Cellular structure of the healthy and keratoconic human cornea imaged in-vivo with sub-micrometer axial resolution OCT (Conference Presentation)

Author(s):  
Kostadinka Bizheva ◽  
Bingyao Tan ◽  
Erik Mason ◽  
Kirsten Carter ◽  
Lacey Haines ◽  
...  
Author(s):  
Zohreh Hosseinaee ◽  
Bingyao Tan ◽  
Kirsten Carter ◽  
Denise Hileeto ◽  
Luigina Sorbara ◽  
...  

2017 ◽  
Vol 8 (2) ◽  
pp. 800 ◽  
Author(s):  
Kostadinka Bizheva ◽  
Bingyao Tan ◽  
Benjamin MacLelan ◽  
Olivera Kralj ◽  
Mojtaba Hajialamdari ◽  
...  

2012 ◽  
Vol 53 (4) ◽  
pp. 2354 ◽  
Author(s):  
Johan Germundsson ◽  
Per Fagerholm ◽  
Marina Koulikovska ◽  
Neil S. Lagali

2018 ◽  
Vol 8 (1) ◽  
pp. 1-12 ◽  
Author(s):  
Shijun Sung ◽  
Alex Li ◽  
Sophie X. Deng ◽  
Elliott Brown ◽  
Warren S. Grundfest ◽  
...  

1992 ◽  
Vol 165 (1) ◽  
pp. 169-181 ◽  
Author(s):  
James V. Jester ◽  
W. Matthew Petroll ◽  
Randa M. R. Garana ◽  
Michael A. Lemp ◽  
H. Dwight Cavanagh

1993 ◽  
Vol 15 (2) ◽  
pp. 122-133 ◽  
Author(s):  
Jørgen Arendt Jensen ◽  
Jan Mathorne ◽  
Torben Gravesen ◽  
Bjarne Stage

An algorithm for deconvolution of medical ultrasound images is presented. The procedure involves estimation of the basic one-dimensional ultrasound pulse, determining the ratio of the covariance of the noise to the covariance of the reflection signal, and finally deconvolution of the rf signal from the transducer. Using pulse and covariance estimators makes the approach self-calibrating, as all parameters for the procedure are estimated from the patient under investigation. An example of use on a clinical, in-vivo image is given. A 2 × 2 cm region of the portal vein in a liver is deconvolved. An increase in axial resolution by a factor of 2.4 is obtained. The procedure can also be applied to whole images, when it is ensured that the rf signal is properly measured. A method for doing that is outlined.


2015 ◽  
Vol 48 (1) ◽  
pp. 38-43 ◽  
Author(s):  
M.A. Lago ◽  
M.J. Rupérez ◽  
F. Martínez-Martínez ◽  
C. Monserrat ◽  
E. Larra ◽  
...  

2005 ◽  
Vol 46 (10) ◽  
pp. 3616 ◽  
Author(s):  
Sean G. Every ◽  
John P. Leader ◽  
Anthony C. B. Molteno ◽  
Tui H. Bevin ◽  
Gordon Sanderson

Author(s):  
Catherine E. Frisch ◽  
Hirohito Kobayashi ◽  
Ray Vanderby

Damage to connective tissue such as tendons can occur via stretch injuries. During stretch injury, a tendon experiences permanent subfailure damage. Provenzano et al. showed that irreversible damage to the cellular structure of tendon or ligament occurs before noticeable changes can be measured in the mechanical behavior of the tissue [1]. The same paper also showed that during loading a portion of the curve can be classified as a sub-damage region where repeated loading in that range will have no effect on mechanical properties. There is also a damage region where plastic deformation and fiber tearing occurs. In this region, the severity of damage increases as the amount of strain increases. For the same level of functional loading after damage, tissue stiffness decreases while tissue strain increases. In-vivo measurements of damage indicators, such as strain and stiffness of a tendon, prove difficult using current techniques, since many of those methods are invasive (implanted strain gages) or large and non-portable (MRI)[2]. Recent studies have shown that ultrasound can be employed to assess ligaments and tendons by measuring ultrasound wave velocity and echo reflection [3,4].


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