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The mechanical properties of biological networks are often overseen in functional research of healthy tissue as well as in the diagnosis of potentially diseased tissue and in treatment monitoring. For example, in the classification of skin conditions (such as scars or burn wounds) and the following control of disease progression or healing, physicians in most cases prefer visual assessment and subjective scaling above quantitative mechanical information (Draaijers et al.; Durani et al.; Huang et al.; Gurtner et al. Moreover, tissue mechanics can be linked to a wide array of physiological processes (Cowin and Doty; Cowin and Humphrey; Butler et al.

Cells have very sophisticated methods to sense and adapt to their mechanical environment. Stem cells, for instance, have been proven to adapt their differentiation to the stiffness of their extracellular matrix (Swift et al.; Fu et al. ) and white blood cells, as well as tumor cells, are able to manipulate their own stiffness and shape to migrate in and out of blood vessels (Friedl and Wolf K. At the tissue level, the interplay between the cellular mechanics and the extracellular network determines the stiffness at the micron scale, changes of which have been associated with Alzheimer’s disease (Murphy et al. ) and multiple sclerosis (Wuerfel et al.; Streitberger et al. ) (in the brain), cancerous growth (Plodinec et al.; Li et al.

) (breast) and osteoarthritis (Stolz et al.; Desrochers et al. ) (cartilage). Hence, a method to quantify local mechanical properties of tissue, preferably in situ, is of high interest. Classically, the biomechanical response of complex networks is assessed by means of Atomic Force Microscope (AFM) nanoindentation (Hengsberger et al.; Franze; Zhu et al.; Mathur et al.; Li et al.; Gautier et al. The utilization of an AFM for classification of biological tissues has, however, some principle limitations that cannot be easily overcome, such as size, stability and flexibility. To mitigate those limitations, we have recently introduced a new probe, called ferrule-top cantilever, that provides a good alternative for indentation of biological samples in harsh environments (Chavan et al.; Kahn et al.; Neufurth et al. Both AFM and ferrule-top indentation are restricted to probing the surface of a sample, while the advantages of probing in depth (i.e. Plane And Spherical Trigonometry By William Hart Pdf Printer there. , underneath the surface) would clearly be multiple.

By integrating an indenter at the tip of a needle one could not only quantify between layers of different stiffness, but also navigate to the target location and perform a minimally invasive measurement based on the tissue mechanical properties. An example of an in situ AFM indenter for arthroscopic knee cartilage inspection was presented by Imer et al. The indenter consists of an extensive stabilization stage connected to a piezoelectric scanning module, both of which are inserted into the sample, resulting in a large footprint. Moreover, the lack of calibration of the piezoelectric tube hampered a quantitative analysis. Here, we demonstrate a ferrule-top indenter on the distal end of a rigid needle and we show its ability to quantify local mechanical properties of tissue in situ. Thanks to the remote actuation of the sensor by a piezoelectric translator the size of the needle is limited to the dimensions of the indentation probe at the tip. Download Soal Sbmptn Soshum 2013 Dan Pembahasannya.

The performance of our indenter is tested on an engineered layered sample as well as on biological tissue. 2 Experimental section. 1 Schematic view of the experimental setup, showing a microscope image of the indenter ( a), a closeup of the indentation module ( b), and a sketch of the complete needle insertion setup ( c) (not to scale) 2.2 Indentation module To reduce the dimensions of the indenter, we have developed an indentation module that enables remote actuation of the force transducer.