Ohio University

Lyn Bowman

Jarlath McEntee

Emily R Ellerbrock

Patricia A Arnold

David M Berchowitz

Anne B Loucks

John R Cotton

Joseph Oberhauser

Israel Urieli

Parametric model based computer implemented methods for determining the stiffness of a bone, systems for estimating h the stiffness of a bone in vivo, and methods for determining the stiffness of a bone. The computer implemented methods include determining a complex compliance frequency response function Y(f) and an associated complex stiffness frequency response function H(f) and independently fitting a parametric mathematical model to Y(f) and to H(f), and using a first measure of conformity and a second measure of conformity of the collected data to determine accuracy and repeatability of measurements. The systems include a device for measuring the stiffness of the bone in vivo and a data analyzer to determine a complex compliance frequency response function Y(f) and an associated complex stiffness frequency response function H(f).

Methods for establishing the stiffness of a bone using mechanical response tissue analysis

Parametric model based computer implemented methods for determining the stiffness of a bone and systems for estimating the stiffness of a bone in vivo. The computer implemented methods include determining a complex compliance frequency response function Y(f) and an associated complex stiffness frequency response function H(f) and independently fitting a parametric mathematical model to Y(f) and to H(f). The systems include a device for measuring the stiffness of the bone in vivo and a data analyzer to determine a complex compliance frequency response function Y(f) and an associated complex stiffness frequency response function H(f).

Systems and methods for establishing the stiffness of a ulna bone using mechanical response tissue analysis

Methods of patient-specific modeling of the mechanical properties of bone and related systems. The methods include obtaining a bending stiffness (K) of a bone specimen non-invasively and non-destructively in a dynamic 3-point bending test, creating a mathematical mechanical model of the bone specimen, assigning an elastic modulus (E) to the bone specimen of the mathematical mechanical model, determining the flexural rigidity of the bone specimen from simulating the mathematical mechanical model, determining a discrepancy between the flexural rigidity of the bone specimen from the simulated mechanical model and based on the obtained K, adjusting the elastic modulus of the simulated mechanical model to minimize the discrepancy, adjusting the elastic modulus until an optimized elastic modulus is determined where the discrepancy is reduced below a predetermined threshold, and applying the optimized elastic modulus to the simulated mechanical model to determine a strength of the bone.

Systems and methods for patient specific modeling of the mechanical properties of bone

Parametric model based computer implemented methods for determining the stiffness of a bone, systems for estimating the stiffness of a bone in vivo, and methods for determining the stiffness of a bone. The computer implemented methods include determining a complex compliance frequency response function Y(f) and an associated complex stiffness frequency response function H(f) and fitting a parametric mathematical model to Y(f) and to H(f). The systems include a device for measuring the stiffness of the bone in vivo and a data analyzer to determine a complex compliance frequency response function Y(f) and an associated complex stiffness frequency response function H(f). The methods for determining the stiffness include fitting a parametric model to stiffness of the skin-bone complex as a function of frequency H(f) and the compliance of the skin-bone complex as a function of frequency Y(f).

Systems and methods for establishing the stiffness of a bone using mechanical response tissue analysis

A microminiature Stirling cycle engine or cooler is formed utilizing semiconductor, planar processing techniques. Such a Stirling cycle thermomechanical transducer has silicon end plates and an intermediate regenerator. The end plates are formed with diaphragms and backspaces, one end plate forming the expansion end and the opposite end plate forming the compression end, with the regenerator bonded in between. A control circuit apparatus is linked to the diaphragms for controlling the amplitude, phase and frequency of their deflections. The control circuit apparatus is adapted to operate the transducer above 500 Hz and the passages and the workspace, including those within the regenerator, expansion space and compression space, are sufficiently narrow to provide a characteristic Wolmersley number, which is characteristic of the irreversibilities generated by the oscillating flow of the working fluid in the workspace, below substantially 5 at the operating frequency above 500 Hz. Additionally, the amplitude of the vibrations of the diaphragm vibrations are sufficiently small to provide the working fluid a maximum Mach number below substantially 0.1 at an operating frequency above 500 Hz.

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Athens, OH, United States of America

Lyn Bowman