WO2009045492A1 - Optical device components - Google Patents
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- WO2009045492A1 WO2009045492A1 PCT/US2008/011438 US2008011438W WO2009045492A1 WO 2009045492 A1 WO2009045492 A1 WO 2009045492A1 US 2008011438 W US2008011438 W US 2008011438W WO 2009045492 A1 WO2009045492 A1 WO 2009045492A1
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- light
- light beams
- target area
- lens
- collection system
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- 210000004369 blood Anatomy 0.000 claims abstract description 35
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- 206010012601 diabetes mellitus Diseases 0.000 description 14
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 description 10
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- WQZGKKKJIJFFOK-VFUOTHLCSA-N beta-D-glucose Chemical compound OC[C@H]1O[C@@H](O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-VFUOTHLCSA-N 0.000 description 1
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Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
- G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
- G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
- G01N21/359—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light using near infrared light
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
- G01N21/4738—Diffuse reflection, e.g. also for testing fluids, fibrous materials
- G01N21/474—Details of optical heads therefor, e.g. using optical fibres
Definitions
- a fundamental property of a sample is its tendency or lack of tendency to absorb or scatter light at certain wavelengths. Characterization of the tendency of a sample to absorb, scatter or transmit is the basis for many optical measurements and instrumentation (e.g., spectrophotometry). The accuracy and repeatability of measurements taken with optical devices relates to many factors, including the strength of signal reaching one or more detectors.
- Optical devices may be used to measure the presence and quantities of components in human or animal blood or interstitial fluid.
- a non-invasive optical apparatus may use some form of spectroscopy to acquire the signal or spectrum from a target area of a body of the user.
- Diabetes is a chronic disease that, when not controlled, over time leads to serious damage to many of the body's systems, including the nerves, blood vessels, eyes, kidneys and heart.
- NIDDK National Institute of Diabetes and Digestive and Kidney Diseases
- WHO World Health Organization
- a vital element of diabetes management is the self-monitoring of blood glucose (SMBG) concentration by diabetics in the home environment. By testing blood glucose levels often, diabetics can better manage medication, diet and exercise to maintain control and prevent the long-term negative health outcomes.
- SMBG blood glucose
- a non-invasive monitor will make testing multiple times each day pain-free and more palatable for children with diabetes. According to a study published in 2005 (J, Wagner, C. Malchoff, and G. Abbott, Diabetes Technology & Therapeutics, 7(4) 2005, 612 - 619), people with diabetes would perform SMBG more frequently and have improved quality of life with a non-invasive blood glucose monitoring device. [0007] There exist a number of non-invasive approaches for blood glucose determination.
- One technique of non-invasive blood chemicals detection involves collecting and analyzing light spectra data.
- Extracting information about blood characteristics such as glucose concentration from spectral or other data obtained from spectroscopy is a complex problem due to the presence of components (e.g., skin, fat, muscle, bone, interstitial fluid) other than blood in the area that is being sensed. Such other components can influence these signals in such a way as to alter the reading.
- the resulting signal may be much larger in magnitude than the portion of the signal that
- SLW Docket No. 2743.003WOI corresponds to blood, and therefore limits the ability to accurately extract blood characteristics information.
- Embodiments of the invention relate to. an apparatus including a light source to generate a plurality of light beams with each of the plurality of light beams having a different wavelength range.
- the apparatus also includes a light funnel to direct the plurality of light beams to the target area, an aperture to direct the plurality of light beams emitting from the target area to a lens, the lens configured to collect the light beams emitting from the target area.
- the apparatus includes a detector including a plurality of light-sensing devices each configured to detect a light beam and configured to generate an output signal indicative of an intensity of light detected and a processor for determining the blood characteristic as a function of each generated output signal.
- Embodiments relate to a light collection system, including a lens positioned adjacent a target area, an aperture positioned between the lens and target area and configured to direct a plurality of light beams emitting from the target area; and one or more filters,
- FIGS. IA-B illustrate plots of a pulse wave corresponding to light absorption of arterial blood, according to some embodiments.
- FIG. 2 illustrates an optical configuration, according to some embodiments.
- FIG. 3 illustrates an existing optical configuration for performing optical measurements of a biological sample, according to some embodiments.
- FIGS. 4A-B illustrate optical configurations for performing optical measurements of a biological sample, according to some embodiments.
- FIG. 5 illustrates a cross sectional view of a light funnel, according to some embodiments.
- FIG. 6 illustrates components of the light source, according to some embodiments.
- FIG. 7 illustrates a cross-sectional view of a light funnel with an infrared emitting diode (IRED) array matrix disposed therein, according to some embodiments.
- IRED infrared emitting diode
- Embodiments of the present invention relate to optical components, such as light funnels for illumination and measurement of optical properties of a sample.
- SLW Docket No. 2743.003WOI 4 body regions are exemplified, the embodiments relate to all types of optical instrumentation, including optical detectors, microscopes, spectrometers, etc.
- Optical spectroscopy can be used to determine the amount of light absorbed by a biological sample such as human finger. By measuring the amount of light absorbed by the finger, it is possible to determine glucose, cholesterol, and hemoglobin levels of a person non-invasively. Fingertip measurements are usually preferred because of the large concentration of capillaries in the fingertip and because of the conversion of arterial blood into venous blood that occurs in the fingertip.
- FIG. IA depicts a plot 102 of a pulse wave that corresponds to the light absorption of arterial blood in the capillary due to the heartbeat of the user.
- the magnitude of the cyclic pattern is small in comparison to the total photocurrent generated by the detector, considerable information can be extracted from the cyclic pattern of the plot 102.
- the plot will have a maximum or peak 104 reading and minimum or valley 106 reading.
- the peak 104 reading of the plot corresponds to when there is a minimum amount of blood in the capillaries
- the valley 106 reading corresponds to when there is a maximum amount of blood in the capillaries.
- the transmittances corresponding to the peak and valley photo currents can be defined as:
- the baseline noise of the device being used to measure the light absorption by the finger should not be larger than 3.0 ⁇ 10 "5 in absorbance (peak to peak), within a 10 Hz bandwidth.
- a 3.0 x 10 "5 absorbance (peak to peak) baseline noise level within a 10 Hz bandwidth is difficult to obtain with the low light power levels that are used by some battery powered hand held non-invasive blood
- SLW Docket No. 2743.003WOI 6 chemicals measurement devices One solution involves increasing light illumination power. However, due to size limitations of some devices, it may not be possible or it may be inefficient to increase illumination power to achieve a desired baseline noise level (e.g., battery drain). Thus, there is a need for a system and method to increase the amount light power that can be detected by such devices without significantly increasing device size and battery power consumption.
- FIG. 2 is a simplified block diagram that illustrates components of a current optical measurement system 200 that uses the "pulsatile" concept for determining an amount of light absorbed and scattered solely by the blood in a human finger.
- a power source 201 such as a battery, provides power to a light source 202 that generates a plurality of light beams 204, 206, 208, 210 that are directed toward the top of the finger of a user.
- each of the light beams 204, 206, 208, 210 have a different wavelength or a different wavelength range, typically within 800 ran to 1600 nm.
- the first light beam 204 may have a wavelength range between 850-900 nm
- the second light beam 206 may have a wavelength range between 875-940 nm
- the third light beam 208 may have a wavelength between 920-980 nm
- the fourth light beam 210 may have a wavelength between 950-1050 nm.
- the optical measurement system 200 is described herein as generating four (4) light beams, it is contemplated that the light source 202 can be altered to generate fewer light beams or additional light beams in other embodiments.
- a first aperture 212 ensures that the light beams 204, 206, 208, 210 strike a target area of the finger.
- a second aperture 214 ensures that the portion of the light beams that are transmitted through the finger strike a lens 216.
- Light beams 204, 206, 208, 210 are attenuated by the finger and components of the optical measurement system 200, and, thus, attenuated light beams 218, 220, 222, 224 are emitted from the finger.
- the attenuated light beams 218, 220, 222, 224 strike the lens 216, and the lens 216 collects the attenuated light beams 218, 220, 222, 224 so that they impinge more efficiently on a detector block 226.
- the detector block 226 is positioned directly under the lens 216 and comprises a plurality of light-sensing devices (LSD) 228, 230, 232, 234 such
- each of the light-sensing devices 228, 230, 232, 234 detects a specific wavelength of light as defined by corresponding interference filters (IF) 236, 238, 240, 242, respectively.
- the interference filter transmits one or more spectral bands or lines of light, and blocks others.
- Each of the light-sensing devices 228, 230, 232, 234 generates a corresponding current signal that is proportional to the power of the light received by the particular light sensing device.
- the current signal generated by the photodiode can be converted to another form of signal, such as an analog voltage signal or a digital signal.
- a processor 243 is coupled to the detector block 226 and is configured to calculate the change of photo current signals 244, 246, 248, 250. [0041] According to one aspect, the processor 243 executes an algorithm such as shown in the equation (5) to calculate the change in the light absorption ( ⁇ A) solely caused by the blood in the finger. Thereafter, this quantitative calculation of light absorption of the blood can be used to determine a characteristic of the blood. For example, by comparing the calculated light absorption value to predetermined values corresponding to different glucose levels stored in a memory (not shown), a glucose level of the user can be determined.
- An Infrared Emitting Diode (“IRED") block 302 includes a plurality of IREDs that generate near infrared (“NIR”) radiation or light beams from 850 nm to 1100 nm.
- the generated NIR light beams enter an entrance aperture 304 and pass through the finger.
- the NIR light beams transmitted through the finger pass through an exit aperture 306 onto a lens 308.
- the lens 308 collimates light beams and projects them onto filter array 310 and then detector array 312.
- the apparatus also includes a wall housing 314 to prevent stray light from reaching the light detectors.
- the light beams passing through the exit aperture 306 are completely mixed in wavelength. More specifically, the entire light power distribution from 850 nm to 1100 nm is transmitted to every detector in the detector array 312.
- the total usable power is approximately five (5) mW (e.g., 4 x 2.5 mW x .50) for the entire wavelength range covered by the four IREDs, typically 850 nm to 1 100 nm.
- the light that enters the finger will be attenuated by skin, fat, muscle, blood, and bone.
- absorption and scattering of light by the human finger can reduce the power of transmitted light within the NIR region of 850 nm to 1100 nm by a factor of approximately 200.
- the total IR power transmitted through the finger is approximately only 25 microwatts ( ⁇ W) (e.g., 5mW/200) in the entire wavelength region covered by the four IREDs, typically 850 nm to 1 100 nm.
- SLW Docket No. 2743.003WOI 9 aperture 306 cannot be treated as a point source.
- the total light power collected using optical layout shown in Fig. 3 is only about 10%, or a power reduction by a factor of 10 to 2.5 ⁇ W within the entire wavelength region covered by the four IREDs, typically 850 nm to 1100 nm. Note that this is the optical power sent to all detectors in FIG. 3.
- optical systems such as shown in FIG. 3, may require as many as twenty (20) to thirty (30) diode detectors to obtain accurate information regarding chemical components in blood. Therefore, the light power goes to each detector will be about 125 nW or less.
- the interference filter placed on top of each detector typically has a full width at half maximum (FWHM) bandwidth of 10 nm, which reduces the light power by a factor of 25 to 5 nW, assuming a uniform power distribution across the entire wavelength region from 850 nm to 1100 nm. Furthermore, the peak transmittance of each interference filter is about 50% or less. Accordingly, the light power received by each detector is reduced to about 2.5 nW or less.
- FWHM full width at half maximum
- the photoelectric conversion efficiency for Silicon Diode detectors ranges from 0.1 amps/watts (AAV) at 1100 nm to about 0.5 AAV at 900 nm.
- AAV amps/watts
- the photocurrent produced by each detector is between 0.25 nano-amps or less (nA) to 1.25 nA or less for each detector.
- the corresponding high end shot noise, within 10 Hz bandwidth, is about 2.0 x 10 "4 Absorbance (p- p) or larger, which is over a factor of 6 of what is required for accurate determination of the value of ⁇ A, as defined by equation (5), with an S/N ratio of 100.
- FIG. 4 A illustrates an optical configuration for performing optical detection of a biological sample according to one aspect of the present optical measurement system 400.
- a light source 402 generates a plurality of
- each of the light beams 404, 406, 408, 410 have a different wavelength or a different wavelength range.
- the first light beam 404 may have a wavelength range between 850 - 920 nm
- the second light beam 406 may have a wavelength range between 900 - 980 nm
- the third light beam 408 may have a wavelength between 970 - 1050 nm
- the fourth light beam 410 may have a wavelength between 1030-1100 nm.
- the total wavelength range may include from about 800 nm to about 1600nm, for example.
- the optical measurement system 400 is described herein as generating four (4) light beams, it is contemplated that the light source can be altered to generate fewer light beams or additional light beams in other embodiments.
- the light beams 404, 406, 408, 410 from the light source 402 enter a light illumination funnel 412 through an entrance opening 414 and exit the light illumination funnel 412 through an exit opening 416.
- the diameter of the exit opening 416 of the light illumination funnel 412 is smaller than or equal to the diameter of the entrance opening 414.
- the diameter of the entrance opening 414 is approximately 0.625 (5/8) inches and the diameter of the exit opening 416 is approximately 0.25 (1/4) inches.
- the light illumination funnel 412 focuses the light beams 404, 406, 408, 410 in the same general direction toward the top of the finger of a user.
- the light illumination funnel may significantly increase the total light power received by the target area in comparison to the configuration of FIG. 3, and therefore substantially increase the Signal-to-Noise Ratio.
- FIG. 5 depicts a cross sectional view of the light illumination component or funnel 412.
- the light illumination funnel 412 has a substantially cylindrical outer wall 502 with diameter Dl, and a central cavity defined by an inner wall 506 that is of a frusto-conical shape and two light entrance/exit openings 508 and 504.
- the opening 508 (second opening) has a smaller diameter, D3, and opening 504 (first opening) has a larger diameter, D2.
- the separation distance between the two light openings is L
- the Half Angle of the frusto-conical shape of the inner surface is ⁇ .
- the value of Half Angle ⁇ ranges from 10 to 15 degrees.
- the Half Angles may be less than about 25 degrees, for example.
- the light illumination funnel 412 may be formed from plastic, metal or other suitable material or compound/layers of material, with any desired refractive index(es). According to one aspect, the light illumination funnel 412 is formed from metal and the surface of inner wall 506 is made highly reflective. When configured properly, the light intensity at the exit 508 may be increased by a factor of 50 to 100 over the light intensity at the entrance 504. [0054] FIG. 6 depicts components of the light source 402 according to one aspect of the optical measurement system 400.
- a circuit board may be positioned near or in contact with the first opening of the funnel and may include light sources mounted on or in contact with the board.
- a plurality of IREDs 602, 604, 606, and 608 are mounted to a printed circuit board (PCB) 610.
- the PCB 610 receives electric power through a power line 612 that is connected to a power source (e.g., power source 201) such as a battery.
- a power source e.g., power source 201
- each of the IREDs 602, 604, 606, and 608 receives power and generates a plurality of light beams (e.g., light beams 404, 406, 408, 410).
- IREDs with similar operational current can be connected in series to increase battery life.
- the light source may be mounted within the funnel or above the funnel, such as by being surrounded by a housing, for example.
- the light illumination funnel 412 may be mounted to the PCB 610 via screws, posts or other connecting means.
- the frusto-conical shape of the inner surface of the light illumination funnel 412 serves to concentrate and focus the light beams 404, 406, 408, 410 from the IREDs 602, 604, 606, 608 into a generally conical beam toward the finger.
- FIG. 7 depicts cross-section view of another embodiment of the light illumination funnel 412 with a three-dimensional (3-D) IRED array matrix 702 disposed therein.
- Multiple light sources, such as IREDs may be positioned in three-dimensional layers and arranged to optimize light intensity.
- the light sources may be positioned in horizontal and vertical layers, for example. According to this embodiment, there are a total of twenty six (26) IREDs included in the 3-D array matrix.
- the IREDs are arranged in four (4) layers.
- a second layer, as indicated by 706, includes five (5) IREDs (two IREDs not shown), a third layer, as indicated by 708, includes seven (7) IREDs (four IREDs not shown), and a fourth layer, as indicated by 710, includes ten (10) IREDs (six IREDs not shown).
- Power line 712 provides power for all IREDs. According to other embodiments, other IRED patterns may also be utilized. Any number of light sources or layers may be utilized to optimize the light intensity. [0057] Because IREDs are optically transparent to infrared lights, the light loss due to blocking effect within the funnel cavity should be low and the structure shown in FIG.
- the total light power transmitted through the 0.25-inch diameter of the exit opening 416 of the light illumination funnel 412 should be approximately 55 mW (e.g., 26 x 2.5 mW x 0.85). Therefore, the total light power transmitted through the 0.25 inch opening above the finger in present optical measurement system 400 is approximately eleven (11) times of the corresponding power reached at the aperture 306 (e.g., 5mW) of the configuration described in reference to FIG. 3. Moreover, the increased light power received at the finger will increase the amount of light power that can be transmitted through the finger and, thus, increases the light power that can be detected at the detector block 428.
- light beams 404, 406, 408, 410 are attenuated by the finger and components of the optical measurement system 400.
- the attenuated light beams then pass an exit aperture 418, collected by an aspheric lens 430.
- the beams 432 exiting the lens 430 may then pass through filters 426 to detectors 428.
- the major advantage of using an aspheric lens 430 for light collection is its much larger solid angle for light collection.
- the total light power received by each detector may be increased by a factor 3 to 4 when an aspheric lens 430 is used for collecting light emitted from the target area in comparison to the light collection configuration shown in FIG. 3.
- the combination of utilizing a light illumination funnel 412 and an aspheric lens 430 as light collector may increase the light power received by each detector by about 20 to about 40 times in comparison to the optical configuration shown in FIG. 3
- the detector block 428 is positioned beneath the aspheric lens
- each of the light-sensing devices detects a specific wavelength of light as defined by a corresponding interference filter 426 placed on top of the detector.
- a processor e.g., processor 243 can be coupled to the detector block 428 and configured to calculate a change of current signals generated by the light sensing devices. For example, as described above in reference to FIG. 2, the processor 243 executes an algorithm such as shown in equation (5) to calculate the change in the light absorption ( ⁇ A) solely caused by the blood in the finger. Thereafter, this quantitative calculation of light absorption of the blood can be used to determine a characteristic of the blood.
- FIG. 4B illustrates another optical configuration for performing optical detection of a biological sample according to one aspect of the present optical measurement system 400.
- a light source 402 generates a plurality of light beams 404, 406, 408, 410.
- the light source 402 may be incandescent light sources or infrared emitting diodes, for example.
- each of the light beams 404, 406, 408, 410 have a different wavelength or a different wavelength range.
- the first light beam 404 may have a wavelength range between 850 - 920 nm
- the second light beam 406 may have a wavelength range between 900 - 980 nm
- the third light beam 408 may have a wavelength between 970 - 1050 nm
- the fourth light beam 410 may have a wavelength between 1030-1100 nm.
- the total wavelength range may include from about 800 nm to about 1200nm, for example.
- the optical measurement system 400 is described herein as generating four (4) light beams, it is contemplated that the light source can be altered to generate fewer light beams or additional light beams in other embodiments.
- the light beams 404, 406, 408, 410 from the light source 402 enter a light illumination funnel 412 through an entrance opening 414 and exit the light illumination funnel 412 through an exit opening 416.
- the diameter of the exit opening 416 of the light illumination funnel 412 is smaller than or equal to the diameter of the entrance opening 414.
- the diameter of the entrance opening 414 is approximately 0.625
- the light illumination funnel 412 focuses the light beams 404, 406, 408, 410 in the same general direction toward the top of the finger of a user.
- the light illumination funnel may significantly increase the total light power received by the target area in comparison to the configuration of FIG. 3, and therefore substantially increase the Signal-to-Noise Ratio.
- light beams 404, 406, 408, 410 are attenuated by the finger and components of the optical measurement system 400.
- the attenuated light NIR beams then pass an exit aperture 418, collected by a condenser lens 420, and projected onto a transmission grating device 422.
- the transmission diffraction grating 422 angularly resolves the various wavelength components of the mixed NIR light beams into a spectrum with wavelength increasing monotonically in the direction depicted by the arrow. In other words, because the diffraction angle of a particular light beam depends on the wavelength of the light beam, each of the light beams can be separated by wavelength.
- the optical spectrum 424 comes out from the transmission diffraction grating 422 is then narrowed down by interference filter array 426 and detected by diode array 428.
- the center wavelength of each interference filter in the filter array 426 is arranged to increase monotonically to coincide with corresponding wavelength component of the spectrum come from the transmission diffraction grating 422.
- the approach utilizing transmission diffraction grating will send each detector only the wavelength components near the center wavelength of the corresponding filter.
- the combination of utilizing a light illumination funnel 412, an aspheric lens 420 as light collector, and a transmission grating 422 as wavelength separation device may increase the light power received by the photodiodes by about 100 to about 200 times in comparison to the optical configuration shown in FIG. 3
- Embodiments of the invention may also include methods of using the apparatus as describe above or a light collection system,
- a light source may contact a target through an illumination funnel, sufficient to generate transmitted, transflected or reflected light.
- the transmitted, transflected or reflected light may enter a light collection system and be directed to one or more detectors, for example.
Abstract
Description
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Priority Applications (8)
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US9788764B2 (en) | 2008-05-22 | 2017-10-17 | St. Louis Medical Devices, Inc. | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
US8340738B2 (en) | 2008-05-22 | 2012-12-25 | The Curators Of The University Of Missouri | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
US9877670B2 (en) | 2008-05-22 | 2018-01-30 | St. Louis Medical Devices, Inc. | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
US10070809B2 (en) | 2008-05-22 | 2018-09-11 | St. Louis Medical Devices, Inc. | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
US10080515B2 (en) | 2008-05-22 | 2018-09-25 | St. Louis Medical Devices, Inc. | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
CN102083360A (en) * | 2008-05-22 | 2011-06-01 | 密苏里大学董事会 | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
US10959650B2 (en) | 2008-05-22 | 2021-03-30 | St. Louis Medical Devices, Inc. | Method and system for non-invasive optical blood glucose detection utilizing spectral data analysis |
EP2413784A1 (en) * | 2009-04-01 | 2012-02-08 | The Curators Of The University Of Missouri | Optical spectroscopy device for non-invasive blood glucose detection and associated method of use |
EP2413784A4 (en) * | 2009-04-01 | 2014-01-22 | Univ Missouri | Optical spectroscopy device for non-invasive blood glucose detection and associated method of use |
WO2010114736A1 (en) | 2009-04-01 | 2010-10-07 | The Curators Of The University Of Missouri | Optical spectroscopy device for non-invasive blood glucose detection and associated method of use |
US8552359B2 (en) | 2009-04-01 | 2013-10-08 | The Curators of the Univesity of Missouri | Optical spectroscopy device for non-invasive blood glucose detection and associated method of use |
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EP2198268B1 (en) | 2022-03-16 |
HK1151351A1 (en) | 2012-01-27 |
CA2700996C (en) | 2016-12-13 |
CN101903757B (en) | 2012-08-29 |
CN101903757A (en) | 2010-12-01 |
BRPI0818177B1 (en) | 2022-09-27 |
EP2198268A1 (en) | 2010-06-23 |
JP2010540964A (en) | 2010-12-24 |
AU2008307505A1 (en) | 2009-04-09 |
AU2008307505B2 (en) | 2013-01-31 |
RU2478197C2 (en) | 2013-03-27 |
RU2010117396A (en) | 2011-11-10 |
BRPI0818177A2 (en) | 2022-01-18 |
CA2700996A1 (en) | 2009-04-09 |
EP2198268A4 (en) | 2016-04-06 |
US7809418B2 (en) | 2010-10-05 |
US20090105565A1 (en) | 2009-04-23 |
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