University of Utah Research Foundation

Braingate Co., LLC

Albion Instruments, Inc.

Biomaterials International, Inc.

Richard A Van Wagenen

Joseph D Andrade

J Christopher Flaherty

Dwayne Ronald Westenskow

Robert E Benner

Donald E Gregonis

Dennis L Coleman

Jeffrey D Geisler

Almut Branner

Christine Decaria

Christopher Smith

Nephi Harvey

A system and method for an improved biological interface system that processes multicellular signals of a patient and controls one or more devices is disclosed. The system includes a sensor that detects the multicellular signals and a processing unit for producing the control signal based on the multicellular signals. The system may include improved communication, self-diagnostics, and surgical insertion tools.

Biological interface system

The concentration of multiple polyatomic gases are determined simultaneously by Raman light scattering. The gas sample is placed in a sampling cell and a polarized laser beam is passed through the cell, along a longitudinal axis. A portion of the light scattered by the gas sample is captured and detected by means of multiple collection optics-filter-detector channels. The scattered light exits the gas cell via windows located in the sides of the gas cell and enters the collection channels which are aligned with the cell windows. The cell windows are along the longitudinal axis of the laser beam and gas cell. Light scattered by the gas sample provides signals of both inelastic Raman scattered light and elastic laser scattered light which are directed to the collection channels. The optics of each channel transports the scattered light signals onto a laser line rejection filter where the elastic scattered laser signals are attenuated. The remaining inelastic Raman scattered signals are caused to be incident upon an interference filter which is specific to the transmission of one or more specific Raman lines. The interference filter in each collection channel is selected to a specific wavelength which is characteristic of Raman scattering from a particular polyatomic gas. The optical signals representative of these specific Raman lines passing through the interference filters are sensed by optical detectors, and amplified and converted into digital electrical pulses which are processed into simultaneous visual readouts indicative of the identity and concentration of each of the polyatomic gas molecules present in the sample of gas being analyzed.

Multi-channel molecular gas analysis by laser-activated Raman light

A sample gas cell and casing system for use in sampling and analysis of gas samples by Raman light scattering comprises a tubular casing means forming a longitudinal bore, a gas sampling cell transversely mounted in the tubular casing means relative to the longitudinal bore with the gas sampling cell protruding at either end through the tubular casing. The gas cell has opposing windows at the ends which are located outside the tubular casing and are interconnected by a continuous sidewall passing through the casing. The end windows and sidewall define a longitudinal gas chamber having an axis perpendicular to the axis of longitudinal bore in the tubular casing. At least a portion of the continuous sidewall located inside the casing has window means through which scattered light may pass. The cell further contains inlet and outlet means communicating with the chamber to pass a sample gas through said cell. Light collection and/or reflection means are located relative to the side window means to collect and/or reflect Raman scattered light passing through the sidewall window means to a detection system.

Gas cell for raman scattering analysis by laser means

The concentration of multiple polyatomic gases are determined almost simultaneously by Raman scattering. The gas sample is placed in a sampling cell located in the resonance cavity of a laser and a polarized laser beam having sufficient intensity to produce detectable signals of Raman scattered light is passed through the cell. The scattered light is captured and redirected by means of a reflection mirror located parallel to the axis of the laser beam adjacent to and outside of the cell. Signals of both inelastic Raman scattered light and elastic laser scattered light are collected by a collection lens means opposite the reflection mirror and outside the gas cell. The collection lens is also parallel to the axis of the laser beam. The collected scattered signals are directed onto a laser line rejection filter where the scattered elastic laser signals are filtered out and the inelastic Raman scattered signals are transmitted to come in contact with a rotating filter wheel containing a series of interference filters with each filter being specific to the transmission of one Raman line. The Raman lines passing through the rotating filters are sensed sequentially by a single detector means and amplified and converted into digital electrical pulses which are processed and converted into visual readouts indicative of the concentration of each of the polyatomic molecules in the gas being determined.

Molecular gas analysis by Raman scattering in intracavity laser

A process is presented for conducting fluorescence immunoassays without the use of added labels by utilizing ultraviolet radiation and internal reflection optics to activate fluorescent groups present in the molecules of interest. The assay is accomplished by directing a beam of light having wavelengths in the ultraviolet region to a solid liquid interface which (1) has a material X immobilized thereon, and (2) is contacted with an assay solution containing in unknown Y which contains intrinsic tyrosine, tryptophan, nucleic acid or related fluorescence groups which are activated by wavelengths in the ultraviolet region; X and Y may be in the relationship of antibody and antigen in that one had the ability of recognizing the particular spatial and polar configuration of the other and is attracted to and bound to such configuration, said beam of ultraviolet light being projected under such conditions that there is internal reflection at the interface, and then measuring the amount of fluorescence emitted from the surface of the interface, the amount of the fluorescence emission being a function of the amount of the unknown Y being detected. In the event that Y is not fluorescent, the X-Y sandwich can be further exposed to a solution containing X, to form XYX sandwich. The observed fluorescence of X is proportional to the amount of bound Y which is in turn related to the solution concentration of Y.

Process for conducting fluorescence immunoassays without added labels

Growing community of inventors

Salt Lake City, UT, United States of America

Richard A Van Wagenen