67, pp. 1–14, 2019

    2019

  9. [17]

    The lubricating function of mucin at the gastroscope device-esophagus interface,

    C. Lin, W. Liu, J. Xie, W. Li, and Z. Zhou, “The lubricating function of mucin at the gastroscope device-esophagus interface,”Tri- bology Letters, vol. 68, pp. 1–10, 2020

    2020

  10. [18]

    Effects of vision and friction on haptic perception,

    J. O. Perreault and C. G. Cao, “Effects of vision and friction on haptic perception,” Human Factors, vol. 48, no. 3, pp. 574–586, 2006

    2006

  11. [19]

    Haptics for robot-assisted minimally invasive surgery,

    A. M. Okamura, L. N. Verner, C. E. Reiley, and M. Mahvash, “Haptics for robot-assisted minimally invasive surgery,”Springer Tracts in Advanced Robotics, vol. 66, no. STAR, pp. 361–372, 2010

    2010

  12. [20]

    Haptics in minimally invasive surgery - A review,

    E. P. van der Putten, R. H. Goossens, J. J. Jakimowicz, and J. Dankelman, “Haptics in minimally invasive surgery - A review,”Min- imally Invasive Therapy and Allied Technolo- gies, vol. 17, no. 1, pp. 3–16, 2008

    2008

  13. [21]

    Soft robotic steerable microcatheter for the endovascular treat- ment of cerebral disorders,

    T. Gopesh, J. H. Wen, D. Santiago-Dieppa, B. Yan, J. S. Pannell, A. Khalessi, A. Nor- bash, and J. Friend, “Soft robotic steerable microcatheter for the endovascular treat- ment of cerebral disorders,”Science Robotics, vol. 6, no. 57, p. eabf0601, 2021

    2021

  14. [22]

    Mag- netic steering continuum robot for translu- minal procedures with programmable shape and functionalities,

    L. Mao, P. Yang, C. Tian, X. Shen, F. Wang, H. Zhang, X. Meng, and H. Xie, “Mag- netic steering continuum robot for translu- minal procedures with programmable shape and functionalities,”Nature Communica- tions, vol. 15, no. 1, p. 3759, 2024

    2024

  15. [23]

    Buckling prevention strategies in nature as inspiration for improving percutaneous instruments: A review,

    A. Sakes, D. Dodou, and P. Breedveld, “Buckling prevention strategies in nature as inspiration for improving percutaneous instruments: A review,”Bioinspiration and Biomimetics, vol. 11, no. 2, 2016

    2016

  16. [24]

    Design and analysis of feeder mech- anism for buckling prevention in robotic catheterization,

    H. Baek, B. Cheon, J. M. You, and D. S. Kwon, “Design and analysis of feeder mech- anism for buckling prevention in robotic catheterization,”Journal of Computational Design and Engineering, vol. 9, no. 4, pp. 1467–1481, 2022

    2022

  17. [25]

    A novel suction- based lung-stabilizing device in single-port video-assisted thoracoscopic surgical proce- dures,

    Y. Muranishi, T. Sato, Y. Ueda, Y. Yutaka, 16 T. Nakamura, and H. Date, “A novel suction- based lung-stabilizing device in single-port video-assisted thoracoscopic surgical proce- dures,”General Thoracic and Cardiovascular Surgery, vol. 68, no. 5, pp. 503–507, 2020

    2020

  18. [26]

    Scopes too flexible and too stiff,

    A. Loeve, P. Breedveld, and J. Dankelman, “Scopes too flexible and too stiff,”IEEE Pulse, vol. 1, no. 3, pp. 26–41, 2010

    2010

  19. [27]

    Deployable stabilization mechanisms for endoscopic procedures,

    T. Ranzani, S. Russo, F. Schwab, C. J. Walsh, and R. J. Wood, “Deployable stabilization mechanisms for endoscopic procedures,”Pro- ceedings - IEEE International Conference on Robotics and Automation, pp. 1125–1131, 2017

    2017

  20. [28]

    Warm water or oil-assisted colonoscopy: Toward simpler examinations?,

    E. Brocchi, R. Pezzilli, P. Tomassetti, D. Campana, A. M. Morselli-Labate, and R. Corinaldesi, “Warm water or oil-assisted colonoscopy: Toward simpler examinations?,” American Journal of Gastroenterology, vol. 103, no. 3, pp. 581–587, 2008

    2008

  21. [29]

    Catheter lubrication and fixa- tion: interventions,

    M. Wilson, “Catheter lubrication and fixa- tion: interventions,”British Journal of Nurs- ing, vol. 22, no. 10, pp. 566–569, 2013

    2013

  22. [30]

    Comparison of silicone spray versus water soluble lubricating jelly for the aid in bronchoscopic examina- tion,

    A. Hernandez, R. Cogdill, C. Hinojosa- Laborde, and M. I. Restrepo, “Comparison of silicone spray versus water soluble lubricating jelly for the aid in bronchoscopic examina- tion,”journal of Anesthesiology and Clinical Science, vol. 2, no. 1, p. 7, 2013

    2013

  23. [31]

    Influence of different lubricating fluids on friction trauma of small intestine dur- ing enteroscopy,

    J. Wang, L. Ma, W. Li, and Z. Zhou, “Influence of different lubricating fluids on friction trauma of small intestine dur- ing enteroscopy,”Tribology International, vol. 126, no. February, pp. 29–38, 2018

    2018

  24. [32]

    Identification of lubricant viscosity to minimize the frictional impact of colonoscopy on colonic mucosa,

    N. Watanabe, R. Hirose, H. Ikegaya, K. Yamauchi, H. Miyazaki, T. Yoshida, R. Bandou, K. Inoue, O. Dohi, N. Yoshida, et al., “Identification of lubricant viscosity to minimize the frictional impact of colonoscopy on colonic mucosa,”Communications Engi- neering, vol. 3, no. 1, p...

    2024

  25. [33]

    Hydrophilic coatings for biomedical applications in and ex vivo,

    P. Wyman, “Hydrophilic coatings for biomedical applications in and ex vivo,” Coatings for Biomedical Applications, pp. 3–42, 2012

    2012

  26. [34]

    Friction behaviour of hydrophilic lubricious coatings for medical device applications,

    A. Niemczyk, M. El Fray, and S. E. Franklin, “Friction behaviour of hydrophilic lubricious coatings for medical device applications,” Tribology International, vol. 89, pp. 54–61, 2015

    2015

  27. [35]

    Compressible Squeeze Films and Squeeze Bearings,

    E. O. J. Salbu, “Compressible Squeeze Films and Squeeze Bearings,”Journal of Basic Engineering, vol. 86, pp. 355–364, 06 1964

    1964

  28. [36]

    Partial squeeze film levitation mod- ulates fingertip friction,

    M. Wiertlewski, R. F. Friesen, and J. E. Colgate, “Partial squeeze film levitation mod- ulates fingertip friction,”Proceedings of the National Academy of Sciences of the United States of America, vol. 113, no. 33, pp. 9210– 9215, 2016

    2016

  29. [37]

    T-PaD: Tactile pattern display through variable friction reduction,

    L. Winfield, J. Glassmire, J. E. Colgate, and M. Peshkin, “T-PaD: Tactile pattern display through variable friction reduction,”Proceed- ings - Second Joint EuroHaptics Conference and Symposium on Haptic Interfaces for Vir- tual Environment and Teleoperator Systems, World Hapti...

    2007

  30. [38]

    A Contactless Stage Based on Near-Field Acoustic Levitation for Object Handling and Positioning-Concept, Design, Modeling, and Experiments,

    R. Gabai, R. Shaham, S. Davis, N. Cohen, and I. Bucher, “A Contactless Stage Based on Near-Field Acoustic Levitation for Object Handling and Positioning-Concept, Design, Modeling, and Experiments,”IEEE/ASME Transactions on Mechatronics, vol. 24, no. 5, pp. 1954–1963, 2019

    1954

  31. [39]

    An ultrasonic levitation journal bearing able to control spindle center position,

    S. Zhao, S. Mojrzisch, and J. Wallaschek, “An ultrasonic levitation journal bearing able to control spindle center position,”Mechanical Systems and Signal Processing, vol. 36, no. 1, pp. 168–181, 2013

    2013

  32. [40]

    Near-field acoustic levitation and applica- tions to bearings: A critical review,

    M. Shi, K. Feng, J. Hu, J. Zhu, and H. Cui, “Near-field acoustic levitation and applica- tions to bearings: A critical review,”Inter- national Journal of Extreme Manufacturing, vol. 1, no. 3, 2019

    2019

  33. [41]

    Incompress- ible squeeze-film levitation,

    M. A. Atalla, R. A. J. van Ostayen, A. Sakes, and M. Wiertlewski, “Incompress- ible squeeze-film levitation,”Applied Physics Letters, vol. 122, no. 24, 2023

    2023

  34. [42]

    Toward variable-friction catheters using ultrasonic lubrication,

    M. A. Atalla, J. J. Tuijp, M. Wiertlewski, and A. Sakes, “Toward variable-friction catheters using ultrasonic lubrication,”IEEE Trans- actions on Medical Robotics and Bionics, pp. 1–1, 2024

    2024

  35. [43]

    Squeeze film effect for the design of an ultrasonic tactile plate,

    M. Biet, F. Giraud, and B. Lemaire-Semail, “Squeeze film effect for the design of an ultrasonic tactile plate,”IEEE Transactions on Ultrasonics, Ferroelectrics, and Frequency Control, vol. 54, no. 12, pp. 2678–2688, 2007

    2007

  36. [44]

    A method for 17 controlling tactile sensation of surface rough- ness using ultrasonic vibration,

    T. Watanabe and S. Fukui, “A method for 17 controlling tactile sensation of surface rough- ness using ultrasonic vibration,” inProceed- ings of 1995 IEEE International Confer- ence on Robotics and Automation, vol. 1, pp. 1134–1139 vol.1, 1995

    1995

  37. [45]

    Fiberbots: Robotic fibers for high-precision minimally invasive surgery,

    M. E. M. K. Abdelaziz, J. Zhao, B. G. Rosa, H.-T. Lee, D. Simon, K. Vyas, B. Li, H. Koguna, Y. Li, A. A. Demircali, H. Uvet, G. Gencoglan, A. Akcay, M. Elriedy, J. Kin- ross, R. Dasgupta, Z. Takats, E. Yeatman, G.-Z. Yang, and B. Temelkuran, “Fiberbots: Robotic fibers for high...

    2024

  38. [46]

    Coronary artery calcification and its progression: What does it really mean?,

    H. Mori, S. Torii, M. Kutyna, A. Sakamoto, A. V. Finn, and R. Virmani, “Coronary artery calcification and its progression: What does it really mean?,”JACC: Cardiovascular Imaging, vol. 11, no. 1, pp. 127–142, 2018

    2018

  39. [47]

    Preva- lence of coronary atherosclerosis in asymp- tomatic healthy subjects: An intravascular ultrasound study of donor hearts,

    M.-S. Kim, S.-J. Kang, C.-W. Lee, S. Han, D.-W. Park, S.-W. Lee, Y.-H. Kim, S.-W. Park, S.-J. Park, and J.-J. Kim, “Preva- lence of coronary atherosclerosis in asymp- tomatic healthy subjects: An intravascular ultrasound study of donor hearts,”Journal of Atherosclerosis and Th...

    2013

  40. [48]

    High preva- lence of coronary atherosclerosis in asymp- tomatic teenagers and young adults: evidence from intravascular ultrasound,

    E. M. Tuzcu, S. R. Kapadia, E. Tutar, K. M. Ziada, R. E. Hobbs, P. M. McCarthy, J. B. Young, and S. E. Nissen, “High preva- lence of coronary atherosclerosis in asymp- tomatic teenagers and young adults: evidence from intravascular ultrasound,”Circulation, vol. 103, pp. 2705–2...

    2001

  41. [49]

    An in vitro model quantifying the effect of calcification on the tissue–stent inter- action in a stenosed aortic root,

    O. M. McGee, W. Sun, and L. M. McNa- mara, “An in vitro model quantifying the effect of calcification on the tissue–stent inter- action in a stenosed aortic root,”Journal of Biomechanics, vol. 82, pp. 109–115, 2019

    2019

  42. [50]

    Contact and friction between catheter and blood vessel,

    K. Takashima, R. Shimomura, T. Kitou, H. Terada, K. Yoshinaka, and K. Ikeuchi, “Contact and friction between catheter and blood vessel,”Tribology International, vol. 40, no. 2, pp. 319–328, 2007. First Inter- national Conference on Advanced Tribology (iCAT 2004)

    2007

  43. [51]

    Thresholds for thermal damage to normal tissues: An update,

    P. S. Yarmolenko, E. J. Moon, C. Landon, A. Manzoor, D. W. Hochman, B. L. Viglianti, and M. W. Dewhirst, “Thresholds for thermal damage to normal tissues: An update,”Inter- national Journal of Hyperthermia, vol. 27, no. 4, pp. 320–343, 2011. PMID: 21591897

    2011

  44. [52]

    Thermal manage- ment of an interventional medical device with double layer encapsulation,

    N. B. D. Do, E. Andreassen, S. Edward- sen, A. Lifjeld, K. E. Aasmundtveit, H.-V. Nguyen, and K. Imenes, “Thermal manage- ment of an interventional medical device with double layer encapsulation,”Experimen- tal Heat Transfer, vol. 35, no. 5, pp. 708–725, 2022

    2022

  45. [53]

    A robotic catheter system with real-time force feedback and monitor,

    N. Xiao, J. Guo, S. Guo, and T. Tamiya, “A robotic catheter system with real-time force feedback and monitor,”Australasian physical & engineering sciences in medicine, vol. 35, no. 3, p. 283—289, 2012

    2012

  46. [54]

    Con- tact of nominally flat surfaces,

    J. A. Greenwood and J. P. Williamson, “Con- tact of nominally flat surfaces,”Proceedings of the royal society of London. Series A. Mathematical and physical sciences, vol. 295, no. 1442, pp. 300–319, 1966

    1966

  47. [55]

    The elastic contact of a rough surface,

    A. Bush, R. Gibson, and T. Thomas, “The elastic contact of a rough surface,”Wear, vol. 35, no. 1, pp. 87–111, 1975

    1975

  48. [56]

    Relation between interfa- cial separation and load: A general theory of contact mechanics,

    B. N. J. Persson, “Relation between interfa- cial separation and load: A general theory of contact mechanics,”Phys. Rev. Lett., vol. 99, p. 125502, Sep 2007

    2007

  49. [57]

    Isothermal squeeze films,

    W. Langlois, “Isothermal squeeze films,” Quarterly of Applied Mathematics, vol. 20, no. 2, pp. 131–150, 1962

    1962

  50. [58]

    An overview of thermal necro- sis: present and future,

    M. Mediouni, T. Kucklick, S. Poncet, R. Madiouni, A. Abouaomar, H. Madry, M. Cucchiarini, B. Chopko, N. Vaughan, M. Arora, K. G¨ okku¸ s, L. P. C. Mario Lozoya Lara, A. Volosnikov, M. Hesmati, and K. Ho, “An overview of thermal necro- sis: present and future,”Current Medi- cal...

    2019

Pith tools

Reviewed August 7, 2026 · model on record in the stance chip above.