2020
DOI: 10.1038/s41598-020-75875-z
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Load-deformation characteristics of acellular human scalp: assessing tissue grafts from a material testing perspective

Abstract: Acellular matrices seem promising scaffold materials for soft tissue regeneration. Biomechanical properties of such scaffolds were shown to be closely linked to tissue regeneration and cellular ingrowth. This given study investigated uniaxial load-deformation properties of 34 human acellular scalp samples and compared these to age-matched native tissues as well as acellular dura mater and acellular temporal muscle fascia. As previously observed for human acellular dura mater and temporal muscle fascia, elastic… Show more

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Cited by 8 publications
(6 citation statements)
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References 27 publications
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“…One clamp was used for each side. Deviating from previous interlocking two-part designs [18][19][20][21], this new setup involved a single squeezing part with a central opening. The clamps consisted of a pattern of small 4-sided pyramids (design with flat pyramids, pyramid height = 0.75 mm, diagonal base = 2.12 mm).…”
Section: Methodsmentioning
confidence: 99%
“…One clamp was used for each side. Deviating from previous interlocking two-part designs [18][19][20][21], this new setup involved a single squeezing part with a central opening. The clamps consisted of a pattern of small 4-sided pyramids (design with flat pyramids, pyramid height = 0.75 mm, diagonal base = 2.12 mm).…”
Section: Methodsmentioning
confidence: 99%
“…In general, since the surgical sites of the stapedectomy and stapedotomy are closed or filled with fascia or fat, the properties of the closing materials in the simulations were determined as those of fascia or fat. According to previous studies, the Young's modulus of the fascia was reported to be in the range of 1-24 MPa (Trindade et al, 2012;Zwirner et al, 2020) whereas that of fat was reported to be about 1 kPa (Comley and Fleck, 2010a,b). In Figures 2B, D, the center of the prosthesis and footplate could be not perfectly aligned according to the calculation method to find the center of the asymmetric-oval shape.…”
Section: Stapes Tendonmentioning
confidence: 98%
“…3.8 × 10 3 (Gan et al, 2004) 1.2 × 10 3 (Homma et al, 2010) 0.15 Incus ligament 4.8 (Gan et al, 2004) 1.2 × 10 3 (Homma et al, 2010) 0.15 Tympanic membrane, pars tensa 2 × 10 1 (Homma et al, 2010) 1.2 × 10 3 (Koike et al, 2002) 0.7 Tympanic membrane, pars flaccida 7 (Homma et al, 2010) 1.2 × 10 3 (Koike et al, 2002) 0.15 Tympanic annulus 0.6 (Koike et al, 2002) 1.2 × 10 3 (Homma et al, 2010) 0.5 Stapes annular ligament 0.7 (Kim et al, 2014) 1.2 × 10 3 (Homma et al, 2010) 0.3 Round window 0.05 (Kim et al, 2014) 1.2 × 10 3 (Kim et al, 2014) 0.8 Cochlear bone 20 × 10 3 (Turner et al, 1999) 1.8 × 10 3 (Peterson and Dechow, 2003) 0.3 Cochlear fluid 1,500 [m/s; sound speed] ( Levin et al, 1981) 1 × 10 3 (Levin et al, 1981) 0.1 Basilar membrane 6.5-5.5 (longitudinally from base to apex) 0.2-1 × 10 3 (transversely from base to apex) (Kim et al, 2014) 1 × 10 3 (Kim et al, 2014) 0.3 Prosthesis 150 × 10 3 (Salvinelli et al, 2009) 21 × 10 3 (Salvinelli et al, 2009) 0.01 Closing materials 0.001, 1, 24 (Comley and Fleck, 2010a,b;Trindade et al, 2012;Zwirner et al, 2020) 1.2 × 10 3 (Ward and Lieber, 2005) 0.3…”
Section: Stapes Tendonmentioning
confidence: 99%
“…Inaccurate assessment of sample cross-sectional area can result in significant errors in the calculation of experimental tensile stresses and can thus influence experimentally-derived tissue mechanical properties. 92 Consequently, future studies should focus on the use of noncontact photogrammetry methods 37 or laser scanning methods 93,94 to determine sample cross-sectional area.…”
Section: Measurement Of Sample Geometries For Sample Stress Evaluationmentioning
confidence: 99%